US20080033273A1 - Embedded Bio-Sensor System - Google Patents
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- US20080033273A1 US20080033273A1 US11/872,553 US87255307A US2008033273A1 US 20080033273 A1 US20080033273 A1 US 20080033273A1 US 87255307 A US87255307 A US 87255307A US 2008033273 A1 US2008033273 A1 US 2008033273A1
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1486—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase
- A61B5/14865—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase invasive, e.g. introduced into the body by a catheter or needle or using implanted sensors
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0031—Implanted circuitry
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
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- A—HUMAN NECESSITIES
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- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/08—Sensors provided with means for identification, e.g. barcodes or memory chips
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- G—PHYSICS
- G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
- G16H—HEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
- G16H40/00—ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices
- G16H40/60—ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices for the operation of medical equipment or devices
- G16H40/67—ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices for the operation of medical equipment or devices for remote operation
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Abstract
Description
- This application is a continuation of co-pending U.S. patent application Ser. No. 11/582,790, filed on Oct. 18, 2006, which is a continuation of U.S. application Ser. No. 10/849,614, filed on May 20, 2004, which issued as U.S. Pat. No. 7,125,382 on Oct. 24, 2006, all of which are incorporated herein in their entirety by reference.
- The present invention relates to sensor devices and, more particularly, to an bio-sensor system configured for wirelessly transmitting data to a remote transponder from an on-chip transponder having a sensor and which is implantable in a patient. The bio-sensor system is specifically adapted to apply a stable and precise voltage to an electrode system of the sensor such that glucose concentration levels of the patient may be accurately measured.
- The blood glucose concentration level of a patient is normally controlled by the pancreas. However, for patients suffering from diabetes, the pancreas does not properly regulate the production of insulin needed to metabolize food into energy for the individual. For diabetic patients, glucose levels must be checked or monitored several times throughout the day so that insulin may be periodically administered in order to maintain the glucose concentration at a normal level. In one popular method, the glucose level is monitored by first obtaining a sample of blood from finger-pricking. The glucose level of the blood sample is then placed on a glucose measurement strip and a subsequent chemical reaction produces a color change that may be compared to a reference chart. In this manner, the reaction of the blood sample with the glucose measurement strip provides an indication as to whether the glucose level is abnormally low or high such that the diabetic patient may administer the proper amount of insulin in order to maintain the glucose concentration within a predetermined range. Such administration of insulin is typically performed by way of self-injection with a syringe.
- Unfortunately, the finger-pricking method of glucose testing is uncomfortable as both the blood-pricking and the insulin injections are painful and time-consuming such that many diabetic patients are reluctant to check their glucose levels at regular intervals throughout the day. Unfortunately, glucose levels often fluctuate throughout the day. Therefore, even diabetic patients who are otherwise consistent in checking their glucose levels at regular intervals throughout the day may be unaware of periods wherein their glucose levels are dangerously low or high. Furthermore, the finger-pricking method is dependent on patient skill for accurate testing such that the patient may rely on erroneous data in determining the dosage level of insulin. Finally, self-monitoring of glucose levels imposes a significant burden on less capable individuals such as the young, the elderly and the mentally-challenged.
- At the time of this writing, it is estimated that 17 million people in the United States, or about six percent of the population, have diabetes. Due in part to dietary habits and an increasingly sedentary lifestyle, particularly among children, diabetes is expected to increase at the rate of about 7 percent every year such that the disease is predicted to eventually reach epidemic proportions. In addition, the current cost of diabetes in the United States alone is estimated at over $120 billion with the total U.S. sales of the glucose measuring strips alone estimated at about $2 billion. Thus, there is a demand for continuous, reliable and low-cost monitoring of glucose levels of diabetic patients due to the increasing number of people diagnosed with diabetes.
- Included in the prior art are several implantable devices have been developed in an effort to provide a system for continuous and reliable glucose monitoring. In such implantable devices, an electrochemical sensor is embedded beneath the skin of the patient. The electrochemical sensor detects the glucose concentration level and transmits signals representative of the glucose concentration level to a receiving device. Unfortunately, such implantable devices suffer from several deficiencies. One such deficiency is that implantable devices may expend a substantial amount of power in sensing and processing bio-signals. The power requirement for such devices necessitates the use of large batteries in order to prolong the useful life. Unfortunately, implantable devices having batteries as the power source may require periodic surgeries for replacement of the batteries when the capacity drops below a minimum level.
- Furthermore, some batteries contain materials that may present a risk of harm to the patient due to toxic substances or chemical within the battery that may leak into the patient after implantation. Also, due to the relatively limited power capacity of batteries, the range of functions that may be performed by the implantable device may be somewhat limited. Finally, it may be desirable to monitor multiple physiological parameters in addition to glucose concentration levels. In such cases, the implantable device may require multiple sensors wherein each sensor simultaneously monitors a different physiological parameter of the patient. For example, in addition to monitoring glucose concentration levels, the temperature and heart rate of the patient may also be monitored. Such an implantable device having multiple sensors may consume more power than can be supplied by a battery that is miniaturized for use in an implantable device.
- One implantable device in the prior art overcomes the above noted deficiency associated with large power requirements by providing a bio-sensor system that is passively powered such that the operating life of the bio-sensor is theoretically unlimited. As understood, the passively powered bio-sensor system includes at least one sensor that is implanted in a patient. The implanted sensor monitors physiological conditions of the patient. An implanted passive transponder receives the sensor signals from the sensor, digitizes the sensor signals and transmits the digitized sensor signal out of the patient's body when subjected to an interrogation signal from a remote interrogator. The interrogator also energizes the implanted transponder such that the bio-sensor system may be passively powered. In this manner, the passively powered bio-sensor system requires no batteries such that it essentially has an unlimited operating life.
- Another deficiency of implantable devices pertains to electrochemical sensors that are utilized therein to measure glucose concentration levels in the patient's blood. Such sensors typically use an amperometric detection method wherein oxidation or reduction of a compound is measured at a working electrode in order to determine substance concentration levels. A potentiostat is used to apply a constant potential or excitation voltage to the working electrode with respect to a reference electrode. In measuring glucose concentration levels in the blood, glucose oxidase (GOX) is typically used as a catalyst to oxidize glucose and form gluconic acid, leaving behind two electrons and two protons and reducing the GOX. Oxygen that is dissolved in the patient's blood then reacts with GOX by accepting the two electrons and two protons to form hydrogen peroxide (H2O2) and regenerating oxidized GOX.
- The cycle repeats as the regenerated GOX reacts once again with glucose. The consumption of O2 or the formation of H2O2 is subsequently measured at the working electrode which is typically a platinum electrode. As oxidation occurs at the working electrode, reduction also occurs at the reference electrode which is typically a silver/silver chloride electrode. The more oxygen that is consumed, the greater the amount of glucose in the patient's blood. In the same reaction, the rate at which H2O2 is produced is also indicative of the glucose concentration level in the patient's blood. Because the potentiostat controls the voltage difference between the working electrode and the reference electrode, the accuracy with which the sensor measures glucose concentration levels is dependent on the accuracy with which the voltage is applied. If the voltage that is applied to the sensor is excessive, the silver or silver chloride reference electrode may be excessively consumed such that the reference electrode may become damaged. Furthermore, erroneous measurements of glucose concentration levels may result such that the ability of the patient to administer insulin in order to correct for abnormalities in glucose concentration levels may be compromised
- In an attempt to overcome the above-described deficiency associated with two-electrode electrochemical sensors, three-electrode electrochemical sensors have been developed wherein an auxiliary electrode is included with the working electrode and the reference electrode. The inclusion of the auxiliary electrode is understood to reduce the consumption of silver and silver chloride by reducing the magnitude of current flowing through the reference electrode, thereby stabilizing the electrode potential. Unfortunately, such three-electrode electrochemical sensors of the type describe above add complexity and cost to the bio-sensor system due to the increased difficulty in manufacturing and operating such electrochemical sensors.
- As can be seen, there is a need for an implantable bio-sensor system that overcomes the above-described deficiencies associated with the stability of the reference electrode potential with respect to the working electrode. More specifically, there exists a need in the art for an implantable bio-sensor system that provides a stable and accurate voltage to the electrochemical sensor in order to improve the accuracy with which glucose concentration levels may be measured. In combination with the power requirements, there is also a need in the art for an implantable bio-sensor system that enables the simultaneous and selective monitoring of multiple physiological parameters of the patient through the use of multiple bio-sensors included with the implantable device. Furthermore, there exists a need in the art for an implantable bio-sensor system which allows full-duplex operation such that requests for data (i.e., physiological parameters of the patient) and transmission of such data can be simultaneously performed. Finally, there is a need in the art for an implantable bio-sensor system that enables continuous readout of the data at a remote device.
- Provided is a telemetric bio-sensor system which utilizes radio frequency identification (RFID) technology and which includes a remote transponder that is in wireless communication with a passively powered on-chip transponder. The bio-sensor system is specifically adapted to provide a substantially stable and precise voltage to a sensor assembly that is included with an implantable on-chip transponder. The remote transponder is placed within a predetermined distance of the on-chip transponder in order to supply power to and request telemetry data from the on-chip transponder. The remote transponder is also configured to remotely receive data representative of a physiological parameter of the patient as well as identification data and may enable readout of one or more of the physiological parameters that are measured, processed and transmitted by the on-chip transponder upon request by the remote transponder.
- Importantly, the power receiver supplies a substantially non-deviating sensor reference voltage to the sensor in order to enhance the accuracy with which the physiological parameter is measured. The precision and stability of the sensor reference voltage (i.e., the sensor power) is enhanced by the specific circuit architecture of the glucose sensor. The application of the substantially stable voltage to the sensor assembly allows for relatively accurate measurement of the physiological parameter of the patient such as measurement of a glucose concentration level by a glucose sensor. The technique of generating the stable and precise voltage may be applied to a 2-pin glucose sensor as well as to a 3-pin glucose sensor without the use of a microprocessor such that cost and power consumption of the on-chip transponder may be reduced. Advantageously, the stability and accuracy of the sensor reference voltage is achieved without the use of a microprocessor to reduce power consumption of the on-chip transponder as well as reduce overall costs of the bio-sensor system.
- The on-chip transponder includes the sensor assembly having the sensor which may be the 2-pin or 3-pin glucose sensor. However, any other sensor may be used with the on-chip transponder. Components of the on-chip transponder may include: the sensor, a power receiver, an analog-to-digital (A/D) assembly, a data processor and an RF transmitter which may preferably be interconnected using conventional integrated circuit technology such that the on-chip transponder may be packaged into a sufficiently small size for implantation into a patient. An RF receiver may also be included with the on-chip transponder to allow for selection among a plurality of sensors and to allow for full-duplexing, which enables continuous and/or simultaneous two-way wireless communication between the remote transponder and the on-chip transponder.
- The remote transponder emits a scanner signal that is received by a power receiver of the on-chip transponder. The power receiver converts the scanner signal to a power signal to power the A/D assembly, a data processor and an RF transmitter. The A/D assembly converts the physiological parameter contained in an analog electrical signal coming from the sensor into digital format in a digital signal. The A/D assembly may also add a unique identification code to the digital signal to identify the particular sensor from which the sensor signal originated.
- The data processor receives the digital signal from the A/D assembly and filters, amplifies and/or encodes the digital signal to generate a processed data signal. The data processor may also gate the data signal to determine when to transmit the data signal and may also sum the data signal with other data (i.e., from other sensors). The RF transmitter impresses (i.e., modulates) the data signal onto a radio carrier of a desired frequency, amplifies the modulated carrier and sends it to an antenna for radiation to the remote transponder.
