WO1994012235A1 - Automated drug infusion system - Google Patents

Automated drug infusion system Download PDF

Info

Publication number
WO1994012235A1
WO1994012235A1 PCT/US1993/011033 US9311033W WO9412235A1 WO 1994012235 A1 WO1994012235 A1 WO 1994012235A1 US 9311033 W US9311033 W US 9311033W WO 9412235 A1 WO9412235 A1 WO 9412235A1
Authority
WO
WIPO (PCT)
Prior art keywords
drug
channel
pumping
fluid
control system
Prior art date
Application number
PCT/US1993/011033
Other languages
French (fr)
Inventor
Noel L. Johnson
Terry Jyh-Yi Huang
Robert R. Burnside
Original Assignee
Abbott Laboratories
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=25528567&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=WO1994012235(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Application filed by Abbott Laboratories filed Critical Abbott Laboratories
Priority to AU56063/94A priority Critical patent/AU5606394A/en
Publication of WO1994012235A1 publication Critical patent/WO1994012235A1/en

Links

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16804Flow controllers
    • A61M5/16827Flow controllers controlling delivery of multiple fluids, e.g. sequencing, mixing or via separate flow-paths
    • GPHYSICS
    • G16INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16HHEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H20/00ICT specially adapted for therapies or health-improving plans, e.g. for handling prescriptions, for steering therapy or for monitoring patient compliance
    • G16H20/10ICT specially adapted for therapies or health-improving plans, e.g. for handling prescriptions, for steering therapy or for monitoring patient compliance relating to drugs or medications, e.g. for ensuring correct administration to patients
    • G16H20/17ICT specially adapted for therapies or health-improving plans, e.g. for handling prescriptions, for steering therapy or for monitoring patient compliance relating to drugs or medications, e.g. for ensuring correct administration to patients delivered via infusion or injection
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/60General characteristics of the apparatus with identification means
    • A61M2205/6063Optical identification systems
    • A61M2205/6072Bar codes
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S128/00Surgery
    • Y10S128/12Pressure infusion
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S128/00Surgery
    • Y10S128/13Infusion monitoring

