US20100198034A1 - Compact On-Body Physiological Monitoring Devices and Methods Thereof - Google Patents
Compact On-Body Physiological Monitoring Devices and Methods Thereof Download PDFInfo
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- US20100198034A1 US20100198034A1 US12/698,124 US69812410A US2010198034A1 US 20100198034 A1 US20100198034 A1 US 20100198034A1 US 69812410 A US69812410 A US 69812410A US 2010198034 A1 US2010198034 A1 US 2010198034A1
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Definitions
- the detection of the level of glucose or other analytes, such as lactate, oxygen or the like, in certain individuals is vitally important to their health.
- the monitoring of glucose is particularly important to individuals with diabetes. Diabetics may need to monitor glucose levels to determine when insulin is needed to reduce glucose levels in their bodies or when additional glucose is needed to raise the level of glucose in their bodies.
- Devices have been developed for continuous or automatic monitoring of analytes, such as glucose, in bodily fluid such as in the blood stream or in interstitial fluid.
- analytes such as glucose
- Some of these analyte measuring devices are configured so that at least a portion of the devices are positioned below a skin surface of a user, e.g., in a blood vessel or in the subcutaneous tissue of a user.
- Ease of insertion and use, including minimal user intervention and on-body size and height (or thickness) of such transcutaneous or percutaneous medical devices that are worn on the body are important in usability, wearability, and comfort during the device usage.
- power management as well as shelf life is important.
- Embodiments of the subject disclosure include devices and methods and kits for providing sensor electronics assembly including an analyte sensor for monitoring of analyte levels such as glucose levels over a sensing time period.
- Sensing time period may be determined by the analyte sensor life, for example, including, but not limited to about three days or more, about five days or more, or about seven days or more, or about fourteen days or more.
- Embodiments include methods, devices and systems for monitoring glucose levels and obtaining glucose measurements that are discreet, automated, minimally invasive and with reduced pain and repetition of glucose testing procedures to obtain multiple discrete measurements over the sensing time period. Also provided are kits.
- Embodiments further include a control unit, a control command generator coupled to the control unit to receive a control signal and to generate a control command based on a carrier signal, an antenna section coupled to the control command generator to transmit the control command with the carrier signal and to receive a backscatter response data packet using the carrier signal, and a receiver section coupled to the antenna section to process the received backscatter response data packet and to generate an output glucose data.
- a control unit a control command generator coupled to the control unit to receive a control signal and to generate a control command based on a carrier signal
- an antenna section coupled to the control command generator to transmit the control command with the carrier signal and to receive a backscatter response data packet using the carrier signal
- a receiver section coupled to the antenna section to process the received backscatter response data packet and to generate an output glucose data.
- Embodiments also include real time discrete glucose measurement data acquisition on-demand, as desired by the user or upon request, based on, for example, RFID data communication techniques for data transmission and acquisition from the analyte sensor/electronics assembly or the on-body patch device including the analyte sensor and the data processing and communication components provided in a compact, low profile housing and placed on the skin surface of the user.
- the analyte sensor in certain embodiments includes a portion that is transcutaneously positioned and maintained in fluid contact with an interstitial fluid under the skin surface continuously during the sensing time period as discussed above, for example.
- FIG. 1 shows a data monitoring and management system such as, for example, an analyte (e.g., glucose) monitoring system in accordance with certain embodiments of the present disclosure
- analyte e.g., glucose
- FIG. 2 illustrates a data monitoring and management system for real time glucose measurement data acquisition and processing in one aspect of the present disclosure
- FIG. 3 is a block diagram of a receiver/monitor unit such as that shown in FIG. 1 in accordance with certain embodiments;
- FIG. 4 is a block diagram of a reader device/receiver unit such as that shown in FIG. 2 in one aspect of the present disclosure
- FIG. 5 is an exemplary schematic of an on-body patch device including an integrated sensor and sensor electronics assembly for use in the monitoring systems of FIGS. 1 and 2 in one aspect of the present disclosure
- FIG. 6 is a block diagram of the integrated sensor and sensor electronics assembly for use in the monitoring systems of FIGS. 1 and 2 in another aspect of the present disclosure
- FIG. 7 is a schematic of the reader device/receiver unit for use in the monitoring systems of FIGS. 1 and 2 in accordance with one aspect of the present disclosure
- FIGS. 8A and 8B illustrate a top view and a side view, respectively, of antenna and electronic circuit layout of the on-body patch device including an sensor and sensor electronics assembly for use in the monitoring systems of FIGS. 1 and 2 in one aspect of the present disclosure
- FIG. 9 illustrates an exemplary circuit schematic of the on-body patch device including an sensor and sensor electronics assembly in accordance with aspects of the present disclosure
- FIG. 10A is a perspective view of the components of the on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure
- FIG. 10B is another perspective view of the components of the on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure
- FIG. 10C is another perspective view of the assembled on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure
- FIGS. 11A-11C illustrate circuit layouts for the sensor electronics assembly in the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIGS. 12A-12B illustrate pre-deployment and post insertion configurations of the insertion device for positioning the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIGS. 12C-12G illustrate cross sectional perspective views of the operation of the insertion device for deploying the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIGS. 13A-13B illustrate embodiments of a power supply switch mechanism including conductive plugs of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIGS. 13C-13E illustrate another configuration of the power supply switch mechanism including conductive pads of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIG. 14 illustrates a power supply switch mechanism including an internal switch with a push rod activation of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIG. 15 illustrates a power supply switch mechanism including introducer retraction trigger activation of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIG. 16 illustrates a power supply switch mechanism with a contact switch of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIGS. 17A-17B illustrate a power supply switch mechanism with a battery contact locking mechanism of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure
- FIGS. 18A-18B illustrate a power supply switch mechanism with a bi-modal dome switch of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- devices, systems, kits and methods for providing compact, low profile, on-body physiological parameter monitoring device (physiological parameters such as for example, but not limited to analyte levels, temperature levels, heart rate, etc), configured for single or multiple use over a predetermined time period, which provide a low profile geometry, effective power management, improved shelf life, and ease and comfort of use including device positioning, and activation.
- Embodiments include an on-body assembly including a transcutaneously positioned analyte sensor and sensor electronics in a compact, low profile integrated assembly and coupled to an insertion device for deployment.
- Embodiments include continuous glucose monitoring (CGM) system or routines or functions for execution operations to continuously or semi-continuously monitor an analyte level such as glucose level with the transcutaneously positioned analyte sensor, where the real time analyte measurements are provided to a data receiver unit, a reader device, a data repeater or relay device such as data processing module, a data processing terminal or a remote terminal for data processing automatically upon data sampling at predetermined time intervals or based on programmed or programmable data transmission schedule.
- Data processing may include display, storage, execution of related alarm or notification functions, and analysis such as generating charts or graphs based on, for example, the monitored analyte levels received from the sensor/sensor electronics assembly.
- Embodiments further include analyte data acquisition in real time where the analyte level detected by the transcutaneously positioned analyte sensor is stored either permanently or temporarily in a memory or storage unit of a data processing unit or an integrated sensor and data processing unit assembly, such as an on-body patch device (stored for example, for about one day or less, or for about 10 hours or less, or for about 5 hours or less, or for about 3 hours or less, or for about one hour or less).
- the receiver unit or the reader device may be used to acquire the detected analyte level in real time, and/or on-demand or upon request using, for example, RFID communication protocol or other suitable data communication protocols.
- Sampled analyte related data in certain embodiments are received by the receiver unit or the reader device upon activation or initiation by the user or the patient, for example, of a switch or other initiation mechanism to initiate the data transfer or provide data request command.
- a switch or other initiation mechanism to initiate the data transfer or provide data request command.
- Such activation switch or mechanism may be provided or included in the user interface of the reader device or the receiver unit.
- Embodiments of the present disclosure relate to methods and devices for detecting at least one analyte such as glucose in body fluid.
- Embodiments include glucose measurements by an on-body patch device that includes a transcutaneously positioned analyte sensor in fluid contact with the body fluid such as interstitial fluid, and sensor electronics in signal communication with the analyte sensor, where the on-body patch device is configured to transmit one or more signals or data packets associated with a monitored analyte level upon detection of a reader device or the receiver unit of the analyte monitoring system within a predetermined proximity for a period of time (for example, about 10 seconds or less, or preferably about 5 seconds or less, or preferably about 2 seconds or less, or until a confirmation, such as an audible notification, is output on the reader device/receiver unit indicating successful acquisition of the analyte related signal from the on-body patch device).
- a period of time for example, about 10 seconds or less, or preferably about 5 seconds or less, or
- a radio frequency source within the reader device/receiver unit may be configured to provide RF power to the on-body patch device.
- the on-body patch device in one embodiment may be configured to generate an output signal (e.g., an RF signal) and transmit it to the reader device/receiver unit which includes, among others data indicating the glucose measurement.
- the signal communication and/or RF power transmission may initiate automatically upon detection of the reader device/receiver unit within a predetermined proximity to the on-demand patch device, or alternatively the reader device/receiver unit may require a user activation or confirmation prior to initiating signal communication and/or RF power transmission with the on-body patch device as discussed above.
- the transmitted data from the on-body patch device to the reader device/receiver unit may include glucose trend information that was stored in the on-body patch device for a predetermined time period, since the initialization of the sensor and positioning it in fluid contact with the interstitial fluid, or since the last transmission of data to the reader device, or any one or more combinations of the above.
- the trend information may indicate the variation in the monitored glucose level over the particular time period based on signals received from the analyte sensor and stored in the on-body patch device.
- the on-body patch device may optionally include an output component such as a speaker, a light indicator (for example, an LED indicator), or the like to provide one or more indications associated with its functions such as a successful transmission of data to the reader device or the receiver unit, alarm or alert conditions associated with its internal components, or a detection of the RF power received from the reader device or the receiver unit, for example.
- an output component such as a speaker, a light indicator (for example, an LED indicator), or the like to provide one or more indications associated with its functions such as a successful transmission of data to the reader device or the receiver unit, alarm or alert conditions associated with its internal components, or a detection of the RF power received from the reader device or the receiver unit, for example.
- one or more exemplary output indication may include an audible sound (including for example, a short tone, a changing tone, multi-tone, one or more programmed ringtones or one or more combinations thereof), a visual indication such as a blinking light of the LED indicator, a solid light on the LED indicator maintained at a predetermined or programmed or programmable time period (for example, 5 seconds), each of which may be pre-programmed in the on-body patch device, or alternatively programmable by the user through the user interface of the reader device/receiver unit when in communication with the on-body patch device.
- an audible sound including for example, a short tone, a changing tone, multi-tone, one or more programmed ringtones or one or more combinations thereof
- a visual indication such as a blinking light of the LED indicator, a solid light on the LED indicator maintained at a predetermined or programmed or programmable time period (for example, 5 seconds), each of which may be pre-programmed in the on-body patch device, or
- the one or more output indications may be generated in the on-body patch device and presented to the patient or the user so that corrective action may be timely taken.
- the output indications may be additionally or alternatively presented or output on the reader device/receiver unit when, for example, the reader device/receiver unit is within range of the on-body patch device
- future or anticipated analyte levels may be predicted based on information obtained, e.g., the current analyte level, the rate of change of the analyte level and analyte trend information.
- Predictive alarms may be programmed or programmable in the reader device/receiver unit, or the on-body patch device, or both, and may be configured to notify the user of a predicted analyte levels that may be of concern in advance of the user's analyte level reaching the future level. This provides the user an opportunity to take corrective action.
- embodiments of the present disclosure relate to methods and devices for detecting at least one analyte such as glucose in body fluid.
- the present disclosure relates to the continuous and/or automatic in vivo monitoring of the level of an analyte using an analyte sensor.
- embodiments include analyte monitoring devices and systems that include an analyte sensor—at least a portion of which is positionable beneath the skin of the user—for the in vivo detection, of an analyte, such as glucose, lactate, and the like, in a body fluid.
- an analyte such as glucose, lactate, and the like
- Embodiments include wholly implantable analyte sensors and analyte sensors in which only a portion of the sensor is positioned under the skin and a portion of the sensor resides above the skin, e.g., for contact to a transmitter, receiver, transceiver, processor, etc.
- the sensor may be, for example, subcutaneously positionable in a patient for the continuous or periodic monitoring of a level of an analyte in a patient's interstitial fluid.
- Discrete monitoring includes the acquisition or reception of monitored analyte data where real time monitored analyte level information is received or acquired on demand or in response to a request to the on-body patch device including sensor and sensor electronics. That is, embodiments include analyte sensors and sensor electronics which sample and process analyte related information based on a programmed or programmable schedule such as every minute, every five minutes and so on. Such analyte monitoring routines may be reported or transmitted in real time to the receiver unit/reader device at the time of data sampling and processing.
- the continuously sampled analyte data and processed analyte related signals may be stored and transmitted to a remote location such as the receiver unit, data processing module, the data processing terminal, the reader device or the remote terminal in response to a request for such information from the remote location.
- the analyte level may be correlated and/or converted to analyte levels in blood or other fluids.
- an analyte sensor may be positioned in contact with interstitial fluid to detect the level of glucose, which detected glucose may be used to infer the glucose level in the patient's bloodstream.
- Analyte sensors may be insertable into a vein, artery, or other portion of the body containing fluid.
- Embodiments of the analyte sensors of the subject disclosure may be configured for monitoring the level of the analyte over a time period which may range from minutes, hours, days, weeks, or longer.
- analyte sensors such as glucose sensors, that are capable of in vivo detection of an analyte for about one hour or more, e.g., about a few hours or more, e.g., about a few days of more, e.g., about three or more days, e.g., about five days or more, e.g., about seven days or more, e.g., about several weeks or at least one month.
- Future analyte levels may be predicted based on information obtained, e.g., the current analyte level at time t 0 , the rate of change of the analyte, etc.
- Predictive alarms may notify the user of predicted analyte levels that may be of concern prior in advance of the analyte level reaching the future level. This enables the user an opportunity to take corrective action.
- Embodiments include transmission of the acquired real time analyte information on-demand from the user (using for example, the reader device/receiver unit positioned in close proximity to the low profile on-body patch device), storage of the acquired real time analyte information, and subsequent transmission based on retrieval from the storage device (such as a memory device).
- FIG. 1 shows a data monitoring and management system such as, for example, an analyte (e.g., glucose) monitoring system in accordance with certain embodiments of the present disclosure.
- analyte e.g., glucose
- FIG. 1 shows a data monitoring and management system such as, for example, an analyte (e.g., glucose) monitoring system in accordance with certain embodiments of the present disclosure.
- analyte e.g., glucose
- Analytes that may be monitored include, but are not limited to, acetyl choline, amylase, bilirubin, cholesterol, chorionic gonadotropin, creatine kinase (e.g., CK-MB), creatine, DNA, fructosamine, glucose, glutamine, growth hormones, hormones, ketones, lactate, peroxide, prostate-specific antigen, prothrombin, RNA, thyroid stimulating hormone, and troponin.
- concentration of drugs such as, for example, antibiotics (e.g., gentamicin, vancomycin, and the like), digitoxin, digoxin, drugs of abuse, theophylline, and warfarin, may also be monitored. In those embodiments that monitor more than one analyte, the analytes may be monitored at the same or different times.
- the analyte monitoring system 100 includes a sensor 101 , a data processing unit (e.g., sensor electronics) 102 connectable to the sensor 101 , and a primary receiver unit 104 which is configured to communicate with the data processing unit 102 via a communication link 103 .
- the sensor 101 and the data processing unit (sensor electronics) 102 may be configured as a single integrated assembly 110 .
- the integrated sensor and sensor electronics assembly 110 may be configured as an on-body patch device.
- the on-body patch device may be configured for, for example, RFID or RF communication with a reader device/receiver unit.
- the primary receiver unit 104 may be further configured to transmit data to a data processing terminal 105 to evaluate or otherwise process or format data received by the primary receiver unit 104 .
- the data processing terminal 105 may be configured to receive data directly from the data processing unit 102 via a communication link which may optionally be configured for bi-directional communication.
- the data processing unit 102 may include a transmitter or a transceiver to transmit and/or receive data to and/or from the primary receiver unit 104 , the data processing terminal 105 or optionally the secondary receiver unit 106 .
- an optional secondary receiver unit 106 which is operatively coupled to the communication link and configured to receive data transmitted from the data processing unit 102 .
- the secondary receiver unit 106 may be configured to communicate with the primary receiver unit 104 , as well as the data processing terminal 105 .
- the secondary receiver unit 106 may be configured for bi-directional wireless communication with each of the primary receiver unit 104 and the data processing terminal 105 .
- the secondary receiver unit 106 may be a de-featured receiver as compared to the primary receiver unit 104 , i.e., the secondary receiver unit 106 may include a limited or minimal number of functions and features as compared with the primary receiver unit 104 .
- the secondary receiver unit 106 may include a smaller (in one or more, including all, dimensions), compact housing or embodied in a device such as a wrist watch, arm band, etc., for example.
- the secondary receiver unit 106 may be configured with the same or substantially similar functions and features as the primary receiver unit 104 .
- the secondary receiver unit 106 may include a docking portion to be mated with a docking cradle unit for placement by, e.g., the bedside for night time monitoring, and/or bi-directional communication device.
- the analyte monitoring system 100 may include more than one sensor 101 and/or more than one data processing unit 102 , and/or more than one data processing terminal 105 .
- Multiple sensors may be positioned in a patient for analyte monitoring at the same or different times.
- analyte information obtained by a first positioned sensor may be employed as a comparison to analyte information obtained by a second sensor. This may be useful to confirm or validate analyte information obtained from one or both of the sensors. Such redundancy may be useful if analyte information is contemplated in critical therapy-related decisions.
- a first sensor may be used to calibrate a second sensor.
- the analyte monitoring system 100 may be a continuous monitoring system, or semi-continuous, or a discrete monitoring system.
- each component may be configured to be uniquely identified by one or more of the other components in the system so that communication conflict may be readily resolved between the various components within the analyte monitoring system 100 .
- unique IDs, communication channels, and the like may be used.
- the senor 101 is physically positioned in or on the body of a user whose analyte level is being monitored.
- the sensor 101 may be configured to at least periodically sample the analyte level of the user and convert the sampled analyte level into a corresponding signal for transmission by the data processing unit 102 .
- the data processing unit 102 is coupleable to the sensor 101 so that both devices are positioned in or on the user's body, with at least a portion of the analyte sensor 101 positioned transcutaneously.
- the data processing unit 102 in certain embodiments may include a portion of the sensor 101 (proximal section of the sensor in electrical communication with the data processing unit 102 ) which is encapsulated within or on the printed circuit board of the data processing unit 102 with, for example, potting material or other protective material.
- the data processing unit 102 performs data processing functions, where such functions may include but are not limited to, filtering and encoding of data signals, each of which corresponds to a sampled analyte level of the user, for transmission to the primary receiver unit 104 via the communication link 103 .
- the sensor 101 or the data processing unit 102 or a combined sensor/data processing unit may be wholly implantable under the skin layer of the user.
- the primary receiver unit 104 may include an analog interface section including an RF receiver and an antenna that is configured to communicate with the data processing unit 102 via the communication link 103 , and a data processing section for processing the received data from the data processing unit 102 such as data decoding, error detection and correction, data clock generation, and/or data bit recovery.
- the primary receiver unit 104 in certain embodiments is configured to synchronize with the data processing unit 102 to uniquely identify the data processing unit 102 , based on, for example, an identification information of the data processing unit 102 , and thereafter, to periodically receive signals transmitted from the data processing unit 102 associated with the monitored analyte levels detected by the sensor 101 . That is, when operating in the CGM mode, the receiver unit 104 in certain embodiments is configured to automatically receive time spaced analyte related data packets from the analyte sensor/sensor electronics when the communication link (e.g., RF range) is maintained between these components.
- the communication link e.g., RF range
- the data processing terminal 105 may include a personal computer, a portable data processing devices or computers such as a laptop computer or a handheld device (e.g., personal digital assistants (PDAs), communication devices such as a cellular phone (e.g., a multimedia and Internet-enabled mobile phone such as an iPhone, a Blackberry device, a Palm device such as Palm Pre, Treo, or similar phone), mp3 player, pager, and the like), drug delivery device, each of which may be configured for data communication with the receiver via a wired or a wireless connection. Additionally, the data processing terminal 105 may further be connected to a data network (not shown) for storing, retrieving, updating, and/or analyzing data corresponding to the detected analyte level of the user.
- a data network not shown
- the data processing terminal 105 may include an infusion device such as an insulin infusion pump or the like, which may be configured to administer insulin to patients, and which may be configured to communicate with the primary receiver unit 104 for receiving, among others, the measured analyte level.
- the primary receiver unit 104 may be configured to integrate an infusion device therein so that the primary receiver unit 104 is configured to administer insulin (or other appropriate drug) therapy to patients, for example, for administering and modifying basal profiles, as well as for determining appropriate boluses for administration based on, among others, the detected analyte levels received from the data processing unit 102 .
- An infusion device may be an external device or an internal device (wholly implantable in a user).
- the data processing terminal 105 which may include an insulin pump, may be configured to receive the analyte signals from the data processing unit 102 , and thus, incorporate the functions of the primary receiver unit 104 including data processing for managing the patient's insulin therapy and analyte monitoring.
- the communication link 103 as well as one or more of the other communication interfaces shown in FIG. 1 may use one or more of an RF communication protocol, an infrared communication protocol, a Bluetooth enabled communication protocol, an 802.11x wireless communication protocol, or an equivalent wireless communication protocol which would allow secure, wireless communication of several units (for example, per HIPPA requirements) while avoiding potential data collision and interference.
- the analyte monitoring system may include an on-body patch device with a thin profile that can be worn on the arm or other locations on the body (and under clothing worn by the user or the patient), the on-body patch device including an analyte sensor and circuitry and components for operating the sensor and processing and storing signals received from the sensor as well as for communication with the reader device.
- the on-body patch device may include electronics to sample the voltage signal received from the analyte sensor in fluid contact with the body fluid, and to process the sampled voltage signals into the corresponding glucose values and/or store the sampled voltage signal as raw data.
- the on-body patch device includes an antenna such as a loop antenna to receive RF power from the an external device such as the reader device/receiver unit described above, electronics to convert the RF power received via the antenna into DC (direct current) power for the on-body patch device circuitry, communication module or electronics to detect commands received from the reader device, and communication component to transmit data to the reader device, a low capacity battery for providing power to sensor sampling circuitry (for example, the analog front end circuitry of the on-body patch device in signal communication with the analyte sensor), one or more non-volatile memory or storage device to store data including raw signals from the sensor or processed data based on the raw sensor signals.
- an antenna such as a loop antenna to receive RF power from the an external device such as the reader device/receiver unit described above
- electronics to convert the RF power received via the antenna into DC (direct current) power for the on-body patch device circuitry
- communication module or electronics to detect commands received from the reader device
- communication component to transmit data to the reader device
- the on body patch device in certain embodiments is configured to transmit real time analyte related data and/or stored historical analyte related data when within the RF power range of the reader device. As such, when the reader device is removed of positioned out of range relative to the on body patch device, the on body patch device may no longer transmit the analyte related data.
- a data processing module/terminal may be provided in the analyte monitoring system that is configured to operate as a data logger, interacting or communicating with the on-body patch device by, for example, transmitting requests for analyte level information to the on-body patch device, and storing the responsive analyte level information received from the on-body patch device in one or more memory components of the data processing module.
- data processing module may be configured as a compact on-body relay device to relay or retransmit the received analyte level information from the on-body patch device to the reader device/receiver unit or the remote terminal or both.
- the data processing module in one aspect may be physically coupled to the on-body patch device, for example, on a single adhesive patch on the skin surface of the patient.
- the data processing module may be positioned close to but not in contact with the on-body patch device.
- the data processing module may be worn on a belt of the patient or the user, such that the desired close proximity or predetermined distance of approximately 1-5 inches (or about 1-10 inches, for example, or more) between the on-body patch device and the data processing module may be maintained.
- the various processes described above including the processes operating in the software application execution environment in the analyte monitoring system including the on-body patch device, the reader device, data processing module and/or the remote terminal performing one or more routines described above may be embodied as computer programs developed using an object oriented language that allows the modeling of complex systems with modular objects to create abstractions that are representative of real world, physical objects and their interrelationships.
- the software required to carry out the inventive process which may be stored in a memory or storage device of the storage unit of the various components of the analyte monitoring system described above in conjunction to the Figures including the on-body patch device, the reader device, the data processing module, various described communication devices, or the remote terminal may be developed by a person of ordinary skill in the art and may include one or more computer program products.
- an apparatus for bi-directional communication with an analyte monitoring system may comprise a storage device having stored therein one or more routines, a processing unit operatively coupled to the storage device and configured to retrieve the stored one or more routines for execution, a data transmission component operatively coupled to the processing unit and configured to transmit data based at least in part on the one or more routines executed by the processing unit, and a data reception component operatively coupled to the processing unit and configured to receive analyte related data from a remote location and to store the received analyte related data in the storage device for retransmission, wherein the data transmission component is programmed to transmit a query to a remote location, and further wherein the data reception component receives the analyte related data from the remote location in response to the transmitted query when one or more electronics in the remote location transitions from an inactive state to an active state upon detection of the query from the data transmission component.
- FIG. 2 illustrates a data monitoring and management system for real time glucose measurement data acquisition and processing in one aspect of the present disclosure. More specifically, as shown in FIG. 2 , the on-body patch device 211 including sensor electronics coupled to an analyte sensor 250 is positioned on a skin surface 210 of a patient or a user.
- an introducer mechanism may be provided, as discussed in further detail below in conjunction with FIGS. 12A-12G , for the transcutaneous placement of the analyte sensor 250 such that when the on-body patch device 211 is positioned on the skin surface, a portion of the sensor 250 is inserted through the skin surface and in fluid contact with a body fluid of the patient or the user under the skin layer 210 .
- the introducer mechanism may be fully or partially automated, for example with a trigger mechanism, or may be fully or partially manual such that the sensor 250 is positioned transcutaneously by a manual operation of the user.
- the on-body patch device 211 may include an introducer needle and/or lumen (and/or catheter) which may guide the sensor 250 during the insertion process through the skin layer 210 .
- the placement of the on-body patch device 211 on the skin layer 210 includes the initial piercing of the skin layer 210 with a force applied on the on-body patch device 211 in conjunction with the on-body patch device 211 placement on the skin layer 210 , effectively driving the sensor 250 (and/or the introducer) through the skin layer 210 .
- a mechanism (such as a spring, for example) may be provided within the on-body patch device 211 or alternatively, in the introducer in cooperation with the on-body patch device 211 , to withdraw the introducer needle after the sensor 250 has been positioned in fluid contact with the body fluid.
- a lumen may be provided, with the analyte sensor 250 provided within the hollow cavity of the lumen for insertion, and maintained in position with the on-body patch device 211 during the time period that the on-body patch device 211 is worn on the skin layer 210 .
- the RF power supply in the reader device/receiver unit 220 may be configured to provide the necessary power to operate the electronics in the on-body patch device 211 , and the on-body patch device 211 may be configured to, upon detection or the RF power from the reader device/receiver unit 220 , perform preprogrammed routines including, for example, transmitting one or more signals 240 to the reader device/receiver unit 220 indicative of the sampled analyte level measured by the analyte sensor 250 .
- the reader device/receiver unit 220 may include an RF power switch that is user activatable or activated upon positioning within a predetermined distance from the on body patch device 211 to turn on the analyte sensor in the on body patch device 211 . That is, using the RF signal, the analyte sensor coupled to the sensor electronics in the on-body patch device 211 may be initialized or activated.
- a passive RFID function may be provided or programmed such that upon receiving a “turn on” signal which, when authenticated, will turn on the electronic power switch that activates the on-body patch device 211 . That is, the passive RFID configuration may include drawing energy from the RF field radiated from the reader device/receiver unit 220 so as to prompt for and/or detect the “turn on” signal which, upon authentication, activates the on body patch device 211 .
- communication and/or RF power transfer between the reader device/receiver unit 220 and the on-body patch device 211 may be automatically initiated when the reader device/receiver unit 220 is placed in close proximity to the on-body patch device 211 as discussed above.
- the reader device/receiver unit 220 may be configured such that user activation, such as data request initiation and subsequent confirmation by the user using, for example, the display 222 and/or input components 221 of the reader device/receiver unit 220 , may be required prior to the initiation of communication and/or RF power transfer between the reader device/receiver unit 220 and the on-body patch device 211 .
- the reader device/receiver unit 220 may be user configurable between multiple modes, such that the user may choose whether the communication between the reader device/receiver unit 220 and on-body patch device 211 is performed automatically or requires a user activation and/or confirmation.
- the reader device/receiver unit 220 may include display 222 or output component to provide output indication to the user or the patient, including, for example, the corresponding glucose level measurement.
- the display 222 of the reader device/receiver unit 220 may be additionally configured to provide the functionalities of a user interface to present other information such as alarm or alert notification to the user.
- the reader device/receiver unit 220 may include other output components such as a speaker, vibratory output component and the like to provide audible and/or vibratory output indication to the user in addition to the visual output indication provided on the display 222 .
- the reader device/receiver unit 220 may also include one or more input components 221 (such as, for example, push buttons, switches, capacitive sliders, jog wheels, etc.) for receiving input commands or information from the user or the patient by operation of the input components 221 .
- the display 222 and the input component 221 may be integrated into a single component, for example as a touch screen display.
- the user may be able to manipulate the reader device/receiver unit 220 by utilizing a set of pre-programmed motion commands, including, but not limited to, single or double tapping the display, dragging a finger or instrument across the display, motioning multiple fingers toward one another, motioning multiple fingers away from one another, etc.
- the input components 221 correspond to dynamic menus on the display 222 to control features and operation of the reader device/receiver unit 220 .
- the input component 221 may include a microphone and the reader device/receiver unit 220 may include software configured to analyze audio input received from the microphone, such that functions and operation of the reader device/receiver unit 220 may be controlled audibly by the user or patient.
- the electronics in the on-body patch device 211 in one embodiment may be configured to rely on the RF power received from the reader device/receiver unit 220 to perform analyte data processing and/or transmission of the processed analyte information to the reader device/receiver unit 220 . That is, the on-body patch device 211 may be discreetly worn on the body of the user or the patient, and under clothing, for example, and when desired, by positioning the reader device/receiver unit 220 within a predetermined distance from the on-body patch device 211 , real time glucose level information may be received by the reader device/receiver unit 220 . This routine may be repeated as desired by the patient (or on-demand, for example) to determine glucose levels at any time during the time period that the on-body patch device 211 is worn by the user or the patient.
- data processing module 260 may include a stand alone device configured for bi-directional communication to communicate with the on-body patch device 211 , the reader device/receiver unit 220 and/or the remote terminal 270 . More specifically, data processing module 260 may include one or more microprocessors or similar data processing components configured to execute one or more software routines for communication, as well as data storage and retrieval to and from one or more memory components provided in the housing of the data processing module 260 .
- the data processing module 260 in one embodiment may be configured to communicate with the on-body patch device 211 in a similar manner as the reader device/receiver unit 220 and may include communication components such as antenna, power supply and memory, among others, for example, to allow provision of RF power to the on-body patch device 211 or to request or prompt the on-body patch device 211 to send the current analyte related data and optionally other stored analyte related data.
- the data processing module 260 may be configured to interact with the on-body patch device 211 in a similar manner as the reader device/receiver unit 220 such that the data processing module 260 may be positioned within a predetermined distance from the on-body patch device 211 for communication with the on-body patch device 211 .
- the on-body patch device 211 and the data processing module 260 may be positioned on the skin surface of the user or the patient within the predetermined distance of each other (for example, within approximately 5 inches or less) such that the communication between the on-body patch device 211 and the data processing module 260 is maintained.
- the housing of the data processing module 260 may be configured to couple to or cooperate with the housing of the on-body patch device 211 such that the two devices are combined or integrated as a single assembly and positioned on the skin surface.
- the data processing module 260 may be configured or programmed to prompt or ping the on-body patch device 211 at a predetermined time interval such as once every minute, or once every five minutes or once every 30 minutes or any other suitable or desired programmable time interval to request analyte related data from the on-body patch device 211 which is received and is stored in one or more memory devices or components of the data processing module 260 .
- the data processing module 260 is configured to prompt or ping the on-body patch device 211 when desired by the patient or the user on-demand, and not based on a predetermined time interval.
- the data processing module 260 is configured to prompt or ping the on-body patch device 211 when desired by the patient or the user upon request only after a programmable time interval has elapsed. For example, in certain embodiments, if the user does not initiate communication within a programmed time period, such as, for example 5 hours from last communication (or 10 hours from the last communication), the data processing module 260 may by programmed to automatically ping or prompt the on-body patch device 211 or alternatively, initiate an alarm function to notify the user that an extended period of time has elapsed since the last communication between the data processing module 260 and the on-body patch device 211 .
- a programmed time period such as, for example 5 hours from last communication (or 10 hours from the last communication
- users, healthcare providers, or the patient may program or configure the data processing module 260 to provide certain compliance with analyte monitoring regimen, so that frequent determination of analyte levels is maintained or performed by the user.
- Similar functionalities may be provided or programmed in the receiver unit or the reader device in certain embodiments.
- the data processing module 260 in one aspect may be configured to transmit the stored data received from the on-body patch device 211 to the reader device/receiver unit 220 when communication between the data processing module 260 and the reader device/receiver unit 220 is established. More specifically, in addition to RF antenna and RF communication components described above, data processing module 260 may include components to communicate using one or more wireless communication protocols such as, for example, but not limited to, infrared (IR) protocol, Bluetooth protocol, Zigbee protocol, and 802.11 wireless LAN protocol. Additional description of communication protocols including those based on Bluetooth protocol and/or Zigbee protocol can be found in U.S. Patent Publication No. 2006/0193375 incorporated herein by reference for all purposes.
- IR infrared
- the data processing module 260 may further include communication ports, drivers or connectors to establish wired communication with one or more of the reader device/receiver unit 220 , on-body patch device 211 , or the remote terminal 270 including, for example, but not limited to USB connector and/or USB port, Ethernet connector and/or port, FireWire connector and/or port, or RS-232 port and/or connector.
- the data processing module 260 may be configured to operate as a data logger configured or programmed to periodically request or prompt the on-body patch device 211 to transmit the analyte related information, and to store the received information for later retrieval or subsequent transmission to the reader device/receiver unit 220 or to the remote terminal 270 or both, for further processing and analysis.
- the memory or storage component in the data processing module 260 may be sufficiently large to store or retain analyte level information over an extended time period, for example, coinciding with the usage life of the analyte sensor 250 in the on-body patch device 211 . In this manner, the analyte monitoring system described above in conjunction with FIGS.
- CGM continuous glucose monitoring
- the stored data in the data processing module 260 may be subsequently provided to or transmitted to the reader device/receiver unit 220 , the remote terminal 270 or the like for further analysis such as identifying frequency of periods of glycemic level excursions over the monitored time period to improve or enhance therapy related decisions.
- the doctor, healthcare provider or the patient may adjust or recommend modification to the diet, daily habits and routines such as exercise, and the like.
- the functionalities of the data processing module 260 may be configured or incorporated into a memory device such as an SD card, microSD card, compact flash card, XD card, Memory Stick card, Memory Stick Duo card, or USB memory stick/device including software programming resident in such devices to execute upon connection to the respective one or more of the on-body patch device 211 , the remote terminal 270 or the reader device/receiver unit 220 .
- a memory device such as an SD card, microSD card, compact flash card, XD card, Memory Stick card, Memory Stick Duo card, or USB memory stick/device including software programming resident in such devices to execute upon connection to the respective one or more of the on-body patch device 211 , the remote terminal 270 or the reader device/receiver unit 220 .
- the functionalities of the data processing module 260 may be provided to a communication device such as a mobile telephone including, for example, iPhone, iTouch, Blackberry device, Palm based device (such as Palm Pre, Treo, Treo Pro, Centro), personal digital assistants (PDAs) or any other communication enabled operating system (such as Windows or Android operating systems) based mobile telephones as a downloadable application for execution by the downloading communication device.
- a communication device such as a mobile telephone including, for example, iPhone, iTouch, Blackberry device, Palm based device (such as Palm Pre, Treo, Treo Pro, Centro), personal digital assistants (PDAs) or any other communication enabled operating system (such as Windows or Android operating systems) based mobile telephones as a downloadable application for execution by the downloading communication device.
- the remote terminal 270 as shown in FIG. 2 may include a personal computer, or a server terminal that is configured to provide the executable application software to the one or more of the communication devices described above when communication between the remote terminal 270 and the devices are
- the executable downloadable application may be provided over-the-air (OTA) as an OTA download such that wired connection to the remote terminal 270 is not necessary.
- OTA over-the-air
- the executable application may be automatically downloaded as an available download to the communication device, and depending upon the configuration of the communication device, installed on the device for use automatically, or based on user confirmation or acknowledgement on the communication device to execute the installation of the application.
- the downloaded application may be programmed or customized using the user interface of the respective communication device (screen, keypad, and the like) to establish or program the desired settings such as hyperglycemia alarm, hypoglycemia alarm, sensor replacement alarm, sensor calibration alarm, or any other alarm or alert conditions as may be desired by the user.
- the programmed notification settings on the communication device may be output using the output components of the respective communication devices, such as speaker, vibratory output component, or visual output/display.
- the communication device may be provided with programming and application software to communicate with the on-body patch device 211 such that a frequency or periodicity of data acquisition is established.
- the communication device may be configured to conveniently receive analyte level information from the on-body patch device 211 at predetermined time periods such as, for example, but not limited to once every minute, once every five minutes, or once every 10 or 15 minutes, and store the received information, as well as to provide real time display of the monitored or received analyte level information and other related output display such as trend indication of the analyte level (for example, based on the received analyte level information), projection of future analyte levels based on the analyte trend, and any other desired or appropriate warning indication or notification to the user or the patient.
- predetermined time periods such as, for example, but not limited to once every minute, once every five minutes, or once every 10 or 15 minutes
- the communication device may be configured to conveniently receive analyte level information from the on-body patch device 211 at predetermined time periods such as, for example, but not limited to once every minute, once every five minutes, or once every 10 or 15 minutes, and store the received information, as well as
- Information such as trend information, for example, may be output on one or more of the reader device/receiver unit 220 , data processing module 260 , remote terminal 270 , or any other connected device with output capabilities.
- Trend, and other, information may be output on a display unit of a device, for example the display 222 of the reader device/receiver unit 220 .
- Trend information may be displayed as, for example, a graph (such as a line graph) to indicate to the user or patient the current, historical, and predicted future analyte levels as measured and predicted by the analyte monitoring system.
- Trend information may also be displayed as trend arrows, indicating whether the analyte level is increasing or decreasing as well as the acceleration or deceleration of the increase or decrease in analyte level. This information may be utilized by the user or patient to determine any necessary corrective actions to ensure the analyte level remains within an acceptable and/or clinically safe range.
- Other visual indicators, including colors, flashing, fading, etc., as well as audio indicators including a change in pitch, volume, or tone of an audio output and/or vibratory or other tactile indicators may also be incorporated into the display of trend data as means of notifying the user or patient of the current level and/or direction and/or rate of change of the level of the monitored analyte.
- the communication devices described above may be programmed to operate in the optional CGM mode to receive the time spaced monitored analyte level information from the on-body patch device 211 .
- software updates such as software patches, firmware updates or driver upgrades, among others, to the reader device/receiver unit 220 , on-body patch device 211 or the data processing module 260 may be provided by the remote terminal 270 when communication between the remote terminal 270 and the reader device/receiver unit 220 and/or the data processing module 260 is established.
- software upgrades, programming changes or modification to the on-body patch device 211 may be received from the remote terminal 270 by one or more of the reader device/receiver unit 220 or the data processing module 260 , and thereafter, provided to the on-body patch device 211 by the reader device/receiver unit 220 or the data processing module 260 .
- FIG. 3 is a block diagram of a receiver/monitor unit such as that shown in FIG. 1 in accordance with certain embodiments.
- the primary receiver unit 104 ( FIG. 1 ) includes one or more of: a blood glucose test strip interface 301 , an RF receiver 302 , an input 303 , a temperature detection section 304 , and a clock 305 , each of which is operatively coupled to a processing and storage section 307 .
- the primary receiver unit 104 also includes a power supply 306 operatively coupled to a power conversion and monitoring section 308 . Further, the power conversion and monitoring section 308 is also coupled to the receiver processor 307 .
- a receiver serial communication section 309 and an output 310 , each operatively coupled to the processing and storage unit 307 .
- the receiver may include user input and/or interface components or may be free of user input and/or interface components.
- the test strip interface 301 includes a glucose level testing portion to receive a blood (or other body fluid sample) glucose test or information related thereto.
- the interface may include a test strip port to receive a glucose test strip.
- the device may determine the glucose level of the test strip, and optionally display (or otherwise notice) the glucose level on the output 310 of the primary receiver unit 104 .
- Any suitable test strip may be employed, e.g., test strips that only require a very small amount (e.g., one microliter or less, e.g., about 0.5 microliter or less, e.g., about 0.1 microliter or less), of applied sample to the strip in order to obtain accurate glucose information, e.g.
- Glucose information obtained by the in vitro glucose testing device may be used for a variety of purposes, computations, etc.
- the information may be used to calibrate sensor 101 , confirm results of the sensor 101 to increase the confidence thereof (e.g., in instances in which information obtained by sensor 101 is employed in therapy related decisions), etc.
- the RF receiver 302 is configured to communicate, via the communication link 103 ( FIG. 1 ) with the data processing unit (sensor electronics) 102 , to receive encoded data from the data processing unit 102 for, among others, signal mixing, demodulation, and other data processing.
- the input 303 of the primary receiver unit 104 is configured to allow the user to enter information into the primary receiver unit 104 as needed.
- the input 303 may include keys of a keypad, a touch-sensitive screen, and/or a voice-activated input command unit, and the like.
- the temperature monitor section 304 may be configured to provide temperature information of the primary receiver unit 104 to the processing and control section 307 , while the clock 305 provides, among others, real time or clock information to the processing and storage section 307 .
- Each of the various components of the primary receiver unit 104 shown in FIG. 3 is powered by the power supply 306 (or other power supply) which, in certain embodiments, includes a battery. Furthermore, the power conversion and monitoring section 308 is configured to monitor the power usage by the various components in the primary receiver unit 104 for effective power management and may alert the user, for example, in the event of power usage which renders the primary receiver unit 104 in sub-optimal operating conditions.
- the serial communication section 309 in the primary receiver unit 104 is configured to provide a bi-directional communication path from the testing and/or manufacturing equipment for, among others, initialization, testing, and configuration of the primary receiver unit 104 .
- Serial communication section 104 can also be used to upload data to a computer, such as time-stamped blood glucose data.
- the communication link with an external device can be made, for example, by cable (such as USB or serial cable), infrared (IR) or RF link.
- the output/display 310 of the primary receiver unit 104 is configured to provide, among others, a graphical user interface (GUI), and may include a liquid crystal display (LCD) for displaying information. Additionally, the output/display 310 may also include an integrated speaker for outputting audible signals as well as to provide vibration output as commonly found in handheld electronic devices, such as mobile telephones, pagers, etc.
- the primary receiver unit 104 also includes an electro-luminescent lamp configured to provide backlighting to the output 310 for output visual display in dark ambient surroundings.
- the primary receiver unit 104 may also include a storage section such as a programmable, non-volatile memory device as part of the processor 307 , or provided separately in the primary receiver unit 104 , operatively coupled to the processor 307 .
- the processor 307 may be configured to perform Manchester decoding (or other protocol(s)) as well as error detection and correction upon the encoded data received from the data processing unit 102 via the communication link 103 .
- the data processing unit 102 and/or the primary receiver unit 104 and/or the secondary receiver unit 105 , and/or the data processing terminal/infusion section 105 may be configured to receive the blood glucose value wirelessly over a communication link from, for example, a blood glucose meter.
- a user manipulating or using the analyte monitoring system 100 may manually input the blood glucose value using, for example, a user interface (for example, a keyboard, keypad, voice commands, and the like) incorporated in the one or more of the data processing unit 102 , the primary receiver unit 104 , secondary receiver unit 105 , or the data processing terminal/infusion section 105 .
- FIG. 4 is a block diagram of a reader device/receiver unit such as that shown in FIG. 2 in one aspect of the present disclosure.
- the reader device/receiver unit includes a control unit 410 , such as one or more microprocessors, operatively coupled to a display 430 and a user interface 420 .
- the reader device/receiver unit may also include one or more data communication ports such as USB port (or connector) 470 or RS-232 port 450 (or any other wired communication ports) for data communication with other devices such as a personal computer, a server, a mobile computing device, a mobile telephone, a pager, or other handheld data processing devices including smart phones such as Blackberry, iPhone and Palm based mobile devices, with data communication and processing capabilities including data storage and output.
- data communication ports such as USB port (or connector) 470 or RS-232 port 450 (or any other wired communication ports) for data communication with other devices
- other devices such as a personal computer, a server, a mobile computing device, a mobile telephone, a pager, or other handheld data processing devices including smart phones such as Blackberry, iPhone and Palm based mobile devices, with data communication and processing capabilities including data storage and output.
- a power supply 440 such as one or more batteries, is also provided and operatively coupled to the control unit 410 and configured to provide the necessary power to the reader device/receiver unit for operation.
- the reader device/receiver unit may include a loop antenna 481 such as a 433 MHz (or other equivalent) loop antenna coupled to a receiver processor 480 (which may include a 433 MHz receiver chip, for example) for wireless communication with the sensor electronics in the on-body patch device/sensor data processing unit.
- a primary inductive loop antenna 491 is provided and coupled to a squarewave driver 490 which is operatively coupled to the control unit 410 .
- the reader device/receiver unit of the analyte monitoring system may include a strip port 460 configured to receive an in vitro test strip, the strip port 460 coupled to the control unit 410 , and further, where the control unit 410 includes programming to process the sample on the in vitro test strip which is received in the strip port 460 .
- some of the components of the reader device/receiver unit shown in FIG. 4 may be integrated as a single component such as the user interface 420 and the display 430 may be configured as a single touch sensitive display which may be configured to include soft buttons of the display itself, operable by the user or the patient for providing input commands or information to the reader device.
- the reader device/receiver unit of the analyte monitoring system described herein may be configured to include a compact form factor, similar to a USB memory device, where the USB port 470 may be configured as a USB connector for insertion or connection to a USB port on another device such as a personal computing device or the like.
- a compact form factor may include some or all of the components of the reader device/receiver unit described above.
- FIG. 5 is an exemplary schematic of an on-body patch device including an integrated sensor and sensor electronics assembly for use in the analyte monitoring systems of FIGS. 1 and 2 in one aspect of the present disclosure.
- the integrated sensor and sensor electronics assembly/on-body patch device of the analyte monitoring system may include a loop antenna 520 for transmitting the analyte related data to the reader device/receiver unit and further, an inductive power loop antenna 530 for processing the RF power from the reader device/receiver unit, and including converting the RF power to corresponding DC power for the operation of the electronics of the on-body patch device.
- the on-body patch device may be configured to operate as a passive data transmitter, adopting inductive coupling power without a separate power supply or battery for data transmission. Furthermore, the on-body patch device in one aspect does not require a mechanism to turn the device in operational mode nor to deactivate or turn off the on-body patch device. That is, the on-body patch device may be configured to enter an active or operational mode when it detects the RF power from the reader device. Further shown in FIG. 5 is a plurality of super capacitors C 1 , C 2 coupled to the inductive power loop antenna 530 and the controller 510 . Referring still to FIG.
- the controller 510 may be provided on a printed circuit board assembly including the loop antenna 520 , thermistor (not shown), analyte sensor contact pads for coupling to the electrodes of the sensor 540 , one or more storage devices such as non-volatile memory (not shown), and other discrete components.
- the printed circuit board assembly may be partially or fully encapsulated with, for example, potting material.
- FIG. 6 is a block diagram of the integrated sensor and sensor electronics assembly for use in the analyte monitoring systems of FIGS. 1 and 2 in another aspect of the present disclosure.
- the on-body patch device includes a control unit 610 (such as, for example but not limited to, one or more microprocessors, and/or application specific integrated circuits (ASICs)), operatively coupled to analog front end circuitry 670 to process signals such as raw voltage or current signals received from the sensor 680 .
- ASICs application specific integrated circuits
- FIG. 6 includes a memory 620 operatively coupled to the control unit 610 for storing data and/or software routines for execution by the control unit 610 .
- control unit 610 may be configured to access the data or routines stored in the memory 620 to update, store or replace information in the memory 620 , in addition to retrieving one or more stored routines for execution.
- a power supply 660 which, in certain embodiments, provides power to the electronics of the on-body patch device for operation, under the control of the control unit 610 , to process signals from the sensor 680 and to store the processed sensor data for subsequent transmission to the reader device/receiver unit when prompted or pinged by the reader device/receiver unit for transmission of the stored data in addition to the real time analyte level data.
- the on-body patch device does not include the power supply 660 and is configured to rely upon the RF power from the reader device.
- an optional output unit 650 is provided to the on-body patch device as shown in FIG. 6 .
- the output unit 650 may include an LED indicator, for example, to alert the user or the patient of one or more predetermined conditions associated with the operation of the on-body patch device and/or the determined analyte level.
- the on-body patch device may be programmed or configured to provide a visual indication to notify the user of one or more predetermined operational conditions of the on-body patch device.
- the one or more predetermined operational conditions may be configured by the user or the patient or the healthcare provider, so that certain conditions are associated with an output indication on the on-body patch device.
- the on-body patch device may be programmed to assert a notification using the LED indicator on the on-body patch device when signals from the sensor 680 are indicated to be beyond a programmed acceptable range (based on one sampled sensor data point, or multiple sensor data points), potentially indicating a health risk condition such as hyperglycemia or hypoglycemia, or the onset of such conditions.
- a health risk condition such as hyperglycemia or hypoglycemia, or the onset of such conditions.
- the user or the patient may be timely informed of such potential condition, and using the reader device, acquire the glucose level information from the on-body patch device to confirm the presence of such conditions so that timely corrective actions may be taken.
- the on-body patch device may include a speaker or an audible output component instead of or in addition to the LED indicator to provide an audible indication of one or more such conditions described above.
- the type of audible output may be programmed or programmable in the on-body patch device, for example, via the reader device, and may include a standard audible tone (monotone or multi tone), or include one or more ring tones provided to the on-body patch device.
- different conditions may be associated with a different type of audible output/alert such that the patient or the user may easily recognize the underlying detected condition based on the type of audible notification.
- different levels of audible tones may be associated (programmed by the user or the patient, or pre-programmed in the on-body patch device) with different conditions such that when asserted, each outputted tone may be easily recognized by the user or the patient as an indication of the particular associated condition. That is, the detected onset of hyperglycemic condition based on the signal from the analyte sensor may be associated with a first predetermined loudness and/or tone, while the detected onset of hypoglycemic condition based on the signal from the analyte sensor may be associated with a second predetermined loudness and/or tone.
- the programmed or programmable audible alerts may include one or more sequence of audible outputs that are output based on a temporally spaced sequence or a sequence indicating an increase or decrease in the level of loudness (using the same tone, or gradually increasing/decreasing tones).
- audible output indication may be asserted in conjunction with the visual output indicator, simultaneously or alternatingly, as may be customized or programmable in the on-body patch device or pre-programmed.
- the antenna 630 and the communication module 640 operatively coupled to the control unit 610 may be configured to detect and process the RF power when in predetermined proximity to the reader device/receiver unit providing the RF power, and further, in response, to transmit the analyte level information and optionally analyte trend information based on stored analyte level data, to the reader device.
- the trend information may includes a plurality of analyte level information over a predetermined time period that are stored in the memory 620 of the on-body patch device and provided to the reader device/receiver unit with the real time analyte level information.
- the trend information may include a series of time spaced analyte level data for the time period since the last transmission of the analyte level information to the reader device.
- the trend information may include analyte level data for the prior 30 minutes or one hour that are stored in memory 620 and retrieved under the control of the control unit 610 for transmission to the reader device.
- the on-body patch device and the reader device/receiver unit may be configured to communicate using RFID (radio frequency identification) techniques where the reader device/receiver unit is configured to interrogate the on-body patch device (associated with an RFID tag) over an RF communication link, such that the on-body patch device, in response to the RF interrogation signal from the reader device, transmits an RF response signal including, for example, data associated with the sampled analyte level from the sensor.
- RFID radio frequency identification
- the reader device/receiver unit may include a backscatter RFID reader configured to transmit an RF field such that when the on-body patch device is within the transmitted RF field, its antenna is tuned and in turn provides a reflected or response signal (for example, a backscatter signal) to the reader device.
- the reflected or response signal may include sampled analyte level data from the analyte sensor.
- the reader device/receiver unit may be configured such that when the reader device/receiver unit is positioned in close proximity to the on-body patch device and receives the response signal from the on-body patch device, the reader device/receiver unit is configured to output an indication (audible, visual or otherwise) to confirm the analyte level measurement acquisition. That is, during the course of the 5 to 10 days of wearing the on-body patch device on the body, the user or the patient may at any time position the reader device/receiver unit within a predetermined distance (for example, approximately 1-5 inches) from the on-body patch device, and after waiting a few seconds, output an audible indication confirming the receipt of the real time analyte level information.
- the received analyte information may be output to the display 430 ( FIG. 4 ) of the reader device/receiver unit for presentation to the user or the patient.
- the on-body patch device is configured to be worn over a predetermined time period on the body of the user or the patient.
- certain embodiments described below include configurations of the on-body patch device to provide for a compact configuration which is configured to remain adhered to the skin surface for the predetermined wear time period comfortably and without detaching from the skin surface.
- the on-body patch device may include a single integrated housing or body assembly that includes the analyte sensor, electronics and an adhesive path.
- Such configuration provides for fewer parts that require manipulation by the patient or the user, leading to improved ease of use, and further, with an overmolded assembly, may be configured to provide the desired water tight seal during the course of the wear, preventing moisture or other contaminants from entering into the on-body patch device housing.
- Such single body configurations may additionally provide ease of manufacturing with the fewer components that require assembly.
- the on-body patch device may include a two part assembly including a reusable electronics component mated or coupled (detachably or fixedly) to a disposable component including the analyte sensor, a base or mount for the electronics component, and the adhesive patch.
- FIG. 7 is a schematic of the reader device/receiver unit for use in the analyte monitoring systems of FIGS. 1 and 2 in accordance with one aspect of the present disclosure.
- the reader device/receiver unit 220 FIG. 2 or the handheld controller in accordance with one aspect of the present disclosure, includes a surface acoustic wave (SAW) resonator 701 which may includes a resonator that generates the RF signal operating in conjunction with an oscillator (OSC) 702 .
- SAW surface acoustic wave
- OSC oscillator
- the oscillator 702 is the active RF transistor component, and in conjunction with the SAW resonator 701 , is configured to send out control commands (the ping signals), transmit the RF power to receive the backscatter signal from the on-body patch unit, and generate local oscillation signal to the mixer 703 , as described in further detail below.
- the transmit data (TX data) as shown is the control signal received from the control unit 410 of the reader device/receiver unit (see e.g., FIG. 4 ) and received from the power amplifier (PA) 706 is the RF control command to be transmitted to the on-body patch device.
- the SAW resonator 701 in one embodiment is configured to provide the carrier signal for the control commands (ping signals).
- the control signal from the control unit 410 in one embodiment include data packets that are to be transmitted to the on-body patch device to ping it to return a response signal back to the reader device.
- a turn on signal from the control unit 410 is received at the TX enable line (as shown in FIG. 7 ) and provided to the oscillator 702 .
- the carrier signal which is used to carry the control signal is maintained.
- the same carrier signal in one embodiment may be used to receive the response data packet from the on-body patch device.
- the carrier signal is maintained during transmit/receive time periods between the reader device/receiver unit and the on-body patch device, the RF power is provided during the ping (or control signal) request transmission of the RF control signal and also during the time period when the backscatter response is received from the on-body patch device.
- the reader device/receiver unit loop antenna 708 uses the same carrier signal to transmit the RF power and the RF control signal to the on-body patch device.
- an LC power splitter 704 which his configured in one aspect of the present disclosure, to split the power two ways to the buffer 705 and to the power amplifier (PA) 706 .
- the buffer 705 in one embodiment is configured to boost the RF signal received from LC power splitter 704 .
- Output of the power amplifier 706 is the control command that is provided to a second LC power splitter 707 which splits the antenna signal (from the loop antenna into transmit signal (the control signal) and the receive signal (backscatter signal from the on-body patch device)). That is, in one embodiment, the second LC power splitter 707 may be configured to manage the transmit/receive signals using one loop antenna 708 . Referring again to FIG.
- a balun 709 provided between the loop antenna 708 and the second LC power splitter 707 is used in one embodiment to match the balanced signal from the loop antenna 708 to the unbalanced signal from the power splitter 707 (as most circuit components are unbalanced relative to ground terminal).
- the balun 709 includes, in one embodiment, an electrical transformer that can convert electrical signals that are balanced about ground (differential) to signals that are unbalanced (single-ended), and vice versa, using electromagnetic coupling for operation.
- the loop antenna 708 transmits the RF control signal (the ping signal) and in response, receives a backscatter signal from the on-body patch device.
- the received backscatter response signal by the loop antenna is passed through the balun 709 , and to the power splitter 707 to the SAW filter 711 .
- SAW filter 711 in one aspect includes a bandpass filter configured to remove noise or interference components in the received backscatter signal, for example.
- the output of the SAW filter 711 is passed through ASK receiver 720 .
- the ASK receiver 720 includes a low noise amplifier (LNA) 721 whose output is sent to mixer 703 which mixes the low noise amplified signal output from the LNA 721 with the RF carrier signal from the buffer 705 .
- LNA low noise amplifier
- the output of the mixer 703 is passed to the high pass filter (HPF) 712 that filters out the DC component and low frequency components of the signal, and then the output of the HPF 712 is sent to the intermediate frequency amplifier (IF amplifier) 713 which is configured to amplify the received signal.
- the amplified output signal from the IF amplifier 713 is provided to the low pass filter (LPF) 722 of the ASK receiver 720 , and the output low pass filtered signal from LPF 722 is provided to another intermediate frequency amplifier 723 of the ASK receiver 720 which is configured to amplify the low pass filtered signal output from the LPF 722 .
- the IF amplifier 723 of the ASK receiver 720 is provided between the LPF 722 and the ASK demodulator 724 .
- the gain controller signal from IF amplifier 723 of the ASK receiver 720 controls the low noise amplifier (LNA) 721 that receives the filtered backscatter signal.
- the gain controller signal in one embodiment switches between high gain and low gain state of the LNA 721 . For example, if IF amplifier 723 has high gain, then the gain controller signal to the LNA 721 switches the LNA 721 to low gain operation, and vice versa.
- the output of the IF amplifier 723 of the ASK receiver 720 is provided to the ASK demodulator 724 of the ASK receiver 720 which is configured to demodulate (or recover the data) the output signal from the IF amplifier 723 .
- the RX enable line to the ASK receiver 720 is configured to turn on after the TX enable line where the turn on signal from the control unit 410 ( FIG. 4 ) is received in the reader device/receiver unit such that with the receive enable signal from the control unit 410 , the data out line (i.e., the output of the ASK demodulator 724 ) of the ASK receiver 720 provides the data or signal associated with the monitored glucose level based on the raw current signals from the glucose sensor.
- the on-body patch device may include a power supply to power the electronic components as well as the sensor, or alternatively, the on-body patch device may not includes a separate dedicated power supply and rather, include a self-powered sensor as described in further detail in U.S. patent application Ser. No. 12/393,921 filed Feb. 27, 2009 and incorporated by reference herein for all purposes.
- the on-body patch device may be configured to listen for the RF control command (ping signal) from the reader device.
- an On/Off Key (OOK) detector may be provided in the on-body patch device which is turned on and powered by the battery to listen for the RF control command or the ping signal from the reader device. Additional details if the OOK detector are provided in U.S. Patent Publication No. 2008/0278333, the disclosure of which is incorporated by reference for all purposes.
- OOK detector when the RF control command is detected, on-body patch device determines what response packet is necessary, and generates the response packet for transmission back to the reader device.
- the sensor is always turned on and configured to continuously receive power from the power supply or the battery of the on-body patch device.
- the sampled current signal from the sensor may not be transmitted out to the reader device/receiver unit until the on-body patch device receives the RF power (from the reader device/receiver unit) to enable the transmission of the data to the reader device.
- the battery may be a rechargeable battery configured to be charged when the on-body patch device received the RF power (from the reader device/receiver unit).
- the on-body patch device does not include an RF communication chip, nor any other dedicated communication chip to allow for wireless transmission separate from being powered on based on the RF power received from the reader device/receiver unit and transmitting the backscatter response packet to the reader device.
- an RF transmitter chip or an ASK transmitter may be provided to the reader device/receiver unit 220 ( FIG. 2 ) to replace the SAW resonator 701 , the oscillator 702 , the mixer 703 , the LC power splitter 704 , the buffer 705 , the power amplifier 706 , the high pass filter (HPF) 712 , and the IF amplifier 713 shown in FIG. 7 .
- the RF transmitter chip may be coupled to a crystal which provides the frequency reference base for generating the RF carrier signal to receive the backscatter from the on-body patch device, and also to send the control commands (ping signals) to the on-body patch device.
- the RF transmitter chip or unit may be coupled to the LC power splitter, a balun and the loop antenna similar to the LC power splitter 707 , the balun 709 , and the loop antenna 708 shown in FIG. 7 , in addition to a SAW filter and ASK receiver similar to the SAW filter 711 and ASK receiver 720 shown in FIG. 7 .
- another crystal may be coupled to the ASK receiver to provide the frequency reference base for receiving the backscatter signal from the on-body patch device.
- FIGS. 8A and 8B illustrate a top view and a side view, respectively, of antenna and electronic circuit layout of the on-body patch device including an sensor and sensor electronics assembly for use in the analyte monitoring systems of FIGS. 1 and 2 in one aspect of the present disclosure.
- the loop antenna and circuit layout of the on-body patch device in one embodiment includes a conductive layer 801 , such as a PCB copper trace, provided on a substrate 802 , and further includes, a plurality of inductors 803 a - 803 e disposed on the substrate and electrically connected to the conductive layer 801 in a loop configuration.
- the inductors 803 a - 803 e are spaced equidistantly from each other around the loop configuration. In a further aspect, the inductors 803 a - 803 e may not be equidistantly spaced apart from each other in the loop configuration. Also shown in FIGS. 8A and 8B is a data processor or controller 804 in electrical communication with the conductive layer 801 for processing signals from the sensor (not shown) and interfacing with the sensor in addition to processing the control commands from the reader device/receiver unit and generating and/or transmitting the backscatter response data packet to the reader device.
- loop antenna configurations are provided for a passive glucose sensor and a low power glucose reader device/receiver unit at Ultra High Frequency (UHF) frequency bands, providing an on-demand glucose data acquisition system that includes the reader device/receiver unit which is configured to generate a strong near electromagnetic field to power the passive glucose sensor, and further provide a weak far electromagnetic field such that the strength of the generated magnetic field at a far distance, such as approximately 3 meters away from the on-body patch device, including the sensor is in compliance with the regulated radiation level.
- UHF Ultra High Frequency
- the on-body patch device antenna may be printed as an internal conductive layer of a printed circuit board surrounded by the ground plane on the top and bottom layers. That is, in one aspect, the top and bottom conductive layers may be separated by layers of dielectrics and a conductive layer of loop antenna disposed therebetween. Further, the antenna for the on-body patch device may be printed on the top conductive layer of the printed circuit in series with a plurality of inductors chips, such as, for example, but not limited to, five inductor elements.
- FIG. 9 illustrates an exemplary circuit schematic of the on-body patch device including an sensor and sensor electronics assembly in accordance with aspects of the present disclosure.
- the sensor contacts 910 are provided to establish contact with the various electrodes of the sensor including working electrode, reference electrode and counter electrode.
- an RF transmission antenna 920 operatively coupled to the control unit 950 .
- the control unit 950 may be implemented as application specific integrated circuits (ASICs), or include microprocessors or both.
- ASICs application specific integrated circuits
- An activation switch 930 is also shown in FIG. 9 along the electrical path from the power supply 940 for switching on or turning on the sensor electronics of the on-body patch device.
- analog front end circuitry/components 970 coupled to the sensor contacts 910 for processing the raw current signals generated by the analyte sensor and detected at the sensor contacts 910 .
- Additional passive storage capacitors 960 coupled to the power supply such as a battery is shown.
- crystal oscillators 980 , 990 are provided as shown in FIG. 9 , where in certain embodiments, crystal oscillator 980 is configured to provide clock signals for the state machine in the ASIC 950 , while crystal oscillator 990 may be configured to provide frequency reference for the RF communication components within the ASIC 950 .
- FIG. 10A is a perspective view of the components of the an on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure.
- an integrated sensor and sensor electronics assembly/on-body patch device 110 of FIG. 1 in one embodiment is shown.
- the housing 1010 in one embodiment is substantially shaped such that the height profile is minimized (for example, to less than or equal to approximately 10 mm, e.g., about 4 mm or less).
- the housing of the integrated assembly may have a dome-like shape, or otherwise tapered shape.
- a height dimension may be at most about 4 mm, and may taper (gradually or step wise) to heights less than about 4 mm, e.g., 3 mm or less, e.g., 2 mm or less, e.g., 1 mm or less.
- the analyte sensor 1020 is assembled (e.g., provided to the user) with the sensor electronics 1030 and provided within the housing 1010 .
- an adhesive (single sided or two sided) layer 1040 may be provided on a lower surface of the housing 1010 to provide secure positioning of the housing 1010 on the skin surface during and after sensor deployment.
- the integrated sensor and sensor electronics assembly/on-body patch device 110 may be positioned (e.g., during manufacture to provide to the user) within the housing of an insertion device, avoiding the need for a user to align, position, or otherwise connect or couple the sensor and sensor electronics to the insertion device prior to the insertion of the sensor and turning on the sensor electronics. Accordingly, potential misuse, misalignment of the sensor relative to the introducer of the insertion device, or errors and difficulties in use of the integrated assembly by the user may be avoided.
- FIG. 10B is another perspective view of the components of the on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure.
- each component of the integrated assembly is separated to illustrate the relative position of each component, in one embodiment.
- the sensor 1020 includes a bent configuration, whereby at least a portion of the body of the sensor is maintained in a direction substantially planar to the surface of the skin.
- this configuration allows for the low profile dimension of the housing 1010 that includes the sensor 1020 such that the protrusion of the housing 1010 , when positioned on the skin surface of the user, is minimized.
- the sensor 1020 may be bent, or may be bendable, from about 1 degree to about 90 degrees or more.
- FIG. 10C is another perspective view of the assembled on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure.
- the adhesive layer 1040 may be configured to substantially fixedly retain the integrated assembly 110 on the skin surface such that movement of the sensor 1020 during the course of wearing the device is minimized.
- the adhesive layer 1040 may be configured to provide a substantially water tight seal between the integrated assembly 110 and the skin surface during the predetermined time period of wear such that the likelihood of the integrated assembly 110 detaching from the skin surface is minimized.
