US3698381A - Monitoring system for physiological support systems - Google Patents

Monitoring system for physiological support systems Download PDF

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Publication number
US3698381A
US3698381A US102778A US3698381DA US3698381A US 3698381 A US3698381 A US 3698381A US 102778 A US102778 A US 102778A US 3698381D A US3698381D A US 3698381DA US 3698381 A US3698381 A US 3698381A
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pressure
predetermined
predetermined level
venting
combination
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US102778A
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English (en)
Inventor
Armando Federico
Henry R Guarino
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KONTROL CARDIOVASCULAR Inc
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Avco Corp
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/40—Details relating to driving
    • A61M60/497—Details relating to driving for balloon pumps for circulatory assistance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/515—Regulation using real-time patient data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/10—Location thereof with respect to the patient's body
    • A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
    • A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
    • A61M60/135—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting
    • A61M60/139—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel inside a blood vessel, e.g. using grafting inside the aorta, e.g. intra-aortic balloon pumps
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/295—Balloon pumps for circulatory assistance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/50—Details relating to control
    • A61M60/508—Electronic control means, e.g. for feedback regulation
    • A61M60/538—Regulation using real-time blood pump operational parameter data, e.g. motor current
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/89—Valves
    • A61M60/892—Active valves, i.e. actuated by an external force
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/80—Constructional details other than related to driving
    • A61M60/855—Constructional details other than related to driving of implantable pumps or pumping devices
    • A61M60/89—Valves
    • A61M60/894—Passive valves, i.e. valves actuated by the blood
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3303—Using a biosensor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES 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
    • A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
    • A61M60/20—Type thereof
    • A61M60/247—Positive displacement blood pumps
    • A61M60/253—Positive displacement blood pumps including a displacement member directly acting on the blood
    • A61M60/268—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders
    • A61M60/274—Positive displacement blood pumps including a displacement member directly acting on the blood the displacement member being flexible, e.g. membranes, diaphragms or bladders the inlet and outlet being the same, e.g. para-aortic counter-pulsation blood pumps

Definitions

  • ABSTRACT A system for automatically monitoring and controlling the fluid load in physiological support systems. The system samples gas pressure at fixed periods and adds fluid or vents fluid from the system to prevent malfunction and the catastrophic results.
  • This type of support system pressure is exerted upon and transmitted across a membrane in contact with the blood, Blood is displaced with the creation of controlled pressure changes which tend to reduce cardiac effort and pump blood systemically.
  • the membrane which separates'the driving gas or liquid from the blood in these devices is subjected to repeated bending stresses and requires superior mechanical properties.
  • the second general category of devices are diffusion system Examples of these are the membrane oxygenator type of artificial lung and the hemodialysis typeof artificial hiding. In these types of devices the membrane serves to separate the blood from the diffusion gas or liquid and is permeable to the substances which are exchanged from fluid to flood or vice versa, versa, The separating membrane must be generally quite thin in relation to its surface area.
  • One type of heart pump the intra-arterial balloon pump and more particularly the intra-aortic balloon pump, consists of a balloon attached to a catheter, which is introduced into the patients femoral artery and positioned in the descending aorta to provide benign cardiac assistance to the patient.
  • a constant amount of load gas isrequired in the system at all times to insure proper inflation and deflation of the balloon which is controlled by a volumeter that increases and decreases the pressure on the load gas.
  • gas may leak from the system. Excessive amounts of gas leaking into the patients blood system must be stopped to protect the patient. Also, excessive leaks from the gas system outside the patients body, which indicate a substantial failure in the system must be stopped.
  • the surveillance system be fail-safe so that the balloon pump in the patients body imposes the least restriction to blood flow upon failure.
  • the gas pressure load in an intra-arterial or intra-aortic pump is measured during quiescent periods between pump impulses and the load system is filled or vented slowly if pressure is within a safe region to maintain ideal pressure load. If pressure is outside the safe region, the system is rapidly vented to collapse the balloon so that it will provide minimal resistance to blood flow.
  • the surveillance system also vents to collapse the balloon if filling to maintain the desired pressure occurs too frequently or if it takes too long to fill to maintain normal operating pressure. Either of these indicates there is excessive leakage somewhere in the load system.