- These as well as other features of the present invention will become more apparent upon reference to the drawings wherein:
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FIG. 1 a is a block diagram of a sensor assembly and an on-chip transponder of an implantable bio-sensor system of the present invention in an embodiment enabling simplex operation wherein the content and duration of a signal transmitted by the on-chip transponder is pre-programmed; -
FIG. 1 b is a block diagram of the sensor assembly and the on-chip transponder of the bio-sensor system in an embodiment enabling duplex operation wherein the duration and content of signals transmitted by the on-chip transponder to a remote transponder, and vice versa, is selectable; -
FIG. 2 is a block diagram of a remote transponder of the implantable bio-sensor system; -
FIG. 3 is a block diagram of a data processor that may be included with the on-chip transponder; -
FIG. 4 is a block diagram of a radio frequency (RF) transmitter that may be included with the on-chip transponder; -
FIG. 5 a is a block diagram of an analog-to-digital (A/D) assembly as may be included with the on-chip transponder for the embodiment of the bio-sensor system configured to receive a single one of the sensor signals; -
FIG. 5 b is a block diagram of the A/D assembly as may be included with the on-chip transponder for the embodiment of the bio-sensor system that may include a switch for selecting a sensor signal sent from multiple sensors; -
FIG. 6 is a block diagram of a power receiver that may be included with the on-chip transponder; -
FIG. 7 is a block diagram of an RF receiver that may be included with the on-chip transponder; -
FIG. 8 a is a schematic representation of a 2-pin glucose sensor as may be incorporated into the sensor assembly; and -
FIG. 8 b is a schematic representation of a 3-pin glucose sensor as may be incorporated into the sensor assembly. - Referring now to the drawings wherein the showings are for purposes of illustrating various aspects of the invention and not for purposes of limiting the same, provided is a uniquely configured telemetric bio-sensor system 10 which utilized radio frequency identification (RFID) technology and which includes a
remote transponder 800 that is in wireless communication with a passively powered on-chip transponder 100. The bio-sensor system 10 is specifically adapted to provide a substantially stable and precise voltage to asensor assembly 200 that is included with the on-chip transponder 100. The on-chip transponder 100 is implantable into a host such as a human patient. - The
remote transponder 800, which may be a compact handheld device, may be manually placed within a predetermined distance (e.g., within several feet) of the on-chip transponder 100 in order to supply power to and request telemetry data from the on-chip transponder 100. Theremote transponder 800 may alternatively be fixedly mounted and may be configured to automatically transmit power and telemetry request data to the patient and, hence, the on-chip transponder 100 when the patient moves within the predetermined distance to theremote transponder 800. Regardless of whether it is handheld, fixedly mounted or otherwise supported, theremote transponder 800 is configured to remotely receive data representative of a physiological parameter of the patient as well as identification data such that the data may be stored or displayed. - Importantly, the application of the substantially stable voltage to the
sensor assembly 200 allows for relatively accurate measurement of the physiological parameter of the patient such as measurement of a glucose concentration level by aglucose sensor 210. As will be demonstrated below, the technique of generating the stable and precise voltage may be applied to a 2-pin glucose sensor 210 as well as to a 3-pin glucose sensor 210. Importantly, the bio-sensor system 10 provides the stable and precise voltage to thesensor assembly 200 without the use of a microprocessor such that cost and power consumption of the on-chip transponder 100 may be reduced. - In its broadest sense, the bio-sensor system 10 and operational method of use thereof comprises the implantable on-
chip transponder 100 and theremote transponder 800 in wireless communication with one another. As mentioned above, thesensor assembly 200 is connected to or integral with the on-chip transponder 100 and may be implanted in the patient with the on-chip transponder 100. The bio-sensor system 10 is configured such that theremote transponder 800 may enable readout of one or more of the physiological parameters that are measured, processed and transmitted by the on-chip transponder 100 upon request by theremote transponder 800. The bio-sensor system 10 may be configured to operate in simplex mode as shown inFIG. 1 a. - Alternatively, the bio-sensor system 10 may be configured to operate in duplex mode as shown in
FIG. 1 b wherein the on-chip transponder 100 additionally includes an intelligent radio frequency (RF) receiver. When provided with theRF receiver 700, the bio-sensor system 10 enables features such as selection betweenmultiple sensors 210 and/or continuous readout of data (e.g., physiological parameters of the patient) in addition to readout of identification data which may be correlated to a patient database containing information regarding the patient's identity as well as information regarding the patient's age, weight, medical history, etc. - Referring more particularly now to
FIGS. 1 a and 1 b, shown are block diagrams of thesensor assembly 200 as connected to the on-chip transponder 100 of the bio-sensor system 10 for respective embodiments enabling simplex and duplex operation. The on-chip transponder 100 includes thesensor assembly 200 having thesensor 210. Thesensor 210 may be configured as the 2-pin glucose sensor 210 or as 3-pin glucose sensor 210 as was mentioned above. However, any other sensor may be used with the on-chip transponder 100. For example, thesensor 210 may be configured as at least one of the following: a pressure transducer, a blood sugar sensor, a blood oxygen sensor, a heart rate monitor, a respiratory rate sensor, etc. In this regard, thesensor 210 may be configured as any type of sensor for measuring, monitoring or detecting any type of physiological parameter of the patient. - Shown in
FIG. 2 is a block diagram of theremote transponder 800. Theremote transponder 800 is configured to wirelessly request data regarding the physiological parameter by transmitting ascanner signal 882 to the on-chip transponder 100. Theremote transponder 800 is also configured to receive adata signal 462 representative of the physiological parameter from the on-chip transponder 100. In the same manner, the on-chip transponder 100 is configured to communicate with theremote transponder 800 and receive thescanner signal 882 and transmit the data signal 462 therefrom once theremote transponder 800 and on-chip transponder 100 are within sufficiently close proximity to one another to enable wireless communication therebetween. - Components of the on-
chip transponder 100 for the embodiment of the bio-sensor system 10 enabling simplex operation include: thesensor 210, apower receiver 600, an analog-to-digital (A/D)assembly 300, adata processor 400 and anRF transmitter 500, as shown inFIG. 1 a. For embodiments of the bio-sensor system 10 enabling duplex operation, theRF receiver 700 is included with the on-chip transponder 100, as shown inFIG. 1 b. Each of the components of the on-chip transponder 100 may be electrically interconnected via conventional conductive wiring. However, electrical connections may preferably be provided using conventional integrated circuit technology such that the on-chip transponder 100 may be packaged into a sufficiently small size for implantation into the patient. - The
sensor 210 is configured to generate asensor signal 234 representative of the physiological parameter of the patient and is made up of a positive signal and a negative signal transmitted in parallel and sent from thesensor 210 to the A/D assembly 300, as shown inFIGS. 1 a and 1 b. For embodiments of the bio-sensor system 10 enabling simplex operation, thepower receiver 600 is configured to receive thescanner signal 882 atantenna 601 and to generate apower signal 602 for passively powering the on-chip transponder 100. For embodiments of the bio-sensor system 10 enabling duplexing, theRF receiver 700 receives thescanner signal 882 atantenna 701 for delivery to thepower receiver 600. The A/D assembly 300 is connected to thepower receiver 600 viapower line 604 to receive thepower signal 602. The A/D assembly 300 is also connected to thesensor 210 to receive theanalog sensor signal 234 therefrom. Once powered by thepower signal 602, the A/D assembly 300 is configured to generate adigital signal 372 in response to theanalog sensor signal 234 coming from thesensor 210. - Referring still to
FIGS. 1 a and 1 b, thedata processor 400 is connected to the A/D assembly 300 and thepower receiver 600 and is configured to receive thepower signal 602, viapower line 606, as well as thedigital signal 372 from the A/D assembly 300. Upon powering by thepower signal 602, thedata processor 400 is configured to generate adata signal 462 in response to thedigital signal 372. In general, thedata processor 400 receives thedigital signal 372 and filters, amplifies and/or encodes thedigital signal 372 to generate the data signal 462. Thedata processor 400 may be configured to gate the data signal 462 to determine when to transmit the data signal 462 to theremote transponder 800. In addition, thedata processor 400 may also be configured to sum the data signal 462 with other data (i.e., from other sensors 210), as will be explained in greater detail below. - The
RF transmitter 500 is connected to thepower receiver 600 viapower line 608 to receive thepower signal 602. TheRF transmitter 500 is also connected to thedata processor 400 and is configured to receive the data signal 462 therefrom. TheRF transmitter 500 is also configured to modulate, amplify, filter and transmit the data signal 462 for receipt back to theremote transponder 800. In general, theRF transmitter 500 impresses (i.e., modulates) the data signal 462 onto a radio carrier of a desired frequency, amplifies the modulated signal and sends the modulated signal to antenna for radiation to theremote transponder 800. - The
power receiver 600 circuitry is configured similar to the circuitry of a voltage regulator, as is well known in the art, wherein reference diodes and resistors are arranged in such a manner as to generate an approximate supply voltage. However, thepower receiver 600 is also specifically configured to supply a suitable voltage to thesensor 210 processing circuitry without delivering substantial current so as to reduce complexity. Thus, in addition to collecting, rectifying, filtering and regulating power for supply to the A/D assembly 300,data processor 400 andRF transmitter 500, thepower receiver 600 also provides the substantially stable and precise voltage to thesensor assembly 200. - More specifically, the
power receiver 600 is configured to supply a substantially non-deviating sensorreference voltage signal 642 to thesensor 210 in order to enhance the accuracy with which the physiological parameter is measured. The precision and stability of the sensor reference voltage signal 642 (i.e., thesensor 210 power) is enhanced by the specific circuit architecture of theglucose sensor 210, as is shown inFIGS. 8 a and 8 b and as will be described in greater detail below. In this manner, the accuracy of glucose concentration levels, as represented by an output signal from theglucose sensor 210, is improved. As was earlier mentioned, once the physiological parameter is measured by thesensor 210, theremote transponder 800 is configured to receive the data signal 462 from theRF transmitter 500 and extract data representative of the physiological parameter for storage and/or display. - For embodiments of the bio-sensor system 10 enabling duplex operation, the on-
chip transponder 100 additionally includes theRF receiver 700 which is configured to receive thescanner signal 882 from theremote transponder 800, as shown inFIG. 1 b. In a broadest sense, thescanner signal 882 is received atantenna 701 and is decoded by theRF receiver 700 to inform the on-chip transponder 100, via amessage signal 702, that a request for data has been made. Thepower receiver 600 also converts thescanner signal 882 into thepower signal 602 for relay to the A/D assembly 300, thedata processor 400 and theRF transmitter 500 via respective ones of thepower lines RF receiver 700 is configured to filter, amplify and demodulate thescanner signal 882 and generate the message signal 702 for delivery to controlling components of the on-chip transponder 100. More specifically, the message signal 702 is transmitted to the A/D assembly 300, thedata processor 400 and theRF transmitter 500 via respective ones of the message/control lines FIG. 1 b. TheRF receiver 700 may be in two-way communication with the A/D assembly 300, thedata processor 400 and theRF transmitter 500 via respective ones of the message/control lines - For configurations of the bio-sensor system 10 having a plurality of
sensors 210, each one of thesensors 210 may be operative to sense a distinct physiological parameter of the patient and generate thesensor signal 234 representative thereof. For example, an additional one of thesensors 210 may be provided to measure an internal body temperature of the patient. Still further, an additional one of thesensors 210 may be provided to measure a blood pressure level of the patient. The plurality ofsensors 210 may generate a plurality of sensor signals 234. TheRF receiver 700 may be configured to coordinate requests for data from one or more of the plurality ofsensors 210 for subsequent transmission of the data back to theremote transponder 800, as will be described in greater detail below. For embodiments of the bio-sensor system 10 havingmultiple sensors 210, thedata processor 400 may be configured to assign a preset identification code to thedigital signal 372 for identifying thesensor 210 from which thesensor signal 234 originates. In such an embodiment, the A/D assembly 300 may include aswitch 310 that is responsive to the message signal 702 and which is operative to select among the plurality of sensor signals 234 for subsequent transmission thereof. - Referring now to
FIGS. 8 a and 8 b, for configurations of the bio-sensor system 10 wherein thesensor 210 is aglucose sensor 210 having an electrode assembly 201, the specific circuit architecture of theglucose sensor 210 is preferably such that the sensorreference voltage signal 642 is supplied to the electrode assembly 201 at a substantially constant value of about positive 0.7 volts. Advantageously, the stability and accuracy of the sensorreference voltage signal 642 is achieved without the use of a microprocessor. The circuit architecture includes an electrode assembly 201 having a first terminal 202 (i.e., a working electrode) and a second terminal 204 (i.e., a reference electrode) that are both placed in fluid communication with the patient's blood. - The 2-
pin glucose sensor 210 may be configured to measure the glucose level using glucose oxidase (GOX) as a catalyst to cause oxidation of glucose in the patient's blood which forms gluconic acid and which reduces the GOX. Oxygen (O2) in the patient's blood reacts with the GOX to form hydrogen peroxide (H2O2) and regenerate the oxidized GOX. The consumption of O2 or the formation of H2O2 is measured at the first terminal 202, which may be fabricated of platinum. While oxidation occurs at the first terminal 202, reduction is measured at thesecond terminal 204, which may be fabricated of silver/silver chloride. The rate at which O2 is consumed and H2O2 is formed is indicative of the glucose concentration level in the patient's blood. Advantageously, supplying the sensorreference voltage signal 642 to the first terminal 202 at a substantially constant value of about positive 0.7 increases the accuracy with which the glucose concentration level may be measured by the 2-pin glucose sensor 210 as well as the 3-pin glucose sensor 210. - Referring still to
FIG. 8 a, measurement accuracy of glucose concentration level by the 2-pin glucose sensor 210 is enhanced by the circuit architecture thereof. As can be seen, the 2-pin glucose sensor 210 includes afirst precision resistor 224, a firstoperational amplifier 220, avoltmeter 250, a secondoperational amplifier 230 and a tunablesecond precision resistor 240. Thefirst precision resistor 224 is connected to thepower receiver 600 and is configured to receive the sensorreference voltage signal 642 therefrom for excitation of theglucose sensor 210. The firstoperational amplifier 220 is connected to thefirst precision resistor 224 through thefirst signal line 212 and is configured to receive the sensorreference voltage signal 642. The firstoperational amplifier 220 discharges a precision sensorreference voltage signal 223 at anon-inverting input 232 thereof in response to the sensorreference voltage signal 642. - The
voltmeter 250 is connected to a non-inverting input of firstoperational amplifier 220 and to thefirst precision resistor 224 and is configured to monitor the precision sensorreference voltage signal 223. Thevoltmeter 250 is configured to establish asensor 210 operating point and more accurately interpret responses of thesensor 210. Thevoltmeter 250 also cooperates with non-inverting firstoperational amplifier 220 to buffer the precision sensorreference voltage signal 223 and apply a substantially accurate sensorreference voltage signal 226 to the first terminal 202. The secondoperational amplifier 230 is connected to thesecond terminal 204 through thesecond signal line 214 and is configured to receive current discharging from thesecond terminal 204 in response to the accurate sensorreference voltage signal 226 applied to the first terminal 202. - The tunable
second precision resistor 240 is connected between an output and an inverting input of the secondoperational amplifier 230 and cooperates therewith to generate thesensor signal 234 that is substantially proportional to the glucose level of the patient's blood. The current is delivered to an inverting terminal of the secondoperational amplifier 230 having anon-inverting input 232 which is grounded, as shown inFIG. 8 a. Accurate current measure (e.g., discharging from the second terminal 204) at the secondoperational amplifier 230 is established by the tunablesecond precision resistor 240. By configuring theglucose sensor 210 in this manner, the need for a microprocessor is eliminated and the associated calibration procedures and current drain. Output of the secondoperational amplifier 230 as determined by the precisionsensor reference voltage 223 as well as by thesensor 210 operating point (i.e., glucose levels) and thesecond precision resistor 240, is then processed and transmitted upon request by theremote transponder 800. - Referring briefly to
FIG. 8 b, shown is a block diagram of the 3-pin glucose sensor 210 which is similar to the block diagram of the 2-pin glucose sensor 210 shown inFIG. 8 a with the addition of a third terminal 206 (i.e., an auxiliary electrode) to the electrode assembly 201. The 3-pin glucose sensor 210 also includes anauxiliary control circuit 260. Thethird terminal 206 is co-located with the first andsecond terminals auxiliary control circuit 260 is connected between thethird terminal 206 and the secondoperational amplifier 230 through the third signal line 216 and is configured to monitor and control an amount of current discharging from thethird terminal 206. Thethird terminal 206 is configured to divert current away from thesecond terminal 204 during application of the accurate sensorreference voltage signal 226 applied to the first terminal 202. The addition of thethird terminal 206 to the electrode assembly 201 of the 3-pin glucose sensor 210 may help to reduce the consumption of silver and/or silver chloride contained in thesecond terminal 204 by drawing a portion of current away from thesecond terminal 204. In this manner, the third terminal 206 acts to stabilize the electrode potential and the operational life of theglucose sensor 210 may be increased. - Referring now to
FIGS. 5 a and 5 b, the architecture of the A/D assembly 300 will be described in detail. In general, the A/D assembly 300 is configured to convert the physiological parameter contained into an analog electrical signal which may be represented as current or voltage. The A/D assembly 300 may also perform encoding to include message encryption of thesensor signal 234, the addition of a unique identification code or message (e.g., to identify the particular sensor 210(s) from which the sensor signal(s) 234 originated). In addition, the A/D assembly 300 may include error detection and prevention bits with thesensor signal 234 to ensure the integrity of the sensor signal 234 (i.e., to verify that the data sent from thesensor 210 is equivalent to the data received). - Referring more specifically to
FIG. 5 a, shown is a block diagram of the A/D assembly 300 for the embodiment of the bio-sensor system 10 configured to receive thesensor signal 234 from asingle sensor 210, such as from theglucose sensor 210.FIG. 5 b is a block diagram of the A/D assembly 300 for the embodiment of the bio-sensor system 10 additionally including theswitch 310 to allow for selection among a plurality of sensor signals 234 sent from a plurality of thesensors 210. InFIGS. 5 a and 5 b, common subcomponents of the A/D assembly 300 include aprocessor filter 320, anamplifier 330, avoltage comparator 340, an A/D converter 350, acovert logic device 360 and acontroller 370. Theprocessor filter 320 is connected to thesensor 210 and is configured to receive thesensor signal 234 therefrom. Thesensor signal 234 is characterized by an analog voltage which, in the case of theglucose sensor 210, is substantially proportional to glucose concentration. The voltage may or may not have been processed in preparation for transmission to theremote transponder 800. In any case,further sensor signal 234 preparation may be required. - As shown in
FIGS. 5 a and 5 b, theprocessor filter 320 receives thesensor signal 234 and generates a filteredsignal 322 in response thereto. Theprocessor filter 320 may perform biasing functions as well as measurement of thesensor 210 status. Theprocessor filter 320 may also strip off spectral components (e.g., high frequency noise spikes) from thesensor signal 234 as well as perform normalizing of the voltage levels to match the capabilities of the on-chip transponder 100. Additional functions may be performed by theprocessor filter 320 such as averaging and other functions required to ensure accurate sampling of thesensor 210 data. - The
amplifier 330 is connected to theprocessor filter 320 and is configured to receive the filteredsignal 322 therefrom and amplify the filteredsignal 322 such that a minimum and maximum voltage of the signal is within the limits of the A/D converter 350 in order to provide maximum resolution of the digitized signal. Upon receiving the filteredsignal 322, theamplifier 330 is configured to generate an amplifiedsignal 332 in response to the filteredsignal 322. Thevoltage comparator 340 is connected to thepower receiver 600 and is configured to receive thepower signal 602 therefrom and generate a normalizedvoltage signal 342 in response thereto. More specifically, thevoltage comparator 340 normalizes the A/D assembly 300 circuitry such that its operating conditions match the need of thesensor signal 234 to be digitized. - The normalized