- FIGS. 11A-11C illustrate circuit layouts for the sensor electronics assembly in the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- embodiments of the sensor electronics of the integrated assembly includes dimensions that are optimized for reduction and thus maximized for comfort in use and wear.
- embodiments of the sensor electronics shown in FIGS. 11A-11C may include a diameter of approximately 25 mm or less (typical size of a quarter coin, for example), e.g., 20 mm or less, or 15 mm or less.
- the control unit including an application specific integrated circuit (ASIC) 1110 is provided in electrical contact with a plurality of RF communication transmission capacitors 1130 positioned, for example, substantially around the outer periphery of the flexible circuit board.
- RF transmission capacitors 1130 of different capacitance may be provided.
- FIG. 11A illustrates RF transmission capacitors 1130 of 600 ⁇ F
- FIGS. 11B and 11C illustrate RF transmission capacitors 1130 having approximately 610 ⁇ F and 240 ⁇ F, respectively.
- a battery 1120 configured to provide the necessary power for the operation of the sensor electronics, and may include a single use coin-cell type battery that is disposable after single use, but which is sufficient to provide the necessary power to operate the integrated sensor and sensor electronics assembly 110 ( FIG. 1 ) during the desired time period (for example, such as 5 days or 7 days or longer).
- RF antennas 1140 are positioned, in one embodiment substantially around the circumference of a portion of the flexible circuit board.
- the circuit layout of the sensor electronics may be optimized to minimize the surface area of the circuit board (and thus the overall size of the integrated assembly), by positioning the various components in the manner as shown in FIGS. 11A-11C .
- FIGS. 12A-12B illustrate pre-deployment and post insertion configurations of the insertion device for positioning the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- insertion device 1200 in one embodiment includes a housing or body 1210 and a cap 1220 which is configured to provide closure or seal on the open end of the insertion device. As shown, the insertion device 1200 may be configured for sensor insertion and sensor electronics assembly positioning in a direction substantially perpendicular to the skin surface.
- the integrated sensor and sensor electronics assembly provided within the housing (not shown) is configured to come into contact with the skin surface 1230 .
- the force applied as discussed above also may be configured to move the introducer (not shown) within the housing in the same direction as shown by arrow 1240 to pierce the skin surface 1230 and position the sensor in fluid contact with an analyte of the user.
- FIGS. 12C-12G illustrate cross sectional perspective views of the operation of the insertion device for deploying the on-body integrated sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- the introducer 1260 in response to the force applied on the insertion device housing 1210 , the introducer 1260 is driven in a direction substantially perpendicular to the skin surface 1230 , and along with the movement of the introducer 1260 , the sensor 1280 and the sensor electronics assembly 1270 are moved in the same direction.
- the bottom surface of the sensor electronics assembly 1270 comes into contact with the skin surface 1230 , the bottom surface is maintained in an adhered relationship with the skin surface 1230 by, for example, the adhesive layer 1290 ( FIG. 12G ).
- a bias spring 1250 which, in one embodiment, is configured to retract the introducer needle from the insertion position to a retracted position which is an opposite direction from the direction indicated by arrow 1240 ( FIG. 12B ).
- the introducer needle 1260 is substantially and entirely retained within the insertion device housing 1210 after sensor insertion, and thereafter, when the insertion device 1200 is removed from the skin surface 1230 , the sensor electronics assembly 1270 is retained on the skin surface 1230 , while the position of the sensor 1280 is maintained in fluid contact with the analyte of the user under the skin layer 1230 .
- embodiments of the present disclosure include systems that are activated merely by positioning the sensor and electronics unit on a skin surface as described above, i.e., no additional action need be required of the user other than applying a force to housing 1210 .
- insertion of the sensor causes activation of the electronics unit.
- activation switch configurations are included which may be configured to be triggered, for example, by the insertion device activation, thereby turning on the integrated sensor and sensor electronics assembly into an active mode.
- FIGS. 13A-13B illustrate embodiments of a power supply switch mechanism including conductive plugs of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- the sensor electronics assembly circuit board 1310 may be provided with a physical gap 1350 that breaks the electrical circuit between the power supply (e.g., battery) and the other circuitry of the sensor electronics assembly.
- a conductive portion 1320 provided within the housing of the sensor electronics may be moved in a direction as shown by arrow 1330 such that electrical contact is established in the physical gap 1350 on the circuit board, by for example, the conductive portion 1320 coming into physical contact with the conductive portions 1360 of the circuit board. In this manner, in one embodiment, the electrical path from the power supply and the remaining circuitry on the circuit board of the sensor electronics is completed, thereby powering the sensor electronics.
- the conductive portions 1360 of the circuit board are provided on the board itself, and the conductive plug 1340 , for example, when pushed into the cavity 1350 , establishes electrical contact between the conductive portions 1360 of the circuit board.
- the actuation of the insertion device to position the sensor and sensor electronics assembly triggers the switch mechanism shown in FIGS. 13A and 13B by also moving the conductive portion 1320 or the conductive plug 1360 in the direction complimentary to the direction of the introducer movement, and thereby switching on the sensor electronics.
- the activation of the sensor electronics by moving the conductive portion 1320 or the conductive plug may include a separate procedure, where after positioning the sensor and the sensor electronics assembly on the skin surface, a predetermined force is applied on the housing of the integrated sensor and sensor electronics assembly such that the desired movement of the conductive portion 1320 or the conductive plug 1360 may be achieved.
- FIGS. 13C-13E illustrate another configuration of the power supply switch mechanism including conductive pads of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- an exposed conductive ring 1371 may be provided and configured to contact the surface of the circuit board in the sensor electronics such that, the insertion device activation positions the conductive ring 1371 on the surface of the circuit board so as to complete the electrical contact of the sensor electronics assembly (by for example, manual force applied on the insertion device placing the conductive ring in contact with the circuit board of the sensor electronics).
- electrical contact pads 1372 , 1373 may be provided to the circuit board in the sensor electronics assembly such that the mating of the contact pads with the conductive ring 1371 switches on the sensor electronics device to provide power to the device from its power source.
- FIG. 13E shows yet another configuration of the switch activation mechanism in accordance with the present disclosure, where a portion of the conductive ring 1374 is selectively positioned and provided to establish electrical contact in the device.
- each of the activation configuration described above includes a break in the circuitry from the power source such that the power supply is not drained when the device is not in use, and upon activation, the break in the electrical contact is completed, thereby powering the device and activating it for operation.
- FIG. 14 illustrates a power supply switch mechanism including an internal switch with a push rod activation of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- push rod 1410 may be provided and positioned in the sensor electronics such that when a force is applied in the direction as shown by arrow 1430 , the push rod 1410 is displaced in the same direction, and completes the electrical contact between the two contacts 1420 , 1421 .
- the push rod 1410 may be provided within a seal 1440 such as an O-ring or similar components.
- FIG. 15 illustrates a power supply switch mechanism including introducer retraction trigger activation of the on-body integrated sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- a nonconducting needle or device 1510 is provided to physically separate two electrical contacts 1520 , 1521 .
- Each of the electrical contacts 1520 , 1521 is biased or spring loaded to be urged towards each other, physically separated by the nonconducting needle 1510 . Accordingly, when the nonconducting needle 1510 is retracted or pulled away from the sensor electronics assembly in the direction as shown by arrow 1530 , the two electrical contacts 1520 , 1521 are configured to contact each other, thereby completing the break in the circuit and establishing electrical connection to activate the sensor electronics assembly.
- the nonconducting device or needle 1510 may include, for example, but not limited to, glass, plastic or any other material suitable to separate two electrical contacts and provide insulation therebetween.
- FIG. 16 illustrates a power supply switch mechanism with a contact switch of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- an electronic switch 1601 that is configured to draw an insubstantial amount of power from the sensor electronics power supply
- the activation component 1602 that completes the circuit in the sensor electronics from its power supply such as battery to activate the device for operation.
- FIGS. 17A-17B illustrate a power supply switch mechanism with a battery contact locking mechanism of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- the battery contact of the sensor electronics may be provided with a barbed tab 1710 .
- the tab 1710 In post manufacturing shelf mode when the device is nonoperational, the tab 1710 is positioned within the sensor electronics housing in the position as shown in FIG. 17A so that it is not in contact with the conductive contact 1720 of the sensor electronics circuit board.
- the tab 1710 may be biased such that it physically contacts the conductive contact 1720 on the circuit board, thereby closing the circuit to/from the battery/power source and thus activating or switching on the sensor electronics.
- the tab 1710 may be configured that upon biasing to establish contact with the conductive contact 1720 , it locks or latches with the conductive contact 1620 and the circuit board so as to maintain the electrical connection.
- FIGS. 18A-18B illustrate a power supply switch mechanism with a bi-modal dome switch of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure.
- a bi-modal dome shaped switch 1810 is provided on the circuit board of the sensor electronics assembly such that, when pressed down (as shown in FIG. 18B ), the dome shaped layer 1810 (which may include, for example, a thin sheet metal dome) may be configured to retain the concave shape as shown in FIG. 18B and effectively closing the circuit on the circuit board at the contact point 1820 .
- the dome shaped layer 1810 may be configured to shunt to short two or more electrical contacts at the contact point 1820 of the circuit board.
- the dome shaped layer 1810 may be connected to the circuit board such that one end of the dome shaped layer 1810 is in contact with one of the two or more open electrical contacts, and the depression of the dome shaped layer 1810 closes the circuit on the circuit board by physically contacting the other one or more of the open electrical contacts.
- sensor electronics activation switch configurations are provided that may be triggered or activated automatically or semi-automatically in response to the activation of the insertion device described above, or alternatively, may be separately activated by the user by, for example, depressing upon a portion of the housing or switch provided on the housing of the sensor electronics. Accordingly, power consumption may be optimized for the sensor electronics assembly while improving post manufacturing shelf life of the device prior to use or activation.
- discrete glucose measurement data may be acquired on-demand or upon request from the reader device, where the glucose measurement is obtained from an in vivo glucose sensor transcutaneously positioned under the skin layer of a patient or a subject, and further having a portion of the sensor maintained in fluid contact with the interstitial fluid under the skin layer.
- the patient or the user of the analyte monitoring system may conveniently determine real time glucose information at any time, using the RFID communication protocol as described above.
- discrete glucose measurements may be obtained within the need for lancing or performing fingerprick test for access to blood sample each time a measurement is desired.
- the analyte monitoring system described in further aspects may be configured to log or store glucose data monitored by the analyte sensor continuously over a predetermined or programmable time period, or over the life of the sensor without user intervention, and which data may be retrieved at a later time as desired.
- output indications such as audible, visual or vibratory alerts may be provided to inform the user of a predetermined condition or when the monitored glucose level deviates from a predefined acceptable range (for example, as warning indication of low glucose or high glucose level).
- the various processes described above including the processes operating in the software application execution environment in the analyte monitoring system including the on-body patch device, sensor electronics, the reader device, the receiver unit, data processing module and/or the remote terminal performing one or more routines described above may be embodied as computer programs developed using an object oriented language that allows the modeling of complex systems with modular objects to create abstractions that are representative of real world, physical objects and their interrelationships.
- the software required to carry out the inventive process which may be stored in a memory or storage device of the storage unit of the various components of the analyte monitoring system described above in conjunction to the Figures including the on-body patch device, the reader device, the data processing module, various described communication devices, or the remote terminal may be developed by a person of ordinary skill in the art and may include one or more computer program products.
- the methods, devices and systems described above may be configured to log and store (for example, with an appropriate time stamp and other relevant information such as, for example, contemporaneous temperature reading)) the real time analyte data received from the analyte sensor, and may be configured to provide the real time analyte data on-demand by using, for example a device such as a blood glucose meter or a controller discussed above that is configured for communication with the on-body integrated sensor and sensor electronics assembly.
- a device such as a blood glucose meter or a controller discussed above that is configured for communication with the on-body integrated sensor and sensor electronics assembly.
- real time data associated with the analyte being monitored is continuously or intermittently measured and stored in the integrated on-body sensor and sensor electronics assembly, and upon request from another device such as the receiver unit or the reader device/receiver unit (operated by the user, for example) or any other communication enabled device such as a cellular telephone, a personal digital assistant, an iPhone, a Blackberry device, a Palm device such as Palm Treo, Pro, Pre, Centro), or any other suitable communication enabled device which may be used to receive the desired analyte data from the on-body integrated sensor and sensor electronics assembly while being worn and used by the user.
- another device such as the receiver unit or the reader device/receiver unit (operated by the user, for example) or any other communication enabled device such as a cellular telephone, a personal digital assistant, an iPhone, a Blackberry device, a Palm device such as Palm Treo, Pro, Pre, Centro), or any other suitable communication enabled device which may be used to receive the desired analyte data from the on-body integrated sensor
- such communication enabled device may be positioned within a predetermined proximity to the integrated on-body sensor and sensor electronics assembly, and when the communication enabled device is positioned within the predetermined proximity, the data from the integrated on-body sensor and sensor electronics assembly may be transmitted to the communication enabled device.
- data communication may include inductive coupling using, for example, electromagnetic fields, Zigbee protocol based communication, or any other suitable proximity based communication techniques. In this manner, glucose on-demand mode may be provided such that the information associated with contemporaneously monitored analyte level information is provided to the user on-demand from the user.
- the size and dimension of the on-body sensor electronics may be optimized for reduction by, for example, flexible or rigid potted or low pressure/low temperature overmolded circuitry that uses passive and active surface mount devices for securely positioning and adhering to the skin surface of the user.
- the sensor electronics may includes the analyte sensor and/or other physiological condition detection sensor on the flex circuit.
- one or more printed RF antenna may be provided within the sensor electronics circuitry for RF communication with one or more remote devices, and further, the device operation and/or functionalities may be programmed or controlled using one or more a microprocessors, or application specific integrated circuits (ASIC) to reduce the number of internal components.
- ASIC application specific integrated circuits
- Embodiments of the present disclosure include one or more low pressure molding materials that directly encapsulate the integrated circuits or the sensor electronic components.
- the thermal process entailed in the encapsulation using the low pressure molding materials may be configured to shield temperature sensitive components such as, for example, the analyte sensor or other components of the sensor electronics from the heat generated during the thermal overmolding process.
- Other techniques such as injection molding and/or potting may be used.
- the sensor electronics may be molded using optical techniques such as with a UV cured material, for example, or using two photon absorption materials, which may also be used to reduce the dead or unused volume surrounding the sensor electronics within the housing of the device such that the reduction of its size and dimension may be achieved.
- the sensor electronics may be configured to reduce the number of components used, for example, by the inclusion of an application specific integrated circuit (ASIC) that may be configured to perform the one or more functions of discrete components such as a potentiostat, data processing/storage, thermocouple/thermister, RF communication data packet generator, and the like.
- ASIC application specific integrated circuit
- FPGA field programmable gate array
- embodiments of the present disclosure includes analyte sensors that may be fabricated from flex circuits and integrated with the sensor electronics within the device housing, as a single integrated device.
- Example of flex circuits may include evaporated or sputtered gold on polyester layer, single or multi-layer copper or gold on polymide flex circuit.
- gold or other inert material may be selectively plated on the implantable portion of the circuit to minimize the corrosion of the copper.
- the flex circuit may be die or laser cut, or alternatively chemically milled to define the sensor from the flex circuit roll.
- a further configuration of embodiments of the present disclosure includes RF communication module provided on the flex circuit instead of as a separate component in the sensor electronics.
- the RF antenna may be provided directly on the flex circuit by, such as surrounding the sensor electronics components within the housing on the flex circuit, or folded over the components, and encapsulated with the electronic components within the housing of the device.
- the integrated sensor and sensor electronics assembly may be positioned on the skin surface of the user using an insertion device.
- an insertion device for example, automated or semi-automated, spring biased and/or manual insertion device may be provided to deploy the sensor and the sensor electronics such that the implantable portion of the sensor is positioned in fluid contact with the analyte of the user such as the interstitial fluid, while the housing of the sensor electronics is securely positioned and adhered to the skin surface.
- the sensor electronics device for example, a transmitter unit of an analyte monitoring system
- integrated sensor and sensor electronics assembly may be pre-loaded or otherwise pre-assembled within the insertion device, such that, when in use, the user may, by a single operation of the insertion device, deploy the integrated sensor and sensor electronics assembly, without the need to couple the integrated assembly with the insertion device prior to deployment.
- the integrated sensor and sensor electronics assembly and the insertion device may be sterilized and packaged as one single device and provided to the user.
- the insertion device assembly may be terminal packaged providing cost savings and avoiding the use of, for example, costly thermoformed tray or foil seal.
- the inserter device may include an end cap that is rotatably coupled to the insertion device body, and which provides a safe and sterile environment (and avoid the use of desiccants for the sensor) for the sensor provided within the insertion device along with the integrated assembly.
- the insertion device sealed with the end cap may be configured to retain the sensor within the housing from significant movement during shipping such that the sensor position relative to the integrated assembly and the insertion device is maintained from manufacturing, assembly and shipping, until the device is ready for use by the user.
- the insertion device in embodiments of the present disclosure includes a sharp needle or introducer for aiding the transcutaneous insertion of the sensor through the skin layer of the user.
- the sharp needle or the introducer may be configured to be retracted within the insertion device housing after deployment to permit movement, such as tilting or angled movement, to position the adhesive on the housing of the sensor electronics onto the skin surface of the user without the introducer interfering such movement.
- movement such as tilting or angled movement
- the disposal of the used introducer may be safer, without presenting possible biohazard concerns.
- the sharp needle or the introducer is not visible to the user prior to, during and after the use of the insertion device to position the sensor and the sensor electronics. As such, potential for perceived pain associated with when the sharp needle is visible is minimized.
- the insertion device may be configured for manual deployment with spring biased or automatic refraction of the introducer. That is, sensor insertion, the user may apply a predetermined amount of pressure upon the housing of the insertion device to insert the introducer and the sensor, the applied pressure sufficient to pierce through the skin layer of the user, and the device housing configured such that the applied pressure or the distance traveled by the introducer is predetermined (for example, by the use of a stopper or a protrusion within the inner wall of the insertion device that effectively stops of blocks further downward movement of the introducer towards the skin piercing direction after the introducer has reached a predetermined distance.
- the applied pressure may be configured to also press down upon a spring or a bias mechanism provided within the housing of the insertion device such that, when the applied pressure is released, the introducer is automatically retracted to its original pre-deployment position within the housing of the insertion device, by the return force from the spring or bias mechanism.
- the insertion device housing (for example, a plastic or a combination of plastic and metal housing) may not be under the stress of spring tension since the bias spring provided for refraction of the introducer is, in the predeployment state, unbiased and in a relaxed state.
- two sided adhesive layer may be provided along the other periphery of the insertion device that is positioned to be in contact with the skin surface of the user such that, proper alignment and positioning of the introducer, the sensor and the sensor electronics assembly may be provided before and during the sensor positioning process, in addition to increased comfort and breathability of the material once adhered to the skin layer of the user.
- an integrated analyte monitoring device assembly may comprise an analyte sensor for transcutaneous positioning through a skin layer and maintained in fluid contact with an interstitial fluid under the skin layer during a predetermined time period, the analyte sensor having a proximal portion and a distal portion, and sensor electronics coupled to the analyte sensor, the sensor electronics comprising a circuit board having a conductive layer and a sensor antenna disposed on the conductive layer, one or more electrical contacts provided on the circuit board and coupled with the proximal portion of the analyte sensor to maintain continuous electrical communication, and a data processing component provided on the circuit board and in signal communication with the analyte sensor, the data processing component configured to execute one or more routines for processing signals received from the analyte sensor, the data processing component configured to control the transmission of data associated with the processed signals received from the analyte sensor to a remote location using the sensor antenna in response to a request signal received from the remote location.
- the proximal portion of the analyte sensor and the circuit board may be encapsulated.
- the proximal portion of the analyte sensor and the circuit board may be encapsulated with a potting material.
- the circuit board may include an upper layer and a lower layer, where the conductive layer is disposed between the upper layer and the lower layer.
- the antenna may include a loop antenna or a dipole antenna.
- the antenna may be printed on the conductive layer.
- the assembly may include a plurality of inductive components coupled to the sensor antenna on the conductive layer of the circuit board.
- the plurality of inductive components may be coupled in series to the sensor antenna.
- the plurality of inductive components may be positioned substantially around an outer edge of the circuit board.
- the circuit board may be substantially circular, and the plurality of components may be positioned around the outer circumference of the circular circuit board.
- Each of the plurality of the inductive components may be positioned substantially equidistant to each other on the circuit board.
- the assembly may include a power supply to provide power to the sensor electronics.
- the data processing component may include an application specific integrated circuit (ASIC) disposed on the circuit board and configured to process signals from the analyte sensor.
- ASIC application specific integrated circuit
- the data processing component may include a state machine.
- the state machine may be configured to execute one or more programmed or programmable logic for processing the signals received from the analyte sensor.
- the analyte sensor may include a glucose sensor.
- an analyte data acquisition device may comprise a control unit configured to generate a control command based on a carrier signal, an antenna section coupled to the control unit to transmit the control command with the carrier signal and to receive a backscatter response data packet using the carrier signal, and a receiver section coupled to the antenna section and the control unit to process the received backscatter response data packet and to generate an output glucose data.
- the control unit may include a signal resonator coupled to an oscillator, and configured to generate RF power.
- the signal resonator may include a surface acoustic wave resonator.
- the generated RF power and the control command may be transmitted with the carrier signal.
- the control command may include an RF control command transmitted with the carrier signal to a remote location.
- the backscatter response data packet may be received from the remote location when the antenna is positioned no more than approximately ten inches from the remote location.
- the antenna may be positioned about five inches or less from the remote location.
- the antenna section may include one or more of a loop antenna, or a dipole antenna.
- the control unit may be configured to generate the carrier signal.
- the receiver section may include a filter to filter the received backscatter response data packet.
- a further aspect may include an output unit operatively coupled to the control unit to output an indication corresponding to the generated glucose data.
- the outputted indication may include one or more of a visual output, an audible output, a vibratory output, or one or more combinations thereof.
- the control unit may generate a receipt confirmation signal upon successful receipt of the backscatter response data packet.
- the generated receipt confirmation signal may be output to the user.
- the device may further include a storage device coupled to the control unit to store the generated control command, carrier signal, the received backscatter response data packet, the generated output glucose data, or one or more combinations thereof.
- the storage device may include a nonvolatile memory device.
- the control unit may include a microprocessor.
- the control unit may include an application specific integrated circuit.
- Yet another aspect may include a strip port for receiving an in vitro blood glucose test strip, the strip port including an electrical connection in signal communication with the control unit.
- the control unit may be configured to process a sample on the test strip to determine a corresponding blood glucose level.
- an integrated analyte monitoring device may comprise a sensor electronics assembly including an analyte sensor, a power supply, an activation switch operatively coupled to the power supply and the analyte sensor, a controller unit in electrical contact with the analyte sensor and the activation switch having one or more programming instructions stored therein for execution, the controller unit configured to process one or more signals received from the analyte sensor when the activation switch is triggered, and an insertion device including a housing, an introducer coupled to the housing configured to move between a first position and a second position, and a bias mechanism operatively coupled to the housing configured to automatically retract the introducer from the second position to the first position.
- the sensor electronics assembly may be retained entirely within the housing of the insertion device prior to the introducer movement from the first position to the second position.
- the activation switch may be not triggered until the introducer has reached the second position.
- the analyte sensor may include a glucose sensor.
- the activation switch may be triggered after the introducer has reached the second position, and prior to the introducer retraction from the second position to the first position.
- the introducer may engage with the analyte sensor during its movement from the first position to the second position, and further, wherein the introducer disengages from the analyte sensor during its movement from the second position to the first position.
- the movement of the introducer from the first position to the second position may be in response to a manual force applied on the housing.
- the bias mechanism may include a spring.
- a further aspect may include an adhesive layer provided on a bottom surface of the housing for placement on a skin layer.
- the adhesive layer may be configured to retain the sensor electronics assembly on the skin layer for a predetermined time period.
- the power supply may include a single use disposable battery.
- the active operational life of the power supply may exceed the active operational life of the analyte sensor.
- one aspect may include a cap configured to mate with an open end of the housing of the insertion device.
- the interior space of the housing may be maintained in a substantially contaminant free environment.
- the sensor electronics assembly may include a printed circuit board including a portion of the analyte sensor permanently connected thereto.
- the controller unit may include an application specific integrated circuit (ASIC).
- ASIC application specific integrated circuit
- the movement of the introducer between the first position and the second position may be at an angle at approximately 90 degrees or less from a skin surface.
- the sensor electronics assembly may include a housing having a height of less than approximately 4 mm.
Abstract
Methods and devices to monitor an analyte in body fluid are provided. Embodiments include continuous or discrete acquisition of analyte related data from a transcutaneously positioned analyte sensor automatically or on demand upon request from a user.
Description
- The present application claims priority under 35 U.S.C. §119(e) to U.S. provisional application No. 61/149,639 filed Feb. 3, 2009 entitled “Compact On-Body Physiological Monitoring Devices and Methods Thereof”, the disclosure of which is incorporated by reference for all purposes. The present application is further related to US patent Application entitled “Analyte Sensor and Apparatus for Insertion of the Sensor (Attorney Docket No. 031312-06099) filed concurrently on Feb. 1, 2010, and the disclosure of which is incorporated by reference for all purposes.
- The detection of the level of glucose or other analytes, such as lactate, oxygen or the like, in certain individuals is vitally important to their health. For example, the monitoring of glucose is particularly important to individuals with diabetes. Diabetics may need to monitor glucose levels to determine when insulin is needed to reduce glucose levels in their bodies or when additional glucose is needed to raise the level of glucose in their bodies.
- Devices have been developed for continuous or automatic monitoring of analytes, such as glucose, in bodily fluid such as in the blood stream or in interstitial fluid. Some of these analyte measuring devices are configured so that at least a portion of the devices are positioned below a skin surface of a user, e.g., in a blood vessel or in the subcutaneous tissue of a user.
- Ease of insertion and use, including minimal user intervention and on-body size and height (or thickness) of such transcutaneous or percutaneous medical devices that are worn on the body are important in usability, wearability, and comfort during the device usage. Moreover, for many of such medical devices that require a battery or a similar power source to perform the device specific operations, power management as well as shelf life is important.
- Embodiments of the subject disclosure include devices and methods and kits for providing sensor electronics assembly including an analyte sensor for monitoring of analyte levels such as glucose levels over a sensing time period. Sensing time period may be determined by the analyte sensor life, for example, including, but not limited to about three days or more, about five days or more, or about seven days or more, or about fourteen days or more.
- Embodiments include methods, devices and systems for monitoring glucose levels and obtaining glucose measurements that are discreet, automated, minimally invasive and with reduced pain and repetition of glucose testing procedures to obtain multiple discrete measurements over the sensing time period. Also provided are kits.
- Embodiments further include a control unit, a control command generator coupled to the control unit to receive a control signal and to generate a control command based on a carrier signal, an antenna section coupled to the control command generator to transmit the control command with the carrier signal and to receive a backscatter response data packet using the carrier signal, and a receiver section coupled to the antenna section to process the received backscatter response data packet and to generate an output glucose data.
- Embodiments also include real time discrete glucose measurement data acquisition on-demand, as desired by the user or upon request, based on, for example, RFID data communication techniques for data transmission and acquisition from the analyte sensor/electronics assembly or the on-body patch device including the analyte sensor and the data processing and communication components provided in a compact, low profile housing and placed on the skin surface of the user. The analyte sensor in certain embodiments includes a portion that is transcutaneously positioned and maintained in fluid contact with an interstitial fluid under the skin surface continuously during the sensing time period as discussed above, for example.
- These and other features, objects and advantages of the present disclosure will become apparent to those persons skilled in the art upon reading the details of the present disclosure as more fully described below.
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FIG. 1 shows a data monitoring and management system such as, for example, an analyte (e.g., glucose) monitoring system in accordance with certain embodiments of the present disclosure; -
FIG. 2 illustrates a data monitoring and management system for real time glucose measurement data acquisition and processing in one aspect of the present disclosure; -
FIG. 3 is a block diagram of a receiver/monitor unit such as that shown inFIG. 1 in accordance with certain embodiments; -
FIG. 4 is a block diagram of a reader device/receiver unit such as that shown inFIG. 2 in one aspect of the present disclosure; -
FIG. 5 is an exemplary schematic of an on-body patch device including an integrated sensor and sensor electronics assembly for use in the monitoring systems ofFIGS. 1 and 2 in one aspect of the present disclosure; -
FIG. 6 is a block diagram of the integrated sensor and sensor electronics assembly for use in the monitoring systems ofFIGS. 1 and 2 in another aspect of the present disclosure; -
FIG. 7 is a schematic of the reader device/receiver unit for use in the monitoring systems ofFIGS. 1 and 2 in accordance with one aspect of the present disclosure; -
FIGS. 8A and 8B illustrate a top view and a side view, respectively, of antenna and electronic circuit layout of the on-body patch device including an sensor and sensor electronics assembly for use in the monitoring systems ofFIGS. 1 and 2 in one aspect of the present disclosure; -
FIG. 9 illustrates an exemplary circuit schematic of the on-body patch device including an sensor and sensor electronics assembly in accordance with aspects of the present disclosure; -
FIG. 10A is a perspective view of the components of the on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure; -
FIG. 10B is another perspective view of the components of the on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure; -
FIG. 10C is another perspective view of the assembled on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure; -
FIGS. 11A-11C illustrate circuit layouts for the sensor electronics assembly in the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; -
FIGS. 12A-12B illustrate pre-deployment and post insertion configurations of the insertion device for positioning the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; -
FIGS. 12C-12G illustrate cross sectional perspective views of the operation of the insertion device for deploying the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; -
FIGS. 13A-13B illustrate embodiments of a power supply switch mechanism including conductive plugs of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; -
FIGS. 13C-13E illustrate another configuration of the power supply switch mechanism including conductive pads of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; -
FIG. 14 illustrates a power supply switch mechanism including an internal switch with a push rod activation of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; -
FIG. 15 illustrates a power supply switch mechanism including introducer retraction trigger activation of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; -
FIG. 16 illustrates a power supply switch mechanism with a contact switch of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; -
FIGS. 17A-17B illustrate a power supply switch mechanism with a battery contact locking mechanism of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure; and -
FIGS. 18A-18B illustrate a power supply switch mechanism with a bi-modal dome switch of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. - The following patents, applications and/or publications are incorporated herein by reference for all purposes: U.S. Pat. Nos. 4,545,382; 4,711,245; 5,262,035; 5,262,305; 5,264,104; 5,320,715; 5,509,410; 5,543,326; 5,593,852; 5,601,435; 5,628,890; 5,820,551; 5,822,715; 5,899,855; 5,918,603; 6,071,391; 6,103,033; 6,120,676; 6,121,009; 6,134,461; 6,143,164; 6,144,837; 6,161,095; 6,175,752; 6,270,455; 6,284,478; 6,299,757; 6,338,790; 6,377,894; 6,461,496; 6,503,381; 6,514,460; 6,514,718; 6,540,891; 6,560,471; 6,579,690; 6,591,125; 6,592,745; 6,600,997; 6,605,200; 6,605,201; 6,616,819; 6,618,934; 6,650,471; 6,654,625; 6,676,816; 6,730,200; 6,736,957; 6,746,582; 6,749,740; 6,764,581; 6,773,671; 6,881,551; 6,893,545; 6,932,892; 6,932,894; 6,942,518; 7,167,818; and 7,299,082; U.S. Published Application Nos. 2004/0186365; 2005/0182306; 2007/0056858; 2007/0068807; 2007/0227911; 2007/0233013; 2008/0081977; 2008/0161666; and 2009/0054748; U.S. patent application Ser. Nos. 12/131,012; 12/242,823; and 12/363,712; and U.S. Provisional Application Ser. Nos. 61/149,639; 61/155,889; 61/155,891; 61/155,893; 61/165,499; 61/230,686; 61/227,967 and 61/238,461.
- Within the scope of the present disclosure, there are provided devices, systems, kits and methods for providing compact, low profile, on-body physiological parameter monitoring device (physiological parameters such as for example, but not limited to analyte levels, temperature levels, heart rate, etc), configured for single or multiple use over a predetermined time period, which provide a low profile geometry, effective power management, improved shelf life, and ease and comfort of use including device positioning, and activation. Embodiments include an on-body assembly including a transcutaneously positioned analyte sensor and sensor electronics in a compact, low profile integrated assembly and coupled to an insertion device for deployment.
- Embodiments include continuous glucose monitoring (CGM) system or routines or functions for execution operations to continuously or semi-continuously monitor an analyte level such as glucose level with the transcutaneously positioned analyte sensor, where the real time analyte measurements are provided to a data receiver unit, a reader device, a data repeater or relay device such as data processing module, a data processing terminal or a remote terminal for data processing automatically upon data sampling at predetermined time intervals or based on programmed or programmable data transmission schedule. Data processing may include display, storage, execution of related alarm or notification functions, and analysis such as generating charts or graphs based on, for example, the monitored analyte levels received from the sensor/sensor electronics assembly.
- Embodiments further include analyte data acquisition in real time where the analyte level detected by the transcutaneously positioned analyte sensor is stored either permanently or temporarily in a memory or storage unit of a data processing unit or an integrated sensor and data processing unit assembly, such as an on-body patch device (stored for example, for about one day or less, or for about 10 hours or less, or for about 5 hours or less, or for about 3 hours or less, or for about one hour or less). In such embodiments, the receiver unit or the reader device may be used to acquire the detected analyte level in real time, and/or on-demand or upon request using, for example, RFID communication protocol or other suitable data communication protocols. Sampled analyte related data in certain embodiments are received by the receiver unit or the reader device upon activation or initiation by the user or the patient, for example, of a switch or other initiation mechanism to initiate the data transfer or provide data request command. Such activation switch or mechanism may be provided or included in the user interface of the reader device or the receiver unit.
- Embodiments of the present disclosure relate to methods and devices for detecting at least one analyte such as glucose in body fluid. Embodiments include glucose measurements by an on-body patch device that includes a transcutaneously positioned analyte sensor in fluid contact with the body fluid such as interstitial fluid, and sensor electronics in signal communication with the analyte sensor, where the on-body patch device is configured to transmit one or more signals or data packets associated with a monitored analyte level upon detection of a reader device or the receiver unit of the analyte monitoring system within a predetermined proximity for a period of time (for example, about 10 seconds or less, or preferably about 5 seconds or less, or preferably about 2 seconds or less, or until a confirmation, such as an audible notification, is output on the reader device/receiver unit indicating successful acquisition of the analyte related signal from the on-body patch device).
- For example, in one aspect, when a reader device/receiver unit is positioned within approximately 5 inches or less (or about 10 inches or less, for example) to the on-body patch device that is adhesively placed or mounted on the skin surface of a patient (with the analyte sensor transcutaneously positioned in fluid contact under the skin surface and in signal communication with the sensor electronics of the on-body patch device), a radio frequency source within the reader device/receiver unit may be configured to provide RF power to the on-body patch device. In response, the on-body patch device in one embodiment may be configured to generate an output signal (e.g., an RF signal) and transmit it to the reader device/receiver unit which includes, among others data indicating the glucose measurement. In one aspect the signal communication and/or RF power transmission may initiate automatically upon detection of the reader device/receiver unit within a predetermined proximity to the on-demand patch device, or alternatively the reader device/receiver unit may require a user activation or confirmation prior to initiating signal communication and/or RF power transmission with the on-body patch device as discussed above.
- In a further aspect, the transmitted data from the on-body patch device to the reader device/receiver unit may include glucose trend information that was stored in the on-body patch device for a predetermined time period, since the initialization of the sensor and positioning it in fluid contact with the interstitial fluid, or since the last transmission of data to the reader device, or any one or more combinations of the above. For example, the trend information may indicate the variation in the monitored glucose level over the particular time period based on signals received from the analyte sensor and stored in the on-body patch device.
- As described in further detail below, the on-body patch device may optionally include an output component such as a speaker, a light indicator (for example, an LED indicator), or the like to provide one or more indications associated with its functions such as a successful transmission of data to the reader device or the receiver unit, alarm or alert conditions associated with its internal components, or a detection of the RF power received from the reader device or the receiver unit, for example. By way of a non-limiting example, one or more exemplary output indication may include an audible sound (including for example, a short tone, a changing tone, multi-tone, one or more programmed ringtones or one or more combinations thereof), a visual indication such as a blinking light of the LED indicator, a solid light on the LED indicator maintained at a predetermined or programmed or programmable time period (for example, 5 seconds), each of which may be pre-programmed in the on-body patch device, or alternatively programmable by the user through the user interface of the reader device/receiver unit when in communication with the on-body patch device.
- In a further aspect, when an alarm or alert condition is detected (for example, a detected glucose level monitored by the analyte sensor that is outside a predetermined acceptable range indicating a physiological condition which requires attention or intervention for medical treatment or analysis (for example, a hypoglycemic condition, a hyperglycemic condition, an impending hyperglycemic condition or an impending hypoglycemic condition)), the one or more output indications may be generated in the on-body patch device and presented to the patient or the user so that corrective action may be timely taken. Alternatively, the output indications may be additionally or alternatively presented or output on the reader device/receiver unit when, for example, the reader device/receiver unit is within range of the on-body patch device
- In certain aspects, future or anticipated analyte levels may be predicted based on information obtained, e.g., the current analyte level, the rate of change of the analyte level and analyte trend information. Predictive alarms may be programmed or programmable in the reader device/receiver unit, or the on-body patch device, or both, and may be configured to notify the user of a predicted analyte levels that may be of concern in advance of the user's analyte level reaching the future level. This provides the user an opportunity to take corrective action.
- Before the present disclosure is described in additional detail, it is to be understood that this disclosure is not limited to particular embodiments described, as such may, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting, since the scope of the present disclosure will be limited only by the appended claims.
- Where a range of values is provided, it is understood that each intervening value, to the tenth of the unit of the lower limit unless the context clearly dictates otherwise, between the upper and lower limit of that range and any other stated or intervening value in that stated range, is encompassed within the disclosure. The upper and lower limits of these smaller ranges may independently be included in the smaller ranges is also encompassed within the disclosure, subject to any specifically excluded limit in the stated range. Where the stated range includes one or both of the limits, ranges excluding either or both of those included limits are also included in the disclosure.
- Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this disclosure belongs. Although any methods and materials similar or equivalent to those described herein can also be used in the practice or testing of the present disclosure, the preferred methods and materials are now described. All publications mentioned herein are incorporated herein by reference to disclose and describe the methods and/or materials in connection with which the publications are cited.
- It must be noted that as used herein and in the appended claims, the singular forms “a”, “an”, and “the” include plural referents unless the context clearly dictates otherwise.
- The publications discussed herein are provided solely for their disclosure prior to the filing date of the present application. Nothing herein is to be construed as an admission that the present disclosure is not entitled to antedate such publication by virtue of prior disclosure. Further, the dates of publication provided may be different from the actual publication dates which may need to be independently confirmed.
- As will be apparent to those of skill in the art upon reading this disclosure, each of the individual embodiments described and illustrated herein has discrete components and features which may be readily separated from or combined with the features of any of the other several embodiments without departing from the scope or spirit of the present disclosure.
- The figures shown herein are not necessarily drawn to scale, with some components and features being exaggerated for clarity.
- Generally, embodiments of the present disclosure relate to methods and devices for detecting at least one analyte such as glucose in body fluid. In certain embodiments, the present disclosure relates to the continuous and/or automatic in vivo monitoring of the level of an analyte using an analyte sensor.
- Accordingly, embodiments include analyte monitoring devices and systems that include an analyte sensor—at least a portion of which is positionable beneath the skin of the user—for the in vivo detection, of an analyte, such as glucose, lactate, and the like, in a body fluid. Embodiments include wholly implantable analyte sensors and analyte sensors in which only a portion of the sensor is positioned under the skin and a portion of the sensor resides above the skin, e.g., for contact to a transmitter, receiver, transceiver, processor, etc. The sensor may be, for example, subcutaneously positionable in a patient for the continuous or periodic monitoring of a level of an analyte in a patient's interstitial fluid.
- For the purposes of this description, continuous monitoring and periodic monitoring will be used interchangeably, unless noted otherwise. Discrete monitoring as used herein includes the acquisition or reception of monitored analyte data where real time monitored analyte level information is received or acquired on demand or in response to a request to the on-body patch device including sensor and sensor electronics. That is, embodiments include analyte sensors and sensor electronics which sample and process analyte related information based on a programmed or programmable schedule such as every minute, every five minutes and so on. Such analyte monitoring routines may be reported or transmitted in real time to the receiver unit/reader device at the time of data sampling and processing. Alternatively, as discussed, the continuously sampled analyte data and processed analyte related signals may be stored and transmitted to a remote location such as the receiver unit, data processing module, the data processing terminal, the reader device or the remote terminal in response to a request for such information from the remote location. The analyte level may be correlated and/or converted to analyte levels in blood or other fluids. In certain embodiments, an analyte sensor may be positioned in contact with interstitial fluid to detect the level of glucose, which detected glucose may be used to infer the glucose level in the patient's bloodstream. Analyte sensors may be insertable into a vein, artery, or other portion of the body containing fluid. Embodiments of the analyte sensors of the subject disclosure may be configured for monitoring the level of the analyte over a time period which may range from minutes, hours, days, weeks, or longer.
- Of interest are analyte sensors, such as glucose sensors, that are capable of in vivo detection of an analyte for about one hour or more, e.g., about a few hours or more, e.g., about a few days of more, e.g., about three or more days, e.g., about five days or more, e.g., about seven days or more, e.g., about several weeks or at least one month. Future analyte levels may be predicted based on information obtained, e.g., the current analyte level at time t0, the rate of change of the analyte, etc. Predictive alarms may notify the user of predicted analyte levels that may be of concern prior in advance of the analyte level reaching the future level. This enables the user an opportunity to take corrective action. Embodiments include transmission of the acquired real time analyte information on-demand from the user (using for example, the reader device/receiver unit positioned in close proximity to the low profile on-body patch device), storage of the acquired real time analyte information, and subsequent transmission based on retrieval from the storage device (such as a memory device).
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FIG. 1 shows a data monitoring and management system such as, for example, an analyte (e.g., glucose) monitoring system in accordance with certain embodiments of the present disclosure. Embodiments of the subject disclosure are described primarily with respect to glucose monitoring devices and systems, and methods of glucose detection, for convenience only and such description is in no way intended to limit the scope of the disclosure. It is to be understood that the analyte monitoring system may be configured to monitor a variety of analytes at the same time or at different times. - Analytes that may be monitored include, but are not limited to, acetyl choline, amylase, bilirubin, cholesterol, chorionic gonadotropin, creatine kinase (e.g., CK-MB), creatine, DNA, fructosamine, glucose, glutamine, growth hormones, hormones, ketones, lactate, peroxide, prostate-specific antigen, prothrombin, RNA, thyroid stimulating hormone, and troponin. The concentration of drugs, such as, for example, antibiotics (e.g., gentamicin, vancomycin, and the like), digitoxin, digoxin, drugs of abuse, theophylline, and warfarin, may also be monitored. In those embodiments that monitor more than one analyte, the analytes may be monitored at the same or different times.
- Referring to
FIG. 1 , theanalyte monitoring system 100 includes asensor 101, a data processing unit (e.g., sensor electronics) 102 connectable to thesensor 101, and aprimary receiver unit 104 which is configured to communicate with thedata processing unit 102 via acommunication link 103. In aspects of the present disclosure, thesensor 101 and the data processing unit (sensor electronics) 102 may be configured as a singleintegrated assembly 110. In certain embodiments, the integrated sensor andsensor electronics assembly 110 may be configured as an on-body patch device. In such embodiments, the on-body patch device may be configured for, for example, RFID or RF communication with a reader device/receiver unit. - In certain embodiments, the
primary receiver unit 104 may be further configured to transmit data to adata processing terminal 105 to evaluate or otherwise process or format data received by theprimary receiver unit 104. Thedata processing terminal 105 may be configured to receive data directly from thedata processing unit 102 via a communication link which may optionally be configured for bi-directional communication. Further, thedata processing unit 102 may include a transmitter or a transceiver to transmit and/or receive data to and/or from theprimary receiver unit 104, thedata processing terminal 105 or optionally thesecondary receiver unit 106. - Also shown in
FIG. 1 is an optionalsecondary receiver unit 106 which is operatively coupled to the communication link and configured to receive data transmitted from thedata processing unit 102. Thesecondary receiver unit 106 may be configured to communicate with theprimary receiver unit 104, as well as thedata processing terminal 105. Thesecondary receiver unit 106 may be configured for bi-directional wireless communication with each of theprimary receiver unit 104 and thedata processing terminal 105. As discussed in further detail below, in certain embodiments thesecondary receiver unit 106 may be a de-featured receiver as compared to theprimary receiver unit 104, i.e., thesecondary receiver unit 106 may include a limited or minimal number of functions and features as compared with theprimary receiver unit 104. As such, thesecondary receiver unit 106 may include a smaller (in one or more, including all, dimensions), compact housing or embodied in a device such as a wrist watch, arm band, etc., for example. Alternatively, thesecondary receiver unit 106 may be configured with the same or substantially similar functions and features as theprimary receiver unit 104. Thesecondary receiver unit 106 may include a docking portion to be mated with a docking cradle unit for placement by, e.g., the bedside for night time monitoring, and/or bi-directional communication device. - Only one
sensor 101,data processing unit 102 anddata processing terminal 105 are shown in the embodiment of theanalyte monitoring system 100 illustrated inFIG. 1 . However, it will be appreciated by one of ordinary skill in the art that theanalyte monitoring system 100 may include more than onesensor 101 and/or more than onedata processing unit 102, and/or more than onedata processing terminal 105. Multiple sensors may be positioned in a patient for analyte monitoring at the same or different times. In certain embodiments, analyte information obtained by a first positioned sensor may be employed as a comparison to analyte information obtained by a second sensor. This may be useful to confirm or validate analyte information obtained from one or both of the sensors. Such redundancy may be useful if analyte information is contemplated in critical therapy-related decisions. In certain embodiments, a first sensor may be used to calibrate a second sensor. - The
analyte monitoring system 100 may be a continuous monitoring system, or semi-continuous, or a discrete monitoring system. In a multi-component environment, each component may be configured to be uniquely identified by one or more of the other components in the system so that communication conflict may be readily resolved between the various components within theanalyte monitoring system 100. For example, unique IDs, communication channels, and the like, may be used. - In certain embodiments, the
sensor 101 is physically positioned in or on the body of a user whose analyte level is being monitored. Thesensor 101 may be configured to at least periodically sample the analyte level of the user and convert the sampled analyte level into a corresponding signal for transmission by thedata processing unit 102. - The
data processing unit 102 is coupleable to thesensor 101 so that both devices are positioned in or on the user's body, with at least a portion of theanalyte sensor 101 positioned transcutaneously. Thedata processing unit 102 in certain embodiments may include a portion of the sensor 101 (proximal section of the sensor in electrical communication with the data processing unit 102) which is encapsulated within or on the printed circuit board of thedata processing unit 102 with, for example, potting material or other protective material. Thedata processing unit 102 performs data processing functions, where such functions may include but are not limited to, filtering and encoding of data signals, each of which corresponds to a sampled analyte level of the user, for transmission to theprimary receiver unit 104 via thecommunication link 103. In one embodiment, thesensor 101 or thedata processing unit 102 or a combined sensor/data processing unit may be wholly implantable under the skin layer of the user. - In one aspect, the
primary receiver unit 104 may include an analog interface section including an RF receiver and an antenna that is configured to communicate with thedata processing unit 102 via thecommunication link 103, and a data processing section for processing the received data from thedata processing unit 102 such as data decoding, error detection and correction, data clock generation, and/or data bit recovery. - In operation, the
primary receiver unit 104 in certain embodiments is configured to synchronize with thedata processing unit 102 to uniquely identify thedata processing unit 102, based on, for example, an identification information of thedata processing unit 102, and thereafter, to periodically receive signals transmitted from thedata processing unit 102 associated with the monitored analyte levels detected by thesensor 101. That is, when operating in the CGM mode, thereceiver unit 104 in certain embodiments is configured to automatically receive time spaced analyte related data packets from the analyte sensor/sensor electronics when the communication link (e.g., RF range) is maintained between these components. - Referring again to
FIG. 1 , thedata processing terminal 105 may include a personal computer, a portable data processing devices or computers such as a laptop computer or a handheld device (e.g., personal digital assistants (PDAs), communication devices such as a cellular phone (e.g., a multimedia and Internet-enabled mobile phone such as an iPhone, a Blackberry device, a Palm device such as Palm Pre, Treo, or similar phone), mp3 player, pager, and the like), drug delivery device, each of which may be configured for data communication with the receiver via a wired or a wireless connection. Additionally, thedata processing terminal 105 may further be connected to a data network (not shown) for storing, retrieving, updating, and/or analyzing data corresponding to the detected analyte level of the user. - The
data processing terminal 105 may include an infusion device such as an insulin infusion pump or the like, which may be configured to administer insulin to patients, and which may be configured to communicate with theprimary receiver unit 104 for receiving, among others, the measured analyte level. Alternatively, theprimary receiver unit 104 may be configured to integrate an infusion device therein so that theprimary receiver unit 104 is configured to administer insulin (or other appropriate drug) therapy to patients, for example, for administering and modifying basal profiles, as well as for determining appropriate boluses for administration based on, among others, the detected analyte levels received from thedata processing unit 102. An infusion device may be an external device or an internal device (wholly implantable in a user). - In particular embodiments, the
data processing terminal 105, which may include an insulin pump, may be configured to receive the analyte signals from thedata processing unit 102, and thus, incorporate the functions of theprimary receiver unit 104 including data processing for managing the patient's insulin therapy and analyte monitoring. In certain embodiments, thecommunication link 103 as well as one or more of the other communication interfaces shown inFIG. 1 may use one or more of an RF communication protocol, an infrared communication protocol, a Bluetooth enabled communication protocol, an 802.11x wireless communication protocol, or an equivalent wireless communication protocol which would allow secure, wireless communication of several units (for example, per HIPPA requirements) while avoiding potential data collision and interference. - As described in aspects of the present disclosure, the analyte monitoring system may include an on-body patch device with a thin profile that can be worn on the arm or other locations on the body (and under clothing worn by the user or the patient), the on-body patch device including an analyte sensor and circuitry and components for operating the sensor and processing and storing signals received from the sensor as well as for communication with the reader device. For example, one aspect of the on-body patch device may include electronics to sample the voltage signal received from the analyte sensor in fluid contact with the body fluid, and to process the sampled voltage signals into the corresponding glucose values and/or store the sampled voltage signal as raw data.
- In certain embodiments, the on-body patch device includes an antenna such as a loop antenna to receive RF power from the an external device such as the reader device/receiver unit described above, electronics to convert the RF power received via the antenna into DC (direct current) power for the on-body patch device circuitry, communication module or electronics to detect commands received from the reader device, and communication component to transmit data to the reader device, a low capacity battery for providing power to sensor sampling circuitry (for example, the analog front end circuitry of the on-body patch device in signal communication with the analyte sensor), one or more non-volatile memory or storage device to store data including raw signals from the sensor or processed data based on the raw sensor signals. More specifically, in the on operation demand mode, the on body patch device in certain embodiments is configured to transmit real time analyte related data and/or stored historical analyte related data when within the RF power range of the reader device. As such, when the reader device is removed of positioned out of range relative to the on body patch device, the on body patch device may no longer transmit the analyte related data.
- In certain embodiments, a data processing module/terminal may be provided in the analyte monitoring system that is configured to operate as a data logger, interacting or communicating with the on-body patch device by, for example, transmitting requests for analyte level information to the on-body patch device, and storing the responsive analyte level information received from the on-body patch device in one or more memory components of the data processing module. Further, data processing module may be configured as a compact on-body relay device to relay or retransmit the received analyte level information from the on-body patch device to the reader device/receiver unit or the remote terminal or both. The data processing module in one aspect may be physically coupled to the on-body patch device, for example, on a single adhesive patch on the skin surface of the patient. Alternatively, the data processing module may be positioned close to but not in contact with the on-body patch device. For example, when the on-body patch device is positioned on the abdomen of the patient, the data processing module may be worn on a belt of the patient or the user, such that the desired close proximity or predetermined distance of approximately 1-5 inches (or about 1-10 inches, for example, or more) between the on-body patch device and the data processing module may be maintained.
- The various processes described above including the processes operating in the software application execution environment in the analyte monitoring system including the on-body patch device, the reader device, data processing module and/or the remote terminal performing one or more routines described above may be embodied as computer programs developed using an object oriented language that allows the modeling of complex systems with modular objects to create abstractions that are representative of real world, physical objects and their interrelationships. The software required to carry out the inventive process, which may be stored in a memory or storage device of the storage unit of the various components of the analyte monitoring system described above in conjunction to the Figures including the on-body patch device, the reader device, the data processing module, various described communication devices, or the remote terminal may be developed by a person of ordinary skill in the art and may include one or more computer program products.
- In one embodiment, an apparatus for bi-directional communication with an analyte monitoring system may comprise a storage device having stored therein one or more routines, a processing unit operatively coupled to the storage device and configured to retrieve the stored one or more routines for execution, a data transmission component operatively coupled to the processing unit and configured to transmit data based at least in part on the one or more routines executed by the processing unit, and a data reception component operatively coupled to the processing unit and configured to receive analyte related data from a remote location and to store the received analyte related data in the storage device for retransmission, wherein the data transmission component is programmed to transmit a query to a remote location, and further wherein the data reception component receives the analyte related data from the remote location in response to the transmitted query when one or more electronics in the remote location transitions from an inactive state to an active state upon detection of the query from the data transmission component.
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FIG. 2 illustrates a data monitoring and management system for real time glucose measurement data acquisition and processing in one aspect of the present disclosure. More specifically, as shown inFIG. 2 , the on-body patch device 211 including sensor electronics coupled to ananalyte sensor 250 is positioned on askin surface 210 of a patient or a user. In one aspect, an introducer mechanism may be provided, as discussed in further detail below in conjunction withFIGS. 12A-12G , for the transcutaneous placement of theanalyte sensor 250 such that when the on-body patch device 211 is positioned on the skin surface, a portion of thesensor 250 is inserted through the skin surface and in fluid contact with a body fluid of the patient or the user under theskin layer 210. - The introducer mechanism may be fully or partially automated, for example with a trigger mechanism, or may be fully or partially manual such that the
sensor 250 is positioned transcutaneously by a manual operation of the user. That is, in one aspect, the on-body patch device 211 may include an introducer needle and/or lumen (and/or catheter) which may guide thesensor 250 during the insertion process through theskin layer 210. In a further aspect, the placement of the on-body patch device 211 on theskin layer 210 includes the initial piercing of theskin layer 210 with a force applied on the on-body patch device 211 in conjunction with the on-body patch device 211 placement on theskin layer 210, effectively driving the sensor 250 (and/or the introducer) through theskin layer 210. Within the scope of the present disclosure, a mechanism (such as a spring, for example) may be provided within the on-body patch device 211 or alternatively, in the introducer in cooperation with the on-body patch device 211, to withdraw the introducer needle after thesensor 250 has been positioned in fluid contact with the body fluid. In certain other embodiments, a lumen may be provided, with theanalyte sensor 250 provided within the hollow cavity of the lumen for insertion, and maintained in position with the on-body patch device 211 during the time period that the on-body patch device 211 is worn on theskin layer 210. - Referring back to
FIG. 2 , as shown, when the reader device/receiver unit 220 is positioned or placed in close proximity and within a predetermined range of the on-body patch device 211, the RF power supply in the reader device/receiver unit 220 may be configured to provide the necessary power to operate the electronics in the on-body patch device 211, and the on-body patch device 211 may be configured to, upon detection or the RF power from the reader device/receiver unit 220, perform preprogrammed routines including, for example, transmitting one ormore signals 240 to the reader device/receiver unit 220 indicative of the sampled analyte level measured by theanalyte sensor 250. - In certain embodiments, the reader device/
receiver unit 220 may include an RF power switch that is user activatable or activated upon positioning within a predetermined distance from the onbody patch device 211 to turn on the analyte sensor in the onbody patch device 211. That is, using the RF signal, the analyte sensor coupled to the sensor electronics in the on-body patch device 211 may be initialized or activated. In another embodiment, a passive RFID function may be provided or programmed such that upon receiving a “turn on” signal which, when authenticated, will turn on the electronic power switch that activates the on-body patch device 211. That is, the passive RFID configuration may include drawing energy from the RF field radiated from the reader device/receiver unit 220 so as to prompt for and/or detect the “turn on” signal which, upon authentication, activates the onbody patch device 211. - In one embodiment, communication and/or RF power transfer between the reader device/
receiver unit 220 and the on-body patch device 211 may be automatically initiated when the reader device/receiver unit 220 is placed in close proximity to the on-body patch device 211 as discussed above. Alternatively, the reader device/receiver unit 220 may be configured such that user activation, such as data request initiation and subsequent confirmation by the user using, for example, thedisplay 222 and/orinput components 221 of the reader device/receiver unit 220, may be required prior to the initiation of communication and/or RF power transfer between the reader device/receiver unit 220 and the on-body patch device 211. In a further embodiment, the reader device/receiver unit 220 may be user configurable between multiple modes, such that the user may choose whether the communication between the reader device/receiver unit 220 and on-body patch device 211 is performed automatically or requires a user activation and/or confirmation. - As further shown in
FIG. 2 , the reader device/receiver unit 220 may includedisplay 222 or output component to provide output indication to the user or the patient, including, for example, the corresponding glucose level measurement. Thedisplay 222 of the reader device/receiver unit 220 may be additionally configured to provide the functionalities of a user interface to present other information such as alarm or alert notification to the user. In one aspect, the reader device/receiver unit 220 may include other output components such as a speaker, vibratory output component and the like to provide audible and/or vibratory output indication to the user in addition to the visual output indication provided on thedisplay 222. Moreover, the reader device/receiver unit 220 may also include one or more input components 221 (such as, for example, push buttons, switches, capacitive sliders, jog wheels, etc.) for receiving input commands or information from the user or the patient by operation of theinput components 221. In one embodiment, thedisplay 222 and theinput component 221 may be integrated into a single component, for example as a touch screen display. In such an embodiment, the user may be able to manipulate the reader device/receiver unit 220 by utilizing a set of pre-programmed motion commands, including, but not limited to, single or double tapping the display, dragging a finger or instrument across the display, motioning multiple fingers toward one another, motioning multiple fingers away from one another, etc. Other embodiments include the use of “soft buttons”, whereby theinput components 221 correspond to dynamic menus on thedisplay 222 to control features and operation of the reader device/receiver unit 220. In yet another embodiment, theinput component 221 may include a microphone and the reader device/receiver unit 220 may include software configured to analyze audio input received from the microphone, such that functions and operation of the reader device/receiver unit 220 may be controlled audibly by the user or patient. - As discussed, some or all of the electronics in the on-
body patch device 211 in one embodiment may be configured to rely on the RF power received from the reader device/receiver unit 220 to perform analyte data processing and/or transmission of the processed analyte information to the reader device/receiver unit 220. That is, the on-body patch device 211 may be discreetly worn on the body of the user or the patient, and under clothing, for example, and when desired, by positioning the reader device/receiver unit 220 within a predetermined distance from the on-body patch device 211, real time glucose level information may be received by the reader device/receiver unit 220. This routine may be repeated as desired by the patient (or on-demand, for example) to determine glucose levels at any time during the time period that the on-body patch device 211 is worn by the user or the patient. - Referring still to
FIG. 2 , also shown are a data processing module/terminal 260 and aremote terminal 270. In one aspect, data processing module 260 may include a stand alone device configured for bi-directional communication to communicate with the on-body patch device 211, the reader device/receiver unit 220 and/or theremote terminal 270. More specifically, data processing module 260 may include one or more microprocessors or similar data processing components configured to execute one or more software routines for communication, as well as data storage and retrieval to and from one or more memory components provided in the housing of the data processing module 260. - The data processing module 260 in one embodiment may be configured to communicate with the on-
body patch device 211 in a similar manner as the reader device/receiver unit 220 and may include communication components such as antenna, power supply and memory, among others, for example, to allow provision of RF power to the on-body patch device 211 or to request or prompt the on-body patch device 211 to send the current analyte related data and optionally other stored analyte related data. The data processing module 260 may be configured to interact with the on-body patch device 211 in a similar manner as the reader device/receiver unit 220 such that the data processing module 260 may be positioned within a predetermined distance from the on-body patch device 211 for communication with the on-body patch device 211. - In one aspect, the on-
body patch device 211 and the data processing module 260 may be positioned on the skin surface of the user or the patient within the predetermined distance of each other (for example, within approximately 5 inches or less) such that the communication between the on-body patch device 211 and the data processing module 260 is maintained. In a further aspect, the housing of the data processing module 260 may be configured to couple to or cooperate with the housing of the on-body patch device 211 such that the two devices are combined or integrated as a single assembly and positioned on the skin surface. - Referring again to
FIG. 2 , the data processing module 260 may be configured or programmed to prompt or ping the on-body patch device 211 at a predetermined time interval such as once every minute, or once every five minutes or once every 30 minutes or any other suitable or desired programmable time interval to request analyte related data from the on-body patch device 211 which is received and is stored in one or more memory devices or components of the data processing module 260. In another embodiment, the data processing module 260 is configured to prompt or ping the on-body patch device 211 when desired by the patient or the user on-demand, and not based on a predetermined time interval. In yet another embodiment, the data processing module 260 is configured to prompt or ping the on-body patch device 211 when desired by the patient or the user upon request only after a programmable time interval has elapsed. For example, in certain embodiments, if the user does not initiate communication within a programmed time period, such as, for example 5 hours from last communication (or 10 hours from the last communication), the data processing module 260 may by programmed to automatically ping or prompt the on-body patch device 211 or alternatively, initiate an alarm function to notify the user that an extended period of time has elapsed since the last communication between the data processing module 260 and the on-body patch device 211. In this manner, users, healthcare providers, or the patient may program or configure the data processing module 260 to provide certain compliance with analyte monitoring regimen, so that frequent determination of analyte levels is maintained or performed by the user. Similar functionalities may be provided or programmed in the receiver unit or the reader device in certain embodiments. - As further shown in
FIG. 2 , the data processing module 260 in one aspect may be configured to transmit the stored data received from the on-body patch device 211 to the reader device/receiver unit 220 when communication between the data processing module 260 and the reader device/receiver unit 220 is established. More specifically, in addition to RF antenna and RF communication components described above, data processing module 260 may include components to communicate using one or more wireless communication protocols such as, for example, but not limited to, infrared (IR) protocol, Bluetooth protocol, Zigbee protocol, and 802.11 wireless LAN protocol. Additional description of communication protocols including those based on Bluetooth protocol and/or Zigbee protocol can be found in U.S. Patent Publication No. 2006/0193375 incorporated herein by reference for all purposes. The data processing module 260 may further include communication ports, drivers or connectors to establish wired communication with one or more of the reader device/receiver unit 220, on-body patch device 211, or theremote terminal 270 including, for example, but not limited to USB connector and/or USB port, Ethernet connector and/or port, FireWire connector and/or port, or RS-232 port and/or connector. - In one aspect, the data processing module 260 may be configured to operate as a data logger configured or programmed to periodically request or prompt the on-
body patch device 211 to transmit the analyte related information, and to store the received information for later retrieval or subsequent transmission to the reader device/receiver unit 220 or to theremote terminal 270 or both, for further processing and analysis. Further, the memory or storage component in the data processing module 260 may be sufficiently large to store or retain analyte level information over an extended time period, for example, coinciding with the usage life of theanalyte sensor 250 in the on-body patch device 211. In this manner, the analyte monitoring system described above in conjunction withFIGS. 1 and 2 may be configured to operate in a CGM (continuous glucose monitoring) mode such that a continuous, time spaced monitored analyte level may be received from the on-body patch device 211 and stored in the data processing module 260. The stored data in the data processing module 260 may be subsequently provided to or transmitted to the reader device/receiver unit 220, theremote terminal 270 or the like for further analysis such as identifying frequency of periods of glycemic level excursions over the monitored time period to improve or enhance therapy related decisions. Using this information, the doctor, healthcare provider or the patient may adjust or recommend modification to the diet, daily habits and routines such as exercise, and the like. - In a further aspect, the functionalities of the data processing module 260 may be configured or incorporated into a memory device such as an SD card, microSD card, compact flash card, XD card, Memory Stick card, Memory Stick Duo card, or USB memory stick/device including software programming resident in such devices to execute upon connection to the respective one or more of the on-
body patch device 211, theremote terminal 270 or the reader device/receiver unit 220. In a further aspect, the functionalities of the data processing module 260, including executable software and programming, may be provided to a communication device such as a mobile telephone including, for example, iPhone, iTouch, Blackberry device, Palm based device (such as Palm Pre, Treo, Treo Pro, Centro), personal digital assistants (PDAs) or any other communication enabled operating system (such as Windows or Android operating systems) based mobile telephones as a downloadable application for execution by the downloading communication device. To this end, theremote terminal 270 as shown inFIG. 2 may include a personal computer, or a server terminal that is configured to provide the executable application software to the one or more of the communication devices described above when communication between theremote terminal 270 and the devices are established. In still a further aspect, the executable downloadable application may be provided over-the-air (OTA) as an OTA download such that wired connection to theremote terminal 270 is not necessary. In this configuration, the executable application may be automatically downloaded as an available download to the communication device, and depending upon the configuration of the communication device, installed on the device for use automatically, or based on user confirmation or acknowledgement on the communication device to execute the installation of the application. - Depending upon the user setting or configuration on the communication device, the downloaded application may be programmed or customized using the user interface of the respective communication device (screen, keypad, and the like) to establish or program the desired settings such as hyperglycemia alarm, hypoglycemia alarm, sensor replacement alarm, sensor calibration alarm, or any other alarm or alert conditions as may be desired by the user. Moreover, the programmed notification settings on the communication device may be output using the output components of the respective communication devices, such as speaker, vibratory output component, or visual output/display. As a further example, the communication device may be provided with programming and application software to communicate with the on-
body patch device 211 such that a frequency or periodicity of data acquisition is established. In this manner, the communication device may be configured to conveniently receive analyte level information from the on-body patch device 211 at predetermined time periods such as, for example, but not limited to once every minute, once every five minutes, or once every 10 or 15 minutes, and store the received information, as well as to provide real time display of the monitored or received analyte level information and other related output display such as trend indication of the analyte level (for example, based on the received analyte level information), projection of future analyte levels based on the analyte trend, and any other desired or appropriate warning indication or notification to the user or the patient. - Information, such as trend information, for example, may be output on one or more of the reader device/
receiver unit 220, data processing module 260,remote terminal 270, or any other connected device with output capabilities. Trend, and other, information may be output on a display unit of a device, for example thedisplay 222 of the reader device/receiver unit 220. Trend information may be displayed as, for example, a graph (such as a line graph) to indicate to the user or patient the current, historical, and predicted future analyte levels as measured and predicted by the analyte monitoring system. Trend information may also be displayed as trend arrows, indicating whether the analyte level is increasing or decreasing as well as the acceleration or deceleration of the increase or decrease in analyte level. This information may be utilized by the user or patient to determine any necessary corrective actions to ensure the analyte level remains within an acceptable and/or clinically safe range. Other visual indicators, including colors, flashing, fading, etc., as well as audio indicators including a change in pitch, volume, or tone of an audio output and/or vibratory or other tactile indicators may also be incorporated into the display of trend data as means of notifying the user or patient of the current level and/or direction and/or rate of change of the level of the monitored analyte. - Additionally, when integrated with the functionalities of the data processing module 260, the communication devices described above may be programmed to operate in the optional CGM mode to receive the time spaced monitored analyte level information from the on-
body patch device 211. - Referring back to the
remote terminal 270 ofFIG. 2 , in one aspect, software updates such as software patches, firmware updates or driver upgrades, among others, to the reader device/receiver unit 220, on-body patch device 211 or the data processing module 260 may be provided by theremote terminal 270 when communication between theremote terminal 270 and the reader device/receiver unit 220 and/or the data processing module 260 is established. In still another aspect, software upgrades, programming changes or modification to the on-body patch device 211 may be received from theremote terminal 270 by one or more of the reader device/receiver unit 220 or the data processing module 260, and thereafter, provided to the on-body patch device 211 by the reader device/receiver unit 220 or the data processing module 260. -
FIG. 3 is a block diagram of a receiver/monitor unit such as that shown inFIG. 1 in accordance with certain embodiments. The primary receiver unit 104 (FIG. 1 ) includes one or more of: a blood glucosetest strip interface 301, anRF receiver 302, aninput 303, atemperature detection section 304, and aclock 305, each of which is operatively coupled to a processing andstorage section 307. Theprimary receiver unit 104 also includes a power supply 306 operatively coupled to a power conversion andmonitoring section 308. Further, the power conversion andmonitoring section 308 is also coupled to thereceiver processor 307. Moreover, also shown are a receiverserial communication section 309, and anoutput 310, each operatively coupled to the processing andstorage unit 307. The receiver may include user input and/or interface components or may be free of user input and/or interface components. - In certain embodiments, the
test strip interface 301 includes a glucose level testing portion to receive a blood (or other body fluid sample) glucose test or information related thereto. For example, the interface may include a test strip port to receive a glucose test strip. The device may determine the glucose level of the test strip, and optionally display (or otherwise notice) the glucose level on theoutput 310 of theprimary receiver unit 104. Any suitable test strip may be employed, e.g., test strips that only require a very small amount (e.g., one microliter or less, e.g., about 0.5 microliter or less, e.g., about 0.1 microliter or less), of applied sample to the strip in order to obtain accurate glucose information, e.g. FreeStyle® or Precision® blood glucose test strips and systems from Abbott Diabetes Care Inc. Glucose information obtained by the in vitro glucose testing device may be used for a variety of purposes, computations, etc. For example, the information may be used to calibratesensor 101, confirm results of thesensor 101 to increase the confidence thereof (e.g., in instances in which information obtained bysensor 101 is employed in therapy related decisions), etc. - In one aspect, the
RF receiver 302 is configured to communicate, via the communication link 103 (FIG. 1 ) with the data processing unit (sensor electronics) 102, to receive encoded data from thedata processing unit 102 for, among others, signal mixing, demodulation, and other data processing. Theinput 303 of theprimary receiver unit 104 is configured to allow the user to enter information into theprimary receiver unit 104 as needed. In one aspect, theinput 303 may include keys of a keypad, a touch-sensitive screen, and/or a voice-activated input command unit, and the like. Thetemperature monitor section 304 may be configured to provide temperature information of theprimary receiver unit 104 to the processing andcontrol section 307, while theclock 305 provides, among others, real time or clock information to the processing andstorage section 307. - Each of the various components of the
primary receiver unit 104 shown inFIG. 3 is powered by the power supply 306 (or other power supply) which, in certain embodiments, includes a battery. Furthermore, the power conversion andmonitoring section 308 is configured to monitor the power usage by the various components in theprimary receiver unit 104 for effective power management and may alert the user, for example, in the event of power usage which renders theprimary receiver unit 104 in sub-optimal operating conditions. Theserial communication section 309 in theprimary receiver unit 104 is configured to provide a bi-directional communication path from the testing and/or manufacturing equipment for, among others, initialization, testing, and configuration of theprimary receiver unit 104. -
Serial communication section 104 can also be used to upload data to a computer, such as time-stamped blood glucose data. The communication link with an external device (not shown) can be made, for example, by cable (such as USB or serial cable), infrared (IR) or RF link. The output/display 310 of theprimary receiver unit 104 is configured to provide, among others, a graphical user interface (GUI), and may include a liquid crystal display (LCD) for displaying information. Additionally, the output/display 310 may also include an integrated speaker for outputting audible signals as well as to provide vibration output as commonly found in handheld electronic devices, such as mobile telephones, pagers, etc. In certain embodiments, theprimary receiver unit 104 also includes an electro-luminescent lamp configured to provide backlighting to theoutput 310 for output visual display in dark ambient surroundings. - Referring back to
FIG. 3 , theprimary receiver unit 104 may also include a storage section such as a programmable, non-volatile memory device as part of theprocessor 307, or provided separately in theprimary receiver unit 104, operatively coupled to theprocessor 307. Theprocessor 307 may be configured to perform Manchester decoding (or other protocol(s)) as well as error detection and correction upon the encoded data received from thedata processing unit 102 via thecommunication link 103. - In further embodiments, the
data processing unit 102 and/or theprimary receiver unit 104 and/or thesecondary receiver unit 105, and/or the data processing terminal/infusion section 105 may be configured to receive the blood glucose value wirelessly over a communication link from, for example, a blood glucose meter. In further embodiments, a user manipulating or using the analyte monitoring system 100 (FIG. 1 ) may manually input the blood glucose value using, for example, a user interface (for example, a keyboard, keypad, voice commands, and the like) incorporated in the one or more of thedata processing unit 102, theprimary receiver unit 104,secondary receiver unit 105, or the data processing terminal/infusion section 105. - Additional detailed descriptions are provided in U.S. Pat. Nos. 5,262,035; 5,264,104; 5,262,305; 5,320,715; 5,593,852; 6,175,752; 6,650,471; 6,746,582, 6,284,478, 7,299,082, and in application Ser. No. 10/745,878 filed Dec. 26, 2003 titled “Continuous Glucose Monitoring System and Methods of Use”, and in application Ser. No. 11/060,365 filed Feb. 16, 2005 titled “Method and System for Providing Data Communication in Continuous Glucose Monitoring And Management System” each of which is incorporated herein by reference.