  • FIG. 1 is a block diagram and schematic showing the pneumatic gas load system, the intra-aortic pump and the electronic control and surveillance system which responds to, for example, electrocardiograph equipment monitoring the patient;
  • FIG. 2 is a block diagram showing the circuits in the rapid vent and refill logic of the surveillance system.
  • FIG. 3 shows waveforms in the surveillance system, including a waveform representative of system load pressure and various levels identified with safe and unsafe operation.
  • FIG. I there is shown a block diagram and schematic of a pneumatic system and an electronic control and surveillance system, which function together to control an intra-aortic balloon 1, attached to a catheter 2, which is introduced into the patients femoral artery and positioned in the descending aorta to provide a benign cardiac assist to the patient.
  • the pneumatic system consists principally of two separate pneumatic systems separated by the membrane 3 in isolating piston 4. It is through the isolating piston, and most particularly the membrane 3 in the isolating piston that pressure pulses are delivered from the initiating pneumatic system 6 to the pump load pneumatic system 7.
  • the gases in the systems 6 and 7 may be different because the requirements of the systems are different.
  • the pump load system which extends into the body of the patient through the intra-aortic balloon 1 preferably contains helium which dissolves easily in the blood without injurious effect on the patient.
  • gases which are not substantially injurious are carbon dioxide and oxygen and while these gases are heavier they may also be used because there is a tolerance by the patient to dissolve these gases in the blood.
  • Nitrogen on the other hand, could cause damage or injury to the patient, because of the low toleration for nitrogen in the blood.
  • the initiating pneumatic system 6 that drives the isolating piston 4; and second, in the pump load system 7 it responds to thepressure of the load gas in the intra-aortic balloon and by providing a signal to the pneumatics which maintains that pressure within predetermined limits, refills the system where a leakage not excessively harmful to the patient has occurred or vents the system shutting it down where the leakage has been excessive or where pressure is beyond prescribed pressure limits, indicating a serious malfunction in the system.
  • the system shuts down by venting so as to collapse the intra-aortic balloon.
  • the balloon is collapsed so that it is least obstructive to blood flow in the aorta.
  • the intra-aortic balloon pump must be synchronized with the patients heartbeat. More particularly, the balloon must be pulsed or inflated with pressure during the diastolic phase of the heart cycle. During this phase, as already described, the left ventricle of the heart which feeds the aorta is in dilation, the aortic valve is closed and the aorta is normally distended. At this point, the balloon is inflated and so it aids the aorta to force the blood through the capillaries and other vessels of the patientss body. A representation of the pressure pulses to the balloon is shown by the waveform in FIG. 3 designated System Pressure.
  • the duration I of a pulse in this waveform represents the pumping interval and the point S between pulses indicates a sample point when the pressure to the balloon is sampled and examined by the surveillance system, to determine whether it is within prescribed limits or a dangerous malfunction threatens.
  • the point S in the pumping cycle represents the quiescent or zero pressure, which loads the pump between pumping intervals.
  • the pumping interval is approximately two-thirds of the whole cycle when the patientss pulse rate is 77 beats per second. This interval may be reduced to about one-half the pump full cycle when the patients pulse rate is between and beats per second.
  • An electrical system which responds to the output of an electrocardiograph (EKG) unit monitoring the patients heartbeat provides an electrical drive signal for controlling the pneumatic system 6 that initiates a pressure pulse to the balloon and also triggers a sampling pulse for sampling balloon pressure.
  • This system is designated the heart-pump sync system 10 and produces a drive pulse which is positioned in the heart diastole phase, depending on the patients pulse rate.
  • a suitable heart-pump sync system of this sort is described in U.S. Pat. No.
  • the signal output of the EKG is represented by the waveform denoted EKG input, shown in FIG. 3, and the drive .signal output from the heart-pump sync system 10 is represented by the waveform designated Drive Signal in FIG. 3.
  • the drive signal is amplified by amplifier 11 and energizes the solenoid valve 12 in the pneumatic system 6.
  • This valve connects the isolating piston 4 to a pressure source 13 or a vacuum source 14 and so distends the diaphragm 3 in the isolating piston to deliver pressure pulses to the pump load in the pneumatic system 7.