Definitions

  • the present invention generally relates to systems for delivering drugs and fluids to patients intravenously. More particularly, the present invention relates to a control system for an automated intravenous drug and fluid infusion system.
  • volumetric infusion pumping systems for delivering drugs to patients intravenously.
  • Infusion pumping systems of conventional design have several significant drawbacks that limit their effectiveness. For example, manual entry via keys and knobs is required whenever a drug supply container is connected or replaced in the pumping system. Further, conventional pumping systems require manual identification of drugs and manual priming of pumping channels.
  • the present invention relates to a control system for use with an automated intravenous drug and fluid infusion system having plural pumping channels that operate independently.
  • Each pumping channel is independently controlled by a single microprocessor-based central processing unit (CPU).
  • CPU central processing unit
  • a host controller monitors all of the channels concurrently.
  • the system further includes means for positively identifying the particular drug that is to be pumped through a channel; means for preventing priming of a channel unless verification is provided that the channel is not connected to a patient; and means for independently priming each of the pumping channels.
  • the present invention provides easy to use methods and systems which improve patient care by automating control during all phases of drug and fluid delivery.
  • the system provides positive identification of drugs prior to their administration via the various pumping channels, and provides autopriming of the channels.
  • Dosing and delivery i.e., by bolus, continuous infusion, or pharmacokinetic model-based infusion
  • the control system can also recognize incompatible drug combinations, and subsequently handle the incompatibility or alert the device user via an appropriate warning.
  • Automatic dose limit checking, automatic data storage (e.g., patient record, user data and infusion data), and automatic detection and signaling of error conditions represent additional features of the control system.
  • Figure 1 is an exemplary automated drug infusion (ADI) pumping system of the type that dispenses drugs and fluids to a patient intravenously from one or more drug and fluid supply containers;
  • ADI automated drug infusion
  • Figure 2 is a block diagram of a control system for the Figure 1 pumping system
  • Figures 3a and 3b illustrate an exemplary bar code reader for a pumping channel of the Figure 2 system
  • Figure 4 is a diagram displaying system and channel communication between the user, the host controller and the independent pumping channels of the Figure 2 system. Detailed Description of the Preferred Embodiments
  • Figure 1 shows an ADI pumping system for dispensing drugs and fluids for a patient intravenously from one or more drug and fluid supply containers.
  • the Figure 1 apparatus includes three substantially equal drug delivery channels 4, 6 and 8, and a fluid delivery channel 10. Drug delivery parameters are entered and displayed via a touch screen 14. Fluid parameters are entered via a key pad 15.
  • a base enclosure 50 encloses a host controller 2 for driving the overall system.
  • a key lock 52 is disposed on a side of a pumping channel enclosure 54 and engages a security system.
  • Detailed aspects of an exemplary drug identification and security system which can be used with the Figure 1 apparatus are set forth in commonly assigned U.S. application Serial No. 07/811,516, entitled "Drug Channel Identification And Security System For Infusion And Pumping Systems” and filed December 20, 1991, the contents of which are hereby incorporated by reference.
  • Figure 2 shows a general hardware block diagram of an automated drug and fluid infusion control system for intravenously infusing drugs and fluid to a patient via the Figure 1 pumping system.
  • the Figure 2 system includes three general components: a host controller 2; drug channels 4, 6 and 8; and a fluid channel 10.
  • the Figure 2 system represents a modular, multi-channel infusion device with each drug channel holding a captive drug vial exclusively compatible with the system and with a drug administration set.
  • a master-slave control approach is used, with the host controller 2 overseeing operation of the four independent pump channel modules: three identical channels for the delivery of drug (e.g., anesthetic and cardiovascular agents), and one channel for fluid delivery.
  • drug e.g., anesthetic and cardiovascular agents
  • each drug channel refers to an independent path through which drug is dispensed to a patient from at least one drug supply container, or vial 32.
  • each drug channel includes a cassette pumping device 13. Access to a drug pumping cassette 13 within a drug channel is provided by lifting a protective hood on top of the pumping system. When not in use, the hood or hoods may be locked to prevent removal of the drugs.
  • Pump outlets in each independent drug channel may be connected to a manifold or connected directly to the patient.
  • the preferred manifold contains four one-way check valves which connect all input lines to an outlet line through which drugs and fluid are dispensed to a patient intravenously, for example, a manifold such as described in commonly assigned U.S. Application Serial No. 07/734,828, entitled “Multi-Valve Manifold For Drug Infusion Systems", filed July 24, 1991.
  • a "fluid channel” refers to a path through which a fluid (e.g., flushing fluid) is dispensed via the manifold.
  • the Figure 2 fluid channel 10 can carry fluid such as a patient hydration solution.
  • the fluid channel 10 includes a fluid supply container 33 which is compatible with a conventional drop sensor 30.
  • the drop sensor is connected to fluid conduit 11 that passes through a volumetric fluid channel pump.
  • the fluid channel 10 also connects to the manifold via a one-way check valve.
  • the host controller 2 is a single microprocessor-based computer which responds to user commands, directs intravenous drug • and fluid deliveries, automatically recognizes drug identities, stores and selectively activates a pharmacokinetic (PK) model useful in drug delivery to the patient, handles physical incompatibilities among drugs, and provides automatic record keeping.
  • the host controller 2 includes a microprocessor 16 which monitors and controls the independent pumping channels concurrently.
  • the host controller 2 includes a system user interface which enables the user to identify the drug installed in each drug channel, select infusion modes, set infusion rates, identify drug incompabilities, prevent priming of a drug channel unless verification is provided that the channel is not connected to a patient, and related functions. Further, the host controller 2 causes automatic priming of each pumping channel independently.
  • the automatic priming removes air from each of the pump cassettes 13 and associated tubing independently.
  • a discussion of the autoprime feature is provided in commonly assigned U.S. patent application Serial No. 07/811,195, entitled “Automated Drug Infusion System With Autopriming” filed December 20, 1991. Because an understanding of the auto-prime feature of the system described herein may be useful for a better understanding of the present invention, the above-noted U.S. patent application is herein incorporated by reference.
  • the Figure 2 system includes means for identifying the particular drug that is to be pumped through a drug channel.
  • a modular bar code reading system 12 identifies the drug contained in a drug vial 32 installed in a drug channel of the system.
  • the drugs normally are in liquid form in a drug container which is secured mechanically to a drug channel.
  • a bar code which includes the drug name is included on a drug label.
  • a bar code reader 17 is held manually as shown in Figure 3a, or can be located internally within each drug channel pump. When the bar code reader 17 is placed in a vicinity of the drug container, the bar code reader electronically senses the bar code. Further, the pumping system can use a unique arrangement of electromagnetic Hall sensors and magnetic strips in each drug channel to determine which drug channel is currently being read so that the reading of the drug supply container can be tied to the appropriate drug channel.
  • Hall sensors 15 on the bar code reader 17 detect the presence of magnetic strips 21 placed on a receptacle 19 of a drug channel.
  • the bar code reader must be placed in a vicinity of the receptacle 19 to read a bar code on the label of a drug vial secured in the drug channel.
  • Figure 3b shows an alternate configuration of a receptacle 23 which completely surrounds an end of a bar code reader 17.
  • Hall sensors 15 are replaced by a magnetic strip around a perimeter of the bar code reader.
  • the receptacle includes Hall sensors 25 mounted thereon to detect the magnetic strip located about the perimeter of the bar code reader 17.
  • the Figure 2 host controller 2 operates displays 18 and peripherals (e.g., floppy disk drive 20 for disks 34, system bus interface 22 for bus 36, parallel printer interface 24 for printer 38, graphics display adapter 40 for display 18 and input/output (I/O) card 44).
  • the host controller 2 also controls an A/D converter, a key lock switch, optional VGA compatible graphics, audio output circuitry, a timer circuit, non-volatile memory, battery backed static RAM memory for storage of non-volatile data (e.g., drug information stored in a drug table) and dynamic RAM.
  • Power supply 42 is provided for the Figure 2 system.
  • the host controller 2 can set the audio volume of an audio output signal to be one of a plurality of selected volume levels. In a preferred embodiment, eight separate volumes are provided. However, the number of selected volume levels can be greater or lesser than the number of volume levels selected for the preferred embodiment.
  • the audio output signal is used to provide warnings or alarms to the user for when a failure, malfunction, or other alarm condition occurs within the Figure 2 system.
  • the host controller 2 sends commands to an independent controller 9 (i.e., CPU) for each of the drug channels. (4,6,8) and. fluid channel 10 shown in Figure 4.
  • an independent controller 9 i.e., CPU
  • these commands include signals to stop pumping, set rate or dose, prime a drug channel, change pumping rate, read dose, initiate a backprime, start a pumping operation, perform a fluid prime, change fluid pumping rate, and read a dose from the fluid channel.
  • the host controller 2 receives responses and cases from each of the pumps.
  • the independent controller 9 for each drug channel controller controls and monitors pumping from drug vials, provides automatic priming of drug sets in response to host controller 2 commands, and communicates status, alarm and error conditions within a drug channel to the host controller 2.
  • the independent controller for a fluid channel controls and monitors pumping from fluid containers, provides automatic priming of fluid lines in response to host controller 2 commands, and communicates fluid line status, alarm and error conditions to the host controller 2.
  • the three drug channel modules are based on the known LifeCare 5000, and the fluid pump module is based on the known LifeCare 175, both available from Abbott Laboratories, Inc.
  • the independent controllers of the drug and fluid channels are independent microprocessors which communicate to the host controller 2 through a communication link. Because the drug and fluid channel modules are, for the most part, known modules which do not themselves constitute a portion of the present invention, only features of these modules necessary for understanding the present invention will be provided.
  • a user interface provides a connection between various pumping channel controllers ( Figures 1 and 2) and the user.
  • This interface includes a user accessible panel which is divided into four regions: three drug channel regions, each directly beneath one of the three drug channel mechanisms, and one fluid channel region directly beneath the fluid channel.
  • the user can access all functions' of the Figure 2 system via the interface at any time after power-up, with the exception of self- diagnostics, system administrator functions, and floppy drive use.
  • a touch screen 14 represents a module which is accessible to the user and controlled by the host controller 2.
  • a key pad included on a host controller interface panel includes 16 front panel buttons in a preferred embodiment of the present invention. The panel can accommodate additional buttons if they are needed in alternate embodiments of the present invention, including several hidden buttons. Both an identity of a button being depressed and its state are read by the host controller 2.
  • buttons which control drug delivery to a patient remain visible on the interface panel during the entire time delivery is occurring or is possible on that drug channel. The user is therefore not required to exit a current function to start or stop drug delivery.
  • the drug name, current delivery rate, dose or a ⁇ etpoint of the PK model, and a pumping activity indicator are displayed for each drug channel on the interface panel.
  • the portion of the user interface located beneath the fluid channel mechanism includes a five digit display to identify delivery rate or total value delivered. LEDs are also included on the user interface panel to identify a power-on condition and to indicate when the system is running on battery power.
  • the host controller 2 provides channel set up functions for each of the drug channels 4, 6, 8 and fluid channel 10 shown in Figure 2. This includes automatic identification and channel association of drugs placed in each drug channel and overseeing automatic priming of the drug and fluid channels. In addition, the host controller 2 provides drug and fluid delivery functions, system maintenance functions, data storage functions and handling of exceptional cases (e.g., malfunctions and alarm indications to the user).
  • the drug identification feature is implemented during a drug channel set up, after the host 2 is notified by an independent controller 9 that a drug channel door has been closed with a drug cassette in place. At that time, the host controller 2 prompts the user to scan a bar code included on a drug vial label. For the host controller 2 to accept the scan as valid, the bar coded label must be accessible to the bar code reader. The bar code reader remains active as long as a drug channel door has been closed with a cassette in place and the associated bar code label has not yet been successfully scanned.
  • two sensors provided in each channel indicate the presence or absence of the bar code reader directly in front of that channel.
  • the drug vial to be scanned must be properly positioned in a drug channel to be identified by the bar code reader, otherwise its label will not be recognized by the system.
  • the host controller 2 displays the name of the drug on a host display position below the drug channel receiving the drug vial.
  • the host controller 2 prompts the user to enter drug delivery information associated with that drug. The host controller 2 will not permit a drug channel to prime or pump any drug until the drug vial loaded into the channel has been successfully identified using the bar code reader.
  • a significant delivery function of the present invention is the ability to provide drug specific functions.
  • the host controller 2 allows the user to pick from allowed unit conversion sets specified for a particular drug being used. Unit conversion sets available for each drug are retained in the drug table of the host controller 2 memory. Drug delivery quantities in weight based units require entry of patient weight.
  • the host controller 2 displays all delivery control quantities (i.e., rate, dose and plasma level) using default units specified by a unit conversion set in the host controller's drug table for that drug, or, if preferred by the user, the units that were used during the most recent delivery of that drug. If other unit conversion sets are permitted for that drug, the host controller 2 permits the user to select one. Afterwards, all quantities are displayed using the new units for rate, dose and plasma level specified by the new unit conversion set.
  • delivery control quantities i.e., rate, dose and plasma level
  • the host controller 2 is designed to control infusion rate and bolus dose delivery or PK model-based drug delivery.
  • the host controller 2 permits either bolus delivery or infusion delivery, but when both a bolus delivery and an infusion delivery are recpiested simultaneously, the bolus delivery takes priority, causing delay of the infusion delivery until the bolus has been completed.
  • a bolus dose in units selected by the user must be input by the user before the start of delivery.
  • the host controller 2 will only permit a bolus delivery to occur for drugs which have been identified in a drug table of the host controller's memory as being deliverable by bolus.
  • the user must confirm the request for a bolus delivery prior to starting delivery.
  • the user can also select desired duration for bolus delivery ranging from default (i.e., the shortest time over which the drug can be delivered) to durations which are multiples of the default duration) .
  • a bolus may be paused during delivery, after which the bolus may be resumed (i.e., causing the remaining dose to be delivered) or the bolus may be stopped, cancelling delivery of the remaining dose. No confirmation is required to resume a bolus once paused, and pausing does not affect the status of simultaneously delivered infusion delivery on the same channel.
  • Infusion delivery is only permitted for drugs which have been defined in the drug table as being deliverable by infusion. • Continuous infusion requires that the user input a desired infusion rate and infusion units before the start of infusion delivery. A default value of infusion units is provided by host controller 2.
  • the infusion rate is, in an exemplary embodiment, equivalent to a range of 0.1 ml/hr to 1200 ml/hr.
  • a PK model is maintained in the host controller's memory for all drugs that are listed in the drug table as having PK models.
  • the host controller 2 starts a PK model to continuously predict the theoretical plasma level of the drug being delivered.
  • the selected PK model allows the user to query the predicted plasma level of the drug in a patient at any time during its delivery.
  • PK model-based delivery is only permitted for drugs which have been so defined in the drug table of the host controller 2.
  • the system can provide the user with predicted (theoretical) plasma levels (i.e., level of drug in patient bloodstream) when delivering drugs by bolus or continuous infusion because a background calculation of the theoretical plasma level is continuously updated.
  • the user Before initiating a PK model-based delivery, the user must input a plasma level set point in user selectable units. The host controller 2 will not accept a plasma level set point greater than the maximum plasma level defined in the drug table for that drug. Further, PK delivery cannot be initiated until certain patient parameters, such as weight, have been confirmed by the user. Upon initiation of a PK delivery, the host controller 2 displays setpoint plasma level in user selected units, the predicted (theoretical) plasma level in the same units, and the infusion rate in default units throughout the entire PK model-based delivery.
  • a delivery rate e.g., between 1 and 1200 ml/hr
  • ml and ml/hr are used to define fluid rate and cumulative dose units.
  • a key feature of the present invention is its ability to handle incompatibility between drugs administered to a patient via the Figure 2 system.
  • the host controller 2 detects and informs the user of possible physical incompatibilities between drugs identified by the bar code reader.
  • the host controller 2 allows the user to decide whether to allow the system to automatically handle incompatible drug pairs involving bolus delivery. If the user decides to let the system automatically handle the incompatibility, the host controller 2 provides a visible indication on those channels that an incompatibility exists and that it will be automatically handled.
  • bolus deliveries are preceded by and followed by a flush delivery from the fluid channel. Once a flush delivery for an incompatible bolus is completed, the fluid channel reverts to its previous delivery rate. The volume of each flush delivery is added to the total fluid delivered during the current patient case and stored in memory of the host controller 2.
  • the host controller can be designed to handle incompatibilities in all infusion mode combinations.
  • the host controller 2 does not provide special handling for infusions, PK deliveries, or for three incompatible drugs loaded into the system at the same time, on channels where compatibility handling is active. Rather, the host controller 2 informs the user upon identification of incompatible drug conditions. Further, a visual indication of any currently incompatible drugs is provided to the user.
  • the user can view the current total amount of drug delivered from the start of delivery to a particular patient. This information is stored in the host memory and is continuously updated throughout the delivery. For each drug loaded and identified, the user can specify a maximum dose limit for the duration of delivery to the patient. Once reached, the user is informed, but pumping continues. The user dose limit is reset and disabled when the patient case ends.
  • the host controller 2 also includes a global stop which deactivates all 3 drug channels at once. Each channel must then be individually restarted to resume pumping.
  • fluid specific functions are provided for the fluid channel 10. More particularly, the user can view the current total volume of fluid delivered to a patient from the beginning of the patient case. Further, the user can enter a maximum volume limit of fluid for each patient case. Once reached, the user is informed and fluid delivery is discontinued. The user volume limit is reset and disabled when the patient case ends.
  • the Figure 2 host controller 2 also provides a plurality of system maintenance functions. These functions include a start up/shut down function, disk archiving function, configuration features, installation/security features, and system update.
  • the start up/shut down functions prevent drug and fluid delivery to a patient prior to user instruction to the host controller 2.
  • the host controller 2 allows the user to end a current patient case only when no channel is pumping. Upon ending the patient case, the host controller 2 displays total volumes delivered and used for priming the administration set for each drug used, as well as total volume of fluid delivered and used for priming. These volumes are expressed in display units used at the time the patient case ended.
  • the disk archiving function of the host controller 2 stores event history and patient case information to floppy disk for later use and analysis.
  • Configuration functions of the host controller 2 provide a means for the current date and time to be set.
  • access to certain functions of the host controller 2 is restricted and requires the use of a password.
  • the host controller 2 can be controlled to access an exception conditions log, an event history, user information, patient case information, and installation record/drug usage.
  • entry of this password can be required before information stored in the system can be transferred to the floppy disk.
  • entry of the correct password can be used to control entry of information into the host controller's memory (e.g., hospital name, drug table updates and names of users allowed access to the system) .
  • the password cannot be changed unless access to the system has been obtained, nor can the password be viewed unless access to the system has been obtained following accurate entry of the current password. Use of the password can thus be used to control access to a variety of features of the host controller 2.
  • Event history data is stored by the host controller 2 as a chronological record of system cases associated with the Figure 2 system alarms, malfunctions, and user interaction with the system.
  • the event history data is stored in the non-volatile host controller's memory, and can be viewed by the user.
  • the host controller 2 can store all cases that occur over a period of 7 days of continuous use. Once the case buffer is filled, old cases are discarded as new cases occur. The host controller 2 permits the user to disable and enable event history recording, and when disabled no subsequent cases are stored in the event history portion of the host controller's memory.
  • Exception conditions are stored by the host controller 2 as a chronological record of at least the last 30 exception conditions (i.e., malfunctions and alarms) applicable to the entire Figure 2 system. Again, this log is stored in a non-volatile area of host controller's memory. Pumping channel exceptions are not stored in the individual pumps, but are stored as data in this portion of host controller's memory. Exception data is recorded automatically and cannot be disabled or erased by the user.
  • the host controller 2 also stores user information. This information includes, for example, up to 100 alphanumeric user IDs in a non ⁇ volatile area of host controller's memory.
  • Patient case data can, in an exemplary embodiment, be retained on the last 50 patient cases.
  • the host controller 2 allows the user to optionally store a patient ID as well as other information on age, sex, and weight.
  • the patient weight can be input and displayed in pounds or kilograms.
  • the host controller 2 For each patient case, the host controller 2 stores the user ID of the user who ended the patient case, the total number of users who identified themselves to the system during the patient case, the time the patient case started, and the duration of the patient case. The host controller 2 also records the number of drugs delivered during the patient case, the total volume delivered and total volume used in priming for each drug used during the patient case, as well as the total volume of fluid delivered and total volume used in priming. This information is expressed in display units currently being used at the time the patient case ended.
  • Installation record/drug usage data is retained by the host controller 2 and includes information regarding the installer's name, the site name, installation date and information pertaining to specific hardware configuration of the Figure 2 system.
  • Drug table data is also stored by the host controller 2.
  • the drug table includes information (e.g., drug incompatibilities, suitability for bolus infusion delivery or PK delivery, PK model-based input parameters and maximum allowable infusion rates, bolus doses, and theoretical plasma levels) for each drug as described previously.
  • Another key feature of the present invention is its ability to handle exception conditions. More particularly, when a malfunction, audible alarm or audible warning occurs, audio signal is emitted by the host controller 2 to alert the user. This audio signal is only discontinued when the user has acknowledged the condition, but may be temporarily stopped using a silence alarm button on the host controller interface panel. When a non-audible alarm or non-audible warning occurs, a discrete audio signal is optically generated to alert the user.
  • the host controller 2 detects malfunctions in the Figure 2 system. Malfunctions which are identified by the host controller 2 and communicated to the user include signals indicating that a fluid or drug channel is unavailable due to an internal malfunction, indication that the system is unavailable due to a malfunction, and indications that the disk drive or other peripheral components are unavailable due to a malfunction.
  • the system can be configured to require presence of a drop detector in the fluid channel.
  • the host controller 2 requires the user to discontinue fluid channel operation when an alarm indicating the absence of a drop detector occurs.
  • the fluid channel cannot be restarted until the exception condition regarding absence of the drop detector is rectified.
  • Alarms associated with the fluid delivery channel 10 include, for example, indications that the fluid channel autoprime mechanism has failed, that there is air in the fluid channel line, that the fluid channel door has been opened while pumping or that the fluid channel bag is empty.
  • the host controller 2 allows the user to stop the fluid channel 10 and enter a new pumping rate, but the fluid channel 10 cannot be restarted until the exception condition is rectified.
  • Alarms are also generated when there is a proximal occlusion or distal occlusion in the fluid channel pump, when there is a pressure error in the fluid channel 10, when the fluid channel volume limit is reached.
  • the foregoing alarms are the minimum alarm conditions provided. Those skilled in the art will recognize that any number of alarms based on detection of any desired condition can be provided.
  • alarms associated with the drug channels 4, 6, 8 are, at a minimum, provided to the user when there is proximal or distal air detection in the drug channel cassette 13, when a channel door has been opened while pumping, when there is a proximal or distal occlusion in the cassette, when distal pressure is out of range, or when drug is unavailable.
  • Non-audible alarms generated by host controller 2 include when AC power is not available or when the battery becomes discharged, failure to recognize a bar code, failure to associate a bar code with a channel, or alarms associated with floppy disk operation.
  • audible warnings include, at a minimum, when the battery is low or when a drug container is near empty.
  • Non-audible warnings include detection of excess air in an air trap chamber of a pumping cassette, loss of AC power or potential drug incompabilities.
  • Drug and fluid channel status conditions are also continuously provided from the pumping channels to the host controller 2 for display.
  • Status conditions which are displayed to the user via the host controller interface panel include, channel unavailable status, inactive status, autopriming status, backpriming status, testing cassette status, cassette test failure status, prime needed status, backprime needed status, prime verification needed status, infusion on hold status, bolus on hold status.
  • System status conditions which can be displayed via the host controller interface panel include: battery low status, security covers locked status, fluid channel unavailable status, drop detector missing status, volume limit reached status, disk drive unavailable status, patient parameters needed status, and user ID needed status.
  • user interaction with the Figure 2 system is via a user interface 3 in the host controller 2.
  • Communication of commands, data, exception conditions, status and other information between the host controller 2 and drug and fluid channels is via the aforementioned serial communication link, capable of two-way communication. Communication is, for example, via packets limited to 30 bytes to ensure real time operation.
  • Typical communications between the host controller 2 and pumping channels is via a command- acknowledgement loop.
  • the host controller 2 master
  • the targeted channel sends back an acknowledgement indicating receipt and initiation of appropriate action in.response to the command.
  • Master-slave polling is used to detect synchronous communications between the host controller 2 and pumping channels 4, 6, 8 and 10. These synchronous communications include, for example, the aforementioned alarms and door open/door closed conditions.
  • alarm conditions are sent from a pumping channel 4, 6, 8 and 10 to the host controller 2, the pumping channel awaits acknowledgement from the host controller 2. If an event is not acknowledged within a set time frame, the event is retransmitted until acknowledgement is received. After acknowledging the pump channel communication, the host controller 2 can either send a reset command to the pump or report failure to the user. For multi-event conditions, a pumping channel module will queue cases until all are acknowledged.
  • Each drug channel 4, 6 and 8 includes a pump which is preset at a position having an outlet valve closed, and an inlet valve open.
  • a closed door switch is included in each drug pump to indicate when a drug channel door is closed with a cassette in place.
  • An open door switch indicates that the drug channel door has been opened.
  • Pumping is accomplished in each drug channel via a pumping cassette which includes one or two proximal (inlet) lines and one distal (outlet) line.
  • the pump includes a mechanical reciprocating plunger mechanism and a pumping cassette through which the drugs are pumped.
  • the pumping cassette has a primary inlet port and a pumped-liquid outlet port.
  • the primary inlet port is connected to a piercing pin for receiving drug from a vial.
  • alternative drug containers and connection methods can be used.
  • the cassette also includes a secondary inlet port which remains normally closed. However, if desired, the secondary inlet port can receive a second drug, or drug diluent, for mixing with drug which has been introduced to the cassette via the primary inlet port.
  • a principal function of the independent controller 9 in each drug channel is to control drug delivery, priming of the drug delivery line, communication with the host controller 2, error detection and error reporting within the drug channel.
  • the principal activity of the drug channel is drug delivery, whereby liquid is moved from one of the cassette inlet lines to the outlet line.
  • the inlet lines referred to herein as primary and secondary inlets, are typically configured with the primary line connected to a drug vial, and the secondary line disconnected.
  • An exemplary delivery range is from .1 ml/hr to 1200 ml/hr.
  • the drug channel controller responds to user commands to control bi-directional flow.
  • Bi-directional flow control is critical for autopriming.
  • the host controller 2 instructs operation of the valve actuators and plungers in each drug channel to displace air from the drug cassette. Further, the autopriming sequence can be used for priming the output line to the patient.
  • Each drug channel receives commands directly from the host controller 2 via the serial communication interface at an exemplary data rate of 1200 baud. These commands include the aforementioned communications to set rate, start pumping and so forth. Each independent controller 9 detects anomalies within its own drug channel pumping line. Error conditions and significant cases are communicated by each channel controller to the host controller 2.
  • the drug channel can fill, with drug, a cassette which is full of air distal to the air trap chamber (i.e., completely empty cassettes, cassettes with air in the pumping bowl, and cassettes with air in the distal tubing) ; the drug channel can remove air introduced into the cassette air trap without moving it to the outlet line; and the drug channel can remove air trapped between the secondary inlet and an optional secondary reservoir.
  • the drug channel detects errors and reporting is performed by the drug channel to the host controller 2 with respect to four classes of errors: electronic, mechanical, cassette and communication.
  • Electronic integrity verification concerns the microprocessor memory, A/D lines and other microprocessor board and sensory apparatus.
  • Mechanical integrity verification concerns verifying the mechanical pumping system is moving in accordance with commanded operation via the use of position detection feedback on three stepper motors included in each drug channel.
  • Cassette integrity verification ensures that a cassette introduced to a drug channel is capable of withstanding pressures associated with pumping without leaking and is not occluded.
  • Communication error detection is necessary to verify that transmitted data is accurate in accordance with the serial communication protocol. All failures are transmitted by the drug channel to the host controller 2, and the drug channel will confirm that the host controller 2 is aware when an alarm condition exists.
  • electronic integrity verification is used to verify electronic and software integrity.
  • the drug channel performs a RAM test, a ROM test, an A/D converter test and a watchdog test.
  • the drug channel verifies serial communication integrity by the on-going existence of incoming message packets.
  • the drug channel verifies integrity of the air sensor by ensuring an air signal is seen whenever the door is open.
  • Mechanical integrity verification to ensure safety involves verifying an ability of the pump channel mechanism and cassette to pump accurately. These tests are performed before pumping, and if any test fails, the drug channel is not permitted to pump. Motor position check and re-synchronization tasks (if necessary) are performed prior to pumping (e.g., when the system is activated), and no maximum time requirements are associated with these tasks.
  • each drug channel (4,6,8) is to perform a cassette integrity test to check for static occlusion and valve leaks when a cassette door is closed with a cassette in place.
  • Occlusion detection is performed via the proximal and distal pressure sensors (i.e., pressure threshold is exceeded on proximal or distal side), after which an occlusion alarm is reported by the affected drug channel to the host controller 2.
  • Leak tests are performed automatically whenever the cassette door is closed with a cassette in place. All of these tests are performed by monitoring pressure inside the cassette and are, for example, used to indicate the need for backpriming the cassette (automatic removal of air from the cassette done by pushing it back into the drug container) or to indicate that a bad cassette needs to be replaced.
  • the proximal pressure sensor self-test is used to ensure that the pressure sensor stays within a desired operating range.
  • a priming function of each drug channel (4,6,8) removes air from the drug delivery set.
  • a drug delivery set includes a pumping cassette, distal tubing, and vial adapter. Priming operations perform both proximal and distal occlusion detection.
  • a pumping function is initiated in response to a start pumping command after all integrity tests have been implemented and passed.
  • mechanical motor position flags are monitored continuously by optical sensors.
  • the pumping function of the drug channel provides for proximal occlusion detection and distal occlusion detection using proximal and distal pressure sensors, respectively.
  • a distal air in line alarm and stop pumping signal are generated by a drug channel if an air bubble (e.g., greater than, for example, 100 ⁇ £ ) (microliter) , occurs at the distal air detector.
  • the pump will also generate a distal air in line alarm if, for example, 200 ⁇ S. out of the last 2.0 ml of volume was air.
  • the pumping function also includes an empty container detection when cumulative amount (e.g., 200 ⁇ £ ) of air has entered the cassette from at least one inlet line. This cumulative total is reset whenever the cassette door is opened, or a priming operation is performed.
  • a door open detection mode of the drug channels 4, 6, and 8 is used to trigger return of the step motors in a given drug channel to a preset position.
  • a "door opened” alarm is generated and transmitted to the host controller 2.
  • the drug . channel retains pumping parameters (i.e., rate, dose limit, delivered dose) except for pressure limit.
  • the drug channel retains all of these parameters until commanded to change by the host controller 2.
  • a fluid pump within a fluid channel includes a plunger/inlet valve/outlet valve assembly and a DC motor to pump fluid.
  • the fluid channel controller 9 communicates with the host controller 2 via the serial communication interface to receive commands such as set rate, start and operational commands. Like the drug channels, the fluid channel 10 detects anomalies in the pumping line and communicates error conditions and significant cases to the host controller 2.
  • the fluid channel 10 controls fluid delivery from inlet tubing to outlet tubing in an exemplary range of from 1 ml/hr to 1200 ml/hr. Further, the fluid channel 10 controls priming of air filled delivery tubing automatically. Like the drug channels, the fluid channel can detect four similar classes of errors: electronic, mechanical, fluid and communication.
  • various parameters are accessible by the host controller 2 to configure the fluid channel behavior during pumping cycles. These parameters include delivery rate, dose limit, drop detector, priming time limit and door closed flag.
  • the drop detector parameter determines whether detection of an empty fluid container is required during the delivery cycle. This parameter can be selectively recpiested by the host controller 2.
  • the priming time limit parameter provides fail-safe operation of the priming process.
  • the door closed flag ensures that pumping and priming do not occur unless the delivery tubing is inserted and the pumping mechanism door latches closed. The flag is set whenever both the delivery tubing is inserted and the door latch is closed, and either a door opening or tubing removal will reset this flag.
  • Pumping functions of the fluid channel 10 include a priming cycle and a delivery cycle.
  • Priming of the delivery tubing in response to a command from the host controller 2 consists of two phases: a proximal tubing filling phase and a distal tubing filling phase.
  • the fluid channel 10 activates its priming mechanism and starts pumping until a distal air sensor detects continuous fluid flow.
  • the priming mechanism is deactivated and control advances to a distal tubing filling phase.
  • fluid is delivered at a specified delivery rate until the specified dose limit is reached as with a normal delivery cycle.
  • the priming cycle returns to the proximal tubing filling phase instead of terminating the priming process.
  • Priming is discontinued when a specified dose limit is reached during the distal tube filling phase, upon receipt of a stop command from the host controller 2, upon expiration of a priming time limit, upon detection of an empty container by a drop detector, or by an alarm in response to error detection.
  • the fluid channel 10 delivers fluid from its proximal tubing to its distal tubing at the specified delivery rate, until stopped by the user or the user specified dose limit is reached.
  • Error detection is similar to that of the drug channels and includes electronic, mechanical and fluid integrity checks. An error detected by these tests results in stoppage of the pumping process and communication of the error to the host controller 2.
  • electronic integrity verification includes use of a watchdog timer to interrupt the fluid channel CPU to ensure integrity of the fluid channel CPU, critical data storage verification, and sensor range verification with regard to temperature and power supply voltages.
  • Mechanical integrity verification includes monitoring of motor slippage, monitoring of plunger motor shaft encoder slippage, pumping rate verification and motor voltage verification.
  • Fluid integrity verification includes air-in-line detection, empty container detection, proximal occlusion detection, distal occlusion detection and differential distal occlusion detection (i.e., when average depositive pressure buildup of distal pressure, relative to the distal pressure at pumping start time, is detected). Detection of a drop detector (if required) and loss of the drop detector signal are also monitored.