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FIG. 4 is a block diagram of a reader device/receiver unit such as that shown inFIG. 2 in one aspect of the present disclosure. Referring toFIG. 4 , in one aspect the reader device/receiver unit includes acontrol unit 410, such as one or more microprocessors, operatively coupled to adisplay 430 and auser interface 420. The reader device/receiver unit may also include one or more data communication ports such as USB port (or connector) 470 or RS-232 port 450 (or any other wired communication ports) for data communication with other devices such as a personal computer, a server, a mobile computing device, a mobile telephone, a pager, or other handheld data processing devices including smart phones such as Blackberry, iPhone and Palm based mobile devices, with data communication and processing capabilities including data storage and output. - Referring to
FIG. 4 , apower supply 440, such as one or more batteries, is also provided and operatively coupled to thecontrol unit 410 and configured to provide the necessary power to the reader device/receiver unit for operation. In addition, referring still again toFIG. 4 , the reader device/receiver unit may include aloop antenna 481 such as a 433 MHz (or other equivalent) loop antenna coupled to a receiver processor 480 (which may include a 433 MHz receiver chip, for example) for wireless communication with the sensor electronics in the on-body patch device/sensor data processing unit. Additionally, a primaryinductive loop antenna 491 is provided and coupled to asquarewave driver 490 which is operatively coupled to thecontrol unit 410. - Referring still to
FIG. 4 , the reader device/receiver unit of the analyte monitoring system may include astrip port 460 configured to receive an in vitro test strip, thestrip port 460 coupled to thecontrol unit 410, and further, where thecontrol unit 410 includes programming to process the sample on the in vitro test strip which is received in thestrip port 460. Furthermore, within the scope of the present disclosure some of the components of the reader device/receiver unit shown inFIG. 4 may be integrated as a single component such as theuser interface 420 and thedisplay 430 may be configured as a single touch sensitive display which may be configured to include soft buttons of the display itself, operable by the user or the patient for providing input commands or information to the reader device. - In one aspect, the reader device/receiver unit of the analyte monitoring system described herein may be configured to include a compact form factor, similar to a USB memory device, where the
USB port 470 may be configured as a USB connector for insertion or connection to a USB port on another device such as a personal computing device or the like. Such compact form factor may include some or all of the components of the reader device/receiver unit described above. -
FIG. 5 is an exemplary schematic of an on-body patch device including an integrated sensor and sensor electronics assembly for use in the analyte monitoring systems ofFIGS. 1 and 2 in one aspect of the present disclosure. As shown inFIG. 5 , the integrated sensor and sensor electronics assembly/on-body patch device of the analyte monitoring system, in one aspect, may include aloop antenna 520 for transmitting the analyte related data to the reader device/receiver unit and further, an inductivepower loop antenna 530 for processing the RF power from the reader device/receiver unit, and including converting the RF power to corresponding DC power for the operation of the electronics of the on-body patch device. In this manner, in one aspect of the present disclosure, the on-body patch device may be configured to operate as a passive data transmitter, adopting inductive coupling power without a separate power supply or battery for data transmission. Furthermore, the on-body patch device in one aspect does not require a mechanism to turn the device in operational mode nor to deactivate or turn off the on-body patch device. That is, the on-body patch device may be configured to enter an active or operational mode when it detects the RF power from the reader device. Further shown inFIG. 5 is a plurality of super capacitors C1, C2 coupled to the inductivepower loop antenna 530 and thecontroller 510. Referring still toFIG. 5 , thecontroller 510 may be provided on a printed circuit board assembly including theloop antenna 520, thermistor (not shown), analyte sensor contact pads for coupling to the electrodes of thesensor 540, one or more storage devices such as non-volatile memory (not shown), and other discrete components. In certain aspects, the printed circuit board assembly may be partially or fully encapsulated with, for example, potting material. -
FIG. 6 is a block diagram of the integrated sensor and sensor electronics assembly for use in the analyte monitoring systems ofFIGS. 1 and 2 in another aspect of the present disclosure. Referring toFIG. 6 , in certain aspects of the present disclosure, the on-body patch device includes a control unit 610 (such as, for example but not limited to, one or more microprocessors, and/or application specific integrated circuits (ASICs)), operatively coupled to analogfront end circuitry 670 to process signals such as raw voltage or current signals received from thesensor 680. Also shown inFIG. 6 is amemory 620 operatively coupled to thecontrol unit 610 for storing data and/or software routines for execution by thecontrol unit 610. That is, thecontrol unit 610 may be configured to access the data or routines stored in thememory 620 to update, store or replace information in thememory 620, in addition to retrieving one or more stored routines for execution. Also shown inFIG. 6 is apower supply 660 which, in certain embodiments, provides power to the electronics of the on-body patch device for operation, under the control of thecontrol unit 610, to process signals from thesensor 680 and to store the processed sensor data for subsequent transmission to the reader device/receiver unit when prompted or pinged by the reader device/receiver unit for transmission of the stored data in addition to the real time analyte level data. As discussed above, in certain embodiments, the on-body patch device does not include thepower supply 660 and is configured to rely upon the RF power from the reader device. - Additionally, an
optional output unit 650 is provided to the on-body patch device as shown inFIG. 6 . In certain embodiments, theoutput unit 650 may include an LED indicator, for example, to alert the user or the patient of one or more predetermined conditions associated with the operation of the on-body patch device and/or the determined analyte level. For example, in one aspect, the on-body patch device may be programmed or configured to provide a visual indication to notify the user of one or more predetermined operational conditions of the on-body patch device. The one or more predetermined operational conditions may be configured by the user or the patient or the healthcare provider, so that certain conditions are associated with an output indication on the on-body patch device. By way of nonlimiting example, the on-body patch device may be programmed to assert a notification using the LED indicator on the on-body patch device when signals from thesensor 680 are indicated to be beyond a programmed acceptable range (based on one sampled sensor data point, or multiple sensor data points), potentially indicating a health risk condition such as hyperglycemia or hypoglycemia, or the onset of such conditions. With such prompt or indication, the user or the patient may be timely informed of such potential condition, and using the reader device, acquire the glucose level information from the on-body patch device to confirm the presence of such conditions so that timely corrective actions may be taken. - In certain embodiments, the on-body patch device may include a speaker or an audible output component instead of or in addition to the LED indicator to provide an audible indication of one or more such conditions described above. The type of audible output may be programmed or programmable in the on-body patch device, for example, via the reader device, and may include a standard audible tone (monotone or multi tone), or include one or more ring tones provided to the on-body patch device. In certain embodiments, different conditions may be associated with a different type of audible output/alert such that the patient or the user may easily recognize the underlying detected condition based on the type of audible notification. For example, different levels of audible tones may be associated (programmed by the user or the patient, or pre-programmed in the on-body patch device) with different conditions such that when asserted, each outputted tone may be easily recognized by the user or the patient as an indication of the particular associated condition. That is, the detected onset of hyperglycemic condition based on the signal from the analyte sensor may be associated with a first predetermined loudness and/or tone, while the detected onset of hypoglycemic condition based on the signal from the analyte sensor may be associated with a second predetermined loudness and/or tone. Alternatively, the programmed or programmable audible alerts may include one or more sequence of audible outputs that are output based on a temporally spaced sequence or a sequence indicating an increase or decrease in the level of loudness (using the same tone, or gradually increasing/decreasing tones).
- Furthermore, in aspects of the present disclosure the audible output indication may be asserted in conjunction with the visual output indicator, simultaneously or alternatingly, as may be customized or programmable in the on-body patch device or pre-programmed.
- Referring again to
FIG. 6 , theantenna 630 and thecommunication module 640 operatively coupled to thecontrol unit 610 may be configured to detect and process the RF power when in predetermined proximity to the reader device/receiver unit providing the RF power, and further, in response, to transmit the analyte level information and optionally analyte trend information based on stored analyte level data, to the reader device. In certain aspects, the trend information may includes a plurality of analyte level information over a predetermined time period that are stored in thememory 620 of the on-body patch device and provided to the reader device/receiver unit with the real time analyte level information. For example, the trend information may include a series of time spaced analyte level data for the time period since the last transmission of the analyte level information to the reader device. Alternatively, the trend information may include analyte level data for the prior 30 minutes or one hour that are stored inmemory 620 and retrieved under the control of thecontrol unit 610 for transmission to the reader device. - Referring back to the Figures, in one aspect the on-body patch device and the reader device/receiver unit may be configured to communicate using RFID (radio frequency identification) techniques where the reader device/receiver unit is configured to interrogate the on-body patch device (associated with an RFID tag) over an RF communication link, such that the on-body patch device, in response to the RF interrogation signal from the reader device, transmits an RF response signal including, for example, data associated with the sampled analyte level from the sensor. Additional information regarding the operation of RFID communication can be found in U.S. Patent Publication No. 2009/0108992 and U.S. Pat. No. 7,545,272, the disclosure of which are incorporated herein by reference.
- For example, in one embodiment, the reader device/receiver unit may include a backscatter RFID reader configured to transmit an RF field such that when the on-body patch device is within the transmitted RF field, its antenna is tuned and in turn provides a reflected or response signal (for example, a backscatter signal) to the reader device. The reflected or response signal may include sampled analyte level data from the analyte sensor.
- In one aspect, the reader device/receiver unit may be configured such that when the reader device/receiver unit is positioned in close proximity to the on-body patch device and receives the response signal from the on-body patch device, the reader device/receiver unit is configured to output an indication (audible, visual or otherwise) to confirm the analyte level measurement acquisition. That is, during the course of the 5 to 10 days of wearing the on-body patch device on the body, the user or the patient may at any time position the reader device/receiver unit within a predetermined distance (for example, approximately 1-5 inches) from the on-body patch device, and after waiting a few seconds, output an audible indication confirming the receipt of the real time analyte level information. The received analyte information may be output to the display 430 (
FIG. 4 ) of the reader device/receiver unit for presentation to the user or the patient. - As shown above, the on-body patch device is configured to be worn over a predetermined time period on the body of the user or the patient. Accordingly, certain embodiments described below include configurations of the on-body patch device to provide for a compact configuration which is configured to remain adhered to the skin surface for the predetermined wear time period comfortably and without detaching from the skin surface. For example, in one aspect, the on-body patch device may include a single integrated housing or body assembly that includes the analyte sensor, electronics and an adhesive path. Such configuration provides for fewer parts that require manipulation by the patient or the user, leading to improved ease of use, and further, with an overmolded assembly, may be configured to provide the desired water tight seal during the course of the wear, preventing moisture or other contaminants from entering into the on-body patch device housing. Such single body configurations may additionally provide ease of manufacturing with the fewer components that require assembly.
- In a further aspect, the on-body patch device may include a two part assembly including a reusable electronics component mated or coupled (detachably or fixedly) to a disposable component including the analyte sensor, a base or mount for the electronics component, and the adhesive patch.
-
FIG. 7 is a schematic of the reader device/receiver unit for use in the analyte monitoring systems ofFIGS. 1 and 2 in accordance with one aspect of the present disclosure. Referring to the Figure, the reader device/receiver unit 220 (FIG. 2 ) or the handheld controller in accordance with one aspect of the present disclosure, includes a surface acoustic wave (SAW)resonator 701 which may includes a resonator that generates the RF signal operating in conjunction with an oscillator (OSC) 702. Theoscillator 702 is the active RF transistor component, and in conjunction with theSAW resonator 701, is configured to send out control commands (the ping signals), transmit the RF power to receive the backscatter signal from the on-body patch unit, and generate local oscillation signal to themixer 703, as described in further detail below. - More specifically, in one aspect of the present disclosure, in operation, the transmit data (TX data) as shown is the control signal received from the
control unit 410 of the reader device/receiver unit (see e.g.,FIG. 4 ) and received from the power amplifier (PA) 706 is the RF control command to be transmitted to the on-body patch device. TheSAW resonator 701 in one embodiment is configured to provide the carrier signal for the control commands (ping signals). The control signal from thecontrol unit 410 in one embodiment include data packets that are to be transmitted to the on-body patch device to ping it to return a response signal back to the reader device. - In one embodiment, before the control signal is sent, a turn on signal from the
control unit 410 is received at the TX enable line (as shown inFIG. 7 ) and provided to theoscillator 702. After the control signal from thecontrol unit 410 is provided to theoscillator 702 and theSAW resonator 701, the carrier signal which is used to carry the control signal is maintained. The same carrier signal in one embodiment may be used to receive the response data packet from the on-body patch device. When the RF control signal is provided to the on-body patch device using the loop antenna and over the carrier signal, the RF power is provided at the same time (radiation energy) where the RF power is generated by theoscillator 702 in conjunction with theSAW resonator 701. In certain aspects, because the carrier signal is maintained during transmit/receive time periods between the reader device/receiver unit and the on-body patch device, the RF power is provided during the ping (or control signal) request transmission of the RF control signal and also during the time period when the backscatter response is received from the on-body patch device. In certain aspects, the reader device/receiverunit loop antenna 708 uses the same carrier signal to transmit the RF power and the RF control signal to the on-body patch device. - Referring back to
FIG. 7 , further shown is anLC power splitter 704 which his configured in one aspect of the present disclosure, to split the power two ways to thebuffer 705 and to the power amplifier (PA) 706. Thebuffer 705 in one embodiment is configured to boost the RF signal received fromLC power splitter 704. Output of thepower amplifier 706 is the control command that is provided to a secondLC power splitter 707 which splits the antenna signal (from the loop antenna into transmit signal (the control signal) and the receive signal (backscatter signal from the on-body patch device)). That is, in one embodiment, the secondLC power splitter 707 may be configured to manage the transmit/receive signals using oneloop antenna 708. Referring again toFIG. 7 , abalun 709 provided between theloop antenna 708 and the secondLC power splitter 707 is used in one embodiment to match the balanced signal from theloop antenna 708 to the unbalanced signal from the power splitter 707 (as most circuit components are unbalanced relative to ground terminal). Thebalun 709 includes, in one embodiment, an electrical transformer that can convert electrical signals that are balanced about ground (differential) to signals that are unbalanced (single-ended), and vice versa, using electromagnetic coupling for operation. - Referring still to
FIG. 7 , theloop antenna 708 transmits the RF control signal (the ping signal) and in response, receives a backscatter signal from the on-body patch device. In one aspect, the received backscatter response signal by the loop antenna is passed through thebalun 709, and to thepower splitter 707 to theSAW filter 711.SAW filter 711 in one aspect includes a bandpass filter configured to remove noise or interference components in the received backscatter signal, for example. The output of theSAW filter 711 is passed throughASK receiver 720. In one aspect, theASK receiver 720 includes a low noise amplifier (LNA) 721 whose output is sent tomixer 703 which mixes the low noise amplified signal output from theLNA 721 with the RF carrier signal from thebuffer 705. - The output of the
mixer 703 is passed to the high pass filter (HPF) 712 that filters out the DC component and low frequency components of the signal, and then the output of theHPF 712 is sent to the intermediate frequency amplifier (IF amplifier) 713 which is configured to amplify the received signal. The amplified output signal from theIF amplifier 713 is provided to the low pass filter (LPF) 722 of theASK receiver 720, and the output low pass filtered signal fromLPF 722 is provided to anotherintermediate frequency amplifier 723 of theASK receiver 720 which is configured to amplify the low pass filtered signal output from theLPF 722. As shown inFIG. 7 , theIF amplifier 723 of theASK receiver 720 is provided between theLPF 722 and theASK demodulator 724. - Referring yet still to
FIG. 7 , the gain controller signal from IFamplifier 723 of theASK receiver 720 controls the low noise amplifier (LNA) 721 that receives the filtered backscatter signal. The gain controller signal in one embodiment switches between high gain and low gain state of theLNA 721. For example, if IFamplifier 723 has high gain, then the gain controller signal to theLNA 721 switches theLNA 721 to low gain operation, and vice versa. As discussed above, the output of theIF amplifier 723 of theASK receiver 720 is provided to the ASK demodulator 724 of theASK receiver 720 which is configured to demodulate (or recover the data) the output signal from theIF amplifier 723. - That is, as shown in
FIG. 7 , the RX enable line to theASK receiver 720 is configured to turn on after the TX enable line where the turn on signal from the control unit 410 (FIG. 4 ) is received in the reader device/receiver unit such that with the receive enable signal from thecontrol unit 410, the data out line (i.e., the output of the ASK demodulator 724) of theASK receiver 720 provides the data or signal associated with the monitored glucose level based on the raw current signals from the glucose sensor. - Referring back to the Figures and as described above, in one aspect, the on-body patch device may include a power supply to power the electronic components as well as the sensor, or alternatively, the on-body patch device may not includes a separate dedicated power supply and rather, include a self-powered sensor as described in further detail in U.S. patent application Ser. No. 12/393,921 filed Feb. 27, 2009 and incorporated by reference herein for all purposes. In certain aspects, for configurations of the on-body patch device that includes a power supply, the on-body patch device may be configured to listen for the RF control command (ping signal) from the reader device. More specifically, an On/Off Key (OOK) detector may be provided in the on-body patch device which is turned on and powered by the battery to listen for the RF control command or the ping signal from the reader device. Additional details if the OOK detector are provided in U.S. Patent Publication No. 2008/0278333, the disclosure of which is incorporated by reference for all purposes. In certain aspects, when the RF control command is detected, on-body patch device determines what response packet is necessary, and generates the response packet for transmission back to the reader device. In this embodiment, the sensor is always turned on and configured to continuously receive power from the power supply or the battery of the on-body patch device. However, the sampled current signal from the sensor may not be transmitted out to the reader device/receiver unit until the on-body patch device receives the RF power (from the reader device/receiver unit) to enable the transmission of the data to the reader device. In one embodiment, the battery may be a rechargeable battery configured to be charged when the on-body patch device received the RF power (from the reader device/receiver unit).
- In certain embodiments, the on-body patch device does not include an RF communication chip, nor any other dedicated communication chip to allow for wireless transmission separate from being powered on based on the RF power received from the reader device/receiver unit and transmitting the backscatter response packet to the reader device.
- Referring again to
FIG. 7 , in a further embodiment of the present disclosure, an RF transmitter chip or an ASK transmitter may be provided to the reader device/receiver unit 220 (FIG. 2 ) to replace theSAW resonator 701, theoscillator 702, themixer 703, theLC power splitter 704, thebuffer 705, thepower amplifier 706, the high pass filter (HPF) 712, and theIF amplifier 713 shown inFIG. 7 . More specifically, in this embodiment of the reader device, the RF transmitter chip may be coupled to a crystal which provides the frequency reference base for generating the RF carrier signal to receive the backscatter from the on-body patch device, and also to send the control commands (ping signals) to the on-body patch device. - In the embodiment discussed above, in aspects of the present disclosure, the RF transmitter chip or unit may be coupled to the LC power splitter, a balun and the loop antenna similar to the
LC power splitter 707, thebalun 709, and theloop antenna 708 shown inFIG. 7 , in addition to a SAW filter and ASK receiver similar to theSAW filter 711 andASK receiver 720 shown inFIG. 7 . However, in contrast to the configuration shown inFIG. 7 , in the alternate embodiment, another crystal may be coupled to the ASK receiver to provide the frequency reference base for receiving the backscatter signal from the on-body patch device. -
FIGS. 8A and 8B illustrate a top view and a side view, respectively, of antenna and electronic circuit layout of the on-body patch device including an sensor and sensor electronics assembly for use in the analyte monitoring systems ofFIGS. 1 and 2 in one aspect of the present disclosure. Referring toFIGS. 8A and 8B , the loop antenna and circuit layout of the on-body patch device in one embodiment includes aconductive layer 801, such as a PCB copper trace, provided on asubstrate 802, and further includes, a plurality of inductors 803 a-803 e disposed on the substrate and electrically connected to theconductive layer 801 in a loop configuration. In one aspect, the inductors 803 a-803 e are spaced equidistantly from each other around the loop configuration. In a further aspect, the inductors 803 a-803 e may not be equidistantly spaced apart from each other in the loop configuration. Also shown inFIGS. 8A and 8B is a data processor orcontroller 804 in electrical communication with theconductive layer 801 for processing signals from the sensor (not shown) and interfacing with the sensor in addition to processing the control commands from the reader device/receiver unit and generating and/or transmitting the backscatter response data packet to the reader device. - Accordingly, in aspects of the present disclosure, loop antenna configurations are provided for a passive glucose sensor and a low power glucose reader device/receiver unit at Ultra High Frequency (UHF) frequency bands, providing an on-demand glucose data acquisition system that includes the reader device/receiver unit which is configured to generate a strong near electromagnetic field to power the passive glucose sensor, and further provide a weak far electromagnetic field such that the strength of the generated magnetic field at a far distance, such as approximately 3 meters away from the on-body patch device, including the sensor is in compliance with the regulated radiation level.
- In certain embodiments, the on-body patch device antenna may be printed as an internal conductive layer of a printed circuit board surrounded by the ground plane on the top and bottom layers. That is, in one aspect, the top and bottom conductive layers may be separated by layers of dielectrics and a conductive layer of loop antenna disposed therebetween. Further, the antenna for the on-body patch device may be printed on the top conductive layer of the printed circuit in series with a plurality of inductors chips, such as, for example, but not limited to, five inductor elements.
-
FIG. 9 illustrates an exemplary circuit schematic of the on-body patch device including an sensor and sensor electronics assembly in accordance with aspects of the present disclosure. Referring to the Figure, in one embodiment thesensor contacts 910 are provided to establish contact with the various electrodes of the sensor including working electrode, reference electrode and counter electrode. Also shown is anRF transmission antenna 920 operatively coupled to thecontrol unit 950. In certain embodiments, thecontrol unit 950 may be implemented as application specific integrated circuits (ASICs), or include microprocessors or both. Anactivation switch 930, described in further detail below, is also shown inFIG. 9 along the electrical path from thepower supply 940 for switching on or turning on the sensor electronics of the on-body patch device. - Referring still to
FIG. 9 , also shown in analog front end circuitry/components 970 coupled to thesensor contacts 910 for processing the raw current signals generated by the analyte sensor and detected at thesensor contacts 910. Additionalpassive storage capacitors 960 coupled to the power supply such as a battery is shown. In addition,crystal oscillators FIG. 9 , where in certain embodiments,crystal oscillator 980 is configured to provide clock signals for the state machine in theASIC 950, whilecrystal oscillator 990 may be configured to provide frequency reference for the RF communication components within theASIC 950. -
FIG. 10A is a perspective view of the components of the an on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure. Referring toFIG. 10A , an integrated sensor and sensor electronics assembly/on-body patch device 110 ofFIG. 1 in one embodiment is shown. As can be seen, thehousing 1010 in one embodiment is substantially shaped such that the height profile is minimized (for example, to less than or equal to approximately 10 mm, e.g., about 4 mm or less). For example, as shown in the figures, the housing of the integrated assembly may have a dome-like shape, or otherwise tapered shape. A height dimension may be at most about 4 mm, and may taper (gradually or step wise) to heights less than about 4 mm, e.g., 3 mm or less, e.g., 2 mm or less, e.g., 1 mm or less. - Referring back to
FIG. 10A , in one embodiment, theanalyte sensor 1020 is assembled (e.g., provided to the user) with thesensor electronics 1030 and provided within thehousing 1010. Furthermore an adhesive (single sided or two sided) layer 1040 (FIG. 10C ) may be provided on a lower surface of thehousing 1010 to provide secure positioning of thehousing 1010 on the skin surface during and after sensor deployment. As discussed in further detail below, the integrated sensor and sensor electronics assembly/on-body patch device 110 may be positioned (e.g., during manufacture to provide to the user) within the housing of an insertion device, avoiding the need for a user to align, position, or otherwise connect or couple the sensor and sensor electronics to the insertion device prior to the insertion of the sensor and turning on the sensor electronics. Accordingly, potential misuse, misalignment of the sensor relative to the introducer of the insertion device, or errors and difficulties in use of the integrated assembly by the user may be avoided. -
FIG. 10B is another perspective view of the components of the on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure. As shown in the Figure, each component of the integrated assembly is separated to illustrate the relative position of each component, in one embodiment. As discussed in further detail below, it can be seen in one embodiment that thesensor 1020 includes a bent configuration, whereby at least a portion of the body of the sensor is maintained in a direction substantially planar to the surface of the skin. In one aspect, this configuration allows for the low profile dimension of thehousing 1010 that includes thesensor 1020 such that the protrusion of thehousing 1010, when positioned on the skin surface of the user, is minimized. Accordingly, thesensor 1020 may be bent, or may be bendable, from about 1 degree to about 90 degrees or more. -
FIG. 10C is another perspective view of the assembled on-body patch device including sensor and sensor electronics assembly in accordance with one aspect of the present disclosure. As shown inFIG. 10C , after positioning the integrated sensor and sensor electronics assembly, theadhesive layer 1040 may be configured to substantially fixedly retain theintegrated assembly 110 on the skin surface such that movement of thesensor 1020 during the course of wearing the device is minimized. In one aspect, theadhesive layer 1040 may be configured to provide a substantially water tight seal between theintegrated assembly 110 and the skin surface during the predetermined time period of wear such that the likelihood of theintegrated assembly 110 detaching from the skin surface is minimized. -
FIGS. 11A-11C illustrate circuit layouts for the sensor electronics assembly in the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. Referring toFIGS. 11A-11C , embodiments of the sensor electronics of the integrated assembly includes dimensions that are optimized for reduction and thus maximized for comfort in use and wear. For example, embodiments of the sensor electronics shown inFIGS. 11A-11C may include a diameter of approximately 25 mm or less (typical size of a quarter coin, for example), e.g., 20 mm or less, or 15 mm or less. As shown, for example, the control unit including an application specific integrated circuit (ASIC) 1110 is provided in electrical contact with a plurality of RFcommunication transmission capacitors 1130 positioned, for example, substantially around the outer periphery of the flexible circuit board. Depending upon the size of the circuit board and/or RF transmission requirement,RF transmission capacitors 1130 of different capacitance may be provided. For example,FIG. 11A illustratesRF transmission capacitors 1130 of 600 μF, while theFIGS. 11B and 11C illustrateRF transmission capacitors 1130 having approximately 610 μF and 240 μF, respectively. - Referring back to the Figures, also shown is a
battery 1120 configured to provide the necessary power for the operation of the sensor electronics, and may include a single use coin-cell type battery that is disposable after single use, but which is sufficient to provide the necessary power to operate the integrated sensor and sensor electronics assembly 110 (FIG. 1 ) during the desired time period (for example, such as 5 days or 7 days or longer). Additionally, further shown inFIGS. 11A-11C areRF antennas 1140 that are positioned, in one embodiment substantially around the circumference of a portion of the flexible circuit board. - Accordingly, in aspects of the present disclosure, the circuit layout of the sensor electronics may be optimized to minimize the surface area of the circuit board (and thus the overall size of the integrated assembly), by positioning the various components in the manner as shown in
FIGS. 11A-11C . -
FIGS. 12A-12B illustrate pre-deployment and post insertion configurations of the insertion device for positioning the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. Referring toFIG. 12A ,insertion device 1200 in one embodiment includes a housing orbody 1210 and acap 1220 which is configured to provide closure or seal on the open end of the insertion device. As shown, theinsertion device 1200 may be configured for sensor insertion and sensor electronics assembly positioning in a direction substantially perpendicular to the skin surface. - Referring to
FIG. 12B , when a force, e.g., a manual force, is applied upon the top end of thehousing 1210 in the direction as shown byarrow 1240, and with the open end of the housing on theskin surface 1230, the integrated sensor and sensor electronics assembly provided within the housing (not shown) is configured to come into contact with theskin surface 1230. Furthermore, the force applied as discussed above also may be configured to move the introducer (not shown) within the housing in the same direction as shown byarrow 1240 to pierce theskin surface 1230 and position the sensor in fluid contact with an analyte of the user. - Further details of the mechanism associated with the insertion device for sensor insertion and sensor electronics assembly positioning is shown and described below in conjunction with
FIGS. 12C-12G which illustrate cross sectional perspective views of the operation of the insertion device for deploying the on-body integrated sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. - As shown in these figures, in response to the force applied on the
insertion device housing 1210, theintroducer 1260 is driven in a direction substantially perpendicular to theskin surface 1230, and along with the movement of theintroducer 1260, thesensor 1280 and thesensor electronics assembly 1270 are moved in the same direction. When the bottom surface of thesensor electronics assembly 1270 comes into contact with theskin surface 1230, the bottom surface is maintained in an adhered relationship with theskin surface 1230 by, for example, the adhesive layer 1290 (FIG. 12G ). Moreover, also shown in the Figures is abias spring 1250 which, in one embodiment, is configured to retract the introducer needle from the insertion position to a retracted position which is an opposite direction from the direction indicated by arrow 1240 (FIG. 12B ). - Referring back to the Figure, it can be seen that the
introducer needle 1260 is substantially and entirely retained within theinsertion device housing 1210 after sensor insertion, and thereafter, when theinsertion device 1200 is removed from theskin surface 1230, thesensor electronics assembly 1270 is retained on theskin surface 1230, while the position of thesensor 1280 is maintained in fluid contact with the analyte of the user under theskin layer 1230. - Prior to activation of the integrated sensor and sensor electronics assembly for use, there may be a period of time from the manufacturing that the assembly may be in sleep or idle mode. With a power supply such as a battery integrated within the assembly, for reasons including cost optimization and prolonging shelf life, embodiments of the present disclosure include systems that are activated merely by positioning the sensor and electronics unit on a skin surface as described above, i.e., no additional action need be required of the user other than applying a force to
housing 1210. As such, insertion of the sensor causes activation of the electronics unit. In certain embodiments, activation switch configurations are included which may be configured to be triggered, for example, by the insertion device activation, thereby turning on the integrated sensor and sensor electronics assembly into an active mode. - For example,
FIGS. 13A-13B illustrate embodiments of a power supply switch mechanism including conductive plugs of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. As shown, the sensor electronicsassembly circuit board 1310 may be provided with aphysical gap 1350 that breaks the electrical circuit between the power supply (e.g., battery) and the other circuitry of the sensor electronics assembly. - In one embodiment, when the predetermined force is applied on the insertion device as discussed above, a
conductive portion 1320 provided within the housing of the sensor electronics may be moved in a direction as shown byarrow 1330 such that electrical contact is established in thephysical gap 1350 on the circuit board, by for example, theconductive portion 1320 coming into physical contact with theconductive portions 1360 of the circuit board. In this manner, in one embodiment, the electrical path from the power supply and the remaining circuitry on the circuit board of the sensor electronics is completed, thereby powering the sensor electronics. - By way of another example, referring to
FIG. 13B , theconductive portions 1360 of the circuit board are provided on the board itself, and theconductive plug 1340, for example, when pushed into thecavity 1350, establishes electrical contact between theconductive portions 1360 of the circuit board. - In one embodiment, as discussed above, the actuation of the insertion device to position the sensor and sensor electronics assembly triggers the switch mechanism shown in
FIGS. 13A and 13B by also moving theconductive portion 1320 or theconductive plug 1360 in the direction complimentary to the direction of the introducer movement, and thereby switching on the sensor electronics. Within the scope of the present disclosure, the activation of the sensor electronics by moving theconductive portion 1320 or the conductive plug may include a separate procedure, where after positioning the sensor and the sensor electronics assembly on the skin surface, a predetermined force is applied on the housing of the integrated sensor and sensor electronics assembly such that the desired movement of theconductive portion 1320 or theconductive plug 1360 may be achieved. -
FIGS. 13C-13E illustrate another configuration of the power supply switch mechanism including conductive pads of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. Referring toFIG. 13C , an exposedconductive ring 1371 may be provided and configured to contact the surface of the circuit board in the sensor electronics such that, the insertion device activation positions theconductive ring 1371 on the surface of the circuit board so as to complete the electrical contact of the sensor electronics assembly (by for example, manual force applied on the insertion device placing the conductive ring in contact with the circuit board of the sensor electronics). - Referring to
FIG. 13D , in another aspect,electrical contact pads conductive ring 1371 switches on the sensor electronics device to provide power to the device from its power source.FIG. 13E shows yet another configuration of the switch activation mechanism in accordance with the present disclosure, where a portion of theconductive ring 1374 is selectively positioned and provided to establish electrical contact in the device. - As discussed, each of the activation configuration described above includes a break in the circuitry from the power source such that the power supply is not drained when the device is not in use, and upon activation, the break in the electrical contact is completed, thereby powering the device and activating it for operation.
-
FIG. 14 illustrates a power supply switch mechanism including an internal switch with a push rod activation of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. As shown, in one embodiment,push rod 1410 may be provided and positioned in the sensor electronics such that when a force is applied in the direction as shown byarrow 1430, thepush rod 1410 is displaced in the same direction, and completes the electrical contact between the twocontacts push rod 1410 may be provided within aseal 1440 such as an O-ring or similar components. -
FIG. 15 illustrates a power supply switch mechanism including introducer retraction trigger activation of the on-body integrated sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. As shown, a nonconducting needle ordevice 1510 is provided to physically separate twoelectrical contacts electrical contacts nonconducting needle 1510. Accordingly, when thenonconducting needle 1510 is retracted or pulled away from the sensor electronics assembly in the direction as shown byarrow 1530, the twoelectrical contacts - In one aspect, the nonconducting device or
needle 1510 may include, for example, but not limited to, glass, plastic or any other material suitable to separate two electrical contacts and provide insulation therebetween. -
FIG. 16 illustrates a power supply switch mechanism with a contact switch of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. As shown, in a further aspect, there is provided an electronic switch 1601 (that is configured to draw an insubstantial amount of power from the sensor electronics power supply), and when triggered, completes the break between thecontacts contacts activation component 1602 that completes the circuit in the sensor electronics from its power supply such as battery to activate the device for operation. -
FIGS. 17A-17B illustrate a power supply switch mechanism with a battery contact locking mechanism of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. Referring to the Figures, in still another aspect, the battery contact of the sensor electronics may be provided with abarbed tab 1710. In post manufacturing shelf mode when the device is nonoperational, thetab 1710 is positioned within the sensor electronics housing in the position as shown inFIG. 17A so that it is not in contact with theconductive contact 1720 of the sensor electronics circuit board. When in use as shown inFIG. 17B , thetab 1710 may be biased such that it physically contacts theconductive contact 1720 on the circuit board, thereby closing the circuit to/from the battery/power source and thus activating or switching on the sensor electronics. As shown in the Figures, thetab 1710 may be configured that upon biasing to establish contact with theconductive contact 1720, it locks or latches with the conductive contact 1620 and the circuit board so as to maintain the electrical connection. -
FIGS. 18A-18B illustrate a power supply switch mechanism with a bi-modal dome switch of the on-body patch device including sensor and sensor electronics assembly in accordance with embodiments of the present disclosure. Yet in another embodiment, a bi-modal dome shapedswitch 1810 is provided on the circuit board of the sensor electronics assembly such that, when pressed down (as shown inFIG. 18B ), the dome shaped layer 1810 (which may include, for example, a thin sheet metal dome) may be configured to retain the concave shape as shown inFIG. 18B and effectively closing the circuit on the circuit board at thecontact point 1820. In one aspect, the dome shapedlayer 1810 may be configured to shunt to short two or more electrical contacts at thecontact point 1820 of the circuit board. Alternatively, the dome shapedlayer 1810 may be connected to the circuit board such that one end of the dome shapedlayer 1810 is in contact with one of the two or more open electrical contacts, and the depression of the dome shapedlayer 1810 closes the circuit on the circuit board by physically contacting the other one or more of the open electrical contacts. - In the manner described above, in accordance with various embodiments of the present disclosure, sensor electronics activation switch configurations are provided that may be triggered or activated automatically or semi-automatically in response to the activation of the insertion device described above, or alternatively, may be separately activated by the user by, for example, depressing upon a portion of the housing or switch provided on the housing of the sensor electronics. Accordingly, power consumption may be optimized for the sensor electronics assembly while improving post manufacturing shelf life of the device prior to use or activation.
- As described above, in certain aspects of the present disclosure, discrete glucose measurement data may be acquired on-demand or upon request from the reader device, where the glucose measurement is obtained from an in vivo glucose sensor transcutaneously positioned under the skin layer of a patient or a subject, and further having a portion of the sensor maintained in fluid contact with the interstitial fluid under the skin layer. Accordingly, in aspects of the present disclosure, the patient or the user of the analyte monitoring system may conveniently determine real time glucose information at any time, using the RFID communication protocol as described above.
- In the manner described above, in accordance with various embodiments of the present disclosure, discrete glucose measurements may be obtained within the need for lancing or performing fingerprick test for access to blood sample each time a measurement is desired. The analyte monitoring system described in further aspects may be configured to log or store glucose data monitored by the analyte sensor continuously over a predetermined or programmable time period, or over the life of the sensor without user intervention, and which data may be retrieved at a later time as desired. Furthermore, output indications such as audible, visual or vibratory alerts may be provided to inform the user of a predetermined condition or when the monitored glucose level deviates from a predefined acceptable range (for example, as warning indication of low glucose or high glucose level).
- The various processes described above including the processes operating in the software application execution environment in the analyte monitoring system including the on-body patch device, sensor electronics, the reader device, the receiver unit, data processing module and/or the remote terminal performing one or more routines described above may be embodied as computer programs developed using an object oriented language that allows the modeling of complex systems with modular objects to create abstractions that are representative of real world, physical objects and their interrelationships. The software required to carry out the inventive process, which may be stored in a memory or storage device of the storage unit of the various components of the analyte monitoring system described above in conjunction to the Figures including the on-body patch device, the reader device, the data processing module, various described communication devices, or the remote terminal may be developed by a person of ordinary skill in the art and may include one or more computer program products.
- In still another aspect, the methods, devices and systems described above may be configured to log and store (for example, with an appropriate time stamp and other relevant information such as, for example, contemporaneous temperature reading)) the real time analyte data received from the analyte sensor, and may be configured to provide the real time analyte data on-demand by using, for example a device such as a blood glucose meter or a controller discussed above that is configured for communication with the on-body integrated sensor and sensor electronics assembly.
- That is, in one embodiment, real time data associated with the analyte being monitored is continuously or intermittently measured and stored in the integrated on-body sensor and sensor electronics assembly, and upon request from another device such as the receiver unit or the reader device/receiver unit (operated by the user, for example) or any other communication enabled device such as a cellular telephone, a personal digital assistant, an iPhone, a Blackberry device, a Palm device such as Palm Treo, Pro, Pre, Centro), or any other suitable communication enabled device which may be used to receive the desired analyte data from the on-body integrated sensor and sensor electronics assembly while being worn and used by the user. In one aspect, such communication enabled device may be positioned within a predetermined proximity to the integrated on-body sensor and sensor electronics assembly, and when the communication enabled device is positioned within the predetermined proximity, the data from the integrated on-body sensor and sensor electronics assembly may be transmitted to the communication enabled device. In one aspect, such data communication may include inductive coupling using, for example, electromagnetic fields, Zigbee protocol based communication, or any other suitable proximity based communication techniques. In this manner, glucose on-demand mode may be provided such that the information associated with contemporaneously monitored analyte level information is provided to the user on-demand from the user.
- In this manner, in embodiments of the present disclosure, the size and dimension of the on-body sensor electronics may be optimized for reduction by, for example, flexible or rigid potted or low pressure/low temperature overmolded circuitry that uses passive and active surface mount devices for securely positioning and adhering to the skin surface of the user. When flexible circuitry is with or in the overmold, the sensor electronics may includes the analyte sensor and/or other physiological condition detection sensor on the flex circuit. Furthermore in embodiments of the present disclosure, one or more printed RF antenna may be provided within the sensor electronics circuitry for RF communication with one or more remote devices, and further, the device operation and/or functionalities may be programmed or controlled using one or more a microprocessors, or application specific integrated circuits (ASIC) to reduce the number of internal components.
- Embodiments of the present disclosure include one or more low pressure molding materials that directly encapsulate the integrated circuits or the sensor electronic components. The thermal process entailed in the encapsulation using the low pressure molding materials may be configured to shield temperature sensitive components such as, for example, the analyte sensor or other components of the sensor electronics from the heat generated during the thermal overmolding process. Other techniques such as injection molding and/or potting may be used.
- In another aspect, the sensor electronics may be molded using optical techniques such as with a UV cured material, for example, or using two photon absorption materials, which may also be used to reduce the dead or unused volume surrounding the sensor electronics within the housing of the device such that the reduction of its size and dimension may be achieved. Moreover, the sensor electronics may be configured to reduce the number of components used, for example, by the inclusion of an application specific integrated circuit (ASIC) that may be configured to perform the one or more functions of discrete components such as a potentiostat, data processing/storage, thermocouple/thermister, RF communication data packet generator, and the like. Additionally, a field programmable gate array (FPGA) or any other suitable devices may be used in addition to the ASIC in the sensor electronics to reduce the on-body device dimension.
- Also, embodiments of the present disclosure includes analyte sensors that may be fabricated from flex circuits and integrated with the sensor electronics within the device housing, as a single integrated device. Example of flex circuits may include evaporated or sputtered gold on polyester layer, single or multi-layer copper or gold on polymide flex circuit. When the sensor fabricated from a copper or gold polymide flex circuit, gold or other inert material may be selectively plated on the implantable portion of the circuit to minimize the corrosion of the copper. In aspects of the present disclosure, the flex circuit may be die or laser cut, or alternatively chemically milled to define the sensor from the flex circuit roll.
- A further configuration of embodiments of the present disclosure includes RF communication module provided on the flex circuit instead of as a separate component in the sensor electronics. For example, the RF antenna may be provided directly on the flex circuit by, such as surrounding the sensor electronics components within the housing on the flex circuit, or folded over the components, and encapsulated with the electronic components within the housing of the device.
- In accordance with embodiments of the present disclosure, the integrated sensor and sensor electronics assembly may be positioned on the skin surface of the user using an insertion device. For example, automated or semi-automated, spring biased and/or manual insertion device may be provided to deploy the sensor and the sensor electronics such that the implantable portion of the sensor is positioned in fluid contact with the analyte of the user such as the interstitial fluid, while the housing of the sensor electronics is securely positioned and adhered to the skin surface. In embodiments of the present disclosure, the sensor electronics device (for example, a transmitter unit of an analyte monitoring system) may be switched to an operational state or condition (from an inactive, shelf mode) upon deployment of the integrated assembly by the insertion device.
- In one aspect, integrated sensor and sensor electronics assembly may be pre-loaded or otherwise pre-assembled within the insertion device, such that, when in use, the user may, by a single operation of the insertion device, deploy the integrated sensor and sensor electronics assembly, without the need to couple the integrated assembly with the insertion device prior to deployment.
- In one aspect, the integrated sensor and sensor electronics assembly and the insertion device may be sterilized and packaged as one single device and provided to the user. Furthermore, during manufacturing, the insertion device assembly may be terminal packaged providing cost savings and avoiding the use of, for example, costly thermoformed tray or foil seal. In addition, the inserter device may include an end cap that is rotatably coupled to the insertion device body, and which provides a safe and sterile environment (and avoid the use of desiccants for the sensor) for the sensor provided within the insertion device along with the integrated assembly. Also, the insertion device sealed with the end cap may be configured to retain the sensor within the housing from significant movement during shipping such that the sensor position relative to the integrated assembly and the insertion device is maintained from manufacturing, assembly and shipping, until the device is ready for use by the user.
- Moreover, as discussed above, the insertion device in embodiments of the present disclosure includes a sharp needle or introducer for aiding the transcutaneous insertion of the sensor through the skin layer of the user. The sharp needle or the introducer may be configured to be retracted within the insertion device housing after deployment to permit movement, such as tilting or angled movement, to position the adhesive on the housing of the sensor electronics onto the skin surface of the user without the introducer interfering such movement. Also, by retaining the introducer within the insertion device housing after insertion, the disposal of the used introducer may be safer, without presenting possible biohazard concerns.
- Also, in embodiments of the present disclosure the sharp needle or the introducer is not visible to the user prior to, during and after the use of the insertion device to position the sensor and the sensor electronics. As such, potential for perceived pain associated with when the sharp needle is visible is minimized.
- In a further embodiment, the insertion device may be configured for manual deployment with spring biased or automatic refraction of the introducer. That is, sensor insertion, the user may apply a predetermined amount of pressure upon the housing of the insertion device to insert the introducer and the sensor, the applied pressure sufficient to pierce through the skin layer of the user, and the device housing configured such that the applied pressure or the distance traveled by the introducer is predetermined (for example, by the use of a stopper or a protrusion within the inner wall of the insertion device that effectively stops of blocks further downward movement of the introducer towards the skin piercing direction after the introducer has reached a predetermined distance. In one aspect, the applied pressure may be configured to also press down upon a spring or a bias mechanism provided within the housing of the insertion device such that, when the applied pressure is released, the introducer is automatically retracted to its original pre-deployment position within the housing of the insertion device, by the return force from the spring or bias mechanism.
- In this manner, consistent and repeatable insertion depth for the placement of the analyte sensor may be achieved. Furthermore, the insertion device housing (for example, a plastic or a combination of plastic and metal housing) may not be under the stress of spring tension since the bias spring provided for refraction of the introducer is, in the predeployment state, unbiased and in a relaxed state.
- In a further embodiment, two sided adhesive layer may be provided along the other periphery of the insertion device that is positioned to be in contact with the skin surface of the user such that, proper alignment and positioning of the introducer, the sensor and the sensor electronics assembly may be provided before and during the sensor positioning process, in addition to increased comfort and breathability of the material once adhered to the skin layer of the user.
- In one embodiment, an integrated analyte monitoring device assembly may comprise an analyte sensor for transcutaneous positioning through a skin layer and maintained in fluid contact with an interstitial fluid under the skin layer during a predetermined time period, the analyte sensor having a proximal portion and a distal portion, and sensor electronics coupled to the analyte sensor, the sensor electronics comprising a circuit board having a conductive layer and a sensor antenna disposed on the conductive layer, one or more electrical contacts provided on the circuit board and coupled with the proximal portion of the analyte sensor to maintain continuous electrical communication, and a data processing component provided on the circuit board and in signal communication with the analyte sensor, the data processing component configured to execute one or more routines for processing signals received from the analyte sensor, the data processing component configured to control the transmission of data associated with the processed signals received from the analyte sensor to a remote location using the sensor antenna in response to a request signal received from the remote location.
- The proximal portion of the analyte sensor and the circuit board may be encapsulated.
- The proximal portion of the analyte sensor and the circuit board may be encapsulated with a potting material.
- The circuit board may include an upper layer and a lower layer, where the conductive layer is disposed between the upper layer and the lower layer.
- The antenna may include a loop antenna or a dipole antenna.
- The antenna may be printed on the conductive layer.
- In one aspect, the assembly may include a plurality of inductive components coupled to the sensor antenna on the conductive layer of the circuit board.
- The plurality of inductive components may be coupled in series to the sensor antenna.
- The plurality of inductive components may be positioned substantially around an outer edge of the circuit board.
- The circuit board may be substantially circular, and the plurality of components may be positioned around the outer circumference of the circular circuit board.
- Each of the plurality of the inductive components may be positioned substantially equidistant to each other on the circuit board.
- Moreover, the assembly may include a power supply to provide power to the sensor electronics.
- The data processing component may include an application specific integrated circuit (ASIC) disposed on the circuit board and configured to process signals from the analyte sensor.
- The data processing component may include a state machine.
- The state machine may be configured to execute one or more programmed or programmable logic for processing the signals received from the analyte sensor.
- The analyte sensor may include a glucose sensor.
- In another embodiment, an analyte data acquisition device may comprise a control unit configured to generate a control command based on a carrier signal, an antenna section coupled to the control unit to transmit the control command with the carrier signal and to receive a backscatter response data packet using the carrier signal, and a receiver section coupled to the antenna section and the control unit to process the received backscatter response data packet and to generate an output glucose data.
- The control unit may include a signal resonator coupled to an oscillator, and configured to generate RF power.
- The signal resonator may include a surface acoustic wave resonator.
- The generated RF power and the control command may be transmitted with the carrier signal.
- The control command may include an RF control command transmitted with the carrier signal to a remote location.
- The backscatter response data packet may be received from the remote location when the antenna is positioned no more than approximately ten inches from the remote location.
- The antenna may be positioned about five inches or less from the remote location.
- The antenna section may include one or more of a loop antenna, or a dipole antenna.
- The control unit may be configured to generate the carrier signal.
- The receiver section may include a filter to filter the received backscatter response data packet.
- A further aspect may include an output unit operatively coupled to the control unit to output an indication corresponding to the generated glucose data.
- The outputted indication may include one or more of a visual output, an audible output, a vibratory output, or one or more combinations thereof.
- The control unit may generate a receipt confirmation signal upon successful receipt of the backscatter response data packet.
- The generated receipt confirmation signal may be output to the user.
- In another aspect, the device may further include a storage device coupled to the control unit to store the generated control command, carrier signal, the received backscatter response data packet, the generated output glucose data, or one or more combinations thereof.
- The storage device may include a nonvolatile memory device.
- The control unit may include a microprocessor.
- The control unit may include an application specific integrated circuit.
- Yet another aspect may include a strip port for receiving an in vitro blood glucose test strip, the strip port including an electrical connection in signal communication with the control unit.
- The control unit may be configured to process a sample on the test strip to determine a corresponding blood glucose level.
- In another embodiment, an integrated analyte monitoring device may comprise a sensor electronics assembly including an analyte sensor, a power supply, an activation switch operatively coupled to the power supply and the analyte sensor, a controller unit in electrical contact with the analyte sensor and the activation switch having one or more programming instructions stored therein for execution, the controller unit configured to process one or more signals received from the analyte sensor when the activation switch is triggered, and an insertion device including a housing, an introducer coupled to the housing configured to move between a first position and a second position, and a bias mechanism operatively coupled to the housing configured to automatically retract the introducer from the second position to the first position.
- The sensor electronics assembly may be retained entirely within the housing of the insertion device prior to the introducer movement from the first position to the second position.
- The activation switch may be not triggered until the introducer has reached the second position.
- The analyte sensor may include a glucose sensor.
- The activation switch may be triggered after the introducer has reached the second position, and prior to the introducer retraction from the second position to the first position.
- The introducer may engage with the analyte sensor during its movement from the first position to the second position, and further, wherein the introducer disengages from the analyte sensor during its movement from the second position to the first position.
- The movement of the introducer from the first position to the second position may be in response to a manual force applied on the housing.
- The bias mechanism may include a spring.
- A further aspect may include an adhesive layer provided on a bottom surface of the housing for placement on a skin layer.
- The adhesive layer may be configured to retain the sensor electronics assembly on the skin layer for a predetermined time period.
- The power supply may include a single use disposable battery.
- The active operational life of the power supply may exceed the active operational life of the analyte sensor.
- Moreover, one aspect may include a cap configured to mate with an open end of the housing of the insertion device.
- When the cap is coupled to the housing, the interior space of the housing may be maintained in a substantially contaminant free environment.
- The sensor electronics assembly may include a printed circuit board including a portion of the analyte sensor permanently connected thereto.
- The controller unit may include an application specific integrated circuit (ASIC).
- The movement of the introducer between the first position and the second position may be at an angle at approximately 90 degrees or less from a skin surface.
- The sensor electronics assembly may include a housing having a height of less than approximately 4 mm.
- Various other modifications and alterations in the structure and method of operation of this disclosure will be apparent to those skilled in the art without departing from the scope and spirit of the embodiments of the present disclosure. Although the present disclosure has been described in connection with particular embodiments, it should be understood that the present disclosure as claimed should not be unduly limited to such particular embodiments. It is intended that the following claims define the scope of the present disclosure and that structures and methods within the scope of these claims and their equivalents be covered thereby.
Claims (54)
1. An integrated analyte monitoring device assembly, comprising:
an analyte sensor for transcutaneous positioning through a skin layer and maintained in fluid contact with an interstitial fluid under the skin layer during a predetermined time period, the analyte sensor having a proximal portion and a distal portion; and
sensor electronics coupled to the analyte sensor, the sensor electronics comprising:
a circuit board having a conductive layer and a sensor antenna disposed on the conductive layer;
one or more electrical contacts provided on the circuit board and coupled with the proximal portion of the analyte sensor to maintain continuous electrical communication; and
a data processing component provided on the circuit board and in signal communication with the analyte sensor, the data processing component configured to execute one or more routines for processing signals received from the analyte sensor, the data processing component configured to control the transmission of data associated with the processed signals received from the analyte sensor to a remote location using the sensor antenna in response to a request signal received from the remote location.
2. The assembly of claim 1 wherein the proximal portion of the analyte sensor and the circuit board are encapsulated.
3. The assembly of claim 2 wherein the proximal portion of the analyte sensor and the circuit board are encapsulated with a potting material.
4. The assembly of claim 1 wherein the circuit board includes an upper layer and a lower layer, where the conductive layer is disposed between the upper layer and the lower layer.
5. The assembly of claim 1 wherein the antenna includes a loop antenna or a dipole antenna.
6. The assembly of claim 1 wherein the antenna is printed on the conductive layer.
7. The assembly of claim 1 further including a plurality of inductive components coupled to the sensor antenna on the conductive layer of the circuit board.
8. The assembly of claim 7 wherein the plurality of inductive components are coupled in series to the sensor antenna.
9. The assembly of claim 7 wherein the plurality of inductive components are positioned substantially around an outer edge of the circuit board.
10. The assembly of claim 9 wherein the circuit board is substantially circular, and the plurality of components are positioned around the outer circumference of the circular circuit board.
11. The assembly of claim 7 wherein each of the plurality of the inductive components are positioned substantially equidistant to each other on the circuit board.
12. The assembly of claim 1 including a power supply to provide power to the sensor electronics.
13. The assembly of claim 1 wherein the data processing component includes an application specific integrated circuit (ASIC) disposed on the circuit board and configured to process signals from the analyte sensor.
14. The assembly of claim 1 wherein the data processing component includes a state machine.
15. The assembly of claim 14 wherein the state machine is configured to execute one or more programmed or programmable logic for processing the signals received from the analyte sensor.
16. The assembly of claim 1 wherein the analyte sensor includes a glucose sensor.
17. An analyte data acquisition device, comprising:
a control unit configured to generate a control command based on a carrier signal;
an antenna section coupled to the control unit to transmit the control command with the carrier signal and to receive a backscatter response data packet using the carrier signal; and
a receiver section coupled to the antenna section and the control unit to process the received backscatter response data packet and to generate an output glucose data.
18. The device of claim 17 wherein the control unit includes a signal resonator coupled to an oscillator, and configured to generate RF power.
19. The device of claim 18 wherein the signal resonator includes a surface acoustic wave resonator.
20. The device of claim 18 wherein the generated RF power and the control command are transmitted with the carrier signal.
21. The device of claim 17 wherein the control command includes an RF control command transmitted with the carrier signal to a remote location.
22. The device of claim 21 wherein the backscatter response data packet is received from the remote location when the antenna is positioned no more than approximately ten inches from the remote location.
23. The device of claim 22 wherein the antenna is positioned about five inches or less from the remote location.
24. The device of claim 17 wherein the antenna section includes one or more of a loop antenna, or a dipole antenna.
25. The device of claim 17 wherein the control unit is configured to generate the carrier signal.
26. The device of claim 17 wherein the receiver section includes a filter to filter the received backscatter response data packet.
27. The device of claim 17 including an output unit operatively coupled to the control unit to output an indication corresponding to the generated glucose data.
28. The device of claim 27 wherein the outputted indication includes one or more of a visual output, an audible output, a vibratory output, or one or more combinations thereof.
29. The device of claim 17 wherein the control unit generates a receipt confirmation signal upon successful receipt of the backscatter response data packet.
30. The device of claim 29 wherein the generated receipt confirmation signal is output to the user.
31. The device of claim 17 further including a storage device coupled to the control unit to store the generated control command, carrier signal, the received backscatter response data packet, the generated output glucose data, or one or more combinations thereof.
32. The device of claim 31 wherein the storage device includes a nonvolatile memory device.
33. The device of claim 17 wherein the control unit includes a microprocessor.
34. The device of claim 17 wherein the control unit includes an application specific integrated circuit.
35. The device of claim 17 further including a strip port for receiving an in vitro blood glucose test strip, the strip port including an electrical connection in signal communication with the control unit.
36. The device of claim 35 wherein the control unit is configured to process a sample on the test strip to determine a corresponding blood glucose level.
37. An integrated analyte monitoring device, comprising:
a sensor electronics assembly including:
an analyte sensor;
a power supply;
an activation switch operatively coupled to the power supply and the analyte sensor;
a controller unit in electrical contact with the analyte sensor and the activation switch having one or more programming instructions stored therein for execution, the controller unit configured to process one or more signals received from the analyte sensor when the activation switch is triggered; and
an insertion device including:
a housing;
an introducer coupled to the housing configured to move between a first position and a second position; and
a bias mechanism operatively coupled to the housing configured to automatically retract the introducer from the second position to the first position.
38. The device of claim 37 wherein the sensor electronics assembly is retained entirely within the housing of the insertion device prior to the introducer movement from the first position to the second position.
39. The device of claim 37 wherein the activation switch is not triggered until the introducer has reached the second position.
40. The device of claim 37 wherein the analyte sensor includes a glucose sensor.
41. The device of claim 37 wherein the activation switch is triggered after the introducer has reached the second position, and prior to the introducer refraction from the second position to the first position.
42. The device of claim 37 wherein the introducer engages with the analyte sensor during its movement from the first position to the second position, and further, wherein the introducer disengages from the analyte sensor during its movement from the second position to the first position.
43. The device of claim 37 wherein the movement of the introducer from the first position to the second position is in response to a manual force applied on the housing.
44. The device of claim 37 wherein the bias mechanism includes a spring.
45. The device of claim 37 including an adhesive layer provided on a bottom surface of the housing for placement on a skin layer.
46. The device of claim 45 wherein the adhesive layer is configured to retain the sensor electronics assembly on the skin layer for a predetermined time period.
47. The device of claim 37 wherein the power supply includes a single use disposable battery.
48. The device of claim 37 wherein the active operational life of the power supply exceeds the active operational life of the analyte sensor.
49. The device of claim 37 including a cap configured to mate with an open end of the housing of the insertion device.
50. The device of claim 49 wherein when the cap is coupled to the housing, the interior space of the housing is maintained in a substantially contaminant free environment.
51. The device of claim 37 wherein the sensor electronics assembly includes a printed circuit board including a portion of the analyte sensor permanently connected thereto.
52. The device of claim 37 wherein the controller unit includes an application specific integrated circuit (ASIC).
53. The device of claim 37 wherein the movement of the introducer between the first position and the second position is at an angle at approximately 90 degrees or less from a skin surface.
54. The device of claim 37 wherein the sensor electronics assembly includes a housing having a height of less than approximately 4 mm.