  • the pressure pulses are transmitted from the piston 4 to the intra-aortic balloon pump 1 via the catheter 2.
  • Pressure to the pump is monitored by a pressure transducer 15 in contact with the catheter.
  • the electrical signal from the transducer is amplified by amplifier 16 and fed to the electronic surveillance system, denoted generally by the numeral 17.
  • This signal, the system pressure signal is shown by the waveform in FIG. 3, designated System Pressure.
  • the system pressure signal is sampled during the interval of Sampling Gate pulses, also shown in FIG. 3. These pulses are generated by a monostable multivibrator 18, in response to the Drive Signal pulses from theheart-pump sync system 10.
  • the pneumatic system 7 is initially filled with load gas through valve 21 from a tank of helium gas 22, through a pressure regulator 23.
  • the load gas reservoir 24 in the isolating piston 4 is filled to a maximum gauge pressure of 15 mm, as set by the gas load regulator 23.
  • This amount of initial load gas in the reservoir is variable depending on the size of the balloon used, type of load gas, and the length of the catheter.
  • the balloon is not pumping, it is deflated and the pressure in the catheter is established at safe operating limits for the system, which are by way of example between +7 and -5 mm of pressure for helium.
  • the surveillance system 17 samples the pressure between pump pulses and commands corrective action.
  • the refill valve 27 is opened continuously for more than seconds, it is assumed there is a leak present in the system and so the refill valve 27 is shut and.the rapid vent valve 27 is opened, shutting down the system just as when an over pressure exceeding mm occurs.
  • the refill load valve 27 is open for less than 10 seconds, and the system is restored to the high normal operating pressure of 5 mm. The system is allowed to continue pumping. When the system pressure drops ---20 mm or less, rapid vent is also opened as this indicates that a failure has occurred and the patient is in danger.
  • signal compare circuits 31 to 35 which may be commercially available voltagev comparators, compare the voltage of the pressure signal from amplifier 16 with preset voltages representing the pressure limits designated and when the pressure signal exceeds, or is less than, the designated limit called for by the compare circuit, the circuit produces an output signal. More particularly, circuit 31 produces an output signal when the pressure signal exceeds a reference representing +7 mm pressure. Circuit 32 produces an output when the pressure signal exceeds a reference representing +20 mm of pressure. Circuit 33 produces an output when a reference signal representing 20 mm exceeds the pressure signal. Circuit 34 produces an output when the pressure signal exceeds the reference signal representing 5mm of pressure and circuit 35 produces an output when a reference signal representing 5 mm exceeds the pressure signal.
  • circuits 31 to 35 are gated by gates 36 to 40 and the gates are controlled by Sampling Gate pulses shown in FIG. 3 generated by multivibrator 18.
  • the outputs of the gates are binary signals representing the occurrence of the events indicated during the sample gate intervals, which fall between the system pressure pulses as shown by waveforms in FIG.
  • the output of gate 36 is a negative voltage pulse representing the occurrence of the condition determined by circuit 31.
  • the negative pulse occurs if the condition occurs, such as, for example, a pressure exceeding a reference pressure of +7 mm.
  • the negative pulse initiates a slow vent control signal from pulse shaper 41 amplified by slow vent amplifier circuit 48, which controls the vent valve 26.
  • This slow vent control signal is terminated when the output of gate 36 is a positive level when the system is below +7 mm and is determined by AND circuit 42.
  • the'slow vent valve 26 vents the system continually following initiation and until the system pressure is decreased below +7 mm and a sampling gate pulse disappears.
  • gates 37 and 38 represent the occurrence of an extreme condition, for example, a pressure over or under +20 mm requiring rapid venting of the system and so these gates trigger flipfiop circuits 44 and 45, which feed through OR gate 46 to amplifier 47 that energizes rapid vent valve 25. This shuts down the system as danger points have been exceeded. Thereafter, when the defects are corrected, flipflop 44 and 45 are reset and ready again to initiate rapid vent in case pressure exceeds the extreme limits.
  • the outputs from gates 39 and 40 trigger rapid vent and refill logic circuits 50. These circuits feed signals through OR circuit 46 to the rapid vent amplifier 47 to cause rapid venting of the system in accordance with the logic already described and also perform the logic to determine whether the system will be refilled. If refill is called for, then a signal from circuits 50 is amplified by refill amplifier 51 which energizes refill load valve 27.