Abstract

The present invention relates to a control system for use with an automated intravenous drug and fluid infusion system having plural pumping channels (4, 6, 8, 10) that operate independently for intravenously infusing drugs and fluid. The pumping channels (4, 6, 8, 10) are controlled by a microprocessor-based host controller (2) that monitors each of the channels concurrently. In an exemplary embodiment, the system functions include preventing priming of a channel unless verification is provided that the channel is not connected to a patient and initiating the priming of each of the pumping channels independently.

Description

AUTOMATED DRUG INFUSION SYSTEM
Background of the Invention
Field of the Invention:
The present invention generally relates to systems for delivering drugs and fluids to patients intravenously. More particularly, the present invention relates to a control system for an automated intravenous drug and fluid infusion system.
State of the Art:
It is well known to use volumetric infusion pumping systems for delivering drugs to patients intravenously. Infusion pumping systems of conventional design have several significant drawbacks that limit their effectiveness. For example, manual entry via keys and knobs is required whenever a drug supply container is connected or replaced in the pumping system. Further, conventional pumping systems require manual identification of drugs and manual priming of pumping channels.
The foregoing manual procedures are time consuming, labor-intensive and susceptible to error. Because there is no procedure for identifying and approving use of a drug in an infusion pumping system, successive use of different drugs in the same delivery line can occur, resulting in drug contamination. Further, the lack of drug identification can result in the mixing of incompatible drugs from plural drug channels.
Summary of the Invention
The present invention relates to a control system for use with an automated intravenous drug and fluid infusion system having plural pumping channels that operate independently. Each pumping channel is independently controlled by a single microprocessor-based central processing unit (CPU). A host controller monitors all of the channels concurrently. In an exemplary embodiment, the system further includes means for positively identifying the particular drug that is to be pumped through a channel; means for preventing priming of a channel unless verification is provided that the channel is not connected to a patient; and means for independently priming each of the pumping channels.
The present invention provides easy to use methods and systems which improve patient care by automating control during all phases of drug and fluid delivery. The system provides positive identification of drugs prior to their administration via the various pumping channels, and provides autopriming of the channels. Dosing and delivery (i.e., by bolus, continuous infusion, or pharmacokinetic model-based infusion) can be entered in user-selectable units which are internally converted to system units (ml/hr.).
The control system can also recognize incompatible drug combinations, and subsequently handle the incompatibility or alert the device user via an appropriate warning. Automatic dose limit checking, automatic data storage (e.g., patient record, user data and infusion data), and automatic detection and signaling of error conditions represent additional features of the control system.
Brief Description of the Drawings
The present invention can be further understood with reference to the following description and the appended drawings, wherein like elements are provided with the same reference numerals. In the drawings:
Figure 1 is an exemplary automated drug infusion (ADI) pumping system of the type that dispenses drugs and fluids to a patient intravenously from one or more drug and fluid supply containers;
Figure 2 is a block diagram of a control system for the Figure 1 pumping system;
Figures 3a and 3b illustrate an exemplary bar code reader for a pumping channel of the Figure 2 system;
Figure 4 is a diagram displaying system and channel communication between the user, the host controller and the independent pumping channels of the Figure 2 system. Detailed Description of the Preferred Embodiments
Figure 1 shows an ADI pumping system for dispensing drugs and fluids for a patient intravenously from one or more drug and fluid supply containers. The Figure 1 apparatus includes three substantially equal drug delivery channels 4, 6 and 8, and a fluid delivery channel 10. Drug delivery parameters are entered and displayed via a touch screen 14. Fluid parameters are entered via a key pad 15. A base enclosure 50 encloses a host controller 2 for driving the overall system. A key lock 52 is disposed on a side of a pumping channel enclosure 54 and engages a security system. Detailed aspects of an exemplary drug identification and security system which can be used with the Figure 1 apparatus are set forth in commonly assigned U.S. application Serial No. 07/811,516, entitled "Drug Channel Identification And Security System For Infusion And Pumping Systems" and filed December 20, 1991, the contents of which are hereby incorporated by reference.
Figure 2 shows a general hardware block diagram of an automated drug and fluid infusion control system for intravenously infusing drugs and fluid to a patient via the Figure 1 pumping system. The Figure 2 system includes three general components: a host controller 2; drug channels 4, 6 and 8; and a fluid channel 10.
The Figure 2 system represents a modular, multi-channel infusion device with each drug channel holding a captive drug vial exclusively compatible with the system and with a drug administration set. A master-slave control approach is used, with the host controller 2 overseeing operation of the four independent pump channel modules: three identical channels for the delivery of drug (e.g., anesthetic and cardiovascular agents), and one channel for fluid delivery.
For purposes of the following discussion, the term "drug channel" refers to an independent path through which drug is dispensed to a patient from at least one drug supply container, or vial 32. In systems according to the present invention, each drug channel includes a cassette pumping device 13. Access to a drug pumping cassette 13 within a drug channel is provided by lifting a protective hood on top of the pumping system. When not in use, the hood or hoods may be locked to prevent removal of the drugs.
Pump outlets in each independent drug channel may be connected to a manifold or connected directly to the patient. The preferred manifold contains four one-way check valves which connect all input lines to an outlet line through which drugs and fluid are dispensed to a patient intravenously, for example, a manifold such as described in commonly assigned U.S. Application Serial No. 07/734,828, entitled "Multi-Valve Manifold For Drug Infusion Systems", filed July 24, 1991.
A "fluid channel" refers to a path through which a fluid (e.g., flushing fluid) is dispensed via the manifold. The Figure 2 fluid channel 10 can carry fluid such as a patient hydration solution. The fluid channel 10 includes a fluid supply container 33 which is compatible with a conventional drop sensor 30. The drop sensor is connected to fluid conduit 11 that passes through a volumetric fluid channel pump. The fluid channel 10 also connects to the manifold via a one-way check valve.
The host controller 2 is a single microprocessor-based computer which responds to user commands, directs intravenous drug • and fluid deliveries, automatically recognizes drug identities, stores and selectively activates a pharmacokinetic (PK) model useful in drug delivery to the patient, handles physical incompatibilities among drugs, and provides automatic record keeping. The host controller 2 includes a microprocessor 16 which monitors and controls the independent pumping channels concurrently. The host controller 2 includes a system user interface which enables the user to identify the drug installed in each drug channel, select infusion modes, set infusion rates, identify drug incompabilities, prevent priming of a drug channel unless verification is provided that the channel is not connected to a patient, and related functions. Further, the host controller 2 causes automatic priming of each pumping channel independently.
The automatic priming removes air from each of the pump cassettes 13 and associated tubing independently. A discussion of the autoprime feature is provided in commonly assigned U.S. patent application Serial No. 07/811,195, entitled "Automated Drug Infusion System With Autopriming" filed December 20, 1991. Because an understanding of the auto-prime feature of the system described herein may be useful for a better understanding of the present invention, the above-noted U.S. patent application is herein incorporated by reference.
The Figure 2 system includes means for identifying the particular drug that is to be pumped through a drug channel. A modular bar code reading system 12 identifies the drug contained in a drug vial 32 installed in a drug channel of the system. The drugs normally are in liquid form in a drug container which is secured mechanically to a drug channel. A bar code which includes the drug name is included on a drug label. A bar code reader 17 is held manually as shown in Figure 3a, or can be located internally within each drug channel pump. When the bar code reader 17 is placed in a vicinity of the drug container, the bar code reader electronically senses the bar code. Further, the pumping system can use a unique arrangement of electromagnetic Hall sensors and magnetic strips in each drug channel to determine which drug channel is currently being read so that the reading of the drug supply container can be tied to the appropriate drug channel.
For example, in Figure 3a, Hall sensors 15 on the bar code reader 17 detect the presence of magnetic strips 21 placed on a receptacle 19 of a drug channel. The bar code reader must be placed in a vicinity of the receptacle 19 to read a bar code on the label of a drug vial secured in the drug channel. Figure 3b shows an alternate configuration of a receptacle 23 which completely surrounds an end of a bar code reader 17. In this embodiment, Hall sensors 15 are replaced by a magnetic strip around a perimeter of the bar code reader. The receptacle includes Hall sensors 25 mounted thereon to detect the magnetic strip located about the perimeter of the bar code reader 17.
The Figure 2 host controller 2 operates displays 18 and peripherals (e.g., floppy disk drive 20 for disks 34, system bus interface 22 for bus 36, parallel printer interface 24 for printer 38, graphics display adapter 40 for display 18 and input/output (I/O) card 44). The host controller 2 also controls an A/D converter, a key lock switch, optional VGA compatible graphics, audio output circuitry, a timer circuit, non-volatile memory, battery backed static RAM memory for storage of non-volatile data (e.g., drug information stored in a drug table) and dynamic RAM. Power supply 42 is provided for the Figure 2 system.
The host controller 2 can set the audio volume of an audio output signal to be one of a plurality of selected volume levels. In a preferred embodiment, eight separate volumes are provided. However, the number of selected volume levels can be greater or lesser than the number of volume levels selected for the preferred embodiment. The audio output signal is used to provide warnings or alarms to the user for when a failure, malfunction, or other alarm condition occurs within the Figure 2 system. The host controller 2 sends commands to an independent controller 9 (i.e., CPU) for each of the drug channels. (4,6,8) and. fluid channel 10 shown in Figure 4. For example, these commands include signals to stop pumping, set rate or dose, prime a drug channel, change pumping rate, read dose, initiate a backprime, start a pumping operation, perform a fluid prime, change fluid pumping rate, and read a dose from the fluid channel. In addition, the host controller 2 receives responses and cases from each of the pumps.
The independent controller 9 for each drug channel controller controls and monitors pumping from drug vials, provides automatic priming of drug sets in response to host controller 2 commands, and communicates status, alarm and error conditions within a drug channel to the host controller 2. The independent controller for a fluid channel controls and monitors pumping from fluid containers, provides automatic priming of fluid lines in response to host controller 2 commands, and communicates fluid line status, alarm and error conditions to the host controller 2.
The three drug channel modules are based on the known LifeCare 5000, and the fluid pump module is based on the known LifeCare 175, both available from Abbott Laboratories, Inc. The independent controllers of the drug and fluid channels are independent microprocessors which communicate to the host controller 2 through a communication link. Because the drug and fluid channel modules are, for the most part, known modules which do not themselves constitute a portion of the present invention, only features of these modules necessary for understanding the present invention will be provided.
A user interface provides a connection between various pumping channel controllers (Figures 1 and 2) and the user. This interface includes a user accessible panel which is divided into four regions: three drug channel regions, each directly beneath one of the three drug channel mechanisms, and one fluid channel region directly beneath the fluid channel. The user can access all functions' of the Figure 2 system via the interface at any time after power-up, with the exception of self- diagnostics, system administrator functions, and floppy drive use.
In the Figure 2 embodiment, a touch screen 14 represents a module which is accessible to the user and controlled by the host controller 2. A key pad included on a host controller interface panel includes 16 front panel buttons in a preferred embodiment of the present invention. The panel can accommodate additional buttons if they are needed in alternate embodiments of the present invention, including several hidden buttons. Both an identity of a button being depressed and its state are read by the host controller 2.
The buttons which control drug delivery to a patient remain visible on the interface panel during the entire time delivery is occurring or is possible on that drug channel. The user is therefore not required to exit a current function to start or stop drug delivery. The drug name, current delivery rate, dose or a βetpoint of the PK model, and a pumping activity indicator are displayed for each drug channel on the interface panel.
The portion of the user interface located beneath the fluid channel mechanism includes a five digit display to identify delivery rate or total value delivered. LEDs are also included on the user interface panel to identify a power-on condition and to indicate when the system is running on battery power.
The host controller 2 provides channel set up functions for each of the drug channels 4, 6, 8 and fluid channel 10 shown in Figure 2. This includes automatic identification and channel association of drugs placed in each drug channel and overseeing automatic priming of the drug and fluid channels. In addition, the host controller 2 provides drug and fluid delivery functions, system maintenance functions, data storage functions and handling of exceptional cases (e.g., malfunctions and alarm indications to the user).
The drug identification feature is implemented during a drug channel set up, after the host 2 is notified by an independent controller 9 that a drug channel door has been closed with a drug cassette in place. At that time, the host controller 2 prompts the user to scan a bar code included on a drug vial label. For the host controller 2 to accept the scan as valid, the bar coded label must be accessible to the bar code reader. The bar code reader remains active as long as a drug channel door has been closed with a cassette in place and the associated bar code label has not yet been successfully scanned.
As described previously, two sensors provided in each channel indicate the presence or absence of the bar code reader directly in front of that channel. The drug vial to be scanned must be properly positioned in a drug channel to be identified by the bar code reader, otherwise its label will not be recognized by the system. After a drug has been loaded into a drug channel and a valid bar code has been read and the drug name has been recognized, the host controller 2 displays the name of the drug on a host display position below the drug channel receiving the drug vial. Once the bar code reader identifies the drug contained in a drug vial installed in a drug channel, the host controller 2 prompts the user to enter drug delivery information associated with that drug. The host controller 2 will not permit a drug channel to prime or pump any drug until the drug vial loaded into the channel has been successfully identified using the bar code reader.
A significant delivery function of the present invention is the ability to provide drug specific functions. For example, the host controller 2 allows the user to pick from allowed unit conversion sets specified for a particular drug being used. Unit conversion sets available for each drug are retained in the drug table of the host controller 2 memory. Drug delivery quantities in weight based units require entry of patient weight.
More particularly, after drug identification via the bar code reader, the host controller 2 displays all delivery control quantities (i.e., rate, dose and plasma level) using default units specified by a unit conversion set in the host controller's drug table for that drug, or, if preferred by the user, the units that were used during the most recent delivery of that drug. If other unit conversion sets are permitted for that drug, the host controller 2 permits the user to select one. Afterwards, all quantities are displayed using the new units for rate, dose and plasma level specified by the new unit conversion set.
As mentioned above, one of the primary functions of the host controller 2 is to oversee drug and fluid delivery. With regard to drug delivery, the host controller 2 is designed to control infusion rate and bolus dose delivery or PK model-based drug delivery. The host controller 2 permits either bolus delivery or infusion delivery, but when both a bolus delivery and an infusion delivery are recpiested simultaneously, the bolus delivery takes priority, causing delay of the infusion delivery until the bolus has been completed.
For a bolus delivery, a bolus dose in units selected by the user must be input by the user before the start of delivery. The host controller 2 will only permit a bolus delivery to occur for drugs which have been identified in a drug table of the host controller's memory as being deliverable by bolus. To prevent accidental delivery, the user must confirm the request for a bolus delivery prior to starting delivery. In a preferred embodiment, the user can also select desired duration for bolus delivery ranging from default (i.e., the shortest time over which the drug can be delivered) to durations which are multiples of the default duration) .
A bolus may be paused during delivery, after which the bolus may be resumed (i.e., causing the remaining dose to be delivered) or the bolus may be stopped, cancelling delivery of the remaining dose. No confirmation is required to resume a bolus once paused, and pausing does not affect the status of simultaneously delivered infusion delivery on the same channel.
Infusion delivery is only permitted for drugs which have been defined in the drug table as being deliverable by infusion. • Continuous infusion requires that the user input a desired infusion rate and infusion units before the start of infusion delivery. A default value of infusion units is provided by host controller 2. The infusion rate is, in an exemplary embodiment, equivalent to a range of 0.1 ml/hr to 1200 ml/hr.
A PK model is maintained in the host controller's memory for all drugs that are listed in the drug table as having PK models. When delivery of these drugs is initiated, the host controller 2 starts a PK model to continuously predict the theoretical plasma level of the drug being delivered. The selected PK model allows the user to query the predicted plasma level of the drug in a patient at any time during its delivery. Again, PK model-based delivery is only permitted for drugs which have been so defined in the drug table of the host controller 2. The system can provide the user with predicted (theoretical) plasma levels (i.e., level of drug in patient bloodstream) when delivering drugs by bolus or continuous infusion because a background calculation of the theoretical plasma level is continuously updated.
Before initiating a PK model-based delivery, the user must input a plasma level set point in user selectable units. The host controller 2 will not accept a plasma level set point greater than the maximum plasma level defined in the drug table for that drug. Further, PK delivery cannot be initiated until certain patient parameters, such as weight, have been confirmed by the user. Upon initiation of a PK delivery, the host controller 2 displays setpoint plasma level in user selected units, the predicted (theoretical) plasma level in the same units, and the infusion rate in default units throughout the entire PK model-based delivery.
In the fluid channel 10, only continuous infusion is permitted. The user must enter a delivery rate (e.g., between 1 and 1200 ml/hr) before fluid infusion can be initiated. In an exemplary embodiment, only ml and ml/hr are used to define fluid rate and cumulative dose units.
A key feature of the present invention is its ability to handle incompatibility between drugs administered to a patient via the Figure 2 system. For this purpose, the host controller 2 detects and informs the user of possible physical incompatibilities between drugs identified by the bar code reader. The host controller 2 allows the user to decide whether to allow the system to automatically handle incompatible drug pairs involving bolus delivery. If the user decides to let the system automatically handle the incompatibility, the host controller 2 provides a visible indication on those channels that an incompatibility exists and that it will be automatically handled.
On channels where compatibility handling is active, bolus deliveries are preceded by and followed by a flush delivery from the fluid channel. Once a flush delivery for an incompatible bolus is completed, the fluid channel reverts to its previous delivery rate. The volume of each flush delivery is added to the total fluid delivered during the current patient case and stored in memory of the host controller 2.
The host controller can be designed to handle incompatibilities in all infusion mode combinations. In the preferred embodiment, the host controller 2 does not provide special handling for infusions, PK deliveries, or for three incompatible drugs loaded into the system at the same time, on channels where compatibility handling is active. Rather, the host controller 2 informs the user upon identification of incompatible drug conditions. Further, a visual indication of any currently incompatible drugs is provided to the user.
For each drug loaded and identified on the Figure 2 system, the user can view the current total amount of drug delivered from the start of delivery to a particular patient. This information is stored in the host memory and is continuously updated throughout the delivery. For each drug loaded and identified, the user can specify a maximum dose limit for the duration of delivery to the patient. Once reached, the user is informed, but pumping continues. The user dose limit is reset and disabled when the patient case ends. The host controller 2 also includes a global stop which deactivates all 3 drug channels at once. Each channel must then be individually restarted to resume pumping.