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---|---|---|---|---|
WO2009126942A2 (en) | 2008-04-10 | 2009-10-15 | Abbott Diabetes Care Inc. | Method and system for sterilizing an analyte sensor |
US20100064800A1 (en) * | 2008-07-17 | 2010-03-18 | Abbott Diabetes Care Inc. | Strip connectors for measurement devices |
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US8287495B2 (en) | 2009-07-30 | 2012-10-16 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
WO2012149466A2 (en) * | 2011-04-29 | 2012-11-01 | Proteus Biomedical, Inc. | Body associated device and method of making same |
WO2012154286A1 (en) | 2011-02-28 | 2012-11-15 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US20120302899A1 (en) * | 2011-05-25 | 2012-11-29 | Industry-Academic Cooperation Foundation, Yonsei University | Sensor and sensing method thereof |
WO2013033076A1 (en) * | 2011-08-30 | 2013-03-07 | Glumetrics, Inc. | Information storage for sterilized analyte sensor |
USD680454S1 (en) | 2011-10-25 | 2013-04-23 | Abbott Diabetes Care Inc. | Analyte meter and strip port |
WO2013070794A2 (en) | 2011-11-07 | 2013-05-16 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US20130158504A1 (en) * | 2011-12-16 | 2013-06-20 | Timothy L. Ruchti | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
WO2013090215A2 (en) | 2011-12-11 | 2013-06-20 | Abbot Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
WO2013102158A1 (en) | 2011-12-30 | 2013-07-04 | Abbott Diabetes Care Inc. | Method and apparatus for determining medication dose information |
US8512243B2 (en) | 2005-09-30 | 2013-08-20 | Abbott Diabetes Care Inc. | Integrated introducer and transmitter assembly and methods of use |
WO2013163342A1 (en) | 2012-04-24 | 2013-10-31 | Abbott Diabetes Care Inc. | Methods of lag-compensation for analyte measurements, and devices related thereto |
US8702928B2 (en) | 2010-11-22 | 2014-04-22 | Abbott Diabetes Care Inc. | Modular analyte measurement system with extendable strip port |
US8710993B2 (en) | 2011-11-23 | 2014-04-29 | Abbott Diabetes Care Inc. | Mitigating single point failure of devices in an analyte monitoring system and methods thereof |
US8718965B2 (en) | 2009-07-31 | 2014-05-06 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte monitoring system calibration accuracy |
US8734422B2 (en) | 2008-08-31 | 2014-05-27 | Abbott Diabetes Care Inc. | Closed loop control with improved alarm functions |
US8764657B2 (en) | 2010-03-24 | 2014-07-01 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
US8798934B2 (en) | 2009-07-23 | 2014-08-05 | Abbott Diabetes Care Inc. | Real time management of data relating to physiological control of glucose levels |
US8834366B2 (en) | 2007-07-31 | 2014-09-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
WO2014145049A2 (en) | 2013-03-15 | 2014-09-18 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US8887911B2 (en) | 2011-12-09 | 2014-11-18 | Abbott Diabetes Care Inc. | Packages and kits for analyte monitoring devices, and methods related thereto |
US20150045641A1 (en) * | 2013-03-13 | 2015-02-12 | Optiscan Biomedical Corporation | Method and apparatus for analyte measurement, display, and annotation |
US8965477B2 (en) | 2009-02-26 | 2015-02-24 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US8986208B2 (en) | 2008-09-30 | 2015-03-24 | Abbott Diabetes Care Inc. | Analyte sensor sensitivity attenuation mitigation |
US20150130628A1 (en) * | 2013-07-22 | 2015-05-14 | Center For Integrated Smart Sensors Foundation | Nfc or rfid based bio sensor measurement device and measuring method using the same |
WO2015069563A1 (en) | 2013-11-05 | 2015-05-14 | Abbott Diabetes Care Inc. | Systems, devices, and methods for control of a power supply connection |
US20150172790A1 (en) * | 2012-07-26 | 2015-06-18 | Consejo Superior Investigacion | Wireless telemetry system for the monitoring of static and dynamic magnitudes |
US9069536B2 (en) | 2011-10-31 | 2015-06-30 | Abbott Diabetes Care Inc. | Electronic devices having integrated reset systems and methods thereof |
US9085790B2 (en) | 2010-07-28 | 2015-07-21 | Abbott Diabetes Care Inc. | Analyte sensors having temperature independent membranes |
US20150265203A1 (en) * | 2014-03-20 | 2015-09-24 | Mark McConkie | Monitoring Antepartum Conditions Using a Smart Phone |
US20150292856A1 (en) * | 2014-04-09 | 2015-10-15 | Qualcomm Incorporated | Method, devices and systems for detecting an attachment of an electronic patch |
US9198623B2 (en) | 2010-04-22 | 2015-12-01 | Abbott Diabetes Care Inc. | Devices, systems, and methods related to analyte monitoring and management |
US9226701B2 (en) | 2009-04-28 | 2016-01-05 | Abbott Diabetes Care Inc. | Error detection in critical repeating data in a wireless sensor system |
US20160008664A1 (en) * | 2014-01-13 | 2016-01-14 | Skye Health, Inc. | Methods and devices for sensing, guiding, and/or tracking pelvic exercise |
US20160034658A1 (en) * | 2014-07-31 | 2016-02-04 | Abbott Diabetes Care Inc. | Safety mitigations for hosting a safety critical application on an uncontrolled data processing device |
US9259175B2 (en) | 2006-10-23 | 2016-02-16 | Abbott Diabetes Care, Inc. | Flexible patch for fluid delivery and monitoring body analytes |
US9291591B2 (en) | 2010-01-28 | 2016-03-22 | Abbott Diabetes Care Inc. | Universal test strip port |
US9289164B2 (en) | 2011-06-30 | 2016-03-22 | Abbott Diabetes Care Inc. | Methods for generating hybrid analyte level output, and devices and systems related thereto |
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US9320432B2 (en) | 2010-04-16 | 2016-04-26 | Abbott Diabetes Care Inc. | Analyte meter communication module |
US9320468B2 (en) | 2008-01-31 | 2016-04-26 | Abbott Diabetes Care Inc. | Analyte sensor with time lag compensation |
US20160117532A1 (en) * | 2013-08-22 | 2016-04-28 | Verily Life Sciences Llc | Using Unique Identifiers to Retrieve Configuration Data for Tag Devices |
US9326707B2 (en) | 2008-11-10 | 2016-05-03 | Abbott Diabetes Care Inc. | Alarm characterization for analyte monitoring devices and systems |
US9339229B2 (en) | 2009-02-26 | 2016-05-17 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
US9351669B2 (en) | 2009-09-30 | 2016-05-31 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US20160170532A1 (en) * | 2014-12-15 | 2016-06-16 | Nxp B.V. | User interface unit, electronic device and manufacturing method |
US9398882B2 (en) | 2005-09-30 | 2016-07-26 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor and data processing device |
US9402544B2 (en) | 2009-02-03 | 2016-08-02 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
WO2016133778A1 (en) * | 2015-02-16 | 2016-08-25 | Verily Life Sciences Llc | Bandage type of continuous glucose monitoring system |
US9445445B2 (en) | 2013-03-14 | 2016-09-13 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US9474856B2 (en) | 2007-05-24 | 2016-10-25 | Tandem Diabetes Care, Inc. | Expert system for infusion pump therapy |
US9474475B1 (en) | 2013-03-15 | 2016-10-25 | Abbott Diabetes Care Inc. | Multi-rate analyte sensor data collection with sample rate configurable signal processing |
US9486171B2 (en) | 2013-03-15 | 2016-11-08 | Tandem Diabetes Care, Inc. | Predictive calibration |
US9501272B2 (en) | 2010-05-24 | 2016-11-22 | Abbott Diabetes Care Inc. | Systems and methods for updating a medical device |
WO2016205378A1 (en) | 2015-06-15 | 2016-12-22 | Abbott Diabetes Care Inc. | Stabilized lactate responsive enzymes, electrodes and sensors, and methods for making and using the same |
US9541556B2 (en) | 2008-05-30 | 2017-01-10 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
US9572534B2 (en) | 2010-06-29 | 2017-02-21 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
US9622691B2 (en) | 2011-10-31 | 2017-04-18 | Abbott Diabetes Care Inc. | Model based variable risk false glucose threshold alarm prevention mechanism |
US9622689B2 (en) | 2011-09-28 | 2017-04-18 | Abbott Diabetes Care Inc. | Methods for analyte monitoring management and analyte measurement data management, and articles of manufacture related thereto |
US9675290B2 (en) | 2012-10-30 | 2017-06-13 | Abbott Diabetes Care Inc. | Sensitivity calibration of in vivo sensors used to measure analyte concentration |
US9681807B2 (en) | 2013-03-14 | 2017-06-20 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US9713440B2 (en) | 2010-12-08 | 2017-07-25 | Abbott Diabetes Care Inc. | Modular analyte measurement systems, modular components thereof and related methods |
US9721063B2 (en) | 2011-11-23 | 2017-08-01 | Abbott Diabetes Care Inc. | Compatibility mechanisms for devices in a continuous analyte monitoring system and methods thereof |
US9724470B2 (en) | 2014-06-16 | 2017-08-08 | Icu Medical, Inc. | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
EP3207870A1 (en) * | 2016-02-16 | 2017-08-23 | Roche Diabetes Care GmbH | Body-mountable device, medical sensor assembly and method of use |
WO2017151952A1 (en) | 2016-03-04 | 2017-09-08 | Abbott Diabetes Care Inc. | Nad(p)-dependent responsive enzymes, electrodes and sensors, and methods for making and using the same |
US9760679B2 (en) | 2011-02-11 | 2017-09-12 | Abbott Diabetes Care Inc. | Data synchronization between two or more analyte detecting devices in a database |
EP3216395A1 (en) * | 2016-03-11 | 2017-09-13 | Roche Diabetes Care GmbH | Analyte measuring patch |
US9775549B2 (en) | 2014-08-15 | 2017-10-03 | Abbott Diabetes Care Inc. | Temperature insensitive in vivo analyte devices, methods and systems |
WO2017176802A1 (en) * | 2016-04-08 | 2017-10-12 | Medtronic Minimed, Inc. | Analyte sensor |
US9788771B2 (en) | 2006-10-23 | 2017-10-17 | Abbott Diabetes Care Inc. | Variable speed sensor insertion devices and methods of use |
WO2017181029A1 (en) * | 2016-04-15 | 2017-10-19 | BR Invention Holding, LLC | Mobile medicine communication platform and methods and uses thereof |
US9795326B2 (en) | 2009-07-23 | 2017-10-24 | Abbott Diabetes Care Inc. | Continuous analyte measurement systems and systems and methods for implanting them |
US9804150B2 (en) | 2007-05-14 | 2017-10-31 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US9833177B2 (en) | 2007-05-30 | 2017-12-05 | Tandem Diabetes Care, Inc. | Insulin pump based expert system |
US20170373892A1 (en) * | 2016-06-23 | 2017-12-28 | University Of Massachusetts | Systems and methods for backscatter communication |
US9882660B2 (en) | 2006-10-26 | 2018-01-30 | Abbott Diabetes Care Inc. | Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors |
US9895491B2 (en) | 2013-03-15 | 2018-02-20 | Tandem Diabeters Care, Inc. | Field update of an ambulatory infusion pump system |
US9907504B2 (en) | 2001-11-08 | 2018-03-06 | Optiscan Biomedical Corporation | Analyte monitoring systems and methods |
US9907492B2 (en) | 2012-09-26 | 2018-03-06 | Abbott Diabetes Care Inc. | Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data |
US9913599B2 (en) | 2011-02-11 | 2018-03-13 | Abbott Diabetes Care Inc. | Software applications residing on handheld analyte determining devices |
US9949642B2 (en) | 2015-05-14 | 2018-04-24 | Abbott Diabetes Care Inc. | Systems, devices, and methods for monitoring medical devices |
US9962486B2 (en) | 2013-03-14 | 2018-05-08 | Tandem Diabetes Care, Inc. | System and method for detecting occlusions in an infusion pump |
US9968306B2 (en) | 2012-09-17 | 2018-05-15 | Abbott Diabetes Care Inc. | Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems |
US9971871B2 (en) | 2011-10-21 | 2018-05-15 | Icu Medical, Inc. | Medical device update system |
US9974471B1 (en) * | 2014-10-24 | 2018-05-22 | Verily Life Sciences Llc | Analyte detection system and method for intradermal implantation of biocompatible optode nanosensors |
US9974472B2 (en) | 2011-06-16 | 2018-05-22 | Abbott Diabetes Care Inc. | Temperature-compensated analyte monitoring devices, systems, and methods thereof |
EP3207871A4 (en) * | 2014-10-27 | 2018-05-23 | Shenzhen Waveguider Optical Telecom Technology Inc. | Continuous glucose collecting apparatus and main machine |
US9980670B2 (en) | 2002-11-05 | 2018-05-29 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
US20180146894A1 (en) * | 2016-11-29 | 2018-05-31 | Verily Life Sciences Llc | Wire-assembly apparatus for invasive biosensors |
US9995611B2 (en) | 2012-03-30 | 2018-06-12 | Icu Medical, Inc. | Air detection system and method for detecting air in a pump of an infusion system |
US10006880B2 (en) | 2012-09-21 | 2018-06-26 | Abbott Diabetes Care Inc. | Test strips having ceria nanoparticle electrodes |
US10010273B2 (en) | 2011-03-10 | 2018-07-03 | Abbott Diabetes Care, Inc. | Multi-function analyte monitor device and methods of use |
US10016559B2 (en) | 2009-12-04 | 2018-07-10 | Smiths Medical Asd, Inc. | Advanced step therapy delivery for an ambulatory infusion pump and system |
US10022499B2 (en) | 2007-02-15 | 2018-07-17 | Abbott Diabetes Care Inc. | Device and method for automatic data acquisition and/or detection |
US10039881B2 (en) | 2002-12-31 | 2018-08-07 | Abbott Diabetes Care Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US10042986B2 (en) | 2013-11-19 | 2018-08-07 | Icu Medical, Inc. | Infusion pump automation system and method |
US10046112B2 (en) | 2013-05-24 | 2018-08-14 | Icu Medical, Inc. | Multi-sensor infusion system for detecting air or an occlusion in the infusion system |
US10076285B2 (en) | 2013-03-15 | 2018-09-18 | Abbott Diabetes Care Inc. | Sensor fault detection using analyte sensor data pattern comparison |
EP3381360A1 (en) | 2011-09-28 | 2018-10-03 | Abbott Diabetes Care, Inc. | Methods, devices and systems for analyte monitoring management |
US10092229B2 (en) | 2010-06-29 | 2018-10-09 | Abbott Diabetes Care Inc. | Calibration of analyte measurement system |
US10117606B2 (en) | 2009-10-30 | 2018-11-06 | Abbott Diabetes Care Inc. | Method and apparatus for detecting false hypoglycemic conditions |
US10132793B2 (en) | 2012-08-30 | 2018-11-20 | Abbott Diabetes Care Inc. | Dropout detection in continuous analyte monitoring data during data excursions |
US10136816B2 (en) | 2009-08-31 | 2018-11-27 | Abbott Diabetes Care Inc. | Medical devices and methods |
US10136845B2 (en) | 2011-02-28 | 2018-11-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US10166328B2 (en) | 2013-05-29 | 2019-01-01 | Icu Medical, Inc. | Infusion system which utilizes one or more sensors and additional information to make an air determination regarding the infusion system |
US10213141B2 (en) | 2013-04-30 | 2019-02-26 | Abbott Diabetes Care Inc. | Systems, devices, and methods for energy efficient electrical device activation |
US10213139B2 (en) | 2015-05-14 | 2019-02-26 | Abbott Diabetes Care Inc. | Systems, devices, and methods for assembling an applicator and sensor control device |
US10226207B2 (en) | 2004-12-29 | 2019-03-12 | Abbott Diabetes Care Inc. | Sensor inserter having introducer |
US10242060B2 (en) | 2006-10-16 | 2019-03-26 | Icu Medical, Inc. | System and method for comparing and utilizing activity information and configuration information from multiple medical device management systems |
US10238801B2 (en) | 2009-04-17 | 2019-03-26 | Icu Medical, Inc. | System and method for configuring a rule set for medical event management and responses |
US10238799B2 (en) | 2014-09-15 | 2019-03-26 | Icu Medical, Inc. | Matching delayed infusion auto-programs with manually entered infusion programs |
US10258736B2 (en) | 2012-05-17 | 2019-04-16 | Tandem Diabetes Care, Inc. | Systems including vial adapter for fluid transfer |
US10292630B2 (en) | 2015-06-01 | 2019-05-21 | Verily Life Sciences Llc | Optical sensor for bandage type monitoring device |
US10311972B2 (en) | 2013-11-11 | 2019-06-04 | Icu Medical, Inc. | Medical device system performance index |
US10307091B2 (en) | 2005-12-28 | 2019-06-04 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
US10333843B2 (en) | 2013-03-06 | 2019-06-25 | Icu Medical, Inc. | Medical device communication method |
US10342917B2 (en) | 2014-02-28 | 2019-07-09 | Icu Medical, Inc. | Infusion system and method which utilizes dual wavelength optical air-in-line detection |
US10357606B2 (en) | 2013-03-13 | 2019-07-23 | Tandem Diabetes Care, Inc. | System and method for integration of insulin pumps and continuous glucose monitoring |
US10362972B2 (en) | 2006-09-10 | 2019-07-30 | Abbott Diabetes Care Inc. | Method and system for providing an integrated analyte sensor insertion device and data processing unit |
US10413183B2 (en) | 2016-04-08 | 2019-09-17 | Medtronic Minimed, Inc. | Insertion device |
US10429250B2 (en) | 2009-08-31 | 2019-10-01 | Abbott Diabetes Care, Inc. | Analyte monitoring system and methods for managing power and noise |
US10430761B2 (en) | 2011-08-19 | 2019-10-01 | Icu Medical, Inc. | Systems and methods for a graphical interface including a graphical representation of medical data |
US10433773B1 (en) | 2013-03-15 | 2019-10-08 | Abbott Diabetes Care Inc. | Noise rejection methods and apparatus for sparsely sampled analyte sensor data |
US10434246B2 (en) | 2003-10-07 | 2019-10-08 | Icu Medical, Inc. | Medication management system |
US10452875B2 (en) | 2014-05-22 | 2019-10-22 | Avery Dennison Retail Information Services, Llc | Using RFID devices integrated or included in the packaging of medical devices to facilitate a secure and authorized pairing with a host system |
US10455816B2 (en) * | 2016-07-20 | 2019-10-29 | International Business Machines Corporation | Sensor based activity monitor |
US10463788B2 (en) | 2012-07-31 | 2019-11-05 | Icu Medical, Inc. | Patient care system for critical medications |
US10541987B2 (en) | 2016-02-26 | 2020-01-21 | Tandem Diabetes Care, Inc. | Web browser-based device communication workflow |
WO2020027434A1 (en) * | 2018-07-31 | 2020-02-06 | 주식회사 아이센스 | Body attachment unit for continuous blood glucose monitoring |
US10555695B2 (en) | 2011-04-15 | 2020-02-11 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US10569016B2 (en) | 2015-12-29 | 2020-02-25 | Tandem Diabetes Care, Inc. | System and method for switching between closed loop and open loop control of an ambulatory infusion pump |
US10596316B2 (en) | 2013-05-29 | 2020-03-24 | Icu Medical, Inc. | Infusion system and method of use which prevents over-saturation of an analog-to-digital converter |
US10598624B2 (en) | 2014-10-23 | 2020-03-24 | Abbott Diabetes Care Inc. | Electrodes having at least one sensing structure and methods for making and using the same |
WO2020067630A1 (en) * | 2018-09-27 | 2020-04-02 | 주식회사 아이센스 | Body attachment unit for continuous blood glucose measurement |
WO2020067629A1 (en) * | 2018-09-27 | 2020-04-02 | 주식회사 아이센스 | Body-attachable unit for continuously measuring blood glucose |
US10635784B2 (en) | 2007-12-18 | 2020-04-28 | Icu Medical, Inc. | User interface improvements for medical devices |
US10656894B2 (en) | 2017-12-27 | 2020-05-19 | Icu Medical, Inc. | Synchronized display of screen content on networked devices |
US10674944B2 (en) | 2015-05-14 | 2020-06-09 | Abbott Diabetes Care Inc. | Compact medical device inserters and related systems and methods |
JP2020517333A (en) * | 2017-04-19 | 2020-06-18 | メトロノーム・ヘルス、インコーポレイテッド | Sample sensor inserter |
US10692595B2 (en) | 2018-07-26 | 2020-06-23 | Icu Medical, Inc. | Drug library dynamic version management |
WO2020159780A1 (en) * | 2019-02-01 | 2020-08-06 | Analog Devices, Inc. | Subcutaneous biosensor |
US10741280B2 (en) | 2018-07-17 | 2020-08-11 | Icu Medical, Inc. | Tagging pump messages with identifiers that facilitate restructuring |
US10765799B2 (en) | 2013-09-20 | 2020-09-08 | Icu Medical, Inc. | Fail-safe drug infusion therapy system |
US10765369B2 (en) | 2016-04-08 | 2020-09-08 | Medtronic Minimed, Inc. | Analyte sensor |
US10765348B2 (en) | 2016-04-08 | 2020-09-08 | Medtronic Minimed, Inc. | Sensor and transmitter product |
USD902408S1 (en) | 2003-11-05 | 2020-11-17 | Abbott Diabetes Care Inc. | Analyte sensor control unit |
US10850024B2 (en) | 2015-03-02 | 2020-12-01 | Icu Medical, Inc. | Infusion system, device, and method having advanced infusion features |
US10860687B2 (en) | 2012-12-31 | 2020-12-08 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US10861592B2 (en) | 2018-07-17 | 2020-12-08 | Icu Medical, Inc. | Reducing infusion pump network congestion by staggering updates |
US10856736B2 (en) | 2012-12-31 | 2020-12-08 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US10872696B2 (en) | 2011-02-11 | 2020-12-22 | Abbott Diabetes Care Inc. | Method of hypoglycemia risk determination |
US10874338B2 (en) | 2010-06-29 | 2020-12-29 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
US10881335B2 (en) | 2016-03-31 | 2021-01-05 | Dexcom, Inc. | Systems and methods for display device and sensor electronics unit communication |
US10888272B2 (en) | 2015-07-10 | 2021-01-12 | Abbott Diabetes Care Inc. | Systems, devices, and methods for meal information collection, meal assessment, and analyte data correlation |
US10898641B2 (en) | 2014-04-30 | 2021-01-26 | Icu Medical, Inc. | Patient care system with conditional alarm forwarding |
CN112294270A (en) * | 2019-07-30 | 2021-02-02 | 亘冠智能技术(杭州)有限公司 | Health monitoring system based on RFID technology |
EP3771428A1 (en) * | 2019-08-02 | 2021-02-03 | Bionime Corporation | Physiological signal monitoring device |
US10932672B2 (en) | 2015-12-28 | 2021-03-02 | Dexcom, Inc. | Systems and methods for remote and host monitoring communications |
US10939858B2 (en) | 2014-08-06 | 2021-03-09 | Roche Diabetes Care, Inc. | Medical device and method for producing a medical device |
EP3764465A4 (en) * | 2018-03-07 | 2021-05-05 | PHC Holdings Corporation | Communication device |
US11000215B1 (en) | 2003-12-05 | 2021-05-11 | Dexcom, Inc. | Analyte sensor |
CN113038879A (en) * | 2018-09-07 | 2021-06-25 | 门塔拉布有限公司 | System for detecting biological signals |
USD924406S1 (en) * | 2010-02-01 | 2021-07-06 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
US11071478B2 (en) | 2017-01-23 | 2021-07-27 | Abbott Diabetes Care Inc. | Systems, devices and methods for analyte sensor insertion |
CN113274004A (en) * | 2020-02-20 | 2021-08-20 | 上海移宇科技股份有限公司 | High reliability analyte detection device |
CN113274014A (en) * | 2020-02-20 | 2021-08-20 | 上海移宇科技股份有限公司 | Mounting unit of analyte detection device and mounting method thereof |
US11109121B2 (en) * | 2018-05-10 | 2021-08-31 | Physio-Control, Inc. | Systems and methods of secure communication of data from medical devices |
EP3831302A4 (en) * | 2018-07-31 | 2021-09-01 | i-Sens, Inc. | Body attachment unit for continuous glucose monitoring |
US20210267503A1 (en) * | 2018-07-31 | 2021-09-02 | I-Sens, Inc. | Body attachable unit for continuous blood glucose measurement |
EP3831301A4 (en) * | 2018-07-31 | 2021-09-08 | i-Sens, Inc. | Body attachment unit for continuous blood glucose monitoring |
EP3831300A4 (en) * | 2018-07-31 | 2021-09-15 | i-Sens, Inc. | Continuous blood glucose measurement device |
EP3831295A4 (en) * | 2018-07-31 | 2021-09-15 | i-Sens, Inc. | Continuous glucose monitoring device |
US11135360B1 (en) | 2020-12-07 | 2021-10-05 | Icu Medical, Inc. | Concurrent infusion with common line auto flush |
EP3831293A4 (en) * | 2018-07-31 | 2021-10-06 | i-Sens, Inc. | Continuous blood glucose measurement body attachment unit |
US11167171B2 (en) | 2014-01-13 | 2021-11-09 | Skye Health, Inc. | Device and method for sensing, guiding, and/or tracking pelvic exercise |
JP2021531869A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP2021531870A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP2021531875A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
US11203139B2 (en) | 2017-12-13 | 2021-12-21 | Becton, Dickinson And Company | Medical device with overmolded adhesive patch and method for making same |
JP2022501100A (en) * | 2018-09-27 | 2022-01-06 | アイセンス,インコーポレーテッド | Applicator for continuous blood glucose measuring device |
JP2022503394A (en) * | 2018-06-07 | 2022-01-12 | アボット ダイアベティス ケア インコーポレイテッド | Centralized sterile and sterile subassembly for specimen monitoring systems |
JP2022503393A (en) * | 2018-06-07 | 2022-01-12 | アボット ダイアベティス ケア インコーポレイテッド | Centralized sterile and sterile subassembly for specimen monitoring systems |
US11229382B2 (en) | 2013-12-31 | 2022-01-25 | Abbott Diabetes Care Inc. | Self-powered analyte sensor and devices using the same |
US11235100B2 (en) | 2003-11-13 | 2022-02-01 | Icu Medical, Inc. | System for maintaining drug information and communicating with medication delivery devices |
US11246985B2 (en) | 2016-05-13 | 2022-02-15 | Icu Medical, Inc. | Infusion pump system and method with common line auto flush |
US11278671B2 (en) | 2019-12-04 | 2022-03-22 | Icu Medical, Inc. | Infusion pump with safety sequence keypad |
US11291763B2 (en) | 2007-03-13 | 2022-04-05 | Tandem Diabetes Care, Inc. | Basal rate testing using frequent blood glucose input |
US11298058B2 (en) | 2005-12-28 | 2022-04-12 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
CN114305331A (en) * | 2021-12-01 | 2022-04-12 | 安徽华米信息科技有限公司 | Method, device and equipment for collecting physiological parameters |
US11309070B2 (en) | 2018-07-26 | 2022-04-19 | Icu Medical, Inc. | Drug library manager with customized worksheets |
US11328804B2 (en) | 2018-07-17 | 2022-05-10 | Icu Medical, Inc. | Health checks for infusion pump communications systems |
US11324898B2 (en) | 2013-06-21 | 2022-05-10 | Tandem Diabetes Care, Inc. | System and method for infusion set dislodgement detection |
US11324888B2 (en) | 2016-06-10 | 2022-05-10 | Icu Medical, Inc. | Acoustic flow sensor for continuous medication flow measurements and feedback control of infusion |
US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
US11344673B2 (en) | 2014-05-29 | 2022-05-31 | Icu Medical, Inc. | Infusion system and pump with configurable closed loop delivery rate catch-up |
US11344668B2 (en) | 2014-12-19 | 2022-05-31 | Icu Medical, Inc. | Infusion system with concurrent TPN/insulin infusion |
US11350862B2 (en) | 2017-10-24 | 2022-06-07 | Dexcom, Inc. | Pre-connected analyte sensors |
US20220233110A1 (en) * | 2009-08-31 | 2022-07-28 | Abbott Diabetes Care Inc. | Displays for a medical device |
WO2022164940A1 (en) | 2021-01-26 | 2022-08-04 | Abbott Diabetes Care Inc. | Systems, devices, and methods related to ketone sensors |
USD961778S1 (en) | 2006-02-28 | 2022-08-23 | Abbott Diabetes Care Inc. | Analyte sensor device |
JP2022538964A (en) * | 2019-05-14 | 2022-09-07 | サンヴィタ メディカル コーポレーション | Subcutaneous analyte sensor applicator and continuous measurement system |
US11464908B2 (en) | 2019-02-18 | 2022-10-11 | Tandem Diabetes Care, Inc. | Methods and apparatus for monitoring infusion sites for ambulatory infusion pumps |
US11553883B2 (en) | 2015-07-10 | 2023-01-17 | Abbott Diabetes Care Inc. | System, device and method of dynamic glucose profile response to physiological parameters |
US11574737B2 (en) | 2016-07-14 | 2023-02-07 | Icu Medical, Inc. | Multi-communication path selection and security system for a medical device |
US11571508B2 (en) | 2013-08-30 | 2023-02-07 | Icu Medical, Inc. | System and method of monitoring and managing a remote infusion regimen |
US11571164B2 (en) | 2019-01-04 | 2023-02-07 | Enable Injections, Inc. | Medical fluid injection apparatus and method with detachable patch and monitoring |
US11587669B2 (en) | 2018-07-17 | 2023-02-21 | Icu Medical, Inc. | Passing authentication token to authorize access to rest calls via web sockets |
US11596330B2 (en) | 2017-03-21 | 2023-03-07 | Abbott Diabetes Care Inc. | Methods, devices and system for providing diabetic condition diagnosis and therapy |
US11605468B2 (en) | 2015-05-26 | 2023-03-14 | Icu Medical, Inc. | Infusion pump system and method with multiple drug library editor source capability |
USD982762S1 (en) | 2020-12-21 | 2023-04-04 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
EP3991650A4 (en) * | 2019-08-19 | 2023-06-21 | i-Sens, Inc. | Continuous blood sugar measuring sensor member |
WO2023110190A1 (en) | 2021-12-13 | 2023-06-22 | Heraeus Medical Gmbh | Tests and methods for detecting bacterial infection |
US11717225B2 (en) | 2014-03-30 | 2023-08-08 | Abbott Diabetes Care Inc. | Method and apparatus for determining meal start and peak events in analyte monitoring systems |
US20230251727A1 (en) * | 2010-03-10 | 2023-08-10 | Abbott Diabetes Care Inc. | Systems, devices and methods for managing glucose levels |
US11786173B2 (en) | 2019-01-04 | 2023-10-17 | Enable Injections, Inc. | Medical fluid injection apparatus and method with detachable patch and monitoring |
US11793936B2 (en) | 2009-05-29 | 2023-10-24 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
USD1002852S1 (en) | 2019-06-06 | 2023-10-24 | Abbott Diabetes Care Inc. | Analyte sensor device |
US11883361B2 (en) | 2020-07-21 | 2024-01-30 | Icu Medical, Inc. | Fluid transfer devices and methods of use |
USD1015366S1 (en) | 2020-07-29 | 2024-02-20 | Abbott Diabetes Care Inc. | Display screen or portion thereof with graphical user interface |
US11933650B2 (en) | 2022-07-01 | 2024-03-19 | Icu Medical, Inc. | Air detection system and method for detecting air in a pump of an infusion system |
Families Citing this family (113)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6850788B2 (en) | 2002-03-25 | 2005-02-01 | Masimo Corporation | Physiological measurement communications adapter |
US9743862B2 (en) | 2011-03-31 | 2017-08-29 | Abbott Diabetes Care Inc. | Systems and methods for transcutaneously implanting medical devices |
EP3533387A3 (en) | 2007-06-21 | 2019-11-13 | Abbott Diabetes Care, Inc. | Health management devices and methods |
US8160900B2 (en) | 2007-06-29 | 2012-04-17 | Abbott Diabetes Care Inc. | Analyte monitoring and management device and method to analyze the frequency of user interaction with the device |
US8924159B2 (en) | 2008-05-30 | 2014-12-30 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
DE102010038986A1 (en) * | 2010-08-05 | 2012-02-09 | Endress + Hauser Gmbh + Co. Kg | Composite material, shaped article, electronic device with a shaped article, and method for the production of a shaped article |
JP6090795B2 (en) | 2011-09-09 | 2017-03-08 | テルモ株式会社 | Sensor insertion device |
US9451912B2 (en) | 2012-03-13 | 2016-09-27 | Terumo Kabushiki Kaisha | Sensor insertion device and method for operating said device |
WO2013136968A1 (en) | 2012-03-13 | 2013-09-19 | テルモ株式会社 | Sensor insertion device and method for operating said device |
WO2013140790A1 (en) * | 2012-03-22 | 2013-09-26 | テルモ株式会社 | Puncture device and drug solution administration device |
US9615779B2 (en) | 2012-04-04 | 2017-04-11 | Dexcom, Inc. | Transcutaneous analyte sensors, applicators therefor, and associated methods |
WO2014018928A1 (en) * | 2012-07-27 | 2014-01-30 | Abbott Diabetes Care Inc. | Medical device applicators |
EP2902056B1 (en) * | 2012-09-28 | 2022-04-27 | Terumo Kabushiki Kaisha | Puncture device and medical fluid application device |
CN105228522B (en) | 2013-03-14 | 2018-06-26 | 萨诺智能公司 | For the microsensor on the human body of biological monitoring |
US10820860B2 (en) | 2013-03-14 | 2020-11-03 | One Drop Biosensor Technologies, Llc | On-body microsensor for biomonitoring |
CA2906205A1 (en) | 2013-03-15 | 2014-09-18 | Abbott Diabetes Care Inc. | Medical device data processing and communication methods and systems |
US8742623B1 (en) * | 2013-09-16 | 2014-06-03 | Google Inc. | Device with dual power sources |
SE538612C2 (en) * | 2013-11-20 | 2016-10-04 | Brighter Ab (Publ) | Medical device with safety device |
TWI526976B (en) * | 2013-11-21 | 2016-03-21 | 動聯國際股份有限公司 | Monitoring system, method, and medical monitoring system |
CN103610445B (en) * | 2013-11-26 | 2015-12-30 | 深圳市倍轻松科技股份有限公司 | The check processing method and system of physiological signal |
CN105792751B (en) | 2013-11-27 | 2019-07-05 | 雅培糖尿病护理公司 | System and method for correcting the programming based on permanent ROM |
EP3780689A1 (en) | 2013-12-27 | 2021-02-17 | Abbott Diabetes Care, Inc. | Systems, devices, and methods for authentication in an analyte monitoring environment |
CA2934904A1 (en) | 2013-12-27 | 2015-07-02 | Abbott Diabetes Care Inc. | Application interface and display control in an analyte monitoring environment |
WO2015122964A1 (en) * | 2014-02-11 | 2015-08-20 | Dexcom, Inc. | Packaging system for analyte sensors |
US20150257687A1 (en) * | 2014-03-13 | 2015-09-17 | Sano Intelligence, Inc. | System for monitoring body chemistry |
US10595754B2 (en) | 2014-03-13 | 2020-03-24 | Sano Intelligence, Inc. | System for monitoring body chemistry |
US9452293B2 (en) * | 2014-06-19 | 2016-09-27 | Inspire Medical Systems, Inc. | Hybrid communication channel for communicating with an implantable medical device |
CN104330450A (en) * | 2014-10-30 | 2015-02-04 | 东莞市青麦田数码科技有限公司 | Disposable blood glucose meter |
AU2015349931B2 (en) | 2014-11-19 | 2020-08-13 | Abbott Diabetes Care Inc. | Systems, devices, and methods for revising or supplementing ROM-based RF commands |
USD794800S1 (en) * | 2015-07-09 | 2017-08-15 | Dexcom, Inc. | Medical device inserter |
EP3138488B1 (en) | 2015-09-02 | 2019-06-05 | Roche Diabetes Care GmbH | Sensor module and kit for determining an analyte concentration |
SI3138489T1 (en) | 2015-09-02 | 2020-10-30 | F. Hoffmann-La Roche Ag | Kit for determining an analyte concentration |
US20170112533A1 (en) | 2015-10-21 | 2017-04-27 | Dexcom, Inc. | Transcutaneous analyte sensors, applicators therefor, and associated methods |
CN105342825B (en) * | 2015-11-18 | 2018-07-06 | 上海麦添医疗科技有限公司 | Massage device of alimentary tract and its processing method can be swallowed |
JP7106455B2 (en) * | 2015-11-23 | 2022-07-26 | メイヨ・ファウンデーション・フォー・メディカル・エデュケーション・アンド・リサーチ | Processing of physiological electrical data for analyte evaluation |
USD806711S1 (en) * | 2015-12-11 | 2018-01-02 | SomniQ, Inc. | Portable electronic device |
CN105662337B (en) * | 2015-12-30 | 2018-08-17 | 博迪加科技(北京)有限公司 | A kind of signal processing apparatus and intelligent clothing |
WO2017116915A1 (en) * | 2015-12-30 | 2017-07-06 | Dexcom, Inc. | Transcutaneous analyte sensor systems and methods |
ES2903121T3 (en) | 2016-02-05 | 2022-03-31 | Hoffmann La Roche | Medical device for detecting at least one analyte in a body fluid |
EP3909506B1 (en) | 2016-02-05 | 2023-06-07 | Roche Diabetes Care GmbH | Medical device for detecting at least one analyte in a body fluid |
DE202016009190U1 (en) | 2016-02-05 | 2023-08-23 | Roche Diabetes Care Gmbh | Medical device for detecting at least one analyte in a body fluid |
DE202016009189U1 (en) | 2016-02-05 | 2023-08-25 | Roche Diabetes Care Gmbh | Medical device for detecting at least one analyte in a body fluid |
DE202016009188U1 (en) | 2016-02-05 | 2023-08-30 | Roche Diabetes Care Gmbh | Medical device for detecting at least one analyte in a body fluid |
CA3018351C (en) | 2016-03-29 | 2024-02-13 | F. Hoffmann-La Roche Ag | Method of operating a receiver for receiving analyte data, receiver and computer program product |
WO2017214837A1 (en) * | 2016-06-14 | 2017-12-21 | 彭鹏 | Reagent kit having music playback function and wireless management function |
US11026609B2 (en) * | 2016-08-09 | 2021-06-08 | Verily Life Sciences Llc | Wake-up batteries for invasive biosensors |
CN109844528B (en) * | 2016-10-26 | 2020-09-29 | 豪夫迈·罗氏有限公司 | Multi-chip packaging of integrated circuits and flow cells for nanopore sequencing |
US20180172664A1 (en) | 2016-12-20 | 2018-06-21 | Abbott Diabetes Care Inc. | Systems, devices, and methods for wireless communications in analyte monitoring systems |
KR102422361B1 (en) * | 2016-12-22 | 2022-07-18 | 산비타 메디컬 코포레이션 | Continuous glucose monitoring system and method |
US11278217B2 (en) * | 2017-03-31 | 2022-03-22 | RichHealth Technology Corporation | Transdermal microneedle array patch |
TWI666034B (en) * | 2017-03-31 | 2019-07-21 | 全康科技股份有限公司 | Transdermal microneedle array patch |
JP7113845B2 (en) * | 2017-04-04 | 2022-08-05 | エフ ホフマン-ラ ロッシュ アクチェン ゲゼルシャフト | wearable medical device |
KR102388991B1 (en) | 2017-05-22 | 2022-04-22 | 삼성전자주식회사 | Biosensor, manufacturing method of biosensor and biosignal measuring apparatus |
WO2018222011A1 (en) * | 2017-06-02 | 2018-12-06 | 주식회사 아이센스 | Sensor applicator assembly for continuous glucose monitoring system |
US11179107B2 (en) | 2017-06-02 | 2021-11-23 | I-Sens, Inc. | Sensor applicator assembly for continuous glucose monitoring system |
WO2018222010A1 (en) * | 2017-06-02 | 2018-12-06 | 주식회사 아이센스 | Sensor applicator assembly for continuous glucose monitoring system |
WO2018222012A1 (en) * | 2017-06-02 | 2018-12-06 | 주식회사 아이센스 | Sensor applicator assembly for continuous glucose monitoring system |
WO2018222009A1 (en) * | 2017-06-02 | 2018-12-06 | 주식회사 아이센스 | Sensor applicator assembly for continuous glucose monitoring system |
CN111031903B (en) | 2017-06-16 | 2023-08-04 | 康奈尔大学 | Method and system for electromagnetic near-field coherent sensing |
US11452466B2 (en) | 2017-06-19 | 2022-09-27 | Dexcom, Inc. | Applicators for applying transcutaneous analyte sensors and associated methods of manufacture |
EP3928688B1 (en) | 2017-06-23 | 2022-06-01 | Dexcom, Inc. | Transcutaneous analyte sensors, applicators therefor, and needle hub comprising anti-rotation feature |
CN111093499B (en) * | 2017-09-26 | 2022-12-06 | 美敦力泌力美公司 | Wafer-level physiological characteristic sensor package with integrated wireless transmitter |
US10874300B2 (en) | 2017-09-26 | 2020-12-29 | Medtronic Minimed, Inc. | Waferscale physiological characteristic sensor package with integrated wireless transmitter |
DE202018006862U1 (en) * | 2017-12-21 | 2023-11-16 | Roche Diabetes Care Gmbh | Medical system |
CA3088946A1 (en) * | 2018-01-11 | 2019-07-18 | Shell Internationale Research Maatschappij B.V. | Wireless monitoring and profiling of reactor conditions using arrays of sensor-enabled rfid tags placed at known reactor heights |
TWI797231B (en) | 2018-01-11 | 2023-04-01 | 荷蘭商蜆殼國際研究所 | Wireless reactor monitoring system using passive sensor enabled rfid tag and a method of monitoring process conditions within a reactor vessel |
CN108784859B (en) * | 2018-03-19 | 2021-06-25 | 成都频泰医疗设备有限公司 | Orthodontic system with direct-wear appliances |
USD878325S1 (en) * | 2018-04-19 | 2020-03-17 | Amazon Technologies, Inc. | Electronic input device |
USD900812S1 (en) * | 2018-05-04 | 2020-11-03 | Flint Rehabilitation Devices, LLC | User interface device |
US11392782B2 (en) | 2018-05-14 | 2022-07-19 | Cornell University | Collaborative RFID reader using code divisional multiple access (CDMA) and methods for same |
CN112236079B (en) | 2018-06-06 | 2024-02-06 | 普和希控股公司 | Body-mounted sensor device, sensor insertion device, and sensor insertion method |
USD888252S1 (en) | 2018-06-18 | 2020-06-23 | Dexcom, Inc. | Transcutaneous analyte sensor applicator |
USD926325S1 (en) | 2018-06-22 | 2021-07-27 | Dexcom, Inc. | Wearable medical monitoring device |
US10940554B2 (en) * | 2018-11-30 | 2021-03-09 | International Business Machines Corporation | Planar fabrication of micro-needles |
USD916309S1 (en) * | 2018-12-14 | 2021-04-13 | Nippon Chemiphar Co. Ltd. | Chip for the analysis of biochemical reactions |
USD954719S1 (en) | 2019-01-17 | 2022-06-14 | Bruin Biometrics, Llc | Display screen or portion thereof with a graphical user interface |
USD907216S1 (en) * | 2019-02-07 | 2021-01-05 | Kci Licensing, Inc. | Therapy device |
USD903125S1 (en) * | 2019-02-11 | 2020-11-24 | Bruin Biometrics, Llc | Disposable sensor attachment design |
JP1648060S (en) * | 2019-05-24 | 2019-12-16 | ||
JP1648061S (en) * | 2019-05-24 | 2019-12-16 | ||
TWI699189B (en) * | 2019-05-29 | 2020-07-21 | 華廣生技股份有限公司 | Biological sensing device and method for starting biological sensing device |
USD937422S1 (en) * | 2019-06-06 | 2021-11-30 | Bionime Corporation | Medical device inserter |
TWI735138B (en) * | 2019-08-02 | 2021-08-01 | 華廣生技股份有限公司 | Physiological signal sensing device |
CN112294305A (en) * | 2019-08-02 | 2021-02-02 | 华广生技股份有限公司 | Physiological signal sensing device |
CA3088622C (en) * | 2019-08-02 | 2023-01-03 | Chun-Mu Huang | Insertion device for a biosensor and insertion method thereof |
US20220218240A1 (en) * | 2019-08-19 | 2022-07-14 | Medtrum Technologies Inc. | Sensing device |
KR102303553B1 (en) * | 2019-11-21 | 2021-09-23 | 주식회사 아이센스 | Sensor apparatus for continuous glucose monitoring |
EP4072632A1 (en) * | 2019-12-11 | 2022-10-19 | Sanofi | Modular system for a drug delivery device with electronic and corresponding modules and method |
KR102368154B1 (en) * | 2020-03-31 | 2022-03-02 | 주식회사 아이센스 | Continuous glucose monitoring system |
USD945629S1 (en) * | 2020-09-08 | 2022-03-08 | Kci Manufacturing Unlimited Company | Therapy device |
EP3973870A1 (en) | 2020-09-25 | 2022-03-30 | Roche Diabetes Care GmbH | Insertion device and method for inserting a medical device |
US11534086B2 (en) | 2020-10-30 | 2022-12-27 | Medtronic Minimed, Inc. | Low-profile wearable medical device |
CA3197412A1 (en) | 2020-12-10 | 2022-06-16 | Yi Wang | Systems, devices, and methods for analyte sensor insertion |
USD973300S1 (en) | 2021-01-22 | 2022-12-27 | Spectrum Brands, Inc. | Disc pet chew |
USD1017048S1 (en) * | 2021-03-04 | 2024-03-05 | Inspire Medical Systems, Inc. | Wireless communications assembly |
USD1010134S1 (en) * | 2021-03-04 | 2024-01-02 | Inspire Medical Systems, Inc. | Telemetry element |
USD988160S1 (en) * | 2021-03-16 | 2023-06-06 | Biolinq Incorporated | Wearable dermal sensor |
USD985774S1 (en) * | 2021-03-30 | 2023-05-09 | Ascensia Diabetes Care Holdings Ag | Aanalyte monitoring device |
USD988882S1 (en) | 2021-04-21 | 2023-06-13 | Informed Data Systems Inc. | Sensor assembly |
ES2929788A1 (en) * | 2021-06-01 | 2022-12-01 | Varadero Directorship Sl | DEVICE FOR REMOTE MONITORING OF BODY TEMPERATURE IN CATTLE AND PIGS (Machine-translation by Google Translate, not legally binding) |
IT202100015722A1 (en) * | 2021-06-16 | 2022-12-16 | Theras Lifetech S R L | Infusion device applicator. |
CA3222449A1 (en) | 2021-07-16 | 2023-01-19 | Abbott Diabetes Care Inc. | Systems, devices, and methods for analyte monitoring |
WO2023044888A1 (en) * | 2021-09-27 | 2023-03-30 | Medtrum Technologies Inc. | Installation unit of analyte detection device |
WO2023044890A1 (en) * | 2021-09-27 | 2023-03-30 | Medtrum Technologies Inc. | Installation unit of analyte detection device |
WO2023044889A1 (en) * | 2021-09-27 | 2023-03-30 | Medtrum Technologies Inc. | Analyte detection system |
WO2023044887A1 (en) * | 2021-09-27 | 2023-03-30 | Medtrum Technologies Inc. | Installation unit of analyte detection device and use method |
US11672965B2 (en) | 2021-09-28 | 2023-06-13 | Biolinq Incorporated | Microneedle enclosure and applicator device for microneedle array based continuous analyte monitoring device |
USD1013544S1 (en) * | 2022-04-29 | 2024-02-06 | Biolinq Incorporated | Wearable sensor |
USD996999S1 (en) * | 2021-11-16 | 2023-08-29 | Biolinq Incorporated | Wearable sensor |
USD1012698S1 (en) * | 2022-02-08 | 2024-01-30 | Frost Buddy LLC | Shaker lid |
US20230345650A1 (en) * | 2022-04-26 | 2023-10-26 | Medtronic Minimed, Inc. | Energy management based on an open switch configuration |
US20230337984A1 (en) * | 2022-04-26 | 2023-10-26 | Medtronic Minimed, Inc. | Energy management based on a closed switch configuration |
USD1012744S1 (en) * | 2022-05-16 | 2024-01-30 | Biolinq Incorporated | Wearable sensor with illuminated display |
Citations (93)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4245634A (en) * | 1975-01-22 | 1981-01-20 | Hospital For Sick Children | Artificial beta cell |
US4373527A (en) * | 1979-04-27 | 1983-02-15 | The Johns Hopkins University | Implantable, programmable medication infusion system |
US4425920A (en) * | 1980-10-24 | 1984-01-17 | Purdue Research Foundation | Apparatus and method for measurement and control of blood pressure |
US4431004A (en) * | 1981-10-27 | 1984-02-14 | Bessman Samuel P | Implantable glucose sensor |
US4494950A (en) * | 1982-01-19 | 1985-01-22 | The Johns Hopkins University | Plural module medication delivery system |
US4890620A (en) * | 1985-09-20 | 1990-01-02 | The Regents Of The University Of California | Two-dimensional diffusion glucose substrate sensing electrode |
US4986271A (en) * | 1989-07-19 | 1991-01-22 | The University Of New Mexico | Vivo refillable glucose sensor |
US4995402A (en) * | 1988-10-12 | 1991-02-26 | Thorne, Smith, Astill Technologies, Inc. | Medical droplet whole blood and like monitoring |
US5082550A (en) * | 1989-12-11 | 1992-01-21 | The United States Of America As Represented By The Department Of Energy | Enzyme electrochemical sensor electrode and method of making it |
US5279294A (en) * | 1985-04-08 | 1994-01-18 | Cascade Medical, Inc. | Medical diagnostic system |
US5285792A (en) * | 1992-01-10 | 1994-02-15 | Physio-Control Corporation | System for producing prioritized alarm messages in a medical instrument |
US5289497A (en) * | 1991-05-23 | 1994-02-22 | Interdigital Technology Corporation | Broadcast synchronized communication system |
US5379238A (en) * | 1989-03-03 | 1995-01-03 | Stark; Edward W. | Signal processing method and apparatus |
US5391250A (en) * | 1994-03-15 | 1995-02-21 | Minimed Inc. | Method of fabricating thin film sensors |
US5390671A (en) * | 1994-03-15 | 1995-02-21 | Minimed Inc. | Transcutaneous sensor insertion set |
US5593852A (en) * | 1993-12-02 | 1997-01-14 | Heller; Adam | Subcutaneous glucose electrode |
US5711001A (en) * | 1992-05-08 | 1998-01-20 | Motorola, Inc. | Method and circuit for acquisition by a radio receiver |
US5711861A (en) * | 1995-11-22 | 1998-01-27 | Ward; W. Kenneth | Device for monitoring changes in analyte concentration |
US5856758A (en) * | 1996-11-20 | 1999-01-05 | Adtran, Inc. | Low distortion driver employing positive feedback for reducing power loss in output impedance that effectively matches the impedance of driven line |
US6175752B1 (en) * | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US6338790B1 (en) * | 1998-10-08 | 2002-01-15 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
US20020013538A1 (en) * | 1997-09-30 | 2002-01-31 | David Teller | Method and apparatus for health signs monitoring |
US20020013522A1 (en) * | 1998-05-20 | 2002-01-31 | Steffen Lav | Medical apparatus for use by a patient for medical self treatment of diabetes |
US20030004403A1 (en) * | 2001-06-29 | 2003-01-02 | Darrel Drinan | Gateway platform for biological monitoring and delivery of therapeutic compounds |
US6503381B1 (en) * | 1997-09-12 | 2003-01-07 | Therasense, Inc. | Biosensor |
US20030023461A1 (en) * | 2001-03-14 | 2003-01-30 | Dan Quintanilla | Internet based therapy management system |
US20030023317A1 (en) * | 2001-07-27 | 2003-01-30 | Dexcom, Inc. | Membrane for use with implantable devices |
US6546268B1 (en) * | 1999-06-02 | 2003-04-08 | Ball Semiconductor, Inc. | Glucose sensor |
US6676816B2 (en) * | 2001-05-11 | 2004-01-13 | Therasense, Inc. | Transition metal complexes with (pyridyl)imidazole ligands and sensors using said complexes |
US20040010207A1 (en) * | 2002-07-15 | 2004-01-15 | Flaherty J. Christopher | Self-contained, automatic transcutaneous physiologic sensing system |
US20040011671A1 (en) * | 1997-03-04 | 2004-01-22 | Dexcom, Inc. | Device and method for determining analyte levels |
US20040017300A1 (en) * | 2002-07-25 | 2004-01-29 | Kotzin Michael D. | Portable communication device and corresponding method of operation |
US20050001024A1 (en) * | 2001-12-03 | 2005-01-06 | Yosuke Kusaka | Electronic apparatus, electronic camera, electronic device, image display apparatus, and image transmission system |
US20050004494A1 (en) * | 2001-01-22 | 2005-01-06 | Perez Edward P. | Lancet device having capillary action |
US20050003470A1 (en) * | 2003-06-10 | 2005-01-06 | Therasense, Inc. | Glucose measuring device for use in personal area network |
US20050010269A1 (en) * | 2000-01-21 | 2005-01-13 | Medical Research Group, Inc. | Microprocessor controlled ambulatory medical apparatus with hand held communication device |
US20050017864A1 (en) * | 2001-04-17 | 2005-01-27 | Alexandre Tsoukalis | System for monitoring medical parameters |
US20060004270A1 (en) * | 2004-06-23 | 2006-01-05 | Michel Bedard | Method and apparatus for the monitoring of clinical states |
US20060001538A1 (en) * | 2004-06-30 | 2006-01-05 | Ulrich Kraft | Methods of monitoring the concentration of an analyte |
US20060004439A1 (en) * | 2004-06-30 | 2006-01-05 | Benjamin Spenser | Device and method for assisting in the implantation of a prosthetic valve |
US6983867B1 (en) * | 2002-04-29 | 2006-01-10 | Dl Technology Llc | Fluid dispense pump with drip prevention mechanism and method for controlling same |
US20060010098A1 (en) * | 2004-06-04 | 2006-01-12 | Goodnow Timothy T | Diabetes care host-client architecture and data management system |
US20060009727A1 (en) * | 2004-04-08 | 2006-01-12 | Chf Solutions Inc. | Method and apparatus for an extracorporeal control of blood glucose |
US20060015024A1 (en) * | 2004-07-13 | 2006-01-19 | Mark Brister | Transcutaneous medical device with variable stiffness |
US20060015020A1 (en) * | 2004-07-06 | 2006-01-19 | Dexcom, Inc. | Systems and methods for manufacture of an analyte-measuring device including a membrane system |
US20060020190A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060016700A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060020300A1 (en) * | 2004-06-09 | 2006-01-26 | David Nghiem | Implantable medical device package antenna |
US7134999B2 (en) * | 2003-04-04 | 2006-11-14 | Dexcom, Inc. | Optimized sensor geometry for an implantable glucose sensor |
US20070016381A1 (en) * | 2003-08-22 | 2007-01-18 | Apurv Kamath | Systems and methods for processing analyte sensor data |
US7167818B2 (en) * | 1997-01-10 | 2007-01-23 | Health Hero Network, Inc. | Disease simulation system and method |
US20070017983A1 (en) * | 2005-07-19 | 2007-01-25 | 3M Innovative Properties Company | RFID reader supporting one-touch search functionality |
US20070038044A1 (en) * | 2004-07-13 | 2007-02-15 | Dobbles J M | Analyte sensor |
US20070073129A1 (en) * | 2005-09-23 | 2007-03-29 | Medtronic Minimed, Inc. | Flexible sensor apparatus |
US20070219496A1 (en) * | 2006-02-09 | 2007-09-20 | Dean Kamen | Pumping fluid delivery systems and methods using force application assembly |
US20080009692A1 (en) * | 2005-09-30 | 2008-01-10 | Abbott Diabetes Care, Inc. | Method and Apparatus for Providing Analyte Sensor and Data Processing Device |
US20080009304A1 (en) * | 2006-07-06 | 2008-01-10 | Fry Walter G | Electronic device power management system and method |
US20080018433A1 (en) * | 2003-10-29 | 2008-01-24 | Innovision Research & Technology Plc | Rfid Apparatus |
US20080017522A1 (en) * | 1997-02-06 | 2008-01-24 | Therasense, Inc. | Integrated Lancing and Measurement Device |
US20080021666A1 (en) * | 2003-08-01 | 2008-01-24 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US7324850B2 (en) * | 2004-04-29 | 2008-01-29 | Cardiac Pacemakers, Inc. | Method and apparatus for communication between a handheld programmer and an implantable medical device |
US20080062055A1 (en) * | 2006-09-11 | 2008-03-13 | Elster Electricity, Llc | Printed circuit notch antenna |
US20080242962A1 (en) * | 2007-03-20 | 2008-10-02 | Bernd Roesicke | System for in-vitro measurement of an analyte concentration |
US20090006034A1 (en) * | 2007-05-14 | 2009-01-01 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US20090005666A1 (en) * | 2000-02-23 | 2009-01-01 | Medtronic Minimed, Inc. | Real time self-adjusting calibration algorithm |
US20090005665A1 (en) * | 2007-05-14 | 2009-01-01 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US20090018425A1 (en) * | 2005-12-28 | 2009-01-15 | Tianmei Ouyang | Analyte monitoring: stabilizer for subcutaneous glucose sensor with incorporated antiglycolytic agent |
US20090018424A1 (en) * | 2006-10-04 | 2009-01-15 | Dexcom, Inc. | Analyte sensor |
US20090020502A1 (en) * | 1999-10-04 | 2009-01-22 | Bhullar Raghbir S | Biosensor and method of making |
US20090030294A1 (en) * | 2004-05-03 | 2009-01-29 | Dexcom, Inc. | Implantable analyte sensor |
US20100010329A1 (en) * | 2008-07-14 | 2010-01-14 | Abbott Diabetes Care Inc. | Closed Loop Control System Interface and Methods |
US20100010332A1 (en) * | 2003-12-09 | 2010-01-14 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
US20100016698A1 (en) * | 2003-11-19 | 2010-01-21 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
US7651596B2 (en) * | 2005-04-08 | 2010-01-26 | Dexcom, Inc. | Cellulosic-based interference domain for an analyte sensor |
US7653425B2 (en) * | 2006-08-09 | 2010-01-26 | Abbott Diabetes Care Inc. | Method and system for providing calibration of an analyte sensor in an analyte monitoring system |
US7833151B2 (en) * | 2002-12-26 | 2010-11-16 | Given Imaging Ltd. | In vivo imaging device with two imagers |
US7866026B1 (en) * | 2006-08-01 | 2011-01-11 | Abbott Diabetes Care Inc. | Method for making calibration-adjusted sensors |
US20110021889A1 (en) * | 2009-07-23 | 2011-01-27 | Abbott Diabetes Care Inc. | Continuous Analyte Measurement Systems and Systems and Methods for Implanting Them |
US8090445B2 (en) * | 2003-06-30 | 2012-01-03 | Codman Neuro Sciences Sárl | System and method for controlling an implantable medical device subject to magnetic field or radio frequency exposure |
US8094009B2 (en) * | 2008-08-27 | 2012-01-10 | The Invention Science Fund I, Llc | Health-related signaling via wearable items |
US8093991B2 (en) * | 2009-09-16 | 2012-01-10 | Greatbatch Ltd. | RFID detection and identification system for implantable medical devices |
US20120010642A1 (en) * | 2010-03-24 | 2012-01-12 | Lee Daniel H | Medical device inserters and processes of inserting and using medical devices |
US8098159B2 (en) * | 2006-06-09 | 2012-01-17 | Intelleflex Corporation | RF device comparing DAC output to incoming signal for selectively performing an action |
US8098201B2 (en) * | 2007-11-29 | 2012-01-17 | Electronics & Telecommunications Research Institute | Radio frequency identification tag and radio frequency identification tag antenna |
US8098160B2 (en) * | 2007-01-22 | 2012-01-17 | Cisco Technology, Inc. | Method and system for remotely provisioning and/or configuring a device |
US8098208B2 (en) * | 2006-05-30 | 2012-01-17 | Polyic Gmbh & Co. Kg | Antenna configuration and use thereof |
US8098161B2 (en) * | 2008-12-01 | 2012-01-17 | Raytheon Company | Radio frequency identification inlay with improved readability |
US8103325B2 (en) * | 1999-03-08 | 2012-01-24 | Tyco Healthcare Group Lp | Method and circuit for storing and providing historical physiological data |
US8103241B2 (en) * | 2007-12-07 | 2012-01-24 | Roche Diagnostics Operations, Inc. | Method and system for wireless device communication |
US8102789B2 (en) * | 2005-12-29 | 2012-01-24 | Medtronic, Inc. | System and method for synchronous wireless communication with a medical device |
US8102021B2 (en) * | 2008-05-12 | 2012-01-24 | Sychip Inc. | RF devices |
US8102263B2 (en) * | 2006-12-08 | 2012-01-24 | Electronics And Telecommunications Research Institute | Passive tag including volatile memory |
US8102154B2 (en) * | 2008-09-04 | 2012-01-24 | Medtronic Minimed, Inc. | Energy source isolation and protection circuit for an electronic device |
Family Cites Families (1317)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US587787A (en) | 1897-08-10 | Adjustable speed-gearing for bicycles | ||
US3123790A (en) | 1964-03-03 | tyler | ||
US654089A (en) | 1899-12-07 | 1900-07-17 | William G Browne | Can-opener. |
DE1401400A1 (en) | 1959-09-11 | 1968-12-19 | Karl Eickmann | High pressure rotary piston machine |
US3260656A (en) | 1962-09-27 | 1966-07-12 | Corning Glass Works | Method and apparatus for electrolytically determining a species in a fluid |
US3320725A (en) | 1965-08-17 | 1967-05-23 | Robert L Sampson | Bag vibrator |
GB1191363A (en) | 1968-02-19 | 1970-05-13 | Pavelle Ltd | Improvements in or relating to Electronic Thermostats. |
US3522807A (en) | 1968-10-02 | 1970-08-04 | Bluma Millenbach | Fecal receptacle |
US3653841A (en) | 1969-12-19 | 1972-04-04 | Hoffmann La Roche | Methods and compositions for determining glucose in blood |
US3670727A (en) | 1970-04-16 | 1972-06-20 | American Hospital Supply Corp | Medical infusion set |
US3776832A (en) | 1970-11-10 | 1973-12-04 | Energetics Science | Electrochemical detection cell |
US3719564A (en) | 1971-05-10 | 1973-03-06 | Philip Morris Inc | Method of determining a reducible gas concentration and sensor therefor |
US3837339A (en) | 1972-02-03 | 1974-09-24 | Whittaker Corp | Blood glucose level monitoring-alarm system and method therefor |
US3949388A (en) | 1972-11-13 | 1976-04-06 | Monitron Industries, Inc. | Physiological sensor and transmitter |
US3908657A (en) * | 1973-01-15 | 1975-09-30 | Univ Johns Hopkins | System for continuous withdrawal of blood |
US4100048A (en) | 1973-09-20 | 1978-07-11 | U.S. Philips Corporation | Polarographic cell |
US3926760A (en) | 1973-09-28 | 1975-12-16 | Du Pont | Process for electrophoretic deposition of polymer |
US3972320A (en) | 1974-08-12 | 1976-08-03 | Gabor Ujhelyi Kalman | Patient monitoring system |
US4036749A (en) | 1975-04-30 | 1977-07-19 | Anderson Donald R | Purification of saline water |
US3979274A (en) | 1975-09-24 | 1976-09-07 | The Yellow Springs Instrument Company, Inc. | Membrane for enzyme electrodes |
DE2645048A1 (en) | 1975-10-08 | 1977-04-21 | Gen Electric | PLANTABLE ELECTROCHEMICAL SENSOR |
US4016866A (en) | 1975-12-18 | 1977-04-12 | General Electric Company | Implantable electrochemical sensor |
US4055175A (en) | 1976-05-07 | 1977-10-25 | Miles Laboratories, Inc. | Blood glucose control apparatus |
DE2625834B2 (en) | 1976-06-09 | 1978-10-12 | Boehringer Mannheim Gmbh, 6800 Mannheim | Method for the determination of substrates or enzyme activities |
US4059406A (en) | 1976-07-12 | 1977-11-22 | E D T Supplies Limited | Electrochemical detector system |
US4076596A (en) * | 1976-10-07 | 1978-02-28 | Leeds & Northrup Company | Apparatus for electrolytically determining a species in a fluid and method of use |
US4129128A (en) | 1977-02-23 | 1978-12-12 | Mcfarlane Richard H | Securing device for catheter placement assembly |
FR2387659A1 (en) | 1977-04-21 | 1978-11-17 | Armines | GLYCEMIA CONTROL AND REGULATION DEVICE |
US4098574A (en) | 1977-08-01 | 1978-07-04 | Eastman Kodak Company | Glucose detection system free from fluoride-ion interference |
US4178916A (en) | 1977-09-26 | 1979-12-18 | Mcnamara Elger W | Diabetic insulin alarm system |
JPS5912135B2 (en) | 1977-09-28 | 1984-03-21 | 松下電器産業株式会社 | enzyme electrode |
US4151845A (en) | 1977-11-25 | 1979-05-01 | Miles Laboratories, Inc. | Blood glucose control apparatus |
DK151000C (en) | 1978-02-17 | 1988-06-13 | Radiometer As | PROCEDURE AND APPARATUS FOR DETERMINING A PATIENT'S IN VIVO PLASMA-PH VALUE |
FR2420331A1 (en) | 1978-03-23 | 1979-10-19 | Claude Bernard | COMBINED MEASURING HEAD, INTENDED TO BE PLACED ON OR IN BODY PARTS, ALLOWING THE SIMULTANEOUS OBTAINING OF MEASUREMENT SIGNALS RELATING TO AN ELECTRICAL ACTIVITY ON THE ONE HAND AND AN IONIC ACTIVITY ON THE OTHER HAND |
US4172770A (en) | 1978-03-27 | 1979-10-30 | Technicon Instruments Corporation | Flow-through electrochemical system analytical method |
DE2817363C2 (en) | 1978-04-20 | 1984-01-26 | Siemens AG, 1000 Berlin und 8000 München | Method for determining the concentration of sugar and a suitable electrocatalytic sugar sensor |
US4344438A (en) | 1978-08-02 | 1982-08-17 | The United States Of America As Represented By The Department Of Health, Education And Welfare | Optical sensor of plasma constituents |
HU177369B (en) | 1978-09-08 | 1981-09-28 | Radelkis Electrokemiai | Industrial molecule-selective sensing device and method for producing same |
US4240438A (en) | 1978-10-02 | 1980-12-23 | Wisconsin Alumni Research Foundation | Method for monitoring blood glucose levels and elements |
AU530979B2 (en) | 1978-12-07 | 1983-08-04 | Aus. Training Aids Pty. Ltd., | Detecting position of bullet fired at target |
US4247297A (en) * | 1979-02-23 | 1981-01-27 | Miles Laboratories, Inc. | Test means and method for interference resistant determination of oxidizing substances |
US4573994A (en) | 1979-04-27 | 1986-03-04 | The Johns Hopkins University | Refillable medication infusion apparatus |
US4365637A (en) | 1979-07-05 | 1982-12-28 | Dia-Med, Inc. | Perspiration indicating alarm for diabetics |
US4458686A (en) | 1979-08-02 | 1984-07-10 | Children's Hospital Medical Center | Cutaneous methods of measuring body substances |
US4401122A (en) | 1979-08-02 | 1983-08-30 | Children's Hospital Medical Center | Cutaneous methods of measuring body substances |
GB2067764B (en) | 1980-01-09 | 1984-01-25 | Nat Res Dev | Transcutaneous gas sensor |