  • the logic circuits in 50 are shown in FIG. 2, which is a simple block diagram of logic elements. This consists of a 1 minute timer52 which responds to the output of gate 39 producing a pulse of 1 minute interval, when the pulse output from gate 39 is positive indicating a high normal pressure of +5 mm. Similarly, the output from gate 40 initiates a pulse at a low normal pressure of 5 mm.
  • the logic in circuits 54 which includes an AND circuit and an AND circuit 56 questions first whether the lower pressure limit 5 mm, which requires refilling, has been reached and then asks whether one minute has elapsed since the pressure was last above +5 mm. If the answer to both of these is no, it means the system is losing pressure too rapidly and so there is a serious leak and the system must be shut down.
  • AND circuit 55 is fed through the OR circuit 46 to energize the rapid vent valve 25 that initiates shutdown of the system.
  • the output of AND circuit 56 generates a fill signal to the flipflop 59.
  • the output of the flipflop 59 and a 10 second delay pulse from timer 53 are combined by AND circuit 57.
  • the logic here asks the further question in response to a yes answer from circuit 54 Is the system still filling after 10 seconds? If the answer to this is yes, then the indication is that the system has not been restored to an operating condition and it must be shut down.
  • timers mentioned above may be eliminated along with the high normal comparator (+5 mm) circuit if it is desired to use an analog refill system and/or it is desired to eliminate the 1 minute and seconds timing functions along with the high normal pressure functions as described hereinabove.
  • Such a circuit is activated whenever the pressure drops to the low normal level of 5 mm pressure. This will automatically activate the refill load valve.
  • the rate of refilling is made at least substantially equal to the rate at which the human body may safely absorb the load gas utilized. If this rate of refill is inadequate to maintain the normal operating pressure and the system drops below the safe limit of mm pressure, the
  • the system will rapidly vent and shut down as previously described. Further, if the refill rate is sufficient to bring the system to within the safe operation range, the patient will not be endangered because the rate of adding the gas can be safely absorbed by the human body. If the fill rate increases the pressure to the upper limit of the system, a feedback loop or the like shuts down the fill function at the desired high normal pressure of, for example,+5 mm.
  • a circulatory assist system which sequentially actuates a blood pump by controlling fluid load pressure to the pump, the combination comprising:
  • sensing means for sensing pump fluid load pressure
  • said first means includes a slow fill valve whose rate is not substantially in excess of in vivo blood to absorb the fluid utilized.
  • a circulatory assist system comprising:
  • a plurality of means responsive to said sensing means including, first means for controlling said venting means within a predetermined load pressure range, second means for controlling said pressure increase means within said same predetermined load pressure range, and third means for controlling said pressure venting means above and below said predetermined load pressure range.
  • venting means includes a relatively slow vent and a relatively fast vent, the latter serving to vent above and below the predetermined load pressure range.
  • a system as defined in claim 13 further including fourth means coupling the first and second controlling means to said low pressure venting and to said increasing means, thereby causing pressure to vent when the pressure falls below said predetermined range within a first predetermined interval.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Cardiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Mechanical Engineering (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
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US102778A 1970-12-30 1970-12-30 Monitoring system for physiological support systems Expired - Lifetime US3698381A (en)

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CA (1) CA973767A (it)
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FR (1) FR2121096A5 (it)
GB (1) GB1384394A (it)
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US4522194A (en) * 1983-02-18 1985-06-11 Baylor College Of Medicine Method and an apparatus for intra-aortic balloon monitoring and leak detection