voltage signal 342 is then first sampled and then quantized by the A/D assembly 300 prior to digitization. This function is performed by the A/D converter 350 which is connected between theamplifier 330 and thevoltage comparator 340. The A/D converter 350 is configured to receive the amplifiedsignal 332 and the normalizedvoltage signal 342 and generate aconverter signal 352 in response thereto. A single sample may be collected or multiple samples may be collected in order to provide a more accurate average or to track variations in thesensor signal 234 over a period of time (e.g., over several heartbeats of the patient within whom thesensor 210 may be implanted). Thecovert logic device 360 receives theconverter signal 352 from the A/D converter 350. Thecovert logic device 360 is also in two-way communication with thecontroller 370 such that thecovert logic device 360 receives theconverter signal 352 and generates alogic signal 362 in response thereto. Thecovert logic device 360 may also contain error correction and/or voltage level-shift circuitry. - The
controller 370 is configured to gate the A/D assembly 300 for synchronizing signal transmission with thedata processor 400. As shown inFIG. 5 a, thecontroller 370 is in two-way communication with thecovert logic device 360. Referring toFIG. 5 b for the embodiment of the bio-sensor system 10 including theRF receiver 700, thecontroller 370 is connected to theRF receiver 700 and receives the message signal 702 therefrom via message/control line 704. TheRF receiver 700 also receives thelogic signal 362 from thecovert logic device 360 and is configured to synchronize the A/D converter 350 with thedata processor 400 for subsequent generation of thedigital signal 372 in response to the message signal 702 and thelogic signal 362. - For embodiments of the bio-sensor system 10 including the plurality of
sensors 210, the A/D assembly 300 further includes theswitch 310 which is connected to thecontroller 370 viasensor selection line 314. Theswitch 310 is also connected theprocessor filter 320 viaswitch signal line 312. In such embodiments, thecontroller 370 is responsive to the message signal 702 and is operative to cause theswitch 310 to select among a plurality of sensor signals 234 for subsequent transmission thereof to theprocessor filter 320. As was earlier mentioned, in such configurations of the bio-sensor system 10 having multiple ones of thesensors 210, thedata processor 400 may be configured to assign a preset identification code to thedigital signal 372 for identifying thesensor 210 from which thesensor signal 234 originates. Thedigital signal 372 may be either a packet of serial data (i.e., a burst of data over a fixed duration) or a stream of data that lasts as long as information is requested by theremote transponder 800 depending on the contents of the message signal 702 transmitted to thecontroller 370 via the message/control line 704. - Referring now to
FIG. 3 , the specific architecture of thedata processor 400 will be described in detail. In general, thedata processor 400 receives thedigital signal 372 from the A/D assembly 300 and filters, amplifies and/or encodes thedigital signal 372 to generate a processeddata signal 462. Power to thedata processor 400 is supplied viapower line 606 to theprogram counter 430. If included, theRF receiver 700 transmits the message signal 702 to theprogram counter 430 via message/control line 706 to control and synchronize telemetry operations. Thedata processor 400 may be configured to gate the data signal 462 to determine when to transmit the data signal 462 to theremote transponder 800. In addition, thedata processor 400 may also be configured to sum the data signal 462 with other data (i.e., from other sensors 210). As can be seen inFIG. 3 , thedata processor 400 includes asignal filter 410, anamplifier 420, aprogram counter 430, an interruptrequest device 442, acalculator 450 and adigital filter 460. Thesignal filter 410 is connected to the A/D assembly 300 and is configured to receive thedigital signal 372 and remove unwanted noise or aliasing components that may be included as a result of conversion of thesensor signal 234 from analog to digital. Thesignal filter 410 ultimately generates a filteredsignal 412. The filteredsignal 412 is in digital format and is made up of a series of high and low voltages. - Still referring to
FIG. 3 , theamplifier 420 is connected to thesignal filter 410 and is configured to receive the filteredsignal 412 therefrom and generate an amplifiedsignal 422 in response thereto. Theamplifier 420 isolates thedata processor 400 from the analog-to-digital conversion process and prepares the voltage level for a calculation stage. As was earlier mentioned, theprogram counter 430 is connected to theRF receiver 700 and thepower receiver 600 and is configured to receive respective ones of the message signal 702 and thepower signal 602. Theprogram counter 430 also generates a gated signal 432. The interruptrequest device 442 is connected to theprogram counter 430 and is configured to receive the gated signal 432 and generate an interruptrequest signal 442. - The
calculator 450 is connected to theamplifier 420 and the interruptrequest device 442 and is configured to receive respective ones of the filteredsignal 412, the amplifiedsignal 422 and the gated signal 432 and generate an encodedsignal 452. In this regard, theprogram counter 430, interruptrequest device 442 andcalculator 450 cooperate together in order to gate (i.e., start and stop) the signal and may additionally assign a unique message identification code (e.g., to identify the particular sensor(s) 210 from which the signal originated). In addition, error detection and prevention bits may be added to increase reliability and integrity of the signal by repeating a portion or all of the message in the same data packet. Thedigital filter 460 is connected to thecalculator 450 and is configured to receive the encodedsignal 452 therefrom and generate the data signal 462. Thedigital filter 460 shapes the series of high and low voltages that make up thedigital signal 372 for subsequent modulation by theRF transmitter 500. - Referring now to
FIG. 4 , the architecture of theRF transmitter 500 will be described in detail. In general, theRF transmitter 500 modulates the data signal 462 onto a radio carrier of a desired frequency, amplifies the modulated carrier and sends it to anRF transmitter antenna 501 for radiation to theremote transponder 800. Shown inFIG. 4 are subcomponents of theRF transmitter 500 comprising adata input filter 570, amodulator 580, afirst transmitter amplifier 530, atransmitter filter 540, asecond transmitter amplifier 520, a surface acoustic wave (SAW)filter 510 and theRF transmitter antenna 501. TheRF transmitter 500 is powered upon receiving thepower signal 602 at the modulator 580 from thepower receiver 600 viapower line 608. If the bio-sensor includes theRF receiver 700, the message signal 702 is also received therefrom at themodulator 580 via message/control line 708. Thedata input filter 570 is connected to thedata processor 400 and is configured to receive the data signal 462 therefrom to filter out high-frequency spectral components and generate a filtereddata signal 585 in response thereto. - Referring still to
FIG. 4 , themodulator 580 is connected to thepower receiver 600, theRF receiver 700 and thedata input filter 570 and is configured to pulse code modulate the filtered data signal 585 by varying an amplitude thereof and generating a first and second modulatedsignal first transmitter amplifier 530 is connected to themodulator 580 and is configured to receive the first modulatedsignal 583 therefrom. Thetransmitter filter 540 generates afeedback signal 532 which is received by thefirst transmitter amplifier 530. Thetransmitter filter 540 cooperates with thefirst transmitter amplifier 530 to create a first amplifiedsignal 522 at the desired frequency of radio transmission. Thesecond transmitter amplifier 520 is connected to themodulator 580 and thefirst transmitter amplifier 530 and is configured to receive respective ones of the second modulatedsignal 586 and the first amplifiedsignal 522 therefrom and generate a second amplifiedsignal 512 having a desired power level that is preferably sufficient for reliable transmission to theremote transponder 800. - As shown in
FIG. 4 , themodulator 580 also receives input from enable control 582 input and modulation control 584 input to aid in performing the modulation function. Themodulator 580 impresses (i.e., modulates via pulse-code modulation) the processed data in the data signal 462 onto the radio carrier via the first andsecond transmitter amplifiers modulated signals SAW filter 510 is connected to thesecond transmitter amplifier 520 and is configured to receive the second amplifiedsignal 512 and remove unwanted harmonics that may lie outside the allocated frequency spectrum for the type of radio service utilized by the bio-sensor system 10. TheSAW filter 510 generates a transmittedsignal 502 in response to the second amplifiedsignal 512. TheRF transmitter antenna 501 is connected to theSAW filter 510. The transmittedsignal 502 is passed to theRF transmitter antenna 501 which is configured to radiate the transmittedsignal 502 for receipt by the receivingantenna 801 of theremote transponder 800. - Referring now to
FIG. 6 , the circuit architecture of thepower receiver 600 will be described in detail. As was earlier mentioned, thepower receiver 600 is configured to collect power from thescanner signal 882. Thescanner signal 882 is received at a power receiver antenna 601 (for embodiments lacking the RF receiver 700). The power is delivered to the A/D assembly 300,data processor 400 andRF transmitter 500 viapower lines FIG. 6 , the subcomponents of thepower receiver 600 include asyntonic oscillator 610, arectifier 620, afilter 630, afirst regulator 650, asecond regulator 660 and asensor reference supply 640. Thesyntonic oscillator 610 may be connected to theRF receiver antenna 701 or to thepower receiver antenna 601. Thesyntonic oscillator 610 is configured to receive the scanner signal 882 (in sinusoidal form) and prepare thescanner signal 882 for conversion into a direct current (DC)voltage signal 632. - The
syntonic oscillator 610 is configured to generate an alternating current (AC)voltage signal 612 in response to thescanner signal 882. Thescanner signal 882 cycles between plus and minus currents and has an average current of zero micro-amps. Therectifier 620 is connected to thesyntonic oscillator 610 and is configured to receive theAC voltage signal 612 therefrom. Therectifier 620 sums positive currents and inverts negative currents by means of diode junctions such that all currents are added into one direction. The diodes have a threshold voltage that must be overcome and which creates discontinuities in current flow. In this manner, therectifier 620 generates the coursedirect voltage signal 622 that has discontinuities every half cycle. - The
filter 630 is connected to therectifier 620 and is configured to receive thedirect voltage signal 622 therefrom. Thefilter 630 has a capacitor (not shown) that is configured to store energy from cycles of the generally coarsedirect voltage signal 622 for release as a substantially smoothDC voltage signal 632. As was earlier mentioned, the voltage level is dependent on proximity of theremote transponder 800 and is preferably greater than that which is required to power the on-chip transponder 100. Thefirst regulator 650 is connected to thefilter 630 and is configured to receive the DC voltage signal 632 therefrom and generate afirst voltage signal 652 to power the A/D assembly 300, thedata processor 400 and theRF transmitter 500. - The
second regulator 660 is connected to thefilter 630 and is configured to receive the DC voltage signal 632 therefrom and generate asecond voltage signal 662 to power the A/D assembly 300, thedata processor 400 and theRF transmitter 500. The first andsecond regulators power signal 602 at a specific voltage level as required by the on-chip transponder 100, independent of proximity of theremote transponder 800 to the on-chip transponder 100.Power signal 602 is delivered to the A/D assembly 300, thedata processor 400 and theRF transmitter 500 viapower lines sensor reference supply 640 is connected to thefilter 630 and is configured to receive the DC voltage signal 632 therefrom and generate a sensorreference voltage signal 642 to supply power to thesensor assembly 200. - Referring briefly to
FIG. 7 , shown is a block diagram of theRF receiver 700 that may be included with the on-chip transponder 100. In general, theRF receiver 700 receives thescanner signal 882, which is decoded by theRF receiver 700, and alerts the on-chip transponder 100 that a request for data has been made. The decoded data informs the A/D assembly 300, thedata processor 400 and theRF transmitter 500 as to which data is to be sent and when to send the data. In general, theRF receiver 700 reverses all transmitter steps that are performed by theRF transmitter 500. Subcomponents of theRF receiver 700 include anRF receiver antenna 701, aSAW filter 710, afirst RF amplifier 720, aSAW delay 730, asecond RF amplifier 740, apulse generator 750 and a detector-filter 790. TheRF receiver antenna 701 is configured to receive thescanner signal 882 from theremote transponder 800. TheSAW filter 710 is connected to theRF receiver antenna 701 and is configured to receive thescanner signal 882 therefrom and filter thescanner signal 882 of unwanted signals that may overdrive or interfere with the operation of theRF receiver 700. - The
SAW filter 710 generates a filteredscanner signal 712 in response thereto. The filteredscanner signal 712 may be weak after filtering and is therefore boosted (i.e., amplified) by thefirst RF amplifier 720 to a level that may be detected by demodulation circuitry. The demodulation componentry is comprised of theSAW delay 730, thesecond RF amplifier 740 and thepulse generator 750 connected as shown inFIG. 7 . In general, the demodulating componentry cooperates to recover data contained in thescanner signal 882. Thefirst RF amplifier 720 is connected to theSAW filter 710 and is configured to receive the filteredscanner signal 712 therefrom and generate a first amplifiedRF signal 722 in response thereto. TheSAW delay 730 is connected to thefirst RF amplifier 720 and is configured to receive the first amplified RF signal 722 therefrom and generate a compared signal 732. - The
second RF amplifier 740 is connected to theSAW delay 730 and is configured to receive the compared signal 732 therefrom. Thepulse generator 750 is connected in parallel to theSAW delay 730 at the first andsecond RF amplifiers second RF amplifiers second RF amplifier 740 generates a second amplifiedRF signal 741. The detector-filter 790 is connected to thesecond RF amplifier 740 and is configured receive the second amplified RF signal 741 therefrom and extract data from thescanner signal 882 and generate themessage signal 702. The message signals 702 are passed to telemetry blocks of the A/D assembly 300, thedata processor 400 and theRF transmitter 500 via message/control lines sensor 210 reading has been requested. The message/control lines sensor 210 selection for configurations where the bio-sensor system 10 includes multiple ones of thesensors 210. - Referring now to
FIG. 2 , the circuit architecture of theremote transponder 800 will be described in detail. As shown, theremote transponder 800 may include transmitting subcomponents for transmitting data to the on-chip transponder 100 as well as receiving subcomponents for receiving the data contained in the data signal 462 which is transmitted by the on-chip transponder 100. The transmitting subcomponents may comprise anoscillator 860, anencoder 870, apower transmitter 880 and a transmittingantenna 883. Theoscillator 860 is configured to generate ananalog signal 862 at a predetermined frequency. Theencoder 870 is connected to theoscillator 860 and is configured to receive and modulate theanalog signal 862 and generate an encodedsignal 872 in response thereto. Thepower transmitter 880 is connected to theencoder 870 and is configured to receive and amplify the encodedsignal 872 and generate thescanner signal 882. The transmittingantenna 883 is connected to thepower transmitter 880 and is configured to receive thescanner signal 882 therefrom for radio transmission to the on-chip transponder 100. - Referring still to
FIG. 2 , theremote transponder 800 may also include the receiving subcomponents to allow receiving of thescanner signal 882 from the on-chip transponder 100. The receiving subcomponents of theremote transponder 800 are structurally and functionally equivalent to theRF receiver 700 as shown inFIG. 7 and as described above. The receiving components of theremote transponder 800 may comprise a receivingantenna 801, aSAW filter 810, afirst RF amplifier 820, aSAW delay 830, asecond RF amplifier 840, apulse generator 850 and a detector-filter 890. The receivingantenna 801 is configured to receive the transmittedsignal 502 from theRF transmitter 500. TheSAW filter 810 is connected to the receivingantenna 801 and is configured to receive and filter the transmittedsignal 502 of unwanted signals that may interfere with theremote transponder 800 and generate a filteredRF signal 812 in response thereto. Thefirst RF amplifier 820 is connected to theSAW filter 810 and is configured to receive the filtered RF signal 812 therefrom and generate a first amplifiedRF signal 822 in response thereto. - The SAW delay is connected to the
first RF amplifier 820 and is configured to receive the first amplified RF signal 822 therefrom and generate a comparedsignal 832. The second RF amplifier is connected to theSAW delay 830 and is configured to receive the comparedsignal 832 therefrom. The pulse generator is connected in parallel to theSAW delay 830 at the first andsecond RF amplifiers second RF amplifiers RF signal 841. The detector-filter 890 is connected to the second RF amplifier and is configured receive the second amplified RF signal 841 for extraction of digitized data therefrom. - As is also shown in
FIG. 2 , the bio-sensor system 10 may further include adecoder 900 connected to the detector-filter 890 bydata output lines sensors 210 wherein each one of thesensor 210 is operative to sense a physiological parameter of the patient and generate thesensor signal 234 in response thereto, thedecoder 900 may be configured to select one from among the plurality of sensor signals 234 from which to receive data. - The
decoder 900 may be configured to convert the digitized data back to original physiological data. Thedecoder 900 may also check the second amplified RF signal 841 for errors such that an operator may be notified whether or not the telemetry message was successfully received. Thedecoder 900 allows thesensor signal 234 data to be displayed on theremote transponder 800 such as a handheld device. Alternatively, thesensor signal 234 data may be stored in a computer database. The database may add a time stamp and patient information in order to make a complete record of the telemetry event. Combined with other records, trends and behavior may be graphed and analyzed. - Referring now to
FIGS. 1 and 2 , the operation of the bio-sensor system 10 will now be generally described. More specifically, the method of remotely monitoring physiological parameters using the bio-sensor system 10 will be described wherein the bio-sensor system 10 broadly comprises theremote transponder 800 and the on-chip transponder 100 having thesensor 210 and which is implantable in the patient. The method comprises the steps of remotely generating and wirelessly transmitting thescanner signal 882 with theremote transponder 800 wherein thescanner signal 882 contains radio signal power and a telemetry data request. Thescanner signal 882 is received at the on-chip transponder 100 whereupon thescanner signal 882 is filtered, amplified and demodulated to generate themessage signal 702. - Radio signal power is then collected from the
scanner signal 882 and thepower signal 602 is generated in response thereto. Simultaneously, upon being powered by the sensorreference voltage signal 642, thesensor 210 senses at least one physiological parameter of the patient in the manner as was described above and generates theanalog sensor signal 234. Thepower signal 602, theanalog sensor signal 234 and the message signal 702 are all received at the A/D assembly 300 which then generates thedigital signal 372 which is representative of the analog sensor signal. Thepower signal 602, the message signal 702 and thedigital signal 372 are then received at thedata processor 400 which prepares thedigital signal 372 for modulation. Thedata processor 400 then generates the data signal 462 which is representative of thedigital signal 372. Thepower signal 602, the message signal 702 and the data signal 462 are received at theRF transmitter 500 which then modulates, amplifies, filters and wirelessly transmits a transmittedsignal 502 from the on-chip transponder 100. Theremote transponder 800 then received the transmittedsignal 502 from the on-chip transponder 100 and extracts data that is representative of the physiological parameter of the patient. - Referring briefly to
FIG. 8 a, wherein thesensor 210 is configured as the 2-pin glucose sensor 210, the method may further comprise steps for enhancing the stability and precision of the power supplied to the electrode assembly 201 by first tuning thepower signal 602 with thefirst precision resistor 224 to generate the sensorreference voltage signal 642 at the level of about positive 0.7 volts. The sensorreference voltage signal 642 is received at the firstoperational amplifier 220 which generates the precision sensorreference voltage signal 223. Thevoltmeter 250 monitors the precision sensor reference voltage signal to establish asensor 210 operating point. The firstoperational amplifier 220 cooperates with thevoltmeter 250 to buffer the precision sensorreference voltage signal 223 in order to generate a substantially accurate sensorreference voltage signal 226. - The accurate sensor
reference voltage signal 226 is applied to the first terminal 202 to cause the reaction with the patient's blood which causes current to discharge from thesecond terminal 204 in the manner earlier described. The current discharges at thesecond terminal 204 in proportion to the glucose level. By tuning thesecond precision resistor 240, which is connected in series to the secondoperational amplifier 230, a voltage divider is formed with theglucose sensor 210. Thesecond precision resistor 240, in cooperation with the secondoperational amplifier 230, measures the level of discharging current and generates thesensor signal 234 which is substantially proportional to the glucose level of the patient. - Referring briefly to
FIG. 8 b, for the case where thesensor 210 is a 3-pin glucose sensor 210 including thethird terminal 206 that is co-located with the first andsecond terminals second terminal 204. This is performed by discharging current at thethird terminal 206 during application of the accurate sensorreference voltage signal 226 to the first terminal 202. The current from thethird terminal 206 is passes through theauxiliary control circuit 260 which is connected between the third electrode and the secondoperational amplifier 230. Theauxiliary control circuit 260 monitors and controls the amount of current discharging from thethird terminal 206 in order to stabilize the accurate sensorreference voltage signal 226 applied to the first terminal 202 which may increase the operational life of theglucose sensor 210. - Additional modifications and improvements of the present invention may also be apparent to those of ordinary skill in the art. Thus, the particular combination of parts described and illustrated herein is intended to represent only certain embodiments of the present invention, and is not intended to serve as limitations of alternative devices within the spirit and scope of the invention.