US4450842A (en) | 1980-04-25 | 1984-05-29 | Cordis Corporation | Solid state reference electrode |
US4340458A (en) | 1980-06-02 | 1982-07-20 | Joslin Diabetes Center, Inc. | Glucose sensor |
US4404066A (en) | 1980-08-25 | 1983-09-13 | The Yellow Springs Instrument Company | Method for quantitatively determining a particular substrate catalyzed by a multisubstrate enzyme |
US4356074A (en) | 1980-08-25 | 1982-10-26 | The Yellow Springs Instrument Company, Inc. | Substrate specific galactose oxidase enzyme electrodes |
USRE32947E (en) | 1980-09-30 | 1989-06-13 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US4352960A (en) | 1980-09-30 | 1982-10-05 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US4327725A (en) | 1980-11-25 | 1982-05-04 | Alza Corporation | Osmotic device with hydrogel driving member |
US4390621A (en) | 1980-12-15 | 1983-06-28 | Miles Laboratories, Inc. | Method and device for detecting glucose concentration |
US4436094A (en) | 1981-03-09 | 1984-03-13 | Evreka, Inc. | Monitor for continuous in vivo measurement of glucose concentration |
AT369254B (en) | 1981-05-07 | 1982-12-27 | Otto Dipl Ing Dr Tech Prohaska | MEDICAL PROBE |
FR2508305B1 (en) | 1981-06-25 | 1986-04-11 | Slama Gerard | DEVICE FOR CAUSING A LITTLE BITE TO COLLECT A BLOOD DROP |
US4392849A (en) | 1981-07-27 | 1983-07-12 | The Cleveland Clinic Foundation | Infusion pump controller |
US4440175A (en) | 1981-08-10 | 1984-04-03 | University Patents, Inc. | Membrane electrode for non-ionic species |
DE3138194A1 (en) | 1981-09-25 | 1983-04-14 | Basf Ag, 6700 Ludwigshafen | WATER-INSOLUBLE POROESES PROTEIN MATERIAL, THEIR PRODUCTION AND USE |
DE3278334D1 (en) | 1981-10-23 | 1988-05-19 | Genetics Int Inc | Sensor for components of a liquid mixture |
US4418148A (en) | 1981-11-05 | 1983-11-29 | Miles Laboratories, Inc. | Multilayer enzyme electrode membrane |
JPS58153154A (en) | 1982-03-09 | 1983-09-12 | Ajinomoto Co Inc | Qualified electrode |
US4581336A (en) | 1982-04-26 | 1986-04-08 | Uop Inc. | Surface-modified electrodes |
FI831399L (en) | 1982-04-29 | 1983-10-30 | Agripat Sa | KONTAKTLINS AV HAERDAD POLYVINYL ALCOHOL |
DE3221339A1 (en) | 1982-06-05 | 1983-12-08 | Basf Ag, 6700 Ludwigshafen | METHOD FOR THE ELECTROCHEMICAL HYDRATION OF NICOTINAMIDADENINE-DINUCLEOTIDE |
US4427770A (en) * | 1982-06-14 | 1984-01-24 | Miles Laboratories, Inc. | High glucose-determining analytical element |
EP0098592A3 (en) | 1982-07-06 | 1985-08-21 | Fujisawa Pharmaceutical Co., Ltd. | Portable artificial pancreas |
US4509531A (en) | 1982-07-28 | 1985-04-09 | Teledyne Industries, Inc. | Personal physiological monitor |
DE3228551A1 (en) | 1982-07-30 | 1984-02-02 | Siemens AG, 1000 Berlin und 8000 München | METHOD FOR DETERMINING SUGAR CONCENTRATION |
US4534356A (en) | 1982-07-30 | 1985-08-13 | Diamond Shamrock Chemicals Company | Solid state transcutaneous blood gas sensors |
US4571292A (en) * | 1982-08-12 | 1986-02-18 | Case Western Reserve University | Apparatus for electrochemical measurements |
GB2128453A (en) | 1982-10-08 | 1984-04-26 | Philips Electronic Associated | System identification in communications systems |
US4552840A (en) | 1982-12-02 | 1985-11-12 | California And Hawaiian Sugar Company | Enzyme electrode and method for dextran analysis |
US4527240A (en) | 1982-12-29 | 1985-07-02 | Kvitash Vadim I | Balascopy method for detecting and rapidly evaluating multiple imbalances within multi-parametric systems |
JPS59138086A (en) | 1983-01-25 | 1984-08-08 | シャープ株式会社 | Substrate connecting method |
US4461691A (en) | 1983-02-10 | 1984-07-24 | The United States Of America As Represented By The United States Department Of Energy | Organic conductive films for semiconductor electrodes |
US4679562A (en) | 1983-02-16 | 1987-07-14 | Cardiac Pacemakers, Inc. | Glucose sensor |
IT1170375B (en) * | 1983-04-19 | 1987-06-03 | Giuseppe Bombardieri | Implantable device for measuring body fluid parameters |
CA1226036A (en) | 1983-05-05 | 1987-08-25 | Irving J. Higgins | Analytical equipment and sensor electrodes therefor |
CA1218704A (en) | 1983-05-05 | 1987-03-03 | Graham Davis | Assay systems using more than one enzyme |
US5682884A (en) | 1983-05-05 | 1997-11-04 | Medisense, Inc. | Strip electrode with screen printing |
US5509410A (en) | 1983-06-06 | 1996-04-23 | Medisense, Inc. | Strip electrode including screen printing of a single layer |
CA1219040A (en) | 1983-05-05 | 1987-03-10 | Elliot V. Plotkin | Measurement of enzyme-catalysed reactions |
US4650547A (en) | 1983-05-19 | 1987-03-17 | The Regents Of The University Of California | Method and membrane applicable to implantable sensor |
US4484987A (en) | 1983-05-19 | 1984-11-27 | The Regents Of The University Of California | Method and membrane applicable to implantable sensor |
US4675346A (en) | 1983-06-20 | 1987-06-23 | Loctite Corporation | UV curable silicone rubber compositions |
US4524114A (en) | 1983-07-05 | 1985-06-18 | Allied Corporation | Bifunctional air electrode |
US4538616A (en) | 1983-07-25 | 1985-09-03 | Robert Rogoff | Blood sugar level sensing and monitoring transducer |
US4543955A (en) | 1983-08-01 | 1985-10-01 | Cordis Corporation | System for controlling body implantable action device |
US4655880A (en) | 1983-08-01 | 1987-04-07 | Case Western Reserve University | Apparatus and method for sensing species, substances and substrates using oxidase |
SE8305704D0 (en) | 1983-10-18 | 1983-10-18 | Leo Ab | Cuvette |
US4560534A (en) | 1983-11-02 | 1985-12-24 | Miles Laboratories, Inc. | Polymer catalyst transducers |
US4522690A (en) | 1983-12-01 | 1985-06-11 | Honeywell Inc. | Electrochemical sensing of carbon monoxide |
US6017335A (en) | 1983-12-12 | 2000-01-25 | Burnham; Warren R. | Method for making a tubular product, especially a catheter, and article made thereby |
WO1985002627A1 (en) | 1983-12-16 | 1985-06-20 | Genetics International, Inc. | Assay for nucleic acids |
DE3571456D1 (en) | 1984-04-30 | 1989-08-17 | Stiftung R E | Process for the sensitization of an oxidoreduction photocalatyst, and photocatalyst thus obtained |
US5141868A (en) | 1984-06-13 | 1992-08-25 | Internationale Octrooi Maatschappij "Octropa" Bv | Device for use in chemical test procedures |
DK8601218A (en) | 1984-07-18 | 1986-03-17 | ||
DE3429596A1 (en) | 1984-08-10 | 1986-02-20 | Siemens AG, 1000 Berlin und 8000 München | DEVICE FOR THE PHYSIOLOGICAL FREQUENCY CONTROL OF A PACEMAKER PROVIDED WITH A PICTURE ELECTRODE |
US4820399A (en) | 1984-08-31 | 1989-04-11 | Shimadzu Corporation | Enzyme electrodes |
CA1254091A (en) | 1984-09-28 | 1989-05-16 | Vladimir Feingold | Implantable medication infusion system |
JPS61111428A (en) | 1984-11-06 | 1986-05-29 | Terumo Corp | Electronic clinical thermometer |
US4627842A (en) | 1984-11-19 | 1986-12-09 | William Katz | Intravenous needle assembly |
US4721601A (en) * | 1984-11-23 | 1988-01-26 | Massachusetts Institute Of Technology | Molecule-based microelectronic devices |
US4717673A (en) * | 1984-11-23 | 1988-01-05 | Massachusetts Institute Of Technology | Microelectrochemical devices |
JPH0617889B2 (en) * | 1984-11-27 | 1994-03-09 | 株式会社日立製作所 | Biochemical sensor |
EP0186210B1 (en) | 1984-12-28 | 1992-04-22 | TERUMO KABUSHIKI KAISHA trading as TERUMO CORPORATION | Ion sensor |
GB8500729D0 (en) | 1985-01-11 | 1985-02-13 | Hill H A O | Surface-modified electrode |
DE3502913C1 (en) | 1985-01-29 | 1986-07-03 | Günter Prof. Dr.rer.nat. 5100 Aachen Rau | Sensor for non-invasive detection of electrophysiological values |
AU5481786A (en) | 1985-03-20 | 1986-09-25 | Hochmair, E.S. | Transcutaneous power and signal transmission system |
US4627445A (en) * | 1985-04-08 | 1986-12-09 | Garid, Inc. | Glucose medical monitoring system |
US4781798A (en) | 1985-04-19 | 1988-11-01 | The Regents Of The University Of California | Transparent multi-oxygen sensor array and method of using same |
US4671288A (en) | 1985-06-13 | 1987-06-09 | The Regents Of The University Of California | Electrochemical cell sensor for continuous short-term use in tissues and blood |
DE3687646T3 (en) * | 1985-06-21 | 2001-05-31 | Matsushita Electric Ind Co Ltd | BIOSENSOR AND THEIR PRODUCTION. |
US4938860A (en) | 1985-06-28 | 1990-07-03 | Miles Inc. | Electrode for electrochemical sensors |
US4796634A (en) * | 1985-08-09 | 1989-01-10 | Lawrence Medical Systems, Inc. | Methods and apparatus for monitoring cardiac output |
US4805624A (en) * | 1985-09-09 | 1989-02-21 | The Montefiore Hospital Association Of Western Pa | Low-potential electrochemical redox sensors |
US5245314A (en) | 1985-09-18 | 1993-09-14 | Kah Jr Carl L C | Location monitoring system |
US4680268A (en) * | 1985-09-18 | 1987-07-14 | Children's Hospital Medical Center | Implantable gas-containing biosensor and method for measuring an analyte such as glucose |
US4627908A (en) | 1985-10-24 | 1986-12-09 | Chevron Research Company | Process for stabilizing lube base stocks derived from bright stock |
US4684245A (en) | 1985-10-28 | 1987-08-04 | Oximetrix, Inc. | Electro-optical coupler for catheter oximeter |
US4830959A (en) | 1985-11-11 | 1989-05-16 | Medisense, Inc. | Electrochemical enzymic assay procedures |
GB8529300D0 (en) | 1985-11-28 | 1986-01-02 | Ici Plc | Membrane |
US4755173A (en) | 1986-02-25 | 1988-07-05 | Pacesetter Infusion, Ltd. | Soft cannula subcutaneous injection set |
US4776944A (en) | 1986-03-20 | 1988-10-11 | Jiri Janata | Chemical selective sensors utilizing admittance modulated membranes |
US4685463A (en) | 1986-04-03 | 1987-08-11 | Williams R Bruce | Device for continuous in vivo measurement of blood glucose concentrations |
US4726378A (en) * | 1986-04-11 | 1988-02-23 | Minnesota Mining And Manufacturing Company | Adjustable magnetic supercutaneous device and transcutaneous coupling apparatus |
US4757022A (en) | 1986-04-15 | 1988-07-12 | Markwell Medical Institute, Inc. | Biological fluid measuring device |
US4994167A (en) * | 1986-04-15 | 1991-02-19 | Markwell Medical Institute, Inc. | Biological fluid measuring device |
US4711247A (en) | 1986-04-18 | 1987-12-08 | Henry Fishman | Allergy testing method and apparatus |
US4909908A (en) | 1986-04-24 | 1990-03-20 | Pepi Ross | Electrochemical cncentration detector method |
DE3614821A1 (en) | 1986-05-02 | 1987-11-05 | Siemens Ag | IMPLANTABLE, CALIBRABLE MEASURING DEVICE FOR A BODY SUBSTANCE AND CALIBRATION METHOD |
US4703756A (en) | 1986-05-06 | 1987-11-03 | The Regents Of The University Of California | Complete glucose monitoring system with an implantable, telemetered sensor module |
US4731726A (en) | 1986-05-19 | 1988-03-15 | Healthware Corporation | Patient-operated glucose monitor and diabetes management system |
DE3617161A1 (en) | 1986-05-22 | 1987-11-26 | Boehringer Mannheim Gmbh | SYSTEM FOR DETERMINING THE CONCENTRATION OF INGREDIENTS OF BODY LIQUIDS |
GB8612861D0 (en) | 1986-05-27 | 1986-07-02 | Cambridge Life Sciences | Immobilised enzyme biosensors |
US4698057A (en) | 1986-06-09 | 1987-10-06 | Joishy Suresh K | Built in assembly for stabilizing and securing intravascular needle or catheter like device |
US4969468A (en) | 1986-06-17 | 1990-11-13 | Alfred E. Mann Foundation For Scientific Research | Electrode array for use in connection with a living body and method of manufacture |
AU598820B2 (en) | 1986-06-20 | 1990-07-05 | Molecular Devices Corporation | Zero volume electrochemical cell |
US5001054A (en) | 1986-06-26 | 1991-03-19 | Becton, Dickinson And Company | Method for monitoring glucose |
JPS636451A (en) | 1986-06-27 | 1988-01-12 | Terumo Corp | Enzyme sensor |
US4764416A (en) | 1986-07-01 | 1988-08-16 | Mitsubishi Denki Kabushiki Kaisha | Electric element circuit using oxidation-reduction substances |
US4784736A (en) | 1986-07-07 | 1988-11-15 | Bend Research, Inc. | Functional, photochemically active, and chemically asymmetric membranes by interfacial polymerization of derivatized multifunctional prepolymers |
US4917800A (en) | 1986-07-07 | 1990-04-17 | Bend Research, Inc. | Functional, photochemically active, and chemically asymmetric membranes by interfacial polymerization of derivatized multifunctional prepolymers |
US4726716A (en) * | 1986-07-21 | 1988-02-23 | Mcguire Thomas V | Fastener for catheter |
US4894137A (en) * | 1986-09-12 | 1990-01-16 | Omron Tateisi Electronics Co. | Enzyme electrode |
US5055171A (en) | 1986-10-06 | 1991-10-08 | T And G Corporation | Ionic semiconductor materials and applications thereof |
US4897162A (en) * | 1986-11-14 | 1990-01-30 | The Cleveland Clinic Foundation | Pulse voltammetry |
DE3700119A1 (en) | 1987-01-03 | 1988-07-14 | Inst Diabetestechnologie Gemei | IMPLANTABLE ELECTROCHEMICAL SENSOR |
US4934369A (en) | 1987-01-30 | 1990-06-19 | Minnesota Mining And Manufacturing Company | Intravascular blood parameter measurement system |
GB2201248B (en) | 1987-02-24 | 1991-04-17 | Ici Plc | Enzyme electrode sensors |
US5002054A (en) | 1987-02-25 | 1991-03-26 | Ash Medical Systems, Inc. | Interstitial filtration and collection device and method for long-term monitoring of physiological constituents of the body |
US4854322A (en) | 1987-02-25 | 1989-08-08 | Ash Medical Systems, Inc. | Capillary filtration and collection device for long-term monitoring of blood constituents |
US4777953A (en) | 1987-02-25 | 1988-10-18 | Ash Medical Systems, Inc. | Capillary filtration and collection method for long-term monitoring of blood constituents |
US4848351A (en) | 1987-03-04 | 1989-07-18 | Sentry Medical Products, Inc. | Medical electrode assembly |
US4923586A (en) | 1987-03-31 | 1990-05-08 | Daikin Industries, Ltd. | Enzyme electrode unit |
US4935345A (en) | 1987-04-07 | 1990-06-19 | Arizona Board Of Regents | Implantable microelectronic biochemical sensor incorporating thin film thermopile |
US4759828A (en) | 1987-04-09 | 1988-07-26 | Nova Biomedical Corporation | Glucose electrode and method of determining glucose |
US5352348A (en) | 1987-04-09 | 1994-10-04 | Nova Biomedical Corporation | Method of using enzyme electrode |
US4749985A (en) | 1987-04-13 | 1988-06-07 | United States Of America As Represented By The United States Department Of Energy | Functional relationship-based alarm processing |
EP0290683A3 (en) | 1987-05-01 | 1988-12-14 | Diva Medical Systems B.V. | Diabetes management system and apparatus |
US5286364A (en) | 1987-06-08 | 1994-02-15 | Rutgers University | Surface-modified electochemical biosensor |
US4822337A (en) | 1987-06-22 | 1989-04-18 | Stanley Newhouse | Insulin delivery method and apparatus |
JPH07122624B2 (en) | 1987-07-06 | 1995-12-25 | ダイキン工業株式会社 | Biosensor |
US4874500A (en) | 1987-07-15 | 1989-10-17 | Sri International | Microelectrochemical sensor and sensor array |
GB8718430D0 (en) | 1987-08-04 | 1987-09-09 | Ici Plc | Sensor |
JPS6423155A (en) | 1987-07-17 | 1989-01-25 | Daikin Ind Ltd | Electrode refreshing device for biosensor |
DE3854650T2 (en) | 1987-08-11 | 1996-03-21 | Terumo Corp | AUTOMATIC SPHYGMOMANOMETER. |
US4974929A (en) | 1987-09-22 | 1990-12-04 | Baxter International, Inc. | Fiber optical probe connector for physiologic measurement devices |
NL8702370A (en) | 1987-10-05 | 1989-05-01 | Groningen Science Park | METHOD AND SYSTEM FOR GLUCOSE DETERMINATION AND USEABLE MEASURING CELL ASSEMBLY. |
US4815469A (en) | 1987-10-08 | 1989-03-28 | Siemens-Pacesetter, Inc. | Implantable blood oxygen sensor and method of use |
US4818994A (en) | 1987-10-22 | 1989-04-04 | Rosemount Inc. | Transmitter with internal serial bus |
GB8725936D0 (en) | 1987-11-05 | 1987-12-09 | Genetics Int Inc | Sensing system |
JPH01140054A (en) * | 1987-11-26 | 1989-06-01 | Nec Corp | Glucose sensor |
US5006110A (en) | 1987-12-01 | 1991-04-09 | Pacesetter Infusion, Ltd. | Air-in-line detector infusion system |
US4813424A (en) | 1987-12-23 | 1989-03-21 | University Of New Mexico | Long-life membrane electrode for non-ionic species |
US5108564A (en) | 1988-03-15 | 1992-04-28 | Tall Oak Ventures | Method and apparatus for amperometric diagnostic analysis |
DE68924026T3 (en) | 1988-03-31 | 2008-01-10 | Matsushita Electric Industrial Co., Ltd., Kadoma | BIOSENSOR AND ITS MANUFACTURE. |
US4921199A (en) | 1988-04-25 | 1990-05-01 | Villaveces James W | Device for aiding in preparation of intravenous therapy |
GB8817421D0 (en) | 1988-07-21 | 1988-08-24 | Medisense Inc | Bioelectrochemical electrodes |
US4925268A (en) | 1988-07-25 | 1990-05-15 | Abbott Laboratories | Fiber-optic physiological probes |
US4954129A (en) | 1988-07-25 | 1990-09-04 | Abbott Laboratories | Hydrodynamic clot flushing |
EP0353328A1 (en) | 1988-08-03 | 1990-02-07 | Dräger Nederland B.V. | A polarographic-amperometric three-electrode sensor |
US5340722A (en) | 1988-08-24 | 1994-08-23 | Avl Medical Instruments Ag | Method for the determination of the concentration of an enzyme substrate and a sensor for carrying out the method |
US5264106A (en) | 1988-10-07 | 1993-11-23 | Medisense, Inc. | Enhanced amperometric sensor |
US4895147A (en) * | 1988-10-28 | 1990-01-23 | Sherwood Medical Company | Lancet injector |
US5360404A (en) | 1988-12-14 | 1994-11-01 | Inviro Medical Devices Ltd. | Needle guard and needle assembly for syringe |
US5068536A (en) | 1989-01-19 | 1991-11-26 | Futrex, Inc. | Method for providing custom calibration for near infrared instruments for measurement of blood glucose |
US5305008A (en) | 1991-08-12 | 1994-04-19 | Integrated Silicon Design Pty. Ltd. | Transponder system |
EP0384504A1 (en) | 1989-02-24 | 1990-08-29 | Duphar International Research B.V | Detection strip for detecting and identifying chemical air contaminants, and portable detection kit comprising said strips |
US5205920A (en) | 1989-03-03 | 1993-04-27 | Noboru Oyama | Enzyme sensor and method of manufacturing the same |
US5089112A (en) * | 1989-03-20 | 1992-02-18 | Associated Universities, Inc. | Electrochemical biosensor based on immobilized enzymes and redox polymers |
JPH02298855A (en) | 1989-03-20 | 1990-12-11 | Assoc Univ Inc | Electrochemical biosensor using immobilized enzyme and redox polymer |
US4953552A (en) | 1989-04-21 | 1990-09-04 | Demarzo Arthur P | Blood glucose monitoring system |
SE463604B (en) | 1989-04-25 | 1990-12-17 | Flaekt Ab | DEVICE FOR PURIFICATION OF PREPARED PARTICLES POLLUTANTS VENTILATION AIR FROM A SPRAY BOX BEFORE PAINTING |
EP0396788A1 (en) | 1989-05-08 | 1990-11-14 | Dräger Nederland B.V. | Process and sensor for measuring the glucose content of glucosecontaining fluids |
US4988341A (en) * | 1989-06-05 | 1991-01-29 | Eastman Kodak Company | Sterilizing dressing device and method for skin puncture |
US5198367A (en) | 1989-06-09 | 1993-03-30 | Masuo Aizawa | Homogeneous amperometric immunoassay |
FR2648353B1 (en) | 1989-06-16 | 1992-03-27 | Europhor Sa | MICRODIALYSIS PROBE |
CH677149A5 (en) | 1989-07-07 | 1991-04-15 | Disetronic Ag | |
US5431160A (en) | 1989-07-19 | 1995-07-11 | University Of New Mexico | Miniature implantable refillable glucose sensor and material therefor |
US5013161A (en) | 1989-07-28 | 1991-05-07 | Becton, Dickinson And Company | Electronic clinical thermometer |
US5264104A (en) | 1989-08-02 | 1993-11-23 | Gregg Brian A | Enzyme electrodes |
US5264105A (en) | 1989-08-02 | 1993-11-23 | Gregg Brian A | Enzyme electrodes |
US5262035A (en) | 1989-08-02 | 1993-11-16 | E. Heller And Company | Enzyme electrodes |
US5320725A (en) | 1989-08-02 | 1994-06-14 | E. Heller & Company | Electrode and method for the detection of hydrogen peroxide |
US4944299A (en) | 1989-08-08 | 1990-07-31 | Siemens-Pacesetter, Inc. | High speed digital telemetry system for implantable device |
US5101814A (en) | 1989-08-11 | 1992-04-07 | Palti Yoram Prof | System for monitoring and controlling blood glucose |
US5190041A (en) | 1989-08-11 | 1993-03-02 | Palti Yoram Prof | System for monitoring and controlling blood glucose |
US5095904A (en) | 1989-09-08 | 1992-03-17 | Cochlear Pty. Ltd. | Multi-peak speech procession |
US5050612A (en) | 1989-09-12 | 1991-09-24 | Matsumura Kenneth N | Device for computer-assisted monitoring of the body |
FR2652736A1 (en) | 1989-10-06 | 1991-04-12 | Neftel Frederic | IMPLANTABLE DEVICE FOR EVALUATING THE RATE OF GLUCOSE. |
US5036860A (en) | 1989-11-24 | 1991-08-06 | Medical Device Technologies, Inc. | Disposable soft tissue biopsy apparatus |
EP0429076B1 (en) | 1989-11-24 | 1996-01-31 | Matsushita Electric Industrial Co., Ltd. | Preparation of biosensor |
US5140985A (en) | 1989-12-11 | 1992-08-25 | Schroeder Jon M | Noninvasive blood glucose measuring device |
US5342789A (en) | 1989-12-14 | 1994-08-30 | Sensor Technologies, Inc. | Method and device for detecting and quantifying glucose in body fluids |
AU634863B2 (en) | 1989-12-15 | 1993-03-04 | Roche Diagnostics Operations Inc. | Redox mediator reagent and biosensor |
US5051688A (en) | 1989-12-20 | 1991-09-24 | Rohm Co., Ltd. | Crossed coil meter driving device having a plurality of input parameters |
US5286362A (en) | 1990-02-03 | 1994-02-15 | Boehringer Mannheim Gmbh | Method and sensor electrode system for the electrochemical determination of an analyte or an oxidoreductase as well as the use of suitable compounds therefor |
US5109850A (en) | 1990-02-09 | 1992-05-05 | Massachusetts Institute Of Technology | Automatic blood monitoring for medication delivery method and apparatus |
US5162407A (en) | 1990-03-06 | 1992-11-10 | Investors Diversified Capital, Inc. | Silicone rubber sealant composition |
US5161532A (en) | 1990-04-19 | 1992-11-10 | Teknekron Sensor Development Corporation | Integral interstitial fluid sensor |
US5165407A (en) | 1990-04-19 | 1992-11-24 | The University Of Kansas | Implantable glucose sensor |
US5202261A (en) | 1990-07-19 | 1993-04-13 | Miles Inc. | Conductive sensors and their use in diagnostic assays |
US5250439A (en) | 1990-07-19 | 1993-10-05 | Miles Inc. | Use of conductive sensors in diagnostic assays |
US5124661A (en) | 1990-07-23 | 1992-06-23 | I-Stat Corporation | Reusable test unit for simulating electrochemical sensor signals for quality assurance of portable blood analyzer instruments |
EP0550641B1 (en) | 1990-09-28 | 1994-05-25 | Pfizer Inc. | Dispensing device containing a hydrophobic medium |
US5058592A (en) | 1990-11-02 | 1991-10-22 | Whisler G Douglas | Adjustable mountable doppler ultrasound transducer device |
DE69126885T3 (en) | 1990-12-12 | 2001-10-18 | Sherwood Serv Ag | CALIBRATION OF AN INFRARED THERMOMETER BY MEANS OF AREA CALIBRATION DISPLAY |
US5527288A (en) | 1990-12-13 | 1996-06-18 | Elan Medical Technologies Limited | Intradermal drug delivery device and method for intradermal delivery of drugs |
US5228449A (en) | 1991-01-22 | 1993-07-20 | Athanasios G. Christ | System and method for detecting out-of-hospital cardiac emergencies and summoning emergency assistance |
AU1356792A (en) | 1991-01-25 | 1992-08-27 | Markwell Medical Institute, Inc. | Implantable biological fluid measuring device |
FR2673289B1 (en) * | 1991-02-21 | 1994-06-17 | Asulab Sa | SENSOR FOR MEASURING THE QUANTITY OF A COMPONENT IN SOLUTION. |
US5262305A (en) | 1991-03-04 | 1993-11-16 | E. Heller & Company | Interferant eliminating biosensors |
JPH04278450A (en) | 1991-03-04 | 1992-10-05 | Adam Heller | Biosensor and method for analyzing subject |
US5469855A (en) | 1991-03-08 | 1995-11-28 | Exergen Corporation | Continuous temperature monitor |
US5135004A (en) | 1991-03-12 | 1992-08-04 | Incontrol, Inc. | Implantable myocardial ischemia monitor and related method |
US5238729A (en) | 1991-04-05 | 1993-08-24 | Minnesota Mining And Manufacturing Company | Sensors based on nanosstructured composite films |
US5208154A (en) | 1991-04-08 | 1993-05-04 | The United States Of America As Represented By The Department Of Energy | Reversibly immobilized biological materials in monolayer films on electrodes |
US5192416A (en) | 1991-04-09 | 1993-03-09 | New Mexico State University Technology Transfer Corporation | Method and apparatus for batch injection analysis |
US5293546A (en) | 1991-04-17 | 1994-03-08 | Martin Marietta Corporation | Oxide coated metal grid electrode structure in display devices |
US5122925A (en) | 1991-04-22 | 1992-06-16 | Control Products, Inc. | Package for electronic components |
JP3118015B2 (en) | 1991-05-17 | 2000-12-18 | アークレイ株式会社 | Biosensor and separation and quantification method using the same |
US5209229A (en) | 1991-05-20 | 1993-05-11 | Telectronics Pacing Systems, Inc. | Apparatus and method employing plural electrode configurations for cardioversion of atrial fibrillation in an arrhythmia control system |
FI88223C (en) | 1991-05-22 | 1993-04-13 | Polar Electro Oy | Telemetric transmitter unit |
JP2816262B2 (en) | 1991-07-09 | 1998-10-27 | 工業技術院長 | Carbon microsensor electrode and method of manufacturing the same |
CA2074702C (en) | 1991-07-29 | 1996-11-19 | Donald J. Urbas | Programmable transponder |
US5284156A (en) * | 1991-08-30 | 1994-02-08 | M3 Systems, Inc. | Automatic tissue sampling apparatus |
GB9120144D0 (en) | 1991-09-20 | 1991-11-06 | Imperial College | A dialysis electrode device |
US5234835A (en) | 1991-09-26 | 1993-08-10 | C.R. Bard, Inc. | Precalibrated fiber optic sensing method |
US5322063A (en) | 1991-10-04 | 1994-06-21 | Eli Lilly And Company | Hydrophilic polyurethane membranes for electrochemical glucose sensors |
US5264103A (en) | 1991-10-18 | 1993-11-23 | Matsushita Electric Industrial Co., Ltd. | Biosensor and a method for measuring a concentration of a substrate in a sample |
US5217595A (en) | 1991-10-25 | 1993-06-08 | The Yellow Springs Instrument Company, Inc. | Electrochemical gas sensor |
US5415164A (en) | 1991-11-04 | 1995-05-16 | Biofield Corp. | Apparatus and method for screening and diagnosing trauma or disease in body tissues |
DE4139122C1 (en) | 1991-11-28 | 1993-04-08 | Fenzlein, Paul-Gerhard, 8500 Nuernberg, De | |
US5372427A (en) | 1991-12-19 | 1994-12-13 | Texas Instruments Incorporated | Temperature sensor |
US5271815A (en) | 1991-12-26 | 1993-12-21 | Via Medical Corporation | Method for measuring glucose |
US5246867A (en) | 1992-01-17 | 1993-09-21 | University Of Maryland At Baltimore | Determination and quantification of saccharides by luminescence lifetimes and energy transfer |
IL104365A0 (en) | 1992-01-31 | 1993-05-13 | Gensia Pharma | Method and apparatus for closed loop drug delivery |
NL9200207A (en) | 1992-02-05 | 1993-09-01 | Nedap Nv | IMPLANTABLE BIOMEDICAL SENSOR DEVICE, IN PARTICULAR FOR MEASUREMENT OF THE GLUCOSE CONCENTRATION. |
US5328927A (en) | 1992-03-03 | 1994-07-12 | Merck Sharpe & Dohme, Ltd. | Hetercyclic compounds, processes for their preparation and pharmaceutical compositions containing them |
ZA931077B (en) | 1992-03-05 | 1994-01-04 | Qualcomm Inc | Apparatus and method for reducing message collision between mobile stations simultaneously accessing a base station in a cdma cellular communications system |
DE69319771T2 (en) | 1992-03-31 | 1999-04-22 | Dainippon Printing Co Ltd | Immobilized enzyme electrode, composition for its production and electrically conductive enzymes |
USD342451S (en) * | 1992-04-01 | 1993-12-21 | S. C. Johnson & Son, Inc. | Bottle |
ATE197761T1 (en) | 1992-04-03 | 2000-12-15 | Micromedical Ind Ltd | ARRANGEMENT FOR MONITORING PHYSIOLOGICAL PARAMETERS |
GB9211402D0 (en) | 1992-05-29 | 1992-07-15 | Univ Manchester | Sensor devices |
US5333615A (en) | 1992-06-22 | 1994-08-02 | William Craelius | Apparatus for digitally recording and analyzing electrocardial and other bioelectric signals |
DK95792A (en) | 1992-07-24 | 1994-01-25 | Radiometer As | Sensor for non-invasive, in vivo determination of an analyte and blood flow |
US6283761B1 (en) | 1992-09-08 | 2001-09-04 | Raymond Anthony Joao | Apparatus and method for processing and/or for providing healthcare information and/or healthcare-related information |
US5400782A (en) | 1992-10-07 | 1995-03-28 | Graphic Controls Corporation | Integral medical electrode including a fusible conductive substrate |
US5421816A (en) | 1992-10-14 | 1995-06-06 | Endodermic Medical Technologies Company | Ultrasonic transdermal drug delivery system |
US5387327A (en) | 1992-10-19 | 1995-02-07 | Duquesne University Of The Holy Ghost | Implantable non-enzymatic electrochemical glucose sensor |
US5320098A (en) | 1992-10-20 | 1994-06-14 | Sun Microsystems, Inc. | Optical transdermal link |
WO1994010553A1 (en) | 1992-10-23 | 1994-05-11 | Optex Biomedical, Inc. | Fibre-optic probe for the measurement of fluid parameters |
US5899855A (en) | 1992-11-17 | 1999-05-04 | Health Hero Network, Inc. | Modular microprocessor-based health monitoring system |
US20030212579A1 (en) | 2002-05-08 | 2003-11-13 | Brown Stephen J. | Remote health management system |
US5601435A (en) | 1994-11-04 | 1997-02-11 | Intercare | Method and apparatus for interactively monitoring a physiological condition and for interactively providing health related information |
US5918603A (en) | 1994-05-23 | 1999-07-06 | Health Hero Network, Inc. | Method for treating medical conditions using a microprocessor-based video game |
ZA938555B (en) | 1992-11-23 | 1994-08-02 | Lilly Co Eli | Technique to improve the performance of electrochemical sensors |
US5410326A (en) | 1992-12-04 | 1995-04-25 | Goldstein; Steven W. | Programmable remote control device for interacting with a plurality of remotely controlled devices |
DK148592D0 (en) | 1992-12-10 | 1992-12-10 | Novo Nordisk As | APPARATUS |
US5499243A (en) | 1993-01-22 | 1996-03-12 | Hall; Dennis R. | Method and apparatus for coordinating transfer of information between a base station and a plurality of radios |
US5299571A (en) | 1993-01-22 | 1994-04-05 | Eli Lilly And Company | Apparatus and method for implantation of sensors |
FR2701117B1 (en) | 1993-02-04 | 1995-03-10 | Asulab Sa | Electrochemical measurement system with multizone sensor, and its application to glucose measurement. |
GB9304306D0 (en) | 1993-03-03 | 1993-04-21 | Univ Alberta | Glucose sensor |
US5600301A (en) | 1993-03-11 | 1997-02-04 | Schrader Automotive Inc. | Remote tire pressure monitoring system employing coded tire identification and radio frequency transmission, and enabling recalibration upon tire rotation or replacement |
US5400794A (en) | 1993-03-19 | 1995-03-28 | Gorman; Peter G. | Biomedical response monitor and technique using error correction |
DE59410066D1 (en) | 1993-04-23 | 2002-04-11 | Boehringer Mannheim Gmbh | System for analyzing the contents of liquid samples |
US5558638A (en) | 1993-04-30 | 1996-09-24 | Healthdyne, Inc. | Patient monitor and support system |
DE4318519C2 (en) | 1993-06-03 | 1996-11-28 | Fraunhofer Ges Forschung | Electrochemical sensor |
US5575563A (en) | 1993-07-15 | 1996-11-19 | Chiu; Job | Multiusage thermometer |
JP2979933B2 (en) | 1993-08-03 | 1999-11-22 | セイコーエプソン株式会社 | Pulse wave analyzer |
DE4329898A1 (en) | 1993-09-04 | 1995-04-06 | Marcus Dr Besson | Wireless medical diagnostic and monitoring device |
US5582184A (en) | 1993-10-13 | 1996-12-10 | Integ Incorporated | Interstitial fluid collection and constituent measurement |
US5885211A (en) | 1993-11-15 | 1999-03-23 | Spectrix, Inc. | Microporation of human skin for monitoring the concentration of an analyte |
US6336269B1 (en) | 1993-11-16 | 2002-01-08 | Benjamin N. Eldridge | Method of fabricating an interconnection element |
US5997501A (en) | 1993-11-18 | 1999-12-07 | Elan Corporation, Plc | Intradermal drug delivery device |
US5497772A (en) | 1993-11-19 | 1996-03-12 | Alfred E. Mann Foundation For Scientific Research | Glucose monitoring system |
US5791344A (en) | 1993-11-19 | 1998-08-11 | Alfred E. Mann Foundation For Scientific Research | Patient monitoring system |
FR2713372B1 (en) | 1993-12-01 | 1996-03-01 | Neopost Ind | Thermal protection device for secure electronic device, in particular postage meter. |
JPH07182462A (en) | 1993-12-22 | 1995-07-21 | Toshiba Corp | Character recognition device/method |
US5724968A (en) * | 1993-12-29 | 1998-03-10 | First Opinion Corporation | Computerized medical diagnostic system including meta function |
US5589326A (en) | 1993-12-30 | 1996-12-31 | Boehringer Mannheim Corporation | Osmium-containing redox mediator |
US5320715A (en) | 1994-01-14 | 1994-06-14 | Lloyd Berg | Separation of 1-pentanol from cyclopentanol by extractive distillation |
DE4401400A1 (en) | 1994-01-19 | 1995-07-20 | Ernst Prof Dr Pfeiffer | Method and arrangement for continuously monitoring the concentration of a metabolite |
US5437999A (en) | 1994-02-22 | 1995-08-01 | Boehringer Mannheim Corporation | Electrochemical sensor |
US5543326A (en) | 1994-03-04 | 1996-08-06 | Heller; Adam | Biosensor including chemically modified enzymes |
US5506458A (en) | 1994-03-04 | 1996-04-09 | Quantum Corporation | Low cost permanent magnet disk spindle motor |
US5536249A (en) | 1994-03-09 | 1996-07-16 | Visionary Medical Products, Inc. | Pen-type injector with a microprocessor and blood characteristic monitor |
US5609575A (en) | 1994-04-11 | 1997-03-11 | Graseby Medical Limited | Infusion pump and method with dose-rate calculation |
JP3061351B2 (en) | 1994-04-25 | 2000-07-10 | 松下電器産業株式会社 | Method and apparatus for quantifying specific compounds |
US5569186A (en) | 1994-04-25 | 1996-10-29 | Minimed Inc. | Closed loop infusion pump system with removable glucose sensor |
DE4415896A1 (en) | 1994-05-05 | 1995-11-09 | Boehringer Mannheim Gmbh | Analysis system for monitoring the concentration of an analyte in the blood of a patient |
US5545191A (en) | 1994-05-06 | 1996-08-13 | Alfred E. Mann Foundation For Scientific Research | Method for optimally positioning and securing the external unit of a transcutaneous transducer of the skin of a living body |
US5482473A (en) | 1994-05-09 | 1996-01-09 | Minimed Inc. | Flex circuit connector |
US5472317A (en) | 1994-06-03 | 1995-12-05 | Minimed Inc. | Mounting clip for a medication infusion pump |
US5494562A (en) | 1994-06-27 | 1996-02-27 | Ciba Corning Diagnostics Corp. | Electrochemical sensors |
US5809417A (en) | 1994-07-05 | 1998-09-15 | Lucent Technologies Inc. | Cordless telephone arranged for operating with multiple portable units in a frequency hopping system |
US5549568A (en) | 1994-08-22 | 1996-08-27 | Shields; Jack W. | Elastomeric needle shield and hub-cap |
US5798961A (en) | 1994-08-23 | 1998-08-25 | Emc Corporation | Non-volatile memory module |
US5462051A (en) | 1994-08-31 | 1995-10-31 | Colin Corporation | Medical communication system |
US5549115A (en) | 1994-09-28 | 1996-08-27 | Heartstream, Inc. | Method and apparatus for gathering event data using a removable data storage medium and clock |
US5724030A (en) | 1994-10-13 | 1998-03-03 | Bio Medic Data Systems, Inc. | System monitoring reprogrammable implantable transponder |
CA2159052C (en) | 1994-10-28 | 2007-03-06 | Rainer Alex | Injection device |
US5516832A (en) | 1994-11-03 | 1996-05-14 | Dow Corning Corporation | Curable silicone rubber composition |
IE72524B1 (en) | 1994-11-04 | 1997-04-23 | Elan Med Tech | Analyte-controlled liquid delivery device and analyte monitor |
US5632557A (en) | 1994-12-16 | 1997-05-27 | Weed Instrument Company, Inc. | Modular temperature sensing apparatus |
US5562713A (en) | 1995-01-18 | 1996-10-08 | Pacesetter, Inc. | Bidirectional telemetry apparatus and method for implantable device |
DE69600098T2 (en) | 1995-02-04 | 1998-06-10 | Baumann & Haldi Sa | Individual arrangement for measuring, processing and transferring essentially physiological parameters |
US5551427A (en) | 1995-02-13 | 1996-09-03 | Altman; Peter A. | Implantable device for the effective elimination of cardiac arrhythmogenic sites |
JP3297971B2 (en) | 1995-02-16 | 2002-07-02 | オムロン株式会社 | Electronic sphygmomanometer |
US5568806A (en) | 1995-02-16 | 1996-10-29 | Minimed Inc. | Transcutaneous sensor insertion set |
US5586553A (en) | 1995-02-16 | 1996-12-24 | Minimed Inc. | Transcutaneous sensor insertion set |
US5651869A (en) | 1995-02-28 | 1997-07-29 | Matsushita Electric Industrial Co., Ltd. | Biosensor |
US5596150A (en) * | 1995-03-08 | 1997-01-21 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Capacitance probe for fluid flow and volume measurements |
JPH08247987A (en) * | 1995-03-15 | 1996-09-27 | Omron Corp | Portable measuring instrument |
US5582697A (en) | 1995-03-17 | 1996-12-10 | Matsushita Electric Industrial Co., Ltd. | Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same |
US5788833A (en) | 1995-03-27 | 1998-08-04 | California Institute Of Technology | Sensors for detecting analytes in fluids |
US5752512A (en) | 1995-05-10 | 1998-05-19 | Massachusetts Institute Of Technology | Apparatus and method for non-invasive blood analyte measurement |
US5628310A (en) | 1995-05-19 | 1997-05-13 | Joseph R. Lakowicz | Method and apparatus to perform trans-cutaneous analyte monitoring |
US5567302A (en) | 1995-06-07 | 1996-10-22 | Molecular Devices Corporation | Electrochemical system for rapid detection of biochemical agents that catalyze a redox potential change |
US5584813A (en) | 1995-06-07 | 1996-12-17 | Minimed Inc. | Subcutaneous injection set |
US5638832A (en) | 1995-06-07 | 1997-06-17 | Interval Research Corporation | Programmable subcutaneous visible implant |
US5995860A (en) | 1995-07-06 | 1999-11-30 | Thomas Jefferson University | Implantable sensor and system for measurement and control of blood constituent levels |
US5581206A (en) | 1995-07-28 | 1996-12-03 | Micron Quantum Devices, Inc. | Power level detection circuit |
US6001065A (en) | 1995-08-02 | 1999-12-14 | Ibva Technologies, Inc. | Method and apparatus for measuring and analyzing physiological signals for active or passive control of physical and virtual spaces and the contents therein |
US5766131A (en) | 1995-08-04 | 1998-06-16 | Seiko Epson Corporation | Pulse-wave measuring apparatus |
US6152876A (en) * | 1997-04-18 | 2000-11-28 | Rio Grande Medical Technologies, Inc. | Method for non-invasive blood analyte measurement with improved optical interface |
US5749656A (en) | 1995-08-11 | 1998-05-12 | General Motors Corporation | Thermal probe assembly with mold-over crimp sensor packaging |
DE19530376C2 (en) | 1995-08-18 | 1999-09-02 | Fresenius Ag | Biosensor |
US5682233A (en) | 1995-09-08 | 1997-10-28 | Integ, Inc. | Interstitial fluid sampler |
IE77523B1 (en) | 1995-09-11 | 1997-12-17 | Elan Med Tech | Medicament delivery device |
US5735273A (en) * | 1995-09-12 | 1998-04-07 | Cygnus, Inc. | Chemical signal-impermeable mask |
DE19534887B4 (en) | 1995-09-20 | 2004-04-15 | Robert Bosch Gmbh | temperature sensor |
US5628890A (en) | 1995-09-27 | 1997-05-13 | Medisense, Inc. | Electrochemical sensor |
US5665222A (en) | 1995-10-11 | 1997-09-09 | E. Heller & Company | Soybean peroxidase electrochemical sensor |
US5972199A (en) | 1995-10-11 | 1999-10-26 | E. Heller & Company | Electrochemical analyte sensors using thermostable peroxidase |
ES2121525B1 (en) | 1995-10-11 | 1999-09-16 | Krebs & Co Ag Krebs & Co Sa Kr | SALT PRODUCTION SYSTEM BY FORCED EVAPORATION. |
US5741211A (en) | 1995-10-26 | 1998-04-21 | Medtronic, Inc. | System and method for continuous monitoring of diabetes-related blood constituents |
US5748103A (en) | 1995-11-13 | 1998-05-05 | Vitalcom, Inc. | Two-way TDMA telemetry system with power conservation features |
ZA9610374B (en) * | 1995-12-11 | 1997-06-23 | Elan Med Tech | Cartridge-based drug delivery device |
US5827184A (en) | 1995-12-29 | 1998-10-27 | Minnesota Mining And Manufacturing Company | Self-packaging bioelectrodes |
US5746697A (en) | 1996-02-09 | 1998-05-05 | Nellcor Puritan Bennett Incorporated | Medical diagnostic apparatus with sleep mode |
FI118509B (en) | 1996-02-12 | 2007-12-14 | Nokia Oyj | A method and apparatus for predicting blood glucose levels in a patient |
FI960636A (en) | 1996-02-12 | 1997-08-13 | Nokia Mobile Phones Ltd | A procedure for monitoring the health of a patient |
US5708247A (en) * | 1996-02-14 | 1998-01-13 | Selfcare, Inc. | Disposable glucose test strips, and methods and compositions for making same |
US5833603A (en) | 1996-03-13 | 1998-11-10 | Lipomatrix, Inc. | Implantable biosensing transponder |
WO1997037618A1 (en) | 1996-04-08 | 1997-10-16 | Medtronic, Inc. | Method of fixing a physiologic mitral valve bioprosthesis |
FR2748171B1 (en) | 1996-04-30 | 1998-07-17 | Motorola Inc | METHOD FOR GENERATING A CLOCK SIGNAL FOR USE IN A DATA RECEIVER, CLOCK GENERATOR, DATA RECEIVER AND REMOTE CONTROL ACCESS SYSTEM FOR VEHICLES |
DE19618597B4 (en) | 1996-05-09 | 2005-07-21 | Institut für Diabetestechnologie Gemeinnützige Forschungs- und Entwicklungsgesellschaft mbH an der Universität Ulm | Method for determining the concentration of tissue glucose |
US6130602A (en) | 1996-05-13 | 2000-10-10 | Micron Technology, Inc. | Radio frequency data communications device |
US5954685A (en) | 1996-05-24 | 1999-09-21 | Cygnus, Inc. | Electrochemical sensor with dual purpose electrode |
US5735285A (en) | 1996-06-04 | 1998-04-07 | Data Critical Corp. | Method and hand-held apparatus for demodulating and viewing frequency modulated biomedical signals |
US6230051B1 (en) | 1996-06-18 | 2001-05-08 | Alza Corporation | Device for enhancing transdermal agent delivery or sampling |
US5830064A (en) | 1996-06-21 | 1998-11-03 | Pear, Inc. | Apparatus and method for distinguishing events which collectively exceed chance expectations and thereby controlling an output |
JP3581218B2 (en) | 1996-07-03 | 2004-10-27 | 株式会社東芝 | Mobile communication terminal device and its mobile phone and data terminal device |
AU3596597A (en) | 1996-07-08 | 1998-02-02 | Animas Corporation | Implantable sensor and system for in vivo measurement and control of fluid constituent levels |
US5707502A (en) | 1996-07-12 | 1998-01-13 | Chiron Diagnostics Corporation | Sensors for measuring analyte concentrations and methods of making same |
WO1998004902A1 (en) | 1996-07-26 | 1998-02-05 | The State Of Oregon Acting By And Through The State Board Of Higher Education On Behalf Of The University Of Oregon | Sensor for detecting heparin and other analytes |
US5733313A (en) * | 1996-08-01 | 1998-03-31 | Exonix Corporation | RF coupled, implantable medical device with rechargeable back-up power source |
US6544193B2 (en) | 1996-09-04 | 2003-04-08 | Marcio Marc Abreu | Noninvasive measurement of chemical substances |
US5771001A (en) | 1996-11-18 | 1998-06-23 | Cobb; Marlon J. | Personal alarm system |
US6004278A (en) | 1996-12-05 | 1999-12-21 | Mdc Investment Holdings, Inc. | Fluid collection device with retractable needle |
US6071249A (en) | 1996-12-06 | 2000-06-06 | Abbott Laboratories | Method and apparatus for obtaining blood for diagnostic tests |
US5964993A (en) | 1996-12-19 | 1999-10-12 | Implanted Biosystems Inc. | Glucose sensor |
US6130623A (en) | 1996-12-31 | 2000-10-10 | Lucent Technologies Inc. | Encryption for modulated backscatter systems |
US6122351A (en) | 1997-01-21 | 2000-09-19 | Med Graph, Inc. | Method and system aiding medical diagnosis and treatment |
US6093172A (en) | 1997-02-05 | 2000-07-25 | Minimed Inc. | Injector for a subcutaneous insertion set |
US20070142776A9 (en) * | 1997-02-05 | 2007-06-21 | Medtronic Minimed, Inc. | Insertion device for an insertion set and method of using the same |
US7329239B2 (en) | 1997-02-05 | 2008-02-12 | Medtronic Minimed, Inc. | Insertion device for an insertion set and method of using the same |
US6607509B2 (en) | 1997-12-31 | 2003-08-19 | Medtronic Minimed, Inc. | Insertion device for an insertion set and method of using the same |
US5851197A (en) | 1997-02-05 | 1998-12-22 | Minimed Inc. | Injector for a subcutaneous infusion set |
US5749907A (en) | 1997-02-18 | 1998-05-12 | Pacesetter, Inc. | System and method for identifying and displaying medical data which violate programmable alarm conditions |
US8555894B2 (en) * | 1997-02-26 | 2013-10-15 | Alfred E. Mann Foundation For Scientific Research | System for monitoring temperature |
EP1011426A1 (en) | 1997-02-26 | 2000-06-28 | Diasense, Inc. | Individual calibration of blood glucose for supporting noninvasive self-monitoring blood glucose |
US6159147A (en) | 1997-02-28 | 2000-12-12 | Qrs Diagnostics, Llc | Personal computer card for collection of real-time biological data |
US7657297B2 (en) | 2004-05-03 | 2010-02-02 | Dexcom, Inc. | Implantable analyte sensor |
US6558321B1 (en) | 1997-03-04 | 2003-05-06 | Dexcom, Inc. | Systems and methods for remote monitoring and modulation of medical devices |
US6001067A (en) | 1997-03-04 | 1999-12-14 | Shults; Mark C. | Device and method for determining analyte levels |
US7192450B2 (en) | 2003-05-21 | 2007-03-20 | Dexcom, Inc. | Porous membranes for use with implantable devices |
US9155496B2 (en) | 1997-03-04 | 2015-10-13 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US7899511B2 (en) | 2004-07-13 | 2011-03-01 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US6741877B1 (en) | 1997-03-04 | 2004-05-25 | Dexcom, Inc. | Device and method for determining analyte levels |
US20050033132A1 (en) | 1997-03-04 | 2005-02-10 | Shults Mark C. | Analyte measuring device |
US5959529A (en) | 1997-03-07 | 1999-09-28 | Kail, Iv; Karl A. | Reprogrammable remote sensor monitoring system |
US6699187B2 (en) | 1997-03-27 | 2004-03-02 | Medtronic, Inc. | System and method for providing remote expert communications and video capabilities for use during a medical procedure |
US6270455B1 (en) | 1997-03-28 | 2001-08-07 | Health Hero Network, Inc. | Networked system for interactive communications and remote monitoring of drug delivery |
KR100236035B1 (en) | 1997-03-31 | 1999-12-15 | 전주범 | Method of scheduling virtual channels by using subtables in an atm nic |
US6026321A (en) | 1997-04-02 | 2000-02-15 | Suzuki Motor Corporation | Apparatus and system for measuring electrical potential variations in human body |
US5942979A (en) | 1997-04-07 | 1999-08-24 | Luppino; Richard | On guard vehicle safety warning system |
US5961451A (en) | 1997-04-07 | 1999-10-05 | Motorola, Inc. | Noninvasive apparatus having a retaining member to retain a removable biosensor |
US5987353A (en) | 1997-04-10 | 1999-11-16 | Khatchatrian; Robert G. | Diagnostic complex for measurement of the condition of biological tissues and liquids |
US5935224A (en) | 1997-04-24 | 1999-08-10 | Microsoft Corporation | Method and apparatus for adaptively coupling an external peripheral device to either a universal serial bus port on a computer or hub or a game port on a computer |
US6085342A (en) | 1997-05-06 | 2000-07-04 | Telefonaktiebolaget L M Ericsson (Publ) | Electronic system having a chip integrated power-on reset circuit with glitch sensor |
US6186982B1 (en) | 1998-05-05 | 2001-02-13 | Elan Corporation, Plc | Subcutaneous drug delivery device with improved filling system |
US5779665A (en) | 1997-05-08 | 1998-07-14 | Minimed Inc. | Transdermal introducer assembly |
JPH10305016A (en) | 1997-05-08 | 1998-11-17 | Casio Comput Co Ltd | Behavior information providing system |
US7267665B2 (en) | 1999-06-03 | 2007-09-11 | Medtronic Minimed, Inc. | Closed loop system for controlling insulin infusion |
US6558351B1 (en) | 1999-06-03 | 2003-05-06 | Medtronic Minimed, Inc. | Closed loop system for controlling insulin infusion |
US5954643A (en) | 1997-06-09 | 1999-09-21 | Minimid Inc. | Insertion set for a transcutaneous sensor |
CA2294610A1 (en) * | 1997-06-16 | 1998-12-23 | George Moshe Katz | Methods of calibrating and testing a sensor for in vivo measurement of an analyte and devices for use in such methods |
US6056435A (en) | 1997-06-24 | 2000-05-02 | Exergen Corporation | Ambient and perfusion normalized temperature detector |
DE29711371U1 (en) | 1997-06-30 | 1997-11-27 | Siemens Ag | Device for connecting printed circuit boards of separate devices |
US5865804A (en) | 1997-07-16 | 1999-02-02 | Bachynsky; Nicholas | Rotary cam syringe |
US5823802A (en) | 1997-07-30 | 1998-10-20 | General Motors Corporation | Electrical connector with combination seal and contact member |
US6232950B1 (en) | 1997-08-28 | 2001-05-15 | E Ink Corporation | Rear electrode structures for displays |
US6731976B2 (en) | 1997-09-03 | 2004-05-04 | Medtronic, Inc. | Device and method to measure and communicate body parameters |
US6764581B1 (en) | 1997-09-05 | 2004-07-20 | Abbott Laboratories | Electrode with thin working layer |
DE19836401A1 (en) | 1997-09-19 | 2000-02-17 | Salcomp Oy Salo | Device for charging accumulators |
US6117290A (en) | 1997-09-26 | 2000-09-12 | Pepex Biomedical, Llc | System and method for measuring a bioanalyte such as lactate |
US5904671A (en) | 1997-10-03 | 1999-05-18 | Navot; Nir | Tampon wetness detection system |
DE59810949D1 (en) | 1997-10-15 | 2004-04-15 | Nokia Corp | Mobile phone for internet applications |
US6736957B1 (en) | 1997-10-16 | 2004-05-18 | Abbott Laboratories | Biosensor electrode mediators for regeneration of cofactors and process for using |
US6088608A (en) | 1997-10-20 | 2000-07-11 | Alfred E. Mann Foundation | Electrochemical sensor and integrity tests therefor |
US6119028A (en) | 1997-10-20 | 2000-09-12 | Alfred E. Mann Foundation | Implantable enzyme-based monitoring systems having improved longevity due to improved exterior surfaces |
FI107080B (en) | 1997-10-27 | 2001-05-31 | Nokia Mobile Phones Ltd | measuring device |
CA2305366C (en) | 1997-11-12 | 2007-10-16 | Lightouch Medical, Inc. | Method for non-invasive measurement of an analyte |
US6068399A (en) | 1997-11-12 | 2000-05-30 | K-Jump Health Co., Ltd. | Cost-effective electronic thermometer |
KR100258969B1 (en) | 1997-11-20 | 2000-06-15 | 윤종용 | Firmware upgrading method in wireless communication device and firmware upgrade supporting method in cell base station |
US6482176B1 (en) | 1997-11-27 | 2002-11-19 | Disetronic Licensing Ag | Method and device for controlling the introduction depth of an injection needle |
NZ504879A (en) | 1997-12-04 | 2003-05-30 | Roche Diagnostics Corp | Instrument for engaging a power cell |
ES2186247T3 (en) | 1997-12-04 | 2003-05-01 | Roche Diagnostics Corp | METHOD OF CONFIGURING A PORTABLE INSTRUMENT. |
US6036924A (en) | 1997-12-04 | 2000-03-14 | Hewlett-Packard Company | Cassette of lancet cartridges for sampling blood |
US6579690B1 (en) | 1997-12-05 | 2003-06-17 | Therasense, Inc. | Blood analyte monitoring through subcutaneous measurement |
KR100557261B1 (en) | 1997-12-11 | 2006-03-07 | 알자 코포레이션 | Device for enhancing transdermal agent flux |
DK1743667T3 (en) | 1997-12-31 | 2012-06-18 | Medtronic Minimed Inc | Insertion device for an insertion set |
CA2312919C (en) * | 1997-12-31 | 2004-12-14 | Minimed, Inc. | Insertion device for an insertion set and method of using the same |
US6097480A (en) | 1998-01-27 | 2000-08-01 | Kaplan; Milton | Vehicle interlock system |
US6134461A (en) | 1998-03-04 | 2000-10-17 | E. Heller & Company | Electrochemical analyte |
US6056718A (en) | 1998-03-04 | 2000-05-02 | Minimed Inc. | Medication infusion set |
US6103033A (en) | 1998-03-04 | 2000-08-15 | Therasense, Inc. | Process for producing an electrochemical biosensor |
US6024699A (en) | 1998-03-13 | 2000-02-15 | Healthware Corporation | Systems, methods and computer program products for monitoring, diagnosing and treating medical conditions of remotely located patients |
US6197181B1 (en) | 1998-03-20 | 2001-03-06 | Semitool, Inc. | Apparatus and method for electrolytically depositing a metal on a microelectronic workpiece |
US6579231B1 (en) | 1998-03-27 | 2003-06-17 | Mci Communications Corporation | Personal medical monitoring unit and system |
SE9801121D0 (en) | 1998-03-30 | 1998-03-30 | Astra Ab | Electrical device |
JP3104672B2 (en) | 1998-03-31 | 2000-10-30 | 日本電気株式会社 | Current detection type sensor element and method of manufacturing the same |
US6091975A (en) | 1998-04-01 | 2000-07-18 | Alza Corporation | Minimally invasive detecting device |
US6728560B2 (en) | 1998-04-06 | 2004-04-27 | The General Hospital Corporation | Non-invasive tissue glucose level monitoring |
JPH11296598A (en) | 1998-04-07 | 1999-10-29 | Seizaburo Arita | System and method for predicting blood-sugar level and record medium where same method is recorded |
EP1070244A4 (en) | 1998-04-09 | 2002-04-17 | California Inst Of Techn | Electronic techniques for analyte detection |
GB9808408D0 (en) | 1998-04-18 | 1998-06-17 | Owen Mumford Ltd | Improvements relating to injection devices |
US6091987A (en) | 1998-04-29 | 2000-07-18 | Medtronic, Inc. | Power consumption reduction in medical devices by employing different supply voltages |
US6949816B2 (en) | 2003-04-21 | 2005-09-27 | Motorola, Inc. | Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same |
US8974386B2 (en) | 1998-04-30 | 2015-03-10 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
GB2337122B (en) | 1998-05-08 | 2002-11-13 | Medisense Inc | Test strip |
CA2311487C (en) | 1998-05-13 | 2004-02-10 | Cygnus, Inc. | Signal processing for measurement of physiological analytes |
CA2332112C (en) | 1998-05-13 | 2004-02-10 | Cygnus, Inc. | Monitoring of physiological analytes |
US6121611A (en) | 1998-05-20 | 2000-09-19 | Molecular Imaging Corporation | Force sensing probe for scanning probe microscopy |
TW406018B (en) | 1998-05-21 | 2000-09-21 | Elan Corp Plc | Improved adhesive system for medical devices |
GB9812472D0 (en) | 1998-06-11 | 1998-08-05 | Owen Mumford Ltd | A dose setting device for medical injectors |
JP2000031951A (en) | 1998-07-15 | 2000-01-28 | Fujitsu Ltd | Burst synchronization circuit |
US6493069B1 (en) | 1998-07-24 | 2002-12-10 | Terumo Kabushiki Kaisha | Method and instrument for measuring blood sugar level |
US5993423A (en) | 1998-08-18 | 1999-11-30 | Choi; Soo Bong | Portable automatic syringe device and injection needle unit thereof |
US6248067B1 (en) | 1999-02-05 | 2001-06-19 | Minimed Inc. | Analyte sensor and holter-type monitor system and method of using the same |
US6554798B1 (en) | 1998-08-18 | 2003-04-29 | Medtronic Minimed, Inc. | External infusion device with remote programming, bolus estimator and/or vibration alarm capabilities |
US6558320B1 (en) | 2000-01-20 | 2003-05-06 | Medtronic Minimed, Inc. | Handheld personal data assistant (PDA) with a medical device and method of using the same |
US6304766B1 (en) | 1998-08-26 | 2001-10-16 | Sensors For Medicine And Science | Optical-based sensing devices, especially for in-situ sensing in humans |
US7536478B2 (en) | 1998-09-11 | 2009-05-19 | Rpx-Lv Acquisition Llc | Method and apparatus for opening and launching a web browser in response to an audible signal |
KR20000019716A (en) | 1998-09-15 | 2000-04-15 | 박호군 | Composition comprising bioflavonoid compounds for descending blood sugar |
US6740518B1 (en) | 1998-09-17 | 2004-05-25 | Clinical Micro Sensors, Inc. | Signal detection techniques for the detection of analytes |
US6254586B1 (en) | 1998-09-25 | 2001-07-03 | Minimed Inc. | Method and kit for supplying a fluid to a subcutaneous placement site |
US5951521A (en) | 1998-09-25 | 1999-09-14 | Minimed Inc. | Subcutaneous implantable sensor set having the capability to remove deliver fluids to an insertion site |
DK1102559T3 (en) | 1998-09-30 | 2003-09-29 | Cygnus Therapeutic Systems | Method and apparatus for predicting physiological values |
US6402689B1 (en) | 1998-09-30 | 2002-06-11 | Sicel Technologies, Inc. | Methods, systems, and associated implantable devices for dynamic monitoring of physiological and biological properties of tumors |
AU6255699A (en) | 1998-10-08 | 2000-04-26 | Minimed, Inc. | Telemetered characteristic monitor system |
US20060202859A1 (en) | 1998-10-08 | 2006-09-14 | Mastrototaro John J | Telemetered characteristic monitor system and method of using the same |
US6591125B1 (en) | 2000-06-27 | 2003-07-08 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
US5948006A (en) | 1998-10-14 | 1999-09-07 | Advanced Bionics Corporation | Transcutaneous transmission patch |
US6496729B2 (en) | 1998-10-28 | 2002-12-17 | Medtronic, Inc. | Power consumption reduction in medical devices employing multiple supply voltages and clock frequency control |
EP1130996B1 (en) | 1998-11-20 | 2005-04-13 | The University of Connecticut | Generic integrated implantable potentiostat telemetry unit for electrochemical sensors |
KR100627990B1 (en) | 1998-11-30 | 2006-09-26 | 노보 노르디스크 에이/에스 | A method and a system for assisting a user in a medical self treatment, said self treatment comprising a plurality of actions |
US6377894B1 (en) | 1998-11-30 | 2002-04-23 | Abbott Laboratories | Analyte test instrument having improved calibration and communication processes |
US6022368A (en) | 1998-11-30 | 2000-02-08 | Gavronsky; Stas | Acupuncture method and device |
US6540672B1 (en) | 1998-12-09 | 2003-04-01 | Novo Nordisk A/S | Medical system and a method of controlling the system for use by a patient for medical self treatment |
US6773671B1 (en) | 1998-11-30 | 2004-08-10 | Abbott Laboratories | Multichemistry measuring device and test strips |
US6161095A (en) | 1998-12-16 | 2000-12-12 | Health Hero Network, Inc. | Treatment regimen compliance and efficacy with feedback |
US6433728B1 (en) | 1999-01-22 | 2002-08-13 | Lear Automotive Dearborn, Inc. | Integrally molded remote entry transmitter |
CA2365609A1 (en) | 1999-02-12 | 2000-08-17 | Cygnus, Inc. | Devices and methods for frequent measurement of an analyte present in a biological system |
US6314317B1 (en) | 1999-02-18 | 2001-11-06 | Biovalve Technologies, Inc. | Electroactive pore |
US6424847B1 (en) | 1999-02-25 | 2002-07-23 | Medtronic Minimed, Inc. | Glucose monitor calibration methods |
US6360888B1 (en) | 1999-02-25 | 2002-03-26 | Minimed Inc. | Glucose sensor package system |
ATE552771T1 (en) | 1999-02-25 | 2012-04-15 | Medtronic Minimed Inc | TEST PLUG AND CABLE FOR GLUCOSE MONITORING DEVICE |
US6959211B2 (en) | 1999-03-10 | 2005-10-25 | Optiscan Biomedical Corp. | Device for capturing thermal spectra from tissue |
AU4063100A (en) | 1999-04-01 | 2000-10-23 | University Of Connecticut, The | Optical glucose sensor apparatus and method |
GB9907815D0 (en) | 1999-04-06 | 1999-06-02 | Univ Cambridge Tech | Implantable sensor |
US6285897B1 (en) | 1999-04-07 | 2001-09-04 | Endonetics, Inc. | Remote physiological monitoring system |
US6416471B1 (en) | 1999-04-15 | 2002-07-09 | Nexan Limited | Portable remote patient telemonitoring system |
US6494829B1 (en) | 1999-04-15 | 2002-12-17 | Nexan Limited | Physiological sensor array |
US6200265B1 (en) | 1999-04-16 | 2001-03-13 | Medtronic, Inc. | Peripheral memory patch and access method for use with an implantable medical device |
US6192891B1 (en) * | 1999-04-26 | 2001-02-27 | Becton Dickinson And Company | Integrated system including medication delivery pen, blood monitoring device, and lancer |
US6669663B1 (en) | 1999-04-30 | 2003-12-30 | Medtronic, Inc. | Closed loop medicament pump |
FR2793021B1 (en) | 1999-04-30 | 2001-08-03 | Siemens Automotive Sa | TEMPERATURE SENSOR AND METHOD FOR MANUFACTURING SUCH A SENSOR |
US6514689B2 (en) | 1999-05-11 | 2003-02-04 | M-Biotech, Inc. | Hydrogel biosensor |
US6359444B1 (en) | 1999-05-28 | 2002-03-19 | University Of Kentucky Research Foundation | Remote resonant-circuit analyte sensing apparatus with sensing structure and associated method of sensing |
US6312378B1 (en) | 1999-06-03 | 2001-11-06 | Cardiac Intelligence Corporation | System and method for automated collection and analysis of patient information retrieved from an implantable medical device for remote patient care |
US7806886B2 (en) | 1999-06-03 | 2010-10-05 | Medtronic Minimed, Inc. | Apparatus and method for controlling insulin infusion with state variable feedback |
US6298255B1 (en) * | 1999-06-09 | 2001-10-02 | Aspect Medical Systems, Inc. | Smart electrophysiological sensor system with automatic authentication and validation and an interface for a smart electrophysiological sensor system |
US6256533B1 (en) | 1999-06-09 | 2001-07-03 | The Procter & Gamble Company | Apparatus and method for using an intracutaneous microneedle array |
WO2000078992A2 (en) | 1999-06-18 | 2000-12-28 | Therasense, Inc. | Mass transport limited in vivo analyte sensor |
GB2351153B (en) | 1999-06-18 | 2003-03-26 | Abbott Lab | Electrochemical sensor for analysis of liquid samples |
US6423035B1 (en) | 1999-06-18 | 2002-07-23 | Animas Corporation | Infusion pump with a sealed drive mechanism and improved method of occlusion detection |
US7522878B2 (en) | 1999-06-21 | 2009-04-21 | Access Business Group International Llc | Adaptive inductive power supply with communication |
US6368274B1 (en) | 1999-07-01 | 2002-04-09 | Medtronic Minimed, Inc. | Reusable analyte sensor site and method of using the same |
US6804558B2 (en) | 1999-07-07 | 2004-10-12 | Medtronic, Inc. | System and method of communicating between an implantable medical device and a remote computer system or health care provider |
US6413393B1 (en) | 1999-07-07 | 2002-07-02 | Minimed, Inc. | Sensor including UV-absorbing polymer and method of manufacture |