Similarly, fluid specific functions are provided for the fluid channel 10. More particularly, the user can view the current total volume of fluid delivered to a patient from the beginning of the patient case. Further, the user can enter a maximum volume limit of fluid for each patient case. Once reached, the user is informed and fluid delivery is discontinued. The user volume limit is reset and disabled when the patient case ends.
The Figure 2 host controller 2 also provides a plurality of system maintenance functions. These functions include a start up/shut down function, disk archiving function, configuration features, installation/security features, and system update.
The start up/shut down functions prevent drug and fluid delivery to a patient prior to user instruction to the host controller 2. The host controller 2 allows the user to end a current patient case only when no channel is pumping. Upon ending the patient case, the host controller 2 displays total volumes delivered and used for priming the administration set for each drug used, as well as total volume of fluid delivered and used for priming. These volumes are expressed in display units used at the time the patient case ended.
The disk archiving function of the host controller 2 stores event history and patient case information to floppy disk for later use and analysis. Configuration functions of the host controller 2 provide a means for the current date and time to be set.
At the user's option, access to certain functions of the host controller 2 is restricted and requires the use of a password. Once the password is successfully entered, the host controller 2 can be controlled to access an exception conditions log, an event history, user information, patient case information, and installation record/drug usage. Further, at the user's option, entry of this password can be required before information stored in the system can be transferred to the floppy disk. In addition, entry of the correct password can be used to control entry of information into the host controller's memory (e.g., hospital name, drug table updates and names of users allowed access to the system) . The password cannot be changed unless access to the system has been obtained, nor can the password be viewed unless access to the system has been obtained following accurate entry of the current password. Use of the password can thus be used to control access to a variety of features of the host controller 2.
As mentioned above, the present invention can provide data storage of event history, an exception conditions log, user information, patient case information, installation record/drug usage and drug tables. Event history data is stored by the host controller 2 as a chronological record of system cases associated with the Figure 2 system alarms, malfunctions, and user interaction with the system. The event history data is stored in the non-volatile host controller's memory, and can be viewed by the user.
In an exemplary embodiment, the host controller 2 can store all cases that occur over a period of 7 days of continuous use. Once the case buffer is filled, old cases are discarded as new cases occur. The host controller 2 permits the user to disable and enable event history recording, and when disabled no subsequent cases are stored in the event history portion of the host controller's memory.
Exception conditions are stored by the host controller 2 as a chronological record of at least the last 30 exception conditions (i.e., malfunctions and alarms) applicable to the entire Figure 2 system. Again, this log is stored in a non-volatile area of host controller's memory. Pumping channel exceptions are not stored in the individual pumps, but are stored as data in this portion of host controller's memory. Exception data is recorded automatically and cannot be disabled or erased by the user.
The host controller 2 also stores user information. This information includes, for example, up to 100 alphanumeric user IDs in a non¬ volatile area of host controller's memory.
Patient case data can, in an exemplary embodiment, be retained on the last 50 patient cases. The host controller 2 allows the user to optionally store a patient ID as well as other information on age, sex, and weight. The patient weight can be input and displayed in pounds or kilograms.
For each patient case, the host controller 2 stores the user ID of the user who ended the patient case, the total number of users who identified themselves to the system during the patient case, the time the patient case started, and the duration of the patient case. The host controller 2 also records the number of drugs delivered during the patient case, the total volume delivered and total volume used in priming for each drug used during the patient case, as well as the total volume of fluid delivered and total volume used in priming. This information is expressed in display units currently being used at the time the patient case ended.
Installation record/drug usage data is retained by the host controller 2 and includes information regarding the installer's name, the site name, installation date and information pertaining to specific hardware configuration of the Figure 2 system.
Drug table data is also stored by the host controller 2. The drug table includes information (e.g., drug incompatibilities, suitability for bolus infusion delivery or PK delivery, PK model-based input parameters and maximum allowable infusion rates, bolus doses, and theoretical plasma levels) for each drug as described previously.
Another key feature of the present invention is its ability to handle exception conditions. More particularly, when a malfunction, audible alarm or audible warning occurs, audio signal is emitted by the host controller 2 to alert the user. This audio signal is only discontinued when the user has acknowledged the condition, but may be temporarily stopped using a silence alarm button on the host controller interface panel. When a non-audible alarm or non-audible warning occurs, a discrete audio signal is optically generated to alert the user.
The host controller 2 detects malfunctions in the Figure 2 system. Malfunctions which are identified by the host controller 2 and communicated to the user include signals indicating that a fluid or drug channel is unavailable due to an internal malfunction, indication that the system is unavailable due to a malfunction, and indications that the disk drive or other peripheral components are unavailable due to a malfunction.
The system can be configured to require presence of a drop detector in the fluid channel. When so configured, the host controller 2 requires the user to discontinue fluid channel operation when an alarm indicating the absence of a drop detector occurs. The fluid channel cannot be restarted until the exception condition regarding absence of the drop detector is rectified. Alarms associated with the fluid delivery channel 10 include, for example, indications that the fluid channel autoprime mechanism has failed, that there is air in the fluid channel line, that the fluid channel door has been opened while pumping or that the fluid channel bag is empty. When fluid is unavailable, the host controller 2 allows the user to stop the fluid channel 10 and enter a new pumping rate, but the fluid channel 10 cannot be restarted until the exception condition is rectified. Alarms are also generated when there is a proximal occlusion or distal occlusion in the fluid channel pump, when there is a pressure error in the fluid channel 10, when the fluid channel volume limit is reached. In a preferred embodiment, the foregoing alarms are the minimum alarm conditions provided. Those skilled in the art will recognize that any number of alarms based on detection of any desired condition can be provided.
In a preferred embodiment, alarms associated with the drug channels 4, 6, 8 are, at a minimum, provided to the user when there is proximal or distal air detection in the drug channel cassette 13, when a channel door has been opened while pumping, when there is a proximal or distal occlusion in the cassette, when distal pressure is out of range, or when drug is unavailable. Non-audible alarms generated by host controller 2 include when AC power is not available or when the battery becomes discharged, failure to recognize a bar code, failure to associate a bar code with a channel, or alarms associated with floppy disk operation.
In a preferred embodiment, audible warnings (i.e., potential alarm condition) include, at a minimum, when the battery is low or when a drug container is near empty. Non-audible warnings include detection of excess air in an air trap chamber of a pumping cassette, loss of AC power or potential drug incompabilities.
Drug and fluid channel status conditions are also continuously provided from the pumping channels to the host controller 2 for display. Status conditions which are displayed to the user via the host controller interface panel include, channel unavailable status, inactive status, autopriming status, backpriming status, testing cassette status, cassette test failure status, prime needed status, backprime needed status, prime verification needed status, infusion on hold status, bolus on hold status.
System status conditions which can be displayed via the host controller interface panel include: battery low status, security covers locked status, fluid channel unavailable status, drop detector missing status, volume limit reached status, disk drive unavailable status, patient parameters needed status, and user ID needed status.
As illustrated by Figure 4, user interaction with the Figure 2 system is via a user interface 3 in the host controller 2. Communication of commands, data, exception conditions, status and other information between the host controller 2 and drug and fluid channels is via the aforementioned serial communication link, capable of two-way communication. Communication is, for example, via packets limited to 30 bytes to ensure real time operation. Typical communications between the host controller 2 and pumping channels is via a command- acknowledgement loop. The host controller 2 (master) sends a command packet to one of the four pumping channel controllers 9 (slave), or vice versa. The targeted channel sends back an acknowledgement indicating receipt and initiation of appropriate action in.response to the command.
Master-slave polling is used to detect synchronous communications between the host controller 2 and pumping channels 4, 6, 8 and 10. These synchronous communications include, for example, the aforementioned alarms and door open/door closed conditions. When, alarm conditions are sent from a pumping channel 4, 6, 8 and 10 to the host controller 2, the pumping channel awaits acknowledgement from the host controller 2. If an event is not acknowledged within a set time frame, the event is retransmitted until acknowledgement is received. After acknowledging the pump channel communication, the host controller 2 can either send a reset command to the pump or report failure to the user. For multi-event conditions, a pumping channel module will queue cases until all are acknowledged.
When multiple command packets are received or sent by the host controller 2, either the entire command packet is completed or the entire command packet is aborted. Thus, if an alarm condition occurs during execution of a multi-command packet, the partial command packet is not processed. Rather, the entire packet must be resent and executed in its entirety.
Where an illegal command is attempted, the command is ignored. An illegal command represents a command that cannot be processed at the time it is received. For example, when a drug channel 4, 6 and 8 is an unprimed state, a start command which is received cannot be executed. A more detailed discussion will now be provided of the drug channels 4, 6 and 8. Each drug channel 4, 6 and 8 includes a pump which is preset at a position having an outlet valve closed, and an inlet valve open. A closed door switch is included in each drug pump to indicate when a drug channel door is closed with a cassette in place. An open door switch indicates that the drug channel door has been opened.
Pumping is accomplished in each drug channel via a pumping cassette which includes one or two proximal (inlet) lines and one distal (outlet) line. The pump includes a mechanical reciprocating plunger mechanism and a pumping cassette through which the drugs are pumped. The pumping cassette has a primary inlet port and a pumped-liquid outlet port. The primary inlet port is connected to a piercing pin for receiving drug from a vial. However, alternative drug containers and connection methods can be used. The cassette also includes a secondary inlet port which remains normally closed. However, if desired, the secondary inlet port can receive a second drug, or drug diluent, for mixing with drug which has been introduced to the cassette via the primary inlet port.
A principal function of the independent controller 9 in each drug channel is to control drug delivery, priming of the drug delivery line, communication with the host controller 2, error detection and error reporting within the drug channel. The principal activity of the drug channel is drug delivery, whereby liquid is moved from one of the cassette inlet lines to the outlet line. The inlet lines, referred to herein as primary and secondary inlets, are typically configured with the primary line connected to a drug vial, and the secondary line disconnected. An exemplary delivery range is from .1 ml/hr to 1200 ml/hr.
For each pumping cassette, the drug channel controller responds to user commands to control bi-directional flow. Bi-directional flow control is critical for autopriming. During autopriming, the host controller 2 instructs operation of the valve actuators and plungers in each drug channel to displace air from the drug cassette. Further, the autopriming sequence can be used for priming the output line to the patient.
Each drug channel receives commands directly from the host controller 2 via the serial communication interface at an exemplary data rate of 1200 baud. These commands include the aforementioned communications to set rate, start pumping and so forth. Each independent controller 9 detects anomalies within its own drug channel pumping line. Error conditions and significant cases are communicated by each channel controller to the host controller 2.
Three different priming operations are required for the drug channel: the drug channel can fill, with drug, a cassette which is full of air distal to the air trap chamber (i.e., completely empty cassettes, cassettes with air in the pumping bowl, and cassettes with air in the distal tubing) ; the drug channel can remove air introduced into the cassette air trap without moving it to the outlet line; and the drug channel can remove air trapped between the secondary inlet and an optional secondary reservoir. The drug channel detects errors and reporting is performed by the drug channel to the host controller 2 with respect to four classes of errors: electronic, mechanical, cassette and communication.
Electronic integrity verification concerns the microprocessor memory, A/D lines and other microprocessor board and sensory apparatus. Mechanical integrity verification concerns verifying the mechanical pumping system is moving in accordance with commanded operation via the use of position detection feedback on three stepper motors included in each drug channel. Cassette integrity verification ensures that a cassette introduced to a drug channel is capable of withstanding pressures associated with pumping without leaking and is not occluded. Communication error detection is necessary to verify that transmitted data is accurate in accordance with the serial communication protocol. All failures are transmitted by the drug channel to the host controller 2, and the drug channel will confirm that the host controller 2 is aware when an alarm condition exists.
More particularly, electronic integrity verification is used to verify electronic and software integrity. For example, on power-up, the drug channel performs a RAM test, a ROM test, an A/D converter test and a watchdog test. The drug channel verifies serial communication integrity by the on-going existence of incoming message packets. The drug channel verifies integrity of the air sensor by ensuring an air signal is seen whenever the door is open.
Mechanical integrity verification to ensure safety, involves verifying an ability of the pump channel mechanism and cassette to pump accurately. These tests are performed before pumping, and if any test fails, the drug channel is not permitted to pump. Motor position check and re-synchronization tasks (if necessary) are performed prior to pumping (e.g., when the system is activated), and no maximum time requirements are associated with these tasks.
Another function of each drug channel (4,6,8) is to perform a cassette integrity test to check for static occlusion and valve leaks when a cassette door is closed with a cassette in place. Occlusion detection is performed via the proximal and distal pressure sensors (i.e., pressure threshold is exceeded on proximal or distal side), after which an occlusion alarm is reported by the affected drug channel to the host controller 2.
Leak tests are performed automatically whenever the cassette door is closed with a cassette in place. All of these tests are performed by monitoring pressure inside the cassette and are, for example, used to indicate the need for backpriming the cassette (automatic removal of air from the cassette done by pushing it back into the drug container) or to indicate that a bad cassette needs to be replaced. The proximal pressure sensor self-test is used to ensure that the pressure sensor stays within a desired operating range.
A priming function of each drug channel (4,6,8) removes air from the drug delivery set. A drug delivery set includes a pumping cassette, distal tubing, and vial adapter. Priming operations perform both proximal and distal occlusion detection.
A pumping function is initiated in response to a start pumping command after all integrity tests have been implemented and passed. During pumping, mechanical motor position flags are monitored continuously by optical sensors.
The pumping function of the drug channel provides for proximal occlusion detection and distal occlusion detection using proximal and distal pressure sensors, respectively. A distal air in line alarm and stop pumping signal are generated by a drug channel if an air bubble (e.g., greater than, for example, 100 μ£ ) (microliter) , occurs at the distal air detector. The pump will also generate a distal air in line alarm if, for example, 200 μS. out of the last 2.0 ml of volume was air.
The pumping function also includes an empty container detection when cumulative amount (e.g., 200 μ£ ) of air has entered the cassette from at least one inlet line. This cumulative total is reset whenever the cassette door is opened, or a priming operation is performed. A door open detection mode of the drug channels 4, 6, and 8 is used to trigger return of the step motors in a given drug channel to a preset position. At all times except for electronic self-tests, (i.e., pumping, priming, and so forth), a "door opened" alarm is generated and transmitted to the host controller 2. After the door is opened, the drug . channel retains pumping parameters (i.e., rate, dose limit, delivered dose) except for pressure limit. When the door is again closed, the drug channel retains all of these parameters until commanded to change by the host controller 2.
A description will now be provided of a fluid channel 10 control. A fluid pump within a fluid channel includes a plunger/inlet valve/outlet valve assembly and a DC motor to pump fluid.
The fluid channel controller 9 communicates with the host controller 2 via the serial communication interface to receive commands such as set rate, start and operational commands. Like the drug channels, the fluid channel 10 detects anomalies in the pumping line and communicates error conditions and significant cases to the host controller 2.
The fluid channel 10 controls fluid delivery from inlet tubing to outlet tubing in an exemplary range of from 1 ml/hr to 1200 ml/hr. Further, the fluid channel 10 controls priming of air filled delivery tubing automatically. Like the drug channels, the fluid channel can detect four similar classes of errors: electronic, mechanical, fluid and communication.
Because pumping is the primary function of the fluid channel 10, various parameters are accessible by the host controller 2 to configure the fluid channel behavior during pumping cycles. These parameters include delivery rate, dose limit, drop detector, priming time limit and door closed flag. The drop detector parameter determines whether detection of an empty fluid container is required during the delivery cycle. This parameter can be selectively recpiested by the host controller 2. The priming time limit parameter provides fail-safe operation of the priming process. The door closed flag ensures that pumping and priming do not occur unless the delivery tubing is inserted and the pumping mechanism door latches closed. The flag is set whenever both the delivery tubing is inserted and the door latch is closed, and either a door opening or tubing removal will reset this flag.
Pumping functions of the fluid channel 10 include a priming cycle and a delivery cycle. Priming of the delivery tubing in response to a command from the host controller 2 consists of two phases: a proximal tubing filling phase and a distal tubing filling phase. During the proximal tubing filling phase, the fluid channel 10 activates its priming mechanism and starts pumping until a distal air sensor detects continuous fluid flow. After continuous fluid flow is detected, the priming mechanism is deactivated and control advances to a distal tubing filling phase. In the distal tubing filling phase, fluid is delivered at a specified delivery rate until the specified dose limit is reached as with a normal delivery cycle. The only difference is that when an air-in-line condition is detected during the distal tubing filling phase, the priming cycle returns to the proximal tubing filling phase instead of terminating the priming process.
Priming is discontinued when a specified dose limit is reached during the distal tube filling phase, upon receipt of a stop command from the host controller 2, upon expiration of a priming time limit, upon detection of an empty container by a drop detector, or by an alarm in response to error detection. During the delivery cycle, the fluid channel 10 delivers fluid from its proximal tubing to its distal tubing at the specified delivery rate, until stopped by the user or the user specified dose limit is reached.
Error detection is similar to that of the drug channels and includes electronic, mechanical and fluid integrity checks. An error detected by these tests results in stoppage of the pumping process and communication of the error to the host controller 2.
For example, electronic integrity verification includes use of a watchdog timer to interrupt the fluid channel CPU to ensure integrity of the fluid channel CPU, critical data storage verification, and sensor range verification with regard to temperature and power supply voltages. Mechanical integrity verification includes monitoring of motor slippage, monitoring of plunger motor shaft encoder slippage, pumping rate verification and motor voltage verification. Fluid integrity verification includes air-in-line detection, empty container detection, proximal occlusion detection, distal occlusion detection and differential distal occlusion detection (i.e., when average depositive pressure buildup of distal pressure, relative to the distal pressure at pumping start time, is detected). Detection of a drop detector (if required) and loss of the drop detector signal are also monitored.
It will be appreciated by those skilled in the art that the present invention can be embodied in other specific forms without departing from the spirit or essential characteristics thereof. The presently disclosed embodiments are therefore considered in all respects to be illustrative and not restrictive. The scope of the invention is indicated by the appended claims rather than the foregoing description, and all changes that come within the meaning and range of equivalents thereof are intended to be embraced therein.