Claims (14)
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Cited By (77)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20070117511A1 (en) * | 2005-11-18 | 2007-05-24 | Samsung Electronics Co., Ltd. | RF receiving apparatus and method for removing leakage component of received signal using local signal |
US20080011861A1 (en) * | 2006-06-30 | 2008-01-17 | Takayuki Ikeda | Semiconductor device |
US20080164770A1 (en) * | 2007-01-05 | 2008-07-10 | Apple Inc | Wireless headset having adaptive powering |
US20080164934A1 (en) * | 2007-01-06 | 2008-07-10 | Apple Inc. | Connectors designed for ease of use |
US20080166005A1 (en) * | 2007-01-05 | 2008-07-10 | Apple Inc | Headset electronics |
US20080306360A1 (en) * | 2007-05-24 | 2008-12-11 | Robertson Timothy L | Low profile antenna for in body device |
US20090076338A1 (en) * | 2006-05-02 | 2009-03-19 | Zdeblick Mark J | Patient customized therapeutic regimens |
US20090082645A1 (en) * | 2007-09-25 | 2009-03-26 | Proteus Biomedical, Inc. | In-body device with virtual dipole signal amplification |
US20090118604A1 (en) * | 2007-11-02 | 2009-05-07 | Edwards Lifesciences Corporation | Analyte monitoring system having back-up power source for use in either transport of the system or primary power loss |
US20090135886A1 (en) * | 2007-11-27 | 2009-05-28 | Proteus Biomedical, Inc. | Transbody communication systems employing communication channels |
US20090188811A1 (en) * | 2007-11-28 | 2009-07-30 | Edwards Lifesciences Corporation | Preparation and maintenance of sensors |
US20090227204A1 (en) * | 2005-04-28 | 2009-09-10 | Timothy Robertson | Pharma-Informatics System |
US20100022836A1 (en) * | 2007-03-09 | 2010-01-28 | Olivier Colliou | In-body device having a multi-directional transmitter |
US20100185055A1 (en) * | 2007-02-01 | 2010-07-22 | Timothy Robertson | Ingestible event marker systems |
US20100316158A1 (en) * | 2006-11-20 | 2010-12-16 | Lawrence Arne | Active signal processing personal health signal receivers |
US20110054265A1 (en) * | 2009-04-28 | 2011-03-03 | Hooman Hafezi | Highly reliable ingestible event markers and methods for using the same |
US20110065983A1 (en) * | 2008-08-13 | 2011-03-17 | Hooman Hafezi | Ingestible Circuitry |
US20110196454A1 (en) * | 2008-11-18 | 2011-08-11 | Proteus Biomedical, Inc. | Sensing system, device, and method for therapy modulation |
US20110212782A1 (en) * | 2008-10-14 | 2011-09-01 | Andrew Thompson | Method and System for Incorporating Physiologic Data in a Gaming Environment |
US8036748B2 (en) | 2008-11-13 | 2011-10-11 | Proteus Biomedical, Inc. | Ingestible therapy activator system and method |
US8054140B2 (en) | 2006-10-17 | 2011-11-08 | Proteus Biomedical, Inc. | Low voltage oscillator for medical devices |
US8055334B2 (en) | 2008-12-11 | 2011-11-08 | Proteus Biomedical, Inc. | Evaluation of gastrointestinal function using portable electroviscerography systems and methods of using the same |
US8114021B2 (en) | 2008-12-15 | 2012-02-14 | Proteus Biomedical, Inc. | Body-associated receiver and method |
US8115635B2 (en) | 2005-02-08 | 2012-02-14 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8258962B2 (en) | 2008-03-05 | 2012-09-04 | Proteus Biomedical, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
US8540664B2 (en) | 2009-03-25 | 2013-09-24 | Proteus Digital Health, Inc. | Probablistic pharmacokinetic and pharmacodynamic modeling |
US8547248B2 (en) | 2005-09-01 | 2013-10-01 | Proteus Digital Health, Inc. | Implantable zero-wire communications system |
US8558563B2 (en) | 2009-08-21 | 2013-10-15 | Proteus Digital Health, Inc. | Apparatus and method for measuring biochemical parameters |
US8597186B2 (en) | 2009-01-06 | 2013-12-03 | Proteus Digital Health, Inc. | Pharmaceutical dosages delivery system |
US8602983B2 (en) | 2010-12-20 | 2013-12-10 | Covidien Lp | Access assembly having undercut structure |
US8641610B2 (en) | 2010-12-20 | 2014-02-04 | Covidien Lp | Access assembly with translating lumens |
US8696557B2 (en) | 2010-12-21 | 2014-04-15 | Covidien Lp | Access assembly including inflatable seal member |
US8730031B2 (en) | 2005-04-28 | 2014-05-20 | Proteus Digital Health, Inc. | Communication system using an implantable device |
US8784308B2 (en) | 2009-12-02 | 2014-07-22 | Proteus Digital Health, Inc. | Integrated ingestible event marker system with pharmaceutical product |
US8802183B2 (en) | 2005-04-28 | 2014-08-12 | Proteus Digital Health, Inc. | Communication system with enhanced partial power source and method of manufacturing same |
US8836513B2 (en) | 2006-04-28 | 2014-09-16 | Proteus Digital Health, Inc. | Communication system incorporated in an ingestible product |
US8868453B2 (en) | 2009-11-04 | 2014-10-21 | Proteus Digital Health, Inc. | System for supply chain management |
US8912908B2 (en) | 2005-04-28 | 2014-12-16 | Proteus Digital Health, Inc. | Communication system with remote activation |
US8945005B2 (en) | 2006-10-25 | 2015-02-03 | Proteus Digital Health, Inc. | Controlled activation ingestible identifier |
US8956288B2 (en) | 2007-02-14 | 2015-02-17 | Proteus Digital Health, Inc. | In-body power source having high surface area electrode |
US9014779B2 (en) | 2010-02-01 | 2015-04-21 | Proteus Digital Health, Inc. | Data gathering system |
US9107806B2 (en) | 2010-11-22 | 2015-08-18 | Proteus Digital Health, Inc. | Ingestible device with pharmaceutical product |
US9149423B2 (en) | 2009-05-12 | 2015-10-06 | Proteus Digital Health, Inc. | Ingestible event markers comprising an ingestible component |
US9198608B2 (en) | 2005-04-28 | 2015-12-01 | Proteus Digital Health, Inc. | Communication system incorporated in a container |
US9235683B2 (en) | 2011-11-09 | 2016-01-12 | Proteus Digital Health, Inc. | Apparatus, system, and method for managing adherence to a regimen |
US9268909B2 (en) | 2012-10-18 | 2016-02-23 | Proteus Digital Health, Inc. | Apparatus, system, and method to adaptively optimize power dissipation and broadcast power in a power source for a communication device |
US9270503B2 (en) | 2013-09-20 | 2016-02-23 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US9270025B2 (en) | 2007-03-09 | 2016-02-23 | Proteus Digital Health, Inc. | In-body device having deployable antenna |
US9271897B2 (en) | 2012-07-23 | 2016-03-01 | Proteus Digital Health, Inc. | Techniques for manufacturing ingestible event markers comprising an ingestible component |
US9294830B2 (en) | 2005-09-26 | 2016-03-22 | Apple Inc. | Wireless headset having adaptive powering |
US9439599B2 (en) | 2011-03-11 | 2016-09-13 | Proteus Digital Health, Inc. | Wearable personal body associated device with various physical configurations |
US9439566B2 (en) | 2008-12-15 | 2016-09-13 | Proteus Digital Health, Inc. | Re-wearable wireless device |
US9577864B2 (en) | 2013-09-24 | 2017-02-21 | Proteus Digital Health, Inc. | Method and apparatus for use with received electromagnetic signal at a frequency not known exactly in advance |
US9597487B2 (en) | 2010-04-07 | 2017-03-21 | Proteus Digital Health, Inc. | Miniature ingestible device |
US9603550B2 (en) | 2008-07-08 | 2017-03-28 | Proteus Digital Health, Inc. | State characterization based on multi-variate data fusion techniques |
US9649113B2 (en) | 2011-04-27 | 2017-05-16 | Covidien Lp | Device for monitoring physiological parameters in vivo |
US9659423B2 (en) | 2008-12-15 | 2017-05-23 | Proteus Digital Health, Inc. | Personal authentication apparatus system and method |
US9756874B2 (en) | 2011-07-11 | 2017-09-12 | Proteus Digital Health, Inc. | Masticable ingestible product and communication system therefor |
US9796576B2 (en) | 2013-08-30 | 2017-10-24 | Proteus Digital Health, Inc. | Container with electronically controlled interlock |
US9883819B2 (en) | 2009-01-06 | 2018-02-06 | Proteus Digital Health, Inc. | Ingestion-related biofeedback and personalized medical therapy method and system |
US9967646B2 (en) | 2007-01-06 | 2018-05-08 | Apple Inc. | Headset connector |
US10084880B2 (en) | 2013-11-04 | 2018-09-25 | Proteus Digital Health, Inc. | Social media networking based on physiologic information |
US10175376B2 (en) | 2013-03-15 | 2019-01-08 | Proteus Digital Health, Inc. | Metal detector apparatus, system, and method |
US10187121B2 (en) | 2016-07-22 | 2019-01-22 | Proteus Digital Health, Inc. | Electromagnetic sensing and detection of ingestible event markers |
US10223905B2 (en) | 2011-07-21 | 2019-03-05 | Proteus Digital Health, Inc. | Mobile device and system for detection and communication of information received from an ingestible device |
US10398161B2 (en) | 2014-01-21 | 2019-09-03 | Proteus Digital Heal Th, Inc. | Masticable ingestible product and communication system therefor |
US10420583B2 (en) | 2013-05-22 | 2019-09-24 | Covidien Lp | Methods and apparatus for controlling surgical instruments using a port assembly |
US10529044B2 (en) | 2010-05-19 | 2020-01-07 | Proteus Digital Health, Inc. | Tracking and delivery confirmation of pharmaceutical products |
US10582284B2 (en) | 2015-09-30 | 2020-03-03 | Apple Inc. | In-ear headphone |
US11006870B2 (en) | 2009-02-03 | 2021-05-18 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
US11051543B2 (en) | 2015-07-21 | 2021-07-06 | Otsuka Pharmaceutical Co. Ltd. | Alginate on adhesive bilayer laminate film |
US11149123B2 (en) | 2013-01-29 | 2021-10-19 | Otsuka Pharmaceutical Co., Ltd. | Highly-swellable polymeric films and compositions comprising the same |
US11158149B2 (en) | 2013-03-15 | 2021-10-26 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
EP3923295A1 (en) * | 2009-08-31 | 2021-12-15 | Abbott Diabetes Care, Inc. | Medical devices and methods |
US11529071B2 (en) | 2016-10-26 | 2022-12-20 | Otsuka Pharmaceutical Co., Ltd. | Methods for manufacturing capsules with ingestible event markers |
US11744481B2 (en) | 2013-03-15 | 2023-09-05 | Otsuka Pharmaceutical Co., Ltd. | System, apparatus and methods for data collection and assessing outcomes |
US11883028B2 (en) | 2021-09-08 | 2024-01-30 | Covidien Lp | Systems and methods for post-operative anastomotic leak detection |
Families Citing this family (266)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7899511B2 (en) | 2004-07-13 | 2011-03-01 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US9155496B2 (en) | 1997-03-04 | 2015-10-13 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US6175752B1 (en) | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US8346337B2 (en) | 1998-04-30 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8688188B2 (en) | 1998-04-30 | 2014-04-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US9066695B2 (en) | 1998-04-30 | 2015-06-30 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8974386B2 (en) | 1998-04-30 | 2015-03-10 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8480580B2 (en) | 1998-04-30 | 2013-07-09 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
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 |
US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
WO2002078512A2 (en) | 2001-04-02 | 2002-10-10 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
US20030032874A1 (en) | 2001-07-27 | 2003-02-13 | Dexcom, Inc. | Sensor head for use with implantable devices |
US9247901B2 (en) | 2003-08-22 | 2016-02-02 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US8260393B2 (en) | 2003-07-25 | 2012-09-04 | Dexcom, Inc. | Systems and methods for replacing signal data artifacts in a glucose sensor data stream |
US8010174B2 (en) | 2003-08-22 | 2011-08-30 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US6850788B2 (en) | 2002-03-25 | 2005-02-01 | Masimo Corporation | Physiological measurement communications adapter |
US7553295B2 (en) | 2002-06-17 | 2009-06-30 | Iradimed Corporation | Liquid infusion apparatus |
AU2003303597A1 (en) | 2002-12-31 | 2004-07-29 | Therasense, Inc. | Continuous glucose monitoring system and methods of use |
US7587287B2 (en) | 2003-04-04 | 2009-09-08 | Abbott Diabetes Care Inc. | Method and system for transferring analyte test data |
US7679407B2 (en) | 2003-04-28 | 2010-03-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing peak detection circuitry for data communication systems |
US8066639B2 (en) | 2003-06-10 | 2011-11-29 | Abbott Diabetes Care Inc. | Glucose measuring device for use in personal area network |
US8460243B2 (en) | 2003-06-10 | 2013-06-11 | Abbott Diabetes Care Inc. | Glucose measuring module and insulin pump combination |
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 |
US7074307B2 (en) | 2003-07-25 | 2006-07-11 | Dexcom, Inc. | Electrode systems for electrochemical sensors |
WO2007120442A2 (en) | 2003-07-25 | 2007-10-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US7519408B2 (en) | 2003-11-19 | 2009-04-14 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
US20080119703A1 (en) | 2006-10-04 | 2008-05-22 | Mark Brister | Analyte sensor |
US8060173B2 (en) | 2003-08-01 | 2011-11-15 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US9135402B2 (en) | 2007-12-17 | 2015-09-15 | Dexcom, Inc. | Systems and methods for processing sensor data |
US20190357827A1 (en) | 2003-08-01 | 2019-11-28 | Dexcom, Inc. | Analyte sensor |
US8160669B2 (en) | 2003-08-01 | 2012-04-17 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
US7774145B2 (en) | 2003-08-01 | 2010-08-10 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8622905B2 (en) | 2003-08-01 | 2014-01-07 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US20140121989A1 (en) | 2003-08-22 | 2014-05-01 | Dexcom, Inc. | Systems and methods for processing analyte sensor data |
US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
US8615282B2 (en) | 2004-07-13 | 2013-12-24 | Dexcom, Inc. | Analyte sensor |
US9247900B2 (en) | 2004-07-13 | 2016-02-02 | Dexcom, Inc. | Analyte sensor |