DE19933700A1 (en) | 1999-07-19 | 2001-01-25 | Bsh Bosch Siemens Hausgeraete | dishwasher |
US6514460B1 (en) | 1999-07-28 | 2003-02-04 | Abbott Laboratories | Luminous glucose monitoring device |
US7113821B1 (en) | 1999-08-25 | 2006-09-26 | Johnson & Johnson Consumer Companies, Inc. | Tissue electroperforation for enhanced drug delivery |
US6608562B1 (en) | 1999-08-31 | 2003-08-19 | Denso Corporation | Vital signal detecting apparatus |
US6102896A (en) | 1999-09-08 | 2000-08-15 | Cambridge Biostability Limited | Disposable injector device |
AT408182B (en) | 1999-09-17 | 2001-09-25 | Schaupp Lukas Dipl Ing Dr Tech | DEVICE FOR VIVO MEASURING SIZES IN LIVING ORGANISMS |
EP1217942A1 (en) | 1999-09-24 | 2002-07-03 | Healthetech, Inc. | Physiological monitor and associated computation, display and communication unit |
US6662439B1 (en) | 1999-10-04 | 2003-12-16 | Roche Diagnostics Corporation | Laser defined features for patterned laminates and electrodes |
US7073246B2 (en) | 1999-10-04 | 2006-07-11 | Roche Diagnostics Operations, Inc. | Method of making a biosensor |
US6294997B1 (en) | 1999-10-04 | 2001-09-25 | Intermec Ip Corp. | RFID tag having timing and environment modules |
US7276146B2 (en) | 2001-11-16 | 2007-10-02 | Roche Diagnostics Operations, Inc. | Electrodes, methods, apparatuses comprising micro-electrode arrays |
US6767440B1 (en) | 2001-04-24 | 2004-07-27 | Roche Diagnostics Corporation | Biosensor |
US6645359B1 (en) | 2000-10-06 | 2003-11-11 | Roche Diagnostics Corporation | Biosensor |
US6478736B1 (en) | 1999-10-08 | 2002-11-12 | Healthetech, Inc. | Integrated calorie management system |
DE19948759A1 (en) | 1999-10-09 | 2001-04-12 | Roche Diagnostics Gmbh | Blood lancet device for drawing blood for diagnostic purposes |
US6283982B1 (en) | 1999-10-19 | 2001-09-04 | Facet Technologies, Inc. | Lancing device and method of sample collection |
US6593356B2 (en) | 1999-10-20 | 2003-07-15 | Bristol-Myers Squibb Pharma Company | Acylsemicarbazides as cyclin dependent kinase inhibitors useful as anti-cancer and anti-proliferative agents |
US6616819B1 (en) | 1999-11-04 | 2003-09-09 | Therasense, Inc. | Small volume in vitro analyte sensor and methods |
US20060091006A1 (en) | 1999-11-04 | 2006-05-04 | Yi Wang | Analyte sensor with insertion monitor, and methods |
JP3985022B2 (en) | 1999-11-08 | 2007-10-03 | アークレイ株式会社 | Body fluid measuring device and insertion body used by being inserted into the body fluid measuring device |
DK1230249T3 (en) | 1999-11-15 | 2004-08-30 | Therasense Inc | Transition metal complexes with bidentate ligand having an imidazole ring |
US6291200B1 (en) | 1999-11-17 | 2001-09-18 | Agentase, Llc | Enzyme-containing polymeric sensors |
US6658396B1 (en) | 1999-11-29 | 2003-12-02 | Tang Sharon S | Neural network drug dosage estimation |
US6522927B1 (en) | 1999-12-01 | 2003-02-18 | Vertis Neuroscience, Inc. | Electrode assembly for a percutaneous electrical therapy system |
ATE508687T1 (en) | 1999-12-13 | 2011-05-15 | Arkray Inc | BODY FLUID MEASUREMENT DEVICE WITH LANCET AND LANCET HOLDER USED THEREFOR |
US6418346B1 (en) | 1999-12-14 | 2002-07-09 | Medtronic, Inc. | Apparatus and method for remote therapy and diagnosis in medical devices via interface systems |
US6602191B2 (en) | 1999-12-17 | 2003-08-05 | Q-Tec Systems Llp | Method and apparatus for health and disease management combining patient data monitoring with wireless internet connectivity |
US6497655B1 (en) | 1999-12-17 | 2002-12-24 | Medtronic, Inc. | Virtual remote monitor, alert, diagnostics and programming for implantable medical device systems |
US7060031B2 (en) | 1999-12-17 | 2006-06-13 | Medtronic, Inc. | Method and apparatus for remotely programming implantable medical devices |
US20020091796A1 (en) | 2000-01-03 | 2002-07-11 | John Higginson | Method and apparatus for transmitting data over a network using a docking device |
US7286894B1 (en) | 2000-01-07 | 2007-10-23 | Pasco Scientific | Hand-held computer device and method for interactive data acquisition, analysis, annotation, and calibration |
WO2001052935A1 (en) | 2000-01-21 | 2001-07-26 | Medical Research Group, Inc. | Ambulatory medical apparatus and method having telemetry modifiable control software |
JP4703083B2 (en) | 2000-01-21 | 2011-06-15 | メドトロニック ミニメド インコーポレイテッド | Medical system |
US7369635B2 (en) | 2000-01-21 | 2008-05-06 | Medtronic Minimed, Inc. | Rapid discrimination preambles and methods for using the same |
US6748445B1 (en) | 2000-02-01 | 2004-06-08 | Microsoft Corporation | System and method for exchanging data |
US20010037060A1 (en) | 2000-02-08 | 2001-11-01 | Thompson Richard P. | Web site for glucose monitoring |
CA2395868C (en) | 2000-02-10 | 2009-07-14 | Medtronic Minimed, Inc. | Improved analyte sensor and method of making the same |
US6484045B1 (en) | 2000-02-10 | 2002-11-19 | Medtronic Minimed, Inc. | Analyte sensor and method of making the same |
US7003336B2 (en) | 2000-02-10 | 2006-02-21 | Medtronic Minimed, Inc. | Analyte sensor method of making the same |
US20030060765A1 (en) | 2000-02-16 | 2003-03-27 | Arthur Campbell | Infusion device menu structure and method of using the same |
US6895263B2 (en) | 2000-02-23 | 2005-05-17 | Medtronic Minimed, Inc. | Real time self-adjusting calibration algorithm |
US7027931B1 (en) | 2000-02-24 | 2006-04-11 | Bionostics, Inc. | System for statistical analysis of quality control data |
US6893396B2 (en) | 2000-03-01 | 2005-05-17 | I-Medik, Inc. | Wireless internet bio-telemetry monitoring system and interface |
US6706159B2 (en) | 2000-03-02 | 2004-03-16 | Diabetes Diagnostics | Combined lancet and electrochemical analyte-testing apparatus |
DE10010587A1 (en) | 2000-03-03 | 2001-09-06 | Roche Diagnostics Gmbh | System for the determination of analyte concentrations in body fluids |
US6405066B1 (en) | 2000-03-17 | 2002-06-11 | The Regents Of The University Of California | Implantable analyte sensor |
US6510344B1 (en) | 2000-03-22 | 2003-01-21 | Ge Medical Systems Information Technologies, Inc. | Procedure alarm silence feature for medical telemetry system |
WO2001072208A2 (en) | 2000-03-29 | 2001-10-04 | University Of Virginia Patent Foundation | Method, system, and computer program product for the evaluation of glycemic control in diabetes from self-monitoring data |
US20020063565A1 (en) | 2000-04-04 | 2002-05-30 | Stroth John E. | Arc fault current interrupter testing device |
US6610012B2 (en) | 2000-04-10 | 2003-08-26 | Healthetech, Inc. | System and method for remote pregnancy monitoring |
US6561975B1 (en) | 2000-04-19 | 2003-05-13 | Medtronic, Inc. | Method and apparatus for communicating with medical device systems |
US6440068B1 (en) | 2000-04-28 | 2002-08-27 | International Business Machines Corporation | Measuring user health as measured by multiple diverse health measurement devices utilizing a personal storage device |
US7404815B2 (en) * | 2000-05-01 | 2008-07-29 | Lifescan, Inc. | Tissue ablation by shear force for sampling biological fluids and delivering active agents |
US20020010390A1 (en) | 2000-05-10 | 2002-01-24 | Guice David Lehmann | Method and system for monitoring the health and status of livestock and other animals |
AU2001263022A1 (en) | 2000-05-12 | 2001-11-26 | Therasense, Inc. | Electrodes with multilayer membranes and methods of using and making the electrodes |
US7181261B2 (en) | 2000-05-15 | 2007-02-20 | Silver James H | Implantable, retrievable, thrombus minimizing sensors |
US6442413B1 (en) | 2000-05-15 | 2002-08-27 | James H. Silver | Implantable sensor |
US6459917B1 (en) | 2000-05-22 | 2002-10-01 | Ashok Gowda | Apparatus for access to interstitial fluid, blood, or blood plasma components |
WO2001091902A2 (en) | 2000-05-30 | 2001-12-06 | Massachusetts Institute Of Technology | Methods and devices for sealing microchip reservoir devices |
US6735479B2 (en) | 2000-06-14 | 2004-05-11 | Medtronic, Inc. | Lifestyle management system |
US6604050B2 (en) | 2000-06-16 | 2003-08-05 | Bayer Corporation | System, method and biosensor apparatus for data communications with a personal data assistant |
US6494830B1 (en) | 2000-06-22 | 2002-12-17 | Guidance Interactive Technologies, Inc. | Handheld controller for monitoring/using medical parameters |
US6699188B2 (en) | 2000-06-22 | 2004-03-02 | Guidance Interactive Technologies | Interactive reward devices and methods |
ES2260245T3 (en) | 2000-06-23 | 2006-11-01 | Bodymedia, Inc. | SYSTEM TO CONTROL HEALTH, WELFARE AND EXERCISE. |
US6540675B2 (en) | 2000-06-27 | 2003-04-01 | Rosedale Medical, Inc. | Analyte monitor |
US6400974B1 (en) | 2000-06-29 | 2002-06-04 | Sensors For Medicine And Science, Inc. | Implanted sensor processing system and method for processing implanted sensor output |
US7530964B2 (en) | 2000-06-30 | 2009-05-12 | Elan Pharma International Limited | Needle device and method thereof |
US6589229B1 (en) | 2000-07-31 | 2003-07-08 | Becton, Dickinson And Company | Wearable, self-contained drug infusion device |
US6633772B2 (en) | 2000-08-18 | 2003-10-14 | Cygnus, Inc. | Formulation and manipulation of databases of analyte and associated values |
CA2408338C (en) | 2000-08-18 | 2009-09-08 | Cygnus, Inc. | Methods and devices for prediction of hypoglycemic events |
WO2002015778A1 (en) | 2000-08-18 | 2002-02-28 | Cygnus, Inc. | Analyte monitoring device alarm augmentation system |
EP1311189A4 (en) | 2000-08-21 | 2005-03-09 | Euro Celtique Sa | Near infrared blood glucose monitoring system |
US20020026111A1 (en) | 2000-08-28 | 2002-02-28 | Neil Ackerman | Methods of monitoring glucose levels in a subject and uses thereof |
US6827899B2 (en) | 2000-08-30 | 2004-12-07 | Hypoguard Limited | Test device |
EP1335764B1 (en) | 2000-09-08 | 2007-06-06 | Insulet Corporation | Device and system for patient infusion |
WO2002030264A2 (en) | 2000-10-10 | 2002-04-18 | Microchips, Inc. | Microchip reservoir devices using wireless transmission of power and data |
DE60142178D1 (en) | 2000-10-11 | 2010-07-01 | Mann Alfred E Found Scient Res | IMPROVED ANTENNA FOR AN IMPLANTED MEDICAL MINIATURE DEVICE |
US6712025B2 (en) | 2000-10-13 | 2004-03-30 | Dogwatch, Inc. | Receiver/stimulus unit for an animal control system |
US7198603B2 (en) | 2003-04-14 | 2007-04-03 | Remon Medical Technologies, Inc. | Apparatus and methods using acoustic telemetry for intrabody communications |
US7348183B2 (en) | 2000-10-16 | 2008-03-25 | Board Of Trustees Of The University Of Arkansas | Self-contained microelectrochemical bioassay platforms and methods |
US6603995B1 (en) | 2000-10-19 | 2003-08-05 | Reynolds Medical Limited | Body monitoring apparatus |
EP1330178A1 (en) | 2000-11-01 | 2003-07-30 | 3M Innovative Properties Company | Electrical sensing and/or signal application device |
US6695860B1 (en) | 2000-11-13 | 2004-02-24 | Isense Corp. | Transcutaneous sensor insertion device |
US6574510B2 (en) | 2000-11-30 | 2003-06-03 | Cardiac Pacemakers, Inc. | Telemetry apparatus and method for an implantable medical device |
CA2430590C (en) | 2000-11-30 | 2012-08-14 | Biovalve Technologies, Inc. | Fluid delivery and measurement systems and methods |
US6439446B1 (en) | 2000-12-01 | 2002-08-27 | Stephen J. Perry | Safety lockout for actuator shaft |
WO2002047747A1 (en) | 2000-12-11 | 2002-06-20 | Resmed Ltd. | Methods and apparatus for stroke patient treatment |
US6665558B2 (en) | 2000-12-15 | 2003-12-16 | Cardiac Pacemakers, Inc. | System and method for correlation of patient health information and implant device data |
TW492117B (en) | 2000-12-15 | 2002-06-21 | Acer Labs Inc | Substrate layout method and structure thereof for decreasing crosstalk between adjacent signals |
US20020074162A1 (en) | 2000-12-15 | 2002-06-20 | Bor-Ray Su | Substrate layout method and structure for reducing cross talk of adjacent signals |
US7052483B2 (en) | 2000-12-19 | 2006-05-30 | Animas Corporation | Transcutaneous inserter for low-profile infusion sets |
GB0030929D0 (en) | 2000-12-19 | 2001-01-31 | Inverness Medical Ltd | Analyte measurement |
US6416332B1 (en) | 2000-12-20 | 2002-07-09 | Nortel Networks Limited | Direct BGA socket for high speed use |
EP1353594B1 (en) | 2000-12-29 | 2008-10-29 | Ares Medical, Inc. | Sleep apnea risk evaluation |
US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
US20020151770A1 (en) | 2001-01-04 | 2002-10-17 | Noll Austin F. | Implantable medical device with sensor |
US6970529B2 (en) | 2001-01-16 | 2005-11-29 | International Business Machines Corporation | Unified digital architecture |
US6603770B2 (en) | 2001-01-16 | 2003-08-05 | Physical Optics Corporation | Apparatus and method for accessing a network |
US20040197846A1 (en) | 2001-01-18 | 2004-10-07 | Linda Hockersmith | Determination of glucose sensitivity and a method to manipulate blood glucose concentration |
TW536689B (en) | 2001-01-18 | 2003-06-11 | Sharp Kk | Display, portable device, and substrate |
CN100593390C (en) | 2001-01-19 | 2010-03-10 | 松下电器产业株式会社 | Lancet-integrated sensor |
ITMI20010253A1 (en) | 2001-02-08 | 2002-08-08 | Negri Bossi Spa | INJECTION GROUP FOR INJECTION PRESSES OF PLASTIC MATERIALS |
US6611206B2 (en) | 2001-03-15 | 2003-08-26 | Koninklijke Philips Electronics N.V. | Automatic system for monitoring independent person requiring occasional assistance |
US6968294B2 (en) | 2001-03-15 | 2005-11-22 | Koninklijke Philips Electronics N.V. | Automatic system for monitoring person requiring care and his/her caretaker |
US7041468B2 (en) | 2001-04-02 | 2006-05-09 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
DK3210637T3 (en) | 2001-04-06 | 2021-04-06 | Hoffmann La Roche | Infusion set |
US7916013B2 (en) | 2005-03-21 | 2011-03-29 | Greatbatch Ltd. | RFID detection and identification system for implantable medical devices |
SE0101379D0 (en) | 2001-04-18 | 2001-04-18 | Diabact Ab | Composition that inhibits gastric acid secretion |
US6698269B2 (en) | 2001-04-27 | 2004-03-02 | Oceana Sensor Technologies, Inc. | Transducer in-situ testing apparatus and method |
US6535764B2 (en) | 2001-05-01 | 2003-03-18 | Intrapace, Inc. | Gastric treatment and diagnosis device and method |
JP2004532526A (en) | 2001-05-03 | 2004-10-21 | マシモ・コーポレイション | Flex circuit shield optical sensor and method of manufacturing the flex circuit shield optical sensor |
US20020164836A1 (en) | 2001-05-07 | 2002-11-07 | Advanced Semiconductor Engineering Inc. | Method of manufacturing printed circuit board |
US6613379B2 (en) | 2001-05-08 | 2003-09-02 | Isense Corp. | Implantable analyte sensor |
US7395214B2 (en) | 2001-05-11 | 2008-07-01 | Craig P Shillingburg | Apparatus, device and method for prescribing, administering and monitoring a treatment regimen for a patient |
US6932894B2 (en) | 2001-05-15 | 2005-08-23 | Therasense, Inc. | Biosensor membranes composed of polymers containing heterocyclic nitrogens |
US6549796B2 (en) | 2001-05-25 | 2003-04-15 | Lifescan, Inc. | Monitoring analyte concentration using minimally invasive devices |
ATE400904T1 (en) | 2001-06-01 | 2008-07-15 | Polyfuel Inc | INTERCHANGEABLE FUEL CARTRIDGE, FUEL CELL UNIT WITH SAID FUEL CARTRIDGE FOR PORTABLE ELECTRONIC DEVICES AND CORRESPONDING DEVICE |
US6837988B2 (en) * | 2001-06-12 | 2005-01-04 | Lifescan, Inc. | Biological fluid sampling and analyte measurement devices and methods |
US7025774B2 (en) | 2001-06-12 | 2006-04-11 | Pelikan Technologies, Inc. | Tissue penetration device |
US7179226B2 (en) | 2001-06-21 | 2007-02-20 | Animas Corporation | System and method for managing diabetes |
US20030002682A1 (en) | 2001-07-02 | 2003-01-02 | Phonex Broadband Corporation | Wireless audio/mechanical vibration transducer and audio/visual transducer |
US8016847B2 (en) | 2001-07-11 | 2011-09-13 | Arkray, Inc. | Lancet and lancing apparatus |
US20030208113A1 (en) | 2001-07-18 | 2003-11-06 | Mault James R | Closed loop glycemic index system |
US20030032874A1 (en) | 2001-07-27 | 2003-02-13 | Dexcom, Inc. | Sensor head for use with implantable devices |
US6570386B2 (en) | 2001-07-30 | 2003-05-27 | Hewlett-Packard Development Company, L.P. | System and method for providing power to electrical devices |
US6544212B2 (en) | 2001-07-31 | 2003-04-08 | Roche Diagnostics Corporation | Diabetes management system |
US6788965B2 (en) | 2001-08-03 | 2004-09-07 | Sensys Medical, Inc. | Intelligent system for detecting errors and determining failure modes in noninvasive measurement of blood and tissue analytes |
US6827718B2 (en) | 2001-08-14 | 2004-12-07 | Scimed Life Systems, Inc. | Method of and apparatus for positioning and maintaining the position of endoscopic instruments |
CN1311781C (en) | 2001-08-20 | 2007-04-25 | 因弗内斯医疗有限公司 | Wireless diabetes management devices and methods for using the same |
US7736272B2 (en) | 2001-08-21 | 2010-06-15 | Pantometrics, Ltd. | Exercise system with graphical feedback and method of gauging fitness progress |
US6781522B2 (en) | 2001-08-22 | 2004-08-24 | Kivalo, Inc. | Portable storage case for housing a medical monitoring device and an associated method for communicating therewith |
JP3962250B2 (en) | 2001-08-29 | 2007-08-22 | 株式会社レアメタル | In vivo information detection system and tag device and relay device used therefor |
US6827702B2 (en) | 2001-09-07 | 2004-12-07 | Medtronic Minimed, Inc. | Safety limits for closed-loop infusion pump control |
US6740072B2 (en) | 2001-09-07 | 2004-05-25 | Medtronic Minimed, Inc. | System and method for providing closed loop infusion formulation delivery |
US7025760B2 (en) | 2001-09-07 | 2006-04-11 | Medtronic Minimed, Inc. | Method and system for non-vascular sensor implantation |
CN1555244A (en) | 2001-09-13 | 2004-12-15 | Method for transmitting vital health statistics to a remote location form an aircraft | |
JP2003084101A (en) | 2001-09-17 | 2003-03-19 | Dainippon Printing Co Ltd | Resin composition for optical device, optical device and projection screen |
US7052591B2 (en) | 2001-09-21 | 2006-05-30 | Therasense, Inc. | Electrodeposition of redox polymers and co-electrodeposition of enzymes by coordinative crosslinking |
US6830562B2 (en) | 2001-09-27 | 2004-12-14 | Unomedical A/S | Injector device for placing a subcutaneous infusion set |
US20050137480A1 (en) | 2001-10-01 | 2005-06-23 | Eckhard Alt | Remote control of implantable device through medical implant communication service band |
US6613015B2 (en) | 2001-10-04 | 2003-09-02 | Deltec, Inc. | Right angle safety needle |
US20030069510A1 (en) | 2001-10-04 | 2003-04-10 | Semler Herbert J. | Disposable vital signs monitor |
US6748254B2 (en) | 2001-10-12 | 2004-06-08 | Nellcor Puritan Bennett Incorporated | Stacked adhesive optical sensor |
AU2002346399A1 (en) | 2001-11-14 | 2003-05-26 | Medical Instill Technologies, Inc. | Intradermal delivery device and method |
US20030116447A1 (en) | 2001-11-16 | 2003-06-26 | Surridge Nigel A. | Electrodes, methods, apparatuses comprising micro-electrode arrays |
ATE479089T1 (en) | 2001-11-16 | 2010-09-15 | Stefan Ufer | FLEXIBLE SENSOR AND MANUFACTURING METHOD |
EP1461745A4 (en) | 2001-11-28 | 2006-10-18 | Phemi Inc | Methods and apparatus for automated interactive medical management |
US6993393B2 (en) | 2001-12-19 | 2006-01-31 | Cardiac Pacemakers, Inc. | Telemetry duty cycle management system for an implantable medical device |
US7204823B2 (en) | 2001-12-19 | 2007-04-17 | Medtronic Minimed, Inc. | Medication delivery system and monitor |
US20030119457A1 (en) | 2001-12-19 | 2003-06-26 | Standke Randolph E. | Filter technique for increasing antenna isolation in portable communication devices |
US7082334B2 (en) | 2001-12-19 | 2006-07-25 | Medtronic, Inc. | System and method for transmission of medical and like data from a patient to a dedicated internet website |
US7729776B2 (en) | 2001-12-19 | 2010-06-01 | Cardiac Pacemakers, Inc. | Implantable medical device with two or more telemetry systems |
GB0130684D0 (en) | 2001-12-21 | 2002-02-06 | Oxford Biosensors Ltd | Micro-band electrode |
US20050027182A1 (en) | 2001-12-27 | 2005-02-03 | Uzair Siddiqui | System for monitoring physiological characteristics |
US7022072B2 (en) | 2001-12-27 | 2006-04-04 | Medtronic Minimed, Inc. | System for monitoring physiological characteristics |
US7399277B2 (en) | 2001-12-27 | 2008-07-15 | Medtronic Minimed, Inc. | System for monitoring physiological characteristics |
US20080255438A1 (en) | 2001-12-27 | 2008-10-16 | Medtronic Minimed, Inc. | System for monitoring physiological characteristics |
ITTO20011228A1 (en) | 2001-12-28 | 2003-06-28 | Cane Srl | DISPOSABLE NEEDLE CONTAINER. |
US20030145062A1 (en) | 2002-01-14 | 2003-07-31 | Dipanshu Sharma | Data conversion server for voice browsing system |
US20030155656A1 (en) | 2002-01-18 | 2003-08-21 | Chiu Cindy Chia-Wen | Anisotropically conductive film |
US7184820B2 (en) | 2002-01-25 | 2007-02-27 | Subqiview, Inc. | Tissue monitoring system for intravascular infusion |
US20030144711A1 (en) | 2002-01-29 | 2003-07-31 | Neuropace, Inc. | Systems and methods for interacting with an implantable medical device |
US6985773B2 (en) | 2002-02-07 | 2006-01-10 | Cardiac Pacemakers, Inc. | Methods and apparatuses for implantable medical device telemetry power management |
US7004928B2 (en) | 2002-02-08 | 2006-02-28 | Rosedale Medical, Inc. | Autonomous, ambulatory analyte monitor or drug delivery device |
US8364229B2 (en) | 2003-07-25 | 2013-01-29 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US8260393B2 (en) | 2003-07-25 | 2012-09-04 | Dexcom, Inc. | Systems and methods for replacing signal data artifacts in a glucose sensor data stream |
US9282925B2 (en) | 2002-02-12 | 2016-03-15 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US9247901B2 (en) | 2003-08-22 | 2016-02-02 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US7613491B2 (en) | 2002-05-22 | 2009-11-03 | Dexcom, Inc. | Silicone based membranes for use in implantable glucose sensors |
US8010174B2 (en) | 2003-08-22 | 2011-08-30 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
DE10208575C1 (en) | 2002-02-21 | 2003-08-14 | Hartmann Paul Ag | Blood analyzer device comprises needles, test media, analyzer and display, and has carrier turned with respect to main body, to position needle and test media |
US20030212379A1 (en) | 2002-02-26 | 2003-11-13 | Bylund Adam David | Systems and methods for remotely controlling medication infusion and analyte monitoring |
AU2003213638A1 (en) | 2002-02-26 | 2003-09-09 | Sterling Medivations, Inc. | Insertion device for an insertion set and method of using the same |
US7043305B2 (en) | 2002-03-06 | 2006-05-09 | Cardiac Pacemakers, Inc. | Method and apparatus for establishing context among events and optimizing implanted medical device performance |
DE10392369B4 (en) | 2002-03-06 | 2011-12-15 | HTL-STREFA Spólka z o. o. | Device for puncturing the skin of a patient |
US7468032B2 (en) | 2002-12-18 | 2008-12-23 | Cardiac Pacemakers, Inc. | Advanced patient management for identifying, displaying and assisting with correlating health-related data |
EP1343112A1 (en) | 2002-03-08 | 2003-09-10 | EndoArt S.A. | Implantable device |
US6998247B2 (en) | 2002-03-08 | 2006-02-14 | Sensys Medical, Inc. | Method and apparatus using alternative site glucose determinations to calibrate and maintain noninvasive and implantable analyzers |
US6936006B2 (en) | 2002-03-22 | 2005-08-30 | Novo Nordisk, A/S | Atraumatic insertion of a subcutaneous device |
US20040030531A1 (en) | 2002-03-28 | 2004-02-12 | Honeywell International Inc. | System and method for automated monitoring, recognizing, supporting, and responding to the behavior of an actor |
GB2388898B (en) | 2002-04-02 | 2005-10-05 | Inverness Medical Ltd | Integrated sample testing meter |
US7226461B2 (en) | 2002-04-19 | 2007-06-05 | Pelikan Technologies, Inc. | Method and apparatus for a multi-use body fluid sampling device with sterility barrier release |
US7485128B2 (en) | 2002-04-19 | 2009-02-03 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US9314194B2 (en) | 2002-04-19 | 2016-04-19 | Sanofi-Aventis Deutschland Gmbh | Tissue penetration device |
US7410468B2 (en) | 2002-04-19 | 2008-08-12 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7141058B2 (en) | 2002-04-19 | 2006-11-28 | Pelikan Technologies, Inc. | Method and apparatus for a body fluid sampling device using illumination |
US20050177398A1 (en) | 2002-04-25 | 2005-08-11 | Motokazu Watanabe | Dosage determination supporting device, injector, and health management supporting system |
US6810309B2 (en) | 2002-04-25 | 2004-10-26 | Visteon Global Technologies, Inc. | Vehicle personalization via biometric identification |
GB2388716B (en) | 2002-05-13 | 2004-10-20 | Splashpower Ltd | Improvements relating to contact-less power transfer |
US7134994B2 (en) | 2002-05-20 | 2006-11-14 | Volcano Corporation | Multipurpose host system for invasive cardiovascular diagnostic measurement acquisition and display |
US7226978B2 (en) | 2002-05-22 | 2007-06-05 | Dexcom, Inc. | Techniques to improve polyurethane membranes for implantable glucose sensors |
US8641715B2 (en) | 2002-05-31 | 2014-02-04 | Vidacare Corporation | Manual intraosseous device |
US20040030581A1 (en) | 2002-06-12 | 2004-02-12 | Samuel Leven | Heart monitoring device |
JP4308483B2 (en) | 2002-07-02 | 2009-08-05 | アークレイ株式会社 | Puncture unit and puncture device |
WO2004004565A1 (en) | 2002-07-02 | 2004-01-15 | Arkray, Inc. | Unit for piercing, and piercing device |
US7124027B1 (en) | 2002-07-11 | 2006-10-17 | Yazaki North America, Inc. | Vehicular collision avoidance system |
JP2004054394A (en) | 2002-07-17 | 2004-02-19 | Toshiba Corp | Radio information processing system, radio information recording medium, radio information processor and communication method for radio information processing system |
AU2003302720B9 (en) | 2002-07-19 | 2008-08-21 | Smiths Detection-Pasadena, Inc. | Non-specific sensor array detectors |
US7470533B2 (en) | 2002-12-20 | 2008-12-30 | Acea Biosciences | Impedance based devices and methods for use in assays |
US7058719B2 (en) | 2002-07-22 | 2006-06-06 | Ricoh Company, Ltd. | System, computer program product and method for managing and controlling a local network of electronic devices and reliably and securely adding an electronic device to the network |
US7220387B2 (en) | 2002-07-23 | 2007-05-22 | Apieron Biosystems Corp. | Disposable sensor for use in measuring an analyte in a gaseous sample |
US7278983B2 (en) | 2002-07-24 | 2007-10-09 | Medtronic Minimed, Inc. | Physiological monitoring device for controlling a medication infusion device |
ES2456068T3 (en) | 2002-08-13 | 2014-04-21 | University Of Virginia Patent Foundation | Method, system and software product for glycemia self-monitoring (SMBG) data processing to improve diabetic self-management |
US7020508B2 (en) | 2002-08-22 | 2006-03-28 | Bodymedia, Inc. | Apparatus for detecting human physiological and contextual information |
US7404796B2 (en) | 2004-03-01 | 2008-07-29 | Becton Dickinson And Company | System for determining insulin dose using carbohydrate to insulin ratio and insulin sensitivity factor |
US7637891B2 (en) | 2002-09-12 | 2009-12-29 | Children's Hospital Medical Center | Method and device for painless injection of medication |
US7736309B2 (en) | 2002-09-27 | 2010-06-15 | Medtronic Minimed, Inc. | Implantable sensor method and system |
US20040061232A1 (en) | 2002-09-27 | 2004-04-01 | Medtronic Minimed, Inc. | Multilayer substrate |
US7192405B2 (en) | 2002-09-30 | 2007-03-20 | Becton, Dickinson And Company | Integrated lancet and bodily fluid sensor |
TW557352B (en) | 2002-10-07 | 2003-10-11 | Actherm Inc | Electronic clinical thermometer with rapid response |
US7014625B2 (en) | 2002-10-07 | 2006-03-21 | Novo Nordick A/S | Needle insertion device |
US20040138688A1 (en) | 2002-10-09 | 2004-07-15 | Jean Pierre Giraud | Lancet system including test strips and cassettes for drawing and sampling bodily material |
DK1575656T3 (en) | 2002-10-11 | 2009-09-14 | Becton Dickinson Co | Insulin delivery system with sensor |
US7381184B2 (en) | 2002-11-05 | 2008-06-03 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
US7572237B2 (en) | 2002-11-06 | 2009-08-11 | Abbott Diabetes Care Inc. | Automatic biological analyte testing meter with integrated lancing device and methods of use |
US6676290B1 (en) * | 2002-11-15 | 2004-01-13 | Hsueh-Yu Lu | Electronic clinical thermometer |
GB0226648D0 (en) | 2002-11-15 | 2002-12-24 | Koninkl Philips Electronics Nv | Usage data harvesting |
JP2006507196A (en) | 2002-11-21 | 2006-03-02 | エス.シー. ジョンソン アンド サン、インコーポレイテッド | Products with RFID tags for providing information to product consumers |
US20040100376A1 (en) | 2002-11-26 | 2004-05-27 | Kimberly-Clark Worldwide, Inc. | Healthcare monitoring system |
US7580395B2 (en) | 2002-11-29 | 2009-08-25 | Intermec Ip Corp. | Information gathering apparatus and method having multiple wireless communication options |
EP1618920A3 (en) | 2002-12-16 | 2007-05-30 | Meagan Medical, Inc. | Controlling the depth of percuataneous applications |
US20040116866A1 (en) | 2002-12-17 | 2004-06-17 | William Gorman | Skin attachment apparatus and method for patient infusion device |
US7009511B2 (en) | 2002-12-17 | 2006-03-07 | Cardiac Pacemakers, Inc. | Repeater device for communications with an implantable medical device |
US20040122353A1 (en) | 2002-12-19 | 2004-06-24 | Medtronic Minimed, Inc. | Relay device for transferring information between a sensor system and a fluid delivery system |
US7395117B2 (en) | 2002-12-23 | 2008-07-01 | Cardiac Pacemakers, Inc. | Implantable medical device having long-term wireless capabilities |
JP2004214014A (en) | 2002-12-27 | 2004-07-29 | Shin Etsu Polymer Co Ltd | Electric connector |
US20040127818A1 (en) | 2002-12-27 | 2004-07-01 | Roe Steven N. | Precision depth control lancing tip |
EP1578262A4 (en) | 2002-12-31 | 2007-12-05 | Therasense Inc | Continuous glucose monitoring system and methods of use |
US7154398B2 (en) | 2003-01-06 | 2006-12-26 | Chen Thomas C H | Wireless communication and global location enabled intelligent health monitoring system |
US7228162B2 (en) | 2003-01-13 | 2007-06-05 | Isense Corporation | Analyte sensor |
US20040138544A1 (en) | 2003-01-13 | 2004-07-15 | Ward W. Kenneth | Body fluid trap anlyte sensor |
US7927558B2 (en) | 2003-02-18 | 2011-04-19 | Microteq, Llc | System and apparatus for detecting breach of exposure protection equipment |
GB0304424D0 (en) | 2003-02-26 | 2003-04-02 | Glaxosmithkline Biolog Sa | Novel compounds |
US20040171910A1 (en) | 2003-02-27 | 2004-09-02 | Moore-Steele Robin B. | Sexually stimulating panty insert |
EP2052684A1 (en) | 2003-03-17 | 2009-04-29 | Arkray Inc. | Puncture device |
US20040186373A1 (en) | 2003-03-21 | 2004-09-23 | Dunfield John Stephen | Method and device for targeted epithelial delivery of medicinal and related agents |
US20050070819A1 (en) | 2003-03-31 | 2005-03-31 | Rosedale Medical, Inc. | Body fluid sampling constructions and techniques |
US7447298B2 (en) | 2003-04-01 | 2008-11-04 | Cabot Microelectronics Corporation | Decontamination and sterilization system using large area x-ray source |
US20040199056A1 (en) | 2003-04-03 | 2004-10-07 | International Business Machines Corporation | Body monitoring using local area wireless interfaces |
US7587287B2 (en) | 2003-04-04 | 2009-09-08 | Abbott Diabetes Care Inc. | Method and system for transferring analyte test data |
US20040204868A1 (en) | 2003-04-09 | 2004-10-14 | Maynard John D. | Reduction of errors in non-invasive tissue sampling |
EP1614382B1 (en) | 2003-04-11 | 2012-07-11 | ARKRAY, Inc. | Needle insertion device |
SG182002A1 (en) * | 2003-04-15 | 2012-07-30 | Sensors For Med & Science Inc | System and method for attenuating the effect of ambient light on an optical sensor |
US6797877B1 (en) | 2003-04-28 | 2004-09-28 | Jonn Maneely Company | Electrical metallic tube, coupling, and connector apparatus and method |
ATE474611T1 (en) * | 2003-05-08 | 2010-08-15 | Novo Nordisk As | AN INJECTION DEVICE THAT CAN BE APPLIED TO THE SKIN WITH A SEPARABLE ACTUATING PART FOR INSERTING THE NEEDLE |
AU2003902187A0 (en) | 2003-05-08 | 2003-05-22 | Aimedics Pty Ltd | Patient monitor |
US20040225199A1 (en) | 2003-05-08 | 2004-11-11 | Evanyk Shane Walter | Advanced physiological monitoring systems and methods |
ATE392223T1 (en) * | 2003-05-08 | 2008-05-15 | Novo Nordisk As | INTERNAL NEEDLE INTRODUCER |
US6926694B2 (en) | 2003-05-09 | 2005-08-09 | Medsolve Technologies, Llc | Apparatus and method for delivery of therapeutic and/or diagnostic agents |
US7875293B2 (en) | 2003-05-21 | 2011-01-25 | Dexcom, Inc. | Biointerface membranes incorporating bioactive agents |
WO2004103170A1 (en) | 2003-05-22 | 2004-12-02 | Novo Nordisk A/S | A glucose measuring device |
US7397785B2 (en) | 2003-05-28 | 2008-07-08 | Nokia Corporation | Method for enhancing fairness and performance in a multihop ad hoc network and corresponding system |
KR100502713B1 (en) * | 2003-05-29 | 2005-07-20 | 주식회사 헬스피아 | Battery pack and system for self-diagnosis |
US8460243B2 (en) | 2003-06-10 | 2013-06-11 | Abbott Diabetes Care Inc. | Glucose measuring module and insulin pump combination |
EP1636579A4 (en) | 2003-06-10 | 2011-10-05 | Smiths Detection Inc | Sensor arrangement |
US20040254433A1 (en) | 2003-06-12 | 2004-12-16 | Bandis Steven D. | Sensor introducer system, apparatus and method |
US7604592B2 (en) | 2003-06-13 | 2009-10-20 | Pelikan Technologies, Inc. | Method and apparatus for a point of care device |
US7364699B2 (en) * | 2003-06-18 | 2008-04-29 | Bayer Healthcare Llc | Containers for reading and handling diagnostic reagents and methods of using the same |
US7155290B2 (en) | 2003-06-23 | 2006-12-26 | Cardiac Pacemakers, Inc. | Secure long-range telemetry for implantable medical device |
JP4041018B2 (en) | 2003-06-25 | 2008-01-30 | Tdk株式会社 | Temperature sensor |
US7510564B2 (en) | 2003-06-27 | 2009-03-31 | Abbott Diabetes Care Inc. | Lancing device |
US7722536B2 (en) | 2003-07-15 | 2010-05-25 | Abbott Diabetes Care Inc. | Glucose measuring device integrated into a holster for a personal area network device |
US7108778B2 (en) | 2003-07-25 | 2006-09-19 | Dexcom, Inc. | Electrochemical sensors including electrode systems with increased oxygen generation |
US7424318B2 (en) | 2003-12-05 | 2008-09-09 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US20050176136A1 (en) | 2003-11-19 | 2005-08-11 | Dexcom, Inc. | Afinity domain for analyte sensor |
US7366556B2 (en) | 2003-12-05 | 2008-04-29 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
WO2005012873A2 (en) | 2003-07-25 | 2005-02-10 | Dexcom, Inc. | Electrode systems for electrochemical sensors |
US7761130B2 (en) | 2003-07-25 | 2010-07-20 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
EP1648298A4 (en) | 2003-07-25 | 2010-01-13 | Dexcom Inc | Oxygen enhancing membrane systems for implantable devices |
US7460898B2 (en) | 2003-12-05 | 2008-12-02 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8423113B2 (en) | 2003-07-25 | 2013-04-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
US7467003B2 (en) | 2003-12-05 | 2008-12-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US9135402B2 (en) | 2007-12-17 | 2015-09-15 | Dexcom, Inc. | Systems and methods for processing sensor data |
US20100168543A1 (en) | 2003-08-01 | 2010-07-01 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US8369919B2 (en) | 2003-08-01 | 2013-02-05 | Dexcom, Inc. | Systems and methods for processing sensor data |
US7774145B2 (en) | 2003-08-01 | 2010-08-10 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8626257B2 (en) | 2003-08-01 | 2014-01-07 | Dexcom, Inc. | Analyte sensor |
US8845536B2 (en) | 2003-08-01 | 2014-09-30 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8886273B2 (en) | 2003-08-01 | 2014-11-11 | Dexcom, Inc. | Analyte sensor |
US7986986B2 (en) | 2003-08-01 | 2011-07-26 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
EP1502613A1 (en) | 2003-08-01 | 2005-02-02 | Novo Nordisk A/S | Needle device with retraction means |
US8275437B2 (en) | 2003-08-01 | 2012-09-25 | Dexcom, Inc. | Transcutaneous analyte sensor |
DE10336933B4 (en) | 2003-08-07 | 2007-04-26 | Roche Diagnostics Gmbh | Blood Collection system |
US20050038331A1 (en) | 2003-08-14 | 2005-02-17 | Grayson Silaski | Insertable sensor assembly having a coupled inductor communicative system |
US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
US7097637B2 (en) | 2003-08-27 | 2006-08-29 | C. R. Bard, Inc. | Safety needle with positive flush |
US9133024B2 (en) | 2003-09-03 | 2015-09-15 | Brigitte Chau Phan | Personal diagnostic devices including related methods and systems |
CA2896407A1 (en) | 2003-09-11 | 2005-03-24 | Theranos, Inc. | Medical device for analyte monitoring and drug delivery |
JP4356088B2 (en) | 2003-09-26 | 2009-11-04 | 日本光電工業株式会社 | Telemeter system for multi-channel biological signals |
EP1681992B2 (en) | 2003-09-30 | 2015-03-04 | Roche Diagnostics GmbH | Sensor with increased biocompatibility |
US7203549B2 (en) | 2003-10-02 | 2007-04-10 | Medtronic, Inc. | Medical device programmer with internal antenna and display |
US8140168B2 (en) | 2003-10-02 | 2012-03-20 | Medtronic, Inc. | External power source for an implantable medical device having an adjustable carrier frequency and system and method related therefore |
US7148803B2 (en) | 2003-10-24 | 2006-12-12 | Symbol Technologies, Inc. | Radio frequency identification (RFID) based sensor networks |
US20050090725A1 (en) | 2003-10-28 | 2005-04-28 | Joseph Page | Disposable couplings for biometric instruments |
US20050090607A1 (en) | 2003-10-28 | 2005-04-28 | Dexcom, Inc. | Silicone composition for biocompatible membrane |
US6928380B2 (en) | 2003-10-30 | 2005-08-09 | International Business Machines Corporation | Thermal measurements of electronic devices during operation |
US7299082B2 (en) | 2003-10-31 | 2007-11-20 | Abbott Diabetes Care, Inc. | Method of calibrating an analyte-measurement device, and associated methods, devices and systems |
US7419573B2 (en) | 2003-11-06 | 2008-09-02 | 3M Innovative Properties Company | Circuit for electrochemical sensor strip |
EP1680175B1 (en) | 2003-11-06 | 2019-06-05 | LifeScan, Inc. | Drug delivery pen with event notification means |
US7731691B2 (en) | 2003-11-10 | 2010-06-08 | Smiths Medical Asd, Inc. | Subcutaneous infusion device and device for insertion of a cannula of an infusion device and method |
US7699807B2 (en) | 2003-11-10 | 2010-04-20 | Smiths Medical Asd, Inc. | Device and method for insertion of a cannula of an infusion device |
WO2005046477A2 (en) | 2003-11-12 | 2005-05-26 | Facet Technologies, Llc | Lancing device and multi-lancet cartridge |
DE602004028649D1 (en) | 2003-11-13 | 2010-09-23 | Medtronic Minimed Inc | LONG-TERM ARRANGEMENT ANALYTENSENSOR |
EP1713379A4 (en) | 2003-11-18 | 2009-09-02 | Alive Technologies Pty Ltd | The monitoring of vital signs and performance levels |
CA2536188A1 (en) | 2003-11-20 | 2005-06-09 | Angiotech International Ag | Electrical devices and anti-scarring agents |
US20050113886A1 (en) | 2003-11-24 | 2005-05-26 | Fischell David R. | Implantable medical system with long range telemetry |
FR2863175A1 (en) | 2003-12-03 | 2005-06-10 | Ela Medical Sa | ACTIVE IMPLANTABLE MEDICAL DEVICE WITH HOLTER RECORDING FUNCTIONS |
US8364230B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
EP2239567B1 (en) | 2003-12-05 | 2015-09-02 | DexCom, Inc. | Calibration techniques for a continuous analyte sensor |
US8774886B2 (en) | 2006-10-04 | 2014-07-08 | Dexcom, Inc. | Analyte sensor |
US8425417B2 (en) | 2003-12-05 | 2013-04-23 | Dexcom, Inc. | Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device |
US8423114B2 (en) | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8287453B2 (en) | 2003-12-05 | 2012-10-16 | Dexcom, Inc. | Analyte sensor |
US20100185071A1 (en) | 2003-12-05 | 2010-07-22 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8425416B2 (en) | 2006-10-04 | 2013-04-23 | Dexcom, Inc. | Analyte sensor |
US20080200788A1 (en) | 2006-10-04 | 2008-08-21 | Dexcorn, Inc. | Analyte sensor |
US20080197024A1 (en) | 2003-12-05 | 2008-08-21 | Dexcom, Inc. | Analyte sensor |
EP3241490A1 (en) | 2003-12-08 | 2017-11-08 | DexCom, Inc. | Systems and methods for improving electrochemical analyte sensors |
US7763042B2 (en) | 2003-12-16 | 2010-07-27 | Panasonic Corporation | Lancet for blood collection and puncture needle unit |
WO2005058154A1 (en) | 2003-12-16 | 2005-06-30 | Medeikon Corporation | Method for monitoring of analytes in biological samples using low coherence interferometry |
US7384397B2 (en) | 2003-12-30 | 2008-06-10 | Medtronic Minimed, Inc. | System and method for sensor recalibration |
US7822454B1 (en) | 2005-01-03 | 2010-10-26 | Pelikan Technologies, Inc. | Fluid sampling device with improved analyte detecting member configuration |
GB2409951A (en) | 2004-01-08 | 2005-07-13 | Remote Diagnostic Technologies | Wireless local area network of medical sensors |
US7637868B2 (en) | 2004-01-12 | 2009-12-29 | Dexcom, Inc. | Composite material for implantable device |
JP4250169B2 (en) | 2004-01-16 | 2009-04-08 | 株式会社トップ | Indwelling needle |
US8136735B2 (en) | 2004-01-23 | 2012-03-20 | Semiconductor Energy Laboratory Co., Ltd. | ID label, ID card, and ID tag |
HUE037253T2 (en) | 2004-01-27 | 2018-08-28 | Altivera L L C | Diagnostic radio frequency identification sensors and applications thereof |
JP4526827B2 (en) | 2004-02-03 | 2010-08-18 | オムロンヘルスケア株式会社 | Electronic blood pressure monitor |
US8465696B2 (en) | 2004-02-03 | 2013-06-18 | Polymer Technology Systems, Inc. | Dry test strip with controlled flow and method of manufacturing same |
US8165651B2 (en) | 2004-02-09 | 2012-04-24 | Abbott Diabetes Care Inc. | Analyte sensor, and associated system and method employing a catalytic agent |
US7699964B2 (en) | 2004-02-09 | 2010-04-20 | Abbott Diabetes Care Inc. | Membrane suitable for use in an analyte sensor, analyte sensor, and associated method |
US7364592B2 (en) | 2004-02-12 | 2008-04-29 | Dexcom, Inc. | Biointerface membrane with macro-and micro-architecture |
WO2005089103A2 (en) | 2004-02-17 | 2005-09-29 | Therasense, Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US20060154642A1 (en) | 2004-02-20 | 2006-07-13 | Scannell Robert F Jr | Medication & health, environmental, and security monitoring, alert, intervention, information and network system with associated and supporting apparatuses |
CN1921803B (en) | 2004-02-23 | 2011-01-26 | 伊西康公司 | Diagnostic swab and biopsy punch systems, and diagnostic caps for use in such systems |
JP3590053B1 (en) | 2004-02-24 | 2004-11-17 | 株式会社日立製作所 | Blood glucose measurement device |
US8808228B2 (en) | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
WO2005084257A2 (en) | 2004-02-26 | 2005-09-15 | Vpn Solutions, Llc | Composite thin-film glucose sensor |
WO2005084557A1 (en) | 2004-03-02 | 2005-09-15 | Facet Technologies, Llc | Compact multi-use lancing device |
DE102004011135A1 (en) | 2004-03-08 | 2005-09-29 | Disetronic Licensing Ag | Method and apparatus for calculating a bolus amount |
US7228182B2 (en) | 2004-03-15 | 2007-06-05 | Cardiac Pacemakers, Inc. | Cryptographic authentication for telemetry with an implantable medical device |
US7831828B2 (en) | 2004-03-15 | 2010-11-09 | Cardiac Pacemakers, Inc. | System and method for securely authenticating a data exchange session with an implantable medical device |
GB0405798D0 (en) | 2004-03-15 | 2004-04-21 | E San Ltd | Medical data display |
EP1734858B1 (en) | 2004-03-22 | 2014-07-09 | BodyMedia, Inc. | Non-invasive temperature monitoring device |
EP1735729A2 (en) | 2004-03-26 | 2006-12-27 | Novo Nordisk A/S | Device for displaying data relevant for a diabetic patient |
US20050221504A1 (en) | 2004-04-01 | 2005-10-06 | Petruno Patrick T | Optoelectronic rapid diagnostic test system |
US6971274B2 (en) | 2004-04-02 | 2005-12-06 | Sierra Instruments, Inc. | Immersible thermal mass flow meter |
US20050222518A1 (en) | 2004-04-06 | 2005-10-06 | Genocell, Llc | Biopsy and injection catheters |
US8792955B2 (en) | 2004-05-03 | 2014-07-29 | Dexcom, Inc. | Transcutaneous analyte sensor |
US9101302B2 (en) | 2004-05-03 | 2015-08-11 | Abbott Diabetes Care Inc. | Analyte test device |
US20050245799A1 (en) | 2004-05-03 | 2005-11-03 | Dexcom, Inc. | Implantable analyte sensor |
EP1744679A2 (en) | 2004-05-03 | 2007-01-24 | AMS Research Corporation | Surgical implants and related methods |
US9380975B2 (en) | 2004-05-07 | 2016-07-05 | Becton, Dickinson And Company | Contact activated lancet device |
US7333013B2 (en) | 2004-05-07 | 2008-02-19 | Berger J Lee | Medical implant device with RFID tag and method of identification of device |
US7727147B1 (en) | 2004-05-14 | 2010-06-01 | Flint Hills Scientific Llc | Method and system for implantable glucose monitoring and control of a glycemic state of a subject |
US7125382B2 (en) | 2004-05-20 | 2006-10-24 | Digital Angel Corporation | Embedded bio-sensor system |
JP2008501037A (en) | 2004-06-01 | 2008-01-17 | マイクロチップス・インコーポレーテッド | Devices and methods for measuring and enhancing transport of drugs or analytes to / from medical implants |
US7118667B2 (en) | 2004-06-02 | 2006-10-10 | Jin Po Lee | Biosensors having improved sample application and uses thereof |
WO2006022993A2 (en) | 2004-06-10 | 2006-03-02 | Ndi Medical, Llc | Implantable generator for muscle and nerve stimulation |
US20070100222A1 (en) | 2004-06-14 | 2007-05-03 | Metronic Minimed, Inc. | Analyte sensing apparatus for hospital use |
US7299081B2 (en) | 2004-06-15 | 2007-11-20 | Abbott Laboratories | Analyte test device |
US7585287B2 (en) | 2004-06-16 | 2009-09-08 | Smiths Medical Md, Inc. | Device and method for insertion of a cannula of an infusion device |
US7519430B2 (en) | 2004-06-17 | 2009-04-14 | Cardiac Pacemakers, Inc. | Dynamic telemetry encoding for an implantable medical device |
US7457669B2 (en) | 2004-06-17 | 2008-11-25 | Cardiac Pacemakers, Inc. | On-demand retransmission of data with an implantable medical device |
SI1765288T1 (en) | 2004-06-18 | 2013-02-28 | Novartis Ag | Tobramycin formualtions for treatment of endobronchial infections |
US7565197B2 (en) | 2004-06-18 | 2009-07-21 | Medtronic, Inc. | Conditional requirements for remote medical device programming |
US7556723B2 (en) | 2004-06-18 | 2009-07-07 | Roche Diagnostics Operations, Inc. | Electrode design for biosensor |
DE102004031092A1 (en) | 2004-06-28 | 2006-01-12 | Giesecke & Devrient Gmbh | transponder unit |
US8343074B2 (en) * | 2004-06-30 | 2013-01-01 | Lifescan Scotland Limited | Fluid handling devices |
US20060001551A1 (en) | 2004-06-30 | 2006-01-05 | Ulrich Kraft | Analyte monitoring system with wireless alarm |
AU2005258784A1 (en) | 2004-07-01 | 2006-01-12 | Powerid Ltd. | Battery-assisted backscatter RFID transponder |
US20080242961A1 (en) | 2004-07-13 | 2008-10-02 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8565848B2 (en) | 2004-07-13 | 2013-10-22 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8452368B2 (en) | 2004-07-13 | 2013-05-28 | Dexcom, Inc. | Transcutaneous analyte sensor |
EP3524142B1 (en) | 2004-07-13 | 2021-04-28 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060270922A1 (en) | 2004-07-13 | 2006-11-30 | Brauker James H | Analyte sensor |
JP2006028398A (en) | 2004-07-20 | 2006-02-02 | Nichias Corp | Sheet gasket and method for producing the same |
US7344500B2 (en) | 2004-07-27 | 2008-03-18 | Medtronic Minimed, Inc. | Sensing system with auxiliary display |
US8313433B2 (en) | 2004-08-06 | 2012-11-20 | Medtronic Minimed, Inc. | Medical data management system and process |
EP1781164A1 (en) | 2004-08-10 | 2007-05-09 | Novo Nordisk A/S | A method of forming a sterilised sensor package and a sterilised sensor package |
JP5032321B2 (en) | 2004-08-31 | 2012-09-26 | ライフスキャン・スコットランド・リミテッド | Manufacturing method of automatic calibration sensor |
WO2006029090A2 (en) | 2004-09-02 | 2006-03-16 | Proteus Biomedical, Inc. | Methods and apparatus for tissue activation and monitoring |
EP1788930A1 (en) | 2004-09-03 | 2007-05-30 | Novo Nordisk A/S | A method of calibrating a system for measuring the concentration of substances in body and an apparatus for exercising the method |
US7468033B2 (en) | 2004-09-08 | 2008-12-23 | Medtronic Minimed, Inc. | Blood contacting sensor |
US8211038B2 (en) | 2004-09-17 | 2012-07-03 | Abbott Diabetes Care Inc. | Multiple-biosensor article |
CN101027674A (en) | 2004-09-23 | 2007-08-29 | 诺和诺德公司 | Device for self-care support |
DE102004048864A1 (en) | 2004-10-07 | 2006-04-13 | Roche Diagnostics Gmbh | Analytical test element with wireless data transmission |
US20090048499A1 (en) | 2004-10-18 | 2009-02-19 | Novo Nordisk A/S | Sensor film for transcutaneous insertion and a method for making the sensor film |
ATE490724T1 (en) | 2004-11-02 | 2010-12-15 | Medtronic Inc | DEVICE FOR DATA RETENTION IN AN IMPLANTABLE MEDICAL DEVICE |
US7408132B2 (en) | 2004-11-08 | 2008-08-05 | Rrc Power Solutions Gmbh | Temperature sensor for power supply |
US20090108992A1 (en) | 2004-11-19 | 2009-04-30 | Senomatic Electronics Corporation | Technique And Hardware For Communicating With Backscatter Radio Frequency Identification Readers |
US7237712B2 (en) | 2004-12-01 | 2007-07-03 | Alfred E. Mann Foundation For Scientific Research | Implantable device and communication integrated circuit implementable therein |
DE102004059491B4 (en) | 2004-12-10 | 2008-11-06 | Roche Diagnostics Gmbh | Lancet device for creating a puncture wound and lancet drive assembly |
ATE545361T1 (en) | 2004-12-13 | 2012-03-15 | Koninkl Philips Electronics Nv | MOBILE MONITORING |
US7461192B2 (en) | 2004-12-15 | 2008-12-02 | Rambus Inc. | Interface for bridging out-of-band information and preventing false presence detection of terminating devices |
US7568619B2 (en) | 2004-12-15 | 2009-08-04 | Alcon, Inc. | System and method for identifying and controlling ophthalmic surgical devices and components |
US20110060196A1 (en) | 2009-08-31 | 2011-03-10 | Abbott Diabetes Care Inc. | Flexible Mounting Unit and Cover for a Medical Device |
US20090082693A1 (en) | 2004-12-29 | 2009-03-26 | Therasense, Inc. | Method and apparatus for providing temperature sensor module in a data communication system |
US20090105569A1 (en) | 2006-04-28 | 2009-04-23 | Abbott Diabetes Care, Inc. | Introducer Assembly and Methods of Use |
US20110190603A1 (en) | 2009-09-29 | 2011-08-04 | Stafford Gary A | Sensor Inserter Having Introducer |
US7883464B2 (en) | 2005-09-30 | 2011-02-08 | Abbott Diabetes Care Inc. | Integrated transmitter unit and sensor introducer mechanism and methods of use |
ES2570993T3 (en) | 2004-12-29 | 2016-05-23 | Lifescan Scotland Ltd | Data entry method in an analyte analysis device |
US9259175B2 (en) | 2006-10-23 | 2016-02-16 | Abbott Diabetes Care, Inc. | Flexible patch for fluid delivery and monitoring body analytes |
US9572534B2 (en) | 2010-06-29 | 2017-02-21 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
US9636450B2 (en) | 2007-02-19 | 2017-05-02 | Udo Hoss | Pump system modular components for delivering medication and analyte sensing at seperate insertion sites |
US8029441B2 (en) | 2006-02-28 | 2011-10-04 | Abbott Diabetes Care Inc. | Analyte sensor transmitter unit configuration for a data monitoring and management system |
US7731657B2 (en) | 2005-08-30 | 2010-06-08 | Abbott Diabetes Care Inc. | Analyte sensor introducer and methods of use |
US7697967B2 (en) | 2005-12-28 | 2010-04-13 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
US9788771B2 (en) | 2006-10-23 | 2017-10-17 | Abbott Diabetes Care Inc. | Variable speed sensor insertion devices and methods of use |
US8512243B2 (en) | 2005-09-30 | 2013-08-20 | Abbott Diabetes Care Inc. | Integrated introducer and transmitter assembly and methods of use |
US8571624B2 (en) | 2004-12-29 | 2013-10-29 | Abbott Diabetes Care Inc. | Method and apparatus for mounting a data transmission device in a communication system |
US8333714B2 (en) | 2006-09-10 | 2012-12-18 | Abbott Diabetes Care Inc. | Method and system for providing an integrated analyte sensor insertion device and data processing unit |
US20070027381A1 (en) | 2005-07-29 | 2007-02-01 | Therasense, Inc. | Inserter and methods of use |
US7470237B2 (en) | 2005-01-10 | 2008-12-30 | Ethicon Endo-Surgery, Inc. | Biopsy instrument with improved needle penetration |
US20060166629A1 (en) | 2005-01-24 | 2006-07-27 | Therasense, Inc. | Method and apparatus for providing EMC Class-B compliant RF transmitter for data monitoring an detection systems |
EP1848476A1 (en) | 2005-01-24 | 2007-10-31 | Novo Nordisk A/S | Transcutaneous device assembly |
US20060173260A1 (en) | 2005-01-31 | 2006-08-03 | Gmms Ltd | System, device and method for diabetes treatment and monitoring |
US7547281B2 (en) | 2005-02-01 | 2009-06-16 | Medtronic Minimed, Inc. | Algorithm sensor augmented bolus estimator for semi-closed loop infusion system |
US7545272B2 (en) | 2005-02-08 | 2009-06-09 | Therasense, Inc. | RF tag on test strips, test strip vials and boxes |
KR100638727B1 (en) | 2005-02-28 | 2006-10-30 | 삼성전기주식회사 | Concurrent transceiver for zigbee and bluetooth |
EP1698279A1 (en) | 2005-03-04 | 2006-09-06 | Disetronic Licensing AG | Sequential insertion of main-penetrators |
CN101163440B (en) * | 2005-03-09 | 2010-06-16 | 库蒂森斯股份公司 | A three-dimensional adhesive device having a microelectronic system embedded therein |
EP1871218B1 (en) | 2005-03-09 | 2012-05-16 | Coloplast A/S | A three-dimensional adhesive device having a microelectronic system embedded therein |
US8133178B2 (en) | 2006-02-22 | 2012-03-13 | Dexcom, Inc. | Analyte sensor |
US20090076360A1 (en) | 2007-09-13 | 2009-03-19 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060202805A1 (en) | 2005-03-14 | 2006-09-14 | Alfred E. Mann Foundation For Scientific Research | Wireless acquisition and monitoring system |
US20070071681A1 (en) | 2005-03-15 | 2007-03-29 | Entelos, Inc. | Apparatus and method for computer modeling type 1 diabetes |
EP1863559A4 (en) | 2005-03-21 | 2008-07-30 | Abbott Diabetes Care Inc | Method and system for providing integrated medication infusion and analyte monitoring system |
JP2006280464A (en) | 2005-03-31 | 2006-10-19 | Semiconductor Energy Lab Co Ltd | Biological information detecting apparatus, health care apparatus, health care assisting system using them, and health care assisting method |
US7889069B2 (en) | 2005-04-01 | 2011-02-15 | Codman & Shurtleff, Inc. | Wireless patient monitoring system |
BRPI0610446B1 (en) | 2005-04-07 | 2023-05-16 | Becton, Dickinson And Company | LANCET DEVICE |
JP4718882B2 (en) | 2005-04-08 | 2011-07-06 | 株式会社日立製作所 | Sensor node |
EP1877116A1 (en) | 2005-04-13 | 2008-01-16 | Novo Nordisk A/S | Medical skin mountable device and system |
US8060174B2 (en) | 2005-04-15 | 2011-11-15 | Dexcom, Inc. | Analyte sensing biointerface |
US7270633B1 (en) | 2005-04-22 | 2007-09-18 | Cardiac Pacemakers, Inc. | Ambulatory repeater for use in automated patient care and method thereof |
DE102005019306B4 (en) | 2005-04-26 | 2011-09-01 | Disetronic Licensing Ag | Energy-optimized data transmission of a medical device |
GB2425601B (en) | 2005-04-26 | 2008-01-30 | Bio Nano Sensium Technologies | Sensor configuration |
US8112240B2 (en) | 2005-04-29 | 2012-02-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing leak detection in data monitoring and management systems |
US8700157B2 (en) | 2005-04-29 | 2014-04-15 | Medtronic, Inc. | Telemetry head programmer for implantable medical device and system and method |
US7467065B2 (en) | 2005-05-02 | 2008-12-16 | Home Diagnostics, Inc. | Computer interface for diagnostic meter |
US20060253085A1 (en) | 2005-05-06 | 2006-11-09 | Medtronic Minimed, Inc. | Dual insertion set |
US7905868B2 (en) | 2006-08-23 | 2011-03-15 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with drive device for driving plunger in reservoir |
US7955305B2 (en) | 2005-05-06 | 2011-06-07 | Medtronic Minimed, Inc. | Needle inserter and method for infusion device |
US7604178B2 (en) | 2005-05-11 | 2009-10-20 | Intelleflex Corporation | Smart tag activation |
JP5037496B2 (en) | 2005-05-13 | 2012-09-26 | トラスティーズ オブ ボストン ユニバーシティ | Fully automatic control system for type 1 diabetes |
US7541935B2 (en) | 2005-05-19 | 2009-06-02 | Proacticare Llc | System and methods for monitoring caregiver performance |
US20070033074A1 (en) | 2005-06-03 | 2007-02-08 | Medtronic Minimed, Inc. | Therapy management system |
US20060272652A1 (en) | 2005-06-03 | 2006-12-07 | Medtronic Minimed, Inc. | Virtual patient software system for educating and treating individuals with diabetes |
US20080071580A1 (en) | 2005-06-03 | 2008-03-20 | Marcus Alan O | System and method for medical evaluation and monitoring |
US7387607B2 (en) | 2005-06-06 | 2008-06-17 | Intel Corporation | Wireless medical sensor system |
JP4240007B2 (en) | 2005-06-06 | 2009-03-18 | ニプロ株式会社 | Telemedicine system |
US20060276771A1 (en) | 2005-06-06 | 2006-12-07 | Galley Paul J | System and method providing for user intervention in a diabetes control arrangement |
WO2006133305A2 (en) | 2005-06-08 | 2006-12-14 | Sensors For Medicine And Science, Inc. | Insertion device and method |
DK2260759T3 (en) | 2005-06-17 | 2015-08-17 | Hoffmann La Roche | Feel and conditioning device and method for monitoring a connection, in particular glucose, in body tissue |
US20070016449A1 (en) | 2005-06-29 | 2007-01-18 | Gary Cohen | Flexible glucose analysis using varying time report deltas and configurable glucose target ranges |
WO2007007459A1 (en) | 2005-07-12 | 2007-01-18 | Omron Healthcare Co., Ltd. | Biochemical measuring instrument for measuring information about component of living body accurately |
CN101860089B (en) | 2005-07-12 | 2013-02-06 | 麻省理工学院 | Wireless non-radiative energy transfer |
TWI417543B (en) | 2005-08-05 | 2013-12-01 | Bayer Healthcare Llc | Meters and method of using meters having a multi-level user interface with predefined levels of user features |
WO2007022485A2 (en) | 2005-08-19 | 2007-02-22 | Becton, Dickinson And Company | Sterilization of biosensors |
EP1758039A1 (en) | 2005-08-27 | 2007-02-28 | Roche Diagnostics GmbH | Communication adaptor for portable medical or therapeutical devices |
US20070060801A1 (en) | 2005-08-31 | 2007-03-15 | Isense Corporation | Transcutaneous introducer assembly |
JP2009506852A (en) | 2005-09-09 | 2009-02-19 | エフ.ホフマン−ラ ロシュ アーゲー | System, tool, apparatus and program for diabetes treatment |
US8298389B2 (en) | 2005-09-12 | 2012-10-30 | Abbott Diabetes Care Inc. | In vitro analyte sensor, and methods |
ATE500860T1 (en) | 2005-09-15 | 2011-03-15 | Hoffmann La Roche | SYSTEM COMPRISING INSERTION HEAD AND INSERTER |
DE502005009907D1 (en) | 2005-09-15 | 2010-08-26 | Roche Diagnostics Gmbh | Insertion head with handle |
US7725148B2 (en) | 2005-09-23 | 2010-05-25 | Medtronic Minimed, Inc. | Sensor with layered electrodes |
US7846311B2 (en) | 2005-09-27 | 2010-12-07 | Abbott Diabetes Care Inc. | In vitro analyte sensor and methods of use |
US7761165B1 (en) | 2005-09-29 | 2010-07-20 | Boston Scientific Neuromodulation Corporation | Implantable stimulator with integrated plastic housing/metal contacts and manufacture and use |
US9521968B2 (en) | 2005-09-30 | 2016-12-20 | Abbott Diabetes Care Inc. | Analyte sensor retention mechanism and methods of use |
US8880138B2 (en) | 2005-09-30 | 2014-11-04 | Abbott Diabetes Care Inc. | Device for channeling fluid and methods of use |
US7756561B2 (en) * | 2005-09-30 | 2010-07-13 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
US7550053B2 (en) | 2006-01-26 | 2009-06-23 | Ilh, Llc | Catheters with lubricious linings and methods for making and using them |
IL178557A0 (en) | 2005-10-19 | 2007-02-11 | Animas Corp | Safety infusion set |
US7701052B2 (en) | 2005-10-21 | 2010-04-20 | E. I. Du Pont De Nemours And Company | Power core devices |
WO2007050037A1 (en) | 2005-10-25 | 2007-05-03 | Cadi Scientific Pte Ltd | A system for measuring and tracking at least one physiological parameter and a measuring device for doing the same |
US7486977B2 (en) * | 2005-10-27 | 2009-02-03 | Smiths Medical Pm, Inc. | Single use pulse oximeter |
US20070095661A1 (en) | 2005-10-31 | 2007-05-03 | Yi Wang | Method of making, and, analyte sensor |
US7766829B2 (en) | 2005-11-04 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing basal profile modification in analyte monitoring and management systems |
US8182444B2 (en) | 2005-11-04 | 2012-05-22 | Medrad, Inc. | Delivery of agents such as cells to tissue |
WO2007056504A1 (en) | 2005-11-08 | 2007-05-18 | M2 Medical A/S | Infusion pump system |
WO2007056592A2 (en) | 2005-11-08 | 2007-05-18 | M2 Medical A/S | Method and system for manual and autonomous control of an infusion pump |
US20070173706A1 (en) | 2005-11-11 | 2007-07-26 | Isense Corporation | Method and apparatus for insertion of a sensor |
US7918975B2 (en) | 2005-11-17 | 2011-04-05 | Abbott Diabetes Care Inc. | Analytical sensors for biological fluid |