Claims

What is Claimed is:
1. A control system for use with an automated intravenous drug and fluid infusion system, said control system comprising: plural pumping channels that operate independently for intravenously infusing drugs and fluid, each of said pumping channels having a pumping channel controller for independent delivery in multiple infusion modes; and a host controller that monitors each of the pumping channels concurrently.
2. A control system according to claim 1, further including: a bar code system for reading a bar code from a supply container to be used in a pumping channel, said supply container holding a drug, a fluid or a combination of a drug and a fluid.
3. A control system according to claim 2, wherein said bar code system further includes: sensors located within at least one of said pumping channels to detect a presence of the bar code reader in a vicinity of at least one pumping channel.
4. A control system according to claim 3, wherein said sensors include: electro-magnetic sensors which are arranged in each pumping channel to detect the presence of the bar code reader, the arrangement of sensors in each channel being different to uniquely identify each channel.
5. A control system according to claim 4, wherein said sensors are Hall effect sensors.
6. A control system according to claim 5, wherein said host controller receives signals generated within each of the pumping channels to identify a drug or fluid selected for use in that channel, and to control channel priming and delivery in response to the received signals.
7. A control system according to claim 6, wherein said host controller further includes: a touch screen for user entry of control information, including drug dose and drug delivery rate for each drug pumping channel, and fluid delivery rate for each fluid pumping channel.
8. A control system according to claim 7, wherein said host controller further includes: a display for displaying a selected drug, drug dose and delivery rate to the user for each drug channel, and for displaying fluid delivery rate for the fluid channel.
9. A control system according to claim 8, wherein each pumping channel control responds to commands from the host controller to perform pumping channel priming and delivery, and to signal error and status conditions of each pumping channel to the host controller, such that delivery of significant air to a patient is prevented.
10. A control system for use with an automated intravenous drug and fluid infusion system, said control system comprising: plural pumping channels that operate independently for intravenously infusing drugs and fluid, each of said pumping channels having a pumping channel controller for independent delivery of drug and/or fluid in multiple drug infusion modes; a host controller that monitors each of the pumping channels concurrently, each of said pumping channels further including: automatic priming means for removing gases from each pumping channel independently to prevent delivery of significant air to a patient; and means for preventing priming of a channel unless verification is provided that the channel is not connected to a patient.
11. A control system according to claim 10, wherein said preventing means further includes: means for identifying a drug and fluid selected for use in each pumping channel.
12. A control system according to claim 11, further including: a user touch screen for entering control information, said control information including drug dose and drug delivery rate for each drug pumping channel, and fluid delivery rate for each fluid pumping channel.
13. A control system according to claim 12, further including: means for displaying a selected drug, drug dose and delivery rate to the user for each drug channel, and displaying fluid delivery rate for the fluid channel.
14. A control system according to claim 13, wherein each of said pumping channel controllers further includes: means for responding to commands to perform channel priming and delivery, and for signaling error and status conditions of each pumping channel.
15. A control system according to claim 14, wherein said host controller includes: means for determining whether drugs selected for one or more pumping channels are compatible; and means for displaying incompatible drugs to the user.
16. A control system for use with an automated intravenous drug and fluid infusion system, said control system comprising: plural pumping channels that operate independently for intravenously infusing drugs and fluid, each of said pumping channels having a pumping channel controller for independent delivery from each channel in multiple infusion modes; a host controller that monitors each of the pumping channels concurrently, each of said pumping channels further including: means for identifying a particular drug that is to be pumped through a drug pumping channel.
17. A control system according to claim 16, wherein said identifying means further includes: a bar code system for reading a bar code from a drug supply container to be used in a pumping channel.
18. A control system according to claim 17, wherein said identifying means further includes: means for detecting a presence of a bar code reader in a vicinity of at least one pumping channel.
19. A control system according to claim 18, wherein said detecting means includes: electro-magnetic sensors in each pumping channel to detect the presence of the bar code reader, the arrangement of sensors in each channel being different to uniquely identify each channel.
20. A control system according to claim 16, wherein said host controller further includes: means for prompting a user to input pumping channel control parameters; and means for converting quantities designated by the user into units for processing by the host controller.
21. A control system according to claim 16, wherein said host controller and at least one pumping channel controller include: means for controlling pharmacokinetic-based delivery of a drug; and means for displaying predicted plasma level based on the pharmacokinetic-based delivery.
22. A control system according to claim 16, further including: means for maintaining an updated log of drug and fluid delivery, including a record of system errors which have occurred during delivery.
PCT/US1993/011033 1992-11-25 1993-11-15 Automated drug infusion system WO1994012235A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU56063/94A AU5606394A (en) 1992-11-25 1993-11-15 Automated drug infusion system

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US07/981,673 US5378231A (en) 1992-11-25 1992-11-25 Automated drug infusion system
US07/981,673 1992-11-25

Publications (1)

Publication Number Publication Date
WO1994012235A1 true WO1994012235A1 (en) 1994-06-09

Family

ID=25528567

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1993/011033 WO1994012235A1 (en) 1992-11-25 1993-11-15 Automated drug infusion system

Country Status (4)

Country Link
US (2) US5378231A (en)
AU (1) AU5606394A (en)
CA (1) CA2150258A1 (en)
WO (1) WO1994012235A1 (en)

Cited By (20)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1997021456A1 (en) * 1995-12-12 1997-06-19 The University Of Melbourne Field programmable intravenous infusion system
GB2309801A (en) * 1996-01-31 1997-08-06 Meldet Ltd System for delivery of drugs and therapeutic agents
WO1997037704A1 (en) * 1996-04-10 1997-10-16 Baxter International Inc. Medical infusion pump
WO1999010029A1 (en) * 1997-08-22 1999-03-04 Deka Products Limited Partnership System and method for intelligent admixture and delivery of medications
US5882338A (en) * 1993-05-04 1999-03-16 Zeneca Limited Syringes and syringe pumps
US5980501A (en) * 1994-11-02 1999-11-09 Zeneca Limited Reservoirs and delivery devices
US6019745A (en) * 1993-05-04 2000-02-01 Zeneca Limited Syringes and syringe pumps
US6210361B1 (en) 1997-08-22 2001-04-03 Deka Products Limited Partnership System for delivering intravenous drugs
ITFI20080147A1 (en) * 2008-08-01 2010-02-02 Software Centric Srl DRUG ADMINISTRATION SYSTEM
US7668731B2 (en) 2002-01-11 2010-02-23 Baxter International Inc. Medication delivery system
US7698156B2 (en) 2002-01-29 2010-04-13 Baxter International Inc. System and method for identifying data streams associated with medical equipment
EP2628496A1 (en) * 2005-03-07 2013-08-21 Mallinckrodt LLC Injector auto purge
WO2015040122A1 (en) * 2013-09-20 2015-03-26 Sanofi-Aventis Deutschland Gmbh Conditional required priming
US8994382B2 (en) 2006-04-12 2015-03-31 Novo Nordisk A/S Absolute position determination of movably mounted member in medication delivery device
US9522238B2 (en) 2005-05-10 2016-12-20 Novo Nordisk A/S Injection device comprising an optical sensor
US9950117B2 (en) 2009-02-13 2018-04-24 Novo Nordisk A/S Medical device and cartridge
US10061899B2 (en) 2008-07-09 2018-08-28 Baxter International Inc. Home therapy machine
US10173008B2 (en) 2002-01-29 2019-01-08 Baxter International Inc. System and method for communicating with a dialysis machine through a network
US10294450B2 (en) 2015-10-09 2019-05-21 Deka Products Limited Partnership Fluid pumping and bioreactor system
US11299705B2 (en) 2016-11-07 2022-04-12 Deka Products Limited Partnership System and method for creating tissue