US8287453B2 (en) | 2003-12-05 | 2012-10-16 | Dexcom, Inc. | Analyte sensor |
EP1711790B1 (en) | 2003-12-05 | 2010-09-08 | DexCom, Inc. | Calibration techniques for a continuous analyte sensor |
US8423114B2 (en) | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8364231B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
US11633133B2 (en) | 2003-12-05 | 2023-04-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
EP1718198A4 (en) | 2004-02-17 | 2008-06-04 | Therasense Inc | Method and system for providing data communication in continuous glucose monitoring and management system |
US8808228B2 (en) | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
US7850676B2 (en) | 2004-04-19 | 2010-12-14 | The Invention Science Fund I, Llc | System with a reservoir for perfusion management |
US9801527B2 (en) | 2004-04-19 | 2017-10-31 | Gearbox, Llc | Lumen-traveling biological interface device |
US7998060B2 (en) | 2004-04-19 | 2011-08-16 | The Invention Science Fund I, Llc | Lumen-traveling delivery device |
US8092549B2 (en) | 2004-09-24 | 2012-01-10 | The Invention Science Fund I, Llc | Ciliated stent-like-system |
US8000784B2 (en) | 2004-04-19 | 2011-08-16 | The Invention Science Fund I, Llc | Lumen-traveling device |
US9011329B2 (en) | 2004-04-19 | 2015-04-21 | Searete Llc | Lumenally-active device |
US8353896B2 (en) | 2004-04-19 | 2013-01-15 | The Invention Science Fund I, Llc | Controllable release nasal system |
US8337482B2 (en) | 2004-04-19 | 2012-12-25 | The Invention Science Fund I, Llc | System for perfusion management |
US8024036B2 (en) | 2007-03-19 | 2011-09-20 | The Invention Science Fund I, Llc | Lumen-traveling biological interface device and method of use |
US8361013B2 (en) | 2004-04-19 | 2013-01-29 | The Invention Science Fund I, Llc | Telescoping perfusion management system |
US8792955B2 (en) | 2004-05-03 | 2014-07-29 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7125382B2 (en) * | 2004-05-20 | 2006-10-24 | Digital Angel Corporation | Embedded bio-sensor system |
CA2858901C (en) | 2004-06-04 | 2024-01-16 | Carolyn Anderson | Diabetes care host-client architecture and data management system |
US20060016700A1 (en) | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8565848B2 (en) | 2004-07-13 | 2013-10-22 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7783333B2 (en) | 2004-07-13 | 2010-08-24 | Dexcom, Inc. | Transcutaneous medical device with variable stiffness |
US7654956B2 (en) | 2004-07-13 | 2010-02-02 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8452368B2 (en) | 2004-07-13 | 2013-05-28 | Dexcom, Inc. | Transcutaneous analyte sensor |
WO2006127694A2 (en) | 2004-07-13 | 2006-11-30 | Dexcom, Inc. | Analyte sensor |
US8336553B2 (en) * | 2004-09-21 | 2012-12-25 | Medtronic Xomed, Inc. | Auto-titration of positive airway pressure machine with feedback from implantable sensor |
CN101088267B (en) * | 2004-11-19 | 2011-04-13 | 传感电子公司 | Device, system and method for communicating with backscatter radio frequency identification readers |
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 |
US20070149162A1 (en) * | 2005-02-24 | 2007-06-28 | Powercast, Llc | Pulse transmission method |
CA2596694A1 (en) * | 2005-02-24 | 2006-08-31 | Firefly Power Technologies, Inc. | Method, apparatus and system for power transmission |
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 |
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 |
US7768408B2 (en) | 2005-05-17 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US20060276702A1 (en) * | 2005-06-03 | 2006-12-07 | Mcginnis William | Neurophysiological wireless bio-sensor |
US8486070B2 (en) | 2005-08-23 | 2013-07-16 | Smith & Nephew, Inc. | Telemetric orthopaedic implant |
EP1921980A4 (en) | 2005-08-31 | 2010-03-10 | Univ Virginia | Improving the accuracy of continuous glucose sensors |
US8880138B2 (en) | 2005-09-30 | 2014-11-04 | Abbott Diabetes Care Inc. | Device for channeling fluid and methods of use |
US8211088B2 (en) * | 2005-10-14 | 2012-07-03 | Boston Scientific Scimed, Inc. | Catheter with controlled lumen recovery |
US7583190B2 (en) | 2005-10-31 | 2009-09-01 | Abbott Diabetes Care Inc. | Method and apparatus for providing data communication in data monitoring and management systems |
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 |
US7774038B2 (en) * | 2005-12-30 | 2010-08-10 | Medtronic Minimed, Inc. | Real-time self-calibrating sensor system and method |
US9757061B2 (en) | 2006-01-17 | 2017-09-12 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
ES2871822T3 (en) * | 2006-02-22 | 2021-11-02 | Dexcom Inc | Analyte sensor |
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 |
US8219173B2 (en) | 2008-09-30 | 2012-07-10 | Abbott Diabetes Care Inc. | Optimizing analyte sensor calibration |
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 |
US8346335B2 (en) | 2008-03-28 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte sensor calibration management |
US7620438B2 (en) | 2006-03-31 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for powering an electronic device |
US8226891B2 (en) | 2006-03-31 | 2012-07-24 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods therefor |
US20120035437A1 (en) | 2006-04-12 | 2012-02-09 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Navigation of a lumen traveling device toward a target |
US20080058785A1 (en) | 2006-04-12 | 2008-03-06 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Autofluorescent imaging and target ablation |
DE102006020866A1 (en) * | 2006-05-04 | 2007-11-15 | Siemens Ag | Analyte e.g. DNA, analyzer for use in biosensor, has transponder e.g. passive transponder, provided for wireless information exchange with selection device, which is electrically connected with oscillating crystal |
US20070279217A1 (en) * | 2006-06-01 | 2007-12-06 | H-Micro, Inc. | Integrated mobile healthcare system for cardiac care |
US7920907B2 (en) | 2006-06-07 | 2011-04-05 | Abbott Diabetes Care Inc. | Analyte monitoring system and method |
US8917178B2 (en) * | 2006-06-09 | 2014-12-23 | Dominic M. Kotab | RFID system and method for storing information related to a vehicle or an owner of the vehicle |
US9119582B2 (en) | 2006-06-30 | 2015-09-01 | Abbott Diabetes Care, Inc. | Integrated analyte sensor and infusion device and methods therefor |
US7724145B2 (en) * | 2006-07-20 | 2010-05-25 | Intelleflex Corporation | Self-charging RFID tag with long life |
US7831287B2 (en) | 2006-10-04 | 2010-11-09 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US20080092638A1 (en) * | 2006-10-19 | 2008-04-24 | Bayer Healthcare Llc | Wireless analyte monitoring system |
US9538657B2 (en) | 2012-06-29 | 2017-01-03 | General Electric Company | Resonant sensor and an associated sensing method |
US9658178B2 (en) | 2012-09-28 | 2017-05-23 | General Electric Company | Sensor systems for measuring an interface level in a multi-phase fluid composition |
US9589686B2 (en) | 2006-11-16 | 2017-03-07 | General Electric Company | Apparatus for detecting contaminants in a liquid and a system for use thereof |
US10914698B2 (en) | 2006-11-16 | 2021-02-09 | General Electric Company | Sensing method and system |
US9536122B2 (en) | 2014-11-04 | 2017-01-03 | General Electric Company | Disposable multivariable sensing devices having radio frequency based sensors |
DE102006056723B3 (en) * | 2006-12-01 | 2007-07-19 | Dräger Medical AG & Co. KG | Medical system for use in intensive care unit of hospital, has medical work station detecting physiological data of patient, and system allocating physiological data and patient data to one another based on marking signal |
US20080199894A1 (en) | 2007-02-15 | 2008-08-21 | Abbott Diabetes Care, Inc. | Device and method for automatic data acquisition and/or detection |
US8123686B2 (en) | 2007-03-01 | 2012-02-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing rolling data in communication systems |
US20080242950A1 (en) * | 2007-03-30 | 2008-10-02 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Computational user-health testing |
US8065240B2 (en) | 2007-10-31 | 2011-11-22 | The Invention Science Fund I | Computational user-health testing responsive to a user interaction with advertiser-configured content |
US20090112621A1 (en) * | 2007-10-30 | 2009-04-30 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Computational user-health testing responsive to a user interaction with advertiser-configured content |
US20090112616A1 (en) * | 2007-10-30 | 2009-04-30 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Polling for interest in computational user-health test output |
WO2009096992A1 (en) | 2007-04-14 | 2009-08-06 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in medical communication system |
WO2008130898A1 (en) | 2007-04-14 | 2008-10-30 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in medical communication system |
WO2008130897A2 (en) | 2007-04-14 | 2008-10-30 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in medical communication system |
CA2683930A1 (en) | 2007-04-14 | 2008-10-23 | 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 |
US8665091B2 (en) | 2007-05-08 | 2014-03-04 | Abbott Diabetes Care Inc. | Method and device for determining elapsed sensor life |
US8461985B2 (en) | 2007-05-08 | 2013-06-11 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8456301B2 (en) | 2007-05-08 | 2013-06-04 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US7928850B2 (en) | 2007-05-08 | 2011-04-19 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
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 |
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 |
US10002233B2 (en) | 2007-05-14 | 2018-06-19 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8444560B2 (en) | 2007-05-14 | 2013-05-21 | 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 |
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 |
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 |
EP2157907B1 (en) * | 2007-06-07 | 2013-03-27 | MicroCHIPS, Inc. | Electrochemical biosensors and arrays |
US20080306434A1 (en) | 2007-06-08 | 2008-12-11 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
AU2008265542B2 (en) | 2007-06-21 | 2014-07-24 | Abbott Diabetes Care Inc. | Health monitor |
US8597188B2 (en) | 2007-06-21 | 2013-12-03 | 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 |
US8330579B2 (en) | 2007-07-05 | 2012-12-11 | Baxter International Inc. | Radio-frequency auto-identification system for dialysis systems |
US8105282B2 (en) | 2007-07-13 | 2012-01-31 | Iradimed Corporation | System and method for communication with an infusion device |
JP5147321B2 (en) * | 2007-07-19 | 2013-02-20 | パナソニック株式会社 | Semiconductor integrated circuit and sensor drive / measurement system |
US8834366B2 (en) | 2007-07-31 | 2014-09-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
WO2009026289A2 (en) | 2007-08-20 | 2009-02-26 | Hmicro, Inc. | Wearable user interface device, system, and method of use |
US8926509B2 (en) * | 2007-08-24 | 2015-01-06 | Hmicro, Inc. | Wireless physiological sensor patches and systems |
JP6121088B2 (en) * | 2007-09-06 | 2017-04-26 | スミス アンド ネフュー インコーポレイテッド | System and method for communicating with a telemetric implant |
US11307201B2 (en) * | 2007-09-17 | 2022-04-19 | Red Ivory Llc | Self-actuating signal producing detection devices and methods |
US20100210919A1 (en) * | 2007-09-24 | 2010-08-19 | Arie Ariav | Method and apparatus for monitoring predetermined parameters in a body |
US9452258B2 (en) | 2007-10-09 | 2016-09-27 | Dexcom, Inc. | Integrated insulin delivery system with continuous glucose sensor |
US20110019824A1 (en) * | 2007-10-24 | 2011-01-27 | Hmicro, Inc. | Low power radiofrequency (rf) communication systems for secure wireless patch initialization and methods of use |
EP2212856A4 (en) * | 2007-10-24 | 2012-05-09 | Hmicro Inc | Method and apparatus to retrofit wired healthcare and fitness systems for wireless operation |
US8417312B2 (en) | 2007-10-25 | 2013-04-09 | Dexcom, Inc. | Systems and methods for processing sensor data |
US8290559B2 (en) | 2007-12-17 | 2012-10-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
US20090164239A1 (en) | 2007-12-19 | 2009-06-25 | Abbott Diabetes Care, Inc. | Dynamic Display Of Glucose Information |
CA2715628A1 (en) | 2008-02-21 | 2009-08-27 | Dexcom, Inc. | Systems and methods for processing, transmitting and displaying sensor data |
US8396528B2 (en) | 2008-03-25 | 2013-03-12 | Dexcom, Inc. | Analyte sensor |
EP3659628A1 (en) | 2008-04-10 | 2020-06-03 | Abbott Diabetes Care, Inc. | Method and system for sterilizing an analyte sensor |
AT505632B1 (en) * | 2008-05-14 | 2009-03-15 | Arc Austrian Res Centers Gmbh | METHOD FOR DATA TRANSMISSION |
US8429225B2 (en) | 2008-05-21 | 2013-04-23 | The Invention Science Fund I, Llc | Acquisition and presentation of data indicative of an extent of congruence between inferred mental states of authoring users |
US8615664B2 (en) * | 2008-05-23 | 2013-12-24 | The Invention Science Fund I, Llc | Acquisition and particular association of inference data indicative of an inferred mental state of an authoring user and source identity data |
US9161715B2 (en) * | 2008-05-23 | 2015-10-20 | Invention Science Fund I, Llc | Determination of extent of congruity between observation of authoring user and observation of receiving user |
US9192300B2 (en) * | 2008-05-23 | 2015-11-24 | Invention Science Fund I, Llc | Acquisition and particular association of data indicative of an inferred mental state of an authoring user |
US20090292658A1 (en) * | 2008-05-23 | 2009-11-26 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Acquisition and particular association of inference data indicative of inferred mental states of authoring users |