WO2007062173A1 (en) | 2005-11-22 | 2007-05-31 | Vocollect Healthcare Systems, Inc. | Advanced diabetes management system (adms) |
US7922971B2 (en) | 2005-11-30 | 2011-04-12 | Abbott Diabetes Care Inc. | Integrated meter for analyzing biological samples |
US8815175B2 (en) | 2005-11-30 | 2014-08-26 | Abbott Diabetes Care Inc. | Integrated meter for analyzing biological samples |
US20100036281A1 (en) | 2005-12-01 | 2010-02-11 | Arkray, Inc. | Integrated Sensor and Lancet Device and Method for Collecting Body Fluid Using the Same |
US7963917B2 (en) | 2005-12-05 | 2011-06-21 | Echo Therapeutics, Inc. | System and method for continuous non-invasive glucose monitoring |
US7941200B2 (en) | 2005-12-08 | 2011-05-10 | Roche Diagnostics Operations, Inc. | System and method for determining drug administration information |
US8947233B2 (en) * | 2005-12-09 | 2015-02-03 | Tego Inc. | Methods and systems of a multiple radio frequency network node RFID tag |
US7643798B2 (en) | 2005-12-09 | 2010-01-05 | Sony Ericsson Mobile Communications Ab | Passive NFC activation of short distance wireless communication |
JP5044115B2 (en) | 2005-12-09 | 2012-10-10 | 佳彦 平尾 | Measuring system, information terminal and program |
EP1968432A4 (en) | 2005-12-28 | 2009-10-21 | Abbott Diabetes Care Inc | Medical device insertion |
US8515518B2 (en) | 2005-12-28 | 2013-08-20 | Abbott Diabetes Care Inc. | Analyte monitoring |
EP2004796B1 (en) | 2006-01-18 | 2015-04-08 | DexCom, Inc. | Membranes for an analyte sensor |
US20070179349A1 (en) | 2006-01-19 | 2007-08-02 | Hoyme Kenneth P | System and method for providing goal-oriented patient management based upon comparative population data analysis |
US7574266B2 (en) | 2006-01-19 | 2009-08-11 | Medtronic, Inc. | System and method for telemetry with an implantable medical device |
US8195267B2 (en) | 2006-01-26 | 2012-06-05 | Seymour John P | Microelectrode with laterally extending platform for reduction of tissue encapsulation |
US7736310B2 (en) | 2006-01-30 | 2010-06-15 | Abbott Diabetes Care Inc. | On-body medical device securement |
US7872574B2 (en) | 2006-02-01 | 2011-01-18 | Innovation Specialists, Llc | Sensory enhancement systems and methods in personal electronic devices |
WO2007097754A1 (en) | 2006-02-22 | 2007-08-30 | Dexcom, Inc. | Analyte sensor |
US7811430B2 (en) | 2006-02-28 | 2010-10-12 | Abbott Diabetes Care Inc. | Biosensors and methods of making |
US7885698B2 (en) | 2006-02-28 | 2011-02-08 | Abbott Diabetes Care Inc. | Method and system for providing continuous calibration of implantable analyte sensors |
US7826879B2 (en) | 2006-02-28 | 2010-11-02 | Abbott Diabetes Care Inc. | Analyte sensors and methods of use |
US7576657B2 (en) * | 2006-03-22 | 2009-08-18 | Symbol Technologies, Inc. | Single frequency low power RFID device |
US7887682B2 (en) | 2006-03-29 | 2011-02-15 | Abbott Diabetes Care Inc. | Analyte sensors and methods of use |
US7620438B2 (en) | 2006-03-31 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for powering an electronic device |
US8473022B2 (en) | 2008-01-31 | 2013-06-25 | Abbott Diabetes Care Inc. | Analyte sensor with time lag compensation |
US7801582B2 (en) | 2006-03-31 | 2010-09-21 | Abbott Diabetes Care Inc. | Analyte monitoring and management system and methods therefor |
US9392969B2 (en) | 2008-08-31 | 2016-07-19 | Abbott Diabetes Care Inc. | Closed loop control and signal attenuation detection |
US20070233013A1 (en) | 2006-03-31 | 2007-10-04 | Schoenberg Stephen J | Covers for tissue engaging members |
US7618369B2 (en) | 2006-10-02 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for dynamically updating calibration parameters for an analyte sensor |
US8140312B2 (en) | 2007-05-14 | 2012-03-20 | Abbott Diabetes Care Inc. | Method and system for determining analyte levels |
US7559899B2 (en) | 2006-04-12 | 2009-07-14 | Salutron, Inc. | Power saving techniques for continuous heart rate monitoring |
JP4964946B2 (en) | 2006-04-20 | 2012-07-04 | ライフスキャン・スコットランド・リミテッド | Data transmission method in blood glucose system and corresponding blood glucose system |
US7359837B2 (en) | 2006-04-27 | 2008-04-15 | Medtronic, Inc. | Peak data retention of signal data in an implantable medical device |
US20070253021A1 (en) | 2006-04-28 | 2007-11-01 | Medtronic Minimed, Inc. | Identification of devices in a medical device network and wireless data communication techniques utilizing device identifiers |
US20070255126A1 (en) | 2006-04-28 | 2007-11-01 | Moberg Sheldon B | Data communication in networked fluid infusion systems |
US7942844B2 (en) | 2006-04-28 | 2011-05-17 | Medtronic Minimed, Inc. | Remote monitoring for networked fluid infusion systems |
US20070258395A1 (en) | 2006-04-28 | 2007-11-08 | Medtronic Minimed, Inc. | Wireless data communication protocols for a medical device network |
EP2014105B1 (en) | 2006-05-02 | 2013-06-26 | 3M Innovative Properties Company | A telecommunication enclosure monitoring system |
GB0608829D0 (en) | 2006-05-04 | 2006-06-14 | Husheer Shamus L G | In-situ measurement of physical parameters |
DE102006023213B3 (en) | 2006-05-17 | 2007-09-27 | Siemens Ag | Sensor operating method, involves detecting recording and evaluation device during order and non-order functions of monitoring device in check mode, and watching occurrence of results in mode by sensor, which automatically leaves mode |
EP1857129B8 (en) * | 2006-05-19 | 2009-09-02 | Roche Diagnostics GmbH | Adapter device for sticking a medical instrument to the skin surface |
US20090054749A1 (en) | 2006-05-31 | 2009-02-26 | Abbott Diabetes Care, Inc. | Method and System for Providing Data Transmission in a Data Management System |
EP2023818A2 (en) | 2006-06-07 | 2009-02-18 | Unomedical A/S | Inserter for transcutaneous sensor |
US20080071158A1 (en) | 2006-06-07 | 2008-03-20 | Abbott Diabetes Care, Inc. | Analyte monitoring system and method |
US7796038B2 (en) | 2006-06-12 | 2010-09-14 | Intelleflex Corporation | RFID sensor tag with manual modes and functions |
US7909842B2 (en) * | 2006-06-15 | 2011-03-22 | Abbott Diabetes Care Inc. | Lancing devices having depth adjustment assembly |
US20080177149A1 (en) | 2006-06-16 | 2008-07-24 | Stefan Weinert | System and method for collecting patient information from which diabetes therapy may be determined |
US20090105560A1 (en) | 2006-06-28 | 2009-04-23 | David Solomon | Lifestyle and eating advisor based on physiological and biological rhythm monitoring |
EP2032020A2 (en) | 2006-06-28 | 2009-03-11 | Endo-Rhythm Ltd. | Lifestyle and eating advisor based on physiological and biological rhythm monitoring |
US20080011971A1 (en) | 2006-07-11 | 2008-01-17 | Jiffy-Tite Co., Inc. | Quick opening drain plug assembly |
US8114023B2 (en) * | 2006-07-28 | 2012-02-14 | Legacy Emanuel Hospital & Health Center | Analyte sensing and response system |
MX2009000876A (en) * | 2006-08-02 | 2009-02-04 | Unomedical As | Insertion device. |
GB0616331D0 (en) | 2006-08-16 | 2006-09-27 | Innovision Res & Tech Plc | Near Field RF Communicators And Near Field Communications Enabled Devices |
US20090256572A1 (en) | 2008-04-14 | 2009-10-15 | Mcdowell Andrew F | Tuning Low-Inductance Coils at Low Frequencies |
US7789857B2 (en) | 2006-08-23 | 2010-09-07 | Medtronic Minimed, Inc. | Infusion medium delivery system, device and method with needle inserter and needle inserter device and method |
WO2008022476A1 (en) | 2006-08-24 | 2008-02-28 | F. Hoffmann-La Roche Ag | Insertion device for insertion heads, in particular for infusion sets |
US8758238B2 (en) | 2006-08-31 | 2014-06-24 | Health Hero Network, Inc. | Health related location awareness |
US7769456B2 (en) | 2006-09-01 | 2010-08-03 | Cardiac Pacemakers, Inc. | Frequency-agile system for telemetry with implantable device |
US20080058678A1 (en) | 2006-09-05 | 2008-03-06 | Shinichi Miyata | Kit for the determination of an analyte in a bodily fluid sample that includes a meter with a display-based tutorial module |
US20080057484A1 (en) | 2006-09-05 | 2008-03-06 | Shinichi Miyata | Event-driven method for tutoring a user in the determination of an analyte in a bodily fluid sample |
US9056165B2 (en) | 2006-09-06 | 2015-06-16 | Medtronic Minimed, Inc. | Intelligent therapy recommendation algorithm and method of using the same |
US20080071328A1 (en) | 2006-09-06 | 2008-03-20 | Medtronic, Inc. | Initiating medical system communications |
US8234706B2 (en) | 2006-09-08 | 2012-07-31 | Microsoft Corporation | Enabling access to aggregated software security information |
DE102006043484B4 (en) | 2006-09-15 | 2019-11-28 | Infineon Technologies Ag | Fuse structure and method for producing the same |
US7779332B2 (en) | 2006-09-25 | 2010-08-17 | Alfred E. Mann Foundation For Scientific Research | Rotationally invariant non-coherent burst coding |
US8478377B2 (en) | 2006-10-04 | 2013-07-02 | Dexcom, Inc. | Analyte sensor |
US8562528B2 (en) | 2006-10-04 | 2013-10-22 | Dexcom, Inc. | Analyte sensor |
US8447376B2 (en) | 2006-10-04 | 2013-05-21 | Dexcom, Inc. | Analyte sensor |
US7831287B2 (en) | 2006-10-04 | 2010-11-09 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8275438B2 (en) | 2006-10-04 | 2012-09-25 | Dexcom, Inc. | Analyte sensor |
US8298142B2 (en) | 2006-10-04 | 2012-10-30 | Dexcom, Inc. | Analyte sensor |
US8449464B2 (en) | 2006-10-04 | 2013-05-28 | Dexcom, Inc. | Analyte sensor |
US20080092638A1 (en) | 2006-10-19 | 2008-04-24 | Bayer Healthcare Llc | Wireless analyte monitoring system |
US8126728B2 (en) | 2006-10-24 | 2012-02-28 | Medapps, Inc. | Systems and methods for processing and transmittal of medical data through an intermediary device |
CA2667639A1 (en) | 2006-10-26 | 2008-05-02 | Abbott Diabetes Care Inc. | Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors |
EP1918837A1 (en) | 2006-10-31 | 2008-05-07 | F. Hoffmann-La Roche AG | Method for processing a chronological sequence of measurements of a time dependent parameter |
US7822557B2 (en) | 2006-10-31 | 2010-10-26 | Abbott Diabetes Care Inc. | Analyte sensors and methods |
US20080119705A1 (en) | 2006-11-17 | 2008-05-22 | Medtronic Minimed, Inc. | Systems and Methods for Diabetes Management Using Consumer Electronic Devices |
FI20065735A0 (en) | 2006-11-20 | 2006-11-20 | Salla Koski | Measurement, monitoring and management system and its constituent equipment |
EP2484283A3 (en) | 2006-11-23 | 2012-10-10 | Lifescan Scotland Ltd | Blood glucose meter capable of wireless communication |
FR2909001B1 (en) | 2006-11-24 | 2009-12-18 | Bernard Perriere | MINIATURIZED AND AUTOMATIC INJECTION AND SAMPLING DEVICE FOR MEDICAL USE. |
US8696570B2 (en) | 2006-11-28 | 2014-04-15 | Roche Diagnostics Operations Inc. | Insertion device and method for inserting a subcutaneously insertable element into body |
US20080139910A1 (en) | 2006-12-06 | 2008-06-12 | Metronic Minimed, Inc. | Analyte sensor and method of using the same |
US20080139903A1 (en) | 2006-12-08 | 2008-06-12 | Isense Corporation | Method and apparatus for insertion of a sensor using an introducer |
WO2008071218A1 (en) | 2006-12-14 | 2008-06-19 | Egomedical Swiss Ag | Monitoring device |
US8120493B2 (en) | 2006-12-20 | 2012-02-21 | Intel Corporation | Direct communication in antenna devices |
US20080154513A1 (en) | 2006-12-21 | 2008-06-26 | University Of Virginia Patent Foundation | Systems, Methods and Computer Program Codes for Recognition of Patterns of Hyperglycemia and Hypoglycemia, Increased Glucose Variability, and Ineffective Self-Monitoring in Diabetes |
US7802467B2 (en) | 2006-12-22 | 2010-09-28 | Abbott Diabetes Care Inc. | Analyte sensors and methods of use |
US7946985B2 (en) | 2006-12-29 | 2011-05-24 | Medtronic Minimed, Inc. | Method and system for providing sensor redundancy |
US20080161666A1 (en) | 2006-12-29 | 2008-07-03 | Abbott Diabetes Care, Inc. | Analyte devices and methods |
CA2678109C (en) | 2007-01-15 | 2020-05-26 | Deka Products Limited Partnership | Device and method for food management |
US7742747B2 (en) | 2007-01-25 | 2010-06-22 | Icera Canada ULC | Automatic IIP2 calibration architecture |
US8808515B2 (en) | 2007-01-31 | 2014-08-19 | Abbott Diabetes Care Inc. | Heterocyclic nitrogen containing polymers coated analyte monitoring device and methods of use |
US10154804B2 (en) | 2007-01-31 | 2018-12-18 | Medtronic Minimed, Inc. | Model predictive method and system for controlling and supervising insulin infusion |
US9597019B2 (en) | 2007-02-09 | 2017-03-21 | Lifescan, Inc. | Method of ensuring date and time on a test meter is accurate |
US8930203B2 (en) | 2007-02-18 | 2015-01-06 | Abbott Diabetes Care Inc. | Multi-function analyte test device and methods therefor |
WO2008105768A1 (en) | 2007-03-01 | 2008-09-04 | Dexcom, Inc. | Analyte sensor |
DE502007005457D1 (en) | 2007-03-14 | 2010-12-09 | Roche Diagnostics Gmbh | Insertion head for medical or pharmaceutical applications |
MX2009010000A (en) | 2007-03-19 | 2010-03-17 | Insuline Medical Ltd | Drug delivery device. |
WO2008115409A1 (en) | 2007-03-19 | 2008-09-25 | Bayer Healthcare Llc | Continuous analyte monitoring assembly and method of forming the same |
US8758245B2 (en) | 2007-03-20 | 2014-06-24 | Lifescan, Inc. | Systems and methods for pattern recognition in diabetes management |
DK1972275T3 (en) * | 2007-03-20 | 2016-02-08 | Hoffmann La Roche | A system for in-vivo measurement of an analyte concentration |
US7659823B1 (en) | 2007-03-20 | 2010-02-09 | At&T Intellectual Property Ii, L.P. | Tracking variable conditions using radio frequency identification |
JP2010523227A (en) | 2007-04-04 | 2010-07-15 | アイセンス コーポレーション | Analyte sensing device having one or more sensing electrodes |
EP2146625B1 (en) | 2007-04-14 | 2019-08-14 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
US8140142B2 (en) | 2007-04-14 | 2012-03-20 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
WO2008130896A1 (en) | 2007-04-14 | 2008-10-30 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in medical communication system |
WO2008130895A2 (en) | 2007-04-14 | 2008-10-30 | Abbott Diabetes Care, Inc. | Method and apparatus for providing dynamic multi-stage signal amplification in a medical device |
EP4108162A1 (en) | 2007-04-14 | 2022-12-28 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in medical communication system |
US9615780B2 (en) | 2007-04-14 | 2017-04-11 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
US20100145317A1 (en) | 2007-04-19 | 2010-06-10 | Morris Laster | Device system and method for monitoring and controlling blood analyte levels |
US9554721B1 (en) | 2007-04-23 | 2017-01-31 | Neurowave Systems Inc. | Seizure detector, brain dysfunction monitor and method |
US20080269673A1 (en) | 2007-04-27 | 2008-10-30 | Animas Corporation | Cellular-Enabled Medical Monitoring and Infusion System |
WO2008134587A1 (en) | 2007-04-27 | 2008-11-06 | Abbott Diabetes Care, Inc. | Test strip identification using conductive patterns |
JP5102350B2 (en) | 2007-04-30 | 2012-12-19 | メドトロニック ミニメド インコーポレイテッド | Reservoir filling / bubble management / infusion medium delivery system and method using the system |
WO2008133702A1 (en) | 2007-04-30 | 2008-11-06 | Medtronic Minimed, Inc. | Needle inserting and fluid flow connection for infusion medium delivery system |
US8323250B2 (en) | 2007-04-30 | 2012-12-04 | Medtronic Minimed, Inc. | Adhesive patch systems and methods |
US8692655B2 (en) | 2007-05-07 | 2014-04-08 | Bloomberg Finance L.P. | Dynamically programmable RFID transponder |
US8456301B2 (en) | 2007-05-08 | 2013-06-04 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
WO2008138006A2 (en) | 2007-05-08 | 2008-11-13 | Abbott Diabetes Care, Inc. | Analyte monitoring system and methods |
US8560038B2 (en) | 2007-05-14 | 2013-10-15 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US9125548B2 (en) | 2007-05-14 | 2015-09-08 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US20080312845A1 (en) | 2007-05-14 | 2008-12-18 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8239166B2 (en) | 2007-05-14 | 2012-08-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8600681B2 (en) | 2007-05-14 | 2013-12-03 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8260558B2 (en) | 2007-05-14 | 2012-09-04 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
WO2008143943A1 (en) | 2007-05-14 | 2008-11-27 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US7996158B2 (en) | 2007-05-14 | 2011-08-09 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8103471B2 (en) | 2007-05-14 | 2012-01-24 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US20080287755A1 (en) | 2007-05-17 | 2008-11-20 | Isense Corporation | Method and apparatus for trend alert calculation and display |
US20080294024A1 (en) | 2007-05-24 | 2008-11-27 | Cosentino Daniel L | Glucose meter system and monitor |
DE102007026083A1 (en) | 2007-05-25 | 2008-11-27 | Haselmeier S.A.R.L. | injection device |
WO2008150917A1 (en) | 2007-05-31 | 2008-12-11 | Abbott Diabetes Care, Inc. | Insertion devices and methods |
US8072310B1 (en) | 2007-06-05 | 2011-12-06 | Pulsed Indigo Inc. | System for detecting and measuring parameters of passive transponders |
EP2152350A4 (en) | 2007-06-08 | 2013-03-27 | Dexcom Inc | Integrated medicament delivery device for use with continuous analyte sensor |
US20080312518A1 (en) | 2007-06-14 | 2008-12-18 | Arkal Medical, Inc | On-demand analyte monitor and method of use |
EP2155296B1 (en) | 2007-06-20 | 2019-08-28 | Unomedical A/S | Cannula insertion device with automatic needle retraction comprising only one spring |
EP3533387A3 (en) | 2007-06-21 | 2019-11-13 | Abbott Diabetes Care, Inc. | Health management devices and methods |
CA2690870C (en) | 2007-06-21 | 2017-07-11 | Abbott Diabetes Care Inc. | Health monitor |
US8002752B2 (en) * | 2007-06-25 | 2011-08-23 | Medingo, Ltd. | Protector apparatus |
US20080319327A1 (en) | 2007-06-25 | 2008-12-25 | Triage Wireless, Inc. | Body-worn sensor featuring a low-power processor and multi-sensor array for measuring blood pressure |
US8641618B2 (en) * | 2007-06-27 | 2014-02-04 | Abbott Diabetes Care Inc. | Method and structure for securing a monitoring device element |
WO2009002622A2 (en) | 2007-06-27 | 2008-12-31 | F. Hoffman-La Roche Ag | Patient information input interface for a therapy system |
DK3460644T3 (en) | 2007-06-29 | 2021-03-22 | Hoffmann La Roche | Electronic blood glucose meter |
RU2010104457A (en) | 2007-07-10 | 2011-08-20 | Уномедикал А/С (Dk) | TWO SPRING INPUT DEVICE |
RU2010105684A (en) | 2007-07-18 | 2011-08-27 | Уномедикал А/С (Dk) | TURNING INTRODUCTION DEVICE |
WO2009018058A1 (en) | 2007-07-31 | 2009-02-05 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US7768386B2 (en) | 2007-07-31 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US20090036760A1 (en) | 2007-07-31 | 2009-02-05 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8834366B2 (en) | 2007-07-31 | 2014-09-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
CN103349804B (en) | 2007-08-01 | 2017-04-26 | F·霍夫曼-拉罗氏股份公司 | Device for facilitating infusion of therapeutic fluids and sensing of bodily analytes |
US7731658B2 (en) | 2007-08-16 | 2010-06-08 | Cardiac Pacemakers, Inc. | Glycemic control monitoring using implantable medical device |
US8926509B2 (en) | 2007-08-24 | 2015-01-06 | Hmicro, Inc. | Wireless physiological sensor patches and systems |
US9968742B2 (en) | 2007-08-29 | 2018-05-15 | Medtronic Minimed, Inc. | Combined sensor and infusion set using separated sites |
US8515547B2 (en) | 2007-08-31 | 2013-08-20 | Cardiac Pacemakers, Inc. | Wireless patient communicator for use in a life critical network |
US9848058B2 (en) | 2007-08-31 | 2017-12-19 | Cardiac Pacemakers, Inc. | Medical data transport over wireless life critical network employing dynamic communication link mapping |
US20090063402A1 (en) | 2007-08-31 | 2009-03-05 | Abbott Diabetes Care, Inc. | Method and System for Providing Medication Level Determination |
US8303545B2 (en) | 2007-09-07 | 2012-11-06 | Stat Medical Devices, Inc. | Infusion device and method of using and making the same |
CA2699875A1 (en) | 2007-09-17 | 2009-03-26 | Icu Medical, Inc. | Insertion devices for infusion devices |
EP3660499A1 (en) | 2007-09-24 | 2020-06-03 | Ascensia Diabetes Care Holdings AG | Multi-electrode test sensor |
DE102007047351A1 (en) | 2007-10-02 | 2009-04-09 | B. Braun Melsungen Ag | System and method for monitoring and controlling blood glucose levels |
US20090085768A1 (en) | 2007-10-02 | 2009-04-02 | Medtronic Minimed, Inc. | Glucose sensor transceiver |
US8377031B2 (en) | 2007-10-23 | 2013-02-19 | Abbott Diabetes Care Inc. | Closed loop control system with safety parameters and methods |
US8000918B2 (en) | 2007-10-23 | 2011-08-16 | Edwards Lifesciences Corporation | Monitoring and compensating for temperature-related error in an electrochemical sensor |
US8417312B2 (en) | 2007-10-25 | 2013-04-09 | Dexcom, Inc. | Systems and methods for processing sensor data |
US7783442B2 (en) | 2007-10-31 | 2010-08-24 | Medtronic Minimed, Inc. | System and methods for calibrating physiological characteristic sensors |
EP2060284A1 (en) | 2007-11-13 | 2009-05-20 | F.Hoffmann-La Roche Ag | Medical injection device having data input means and a pivotable display |
US8078592B2 (en) | 2007-12-07 | 2011-12-13 | Roche Diagnostics Operations, Inc. | System and method for database integrity checking |
US8290559B2 (en) | 2007-12-17 | 2012-10-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
US20090164251A1 (en) | 2007-12-19 | 2009-06-25 | Abbott Diabetes Care, Inc. | Method and apparatus for providing treatment profile management |
US20090164239A1 (en) | 2007-12-19 | 2009-06-25 | Abbott Diabetes Care, Inc. | Dynamic Display Of Glucose Information |
EP2235660B1 (en) | 2008-01-15 | 2015-07-08 | Corning Cable Systems LLC | Rfid systems and methods for automatically detecting and/or directing the physical configuration of a complex system |
DE102008008072A1 (en) | 2008-01-29 | 2009-07-30 | Balluff Gmbh | sensor |
WO2009097450A1 (en) | 2008-01-30 | 2009-08-06 | Dexcom. Inc. | Continuous cardiac marker sensor system |
US20110046456A1 (en) | 2008-02-08 | 2011-02-24 | Hoerdum Elo Lau | Assembly Comprising Inserter, Cannula Part and Base Part |
EP2452709B1 (en) | 2008-02-08 | 2022-01-19 | Unomedical A/S | Cannula part |
EP2090996A1 (en) | 2008-02-16 | 2009-08-19 | Roche Diagnostics GmbH | Medical device |
WO2009105337A2 (en) | 2008-02-20 | 2009-08-27 | Dexcom, Inc. | Continuous medicament sensor system for in vivo use |
US8229535B2 (en) | 2008-02-21 | 2012-07-24 | Dexcom, Inc. | Systems and methods for blood glucose monitoring and alert delivery |
US8122783B2 (en) | 2008-02-22 | 2012-02-28 | Sauer-Danfoss Inc. | Joystick and method of manufacturing the same |
BRPI0906017A2 (en) | 2008-02-27 | 2015-06-30 | Mond4D Ltd | System and device for measuring an analyte from a body fluid over a measuring area, device for controlling an analyte measuring device, method for measuring an analyte from a body fluid, system for monitoring an analyte from a body fluid , specialized analyte measuring element and vehicle |
US8317699B2 (en) | 2008-02-29 | 2012-11-27 | Roche Diagnostics Operations, Inc. | Device and method for assessing blood glucose control |
JP5489043B2 (en) | 2008-03-10 | 2014-05-14 | コーニンクレッカ フィリップス エヌ ヴェ | Wireless heart monitoring system |
CN101977543B (en) | 2008-03-19 | 2013-05-22 | 艾利森电话股份有限公司 | NFC communications for implanted medical data acquisition devices |
US20090242399A1 (en) | 2008-03-25 | 2009-10-01 | Dexcom, Inc. | Analyte sensor |
US8396528B2 (en) | 2008-03-25 | 2013-03-12 | Dexcom, Inc. | Analyte sensor |
US8682408B2 (en) | 2008-03-28 | 2014-03-25 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
US8583204B2 (en) | 2008-03-28 | 2013-11-12 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
US20090247856A1 (en) | 2008-03-28 | 2009-10-01 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
WO2009124095A1 (en) | 2008-03-31 | 2009-10-08 | Abbott Diabetes Care Inc. | Shallow implantable analyte sensor with rapid physiological response |
US8600682B2 (en) | 2008-04-04 | 2013-12-03 | Hygieia, Inc. | Apparatus for optimizing a patient's insulin dosage regimen |
EP3659628A1 (en) | 2008-04-10 | 2020-06-03 | Abbott Diabetes Care, Inc. | Method and system for sterilizing an analyte sensor |
US9924898B2 (en) | 2008-04-15 | 2018-03-27 | Becton, Dickinson And Company | Flash activated passive shielding needle assembly |
US20090267765A1 (en) | 2008-04-29 | 2009-10-29 | Jack Greene | Rfid to prevent reprocessing |
USD618337S1 (en) | 2008-05-02 | 2010-06-22 | KCI Licensing, Inc, | Reduced pressure treatment apparatus |
CA2724446C (en) | 2008-05-14 | 2017-04-04 | Espenusa Holding, Llc | Physical activity monitor and data collection unit |
US8610577B2 (en) | 2008-05-20 | 2013-12-17 | Deka Products Limited Partnership | RFID system |
US9295786B2 (en) | 2008-05-28 | 2016-03-29 | Medtronic Minimed, Inc. | Needle protective device for subcutaneous sensors |
US8924159B2 (en) | 2008-05-30 | 2014-12-30 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
US20090294277A1 (en) | 2008-05-30 | 2009-12-03 | Abbott Diabetes Care, Inc. | Method and system for producing thin film biosensors |
US8394637B2 (en) | 2008-06-02 | 2013-03-12 | Roche Diagnostics Operations, Inc. | Handheld analyzer for testing a sample |
US8132037B2 (en) | 2008-06-06 | 2012-03-06 | Roche Diagnostics International Ag | Apparatus and method for processing wirelessly communicated data and clock information within an electronic device |
US8117481B2 (en) | 2008-06-06 | 2012-02-14 | Roche Diagnostics International Ag | Apparatus and method for processing wirelessly communicated information within an electronic device |
CN101621714B (en) | 2008-06-30 | 2013-06-12 | 华为技术有限公司 | Node and data processing system and data processing method |
WO2010003886A1 (en) | 2008-07-07 | 2010-01-14 | Unomedical A/S | Inserter for transcutaneous device |
US8131365B2 (en) | 2008-07-09 | 2012-03-06 | Cardiac Pacemakers, Inc. | Event-based battery monitor for implantable devices |
US20100025238A1 (en) | 2008-07-31 | 2010-02-04 | Medtronic Minimed, Inc. | Analyte sensor apparatuses having improved electrode configurations and methods for making and using them |
US8111042B2 (en) | 2008-08-05 | 2012-02-07 | Broadcom Corporation | Integrated wireless resonant power charging and communication channel |
US8432070B2 (en) | 2008-08-25 | 2013-04-30 | Qualcomm Incorporated | Passive receivers for wireless power transmission |
US9943644B2 (en) | 2008-08-31 | 2018-04-17 | Abbott Diabetes Care Inc. | Closed loop control with reference measurement and methods thereof |
US8734422B2 (en) | 2008-08-31 | 2014-05-27 | Abbott Diabetes Care Inc. | Closed loop control with improved alarm functions |
US20100057040A1 (en) | 2008-08-31 | 2010-03-04 | Abbott Diabetes Care, Inc. | Robust Closed Loop Control And Methods |
EP4227675A3 (en) | 2008-09-19 | 2023-09-06 | DexCom, Inc. | Particle-containing membrane and particulate electrode for analyte sensors |
US8986208B2 (en) | 2008-09-30 | 2015-03-24 | Abbott Diabetes Care Inc. | Analyte sensor sensitivity attenuation mitigation |
US8983568B2 (en) | 2008-09-30 | 2015-03-17 | Abbott Diabetes Care Inc. | Analyte sensors comprising leveling agents |
KR20110081250A (en) | 2008-10-02 | 2011-07-13 | 레이덴 에너지 인코오포레이티드 | Electronic current interrupt device for battery |
US20100331644A1 (en) | 2008-11-07 | 2010-12-30 | Dexcom, Inc. | Housing for an intravascular sensor |
CN102405011A (en) | 2008-11-26 | 2012-04-04 | 弗吉尼亚大学专利基金会 | Method, system, and computer program product for tracking of blood glucose variability in diabetes |
US20100145377A1 (en) | 2008-12-04 | 2010-06-10 | Venture Corporation Limited | Lancing Device For Minimizing Pain |
US8150516B2 (en) | 2008-12-11 | 2012-04-03 | Pacesetter, Inc. | Systems and methods for operating an implantable device for medical procedures |
US20100169035A1 (en) | 2008-12-29 | 2010-07-01 | Medtronic Minimed, Inc. | Methods and systems for observing sensor parameters |
US9320470B2 (en) | 2008-12-31 | 2016-04-26 | Medtronic Minimed, Inc. | Method and/or system for sensor artifact filtering |
US9402544B2 (en) | 2009-02-03 | 2016-08-02 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
CN102308278A (en) | 2009-02-04 | 2012-01-04 | 雅培糖尿病护理公司 | Multi-function analyte test device and methods therefor |
US20100198033A1 (en) | 2009-02-05 | 2010-08-05 | Peter Krulevitch | Flexible indwelling biosensor, flexible indwelling biosensor insertion device, and related methods |
US8394246B2 (en) | 2009-02-23 | 2013-03-12 | Roche Diagnostics Operations, Inc. | System and method for the electrochemical measurement of an analyte employing a remote sensor |
DK3714788T3 (en) | 2009-02-26 | 2023-04-17 | Abbott Diabetes Care Inc | Method for manufacturing improved analyte sensors |
US20100213057A1 (en) | 2009-02-26 | 2010-08-26 | Benjamin Feldman | Self-Powered Analyte Sensor |
WO2010111660A1 (en) | 2009-03-27 | 2010-09-30 | Dexcom, Inc. | Methods and systems for promoting glucose management |
EP2272553A1 (en) | 2009-06-29 | 2011-01-12 | Unomedical A/S | Inserter Assembly |
WO2010127169A2 (en) * | 2009-04-30 | 2010-11-04 | Dexcom, Inc. | Performance reports associated with continuous sensor data from multiple analysis time periods |
WO2010135638A2 (en) | 2009-05-22 | 2010-11-25 | Abbott Diabetes Care Inc. | Methods for reducing false hypoglycemia alarm occurrence |
US8595607B2 (en) | 2009-06-04 | 2013-11-26 | Abbott Diabetes Care Inc. | Method and system for updating a medical device |
US8124452B2 (en) | 2009-06-14 | 2012-02-28 | Terepac Corporation | Processes and structures for IC fabrication |
US9218453B2 (en) | 2009-06-29 | 2015-12-22 | Roche Diabetes Care, Inc. | Blood glucose management and interface systems and methods |
US20100331643A1 (en) | 2009-06-30 | 2010-12-30 | Abbott Diabetes Care Inc. | Extruded Analyte Sensors and Methods of Using Same |
US10376213B2 (en) | 2009-06-30 | 2019-08-13 | Waveform Technologies, Inc. | System, method and apparatus for sensor insertion |
US8613892B2 (en) | 2009-06-30 | 2013-12-24 | Abbott Diabetes Care Inc. | Analyte meter with a moveable head and methods of using the same |
US9237864B2 (en) | 2009-07-02 | 2016-01-19 | Dexcom, Inc. | Analyte sensors and methods of manufacturing same |
US9792408B2 (en) | 2009-07-02 | 2017-10-17 | Covidien Lp | Method and apparatus to detect transponder tagged objects and to communicate with medical telemetry devices, for example during medical procedures |
CA2766961A1 (en) | 2009-08-07 | 2011-02-10 | Unomedical A/S | Delivery device with sensor and one or more cannulas |
CA2770325A1 (en) | 2009-08-17 | 2011-02-24 | The Regents Of The University Of California | Distributed external and internal wireless sensor systems for characterization of surface and subsurface biomedical structure and condition |
WO2011025999A1 (en) | 2009-08-29 | 2011-03-03 | Abbott Diabetes Care Inc. | Analyte sensor |
WO2011026130A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Inserter device including rotor subassembly |
WO2011026149A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Mounting unit having a sensor and associated circuitry |
CN102473276B (en) | 2009-08-31 | 2016-04-13 | 雅培糖尿病护理公司 | Medical treatment device and method |
ES2952361T3 (en) | 2009-08-31 | 2023-10-31 | Abbott Diabetes Care Inc | Displays for a medical device |
US8882710B2 (en) | 2009-09-02 | 2014-11-11 | Medtronic Minimed, Inc. | Insertion device systems and methods |
US20110077469A1 (en) | 2009-09-27 | 2011-03-31 | Blocker Richard A | Systems and methods for utilizing prolonged self monitoring in the analysis of chronic ailment treatments |
CN102724913A (en) | 2009-09-30 | 2012-10-10 | 德克斯康公司 | Transcutaneous analyte sensor |
WO2011041531A1 (en) | 2009-09-30 | 2011-04-07 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
WO2011044386A1 (en) | 2009-10-07 | 2011-04-14 | Abbott Diabetes Care Inc. | Sensor inserter assembly having rotatable trigger |
CN102869400A (en) | 2009-10-30 | 2013-01-09 | 梅丁格有限公司 | Systems, methods and devices for adjusting insertion depth of cannula associated with portable therapeutic device |
US20110123971A1 (en) | 2009-11-20 | 2011-05-26 | Medivoce, Inc. | Electronic Medical Voice Instruction System |
US9949672B2 (en) | 2009-12-17 | 2018-04-24 | Ascensia Diabetes Care Holdings Ag | Apparatus, systems and methods for determining and displaying pre-event and post-event analyte concentration levels |
EP2335565A1 (en) | 2009-12-18 | 2011-06-22 | Roche Diagnostics GmbH | Protective container for holding reusable diagnostic components |
CN102791186B (en) | 2009-12-23 | 2015-08-05 | 德尔塔丹麦光电声学公司 | For being connected to the monitoring device on the surface of target |
US8474335B2 (en) * | 2010-01-12 | 2013-07-02 | Veltek Associates, Inc. | Microbial air sampler |
CA2728831A1 (en) | 2010-01-22 | 2011-07-22 | Lifescan, Inc. | Diabetes management unit, method, and system |
WO2011091336A1 (en) | 2010-01-22 | 2011-07-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing notification in analyte monitoring systems |
WO2011091178A1 (en) | 2010-01-24 | 2011-07-28 | Medtronic, Inc. | Non-rechargeable battery for an implantable medical devices |
US20110184258A1 (en) | 2010-01-28 | 2011-07-28 | Abbott Diabetes Care Inc. | Balloon Catheter Analyte Measurement Sensors and Methods for Using the Same |
USD924406S1 (en) * | 2010-02-01 | 2021-07-06 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
US9041730B2 (en) | 2010-02-12 | 2015-05-26 | Dexcom, Inc. | Receivers for analyzing and displaying sensor data |
AU2011217067A1 (en) | 2010-02-19 | 2012-09-06 | Lightship Medical Limited | Subcutaneous glucose sensor |
US20110208027A1 (en) | 2010-02-23 | 2011-08-25 | Roche Diagnostics Operations, Inc. | Methods And Systems For Providing Therapeutic Guidelines To A Person Having Diabetes |
GB201003581D0 (en) | 2010-03-04 | 2010-04-21 | Bacon Raymond J | Medicament dispenser |
US10448872B2 (en) | 2010-03-16 | 2019-10-22 | Medtronic Minimed, Inc. | Analyte sensor apparatuses having improved electrode configurations and methods for making and using them |
BR112012024635A2 (en) | 2010-03-30 | 2017-08-08 | Unomedical As | medical device |
CA2794104A1 (en) | 2010-03-31 | 2011-10-06 | Animas Corporation | Method and system to display analyte sensor data |
US9591971B2 (en) | 2010-04-05 | 2017-03-14 | Helen Of Troy Limited | Insertion detector for medical probe |
WO2011130545A1 (en) | 2010-04-16 | 2011-10-20 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US9198623B2 (en) | 2010-04-22 | 2015-12-01 | Abbott Diabetes Care Inc. | Devices, systems, and methods related to analyte monitoring and management |
US8588284B2 (en) | 2010-06-01 | 2013-11-19 | Adeptence, Llc | Systems and methods for networked wearable medical sensors |
US9336353B2 (en) | 2010-06-25 | 2016-05-10 | Dexcom, Inc. | Systems and methods for communicating sensor data between communication devices of a glucose monitoring system |
US20110319738A1 (en) | 2010-06-29 | 2011-12-29 | Abbott Diabetes Care Inc. | Medical Devices and Insertion Systems and Methods |
US11064921B2 (en) | 2010-06-29 | 2021-07-20 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
EP2415395A1 (en) | 2010-08-04 | 2012-02-08 | Roche Diagnostics GmbH | Medical device with receptacle channel for bodily fluids |
DK2621339T3 (en) | 2010-09-29 | 2020-02-24 | Dexcom Inc | ADVANCED SYSTEM FOR CONTINUOUS ANALYTICAL MONITORING |
EP3744249A1 (en) | 2010-10-27 | 2020-12-02 | Dexcom, Inc. | Continuous analyte monitor data recording device operable in a blinded mode |
US8784383B2 (en) | 2010-11-30 | 2014-07-22 | Becton, Dickinson And Company | Insulin pump dermal infusion set having partially integrated mechanized cannula insertion with disposable activation portion |
USD668164S1 (en) * | 2011-02-04 | 2012-10-02 | Crestron Electronics Inc. | Battery powered occupancy sensor |
USD694397S1 (en) | 2011-02-28 | 2013-11-26 | Abbott Diabetes Care Inc. | Medical device inserter |
US10136845B2 (en) | 2011-02-28 | 2018-11-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
WO2012118872A2 (en) | 2011-02-28 | 2012-09-07 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
JP2014514032A (en) | 2011-03-11 | 2014-06-19 | プロテウス デジタル ヘルス, インコーポレイテッド | Wearable personal body-related devices with various physical configurations |
EP3536241B1 (en) * | 2011-04-08 | 2023-03-29 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
USD691710S1 (en) | 2011-05-23 | 2013-10-15 | Abbott Diabetes Care Inc. | Medical device inserter |
WO2013066873A1 (en) | 2011-10-31 | 2013-05-10 | Abbott Diabetes Care Inc. | Electronic devices having integrated reset systems and methods thereof |
US9402570B2 (en) * | 2011-12-11 | 2016-08-02 | Abbott Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
US20150326072A1 (en) | 2014-05-07 | 2015-11-12 | Energous Corporation | Boost-Charger-Boost System for Enhanced Power Delivery |
US8930028B2 (en) * | 2012-07-27 | 2015-01-06 | Roche Diagnostics Operations, Inc. | Handheld medical device functionality without battery |
USD731334S1 (en) * | 2013-08-20 | 2015-06-09 | Fibar Group sp. z o.o. | Flood sensor |
CA162350S (en) * | 2014-11-14 | 2016-08-29 | Farmshed Labs Ltd | Sensing device |
US10531831B2 (en) * | 2015-05-14 | 2020-01-14 | Abbott Diabetes Care Inc. | Non-rigid wearable devices |
CA2984939A1 (en) | 2015-05-14 | 2016-11-17 | Abbott Diabetes Care Inc. | Compact medical device inserters and related systems and methods |
USD775987S1 (en) * | 2015-09-08 | 2017-01-10 | Nix Sensor Ltd. | Egg cover |
CA169912S (en) * | 2015-09-30 | 2016-11-01 | Misfit Inc | Activity monitoring device |
USD806254S1 (en) * | 2015-12-07 | 2017-12-26 | Samsung Electronics Co., Ltd. | Apparatus for medical diagnosis |
USD814298S1 (en) * | 2016-02-04 | 2018-04-03 | Henkel Ag & Co. Kgaa | Cap |
US10765348B2 (en) | 2016-04-08 | 2020-09-08 | Medtronic Minimed, Inc. | Sensor and transmitter product |
US10765369B2 (en) | 2016-04-08 | 2020-09-08 | Medtronic Minimed, Inc. | Analyte sensor |
USD810952S1 (en) * | 2016-11-25 | 2018-02-20 | Raymond Hsu | Transcutaneous electrical nerve stimulation or TENS device |
USD824034S1 (en) * | 2016-12-15 | 2018-07-24 | Sano Intelligence, Inc. | Biomonitoring interface device |
USD820988S1 (en) * | 2017-01-20 | 2018-06-19 | Sano Intelligence, Inc. | Biomonitoring sensor system for monitoring body chemistry |
US10379765B2 (en) | 2017-06-27 | 2019-08-13 | Western Digital Technologies, Inc. | Geometry-aware command scheduling |
USD888252S1 (en) * | 2018-06-18 | 2020-06-23 | Dexcom, Inc. | Transcutaneous analyte sensor applicator |
-
2010
- 2010-02-01 US US12/698,129 patent/US9402544B2/en active Active
- 2010-02-01 US US12/698,124 patent/US20100198034A1/en not_active Abandoned
- 2010-02-02 ES ES10739031.2T patent/ES2671054T3/en active Active
- 2010-02-02 WO PCT/US2010/022928 patent/WO2010091028A1/en active Application Filing
- 2010-02-02 WO PCT/US2010/022860 patent/WO2010091005A1/en active Application Filing
- 2010-02-02 DK DK20177712.5T patent/DK3730045T3/en active
- 2010-02-02 EP EP10739015.5A patent/EP2393417B1/en active Active
- 2010-02-02 CN CN201080006481.7A patent/CN102307518B/en active Active
- 2010-02-02 EP EP10739031.2A patent/EP2393418B1/en active Active
- 2010-02-02 ES ES20177712T patent/ES2911905T3/en active Active
- 2010-02-02 BR BRPI1008834A patent/BRPI1008834A2/en not_active IP Right Cessation
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- 2010-02-02 EP EP20177712.5A patent/EP3730045B1/en active Active
- 2010-02-02 EP EP21192910.4A patent/EP3960072A1/en active Pending
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- 2010-02-02 EP EP19151577.4A patent/EP3542712A1/en active Pending
- 2010-02-02 EP EP17201183.5A patent/EP3329842B1/en active Active
- 2010-02-02 EP EP21211041.5A patent/EP3977921B1/en active Active
- 2010-02-02 ES ES20177703T patent/ES2907146T3/en active Active
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- 2015-06-17 US US14/741,458 patent/US20150282711A1/en not_active Abandoned
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- 2016-06-24 US US15/192,531 patent/US9636068B2/en active Active
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- 2019-04-18 US US29/688,180 patent/USD882432S1/en active Active
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-
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Patent Citations (109)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4245634A (en) * | 1975-01-22 | 1981-01-20 | Hospital For Sick Children | Artificial beta cell |
US4373527A (en) * | 1979-04-27 | 1983-02-15 | The Johns Hopkins University | Implantable, programmable medication infusion system |
US4373527B1 (en) * | 1979-04-27 | 1995-06-27 | Univ Johns Hopkins | Implantable programmable medication infusion system |
US4425920A (en) * | 1980-10-24 | 1984-01-17 | Purdue Research Foundation | Apparatus and method for measurement and control of blood pressure |
US4431004A (en) * | 1981-10-27 | 1984-02-14 | Bessman Samuel P | Implantable glucose sensor |
US4494950A (en) * | 1982-01-19 | 1985-01-22 | The Johns Hopkins University | Plural module medication delivery system |
US5279294A (en) * | 1985-04-08 | 1994-01-18 | Cascade Medical, Inc. | Medical diagnostic system |
US4890620A (en) * | 1985-09-20 | 1990-01-02 | The Regents Of The University Of California | Two-dimensional diffusion glucose substrate sensing electrode |
US4995402A (en) * | 1988-10-12 | 1991-02-26 | Thorne, Smith, Astill Technologies, Inc. | Medical droplet whole blood and like monitoring |
US5379238A (en) * | 1989-03-03 | 1995-01-03 | Stark; Edward W. | Signal processing method and apparatus |
US4986271A (en) * | 1989-07-19 | 1991-01-22 | The University Of New Mexico | Vivo refillable glucose sensor |
US5082550A (en) * | 1989-12-11 | 1992-01-21 | The United States Of America As Represented By The Department Of Energy | Enzyme electrochemical sensor electrode and method of making it |
US5289497A (en) * | 1991-05-23 | 1994-02-22 | Interdigital Technology Corporation | Broadcast synchronized communication system |
US5285792A (en) * | 1992-01-10 | 1994-02-15 | Physio-Control Corporation | System for producing prioritized alarm messages in a medical instrument |
US5711001A (en) * | 1992-05-08 | 1998-01-20 | Motorola, Inc. | Method and circuit for acquisition by a radio receiver |
US5593852A (en) * | 1993-12-02 | 1997-01-14 | Heller; Adam | Subcutaneous glucose electrode |
US5391250A (en) * | 1994-03-15 | 1995-02-21 | Minimed Inc. | Method of fabricating thin film sensors |
US5390671A (en) * | 1994-03-15 | 1995-02-21 | Minimed Inc. | Transcutaneous sensor insertion set |
US5711861A (en) * | 1995-11-22 | 1998-01-27 | Ward; W. Kenneth | Device for monitoring changes in analyte concentration |
US5856758A (en) * | 1996-11-20 | 1999-01-05 | Adtran, Inc. | Low distortion driver employing positive feedback for reducing power loss in output impedance that effectively matches the impedance of driven line |
US7167818B2 (en) * | 1997-01-10 | 2007-01-23 | Health Hero Network, Inc. | Disease simulation system and method |
US20080017522A1 (en) * | 1997-02-06 | 2008-01-24 | Therasense, Inc. | Integrated Lancing and Measurement Device |
US20040011671A1 (en) * | 1997-03-04 | 2004-01-22 | Dexcom, Inc. | Device and method for determining analyte levels |
US6503381B1 (en) * | 1997-09-12 | 2003-01-07 | Therasense, Inc. | Biosensor |
US20020013538A1 (en) * | 1997-09-30 | 2002-01-31 | David Teller | Method and apparatus for health signs monitoring |
US6990366B2 (en) * | 1998-04-30 | 2006-01-24 | Therasense, Inc. | Analyte monitoring device and methods of use |
US6175752B1 (en) * | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US20020013522A1 (en) * | 1998-05-20 | 2002-01-31 | Steffen Lav | Medical apparatus for use by a patient for medical self treatment of diabetes |
US6338790B1 (en) * | 1998-10-08 | 2002-01-15 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
US8103325B2 (en) * | 1999-03-08 | 2012-01-24 | Tyco Healthcare Group Lp | Method and circuit for storing and providing historical physiological data |
US6546268B1 (en) * | 1999-06-02 | 2003-04-08 | Ball Semiconductor, Inc. | Glucose sensor |
US20090020502A1 (en) * | 1999-10-04 | 2009-01-22 | Bhullar Raghbir S | Biosensor and method of making |
US7171274B2 (en) * | 2000-01-21 | 2007-01-30 | Medtronic Minimed, Inc. | Method and apparatus for communicating between an ambulatory medical device and a control device via telemetry using randomized data |
US20050010269A1 (en) * | 2000-01-21 | 2005-01-13 | Medical Research Group, Inc. | Microprocessor controlled ambulatory medical apparatus with hand held communication device |
US20090005666A1 (en) * | 2000-02-23 | 2009-01-01 | Medtronic Minimed, Inc. | Real time self-adjusting calibration algorithm |
US20050004494A1 (en) * | 2001-01-22 | 2005-01-06 | Perez Edward P. | Lancet device having capillary action |
US20030023461A1 (en) * | 2001-03-14 | 2003-01-30 | Dan Quintanilla | Internet based therapy management system |
US20050017864A1 (en) * | 2001-04-17 | 2005-01-27 | Alexandre Tsoukalis | System for monitoring medical parameters |
US6676816B2 (en) * | 2001-05-11 | 2004-01-13 | Therasense, Inc. | Transition metal complexes with (pyridyl)imidazole ligands and sensors using said complexes |
US20030004403A1 (en) * | 2001-06-29 | 2003-01-02 | Darrel Drinan | Gateway platform for biological monitoring and delivery of therapeutic compounds |
US20030023317A1 (en) * | 2001-07-27 | 2003-01-30 | Dexcom, Inc. | Membrane for use with implantable devices |
US20050001024A1 (en) * | 2001-12-03 | 2005-01-06 | Yosuke Kusaka | Electronic apparatus, electronic camera, electronic device, image display apparatus, and image transmission system |
US6983867B1 (en) * | 2002-04-29 | 2006-01-10 | Dl Technology Llc | Fluid dispense pump with drip prevention mechanism and method for controlling same |
US20040010207A1 (en) * | 2002-07-15 | 2004-01-15 | Flaherty J. Christopher | Self-contained, automatic transcutaneous physiologic sensing system |
US20040017300A1 (en) * | 2002-07-25 | 2004-01-29 | Kotzin Michael D. | Portable communication device and corresponding method of operation |
US7833151B2 (en) * | 2002-12-26 | 2010-11-16 | Given Imaging Ltd. | In vivo imaging device with two imagers |
US7134999B2 (en) * | 2003-04-04 | 2006-11-14 | Dexcom, Inc. | Optimized sensor geometry for an implantable glucose sensor |
US20050003470A1 (en) * | 2003-06-10 | 2005-01-06 | Therasense, Inc. | Glucose measuring device for use in personal area network |
US8090445B2 (en) * | 2003-06-30 | 2012-01-03 | Codman Neuro Sciences Sárl | System and method for controlling an implantable medical device subject to magnetic field or radio frequency exposure |
US20090012379A1 (en) * | 2003-08-01 | 2009-01-08 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US20080021666A1 (en) * | 2003-08-01 | 2008-01-24 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US20070016381A1 (en) * | 2003-08-22 | 2007-01-18 | Apurv Kamath | Systems and methods for processing analyte sensor data |
US20080018433A1 (en) * | 2003-10-29 | 2008-01-24 | Innovision Research & Technology Plc | Rfid Apparatus |
US20100016698A1 (en) * | 2003-11-19 | 2010-01-21 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
US20100010332A1 (en) * | 2003-12-09 | 2010-01-14 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
US20100010324A1 (en) * | 2003-12-09 | 2010-01-14 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
US20100010331A1 (en) * | 2003-12-09 | 2010-01-14 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
US20100016687A1 (en) * | 2003-12-09 | 2010-01-21 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
US20100022855A1 (en) * | 2003-12-09 | 2010-01-28 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
US20060009727A1 (en) * | 2004-04-08 | 2006-01-12 | Chf Solutions Inc. | Method and apparatus for an extracorporeal control of blood glucose |
US7324850B2 (en) * | 2004-04-29 | 2008-01-29 | Cardiac Pacemakers, Inc. | Method and apparatus for communication between a handheld programmer and an implantable medical device |
US20090030294A1 (en) * | 2004-05-03 | 2009-01-29 | Dexcom, Inc. | Implantable analyte sensor |
US20060010098A1 (en) * | 2004-06-04 | 2006-01-12 | Goodnow Timothy T | Diabetes care host-client architecture and data management system |
US20060020300A1 (en) * | 2004-06-09 | 2006-01-26 | David Nghiem | Implantable medical device package antenna |
US20060004270A1 (en) * | 2004-06-23 | 2006-01-05 | Michel Bedard | Method and apparatus for the monitoring of clinical states |
US20060001538A1 (en) * | 2004-06-30 | 2006-01-05 | Ulrich Kraft | Methods of monitoring the concentration of an analyte |
US20060004439A1 (en) * | 2004-06-30 | 2006-01-05 | Benjamin Spenser | Device and method for assisting in the implantation of a prosthetic valve |
US20060015020A1 (en) * | 2004-07-06 | 2006-01-19 | Dexcom, Inc. | Systems and methods for manufacture of an analyte-measuring device including a membrane system |
US20060020188A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060020189A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060015024A1 (en) * | 2004-07-13 | 2006-01-19 | Mark Brister | Transcutaneous medical device with variable stiffness |
US20060020190A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20080188731A1 (en) * | 2004-07-13 | 2008-08-07 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20070038044A1 (en) * | 2004-07-13 | 2007-02-15 | Dobbles J M | Analyte sensor |
US20060020191A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060019327A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060020192A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060020187A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060020186A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060016700A1 (en) * | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7651596B2 (en) * | 2005-04-08 | 2010-01-26 | Dexcom, Inc. | Cellulosic-based interference domain for an analyte sensor |
US20070017983A1 (en) * | 2005-07-19 | 2007-01-25 | 3M Innovative Properties Company | RFID reader supporting one-touch search functionality |
US20070073129A1 (en) * | 2005-09-23 | 2007-03-29 | Medtronic Minimed, Inc. | Flexible sensor apparatus |
US20080009692A1 (en) * | 2005-09-30 | 2008-01-10 | Abbott Diabetes Care, Inc. | Method and Apparatus for Providing Analyte Sensor and Data Processing Device |
US20090018425A1 (en) * | 2005-12-28 | 2009-01-15 | Tianmei Ouyang | Analyte monitoring: stabilizer for subcutaneous glucose sensor with incorporated antiglycolytic agent |
US8102789B2 (en) * | 2005-12-29 | 2012-01-24 | Medtronic, Inc. | System and method for synchronous wireless communication with a medical device |
US20070219496A1 (en) * | 2006-02-09 | 2007-09-20 | Dean Kamen | Pumping fluid delivery systems and methods using force application assembly |
US8098208B2 (en) * | 2006-05-30 | 2012-01-17 | Polyic Gmbh & Co. Kg | Antenna configuration and use thereof |
US8098159B2 (en) * | 2006-06-09 | 2012-01-17 | Intelleflex Corporation | RF device comparing DAC output to incoming signal for selectively performing an action |
US20080009304A1 (en) * | 2006-07-06 | 2008-01-10 | Fry Walter G | Electronic device power management system and method |
US7866026B1 (en) * | 2006-08-01 | 2011-01-11 | Abbott Diabetes Care Inc. | Method for making calibration-adjusted sensors |
US7653425B2 (en) * | 2006-08-09 | 2010-01-26 | Abbott Diabetes Care Inc. | Method and system for providing calibration of an analyte sensor in an analyte monitoring system |
US20080062055A1 (en) * | 2006-09-11 | 2008-03-13 | Elster Electricity, Llc | Printed circuit notch antenna |
US20090018424A1 (en) * | 2006-10-04 | 2009-01-15 | Dexcom, Inc. | Analyte sensor |
US8102263B2 (en) * | 2006-12-08 | 2012-01-24 | Electronics And Telecommunications Research Institute | Passive tag including volatile memory |
US8098160B2 (en) * | 2007-01-22 | 2012-01-17 | Cisco Technology, Inc. | Method and system for remotely provisioning and/or configuring a device |
US20080242962A1 (en) * | 2007-03-20 | 2008-10-02 | Bernd Roesicke | System for in-vitro measurement of an analyte concentration |
US20090005665A1 (en) * | 2007-05-14 | 2009-01-01 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US20090006034A1 (en) * | 2007-05-14 | 2009-01-01 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8098201B2 (en) * | 2007-11-29 | 2012-01-17 | Electronics & Telecommunications Research Institute | Radio frequency identification tag and radio frequency identification tag antenna |
US8103241B2 (en) * | 2007-12-07 | 2012-01-24 | Roche Diagnostics Operations, Inc. | Method and system for wireless device communication |
US8102021B2 (en) * | 2008-05-12 | 2012-01-24 | Sychip Inc. | RF devices |
US20100010329A1 (en) * | 2008-07-14 | 2010-01-14 | Abbott Diabetes Care Inc. | Closed Loop Control System Interface and Methods |
US8094009B2 (en) * | 2008-08-27 | 2012-01-10 | The Invention Science Fund I, Llc | Health-related signaling via wearable items |
US8102154B2 (en) * | 2008-09-04 | 2012-01-24 | Medtronic Minimed, Inc. | Energy source isolation and protection circuit for an electronic device |
US8098161B2 (en) * | 2008-12-01 | 2012-01-17 | Raytheon Company | Radio frequency identification inlay with improved readability |
US20110021889A1 (en) * | 2009-07-23 | 2011-01-27 | Abbott Diabetes Care Inc. | Continuous Analyte Measurement Systems and Systems and Methods for Implanting Them |
US8093991B2 (en) * | 2009-09-16 | 2012-01-10 | Greatbatch Ltd. | RFID detection and identification system for implantable medical devices |
US20120010642A1 (en) * | 2010-03-24 | 2012-01-12 | Lee Daniel H | Medical device inserters and processes of inserting and using medical devices |
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US9980670B2 (en) | 2002-11-05 | 2018-05-29 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
US11116430B2 (en) | 2002-11-05 | 2021-09-14 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
US11141084B2 (en) | 2002-11-05 | 2021-10-12 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
US10973443B2 (en) | 2002-11-05 | 2021-04-13 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
US10039881B2 (en) | 2002-12-31 | 2018-08-07 | Abbott Diabetes Care Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US10434246B2 (en) | 2003-10-07 | 2019-10-08 | Icu Medical, Inc. | Medication management system |
USD914881S1 (en) | 2003-11-05 | 2021-03-30 | Abbott Diabetes Care Inc. | Analyte sensor electronic mount |
USD902408S1 (en) | 2003-11-05 | 2020-11-17 | Abbott Diabetes Care Inc. | Analyte sensor control unit |
US11235100B2 (en) | 2003-11-13 | 2022-02-01 | Icu Medical, Inc. | System for maintaining drug information and communicating with medication delivery devices |
US11000215B1 (en) | 2003-12-05 | 2021-05-11 | Dexcom, Inc. | Analyte sensor |
US11020031B1 (en) | 2003-12-05 | 2021-06-01 | Dexcom, Inc. | Analyte sensor |
US11627900B2 (en) | 2003-12-05 | 2023-04-18 | Dexcom, Inc. | Analyte sensor |
US10226207B2 (en) | 2004-12-29 | 2019-03-12 | Abbott Diabetes Care Inc. | Sensor inserter having introducer |
US11160475B2 (en) | 2004-12-29 | 2021-11-02 | Abbott Diabetes Care Inc. | Sensor inserter having introducer |
US9398882B2 (en) | 2005-09-30 | 2016-07-26 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor and data processing device |
US9775563B2 (en) | 2005-09-30 | 2017-10-03 | Abbott Diabetes Care Inc. | Integrated introducer and transmitter assembly and methods of use |
USD979766S1 (en) | 2005-09-30 | 2023-02-28 | Abbott Diabetes Care Inc. | Analyte sensor device |
US8512243B2 (en) | 2005-09-30 | 2013-08-20 | Abbott Diabetes Care Inc. | Integrated introducer and transmitter assembly and methods of use |
US9480421B2 (en) | 2005-09-30 | 2016-11-01 | Abbott Diabetes Care Inc. | Integrated introducer and transmitter assembly and methods of use |
US10342489B2 (en) | 2005-09-30 | 2019-07-09 | Abbott Diabetes Care Inc. | Integrated introducer and transmitter assembly and methods of use |
US11298058B2 (en) | 2005-12-28 | 2022-04-12 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
US10307091B2 (en) | 2005-12-28 | 2019-06-04 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
USD961778S1 (en) | 2006-02-28 | 2022-08-23 | Abbott Diabetes Care Inc. | Analyte sensor device |
US10362972B2 (en) | 2006-09-10 | 2019-07-30 | Abbott Diabetes Care Inc. | Method and system for providing an integrated analyte sensor insertion device and data processing unit |
US11194810B2 (en) | 2006-10-16 | 2021-12-07 | Icu Medical, Inc. | System and method for comparing and utilizing activity information and configuration information from multiple device management systems |
US10242060B2 (en) | 2006-10-16 | 2019-03-26 | Icu Medical, Inc. | System and method for comparing and utilizing activity information and configuration information from multiple medical device management systems |
US11724029B2 (en) | 2006-10-23 | 2023-08-15 | Abbott Diabetes Care Inc. | Flexible patch for fluid delivery and monitoring body analytes |
US10070810B2 (en) | 2006-10-23 | 2018-09-11 | Abbott Diabetes Care Inc. | Sensor insertion devices and methods of use |
US9259175B2 (en) | 2006-10-23 | 2016-02-16 | Abbott Diabetes Care, Inc. | Flexible patch for fluid delivery and monitoring body analytes |
US9788771B2 (en) | 2006-10-23 | 2017-10-17 | Abbott Diabetes Care Inc. | Variable speed sensor insertion devices and methods of use |
US10363363B2 (en) | 2006-10-23 | 2019-07-30 | Abbott Diabetes Care Inc. | Flexible patch for fluid delivery and monitoring body analytes |
US11234621B2 (en) | 2006-10-23 | 2022-02-01 | Abbott Diabetes Care Inc. | Sensor insertion devices and methods of use |
US10903914B2 (en) | 2006-10-26 | 2021-01-26 | Abbott Diabetes Care Inc. | Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors |
US11722229B2 (en) | 2006-10-26 | 2023-08-08 | Abbott Diabetes Care Inc. | Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors |
US9882660B2 (en) | 2006-10-26 | 2018-01-30 | Abbott Diabetes Care Inc. | Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors |
US10617823B2 (en) | 2007-02-15 | 2020-04-14 | Abbott Diabetes Care Inc. | Device and method for automatic data acquisition and/or detection |
US10022499B2 (en) | 2007-02-15 | 2018-07-17 | Abbott Diabetes Care Inc. | Device and method for automatic data acquisition and/or detection |
US11291763B2 (en) | 2007-03-13 | 2022-04-05 | Tandem Diabetes Care, Inc. | Basal rate testing using frequent blood glucose input |
US9804150B2 (en) | 2007-05-14 | 2017-10-31 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US11848089B2 (en) | 2007-05-24 | 2023-12-19 | Tandem Diabetes Care, Inc. | Expert system for insulin pump therapy |
US10357607B2 (en) | 2007-05-24 | 2019-07-23 | Tandem Diabetes Care, Inc. | Correction factor testing using frequent blood glucose input |
US11257580B2 (en) | 2007-05-24 | 2022-02-22 | Tandem Diabetes Care, Inc. | Expert system for insulin pump therapy |
US9474856B2 (en) | 2007-05-24 | 2016-10-25 | Tandem Diabetes Care, Inc. | Expert system for infusion pump therapy |
US10943687B2 (en) | 2007-05-24 | 2021-03-09 | Tandem Diabetes Care, Inc. | Expert system for insulin pump therapy |
US9833177B2 (en) | 2007-05-30 | 2017-12-05 | Tandem Diabetes Care, Inc. | Insulin pump based expert system |
US11576594B2 (en) | 2007-05-30 | 2023-02-14 | Tandem Diabetes Care, Inc. | Insulin pump based expert system |
US11298053B2 (en) | 2007-05-30 | 2022-04-12 | Tandem Diabetes Care, Inc. | Insulin pump based expert system |
US8834366B2 (en) | 2007-07-31 | 2014-09-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
US9398872B2 (en) | 2007-07-31 | 2016-07-26 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
US10635784B2 (en) | 2007-12-18 | 2020-04-28 | Icu Medical, Inc. | User interface improvements for medical devices |
US9320468B2 (en) | 2008-01-31 | 2016-04-26 | Abbott Diabetes Care Inc. | Analyte sensor with time lag compensation |
US9770211B2 (en) | 2008-01-31 | 2017-09-26 | Abbott Diabetes Care Inc. | Analyte sensor with time lag compensation |
WO2009126942A2 (en) | 2008-04-10 | 2009-10-15 | Abbott Diabetes Care Inc. | Method and system for sterilizing an analyte sensor |
US9795328B2 (en) | 2008-05-30 | 2017-10-24 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
US9541556B2 (en) | 2008-05-30 | 2017-01-10 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
US10327682B2 (en) | 2008-05-30 | 2019-06-25 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
US9645105B2 (en) | 2008-07-17 | 2017-05-09 | Abbott Diabetes Care Inc. | Analyte measurement devices and systems, and components and methods related thereto |
US20100064800A1 (en) * | 2008-07-17 | 2010-03-18 | Abbott Diabetes Care Inc. | Strip connectors for measurement devices |