Families Citing this family (290)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5803712A (en) 1988-05-17 1998-09-08 Patient Solutions, Inc. Method of measuring an occlusion in an infusion device with disposable elements
EP0650738B1 (en) 1993-10-28 2003-05-02 Medrad, Inc. Multi-patient fluid dispensing
EP1258262A3 (en) * 1993-10-28 2002-12-18 Medrad, Inc. Total system for contrast delivery
CA2129284C (en) * 1993-11-24 1999-03-09 Kenneth J. Niehoff Controlling plunger drives for fluid injection in animals
US5608650A (en) * 1994-08-19 1997-03-04 Spectrel Partners, L.L.C. Systems and methods for testing pump flow rates
US5717603A (en) * 1994-08-19 1998-02-10 Spectrel Partners, L.L.C. Integrated test station for testing liquid flow and electrical safety characteristics of IV pumps
US5856929A (en) * 1994-08-19 1999-01-05 Spectrel Partners, L.L.C. Integrated systems for testing and certifying the physical, functional, and electrical performance of IV pumps
US6757630B2 (en) 1994-08-19 2004-06-29 Mediq/Prn Life Support Services, Inc. Integrated systems for testing and certifying the physical, functional, and electrical performance of IV pumps
EP0778034A4 (en) * 1994-08-24 1998-05-13 Eli Lilly Japan K K Injection apparatus
US5840026A (en) 1994-09-21 1998-11-24 Medrad, Inc. Patient specific dosing contrast delivery systems and methods
US7349858B1 (en) * 1994-12-16 2008-03-25 Automed Technologies, Inc. Method of dispensing and tracking the giving of medical items to patients
US5814015A (en) * 1995-02-24 1998-09-29 Harvard Clinical Technology, Inc. Infusion pump for at least one syringe
US5637093A (en) 1995-03-06 1997-06-10 Sabratek Corporation Infusion pump with selective backlight
US5795327A (en) 1995-03-06 1998-08-18 Sabratek Corporation Infusion pump with historical data recording
US6671563B1 (en) 1995-05-15 2003-12-30 Alaris Medical Systems, Inc. System and method for collecting data and managing patient care
USD386259S (en) * 1995-11-13 1997-11-11 Sanyo Electric Co., Limited Medication dispenser
GB9525562D0 (en) * 1995-12-14 1996-02-14 Smiths Industries Plc Fluid administration
GB9607471D0 (en) * 1996-04-10 1996-06-12 Baxter Int Volumetric infusion pump
IL118766A0 (en) * 1996-07-01 1996-10-31 Medun Ltd Improved infusion apparatus
US7070590B1 (en) * 1996-07-02 2006-07-04 Massachusetts Institute Of Technology Microchip drug delivery devices
US6689091B2 (en) 1996-08-02 2004-02-10 Tuan Bui Medical apparatus with remote control
US5885245A (en) * 1996-08-02 1999-03-23 Sabratek Corporation Medical apparatus with remote virtual input device
US5895371A (en) * 1996-08-27 1999-04-20 Sabratek Corporation Medical treatment apparatus and method
US6605057B2 (en) 1996-10-24 2003-08-12 Medtronic Ave, Inc. Reinforced monorail balloon catheter
US5916197A (en) * 1997-02-14 1999-06-29 Medrad, Inc. Injection system, pump system for use therein and method of use of pumping system
US5984893A (en) * 1997-03-27 1999-11-16 Ward; Roger T. Blood infusion control system
US6070761A (en) 1997-08-22 2000-06-06 Deka Products Limited Partnership Vial loading method and apparatus for intelligent admixture and delivery of intravenous drugs
US6468242B1 (en) 1998-03-06 2002-10-22 Baxter International Inc. Medical apparatus with patient data recording
US7308894B2 (en) * 1998-06-03 2007-12-18 Scott Laboratories, Inc. Apparatuses and methods for providing a conscious patient relief from pain and anxiety associated with medical or surgical procedures according to appropriate clinical heuristics
US6422057B1 (en) * 1998-09-29 2002-07-23 Deltec, Inc. Drug pump testing system and methods
US6164921A (en) 1998-11-09 2000-12-26 Moubayed; Ahmad Maher Curvilinear peristaltic pump having insertable tubing assembly
US6202708B1 (en) * 1998-11-09 2001-03-20 Sims Deltec, Inc. Fillable cassette apparatus and method
US6398727B1 (en) * 1998-12-23 2002-06-04 Baxter International Inc. Method and apparatus for providing patient care
US6231560B1 (en) 1999-02-10 2001-05-15 Baxter International Inc Method and apparatus for automatically controlling the level of medication
SE522908C2 (en) * 1999-05-10 2004-03-16 Aneo Ab Arrangements for granting a living being an anesthetic condition
US7933780B2 (en) * 1999-10-22 2011-04-26 Telaric, Llc Method and apparatus for controlling an infusion pump or the like
WO2001035928A1 (en) 1999-11-17 2001-05-25 Microchips, Inc. Microfabricated devices for the delivery of molecules into a carrier fluid
US7645258B2 (en) * 1999-12-01 2010-01-12 B. Braun Medical, Inc. Patient medication IV delivery pump with wireless communication to a hospital information management system
US6519569B1 (en) * 1999-12-01 2003-02-11 B. Braun Medical, Inc. Security infusion pump with bar code reader
US6790198B1 (en) 1999-12-01 2004-09-14 B-Braun Medical, Inc. Patient medication IV delivery pump with wireless communication to a hospital information management system
AU1453901A (en) * 1999-12-22 2001-07-03 Catharsis Medical Technology, Inc. Adverse drug event monitoring
SE523162C2 (en) * 2000-01-25 2004-03-30 Aneo Ab Arrangements for granting a living being an anesthetic condition
US20010041869A1 (en) * 2000-03-23 2001-11-15 Causey James D. Control tabs for infusion devices and methods of using the same
US7971588B2 (en) * 2000-05-05 2011-07-05 Novartis Ag Methods and systems for operating an aerosol generator
US9427520B2 (en) 2005-02-11 2016-08-30 Carefusion 303, Inc. Management of pending medication orders
US20050171815A1 (en) * 2003-12-31 2005-08-04 Vanderveen Timothy W. Centralized medication management system
US20040172283A1 (en) * 2003-02-09 2004-09-02 Vanderveen Timothy W. Medication management and event logger and analysis system
BR0110933B1 (en) * 2000-05-18 2009-08-11 electrically controlled or computerized syringe to dispense a fluid material.
US10353856B2 (en) 2011-03-17 2019-07-16 Carefusion 303, Inc. Scalable communication system
AU6172301A (en) 2000-05-18 2001-11-26 Alaris Meidical Systems Inc Distributed remote asset and medication management drug delivery system
US7860583B2 (en) * 2004-08-25 2010-12-28 Carefusion 303, Inc. System and method for dynamically adjusting patient therapy
US9069887B2 (en) 2000-05-18 2015-06-30 Carefusion 303, Inc. Patient-specific medication management system
US11087873B2 (en) 2000-05-18 2021-08-10 Carefusion 303, Inc. Context-aware healthcare notification system
US9741001B2 (en) 2000-05-18 2017-08-22 Carefusion 303, Inc. Predictive medication safety
US10062457B2 (en) 2012-07-26 2018-08-28 Carefusion 303, Inc. Predictive notifications for adverse patient events
EP1335764B1 (en) * 2000-09-08 2007-06-06 Insulet Corporation Device and system for patient infusion
AU2002211567A1 (en) * 2000-10-10 2002-04-22 Dentsply International Inc. Fluid material dispensing syringe
EP1355564A4 (en) 2000-12-19 2007-06-06 Univ Rochester Method and device for administering medication and/or placebo
US20030040938A1 (en) * 2001-04-28 2003-02-27 Baxter International Inc. A system and method for managing inventory of blood component collection soft goods in a blood component collection facility
WO2002099457A1 (en) * 2001-05-31 2002-12-12 Massachusetts Inst Technology Microchip devices with improved reservoir opening
US20020184369A1 (en) * 2001-05-31 2002-12-05 Parkinson Steven William Appointment scheme for redistributing service access
EP1436029A4 (en) * 2001-09-24 2009-12-30 Scott Lab Inc Methods and apparatuses for assuring quality and safety of drug administration and medical products and kits
AU2002351275B2 (en) * 2001-12-06 2007-12-20 Carefusion 303, Inc. C02 monitored drug infusion system
US20030125662A1 (en) 2002-01-03 2003-07-03 Tuan Bui Method and apparatus for providing medical treatment therapy based on calculated demand
US8775196B2 (en) * 2002-01-29 2014-07-08 Baxter International Inc. System and method for notification and escalation of medical data
US20030204419A1 (en) * 2002-04-30 2003-10-30 Wilkes Gordon J. Automated messaging center system and method for use with a healthcare system
US20040010425A1 (en) * 2002-01-29 2004-01-15 Wilkes Gordon J. System and method for integrating clinical documentation with the point of care treatment of a patient
US20030141368A1 (en) * 2002-01-29 2003-07-31 Florante Pascual System and method for obtaining information from a bar code for use with a healthcare system
US7109974B2 (en) * 2002-03-05 2006-09-19 Matsushita Electric Industrial Co., Ltd. Remote control system including an on-screen display (OSD)
US20030204416A1 (en) * 2002-04-30 2003-10-30 Sayeh Radpay System and method for facilitating time-based infusion orders
US20040167804A1 (en) * 2002-04-30 2004-08-26 Simpson Thomas L.C. Medical data communication notification and messaging system and method
US20040172301A1 (en) * 2002-04-30 2004-09-02 Mihai Dan M. Remote multi-purpose user interface for a healthcare system
US20040176667A1 (en) * 2002-04-30 2004-09-09 Mihai Dan M. Method and system for medical device connectivity
US6749582B2 (en) * 2002-04-30 2004-06-15 The First Years Inc. Pumping breast milk
US8234128B2 (en) 2002-04-30 2012-07-31 Baxter International, Inc. System and method for verifying medical device operational parameters
US20040172300A1 (en) * 2002-04-30 2004-09-02 Mihai Dan M. Method and system for integrating data flows
US20030201697A1 (en) * 2002-04-30 2003-10-30 Richardson William R. Storage device for health care facility
US20050065817A1 (en) * 2002-04-30 2005-03-24 Mihai Dan M. Separation of validated information and functions in a healthcare system
US20030225596A1 (en) * 2002-05-31 2003-12-04 Richardson Bill R. Biometric security for access to a storage device for a healthcare facility
US20040078231A1 (en) * 2002-05-31 2004-04-22 Wilkes Gordon J. System and method for facilitating and administering treatment to a patient, including clinical decision making, order workflow and integration of clinical documentation
US7018361B2 (en) * 2002-06-14 2006-03-28 Baxter International Inc. Infusion pump
US7835927B2 (en) * 2002-12-27 2010-11-16 Carefusion 303, Inc. Medication management system
WO2004089445A1 (en) * 2003-04-02 2004-10-21 Tsukada Medical Research Co., Ltd. Electric liquid convey and injection system
US20190357827A1 (en) 2003-08-01 2019-11-28 Dexcom, Inc. Analyte sensor
US8422413B2 (en) * 2003-09-18 2013-04-16 Dentsply International Inc. Process and device for the wireless transmission of dental process data
US20060089854A1 (en) * 2003-10-07 2006-04-27 Holland Geoffrey N Medication management system
US7490021B2 (en) 2003-10-07 2009-02-10 Hospira, Inc. Method for adjusting pump screen brightness
US20060100907A1 (en) * 2003-10-07 2006-05-11 Holland Geoffrey N Medication management system
US8065161B2 (en) 2003-11-13 2011-11-22 Hospira, Inc. System for maintaining drug information and communicating with medication delivery devices
US20050278194A1 (en) * 2003-10-07 2005-12-15 Holland Geoffrey N Medication management system
US7895053B2 (en) * 2003-10-07 2011-02-22 Hospira, Inc. Medication management system
US20060089855A1 (en) * 2003-10-07 2006-04-27 Holland Geoffrey N Medication management system
US9123077B2 (en) * 2003-10-07 2015-09-01 Hospira, Inc. Medication management system
US7896572B2 (en) * 2003-10-30 2011-03-01 Hospira, Inc. Medical device system
US7092796B2 (en) * 2003-11-14 2006-08-15 Cardinal Health 303, Inc. System and method for verifying connection of correct fluid supply to an infusion pump
US8020564B2 (en) 2003-12-01 2011-09-20 Carefusion 303, Inc. System and method for analyzing medical treatment data
US8774886B2 (en) 2006-10-04 2014-07-08 Dexcom, Inc. Analyte sensor
AU2004298025B9 (en) * 2003-12-05 2010-12-09 Carefusion 303, Inc. System and method for network monitoring of multiple medical devices
NZ547870A (en) * 2003-12-05 2008-05-30 Cardinal Health 303 Inc Discovery and connection management of medical devices via mobile server
US8571881B2 (en) 2004-11-09 2013-10-29 Spectrum Dynamics, Llc Radiopharmaceutical dispensing, administration, and imaging
US20050277873A1 (en) * 2004-05-27 2005-12-15 Janice Stewart Identification information recognition system for a medical device
US7927313B2 (en) * 2004-05-27 2011-04-19 Baxter International Inc. Medical device configuration based on recognition of identification information
US8961461B2 (en) 2004-05-27 2015-02-24 Baxter International Inc. Multi-state alarm system for a medical pump
US8398592B2 (en) * 2004-09-07 2013-03-19 Thomas Leibner-Druska Medication data transfer system and method for patient infusions
US8900187B2 (en) * 2004-10-13 2014-12-02 Mallinckrodt Llc Powerhead control in a power injection system
US7507221B2 (en) 2004-10-13 2009-03-24 Mallinckrodt Inc. Powerhead of a power injection system
US20060079842A1 (en) * 2004-10-13 2006-04-13 Liebel-Flarsheim Company Powerhead control in a power injection system
NL1029155C2 (en) * 2004-10-19 2006-04-20 Sara Lee De Nv System and method for preparing a drink suitable for consumption.
US8615405B2 (en) 2004-11-09 2013-12-24 Biosensors International Group, Ltd. Imaging system customization using data from radiopharmaceutical-associated data carrier
JP2008520287A (en) * 2004-11-16 2008-06-19 メドラッド インコーポレーテッド System and method for determining patient transfer function for drug infusion and modeling patient response
JP5232473B2 (en) 2004-11-24 2013-07-10 メドラッド インコーポレーテッド System and apparatus for modeling the pressure generated during an injection process
US20060116639A1 (en) * 2004-11-29 2006-06-01 Russell Claudia J Total patient input monitoring
US7775966B2 (en) 2005-02-24 2010-08-17 Ethicon Endo-Surgery, Inc. Non-invasive pressure measurement in a fluid adjustable restrictive device
BRPI0606982A2 (en) * 2005-02-01 2009-07-28 Baxter Int infusion delivery system
US8016744B2 (en) 2005-02-24 2011-09-13 Ethicon Endo-Surgery, Inc. External pressure-based gastric band adjustment system and method
US7699770B2 (en) 2005-02-24 2010-04-20 Ethicon Endo-Surgery, Inc. Device for non-invasive measurement of fluid pressure in an adjustable restriction device
US7775215B2 (en) 2005-02-24 2010-08-17 Ethicon Endo-Surgery, Inc. System and method for determining implanted device positioning and obtaining pressure data
US7927270B2 (en) * 2005-02-24 2011-04-19 Ethicon Endo-Surgery, Inc. External mechanical pressure sensor for gastric band pressure measurements
US7658196B2 (en) 2005-02-24 2010-02-09 Ethicon Endo-Surgery, Inc. System and method for determining implanted device orientation
US8066629B2 (en) 2005-02-24 2011-11-29 Ethicon Endo-Surgery, Inc. Apparatus for adjustment and sensing of gastric band pressure
US20060206356A1 (en) * 2005-03-09 2006-09-14 Vanderveen Timothy W Line verification for multi-pump arrays
DE602006016956D1 (en) * 2005-04-06 2010-10-28 Mallinckrodt Inc Systems and methods for managing information regarding medical fluids and containers therefor
US7945452B2 (en) * 2005-04-11 2011-05-17 Hospira, Inc. User interface improvements for medical devices
WO2007035563A2 (en) * 2005-09-19 2007-03-29 Lifescan, Inc. Malfunction detection via pressure pulsation
US20070066940A1 (en) * 2005-09-19 2007-03-22 Lifescan, Inc. Systems and Methods for Detecting a Partition Position in an Infusion Pump
WO2007035567A2 (en) * 2005-09-19 2007-03-29 Lifescan, Inc. Infusion pump with closed loop control and algorithm
CN200984099Y (en) * 2005-12-21 2007-12-05 皇家飞利浦电子股份有限公司 Cylinder for prepairng beverage, machine for prepairng beverage and system for prepairng beverage
JP4444224B2 (en) * 2006-03-20 2010-03-31 日本電産サーボ株式会社 Infusion device control system
US20080033368A1 (en) * 2006-04-04 2008-02-07 Mallinckrodt Inc. Systems and methods for managing information relating to medical fluids and containers therefor
US20080249806A1 (en) * 2006-04-06 2008-10-09 Ethicon Endo-Surgery, Inc Data Analysis for an Implantable Restriction Device and a Data Logger
US20080250341A1 (en) * 2006-04-06 2008-10-09 Ethicon Endo-Surgery, Inc. Gui With Trend Analysis for an Implantable Restriction Device and a Data Logger
US8870742B2 (en) 2006-04-06 2014-10-28 Ethicon Endo-Surgery, Inc. GUI for an implantable restriction device and a data logger
US8152710B2 (en) * 2006-04-06 2012-04-10 Ethicon Endo-Surgery, Inc. Physiological parameter analysis for an implantable restriction device and a data logger
US10537671B2 (en) 2006-04-14 2020-01-21 Deka Products Limited Partnership Automated control mechanisms in a hemodialysis apparatus
US8894974B2 (en) 2006-05-11 2014-11-25 Spectrum Dynamics Llc Radiopharmaceuticals for diagnosis and therapy
US20070275035A1 (en) * 2006-05-24 2007-11-29 Microchips, Inc. Minimally Invasive Medical Implant Devices for Controlled Drug Delivery
US7601966B2 (en) * 2006-06-28 2009-10-13 Spectrum Dynamics Llc Imaging techniques for reducing blind spots
US20080091466A1 (en) 2006-10-16 2008-04-17 Hospira, Inc. System and method for comparing and utilizing activity information and configuration information from multiple device management systems
US20080154177A1 (en) * 2006-11-21 2008-06-26 Baxter International Inc. System and method for remote monitoring and/or management of infusion therapies
US7654127B2 (en) * 2006-12-21 2010-02-02 Lifescan, Inc. Malfunction detection in infusion pumps
DK2097835T3 (en) 2006-12-29 2018-09-03 Bayer Healthcare Llc PATIENT-BASED PARAMETER GENERATION SYSTEMS FOR MEDICAL INJECTION PROCEDURES
US8491184B2 (en) 2007-02-27 2013-07-23 Deka Products Limited Partnership Sensor apparatus systems, devices and methods
KR101861192B1 (en) 2007-02-27 2018-05-28 데카 프로덕츠 리미티드 파트너쉽 Hemodialysis apparatus and methods
US10463774B2 (en) 2007-02-27 2019-11-05 Deka Products Limited Partnership Control systems and methods for blood or fluid handling medical devices
US8409441B2 (en) 2007-02-27 2013-04-02 Deka Products Limited Partnership Blood treatment systems and methods