US9101263B2 (en) * | 2008-05-23 | 2015-08-11 | The Invention Science Fund I, Llc | Acquisition and association of data indicative of an inferred mental state of an authoring user |
US7826382B2 (en) | 2008-05-30 | 2010-11-02 | Abbott Diabetes Care Inc. | Close proximity communication device and methods |
WO2010009172A1 (en) | 2008-07-14 | 2010-01-21 | Abbott Diabetes Care Inc. | Closed loop control system interface and methods |
WO2010012035A1 (en) * | 2008-07-31 | 2010-02-04 | Newcastle Innovation Limited | A harmonics-based wireless transmission device and associated method |
WO2010033724A2 (en) | 2008-09-19 | 2010-03-25 | Dexcom, Inc. | Particle-containing membrane and particulate electrode for analyte sensors |
US9759202B2 (en) | 2008-12-04 | 2017-09-12 | Deep Science, Llc | Method for generation of power from intraluminal pressure changes |
US9631610B2 (en) | 2008-12-04 | 2017-04-25 | Deep Science, Llc | System for powering devices from intraluminal pressure changes |
US9526418B2 (en) * | 2008-12-04 | 2016-12-27 | Deep Science, Llc | Device for storage of intraluminally generated power |
US9353733B2 (en) * | 2008-12-04 | 2016-05-31 | Deep Science, Llc | Device and system for generation of power from intraluminal pressure changes |
US9567983B2 (en) * | 2008-12-04 | 2017-02-14 | Deep Science, Llc | Method for generation of power from intraluminal pressure changes |
US20100140958A1 (en) * | 2008-12-04 | 2010-06-10 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Method for powering devices from intraluminal pressure changes |
US20100160756A1 (en) * | 2008-12-24 | 2010-06-24 | Edwards Lifesciences Corporation | Membrane Layer for Electrochemical Biosensor and Method of Accommodating Electromagnetic and Radiofrequency Fields |
US8126736B2 (en) | 2009-01-23 | 2012-02-28 | Warsaw Orthopedic, Inc. | Methods and systems for diagnosing, treating, or tracking spinal disorders |
US8685093B2 (en) | 2009-01-23 | 2014-04-01 | Warsaw Orthopedic, Inc. | Methods and systems for diagnosing, treating, or tracking spinal disorders |
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 |
US20100213057A1 (en) * | 2009-02-26 | 2010-08-26 | Benjamin Feldman | Self-Powered Analyte Sensor |
US8497777B2 (en) | 2009-04-15 | 2013-07-30 | Abbott Diabetes Care Inc. | Analyte monitoring system having an alert |
TWI413770B (en) * | 2009-04-24 | 2013-11-01 | Univ Nat Taiwan | Wireless monitoring bio-diagnosis system |
WO2010127050A1 (en) | 2009-04-28 | 2010-11-04 | Abbott Diabetes Care Inc. | Error detection in critical repeating data in a wireless sensor system |
EP2424426B1 (en) | 2009-04-29 | 2020-01-08 | Abbott Diabetes Care, Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
EP2425209A4 (en) | 2009-04-29 | 2013-01-09 | Abbott Diabetes Care Inc | Method and system for providing real time analyte sensor calibration with retrospective backfill |
WO2010138856A1 (en) | 2009-05-29 | 2010-12-02 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
US8939928B2 (en) | 2009-07-23 | 2015-01-27 | Becton, Dickinson And Company | Medical device having capacitive coupling communication and energy harvesting |
EP4309580A3 (en) | 2009-07-23 | 2024-02-28 | Abbott Diabetes Care Inc. | Continuous analyte measurement system |
US8993331B2 (en) | 2009-08-31 | 2015-03-31 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods for managing power and noise |
US9314195B2 (en) | 2009-08-31 | 2016-04-19 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
WO2011026053A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Displays for a medical device |
US9795327B2 (en) * | 2009-09-24 | 2017-10-24 | Arkray, Inc. | Measuring apparatus and measurement method |
US20110077718A1 (en) * | 2009-09-30 | 2011-03-31 | Broadcom Corporation | Electromagnetic power booster for bio-medical units |
US8736425B2 (en) * | 2009-10-30 | 2014-05-27 | General Electric Company | Method and system for performance enhancement of resonant sensors |
WO2011112753A1 (en) | 2010-03-10 | 2011-09-15 | Abbott Diabetes Care Inc. | Systems, devices and methods for managing glucose levels |
LT3766408T (en) | 2010-03-24 | 2022-07-11 | Abbott Diabetes Care, Inc. | Medical device inserters |
CN101856218B (en) * | 2010-05-07 | 2012-11-14 | 浙江大学 | Implanted passive wireless acoustic surface wave sensor detection device |
CN101856222A (en) * | 2010-05-21 | 2010-10-13 | 上海锐灵电子科技有限公司 | Implanted wireless electronic detection device |
US20110295080A1 (en) * | 2010-05-30 | 2011-12-01 | Ralink Technology Corporation | Physiology Condition Detection Device and the System Thereof |
US8635046B2 (en) | 2010-06-23 | 2014-01-21 | Abbott Diabetes Care Inc. | Method and system for evaluating analyte sensor response characteristics |
EP2624745A4 (en) | 2010-10-07 | 2018-05-23 | Abbott Diabetes Care, Inc. | Analyte monitoring devices and methods |
US8542023B2 (en) | 2010-11-09 | 2013-09-24 | General Electric Company | Highly selective chemical and biological sensors |
CN102648845A (en) * | 2011-02-23 | 2012-08-29 | 深圳市迈迪加科技发展有限公司 | Automatic wireless monitoring and early-warning system for heartbeat and breath in sleep |
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 |
EP3583901A3 (en) | 2011-02-28 | 2020-01-15 | Abbott Diabetes Care, Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
ES2847578T3 (en) | 2011-04-15 | 2021-08-03 | Dexcom Inc | Advanced analyte sensor calibration and error detection |
JP6046115B2 (en) * | 2011-04-18 | 2016-12-14 | ノビオセンス ビー.ブイ. | Biosensor |
US8968377B2 (en) | 2011-05-09 | 2015-03-03 | The Invention Science Fund I, Llc | Method, device and system for modulating an activity of brown adipose tissue in a vertebrate subject |
US9238133B2 (en) | 2011-05-09 | 2016-01-19 | The Invention Science Fund I, Llc | Method, device and system for modulating an activity of brown adipose tissue in a vertebrate subject |
US8816814B2 (en) | 2011-08-16 | 2014-08-26 | Elwha Llc | Systematic distillation of status data responsive to whether or not a wireless signal has been received and relating to regimen compliance |
US9069536B2 (en) | 2011-10-31 | 2015-06-30 | Abbott Diabetes Care Inc. | Electronic devices having integrated reset systems and methods thereof |
WO2013066849A1 (en) | 2011-10-31 | 2013-05-10 | Abbott Diabetes Care Inc. | Model based variable risk false glucose threshold alarm prevention mechanism |
EP2775918B1 (en) * | 2011-11-07 | 2020-02-12 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods |
US9317656B2 (en) | 2011-11-23 | 2016-04-19 | Abbott Diabetes Care Inc. | Compatibility mechanisms for devices in a continuous 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 |
WO2013078426A2 (en) | 2011-11-25 | 2013-05-30 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods of use |
CN104769766B (en) * | 2012-02-17 | 2018-04-06 | 弗吉尼亚大学专利基金会以弗吉尼亚大学许可&合资集团名义经营 | Collection of energy and control for sensor node |
US10226212B2 (en) | 2012-04-12 | 2019-03-12 | Elwha Llc | Appurtenances to cavity wound dressings |
US10158928B2 (en) | 2012-04-12 | 2018-12-18 | Elwha Llc | Appurtenances for reporting information regarding wound dressings |
US10130518B2 (en) | 2012-04-12 | 2018-11-20 | Elwha Llc | Appurtenances including sensors for reporting information regarding wound dressings |
US9084530B2 (en) | 2012-04-12 | 2015-07-21 | Elwha Llc | Computational methods and systems for reporting information regarding appurtenances to wound dressings |
US10265219B2 (en) | 2012-04-12 | 2019-04-23 | Elwha Llc | Wound dressing monitoring systems including appurtenances for wound dressings |
US9024751B2 (en) | 2012-04-12 | 2015-05-05 | Elwha Llc | Dormant to active appurtenances for reporting information regarding wound dressings |
EP2653868A1 (en) * | 2012-04-18 | 2013-10-23 | NovioSense B.V. | Process for making biosensor |
US9011330B2 (en) * | 2012-07-09 | 2015-04-21 | California Institute Of Technology | Implantable vascular system biosensor with grown capillary beds and uses thereof |
US10598650B2 (en) | 2012-08-22 | 2020-03-24 | General Electric Company | System and method for measuring an operative condition of a machine |
DE112013004129T5 (en) | 2012-08-22 | 2015-05-21 | General Electric Company | Wireless system and method for measuring an operating condition of a machine |
EP2890297B1 (en) | 2012-08-30 | 2018-04-11 | 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 |
EP2901153A4 (en) | 2012-09-26 | 2016-04-27 | 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 |
US10684268B2 (en) | 2012-09-28 | 2020-06-16 | Bl Technologies, Inc. | Sensor systems for measuring an interface level in a multi-phase fluid composition |
CN102949760B (en) * | 2012-10-11 | 2016-10-12 | 深圳市深迈医疗设备有限公司 | Intelligent guardianship infusion pump |
US9173605B2 (en) * | 2012-12-13 | 2015-11-03 | California Institute Of Technology | Fabrication of implantable fully integrated electrochemical sensors |
US9585563B2 (en) * | 2012-12-31 | 2017-03-07 | Dexcom, Inc. | Remote monitoring of analyte measurements |
JP2016512443A (en) | 2013-02-06 | 2016-04-28 | カリフォルニア インスティチュート オブ テクノロジー | Miniaturized embedded electrochemical sensor device |
WO2014152034A1 (en) | 2013-03-15 | 2014-09-25 | Abbott Diabetes Care Inc. | Sensor fault detection using analyte sensor data pattern comparison |
US10433773B1 (en) | 2013-03-15 | 2019-10-08 | Abbott Diabetes Care Inc. | Noise rejection methods and apparatus for sparsely sampled analyte sensor data |
US9474475B1 (en) | 2013-03-15 | 2016-10-25 | Abbott Diabetes Care Inc. | Multi-rate analyte sensor data collection with sample rate configurable signal processing |
JP6568517B2 (en) * | 2013-04-30 | 2019-08-28 | アボット ダイアベティス ケア インコーポレイテッドAbbott Diabetes Care Inc. | Device for continuous glucose monitoring of a user and method for preparing a sensor control device for continuous analyte monitoring of a user |
TWI492739B (en) * | 2013-06-26 | 2015-07-21 | Shuenn Yuh Lee | A wireless bio-signal acquisition system and a bio-signal |
US9396428B2 (en) * | 2013-11-08 | 2016-07-19 | Gurbinder S Brar | Method for anchoring a linear induction generator to living tissue for RFID signal transmission |
US20170185748A1 (en) | 2014-03-30 | 2017-06-29 | Abbott Diabetes Care Inc. | Method and Apparatus for Determining Meal Start and Peak Events in Analyte Monitoring Systems |
US9878138B2 (en) | 2014-06-03 | 2018-01-30 | Pop Test Abuse Deterrent Technology Llc | Drug device configured for wireless communication |
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 |
CN105266213A (en) * | 2014-11-10 | 2016-01-27 | 北京至感传感器技术研究院有限公司 | Bra for checking breasts' physiological changes |
AU2015353585A1 (en) * | 2014-11-25 | 2017-06-01 | Abbott Diabetes Care Inc. | Analyte monitoring systems and related test and monitoring methods |
WO2017011346A1 (en) | 2015-07-10 | 2017-01-19 | Abbott Diabetes Care Inc. | System, device and method of dynamic glucose profile response to physiological parameters |
US10820844B2 (en) | 2015-07-23 | 2020-11-03 | California Institute Of Technology | Canary on a chip: embedded sensors with bio-chemical interfaces |
US9706269B2 (en) * | 2015-07-24 | 2017-07-11 | Hong Kong Applied Science and Technology Research Institute Company, Limited | Self-powered and battery-assisted CMOS wireless bio-sensing IC platform |
WO2017044702A1 (en) | 2015-09-11 | 2017-03-16 | Pop Test LLC | Therapeutic method and device |
CA3200794A1 (en) | 2015-12-28 | 2017-07-06 | Dexcom, Inc. | Systems and methods for remote and host monitoring communications |
US11529194B2 (en) * | 2016-03-31 | 2022-12-20 | Koninklijke Philips N.V. | Wireless position determination |
JP6650534B2 (en) * | 2016-08-08 | 2020-02-19 | ウェルビーイングソフト インク. | Portable composite sensor device for measuring a plurality of biological information and measurement method |
US10765807B2 (en) * | 2016-09-23 | 2020-09-08 | Insulet Corporation | Fluid delivery device with sensor |
KR101925424B1 (en) | 2016-11-04 | 2018-12-06 | (주)제이디 | Process monitoring circuit being embeded on wafer |
WO2018175489A1 (en) | 2017-03-21 | 2018-09-27 | Abbott Diabetes Care Inc. | Methods, devices and system for providing diabetic condition diagnosis and therapy |
CN107296615A (en) * | 2017-08-28 | 2017-10-27 | 山东连发医用塑胶制品有限公司 | Disposable blood glucose automatic information collecting detecting system |
US11017892B1 (en) | 2017-09-11 | 2021-05-25 | Massachusetts Mutual Life Insurance Company | System and method for ingestible drug delivery |
US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
CN111246797A (en) | 2017-10-24 | 2020-06-05 | 德克斯康公司 | Pre-attached analyte sensors |
US11268506B2 (en) | 2017-12-22 | 2022-03-08 | Iradimed Corporation | Fluid pumps for use in MRI environment |
CN115943737A (en) | 2018-08-01 | 2023-04-07 | 伟创力有限公司 | Biosensing integrated garment |
CN112584894A (en) * | 2018-08-31 | 2021-03-30 | 豪夫迈·罗氏有限公司 | Modular implantable medical device |
CN109917311B (en) * | 2019-03-22 | 2022-05-24 | 上海联影医疗科技股份有限公司 | Magnetic resonance multi-antenna radio frequency transmission device and magnetic resonance system |
US20210030331A1 (en) * | 2019-08-02 | 2021-02-04 | Bionime Corporation | Implantable micro-biosensor |
US11415619B2 (en) * | 2019-09-13 | 2022-08-16 | Joe David Watson | Digital modulation/demodulation with active monitoring for measurement of power factor and capacitance in high-voltage bushings, transformers, reactors, and other electrical equipment with high-voltage insulation |
CN111603175A (en) * | 2020-05-25 | 2020-09-01 | 上海梅斯医药科技有限公司 | Subcutaneous semi-implanted blood glucose monitoring method, terminal equipment and server |
CN111603176A (en) * | 2020-05-25 | 2020-09-01 | 上海梅斯医药科技有限公司 | Semi-implanted optical blood glucose monitoring method, terminal equipment and server |