US9417205B2 (en) | 2008-07-17 | 2016-08-16 | Abbott Diabetes Care Inc. | Analyte measurement devices and systems, and components and methods related thereto |
US9610046B2 (en) | 2008-08-31 | 2017-04-04 | Abbott Diabetes Care Inc. | Closed loop control with improved alarm functions |
US8734422B2 (en) | 2008-08-31 | 2014-05-27 | Abbott Diabetes Care Inc. | Closed loop control with improved alarm functions |
US10045739B2 (en) | 2008-09-30 | 2018-08-14 | Abbott Diabetes Care Inc. | Analyte sensor sensitivity attenuation mitigation |
US8986208B2 (en) | 2008-09-30 | 2015-03-24 | Abbott Diabetes Care Inc. | Analyte sensor sensitivity attenuation mitigation |
US10980461B2 (en) | 2008-11-07 | 2021-04-20 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US9326707B2 (en) | 2008-11-10 | 2016-05-03 | Abbott Diabetes Care Inc. | Alarm characterization for analyte monitoring devices and systems |
US11272890B2 (en) | 2008-11-10 | 2022-03-15 | Abbott Diabetes Care Inc. | Alarm characterization for analyte monitoring devices and systems |
US9730650B2 (en) | 2008-11-10 | 2017-08-15 | Abbott Diabetes Care Inc. | Alarm characterization for analyte monitoring devices and systems |
US11678848B2 (en) | 2008-11-10 | 2023-06-20 | Abbott Diabetes Care Inc. | Alarm characterization for analyte monitoring devices and systems |
US9993188B2 (en) | 2009-02-03 | 2018-06-12 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US9402544B2 (en) | 2009-02-03 | 2016-08-02 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
USD955599S1 (en) | 2009-02-03 | 2022-06-21 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
US9636068B2 (en) | 2009-02-03 | 2017-05-02 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US11213229B2 (en) | 2009-02-03 | 2022-01-04 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US10786190B2 (en) | 2009-02-03 | 2020-09-29 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US11202591B2 (en) | 2009-02-03 | 2021-12-21 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US11006870B2 (en) | 2009-02-03 | 2021-05-18 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
USD957642S1 (en) | 2009-02-03 | 2022-07-12 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
USD957643S1 (en) | 2009-02-03 | 2022-07-12 | Abbott Diabetes Care Inc. | Analyte sensor device |
US11006871B2 (en) | 2009-02-03 | 2021-05-18 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US11166656B2 (en) | 2009-02-03 | 2021-11-09 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US11006872B2 (en) | 2009-02-03 | 2021-05-18 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
USD882432S1 (en) | 2009-02-03 | 2020-04-28 | Abbott Diabetes Care Inc. | Analyte sensor on body unit |
US8965477B2 (en) | 2009-02-26 | 2015-02-24 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US10022077B2 (en) | 2009-02-26 | 2018-07-17 | Abbott Diabeetes Care Inc. | Analyte monitoring devices and methods |
US9724029B2 (en) | 2009-02-26 | 2017-08-08 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US9339229B2 (en) | 2009-02-26 | 2016-05-17 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
US9526453B2 (en) | 2009-02-26 | 2016-12-27 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
US11654237B2 (en) | 2009-04-17 | 2023-05-23 | Icu Medical, Inc. | System and method for configuring a rule set for medical event management and responses |
US11013861B2 (en) | 2009-04-17 | 2021-05-25 | Icu Medical, Inc. | System and method for configuring a rule set for medical event management and responses |
US10238801B2 (en) | 2009-04-17 | 2019-03-26 | Icu Medical, Inc. | System and method for configuring a rule set for medical event management and responses |
US9226701B2 (en) | 2009-04-28 | 2016-01-05 | Abbott Diabetes Care Inc. | Error detection in critical repeating data in a wireless sensor system |
US11872370B2 (en) | 2009-05-29 | 2024-01-16 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
US11793936B2 (en) | 2009-05-29 | 2023-10-24 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
US9795326B2 (en) | 2009-07-23 | 2017-10-24 | Abbott Diabetes Care Inc. | Continuous analyte measurement systems and systems and methods for implanting them |
US10872102B2 (en) | 2009-07-23 | 2020-12-22 | Abbott Diabetes Care Inc. | Real time management of data relating to physiological control of glucose levels |
US8798934B2 (en) | 2009-07-23 | 2014-08-05 | Abbott Diabetes Care Inc. | Real time management of data relating to physiological control of glucose levels |
US10827954B2 (en) | 2009-07-23 | 2020-11-10 | Abbott Diabetes Care Inc. | Continuous analyte measurement systems and systems and methods for implanting them |
US9211377B2 (en) | 2009-07-30 | 2015-12-15 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8287495B2 (en) | 2009-07-30 | 2012-10-16 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8298184B2 (en) | 2009-07-30 | 2012-10-30 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US11285263B2 (en) | 2009-07-30 | 2022-03-29 | Tandem Diabetes Care, Inc. | Infusion pump systems and methods |
US11135362B2 (en) | 2009-07-30 | 2021-10-05 | Tandem Diabetes Care, Inc. | Infusion pump systems and methods |
US8926561B2 (en) | 2009-07-30 | 2015-01-06 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8758323B2 (en) | 2009-07-30 | 2014-06-24 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8718965B2 (en) | 2009-07-31 | 2014-05-06 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte monitoring system calibration accuracy |
US10660554B2 (en) | 2009-07-31 | 2020-05-26 | Abbott Diabetes Care Inc. | Methods and devices for analyte monitoring calibration |
US9936910B2 (en) | 2009-07-31 | 2018-04-10 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte monitoring and therapy management system accuracy |
US11234625B2 (en) | 2009-07-31 | 2022-02-01 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte monitoring and therapy management system accuracy |
US10136816B2 (en) | 2009-08-31 | 2018-11-27 | Abbott Diabetes Care Inc. | Medical devices and methods |
US20220233110A1 (en) * | 2009-08-31 | 2022-07-28 | Abbott Diabetes Care Inc. | Displays for a medical device |
USD962446S1 (en) | 2009-08-31 | 2022-08-30 | Abbott Diabetes Care, Inc. | Analyte sensor device |
WO2011026147A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
US9314195B2 (en) | 2009-08-31 | 2016-04-19 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
US11045147B2 (en) | 2009-08-31 | 2021-06-29 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
US11635332B2 (en) | 2009-08-31 | 2023-04-25 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods for managing power and noise |
US20220233111A1 (en) * | 2009-08-31 | 2022-07-28 | Abbott Diabetes Care Inc. | Displays for a medical device |
US9968302B2 (en) | 2009-08-31 | 2018-05-15 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
US20220401041A1 (en) * | 2009-08-31 | 2022-12-22 | Abbott Diabetes Care Inc. | Displays for a medical device |
US10429250B2 (en) | 2009-08-31 | 2019-10-01 | Abbott Diabetes Care, Inc. | Analyte monitoring system and methods for managing power and noise |
US10492685B2 (en) | 2009-08-31 | 2019-12-03 | Abbott Diabetes Care Inc. | Medical devices and methods |
USD1010133S1 (en) | 2009-08-31 | 2024-01-02 | Abbott Diabetes Care Inc. | Analyte sensor assembly |
US11150145B2 (en) | 2009-08-31 | 2021-10-19 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods for managing power and noise |
US11259725B2 (en) | 2009-09-30 | 2022-03-01 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US9351669B2 (en) | 2009-09-30 | 2016-05-31 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US10765351B2 (en) | 2009-09-30 | 2020-09-08 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US9750444B2 (en) | 2009-09-30 | 2017-09-05 | Abbott Diabetes Care Inc. | Interconnect for on-body analyte monitoring device |
US11207005B2 (en) | 2009-10-30 | 2021-12-28 | Abbott Diabetes Care Inc. | Method and apparatus for detecting false hypoglycemic conditions |
US10117606B2 (en) | 2009-10-30 | 2018-11-06 | Abbott Diabetes Care Inc. | Method and apparatus for detecting false hypoglycemic conditions |
US10016559B2 (en) | 2009-12-04 | 2018-07-10 | Smiths Medical Asd, Inc. | Advanced step therapy delivery for an ambulatory infusion pump and system |
US11090432B2 (en) | 2009-12-04 | 2021-08-17 | Smiths Medical Asd, Inc. | Advanced step therapy delivery for an ambulatory infusion pump and system |
US9291591B2 (en) | 2010-01-28 | 2016-03-22 | Abbott Diabetes Care Inc. | Universal test strip port |
USD924406S1 (en) * | 2010-02-01 | 2021-07-06 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
US20230251727A1 (en) * | 2010-03-10 | 2023-08-10 | Abbott Diabetes Care Inc. | Systems, devices and methods for managing glucose levels |
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US11064922B1 (en) | 2010-03-24 | 2021-07-20 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
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US11013440B2 (en) | 2010-03-24 | 2021-05-25 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
US9186098B2 (en) | 2010-03-24 | 2015-11-17 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
US10881340B2 (en) | 2010-03-24 | 2021-01-05 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
US10292632B2 (en) | 2010-03-24 | 2019-05-21 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
US10772547B1 (en) | 2010-03-24 | 2020-09-15 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
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US8764657B2 (en) | 2010-03-24 | 2014-07-01 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
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US10285632B2 (en) | 2010-04-16 | 2019-05-14 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US9320432B2 (en) | 2010-04-16 | 2016-04-26 | Abbott Diabetes Care Inc. | Analyte meter communication module |
US9339219B2 (en) | 2010-04-22 | 2016-05-17 | Abbott Diabetes Care Inc. | Devices, systems, and methods related to analyte monitoring and management |
US9198623B2 (en) | 2010-04-22 | 2015-12-01 | Abbott Diabetes Care Inc. | Devices, systems, and methods related to analyte monitoring and management |
US10255055B2 (en) | 2010-05-24 | 2019-04-09 | Abbott Diabetes Care Inc. | Systems and methods for updating a medical device |
US11748088B2 (en) | 2010-05-24 | 2023-09-05 | Abbott Diabetes Care Inc. | Systems and methods for updating a medical device |
US11169794B2 (en) | 2010-05-24 | 2021-11-09 | Abbott Diabetes Care Inc. | Systems and methods for updating a medical device |
US9501272B2 (en) | 2010-05-24 | 2016-11-22 | Abbott Diabetes Care Inc. | Systems and methods for updating a medical device |
US11064921B2 (en) | 2010-06-29 | 2021-07-20 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
US10874338B2 (en) | 2010-06-29 | 2020-12-29 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
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US10966644B2 (en) | 2010-06-29 | 2021-04-06 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
US11478173B2 (en) | 2010-06-29 | 2022-10-25 | Abbott Diabetes Care Inc. | Calibration of analyte measurement system |
US10973449B2 (en) | 2010-06-29 | 2021-04-13 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
US10092229B2 (en) | 2010-06-29 | 2018-10-09 | Abbott Diabetes Care Inc. | Calibration of analyte measurement system |
US9572534B2 (en) | 2010-06-29 | 2017-02-21 | Abbott Diabetes Care Inc. | Devices, systems and methods for on-skin or on-body mounting of medical devices |
US10022076B2 (en) | 2010-07-28 | 2018-07-17 | Abbott Diabetes Care Inc. | Analyte sensors having temperature independent membranes |
US9662055B2 (en) | 2010-07-28 | 2017-05-30 | Abbott Diabetes Care Inc. | Analyte sensors having temperature independent membranes |
US9085790B2 (en) | 2010-07-28 | 2015-07-21 | Abbott Diabetes Care Inc. | Analyte sensors having temperature independent membranes |
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EP2624745A4 (en) * | 2010-10-07 | 2018-05-23 | Abbott Diabetes Care, Inc. | Analyte monitoring devices and methods |
WO2012048168A2 (en) | 2010-10-07 | 2012-04-12 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
US11213226B2 (en) | 2010-10-07 | 2022-01-04 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
US8475732B2 (en) | 2010-10-26 | 2013-07-02 | Abbott Diabetes Care Inc. | Analyte measurement devices and systems, and components and methods related thereto |
WO2012058237A1 (en) | 2010-10-26 | 2012-05-03 | Abbott Diabetes Care Inc. | Analyte measurement devices and systems, and components and methods related thereto |
US9952172B2 (en) | 2010-10-26 | 2018-04-24 | Abbott Diabetes Care Inc. | Analyte measurement devices and systems, and components and methods related thereto |
US8632731B2 (en) | 2010-10-26 | 2014-01-21 | Abbott Diabetes Care Inc. | Analyte measurement devices and systems, and components and methods related thereto |
US9465034B2 (en) | 2010-11-22 | 2016-10-11 | Abbott Diabetes Care Inc. | Modular analyte measurement system with extendable strip port |
US9770202B2 (en) | 2010-11-22 | 2017-09-26 | Abbott Diabetes Care Inc. | Modular analyte measurement system with extendable strip port |
US8702928B2 (en) | 2010-11-22 | 2014-04-22 | Abbott Diabetes Care Inc. | Modular analyte measurement system with extendable strip port |
US9103777B2 (en) | 2010-11-22 | 2015-08-11 | Abbott Diabetes Care Inc. | Modular analyte measurement system with extendable strip port |
US9713440B2 (en) | 2010-12-08 | 2017-07-25 | Abbott Diabetes Care Inc. | Modular analyte measurement systems, modular components thereof and related methods |
US10872696B2 (en) | 2011-02-11 | 2020-12-22 | Abbott Diabetes Care Inc. | Method of hypoglycemia risk determination |
US9760679B2 (en) | 2011-02-11 | 2017-09-12 | Abbott Diabetes Care Inc. | Data synchronization between two or more analyte detecting devices in a database |
US10923218B2 (en) | 2011-02-11 | 2021-02-16 | Abbott Diabetes Care Inc. | Data synchronization between two or more analyte detecting devices in a database |
US11017890B2 (en) * | 2011-02-11 | 2021-05-25 | Abbott Diabetes Care Inc. | Systems and methods for aggregating analyte data |
US9913599B2 (en) | 2011-02-11 | 2018-03-13 | Abbott Diabetes Care Inc. | Software applications residing on handheld analyte determining devices |
WO2012118872A3 (en) * | 2011-02-28 | 2014-04-17 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
WO2012154286A1 (en) | 2011-02-28 | 2012-11-15 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US11534089B2 (en) | 2011-02-28 | 2022-12-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
EP3583901A2 (en) | 2011-02-28 | 2019-12-25 | Abbott Diabetes Care, Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
WO2012118872A2 (en) * | 2011-02-28 | 2012-09-07 | Abbott Diabetes Care Inc. | Medical device inserters and processes of inserting and using medical devices |
US11627898B2 (en) | 2011-02-28 | 2023-04-18 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US10136845B2 (en) | 2011-02-28 | 2018-11-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US9532737B2 (en) | 2011-02-28 | 2017-01-03 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US10010273B2 (en) | 2011-03-10 | 2018-07-03 | Abbott Diabetes Care, Inc. | Multi-function analyte monitor device and methods of use |
US10610141B2 (en) | 2011-04-15 | 2020-04-07 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US10555695B2 (en) | 2011-04-15 | 2020-02-11 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US10624568B2 (en) | 2011-04-15 | 2020-04-21 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US10682084B2 (en) | 2011-04-15 | 2020-06-16 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US10722162B2 (en) | 2011-04-15 | 2020-07-28 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US10835162B2 (en) | 2011-04-15 | 2020-11-17 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US10561354B2 (en) | 2011-04-15 | 2020-02-18 | Dexcom, Inc. | Advanced analyte sensor calibration and error detection |
US11033211B2 (en) | 2011-04-20 | 2021-06-15 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods |
WO2012149466A3 (en) * | 2011-04-29 | 2013-01-03 | Proteus Biomedical, Inc. | Body associated device and method of making same |
WO2012149466A2 (en) * | 2011-04-29 | 2012-11-01 | Proteus Biomedical, Inc. | Body associated device and method of making same |
US20120302899A1 (en) * | 2011-05-25 | 2012-11-29 | Industry-Academic Cooperation Foundation, Yonsei University | Sensor and sensing method thereof |
US11571147B2 (en) | 2011-06-16 | 2023-02-07 | Abbott Diabetes Care Inc. | Temperature-compensated analyte monitoring devices, systems, and methods thereof |
EP4122384A1 (en) | 2011-06-16 | 2023-01-25 | Abbott Diabetes Care, Inc. | Temperature-compensated analyte monitoring devices, systems, and methods thereof |
US9974472B2 (en) | 2011-06-16 | 2018-05-22 | Abbott Diabetes Care Inc. | Temperature-compensated analyte monitoring devices, systems, and methods thereof |
EP3556285A1 (en) | 2011-06-16 | 2019-10-23 | Abbott Diabetes Care, Inc. | Temperature-compensated analyte monitoring devices, systems, and methods thereof |
US10028686B2 (en) | 2011-06-30 | 2018-07-24 | Abbott Diabetes Care Inc. | Methods for generating hybrid analyte level output, and devices and systems related thereto |
US9289164B2 (en) | 2011-06-30 | 2016-03-22 | Abbott Diabetes Care Inc. | Methods for generating hybrid analyte level output, and devices and systems related thereto |
US11004035B2 (en) | 2011-08-19 | 2021-05-11 | Icu Medical, Inc. | Systems and methods for a graphical interface including a graphical representation of medical data |
US11599854B2 (en) | 2011-08-19 | 2023-03-07 | Icu Medical, Inc. | Systems and methods for a graphical interface including a graphical representation of medical data |
US10430761B2 (en) | 2011-08-19 | 2019-10-01 | Icu Medical, Inc. | Systems and methods for a graphical interface including a graphical representation of medical data |
EP2751577A1 (en) * | 2011-08-30 | 2014-07-09 | Glumetrics, Inc. | Information storage for sterilized analyte sensor |
EP2751577A4 (en) * | 2011-08-30 | 2015-03-11 | Glumetrics Inc | Information storage for sterilized analyte sensor |
WO2013033076A1 (en) * | 2011-08-30 | 2013-03-07 | Glumetrics, Inc. | Information storage for sterilized analyte sensor |
EP4060673A1 (en) | 2011-09-28 | 2022-09-21 | Abbott Diabetes Care, Inc. | Methods, devices and systems for analyte monitoring management |
EP3381360A1 (en) | 2011-09-28 | 2018-10-03 | Abbott Diabetes Care, Inc. | Methods, devices and systems for analyte monitoring management |
US10945646B2 (en) | 2011-09-28 | 2021-03-16 | Abbott Diabetes Care Inc. | Methods for analyte monitoring management and analyte measurement data management, and articles of manufacture related thereto |
EP3689235A1 (en) | 2011-09-28 | 2020-08-05 | Abbott Diabetes Care, Inc. | Methods for analyte monitoring management and analyte measurement data management, and articles of manufacture related thereto |
US9622689B2 (en) | 2011-09-28 | 2017-04-18 | Abbott Diabetes Care Inc. | Methods for analyte monitoring management and analyte measurement data management, and articles of manufacture related thereto |
US11832973B2 (en) | 2011-09-28 | 2023-12-05 | Abbott Diabetes Care Inc. | Methods for analyte monitoring management and analyte measurement data management, and articles of manufacture related thereto |
US11087868B2 (en) | 2011-09-28 | 2021-08-10 | Abbott Diabetes Care Inc. | Methods, devices and systems for analyte monitoring management |
US9971871B2 (en) | 2011-10-21 | 2018-05-15 | Icu Medical, Inc. | Medical device update system |
US11626205B2 (en) | 2011-10-21 | 2023-04-11 | Icu Medical, Inc. | Medical device update system |
USD680454S1 (en) | 2011-10-25 | 2013-04-23 | Abbott Diabetes Care Inc. | Analyte meter and strip port |
US9622691B2 (en) | 2011-10-31 | 2017-04-18 | Abbott Diabetes Care Inc. | Model based variable risk false glucose threshold alarm prevention mechanism |
US11406331B2 (en) | 2011-10-31 | 2022-08-09 | Abbott Diabetes Care Inc. | Model based variable risk false glucose threshold alarm prevention mechanism |
US9465420B2 (en) | 2011-10-31 | 2016-10-11 | Abbott Diabetes Care Inc. | Electronic devices having integrated reset systems and methods thereof |
US9069536B2 (en) | 2011-10-31 | 2015-06-30 | Abbott Diabetes Care Inc. | Electronic devices having integrated reset systems and methods thereof |
US9913619B2 (en) | 2011-10-31 | 2018-03-13 | Abbott Diabetes Care Inc. | Model based variable risk false glucose threshold alarm prevention mechanism |
WO2013070794A2 (en) | 2011-11-07 | 2013-05-16 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US9743872B2 (en) | 2011-11-23 | 2017-08-29 | Abbott Diabetes Care Inc. | Mitigating single point failure of devices in an analyte monitoring system and methods thereof |
US11205511B2 (en) | 2011-11-23 | 2021-12-21 | Abbott Diabetes Care Inc. | Compatibility mechanisms for devices in a continuous analyte monitoring system and methods thereof |
US10136847B2 (en) | 2011-11-23 | 2018-11-27 | Abbott Diabetes Care Inc. | Mitigating single point failure of devices in an analyte monitoring system and methods thereof |
US8710993B2 (en) | 2011-11-23 | 2014-04-29 | Abbott Diabetes Care Inc. | Mitigating single point failure of devices in an analyte monitoring system and methods thereof |
US10939859B2 (en) | 2011-11-23 | 2021-03-09 | Abbott Diabetes Care Inc. | Mitigating single point failure of devices in an analyte monitoring system and methods thereof |
US9289179B2 (en) | 2011-11-23 | 2016-03-22 | Abbott Diabetes Care Inc. | Mitigating single point failure of devices in an analyte monitoring system and methods thereof |
US11783941B2 (en) | 2011-11-23 | 2023-10-10 | Abbott Diabetes Care Inc. | Compatibility mechanisms for devices in a continuous analyte monitoring system and methods thereof |
US9721063B2 (en) | 2011-11-23 | 2017-08-01 | Abbott Diabetes Care Inc. | Compatibility mechanisms for devices in a continuous analyte monitoring system and methods thereof |
US8887911B2 (en) | 2011-12-09 | 2014-11-18 | Abbott Diabetes Care Inc. | Packages and kits for analyte monitoring devices, and methods related thereto |
US11051725B2 (en) | 2011-12-11 | 2021-07-06 | Abbott Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
US11179068B2 (en) | 2011-12-11 | 2021-11-23 | Abbott Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
US11051724B2 (en) | 2011-12-11 | 2021-07-06 | Abbott Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
EP3300658A1 (en) | 2011-12-11 | 2018-04-04 | Abbott Diabetes Care, Inc. | Analyte sensor methods |
US9693713B2 (en) | 2011-12-11 | 2017-07-04 | Abbott Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
EP4056105A1 (en) | 2011-12-11 | 2022-09-14 | Abbott Diabetes Care, Inc. | Analyte sensor devices |
US9931066B2 (en) | 2011-12-11 | 2018-04-03 | Abbott Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
USD915601S1 (en) | 2011-12-11 | 2021-04-06 | Abbott Diabetes Care Inc. | Analyte sensor device |
EP3831283A1 (en) | 2011-12-11 | 2021-06-09 | Abbott Diabetes Care, Inc. | Analyte sensor devices, connections, and methods |
USD915602S1 (en) | 2011-12-11 | 2021-04-06 | Abbott Diabetes Care Inc. | Analyte sensor device |
USD903877S1 (en) | 2011-12-11 | 2020-12-01 | Abbott Diabetes Care Inc. | Analyte sensor device |
US9402570B2 (en) | 2011-12-11 | 2016-08-02 | Abbott Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
WO2013090215A2 (en) | 2011-12-11 | 2013-06-20 | Abbot Diabetes Care Inc. | Analyte sensor devices, connections, and methods |
US20130158504A1 (en) * | 2011-12-16 | 2013-06-20 | Timothy L. Ruchti | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
US11376361B2 (en) | 2011-12-16 | 2022-07-05 | Icu Medical, Inc. | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
US10022498B2 (en) * | 2011-12-16 | 2018-07-17 | Icu Medical, Inc. | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
WO2013102158A1 (en) | 2011-12-30 | 2013-07-04 | Abbott Diabetes Care Inc. | Method and apparatus for determining medication dose information |
US10578474B2 (en) | 2012-03-30 | 2020-03-03 | Icu Medical, Inc. | Air detection system and method for detecting air in a pump of an infusion system |
US9995611B2 (en) | 2012-03-30 | 2018-06-12 | Icu Medical, Inc. | Air detection system and method for detecting air in a pump of an infusion system |
WO2013163342A1 (en) | 2012-04-24 | 2013-10-31 | Abbott Diabetes Care Inc. | Methods of lag-compensation for analyte measurements, and devices related thereto |
US10561372B2 (en) | 2012-04-24 | 2020-02-18 | Abbott Diabetes Care Inc. | Methods of lag-compensation for analyte measurements, and devices related thereto |
EP3777664A1 (en) | 2012-04-24 | 2021-02-17 | Abbott Diabetes Care, Inc. | Methods of lag-compensation for analyte measurements, and devices related thereto thereto |
US9462970B2 (en) | 2012-04-24 | 2016-10-11 | Abbott Diabetes Care Inc. | Methods of lag-compensation for analyte measurements, and devices related thereto |
US10258736B2 (en) | 2012-05-17 | 2019-04-16 | Tandem Diabetes Care, Inc. | Systems including vial adapter for fluid transfer |
US20150172790A1 (en) * | 2012-07-26 | 2015-06-18 | Consejo Superior Investigacion | Wireless telemetry system for the monitoring of static and dynamic magnitudes |
US10463788B2 (en) | 2012-07-31 | 2019-11-05 | Icu Medical, Inc. | Patient care system for critical medications |
US11623042B2 (en) | 2012-07-31 | 2023-04-11 | Icu Medical, Inc. | Patient care system for critical medications |
US10132793B2 (en) | 2012-08-30 | 2018-11-20 | Abbott Diabetes Care Inc. | Dropout detection in continuous analyte monitoring data during data excursions |
US10942164B2 (en) | 2012-08-30 | 2021-03-09 | Abbott Diabetes Care Inc. | Dropout detection in continuous analyte monitoring data during data excursions |
US10345291B2 (en) | 2012-08-30 | 2019-07-09 | Abbott Diabetes Care Inc. | Dropout detection in continuous analyte monitoring data during data excursions |
US10656139B2 (en) | 2012-08-30 | 2020-05-19 | Abbott Diabetes Care Inc. | Dropout detection in continuous analyte monitoring data during data excursions |
US9968306B2 (en) | 2012-09-17 | 2018-05-15 | Abbott Diabetes Care Inc. | Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems |
US11612363B2 (en) | 2012-09-17 | 2023-03-28 | Abbott Diabetes Care Inc. | Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems |
US10006880B2 (en) | 2012-09-21 | 2018-06-26 | Abbott Diabetes Care Inc. | Test strips having ceria nanoparticle electrodes |
US10004439B2 (en) | 2012-09-21 | 2018-06-26 | Abbott Diabetes Care Inc. | In vivo sensors having ceria nanoparticle electrodes |
US10842420B2 (en) | 2012-09-26 | 2020-11-24 | Abbott Diabetes Care Inc. | Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data |
US9907492B2 (en) | 2012-09-26 | 2018-03-06 | Abbott Diabetes Care Inc. | Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data |
US11896371B2 (en) | 2012-09-26 | 2024-02-13 | Abbott Diabetes Care Inc. | Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data |
US9675290B2 (en) | 2012-10-30 | 2017-06-13 | Abbott Diabetes Care Inc. | Sensitivity calibration of in vivo sensors used to measure analyte concentration |
US10188334B2 (en) | 2012-10-30 | 2019-01-29 | Abbott Diabetes Care Inc. | Sensitivity calibration of in vivo sensors used to measure analyte concentration |
US9801577B2 (en) | 2012-10-30 | 2017-10-31 | Abbott Diabetes Care Inc. | Sensitivity calibration of in vivo sensors used to measure analyte concentration |
US11850020B2 (en) | 2012-12-31 | 2023-12-26 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US10856736B2 (en) | 2012-12-31 | 2020-12-08 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US11744463B2 (en) | 2012-12-31 | 2023-09-05 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US11382508B2 (en) | 2012-12-31 | 2022-07-12 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US11160452B2 (en) | 2012-12-31 | 2021-11-02 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US10993617B2 (en) | 2012-12-31 | 2021-05-04 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US10869599B2 (en) | 2012-12-31 | 2020-12-22 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US11109757B2 (en) | 2012-12-31 | 2021-09-07 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US10860687B2 (en) | 2012-12-31 | 2020-12-08 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US11213204B2 (en) | 2012-12-31 | 2022-01-04 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US10333843B2 (en) | 2013-03-06 | 2019-06-25 | Icu Medical, Inc. | Medical device communication method |
US11470000B2 (en) | 2013-03-06 | 2022-10-11 | Icu Medical, Inc. | Medical device communication method |
US10357606B2 (en) | 2013-03-13 | 2019-07-23 | Tandem Diabetes Care, Inc. | System and method for integration of insulin pumps and continuous glucose monitoring |
US11607492B2 (en) | 2013-03-13 | 2023-03-21 | Tandem Diabetes Care, Inc. | System and method for integration and display of data of insulin pumps and continuous glucose monitoring |
US20150045641A1 (en) * | 2013-03-13 | 2015-02-12 | Optiscan Biomedical Corporation | Method and apparatus for analyte measurement, display, and annotation |
US11677443B1 (en) | 2013-03-14 | 2023-06-13 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US9788354B2 (en) | 2013-03-14 | 2017-10-10 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US9962486B2 (en) | 2013-03-14 | 2018-05-08 | Tandem Diabetes Care, Inc. | System and method for detecting occlusions in an infusion pump |
US9681807B2 (en) | 2013-03-14 | 2017-06-20 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US10985804B2 (en) | 2013-03-14 | 2021-04-20 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US9931037B2 (en) | 2013-03-14 | 2018-04-03 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US9445445B2 (en) | 2013-03-14 | 2016-09-13 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US9931036B2 (en) | 2013-03-14 | 2018-04-03 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US10874336B2 (en) | 2013-03-15 | 2020-12-29 | Abbott Diabetes Care Inc. | Multi-rate analyte sensor data collection with sample rate configurable signal processing |
US9486171B2 (en) | 2013-03-15 | 2016-11-08 | Tandem Diabetes Care, Inc. | Predictive calibration |
US11776689B2 (en) | 2013-03-15 | 2023-10-03 | Tandem Diabetes Care, Inc. | Field update of an ambulatory infusion pump system |
US11152115B2 (en) | 2013-03-15 | 2021-10-19 | Tandem Diabetes Care, Inc. | Field update of an ambulatory infusion pump system |
US9474475B1 (en) | 2013-03-15 | 2016-10-25 | Abbott Diabetes Care Inc. | Multi-rate analyte sensor data collection with sample rate configurable signal processing |
US9895491B2 (en) | 2013-03-15 | 2018-02-20 | Tandem Diabeters Care, Inc. | Field update of an ambulatory infusion pump system |
US10456524B2 (en) | 2013-03-15 | 2019-10-29 | Tandem Diabetes Care, Inc. | Field update of an ambulatory infusion pump system |
US10433773B1 (en) | 2013-03-15 | 2019-10-08 | Abbott Diabetes Care Inc. | Noise rejection methods and apparatus for sparsely sampled analyte sensor data |
US11049614B2 (en) | 2013-03-15 | 2021-06-29 | Tandem Diabetes Care, Inc. | Field update of an ambulatory infusion pump system |
WO2014145049A2 (en) | 2013-03-15 | 2014-09-18 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US10076285B2 (en) | 2013-03-15 | 2018-09-18 | Abbott Diabetes Care Inc. | Sensor fault detection using analyte sensor data pattern comparison |
US11207006B2 (en) | 2013-04-30 | 2021-12-28 | Abbott Diabetes Care Inc. | Systems, devices, and methods for energy efficient electrical device activation |
US10213141B2 (en) | 2013-04-30 | 2019-02-26 | Abbott Diabetes Care Inc. | Systems, devices, and methods for energy efficient electrical device activation |
US11571149B1 (en) | 2013-04-30 | 2023-02-07 | Abbott Diabetes Care Inc. | Systems, devices, and methods for energy efficient electrical device activation |
US10046112B2 (en) | 2013-05-24 | 2018-08-14 | Icu Medical, Inc. | Multi-sensor infusion system for detecting air or an occlusion in the infusion system |
US10874793B2 (en) | 2013-05-24 | 2020-12-29 | Icu Medical, Inc. | Multi-sensor infusion system for detecting air or an occlusion in the infusion system |
US10166328B2 (en) | 2013-05-29 | 2019-01-01 | Icu Medical, Inc. | Infusion system which utilizes one or more sensors and additional information to make an air determination regarding the infusion system |
US11596737B2 (en) | 2013-05-29 | 2023-03-07 | Icu Medical, Inc. | Infusion system and method of use which prevents over-saturation of an analog-to-digital converter |
US11433177B2 (en) | 2013-05-29 | 2022-09-06 | Icu Medical, Inc. | Infusion system which utilizes one or more sensors and additional information to make an air determination regarding the infusion system |
US10596316B2 (en) | 2013-05-29 | 2020-03-24 | Icu Medical, Inc. | Infusion system and method of use which prevents over-saturation of an analog-to-digital converter |
US11324898B2 (en) | 2013-06-21 | 2022-05-10 | Tandem Diabetes Care, Inc. | System and method for infusion set dislodgement detection |
US20150130628A1 (en) * | 2013-07-22 | 2015-05-14 | Center For Integrated Smart Sensors Foundation | Nfc or rfid based bio sensor measurement device and measuring method using the same |
CN105451792A (en) * | 2013-08-05 | 2016-03-30 | 欧文蒙福德有限公司 | Injection devices |
US10936832B2 (en) * | 2013-08-22 | 2021-03-02 | Verily Life Sciences Llc | Using unique identifiers to retrieve configuration data for tag devices |
US20160117532A1 (en) * | 2013-08-22 | 2016-04-28 | Verily Life Sciences Llc | Using Unique Identifiers to Retrieve Configuration Data for Tag Devices |
US10599888B2 (en) * | 2013-08-22 | 2020-03-24 | Verily Life Sciences Llc | Using unique identifiers to retrieve configuration data for tag devices |
US11571508B2 (en) | 2013-08-30 | 2023-02-07 | Icu Medical, Inc. | System and method of monitoring and managing a remote infusion regimen |
US10765799B2 (en) | 2013-09-20 | 2020-09-08 | Icu Medical, Inc. | Fail-safe drug infusion therapy system |
WO2015069563A1 (en) | 2013-11-05 | 2015-05-14 | Abbott Diabetes Care Inc. | Systems, devices, and methods for control of a power supply connection |
US9590438B2 (en) | 2013-11-05 | 2017-03-07 | Abbott Diabetes Care Inc. | Systems, devices, and methods for control of a power supply connection |
US10361574B2 (en) | 2013-11-05 | 2019-07-23 | Abbott Diabetes Care Inc. | Systems, devices, and methods for control of a power supply connection |
US10311972B2 (en) | 2013-11-11 | 2019-06-04 | Icu Medical, Inc. | Medical device system performance index |
US11501877B2 (en) | 2013-11-11 | 2022-11-15 | Icu Medical, Inc. | Medical device system performance index |
US11763927B2 (en) | 2013-11-19 | 2023-09-19 | Icu Medical, Inc. | Infusion pump automation system and method |
US10042986B2 (en) | 2013-11-19 | 2018-08-07 | Icu Medical, Inc. | Infusion pump automation system and method |
US11037668B2 (en) | 2013-11-19 | 2021-06-15 | Icu Medical, Inc. | Infusion pump automation system and method |
US11229382B2 (en) | 2013-12-31 | 2022-01-25 | Abbott Diabetes Care Inc. | Self-powered analyte sensor and devices using the same |
US20160008664A1 (en) * | 2014-01-13 | 2016-01-14 | Skye Health, Inc. | Methods and devices for sensing, guiding, and/or tracking pelvic exercise |
US11167171B2 (en) | 2014-01-13 | 2021-11-09 | Skye Health, Inc. | Device and method for sensing, guiding, and/or tracking pelvic exercise |
US11324999B2 (en) * | 2014-01-13 | 2022-05-10 | Skye Health, Inc. | Methods and devices for sensing, guiding, and/or tracking pelvic exercise |
US10342917B2 (en) | 2014-02-28 | 2019-07-09 | Icu Medical, Inc. | Infusion system and method which utilizes dual wavelength optical air-in-line detection |
US20150265203A1 (en) * | 2014-03-20 | 2015-09-24 | Mark McConkie | Monitoring Antepartum Conditions Using a Smart Phone |
US11717225B2 (en) | 2014-03-30 | 2023-08-08 | Abbott Diabetes Care Inc. | Method and apparatus for determining meal start and peak events in analyte monitoring systems |
US20150292856A1 (en) * | 2014-04-09 | 2015-10-15 | Qualcomm Incorporated | Method, devices and systems for detecting an attachment of an electronic patch |
US9459089B2 (en) * | 2014-04-09 | 2016-10-04 | Qualcomm Incorporated | Method, devices and systems for detecting an attachment of an electronic patch |
US10898641B2 (en) | 2014-04-30 | 2021-01-26 | Icu Medical, Inc. | Patient care system with conditional alarm forwarding |
US11628246B2 (en) | 2014-04-30 | 2023-04-18 | Icu Medical, Inc. | Patient care system with conditional alarm forwarding |
US10452875B2 (en) | 2014-05-22 | 2019-10-22 | Avery Dennison Retail Information Services, Llc | Using RFID devices integrated or included in the packaging of medical devices to facilitate a secure and authorized pairing with a host system |
US11344673B2 (en) | 2014-05-29 | 2022-05-31 | Icu Medical, Inc. | Infusion system and pump with configurable closed loop delivery rate catch-up |
US11628254B2 (en) | 2014-06-16 | 2023-04-18 | Icu Medical, Inc. | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
US9724470B2 (en) | 2014-06-16 | 2017-08-08 | Icu Medical, Inc. | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
US10314974B2 (en) | 2014-06-16 | 2019-06-11 | Icu Medical, Inc. | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
US10646651B2 (en) | 2014-06-16 | 2020-05-12 | Icu Medical, Inc. | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
US20160034658A1 (en) * | 2014-07-31 | 2016-02-04 | Abbott Diabetes Care Inc. | Safety mitigations for hosting a safety critical application on an uncontrolled data processing device |
US10939858B2 (en) | 2014-08-06 | 2021-03-09 | Roche Diabetes Care, Inc. | Medical device and method for producing a medical device |
US9775549B2 (en) | 2014-08-15 | 2017-10-03 | Abbott Diabetes Care Inc. | Temperature insensitive in vivo analyte devices, methods and systems |
US11574721B2 (en) | 2014-09-15 | 2023-02-07 | Icu Medical, Inc. | Matching delayed infusion auto-programs with manually entered infusion programs |
US11289183B2 (en) | 2014-09-15 | 2022-03-29 | Icu Medical, Inc. | Matching delayed infusion auto-programs with manually entered infusion programs |
US10238799B2 (en) | 2014-09-15 | 2019-03-26 | Icu Medical, Inc. | Matching delayed infusion auto-programs with manually entered infusion programs |
US10799632B2 (en) | 2014-09-15 | 2020-10-13 | Icu Medical, Inc. | Matching delayed infusion auto-programs with manually entered infusion programs |
US11300537B2 (en) | 2014-10-23 | 2022-04-12 | Abbott Diabetes Care Inc. | Electrodes having at least one sensing structure and methods for making and using the same |
US10598624B2 (en) | 2014-10-23 | 2020-03-24 | Abbott Diabetes Care Inc. | Electrodes having at least one sensing structure and methods for making and using the same |
US9974471B1 (en) * | 2014-10-24 | 2018-05-22 | Verily Life Sciences Llc | Analyte detection system and method for intradermal implantation of biocompatible optode nanosensors |
EP3207871A4 (en) * | 2014-10-27 | 2018-05-23 | Shenzhen Waveguider Optical Telecom Technology Inc. | Continuous glucose collecting apparatus and main machine |
US20160170532A1 (en) * | 2014-12-15 | 2016-06-16 | Nxp B.V. | User interface unit, electronic device and manufacturing method |
US9916053B2 (en) * | 2014-12-15 | 2018-03-13 | Nxp B.V. | User interface unit, electronic device and manufacturing method |
US11344668B2 (en) | 2014-12-19 | 2022-05-31 | Icu Medical, Inc. | Infusion system with concurrent TPN/insulin infusion |
US10251605B2 (en) | 2015-02-16 | 2019-04-09 | Verily Life Sciences Llc | Bandage type of continuous glucose monitoring system |
WO2016133778A1 (en) * | 2015-02-16 | 2016-08-25 | Verily Life Sciences Llc | Bandage type of continuous glucose monitoring system |
US10850024B2 (en) | 2015-03-02 | 2020-12-01 | Icu Medical, Inc. | Infusion system, device, and method having advanced infusion features |
US9949642B2 (en) | 2015-05-14 | 2018-04-24 | Abbott Diabetes Care Inc. | Systems, devices, and methods for monitoring medical devices |
US10674944B2 (en) | 2015-05-14 | 2020-06-09 | Abbott Diabetes Care Inc. | Compact medical device inserters and related systems and methods |
US10213139B2 (en) | 2015-05-14 | 2019-02-26 | Abbott Diabetes Care Inc. | Systems, devices, and methods for assembling an applicator and sensor control device |
USD980986S1 (en) | 2015-05-14 | 2023-03-14 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
US11605468B2 (en) | 2015-05-26 | 2023-03-14 | Icu Medical, Inc. | Infusion pump system and method with multiple drug library editor source capability |
US10292630B2 (en) | 2015-06-01 | 2019-05-21 | Verily Life Sciences Llc | Optical sensor for bandage type monitoring device |
US9914952B2 (en) | 2015-06-15 | 2018-03-13 | Abbott Diabetes Care, Inc. | Stabilized lactate responsive enzymes, electrodes and sensors, and methods for making and using the same |
WO2016205378A1 (en) | 2015-06-15 | 2016-12-22 | Abbott Diabetes Care Inc. | Stabilized lactate responsive enzymes, electrodes and sensors, and methods for making and using the same |
EP3967227A1 (en) | 2015-06-15 | 2022-03-16 | Abbott Diabetes Care Inc. | Stabilized lactate responsive enzymes, electrodes and sensors, and methods for making and using the same |
US10888272B2 (en) | 2015-07-10 | 2021-01-12 | Abbott Diabetes Care Inc. | Systems, devices, and methods for meal information collection, meal assessment, and analyte data correlation |
US11553883B2 (en) | 2015-07-10 | 2023-01-17 | Abbott Diabetes Care Inc. | System, device and method of dynamic glucose profile response to physiological parameters |
US10932672B2 (en) | 2015-12-28 | 2021-03-02 | Dexcom, Inc. | Systems and methods for remote and host monitoring communications |
US11399721B2 (en) | 2015-12-28 | 2022-08-02 | Dexcom, Inc. | Systems and methods for remote and host monitoring communications |
US11638781B2 (en) | 2015-12-29 | 2023-05-02 | Tandem Diabetes Care, Inc. | System and method for switching between closed loop and open loop control of an ambulatory infusion pump |
US10569016B2 (en) | 2015-12-29 | 2020-02-25 | Tandem Diabetes Care, Inc. | System and method for switching between closed loop and open loop control of an ambulatory infusion pump |
EP3207870A1 (en) * | 2016-02-16 | 2017-08-23 | Roche Diabetes Care GmbH | Body-mountable device, medical sensor assembly and method of use |
WO2017140763A1 (en) * | 2016-02-16 | 2017-08-24 | Roche Diabetes Care Gmbh | Body-mountable device, medical sensor assembly and method of use |
US11470069B2 (en) | 2016-02-26 | 2022-10-11 | Tandem Diabetes Care, Inc. | Web browser-based device communication workflow |
US10541987B2 (en) | 2016-02-26 | 2020-01-21 | Tandem Diabetes Care, Inc. | Web browser-based device communication workflow |
WO2017151952A1 (en) | 2016-03-04 | 2017-09-08 | Abbott Diabetes Care Inc. | Nad(p)-dependent responsive enzymes, electrodes and sensors, and methods for making and using the same |
EP4325222A2 (en) | 2016-03-04 | 2024-02-21 | Abbott Diabetes Care Inc. | Nad(p)-dependent responsive enzymes, electrodes and sensors, and methods for making and using the same |
WO2017153506A1 (en) * | 2016-03-11 | 2017-09-14 | Roche Diabetes Care Gmbh | Analyte measuring patch |
EP3216395A1 (en) * | 2016-03-11 | 2017-09-13 | Roche Diabetes Care GmbH | Analyte measuring patch |
US10881335B2 (en) | 2016-03-31 | 2021-01-05 | Dexcom, Inc. | Systems and methods for display device and sensor electronics unit communication |
US10980450B2 (en) | 2016-03-31 | 2021-04-20 | Dexcom, Inc. | Systems and methods for display device and sensor electronics unit communication |
US10980451B2 (en) | 2016-03-31 | 2021-04-20 | Dexcom, Inc. | Systems and methods for display device and sensor electronics unit communication |
US10980453B2 (en) | 2016-03-31 | 2021-04-20 | Dexcom, Inc. | Systems and methods for display device and sensor electronics unit communication |
US10765369B2 (en) | 2016-04-08 | 2020-09-08 | Medtronic Minimed, Inc. | Analyte sensor |
US10631787B2 (en) | 2016-04-08 | 2020-04-28 | Medtronic Minimed, Inc. | Sensor and transmitter product |
US10420508B2 (en) | 2016-04-08 | 2019-09-24 | Medtronic Minimed, Inc. | Sensor connections |
WO2017176802A1 (en) * | 2016-04-08 | 2017-10-12 | Medtronic Minimed, Inc. | Analyte sensor |
US10765348B2 (en) | 2016-04-08 | 2020-09-08 | Medtronic Minimed, Inc. | Sensor and transmitter product |
US10413183B2 (en) | 2016-04-08 | 2019-09-17 | Medtronic Minimed, Inc. | Insertion device |
US11547357B2 (en) | 2016-04-08 | 2023-01-10 | Medtronic Minimed, Inc. | Insertion device |
US11677134B2 (en) | 2016-04-15 | 2023-06-13 | BR Invention Holding, LLC | Mobile medicine communication platform and methods and uses thereof |
AU2017250805B2 (en) * | 2016-04-15 | 2018-11-08 | BR Invention Holding, LLC | Mobile medicine communication platform and methods and uses thereof |
AU2019200312B2 (en) * | 2016-04-15 | 2019-04-04 | BR Invention Holding, LLC | Mobile medicine communication platform and methods and uses thereof |
US10534894B2 (en) | 2016-04-15 | 2020-01-14 | BR Invention Holding, LLC | Mobile medicine communication platform and methods and uses thereof |
WO2017181029A1 (en) * | 2016-04-15 | 2017-10-19 | BR Invention Holding, LLC | Mobile medicine communication platform and methods and uses thereof |
US11246985B2 (en) | 2016-05-13 | 2022-02-15 | Icu Medical, Inc. | Infusion pump system and method with common line auto flush |
US11324888B2 (en) | 2016-06-10 | 2022-05-10 | Icu Medical, Inc. | Acoustic flow sensor for continuous medication flow measurements and feedback control of infusion |
US10498569B2 (en) * | 2016-06-23 | 2019-12-03 | University Of Massachusetts | Systems and methods for backscatter communication |
US20170373892A1 (en) * | 2016-06-23 | 2017-12-28 | University Of Massachusetts | Systems and methods for backscatter communication |
US11574737B2 (en) | 2016-07-14 | 2023-02-07 | Icu Medical, Inc. | Multi-communication path selection and security system for a medical device |
US10455816B2 (en) * | 2016-07-20 | 2019-10-29 | International Business Machines Corporation | Sensor based activity monitor |
US11642054B2 (en) * | 2016-11-29 | 2023-05-09 | Dexcom, Inc. | Wire-assembly apparatus for invasive biosensors |
US20180146894A1 (en) * | 2016-11-29 | 2018-05-31 | Verily Life Sciences Llc | Wire-assembly apparatus for invasive biosensors |
US10702198B2 (en) * | 2016-11-29 | 2020-07-07 | Dexcom, Inc. | Wire-assembly apparatus for invasive biosensors |
US11071478B2 (en) | 2017-01-23 | 2021-07-27 | Abbott Diabetes Care Inc. | Systems, devices and methods for analyte sensor insertion |
US11596330B2 (en) | 2017-03-21 | 2023-03-07 | Abbott Diabetes Care Inc. | Methods, devices and system for providing diabetic condition diagnosis and therapy |
JP2020517333A (en) * | 2017-04-19 | 2020-06-18 | メトロノーム・ヘルス、インコーポレイテッド | Sample sensor inserter |
US11706876B2 (en) | 2017-10-24 | 2023-07-18 | Dexcom, Inc. | Pre-connected analyte sensors |
US11382540B2 (en) | 2017-10-24 | 2022-07-12 | Dexcom, Inc. | Pre-connected analyte sensors |
US11350862B2 (en) | 2017-10-24 | 2022-06-07 | Dexcom, Inc. | Pre-connected analyte sensors |
US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
US11203139B2 (en) | 2017-12-13 | 2021-12-21 | Becton, Dickinson And Company | Medical device with overmolded adhesive patch and method for making same |
US10656894B2 (en) | 2017-12-27 | 2020-05-19 | Icu Medical, Inc. | Synchronized display of screen content on networked devices |
US11868161B2 (en) | 2017-12-27 | 2024-01-09 | Icu Medical, Inc. | Synchronized display of screen content on networked devices |
US11029911B2 (en) | 2017-12-27 | 2021-06-08 | Icu Medical, Inc. | Synchronized display of screen content on networked devices |
EP3764465A4 (en) * | 2018-03-07 | 2021-05-05 | PHC Holdings Corporation | Communication device |
US11296731B2 (en) * | 2018-03-07 | 2022-04-05 | Phc Holdings Corporation | Communication device |
US11109121B2 (en) * | 2018-05-10 | 2021-08-31 | Physio-Control, Inc. | Systems and methods of secure communication of data from medical devices |
US11792554B2 (en) | 2018-05-10 | 2023-10-17 | Physio-Control, Inc. | Systems and methods of secure communication of data from medical devices |
JP2022503393A (en) * | 2018-06-07 | 2022-01-12 | アボット ダイアベティス ケア インコーポレイテッド | Centralized sterile and sterile subassembly for specimen monitoring systems |
JP2022503395A (en) * | 2018-06-07 | 2022-01-12 | アボット ダイアベティス ケア インコーポレイテッド | Centralized sterile and sterile subassembly for specimen monitoring systems |
JP7210614B2 (en) | 2018-06-07 | 2023-01-23 | アボット ダイアベティス ケア インコーポレイテッド | Centralized Sterilization and Aseptic Subassemblies for Specimen Monitoring Systems |
JP2022503394A (en) * | 2018-06-07 | 2022-01-12 | アボット ダイアベティス ケア インコーポレイテッド | Centralized sterile and sterile subassembly for specimen monitoring systems |
US11152108B2 (en) | 2018-07-17 | 2021-10-19 | Icu Medical, Inc. | Passing authentication token to authorize access to rest calls via web sockets |
US11152110B2 (en) | 2018-07-17 | 2021-10-19 | Icu Medical, Inc. | Tagging pump messages with identifiers that facilitate restructuring |
US10964428B2 (en) | 2018-07-17 | 2021-03-30 | Icu Medical, Inc. | Merging messages into cache and generating user interface using the cache |
US11328804B2 (en) | 2018-07-17 | 2022-05-10 | Icu Medical, Inc. | Health checks for infusion pump communications systems |
US11328805B2 (en) | 2018-07-17 | 2022-05-10 | Icu Medical, Inc. | Reducing infusion pump network congestion by staggering updates |
US11670416B2 (en) | 2018-07-17 | 2023-06-06 | Icu Medical, Inc. | Tagging pump messages with identifiers that facilitate restructuring |
US11587669B2 (en) | 2018-07-17 | 2023-02-21 | Icu Medical, Inc. | Passing authentication token to authorize access to rest calls via web sockets |
US10950339B2 (en) | 2018-07-17 | 2021-03-16 | Icu Medical, Inc. | Converting pump messages in new pump protocol to standardized dataset messages |
US11483403B2 (en) | 2018-07-17 | 2022-10-25 | Icu Medical, Inc. | Maintaining clinical messaging during network instability |
US11923076B2 (en) | 2018-07-17 | 2024-03-05 | Icu Medical, Inc. | Converting pump messages in new pump protocol to standardized dataset messages |
US11152109B2 (en) | 2018-07-17 | 2021-10-19 | Icu Medical, Inc. | Detecting missing messages from clinical environment |
US11594326B2 (en) | 2018-07-17 | 2023-02-28 | Icu Medical, Inc. | Detecting missing messages from clinical environment |
US11783935B2 (en) | 2018-07-17 | 2023-10-10 | Icu Medical, Inc. | Health checks for infusion pump communications systems |
US11483402B2 (en) | 2018-07-17 | 2022-10-25 | Icu Medical, Inc. | Maintaining clinical messaging during an internet outage |
US11139058B2 (en) | 2018-07-17 | 2021-10-05 | Icu Medical, Inc. | Reducing file transfer between cloud environment and infusion pumps |
US10741280B2 (en) | 2018-07-17 | 2020-08-11 | Icu Medical, Inc. | Tagging pump messages with identifiers that facilitate restructuring |
US11881297B2 (en) | 2018-07-17 | 2024-01-23 | Icu Medical, Inc. | Reducing infusion pump network congestion by staggering updates |
US10861592B2 (en) | 2018-07-17 | 2020-12-08 | Icu Medical, Inc. | Reducing infusion pump network congestion by staggering updates |
US11373753B2 (en) | 2018-07-17 | 2022-06-28 | Icu Medical, Inc. | Converting pump messages in new pump protocol to standardized dataset messages |
US11437132B2 (en) | 2018-07-26 | 2022-09-06 | Icu Medical, Inc. | Drug library dynamic version management |
US10692595B2 (en) | 2018-07-26 | 2020-06-23 | Icu Medical, Inc. | Drug library dynamic version management |
US11309070B2 (en) | 2018-07-26 | 2022-04-19 | Icu Medical, Inc. | Drug library manager with customized worksheets |
JP2021531870A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP7132421B2 (en) | 2018-07-31 | 2022-09-06 | アイセンス,インコーポレーテッド | Body Adhesive Unit for Continuous Blood Glucose Monitoring |
JP2022185130A (en) * | 2018-07-31 | 2022-12-13 | アイセンス,インコーポレーテッド | Glucose measurement apparatus |
JP2022179730A (en) * | 2018-07-31 | 2022-12-02 | アイセンス,インコーポレーテッド | Body attachable unit and sensor member |
EP4292530A3 (en) * | 2018-07-31 | 2024-02-28 | i-Sens, Inc. | Body attachment unit for continuous glucose monitoring |
JP2021531871A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP2022166310A (en) * | 2018-07-31 | 2022-11-01 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP2022166311A (en) * | 2018-07-31 | 2022-11-01 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP7161028B2 (en) | 2018-07-31 | 2022-10-25 | アイセンス,インコーポレーテッド | Blood glucose measurement body-adherent unit |
EP3831302A4 (en) * | 2018-07-31 | 2021-09-01 | i-Sens, Inc. | Body attachment unit for continuous glucose monitoring |
JP7161029B2 (en) | 2018-07-31 | 2022-10-25 | アイセンス,インコーポレーテッド | continuous blood glucose meter |
US20210267503A1 (en) * | 2018-07-31 | 2021-09-02 | I-Sens, Inc. | Body attachable unit for continuous blood glucose measurement |
JP2022162114A (en) * | 2018-07-31 | 2022-10-21 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose monitoring |
EP3831301A4 (en) * | 2018-07-31 | 2021-09-08 | i-Sens, Inc. | Body attachment unit for continuous blood glucose monitoring |
EP4137041A1 (en) * | 2018-07-31 | 2023-02-22 | i-Sens, Inc. | Continuous blood glucose measurement body attachment unit |
EP4137048A1 (en) * | 2018-07-31 | 2023-02-22 | i-Sens, Inc. | Body attachment unit for continuous blood glucose monitoring |
EP4137049A1 (en) * | 2018-07-31 | 2023-02-22 | i-Sens, Inc. | Continuous blood glucose measurement body attachment unit |
AU2019314012B2 (en) * | 2018-07-31 | 2022-10-06 | I-Sens, Inc. | Continuous glucose monitoring device |
EP3831300A4 (en) * | 2018-07-31 | 2021-09-15 | i-Sens, Inc. | Continuous blood glucose measurement device |
JP7375136B2 (en) | 2018-07-31 | 2023-11-07 | アイセンス,インコーポレーテッド | Body-attached unit for continuous blood glucose measurement |
JP7132422B2 (en) | 2018-07-31 | 2022-09-06 | アイセンス,インコーポレーテッド | Body Adhesive Unit for Continuous Blood Glucose Monitoring |
JP2021531875A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP7132423B2 (en) | 2018-07-31 | 2022-09-06 | アイセンス,インコーポレーテッド | Body Adhesive Unit for Continuous Blood Glucose Monitoring |
EP3831297A4 (en) * | 2018-07-31 | 2021-09-15 | i-Sens, Inc. | Body attachment unit for continuous blood glucose monitoring |
JP7098815B2 (en) | 2018-07-31 | 2022-07-11 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP7098816B2 (en) | 2018-07-31 | 2022-07-11 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
EP3831295A4 (en) * | 2018-07-31 | 2021-09-15 | i-Sens, Inc. | Continuous glucose monitoring device |
JP7098814B2 (en) | 2018-07-31 | 2022-07-11 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP7086267B2 (en) | 2018-07-31 | 2022-06-17 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
AU2019313138B2 (en) * | 2018-07-31 | 2022-06-16 | I-Sens, Inc. | Body attachment unit for continuous blood glucose monitoring |
AU2019316455B2 (en) * | 2018-07-31 | 2022-06-16 | I-Sens, Inc. | Continuous blood glucose measurement device |
JP7060757B2 (en) | 2018-07-31 | 2022-04-26 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
EP3831293A4 (en) * | 2018-07-31 | 2021-10-06 | i-Sens, Inc. | Continuous blood glucose measurement body attachment unit |
EP3831296A4 (en) * | 2018-07-31 | 2021-10-06 | i-Sens, Inc. | Continuous blood glucose measurement body attachment unit |
WO2020027434A1 (en) * | 2018-07-31 | 2020-02-06 | 주식회사 아이센스 | Body attachment unit for continuous blood glucose monitoring |
JP2022503482A (en) * | 2018-07-31 | 2022-01-12 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP2021531118A (en) * | 2018-07-31 | 2021-11-18 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP2021531873A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP2021531869A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Continuous blood glucose measuring device |
JP2021531868A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP2021531874A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP2021531872A (en) * | 2018-07-31 | 2021-11-25 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP2021534917A (en) * | 2018-09-07 | 2021-12-16 | メンタラブ ゲーエムベーハー | System to detect biological signals |
CN113038879A (en) * | 2018-09-07 | 2021-06-25 | 门塔拉布有限公司 | System for detecting biological signals |
WO2020067630A1 (en) * | 2018-09-27 | 2020-04-02 | 주식회사 아이센스 | Body attachment unit for continuous blood glucose measurement |
JP2022500128A (en) * | 2018-09-27 | 2022-01-04 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP7181385B2 (en) | 2018-09-27 | 2022-11-30 | アイセンス,インコーポレーテッド | Blood glucose measurement body-adherent unit |
WO2020067629A1 (en) * | 2018-09-27 | 2020-04-02 | 주식회사 아이센스 | Body-attachable unit for continuously measuring blood glucose |
JP2022185131A (en) * | 2018-09-27 | 2022-12-13 | アイセンス,インコーポレーテッド | Body attachable unit |
JP2022500127A (en) * | 2018-09-27 | 2022-01-04 | アイセンス,インコーポレーテッド | Body attachment unit for continuous blood glucose measurement |
JP2022168093A (en) * | 2018-09-27 | 2022-11-04 | アイセンス,インコーポレーテッド | Applicator for continuous blood glucose measurement device |
JP7376659B2 (en) | 2018-09-27 | 2023-11-08 | アイセンス,インコーポレーテッド | body attachment unit |
JP2022501100A (en) * | 2018-09-27 | 2022-01-06 | アイセンス,インコーポレーテッド | Applicator for continuous blood glucose measuring device |
JP7139520B2 (en) | 2018-09-27 | 2022-09-20 | アイセンス,インコーポレーテッド | Applicator for continuous blood glucose meter |
JP7161037B2 (en) | 2018-09-27 | 2022-10-25 | アイセンス,インコーポレーテッド | Blood glucose measurement body-adherent unit |
US11571164B2 (en) | 2019-01-04 | 2023-02-07 | Enable Injections, Inc. | Medical fluid injection apparatus and method with detachable patch and monitoring |
US11786173B2 (en) | 2019-01-04 | 2023-10-17 | Enable Injections, Inc. | Medical fluid injection apparatus and method with detachable patch and monitoring |
WO2020159780A1 (en) * | 2019-02-01 | 2020-08-06 | Analog Devices, Inc. | Subcutaneous biosensor |
US11464908B2 (en) | 2019-02-18 | 2022-10-11 | Tandem Diabetes Care, Inc. | Methods and apparatus for monitoring infusion sites for ambulatory infusion pumps |
JP2022538964A (en) * | 2019-05-14 | 2022-09-07 | サンヴィタ メディカル コーポレーション | Subcutaneous analyte sensor applicator and continuous measurement system |
USD1002852S1 (en) | 2019-06-06 | 2023-10-24 | Abbott Diabetes Care Inc. | Analyte sensor device |
CN112294270A (en) * | 2019-07-30 | 2021-02-02 | 亘冠智能技术(杭州)有限公司 | Health monitoring system based on RFID technology |
EP3771428A1 (en) * | 2019-08-02 | 2021-02-03 | Bionime Corporation | Physiological signal monitoring device |
US11737689B2 (en) | 2019-08-02 | 2023-08-29 | Bionime Corporation | Physiological signal monitoring device |
EP3991650A4 (en) * | 2019-08-19 | 2023-06-21 | i-Sens, Inc. | Continuous blood sugar measuring sensor member |
US11278671B2 (en) | 2019-12-04 | 2022-03-22 | Icu Medical, Inc. | Infusion pump with safety sequence keypad |
WO2021164192A1 (en) * | 2020-02-20 | 2021-08-26 | Medtrum Technologies Inc. | High reliability analyte detection device |
CN113274014A (en) * | 2020-02-20 | 2021-08-20 | 上海移宇科技股份有限公司 | Mounting unit of analyte detection device and mounting method thereof |
CN113274004A (en) * | 2020-02-20 | 2021-08-20 | 上海移宇科技股份有限公司 | High reliability analyte detection device |
US11883361B2 (en) | 2020-07-21 | 2024-01-30 | Icu Medical, Inc. | Fluid transfer devices and methods of use |
USD1015366S1 (en) | 2020-07-29 | 2024-02-20 | Abbott Diabetes Care Inc. | Display screen or portion thereof with graphical user interface |
US11135360B1 (en) | 2020-12-07 | 2021-10-05 | Icu Medical, Inc. | Concurrent infusion with common line auto flush |
USD999913S1 (en) | 2020-12-21 | 2023-09-26 | Abbott Diabetes Care Inc | Analyte sensor inserter |
USD1006235S1 (en) | 2020-12-21 | 2023-11-28 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
USD982762S1 (en) | 2020-12-21 | 2023-04-04 | Abbott Diabetes Care Inc. | Analyte sensor inserter |
WO2022164940A1 (en) | 2021-01-26 | 2022-08-04 | Abbott Diabetes Care Inc. | Systems, devices, and methods related to ketone sensors |
CN114305331A (en) * | 2021-12-01 | 2022-04-12 | 安徽华米信息科技有限公司 | Method, device and equipment for collecting physiological parameters |
WO2023110190A1 (en) | 2021-12-13 | 2023-06-22 | Heraeus Medical Gmbh | Tests and methods for detecting bacterial infection |
US11933650B2 (en) | 2022-07-01 | 2024-03-19 | Icu Medical, Inc. | Air detection system and method for detecting air in a pump of an infusion system |
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