JP2008270887A (en) * 2007-04-16 2008-11-06 Murata Mach Ltd Serial communication method
JP5437240B2 (en) 2007-07-17 2014-03-12 メドラッド インコーポレーテッド Apparatus, system and method for determining parameters of cardiopulmonary function evaluation and fluid delivery procedures
US7815605B2 (en) * 2007-11-28 2010-10-19 Souter Steve R Emergency medication pump injection system
JP5695908B2 (en) 2007-12-10 2015-04-08 バイエル メディカル ケア インコーポレーテッド Continuous fluid transport system and fluid transport method
US8187163B2 (en) * 2007-12-10 2012-05-29 Ethicon Endo-Surgery, Inc. Methods for implanting a gastric restriction device
US8100870B2 (en) 2007-12-14 2012-01-24 Ethicon Endo-Surgery, Inc. Adjustable height gastric restriction devices and methods
US8317752B2 (en) * 2007-12-18 2012-11-27 Hospira, Inc. Touch screen system and navigation and programming methods for an infusion pump
US8517990B2 (en) 2007-12-18 2013-08-27 Hospira, Inc. User interface improvements for medical devices
US9044542B2 (en) 2007-12-21 2015-06-02 Carticept Medical, Inc. Imaging-guided anesthesia injection systems and methods
WO2009086182A1 (en) 2007-12-21 2009-07-09 Carticept Medical, Inc. Articular injection system
US8545440B2 (en) * 2007-12-21 2013-10-01 Carticept Medical, Inc. Injection system for delivering multiple fluids within the anatomy
US20090171379A1 (en) * 2007-12-27 2009-07-02 Ethicon Endo-Surgery, Inc. Fluid logic for regulating restriction devices
US8142452B2 (en) * 2007-12-27 2012-03-27 Ethicon Endo-Surgery, Inc. Controlling pressure in adjustable restriction devices
US8377079B2 (en) 2007-12-27 2013-02-19 Ethicon Endo-Surgery, Inc. Constant force mechanisms for regulating restriction devices
US10201647B2 (en) 2008-01-23 2019-02-12 Deka Products Limited Partnership Medical treatment system and methods using a plurality of fluid lines
US10195330B2 (en) 2008-01-23 2019-02-05 Deka Products Limited Partnership Medical treatment system and methods using a plurality of fluid lines
US8337389B2 (en) 2008-01-28 2012-12-25 Ethicon Endo-Surgery, Inc. Methods and devices for diagnosing performance of a gastric restriction system
US8591395B2 (en) 2008-01-28 2013-11-26 Ethicon Endo-Surgery, Inc. Gastric restriction device data handling devices and methods
US8192350B2 (en) 2008-01-28 2012-06-05 Ethicon Endo-Surgery, Inc. Methods and devices for measuring impedance in a gastric restriction system
US20090192534A1 (en) * 2008-01-29 2009-07-30 Ethicon Endo-Surgery, Inc. Sensor trigger
US7844342B2 (en) 2008-02-07 2010-11-30 Ethicon Endo-Surgery, Inc. Powering implantable restriction systems using light
US20090204179A1 (en) * 2008-02-07 2009-08-13 Ethicon Endo-Surgery, Inc. Powering implantable restriction systems using temperature
US8221439B2 (en) * 2008-02-07 2012-07-17 Ethicon Endo-Surgery, Inc. Powering implantable restriction systems using kinetic motion
US8114345B2 (en) * 2008-02-08 2012-02-14 Ethicon Endo-Surgery, Inc. System and method of sterilizing an implantable medical device
US8057492B2 (en) * 2008-02-12 2011-11-15 Ethicon Endo-Surgery, Inc. Automatically adjusting band system with MEMS pump
US8591532B2 (en) 2008-02-12 2013-11-26 Ethicon Endo-Sugery, Inc. Automatically adjusting band system
US8034065B2 (en) * 2008-02-26 2011-10-11 Ethicon Endo-Surgery, Inc. Controlling pressure in adjustable restriction devices
US8608484B2 (en) * 2008-03-04 2013-12-17 Medrad, Inc. Dynamic anthropomorphic cardiovascular phantom
US8233995B2 (en) 2008-03-06 2012-07-31 Ethicon Endo-Surgery, Inc. System and method of aligning an implantable antenna
US20090228063A1 (en) * 2008-03-06 2009-09-10 Ethicon Endo-Surgery, Inc. System and method of communicating with an implantable antenna
US8187162B2 (en) * 2008-03-06 2012-05-29 Ethicon Endo-Surgery, Inc. Reorientation port
US8315449B2 (en) 2008-06-24 2012-11-20 Medrad, Inc. Identification of regions of interest and extraction of time value curves in imaging procedures
US8057679B2 (en) 2008-07-09 2011-11-15 Baxter International Inc. Dialysis system having trending and alert generation
US20100204659A1 (en) * 2008-07-24 2010-08-12 The Regents Of The University Of California Medication delivery system
US20100022953A1 (en) * 2008-07-24 2010-01-28 Walter John Bochenko Medication delivery devices having penetrable sterility barriers and alignment features
US8066672B2 (en) 2008-10-10 2011-11-29 Deka Products Limited Partnership Infusion pump assembly with a backup power supply
US9180245B2 (en) * 2008-10-10 2015-11-10 Deka Products Limited Partnership System and method for administering an infusible fluid
US8262616B2 (en) 2008-10-10 2012-09-11 Deka Products Limited Partnership Infusion pump assembly
US8223028B2 (en) 2008-10-10 2012-07-17 Deka Products Limited Partnership Occlusion detection system and method
US8708376B2 (en) 2008-10-10 2014-04-29 Deka Products Limited Partnership Medium connector
US8554579B2 (en) 2008-10-13 2013-10-08 Fht, Inc. Management, reporting and benchmarking of medication preparation
US8105269B2 (en) * 2008-10-24 2012-01-31 Baxter International Inc. In situ tubing measurements for infusion pumps
US9421330B2 (en) * 2008-11-03 2016-08-23 Bayer Healthcare Llc Mitigation of contrast-induced nephropathy
US8613719B2 (en) * 2008-11-03 2013-12-24 Calibra Medical, Inc. Dosage sensing unit with tactile feedback
US8398584B2 (en) 2009-01-16 2013-03-19 Learning Curve Brands, Inc. Breast pump and method of use
US8137083B2 (en) 2009-03-11 2012-03-20 Baxter International Inc. Infusion pump actuators, system and method for controlling medical fluid flowrate
US8271106B2 (en) 2009-04-17 2012-09-18 Hospira, Inc. System and method for configuring a rule set for medical event management and responses
BR122012017389B8 (en) 2009-07-01 2021-06-22 Fresenius Medical Care Holdings Inc drug delivery device
CN102724946B (en) 2009-07-29 2015-06-10 Icu医学有限公司 Fluid transfer devices and methods of use
US8639525B2 (en) * 2009-10-16 2014-01-28 Codonics, Inc. Drug labeling
US9480791B2 (en) * 2009-12-21 2016-11-01 Bayer Healthcare Llc Pumping devices, systems and methods for use with medical fluids including compensation for variations in pressure or flow rate
US8639363B2 (en) * 2009-12-21 2014-01-28 Blue-White Industries, Ltd. Component control system
US8382447B2 (en) * 2009-12-31 2013-02-26 Baxter International, Inc. Shuttle pump with controlled geometry
US8894631B2 (en) 2010-03-24 2014-11-25 Baxter International Inc. Multiple drug infusion system and method
EP4088762A1 (en) * 2010-03-30 2022-11-16 DEKA Products Limited Partnership Infusion pump methods, systems and apparatus
CA2803169C (en) 2010-06-24 2020-09-22 Medrad, Inc. Modeling of pharmaceutical propagation and parameter generation for injection protocols
US8567235B2 (en) 2010-06-29 2013-10-29 Baxter International Inc. Tube measurement technique using linear actuator and pressure sensor
WO2012040543A1 (en) * 2010-09-24 2012-03-29 Norkunas Matthew W Single operator anesthesia and drug delivery system
WO2012062842A1 (en) * 2010-11-11 2012-05-18 Nestec S.A. Capsule, beverage production machine and system for the preparation of a nutritional product
US8944780B2 (en) 2011-03-25 2015-02-03 Bayer Medical Care Inc. Pumping devices, systems including multiple pistons and methods for use with medical fluids
WO2012106174A1 (en) 2011-01-31 2012-08-09 Fresenius Medical Care Holdings, Inc. Preventing over-delivery of drug
CN106902406B (en) 2011-02-08 2019-11-08 弗雷塞尼斯医疗保健控股公司 Magnetic sensor and related system and method
EP2686037A4 (en) * 2011-03-17 2014-04-02 Sims Micro-infusion system
WO2012142502A2 (en) 2011-04-15 2012-10-18 Dexcom Inc. Advanced analyte sensor calibration and error detection
AU2012299169B2 (en) 2011-08-19 2017-08-24 Icu Medical, Inc. Systems and methods for a graphical interface including a graphical representation of medical data
BR112014006869A2 (en) 2011-09-21 2017-04-04 Bayer Medical Care Inc continuous fluid pump device, drive and actuation system and method
US9594875B2 (en) 2011-10-21 2017-03-14 Hospira, Inc. Medical device update system
US10022498B2 (en) 2011-12-16 2018-07-17 Icu Medical, Inc. System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy
AU2012324021A1 (en) 2011-12-22 2013-07-11 Icu Medical, Inc. Fluid transfer devices and methods of use
US9995611B2 (en) 2012-03-30 2018-06-12 Icu Medical, Inc. Air detection system and method for detecting air in a pump of an infusion system
US9144646B2 (en) 2012-04-25 2015-09-29 Fresenius Medical Care Holdings, Inc. Vial spiking devices and related assemblies and methods
GR20120100242A (en) * 2012-05-04 2014-01-02 Micrel Ιατρικα Μηχανηματα Α.Ε., Analgesia pump/pre-filled bag set
CN104428660A (en) 2012-05-14 2015-03-18 拜耳医疗保健公司 Systems and methods for determination of pharmaceutical fluid injection protocols based on x-ray tube voltage
US9956341B2 (en) 2012-07-03 2018-05-01 Milestone Scientific, Inc. Drug infusion with pressure sensing and non-continuous flow for identification of and injection into fluid-filled anatomic spaces
ES2743160T3 (en) 2012-07-31 2020-02-18 Icu Medical Inc Patient care system for critical medications
CA2883273C (en) 2012-08-31 2023-10-24 Baxter Corporation Englewood Medication requisition fulfillment system and method
CA2889352C (en) 2012-10-26 2021-12-07 Baxter Corporation Englewood Improved work station for medical dose preparation system
KR101974258B1 (en) 2012-10-26 2019-04-30 백스터 코포레이션 잉글우드 Improved image acquisition for medical dose preparation system
US10682460B2 (en) 2013-01-28 2020-06-16 Smiths Medical Asd, Inc. Medication safety devices and methods
US10430554B2 (en) 2013-05-23 2019-10-01 Carefusion 303, Inc. Medication preparation queue
US11182728B2 (en) 2013-01-30 2021-11-23 Carefusion 303, Inc. Medication workflow management
EP2964079B1 (en) 2013-03-06 2022-02-16 ICU Medical, Inc. Medical device communication method
US9555379B2 (en) 2013-03-13 2017-01-31 Bayer Healthcare Llc Fluid path set with turbulent mixing chamber, backflow compensator
WO2014159280A1 (en) 2013-03-13 2014-10-02 Carefusion 303, Inc. Patient-specific medication management system
EP2973370A4 (en) 2013-03-13 2016-08-17 Carefusion 303 Inc Predictive medication safety
US9931463B2 (en) * 2013-03-14 2018-04-03 Carefusion 303, Inc. Infusion channel identifiers
WO2014190264A1 (en) 2013-05-24 2014-11-27 Hospira, Inc. Multi-sensor infusion system for detecting air or an occlusion in the infusion system
AU2014274146B2 (en) 2013-05-29 2019-01-24 Icu Medical, Inc. Infusion system which utilizes one or more sensors and additional information to make an air determination regarding the infusion system
CA2913918C (en) 2013-05-29 2022-02-15 Hospira, Inc. Infusion system and method of use which prevents over-saturation of an analog-to-digital converter
US20150066531A1 (en) 2013-08-30 2015-03-05 James D. Jacobson System and method of monitoring and managing a remote infusion regimen
US9662436B2 (en) 2013-09-20 2017-05-30 Icu Medical, Inc. Fail-safe drug infusion therapy system
US10311972B2 (en) 2013-11-11 2019-06-04 Icu Medical, Inc. Medical device system performance index
US20150133861A1 (en) 2013-11-11 2015-05-14 Kevin P. McLennan Thermal management system and method for medical devices
JP2016537175A (en) 2013-11-19 2016-12-01 ホスピーラ インコーポレイテッド Infusion pump automation system and method
AU2014353184B2 (en) 2013-11-25 2017-08-17 Icu Medical, Inc. Methods and system for filling IV bags with therapeutic fluid
EP3110474B1 (en) 2014-02-28 2019-12-18 ICU Medical, Inc. Infusion system and method which utilizes dual wavelength optical air-in-line detection
US20150257586A1 (en) * 2014-03-11 2015-09-17 Starbucks Corporation Dba Starbucks Coffee Company Single-serve beverage production machine
CA2945647C (en) 2014-04-30 2023-08-08 Hospira, Inc. Patient care system with conditional alarm forwarding
CN106659845A (en) 2014-05-20 2017-05-10 瑟丘尔股份有限公司 Medicine delivery device with restricted access filling port
AU2015266706B2 (en) 2014-05-29 2020-01-30 Icu Medical, Inc. Infusion system and pump with configurable closed loop delivery rate catch-up
US9724470B2 (en) 2014-06-16 2017-08-08 Icu Medical, Inc. System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy
EP3826028A1 (en) 2014-06-30 2021-05-26 Baxter Corporation Englewood Managed medical information exchange
US10143795B2 (en) 2014-08-18 2018-12-04 Icu Medical, Inc. Intravenous pole integrated power, control, and communication system and method for an infusion pump
US9539383B2 (en) 2014-09-15 2017-01-10 Hospira, Inc. System and method that matches delayed infusion auto-programs with manually entered infusion programs and analyzes differences therein
US11575673B2 (en) 2014-09-30 2023-02-07 Baxter Corporation Englewood Central user management in a distributed healthcare information management system
US11107574B2 (en) 2014-09-30 2021-08-31 Baxter Corporation Englewood Management of medication preparation with formulary management
EP3937116A1 (en) 2014-12-05 2022-01-12 Baxter Corporation Englewood Dose preparation data analytics
US11344668B2 (en) 2014-12-19 2022-05-31 Icu Medical, Inc. Infusion system with concurrent TPN/insulin infusion
USD859634S1 (en) * 2015-01-02 2019-09-10 Milestone Scientific Inc. Intra-articular injection device
CA3207200A1 (en) 2015-01-09 2016-07-14 Bayer Healthcare Llc Multiple fluid delivery system with multi-use disposable set and features thereof
US10850024B2 (en) 2015-03-02 2020-12-01 Icu Medical, Inc. Infusion system, device, and method having advanced infusion features
EP3304370B1 (en) 2015-05-26 2020-12-30 ICU Medical, Inc. Infusion pump system and method with multiple drug library editor source capability
AU2016267763B2 (en) 2015-05-26 2021-07-08 Icu Medical, Inc. Disposable infusion fluid delivery device for programmable large volume drug delivery
WO2016207206A1 (en) 2015-06-25 2016-12-29 Gambro Lundia Ab Medical device system and method having a distributed database
US10220180B2 (en) 2015-10-16 2019-03-05 Milestone Scientific, Inc. Method and apparatus for performing a peripheral nerve block
WO2017089317A1 (en) 2015-11-23 2017-06-01 Koninklijke Philips N.V. Pulse oximeter integration for evaluating and updating a drug administration schedule using effectiveness rating
EP3383343A4 (en) * 2015-12-04 2019-07-10 ICU Medical, Inc. Systems methods and components for transferring medical fluids
WO2017152036A1 (en) 2016-03-03 2017-09-08 Bayer Healthcare Llc System and method for improved fluid delivery in multi-fluid injector systems
AU2017264784B2 (en) 2016-05-13 2022-04-21 Icu Medical, Inc. Infusion pump system and method with common line auto flush
EP3468635A4 (en) 2016-06-10 2019-11-20 ICU Medical, Inc. Acoustic flow sensor for continuous medication flow measurements and feedback control of infusion
AU2017295722B2 (en) 2016-07-14 2022-08-11 Icu Medical, Inc. Multi-communication path selection and security system for a medical device
USD851745S1 (en) 2016-07-19 2019-06-18 Icu Medical, Inc. Medical fluid transfer system
EP3487468A4 (en) 2016-07-25 2020-03-25 ICU Medical, Inc. Systems, methods, and components for trapping air bubbles in medical fluid transfer modules and systems
WO2018114346A1 (en) 2016-12-21 2018-06-28 Gambro Lundia Ab Medical device system including information technology infrastructure having secure cluster domain supporting external domain
US10632255B2 (en) 2017-02-15 2020-04-28 Milestone Scientific, Inc. Drug infusion device
US11471595B2 (en) 2017-05-04 2022-10-18 Milestone Scientific, Inc. Method and apparatus for performing a peripheral nerve block
WO2019046299A1 (en) 2017-08-31 2019-03-07 Bayer Healthcare Llc Fluid path impedance assessment for improving fluid delivery performance
AU2018326485B2 (en) 2017-08-31 2024-01-04 Bayer Healthcare Llc Injector pressure calibration system and method
JP7252143B2 (en) 2017-08-31 2023-04-04 バイエル・ヘルスケア・エルエルシー System and method for mechanical calibration of drive member position and fluid injector system
CA3066780A1 (en) 2017-08-31 2019-03-07 Bayer Healthcare Llc Fluid injector system volume compensation system and method
EP3675929A1 (en) 2017-08-31 2020-07-08 Bayer Healthcare LLC Method for dynamic pressure control in a fluid injector system
US10089055B1 (en) 2017-12-27 2018-10-02 Icu Medical, Inc. Synchronized display of screen content on networked devices
US10861592B2 (en) 2018-07-17 2020-12-08 Icu Medical, Inc. Reducing infusion pump network congestion by staggering updates
US11483403B2 (en) 2018-07-17 2022-10-25 Icu Medical, Inc. Maintaining clinical messaging during network instability
WO2020018389A1 (en) 2018-07-17 2020-01-23 Icu Medical, Inc. Systems and methods for facilitating clinical messaging in a network environment
AU2019306490A1 (en) 2018-07-17 2021-02-04 Icu Medical, Inc. Updating infusion pump drug libraries and operational software in a networked environment
CA3107315C (en) 2018-07-26 2023-01-03 Icu Medical, Inc. Drug library management system
US10692595B2 (en) 2018-07-26 2020-06-23 Icu Medical, Inc. Drug library dynamic version management
US10646660B1 (en) 2019-05-16 2020-05-12 Milestone Scientific, Inc. Device and method for identification of a target region
USD939079S1 (en) 2019-08-22 2021-12-21 Icu Medical, Inc. Infusion pump
US11278671B2 (en) 2019-12-04 2022-03-22 Icu Medical, Inc. Infusion pump with safety sequence keypad
US11590057B2 (en) 2020-04-03 2023-02-28 Icu Medical, Inc. Systems, methods, and components for transferring medical fluids
WO2022020184A1 (en) 2020-07-21 2022-01-27 Icu Medical, Inc. Fluid transfer devices and methods of use
US11135360B1 (en) 2020-12-07 2021-10-05 Icu Medical, Inc. Concurrent infusion with common line auto flush
EP4262914A1 (en) * 2020-12-15 2023-10-25 Becton, Dickinson and Company Apparatuses and methods for detecting an empty reservoir in an infusion pump