US20230248270A1 (en) * | 2020-06-24 | 2023-08-10 | Richard Postrel | Autonomous bio-powered nano devices for improving health and quality of life |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6295466B1 (en) * | 1999-01-06 | 2001-09-25 | Ball Semiconductor, Inc. | Wireless EKG |
US6366794B1 (en) * | 1998-11-20 | 2002-04-02 | The University Of Connecticut | Generic integrated implantable potentiostat telemetry unit for electrochemical sensors |
US6546268B1 (en) * | 1999-06-02 | 2003-04-08 | Ball Semiconductor, Inc. | Glucose sensor |
US6579498B1 (en) * | 1998-03-20 | 2003-06-17 | David Eglise | Implantable blood glucose sensor system |
US6659948B2 (en) * | 2000-01-21 | 2003-12-09 | Medtronic Minimed, Inc. | Ambulatory medical apparatus and method using a telemetry system with predefined reception listening periods |
US7125382B2 (en) * | 2004-05-20 | 2006-10-24 | Digital Angel Corporation | Embedded bio-sensor system |
Family Cites Families (15)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4655880A (en) * | 1983-08-01 | 1987-04-07 | Case Western Reserve University | Apparatus and method for sensing species, substances and substrates using oxidase |
US5597534A (en) * | 1994-07-05 | 1997-01-28 | Texas Instruments Deutschland Gmbh | Apparatus for wireless chemical sensing |
US5711861A (en) * | 1995-11-22 | 1998-01-27 | Ward; W. Kenneth | Device for monitoring changes in analyte concentration |
US5704352A (en) * | 1995-11-22 | 1998-01-06 | Tremblay; Gerald F. | Implantable passive bio-sensor |
US5914026A (en) * | 1997-01-06 | 1999-06-22 | Implanted Biosystems Inc. | Implantable sensor employing an auxiliary electrode |
US6239724B1 (en) * | 1997-12-30 | 2001-05-29 | Remon Medical Technologies, Ltd. | System and method for telemetrically providing intrabody spatial position |
US6254548B1 (en) * | 1998-11-25 | 2001-07-03 | Ball Semiconductor, Inc. | Internal thermometer |
WO2000038570A1 (en) * | 1998-12-31 | 2000-07-06 | Ball Semiconductor, Inc. | Miniature implanted orthopedic sensors |
US6415184B1 (en) * | 1999-01-06 | 2002-07-02 | Ball Semiconductor, Inc. | Implantable neuro-stimulator with ball implant |
GB9907815D0 (en) * | 1999-04-06 | 1999-06-02 | Univ Cambridge Tech | Implantable sensor |
US20030114769A1 (en) * | 1999-08-20 | 2003-06-19 | Capital Tool Company Limited | Microminiature radiotelemetrically operated sensors for small animal research |
EP1259992B1 (en) * | 2000-02-23 | 2011-10-05 | SRI International | Biologically powered electroactive polymer generators |
US6559620B2 (en) * | 2001-03-21 | 2003-05-06 | Digital Angel Corporation | System and method for remote monitoring utilizing a rechargeable battery |
KR100380653B1 (en) * | 2000-09-05 | 2003-04-23 | 삼성전자주식회사 | Compressor assembly |
US20020103425A1 (en) * | 2000-09-27 | 2002-08-01 | Mault James R. | self-contained monitoring device particularly useful for monitoring physiological conditions |
-
2004
- 2004-05-20 US US10/849,614 patent/US7125382B2/en not_active Expired - Fee Related
- 2004-05-20 US US10/850,315 patent/US7241266B2/en not_active Expired - Fee Related
-
2005
- 2005-05-20 JP JP2007527472A patent/JP2007537841A/en active Pending
- 2005-05-20 CA CA002563953A patent/CA2563953A1/en not_active Abandoned
- 2005-05-20 WO PCT/US2005/017723 patent/WO2005112744A1/en active Application Filing
- 2005-05-20 MX MXPA06012810A patent/MXPA06012810A/en unknown
- 2005-05-20 CN CNA2005800161549A patent/CN101022760A/en active Pending
- 2005-05-20 EP EP05751113A patent/EP1750577A4/en not_active Withdrawn
- 2005-05-20 AU AU2005244973A patent/AU2005244973A1/en not_active Abandoned
-
2006
- 2006-10-18 US US11/582,790 patent/US7297112B2/en not_active Expired - Fee Related
-
2007
- 2007-10-15 US US11/872,553 patent/US20080033273A1/en not_active Abandoned
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6579498B1 (en) * | 1998-03-20 | 2003-06-17 | David Eglise | Implantable blood glucose sensor system |
US6366794B1 (en) * | 1998-11-20 | 2002-04-02 | The University Of Connecticut | Generic integrated implantable potentiostat telemetry unit for electrochemical sensors |
US6295466B1 (en) * | 1999-01-06 | 2001-09-25 | Ball Semiconductor, Inc. | Wireless EKG |
US6546268B1 (en) * | 1999-06-02 | 2003-04-08 | Ball Semiconductor, Inc. | Glucose sensor |
US6659948B2 (en) * | 2000-01-21 | 2003-12-09 | Medtronic Minimed, Inc. | Ambulatory medical apparatus and method using a telemetry system with predefined reception listening periods |
US7125382B2 (en) * | 2004-05-20 | 2006-10-24 | Digital Angel Corporation | Embedded bio-sensor system |
US7241266B2 (en) * | 2004-05-20 | 2007-07-10 | Digital Angel Corporation | Transducer for embedded bio-sensor using body energy as a power source |
US7297112B2 (en) * | 2004-05-20 | 2007-11-20 | Digital Angel Corporation | Embedded bio-sensor system |
Cited By (183)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8542122B2 (en) | 2005-02-08 | 2013-09-24 | Abbott Diabetes Care Inc. | Glucose measurement device and methods using RFID |
US8115635B2 (en) | 2005-02-08 | 2012-02-14 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8358210B2 (en) | 2005-02-08 | 2013-01-22 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8390455B2 (en) | 2005-02-08 | 2013-03-05 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US8223021B2 (en) | 2005-02-08 | 2012-07-17 | Abbott Diabetes Care Inc. | RF tag on test strips, test strip vials and boxes |
US9681842B2 (en) | 2005-04-28 | 2017-06-20 | Proteus Digital Health, Inc. | Pharma-informatics system |
US9962107B2 (en) | 2005-04-28 | 2018-05-08 | Proteus Digital Health, Inc. | Communication system with enhanced partial power source and method of manufacturing same |
US8802183B2 (en) | 2005-04-28 | 2014-08-12 | Proteus Digital Health, Inc. | Communication system with enhanced partial power source and method of manufacturing same |
US10610128B2 (en) | 2005-04-28 | 2020-04-07 | Proteus Digital Health, Inc. | Pharma-informatics system |
US10542909B2 (en) | 2005-04-28 | 2020-01-28 | Proteus Digital Health, Inc. | Communication system with partial power source |
US10517507B2 (en) | 2005-04-28 | 2019-12-31 | Proteus Digital Health, Inc. | Communication system with enhanced partial power source and method of manufacturing same |
US20090227204A1 (en) * | 2005-04-28 | 2009-09-10 | Timothy Robertson | Pharma-Informatics System |
US8730031B2 (en) | 2005-04-28 | 2014-05-20 | Proteus Digital Health, Inc. | Communication system using an implantable device |
US11476952B2 (en) | 2005-04-28 | 2022-10-18 | Otsuka Pharmaceutical Co., Ltd. | Pharma-informatics system |
US20100081894A1 (en) * | 2005-04-28 | 2010-04-01 | Proteus Biomedical, Inc. | Communication system with partial power source |
US9119554B2 (en) | 2005-04-28 | 2015-09-01 | Proteus Digital Health, Inc. | Pharma-informatics system |
US9161707B2 (en) | 2005-04-28 | 2015-10-20 | Proteus Digital Health, Inc. | Communication system incorporated in an ingestible product |
US9198608B2 (en) | 2005-04-28 | 2015-12-01 | Proteus Digital Health, Inc. | Communication system incorporated in a container |
US8912908B2 (en) | 2005-04-28 | 2014-12-16 | Proteus Digital Health, Inc. | Communication system with remote activation |
US9439582B2 (en) | 2005-04-28 | 2016-09-13 | Proteus Digital Health, Inc. | Communication system with remote activation |
US7978064B2 (en) | 2005-04-28 | 2011-07-12 | Proteus Biomedical, Inc. | Communication system with partial power source |
US8847766B2 (en) | 2005-04-28 | 2014-09-30 | Proteus Digital Health, Inc. | Pharma-informatics system |
US9649066B2 (en) | 2005-04-28 | 2017-05-16 | Proteus Digital Health, Inc. | Communication system with partial power source |
US9597010B2 (en) | 2005-04-28 | 2017-03-21 | Proteus Digital Health, Inc. | Communication system using an implantable device |
US8816847B2 (en) | 2005-04-28 | 2014-08-26 | Proteus Digital Health, Inc. | Communication system with partial power source |
US8674825B2 (en) | 2005-04-28 | 2014-03-18 | Proteus Digital Health, Inc. | Pharma-informatics system |
US8547248B2 (en) | 2005-09-01 | 2013-10-01 | Proteus Digital Health, Inc. | Implantable zero-wire communications system |
US9854343B2 (en) | 2005-09-26 | 2017-12-26 | Apple Inc. | Headset connector |
US9294830B2 (en) | 2005-09-26 | 2016-03-22 | Apple Inc. | Wireless headset having adaptive powering |
US9287657B2 (en) | 2005-09-26 | 2016-03-15 | Apple Inc. | Headset connector |
US20070117511A1 (en) * | 2005-11-18 | 2007-05-24 | Samsung Electronics Co., Ltd. | RF receiving apparatus and method for removing leakage component of received signal using local signal |
US7689170B2 (en) * | 2005-11-18 | 2010-03-30 | Samsung Electronics Co., Ltd. | RF receiving apparatus and method for removing leakage component of received signal using local signal |
US8836513B2 (en) | 2006-04-28 | 2014-09-16 | Proteus Digital Health, Inc. | Communication system incorporated in an ingestible product |
US11928614B2 (en) | 2006-05-02 | 2024-03-12 | Otsuka Pharmaceutical Co., Ltd. | Patient customized therapeutic regimens |
US20090076338A1 (en) * | 2006-05-02 | 2009-03-19 | Zdeblick Mark J | Patient customized therapeutic regimens |
US8956287B2 (en) | 2006-05-02 | 2015-02-17 | Proteus Digital Health, Inc. | Patient customized therapeutic regimens |
US7832647B2 (en) | 2006-06-30 | 2010-11-16 | Semiconductor Energy Laboratory Co., Ltd. | Semiconductor device |
US8261999B2 (en) | 2006-06-30 | 2012-09-11 | Semiconductor Energy Laboratory Co., Ltd. | Semiconductor device |
US20080011861A1 (en) * | 2006-06-30 | 2008-01-17 | Takayuki Ikeda | Semiconductor device |
US8054140B2 (en) | 2006-10-17 | 2011-11-08 | Proteus Biomedical, Inc. | Low voltage oscillator for medical devices |
US11357730B2 (en) | 2006-10-25 | 2022-06-14 | Otsuka Pharmaceutical Co., Ltd. | Controlled activation ingestible identifier |
US8945005B2 (en) | 2006-10-25 | 2015-02-03 | Proteus Digital Health, Inc. | Controlled activation ingestible identifier |
US10238604B2 (en) | 2006-10-25 | 2019-03-26 | Proteus Digital Health, Inc. | Controlled activation ingestible identifier |
US8718193B2 (en) | 2006-11-20 | 2014-05-06 | Proteus Digital Health, Inc. | Active signal processing personal health signal receivers |
US9083589B2 (en) | 2006-11-20 | 2015-07-14 | Proteus Digital Health, Inc. | Active signal processing personal health signal receivers |
US20100316158A1 (en) * | 2006-11-20 | 2010-12-16 | Lawrence Arne | Active signal processing personal health signal receivers |
US9444503B2 (en) | 2006-11-20 | 2016-09-13 | Proteus Digital Health, Inc. | Active signal processing personal health signal receivers |
US20080166005A1 (en) * | 2007-01-05 | 2008-07-10 | Apple Inc | Headset electronics |
US8650925B2 (en) | 2007-01-05 | 2014-02-18 | Apple Inc. | Extrusion method for fabricating a compact tube with internal features |
US20080164770A1 (en) * | 2007-01-05 | 2008-07-10 | Apple Inc | Wireless headset having adaptive powering |
US8867758B2 (en) | 2007-01-05 | 2014-10-21 | Apple Inc. | Headset electronics |
US8712071B2 (en) | 2007-01-05 | 2014-04-29 | Apple Inc. | Headset electronics |
US8185084B2 (en) * | 2007-01-05 | 2012-05-22 | Apple Inc. | Wireless headset having adaptive powering |
US10516931B2 (en) | 2007-01-06 | 2019-12-24 | Apple Inc. | Headset connector |
US11877112B2 (en) | 2007-01-06 | 2024-01-16 | Apple Inc. | In-ear wireless device |
US20180255389A1 (en) | 2007-01-06 | 2018-09-06 | Apple Inc. | Headset connector |
US9118990B2 (en) | 2007-01-06 | 2015-08-25 | Apple Inc. | Connectors designed for ease of use |
US9967646B2 (en) | 2007-01-06 | 2018-05-08 | Apple Inc. | Headset connector |
US10165346B2 (en) | 2007-01-06 | 2018-12-25 | Apple Inc. | Headset connector |
US10993011B2 (en) | 2007-01-06 | 2021-04-27 | Apple Inc. | In-ear wireless listening device |
US10979796B2 (en) | 2007-01-06 | 2021-04-13 | Apple Inc. | In-ear wireless listening device |
US10433043B2 (en) | 2007-01-06 | 2019-10-01 | Apple Inc. | In-ear listening device |
US20080164934A1 (en) * | 2007-01-06 | 2008-07-10 | Apple Inc. | Connectors designed for ease of use |
US10771880B1 (en) | 2007-01-06 | 2020-09-08 | Apple Inc. | In-ear wireless device |
US10959006B2 (en) | 2007-01-06 | 2021-03-23 | Apple Inc. | In-ear wireless listening device |
US11336985B2 (en) | 2007-01-06 | 2022-05-17 | Apple Inc. | In-ear wireless device |
US10313775B2 (en) | 2007-01-06 | 2019-06-04 | Apple Inc. | Portable listening device system |
US20100185055A1 (en) * | 2007-02-01 | 2010-07-22 | Timothy Robertson | Ingestible event marker systems |
US8858432B2 (en) | 2007-02-01 | 2014-10-14 | Proteus Digital Health, Inc. | Ingestible event marker systems |
US10441194B2 (en) | 2007-02-01 | 2019-10-15 | Proteus Digital Heal Th, Inc. | Ingestible event marker systems |
US8956288B2 (en) | 2007-02-14 | 2015-02-17 | Proteus Digital Health, Inc. | In-body power source having high surface area electrode |
US11464423B2 (en) | 2007-02-14 | 2022-10-11 | Otsuka Pharmaceutical Co., Ltd. | In-body power source having high surface area electrode |
US8932221B2 (en) | 2007-03-09 | 2015-01-13 | Proteus Digital Health, Inc. | In-body device having a multi-directional transmitter |
US9270025B2 (en) | 2007-03-09 | 2016-02-23 | Proteus Digital Health, Inc. | In-body device having deployable antenna |
US20100022836A1 (en) * | 2007-03-09 | 2010-01-28 | Olivier Colliou | In-body device having a multi-directional transmitter |
US20080306360A1 (en) * | 2007-05-24 | 2008-12-11 | Robertson Timothy L | Low profile antenna for in body device |
US8115618B2 (en) | 2007-05-24 | 2012-02-14 | Proteus Biomedical, Inc. | RFID antenna for in-body device |
US10517506B2 (en) | 2007-05-24 | 2019-12-31 | Proteus Digital Health, Inc. | Low profile antenna for in body device |