US4648385A (en) * 1983-11-14 1987-03-10 Aisin Seiki Kabushiki Kaisha Apparatus for driving a medical appliance
US4794910A (en) * 1986-06-28 1989-01-03 Aisin Seiki Kabushiki Kaisha Medical appliance driving apparatus
US4832005A (en) * 1986-03-26 1989-05-23 Aisin Seiki Kabushiki Kaisha Medical appliance driving apparatus
US4974774A (en) * 1986-03-26 1990-12-04 Aisin Seiki Kabushiki Kaisha Medical appliance driving apparatus
US5009662A (en) * 1988-08-10 1991-04-23 Wallace William D Medical pressure sensing and display system
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US5201753A (en) * 1989-03-17 1993-04-13 Merit Medical Systems, Inc. Totally self-contained, digitally controlled, disposable syringe inflation system, and method for monitoring, displaying and recording balloon catheter inflation data
US5242374A (en) * 1991-03-29 1993-09-07 Aisin Seiki Kabushiki Kaisha Leak detector for an intra-aortic balloon pump
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US5368565A (en) * 1992-09-28 1994-11-29 Medex, Inc. Balloon catheter pressure monitor for local and remote display
US5383855A (en) * 1992-08-20 1995-01-24 Medex, Inc. Electronically monitored angioplasty system
US5425713A (en) * 1989-03-17 1995-06-20 Merit Medical Systems, Inc. System and method for monitoring, displaying and recording balloon catheter condition interval and inflation location data
US5429606A (en) * 1988-03-08 1995-07-04 Scimed Life Systems, Inc. Balloon catheter inflation device
US5431629A (en) * 1989-03-17 1995-07-11 Merit Medical Systems, Inc. System and method for monitoring, displaying and recording balloon catheter condition interval data
US5449345A (en) * 1989-03-17 1995-09-12 Merit Medical Systems, Inc. Detachable and reusable digital control unit for monitoring balloon catheter data in a syringe inflation system
US5449344A (en) * 1992-06-18 1995-09-12 Merit Medical Systems, Inc. Syringe apparatus with pressure gauge and detachable timer
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US5459700A (en) * 1993-11-22 1995-10-17 Advanced Cardiovascular Systems, Inc. Manual timer control for inflation device
US5458571A (en) * 1989-03-17 1995-10-17 Merit Medical Systems, Inc. System and method for monitoring, displaying and recording balloon catheter condition interval data
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US5472424A (en) * 1994-04-05 1995-12-05 Merit Medical Systems, Inc. Syringe with volume displacement apparatus
US5562614A (en) * 1993-11-22 1996-10-08 Advanced Cardiovascular Systems, Inc. Programmable manifold system for automatic fluid delivery
US5562621A (en) * 1993-11-22 1996-10-08 Advanced Cardiovascular Systems, Inc. Communication system for linking a medical device with a remote console
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US6050932A (en) * 1996-02-21 2000-04-18 Synthelabo Biomedical ( Societe Anonyme) Control circuit for an implantable heart-assist pump of the back-pressure balloon type
US6082105A (en) * 1995-11-21 2000-07-04 Nippon Zeon Co., Ltd. Drive device for medical appliances
US6536260B2 (en) * 1999-06-24 2003-03-25 Datascope Investment Corp. Balloon catheter leak detection method and apparatus
US20060153718A1 (en) * 2002-12-20 2006-07-13 Gibson David J M Peristaltic pump head and tube holder
US20060276744A1 (en) * 2005-05-20 2006-12-07 Falk Theodore J Configuration for drug delivery systems
US8540618B2 (en) 2003-01-31 2013-09-24 L-Vad Technology, Inc. Stable aortic blood pump implant
WO2016185377A1 (en) * 2015-05-20 2016-11-24 Thd S.P.A. A circuit for feeding a fluid to an inflatable chamber
US20160367306A1 (en) * 2005-03-07 2016-12-22 Medtronic Cryocath Lp Fluid control system for a medical device
US9694122B2 (en) * 2003-01-31 2017-07-04 L-Vad Technology, Inc. Rigid body aortic blood pump implant
US20180319417A1 (en) * 2011-05-13 2018-11-08 Maquet Cardiovascular Llc Portable and modular transportation unit with improved transport capabilities

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Also Published As

Publication number Publication date
IL38422A (en) 1975-03-13
GB1384394A (en) 1975-02-19
FR2121096A5 (it) 1972-08-18
JPS5330276B1 (it) 1978-08-25
CA973767A (en) 1975-09-02
IT951686B (it) 1973-07-10
SE377046B (it) 1975-06-23
NL7118076A (it) 1972-07-04
DE2165648B2 (de) 1972-10-05
IL38422A0 (en) 1972-02-29
CH555184A (fr) 1974-10-31
NL165379C (nl) 1981-04-15
DE2165648A1 (it) 1972-10-05

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