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4731051A (en) * 1979-04-27 1988-03-15 The Johns Hopkins University Programmable control means for providing safe and controlled medication infusion
US4898578A (en) * 1988-01-26 1990-02-06 Baxter International Inc. Drug infusion system with calculator
US5072660A (en) * 1988-07-12 1991-12-17 Edward Helbling Automatic infusion-beverage apparatus
US5078683A (en) * 1990-05-04 1992-01-07 Block Medical, Inc. Programmable infusion system

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4513796A (en) * 1982-06-24 1985-04-30 Baxter Travenol Laboratories, Inc. High speed bulk compounder
US4553958A (en) * 1983-02-04 1985-11-19 Quest Medical, Inc. IV Delivery controller
US4533347A (en) * 1983-12-19 1985-08-06 Warner-Lambert Company Controller for a dual drug delivery system
US5100380A (en) * 1984-02-08 1992-03-31 Abbott Laboratories Remotely programmable infusion system
US4756706A (en) * 1985-01-23 1988-07-12 American Hospital Supply Corporation Centrally managed modular infusion pump system

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4731051A (en) * 1979-04-27 1988-03-15 The Johns Hopkins University Programmable control means for providing safe and controlled medication infusion
US4898578A (en) * 1988-01-26 1990-02-06 Baxter International Inc. Drug infusion system with calculator
US5072660A (en) * 1988-07-12 1991-12-17 Edward Helbling Automatic infusion-beverage apparatus
US5078683A (en) * 1990-05-04 1992-01-07 Block Medical, Inc. Programmable infusion system

Cited By (38)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6019745A (en) * 1993-05-04 2000-02-01 Zeneca Limited Syringes and syringe pumps
US5882338A (en) * 1993-05-04 1999-03-16 Zeneca Limited Syringes and syringe pumps
US5980501A (en) * 1994-11-02 1999-11-09 Zeneca Limited Reservoirs and delivery devices
US6234997B1 (en) 1995-06-07 2001-05-22 Deka Products Limited Partnership System and method for mixing and delivering intravenous drugs
WO1997021456A1 (en) * 1995-12-12 1997-06-19 The University Of Melbourne Field programmable intravenous infusion system
GB2309801A (en) * 1996-01-31 1997-08-06 Meldet Ltd System for delivery of drugs and therapeutic agents
US5782805A (en) * 1996-04-10 1998-07-21 Meinzer; Randolph Medical infusion pump
WO1997037704A1 (en) * 1996-04-10 1997-10-16 Baxter International Inc. Medical infusion pump
EP0985420A2 (en) * 1996-04-10 2000-03-15 Baxter International Inc. Medical infusion pump
EP0985421A2 (en) * 1996-04-10 2000-03-15 Baxter International Inc. Medical infusion pump
EP0988867A2 (en) * 1996-04-10 2000-03-29 BAXTER INTERNATIONAL INC. (a Delaware corporation) Medical infusion pump
EP0985421A3 (en) * 1996-04-10 2000-04-19 Baxter International Inc. Medical infusion pump
EP0988867A3 (en) * 1996-04-10 2000-04-19 BAXTER INTERNATIONAL INC. (a Delaware corporation) Medical infusion pump
EP0985420A3 (en) * 1996-04-10 2000-04-19 Baxter International Inc. Medical infusion pump
US6210361B1 (en) 1997-08-22 2001-04-03 Deka Products Limited Partnership System for delivering intravenous drugs
US9408966B2 (en) 1997-08-22 2016-08-09 Deka Products Limited Partnership System and method for drug preparation and delivery
US6464667B1 (en) 1997-08-22 2002-10-15 Deka Products Limited Partnership Method and cassette for delivering intravenous drugs
US7214210B2 (en) 1997-08-22 2007-05-08 Deka Products Limited Partnership Cassette and method for drug preparation and delivery
WO1999010029A1 (en) * 1997-08-22 1999-03-04 Deka Products Limited Partnership System and method for intelligent admixture and delivery of medications
US7668731B2 (en) 2002-01-11 2010-02-23 Baxter International Inc. Medication delivery system
US7698156B2 (en) 2002-01-29 2010-04-13 Baxter International Inc. System and method for identifying data streams associated with medical equipment
US10173008B2 (en) 2002-01-29 2019-01-08 Baxter International Inc. System and method for communicating with a dialysis machine through a network
US10556062B2 (en) 2002-01-29 2020-02-11 Baxter International Inc. Electronic medication order transfer and processing methods and apparatus
EP2628496A1 (en) * 2005-03-07 2013-08-21 Mallinckrodt LLC Injector auto purge
US9522238B2 (en) 2005-05-10 2016-12-20 Novo Nordisk A/S Injection device comprising an optical sensor
US8994382B2 (en) 2006-04-12 2015-03-31 Novo Nordisk A/S Absolute position determination of movably mounted member in medication delivery device
US10224117B2 (en) 2008-07-09 2019-03-05 Baxter International Inc. Home therapy machine allowing patient device program selection
US10095840B2 (en) 2008-07-09 2018-10-09 Baxter International Inc. System and method for performing renal therapy at a home or dwelling of a patient
US10061899B2 (en) 2008-07-09 2018-08-28 Baxter International Inc. Home therapy machine
US10068061B2 (en) 2008-07-09 2018-09-04 Baxter International Inc. Home therapy entry, modification, and reporting system
ITFI20080147A1 (en) * 2008-08-01 2010-02-02 Software Centric Srl DRUG ADMINISTRATION SYSTEM
US9950117B2 (en) 2009-02-13 2018-04-24 Novo Nordisk A/S Medical device and cartridge
US10089443B2 (en) 2012-05-15 2018-10-02 Baxter International Inc. Home medical device systems and methods for therapy prescription and tracking, servicing and inventory
CN105555340A (en) * 2013-09-20 2016-05-04 赛诺菲-安万特德国有限公司 Conditional required priming
WO2015040122A1 (en) * 2013-09-20 2015-03-26 Sanofi-Aventis Deutschland Gmbh Conditional required priming
US10294450B2 (en) 2015-10-09 2019-05-21 Deka Products Limited Partnership Fluid pumping and bioreactor system
US10808218B2 (en) 2015-10-09 2020-10-20 Deka Products Limited Partnership Fluid pumping and bioreactor system
US11299705B2 (en) 2016-11-07 2022-04-12 Deka Products Limited Partnership System and method for creating tissue

Also Published As

Publication number Publication date
US5378231A (en) 1995-01-03
AU5606394A (en) 1994-06-22
US5547470A (en) 1996-08-20
CA2150258A1 (en) 1994-06-09

Similar Documents

Publication Publication Date Title
US5378231A (en) Automated drug infusion system
CA1266809A (en) Multiple solution iv system with setup error protection
US5643212A (en) Infusion pump management system for suggesting an adapted course of therapy
EP3440578B1 (en) Control of a drug infusion device
EP1014915B1 (en) Compounding assembly for nutritional fluids
CA1319068C (en) Clinical configuration of multimode medication infusion system
US4850972A (en) Progammable multiple pump medication infusion system with printer
EP0195024B1 (en) Intravenous fluid control system with fluid runaway prevention
JP4898736B2 (en) Medical infusion pump
CA2268176C (en) Safety monitoring apparatus for a patient care system
US5207642A (en) Closed multi-fluid delivery system and method
JP4747100B2 (en) A system to verify the correct fluid source connection to the infusion pump
US4925444A (en) Closed multi-fluid delivery system and method
US5935099A (en) Drug pump systems and methods
EP0497041B1 (en) Automated infusion pump with replaceable memory cartridges
US20020183693A1 (en) Drug pump systems and methods
JPH11502132A (en) Module patient care system
JPH01308568A (en) User interface for multimode drug injection system
EP0503670B1 (en) Peristaltic intravenous infusion pump capable of displaying an application name selected
KR20110055624A (en) Infusion device
JPH05168708A (en) Transfusion injection pump
JP3281955B2 (en) Flexible tubing occlusion sensor
JP2021016795A (en) Infusion pump system

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AU CA JP

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LU MC NL PT SE

DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
121 Ep: the epo has been informed by wipo that ep was designated in this application
WWE Wipo information: entry into national phase

Ref document number: 2150258

Country of ref document: CA

122 Ep: pct application non-entry in european phase