US8540632B2 (en) | 2007-05-24 | 2013-09-24 | Proteus Digital Health, Inc. | Low profile antenna for in body device |
US20090082645A1 (en) * | 2007-09-25 | 2009-03-26 | Proteus Biomedical, Inc. | In-body device with virtual dipole signal amplification |
US9433371B2 (en) | 2007-09-25 | 2016-09-06 | Proteus Digital Health, Inc. | In-body device with virtual dipole signal amplification |
US8961412B2 (en) | 2007-09-25 | 2015-02-24 | Proteus Digital Health, Inc. | In-body device with virtual dipole signal amplification |
US20090118604A1 (en) * | 2007-11-02 | 2009-05-07 | Edwards Lifesciences Corporation | Analyte monitoring system having back-up power source for use in either transport of the system or primary power loss |
US20090135886A1 (en) * | 2007-11-27 | 2009-05-28 | Proteus Biomedical, Inc. | Transbody communication systems employing communication channels |
US20090188811A1 (en) * | 2007-11-28 | 2009-07-30 | Edwards Lifesciences Corporation | Preparation and maintenance of sensors |
US8834703B2 (en) | 2007-11-28 | 2014-09-16 | Edwards Lifesciences Corporation | Preparation and maintenance of sensors |
US9258035B2 (en) | 2008-03-05 | 2016-02-09 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
US8810409B2 (en) | 2008-03-05 | 2014-08-19 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
US8258962B2 (en) | 2008-03-05 | 2012-09-04 | Proteus Biomedical, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
US8542123B2 (en) | 2008-03-05 | 2013-09-24 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
US9060708B2 (en) | 2008-03-05 | 2015-06-23 | Proteus Digital Health, Inc. | Multi-mode communication ingestible event markers and systems, and methods of using the same |
US10682071B2 (en) | 2008-07-08 | 2020-06-16 | Proteus Digital Health, Inc. | State characterization based on multi-variate data fusion techniques |
US9603550B2 (en) | 2008-07-08 | 2017-03-28 | Proteus Digital Health, Inc. | State characterization based on multi-variate data fusion techniques |
US11217342B2 (en) | 2008-07-08 | 2022-01-04 | Otsuka Pharmaceutical Co., Ltd. | Ingestible event marker data framework |
US8540633B2 (en) | 2008-08-13 | 2013-09-24 | Proteus Digital Health, Inc. | Identifier circuits for generating unique identifiable indicators and techniques for producing same |
US20110065983A1 (en) * | 2008-08-13 | 2011-03-17 | Hooman Hafezi | Ingestible Circuitry |
US9415010B2 (en) | 2008-08-13 | 2016-08-16 | Proteus Digital Health, Inc. | Ingestible circuitry |
US8721540B2 (en) | 2008-08-13 | 2014-05-13 | Proteus Digital Health, Inc. | Ingestible circuitry |
US20110212782A1 (en) * | 2008-10-14 | 2011-09-01 | Andrew Thompson | Method and System for Incorporating Physiologic Data in a Gaming Environment |
US8036748B2 (en) | 2008-11-13 | 2011-10-11 | Proteus Biomedical, Inc. | Ingestible therapy activator system and method |
US20110196454A1 (en) * | 2008-11-18 | 2011-08-11 | Proteus Biomedical, Inc. | Sensing system, device, and method for therapy modulation |
US8583227B2 (en) | 2008-12-11 | 2013-11-12 | Proteus Digital Health, Inc. | Evaluation of gastrointestinal function using portable electroviscerography systems and methods of using the same |
US8055334B2 (en) | 2008-12-11 | 2011-11-08 | Proteus Biomedical, Inc. | Evaluation of gastrointestinal function using portable electroviscerography systems and methods of using the same |
US8114021B2 (en) | 2008-12-15 | 2012-02-14 | Proteus Biomedical, Inc. | Body-associated receiver and method |
US9439566B2 (en) | 2008-12-15 | 2016-09-13 | Proteus Digital Health, Inc. | Re-wearable wireless device |
US8545436B2 (en) | 2008-12-15 | 2013-10-01 | Proteus Digital Health, Inc. | Body-associated receiver and method |
US9149577B2 (en) | 2008-12-15 | 2015-10-06 | Proteus Digital Health, Inc. | Body-associated receiver and method |
US9659423B2 (en) | 2008-12-15 | 2017-05-23 | Proteus Digital Health, Inc. | Personal authentication apparatus system and method |
US9883819B2 (en) | 2009-01-06 | 2018-02-06 | Proteus Digital Health, Inc. | Ingestion-related biofeedback and personalized medical therapy method and system |
US8597186B2 (en) | 2009-01-06 | 2013-12-03 | Proteus Digital Health, Inc. | Pharmaceutical dosages delivery system |
US11166656B2 (en) | 2009-02-03 | 2021-11-09 | 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 |
US11213229B2 (en) | 2009-02-03 | 2022-01-04 | 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 |
EP3730044B1 (en) | 2009-02-03 | 2021-12-29 | Abbott Diabetes Care, Inc. | Compact on-body physiological monitoring device |
US11006871B2 (en) | 2009-02-03 | 2021-05-18 | 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 |
US9119918B2 (en) | 2009-03-25 | 2015-09-01 | Proteus Digital Health, Inc. | Probablistic pharmacokinetic and pharmacodynamic modeling |
US8540664B2 (en) | 2009-03-25 | 2013-09-24 | Proteus Digital Health, Inc. | Probablistic pharmacokinetic and pharmacodynamic modeling |
US9320455B2 (en) | 2009-04-28 | 2016-04-26 | Proteus Digital Health, Inc. | Highly reliable ingestible event markers and methods for using the same |
US8545402B2 (en) | 2009-04-28 | 2013-10-01 | Proteus Digital Health, Inc. | Highly reliable ingestible event markers and methods for using the same |
US10588544B2 (en) | 2009-04-28 | 2020-03-17 | Proteus Digital Health, Inc. | Highly reliable ingestible event markers and methods for using the same |
US20110054265A1 (en) * | 2009-04-28 | 2011-03-03 | Hooman Hafezi | Highly reliable ingestible event markers and methods for using the same |
US9149423B2 (en) | 2009-05-12 | 2015-10-06 | Proteus Digital Health, Inc. | Ingestible event markers comprising an ingestible component |
US8558563B2 (en) | 2009-08-21 | 2013-10-15 | Proteus Digital Health, Inc. | Apparatus and method for measuring biochemical parameters |
EP3923295A1 (en) * | 2009-08-31 | 2021-12-15 | Abbott Diabetes Care, Inc. | Medical devices and methods |
USD1010133S1 (en) | 2009-08-31 | 2024-01-02 | Abbott Diabetes Care Inc. | Analyte sensor assembly |
US8868453B2 (en) | 2009-11-04 | 2014-10-21 | Proteus Digital Health, Inc. | System for supply chain management |
US10305544B2 (en) | 2009-11-04 | 2019-05-28 | Proteus Digital Health, Inc. | System for supply chain management |
US9941931B2 (en) | 2009-11-04 | 2018-04-10 | Proteus Digital Health, Inc. | System for supply chain management |
US8784308B2 (en) | 2009-12-02 | 2014-07-22 | Proteus Digital Health, Inc. | Integrated ingestible event marker system with pharmaceutical product |
US9014779B2 (en) | 2010-02-01 | 2015-04-21 | Proteus Digital Health, Inc. | Data gathering system |
US10376218B2 (en) | 2010-02-01 | 2019-08-13 | Proteus Digital Health, Inc. | Data gathering system |
US10207093B2 (en) | 2010-04-07 | 2019-02-19 | Proteus Digital Health, Inc. | Miniature ingestible device |
US9597487B2 (en) | 2010-04-07 | 2017-03-21 | Proteus Digital Health, Inc. | Miniature ingestible device |
US11173290B2 (en) | 2010-04-07 | 2021-11-16 | Otsuka Pharmaceutical Co., Ltd. | Miniature ingestible device |
US10529044B2 (en) | 2010-05-19 | 2020-01-07 | Proteus Digital Health, Inc. | Tracking and delivery confirmation of pharmaceutical products |
US9107806B2 (en) | 2010-11-22 | 2015-08-18 | Proteus Digital Health, Inc. | Ingestible device with pharmaceutical product |
US11504511B2 (en) | 2010-11-22 | 2022-11-22 | Otsuka Pharmaceutical Co., Ltd. | Ingestible device with pharmaceutical product |
US8827901B2 (en) | 2010-12-20 | 2014-09-09 | Covidien Lp | Access assembly with translating lumens |
US8602983B2 (en) | 2010-12-20 | 2013-12-10 | Covidien Lp | Access assembly having undercut structure |
US9307974B2 (en) | 2010-12-20 | 2016-04-12 | Covidien Lp | Access assembly having undercut structure |
US8641610B2 (en) | 2010-12-20 | 2014-02-04 | Covidien Lp | Access assembly with translating lumens |
US9277907B2 (en) | 2010-12-21 | 2016-03-08 | Covidien Lp | Access assembly including inflatable seal member |
US8696557B2 (en) | 2010-12-21 | 2014-04-15 | Covidien Lp | Access assembly including inflatable seal member |
US9439599B2 (en) | 2011-03-11 | 2016-09-13 | Proteus Digital Health, Inc. | Wearable personal body associated device with various physical configurations |
US9649113B2 (en) | 2011-04-27 | 2017-05-16 | Covidien Lp | Device for monitoring physiological parameters in vivo |
US11160512B2 (en) | 2011-04-27 | 2021-11-02 | Covidien Lp | Device for monitoring physiological parameters in vivo |
US11229378B2 (en) | 2011-07-11 | 2022-01-25 | Otsuka Pharmaceutical Co., Ltd. | Communication system with enhanced partial power source and method of manufacturing same |
US9756874B2 (en) | 2011-07-11 | 2017-09-12 | Proteus Digital Health, Inc. | Masticable ingestible product and communication system therefor |
US10223905B2 (en) | 2011-07-21 | 2019-03-05 | Proteus Digital Health, Inc. | Mobile device and system for detection and communication of information received from an ingestible device |
US9235683B2 (en) | 2011-11-09 | 2016-01-12 | Proteus Digital Health, Inc. | Apparatus, system, and method for managing adherence to a regimen |
US9271897B2 (en) | 2012-07-23 | 2016-03-01 | Proteus Digital Health, Inc. | Techniques for manufacturing ingestible event markers comprising an ingestible component |
US9268909B2 (en) | 2012-10-18 | 2016-02-23 | Proteus Digital Health, Inc. | Apparatus, system, and method to adaptively optimize power dissipation and broadcast power in a power source for a communication device |
US11149123B2 (en) | 2013-01-29 | 2021-10-19 | Otsuka Pharmaceutical Co., Ltd. | Highly-swellable polymeric films and compositions comprising the same |
US11158149B2 (en) | 2013-03-15 | 2021-10-26 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
US11741771B2 (en) | 2013-03-15 | 2023-08-29 | Otsuka Pharmaceutical Co., Ltd. | Personal authentication apparatus system and method |
US11744481B2 (en) | 2013-03-15 | 2023-09-05 | Otsuka Pharmaceutical Co., Ltd. | System, apparatus and methods for data collection and assessing outcomes |
US10175376B2 (en) | 2013-03-15 | 2019-01-08 | Proteus Digital Health, Inc. | Metal detector apparatus, system, and method |
US11172958B2 (en) | 2013-05-22 | 2021-11-16 | Covidien Lp | Methods and apparatus for controlling surgical instruments using a port assembly |
US10420583B2 (en) | 2013-05-22 | 2019-09-24 | Covidien Lp | Methods and apparatus for controlling surgical instruments using a port assembly |
US10421658B2 (en) | 2013-08-30 | 2019-09-24 | Proteus Digital Health, Inc. | Container with electronically controlled interlock |
US9796576B2 (en) | 2013-08-30 | 2017-10-24 | Proteus Digital Health, Inc. | Container with electronically controlled interlock |
US9270503B2 (en) | 2013-09-20 | 2016-02-23 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US10498572B2 (en) | 2013-09-20 | 2019-12-03 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US10097388B2 (en) | 2013-09-20 | 2018-10-09 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US11102038B2 (en) | 2013-09-20 | 2021-08-24 | Otsuka Pharmaceutical Co., Ltd. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US9787511B2 (en) | 2013-09-20 | 2017-10-10 | Proteus Digital Health, Inc. | Methods, devices and systems for receiving and decoding a signal in the presence of noise using slices and warping |
US9577864B2 (en) | 2013-09-24 | 2017-02-21 | Proteus Digital Health, Inc. | Method and apparatus for use with received electromagnetic signal at a frequency not known exactly in advance |
US10084880B2 (en) | 2013-11-04 | 2018-09-25 | Proteus Digital Health, Inc. | Social media networking based on physiologic information |
US11950615B2 (en) | 2014-01-21 | 2024-04-09 | Otsuka Pharmaceutical Co., Ltd. | Masticable ingestible product and communication system therefor |
US10398161B2 (en) | 2014-01-21 | 2019-09-03 | Proteus Digital Heal Th, Inc. | Masticable ingestible product and communication system therefor |
US11051543B2 (en) | 2015-07-21 | 2021-07-06 | Otsuka Pharmaceutical Co. Ltd. | Alginate on adhesive bilayer laminate film |
US10694276B2 (en) | 2015-09-30 | 2020-06-23 | Apple Inc. | In-ear headphone |
US11265638B2 (en) | 2015-09-30 | 2022-03-01 | Apple Inc. | In-ear headphone |
US10582284B2 (en) | 2015-09-30 | 2020-03-03 | Apple Inc. | In-ear headphone |
US11930313B2 (en) | 2015-09-30 | 2024-03-12 | Apple Inc. | In-ear headphone |
US10841683B2 (en) | 2015-09-30 | 2020-11-17 | Apple Inc. | In-ear headphone |
US10187121B2 (en) | 2016-07-22 | 2019-01-22 | Proteus Digital Health, Inc. | Electromagnetic sensing and detection of ingestible event markers |
US10797758B2 (en) | 2016-07-22 | 2020-10-06 | Proteus Digital Health, Inc. | Electromagnetic sensing and detection of ingestible event markers |
US11529071B2 (en) | 2016-10-26 | 2022-12-20 | Otsuka Pharmaceutical Co., Ltd. | Methods for manufacturing capsules with ingestible event markers |
US11793419B2 (en) | 2016-10-26 | 2023-10-24 | Otsuka Pharmaceutical Co., Ltd. | Methods for manufacturing capsules with ingestible event markers |
US11883028B2 (en) | 2021-09-08 | 2024-01-30 | Covidien Lp | Systems and methods for post-operative anastomotic leak detection |
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CN101022760A (en) | 2007-08-22 |
MXPA06012810A (en) | 2007-07-30 |
WO2005112744A1 (en) | 2005-12-01 |
AU2005244973A1 (en) | 2005-12-01 |
US7125382B2 (en) | 2006-10-24 |
US20050261563A1 (en) | 2005-11-24 |
US20070038054A1 (en) | 2007-02-15 |
US20050261562A1 (en) | 2005-11-24 |
US7297112B2 (en) | 2007-11-20 |
EP1750577A4 (en) | 2007-10-31 |
CA2563953A1 (en) | 2005-12-01 |
US7241266B2 (en) | 2007-07-10 |
EP1750577A1 (en) | 2007-02-14 |
JP2007537841A (en) | 2007-12-27 |
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