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WO1998044969A1 - Systeme de transmission pour regler la compression cardiaque - Google Patents

Systeme de transmission pour regler la compression cardiaque Download PDF

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Publication number
WO1998044969A1
WO1998044969A1 PCT/US1998/006353 US9806353W WO9844969A1 WO 1998044969 A1 WO1998044969 A1 WO 1998044969A1 US 9806353 W US9806353 W US 9806353W WO 9844969 A1 WO9844969 A1 WO 9844969A1
Authority
WO
WIPO (PCT)
Prior art keywords
pressure
inflation system
reservoir
chamber
tank
Prior art date
Legal status (The legal status 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 status listed.)
Ceased
Application number
PCT/US1998/006353
Other languages
English (en)
Inventor
Joshua E. Tsitlik
Howard R. Levin
Naum S. Ziselson
Paul C. Michelman
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Cardio Technologies Inc
Original Assignee
Cardio Technologies Inc
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
Application filed by Cardio Technologies Inc filed Critical Cardio Technologies Inc
Priority to EP98915200A priority Critical patent/EP1021217A4/fr
Priority to BR9807926-3A priority patent/BR9807926A/pt
Priority to CA002285231A priority patent/CA2285231A1/fr
Priority to AU69442/98A priority patent/AU6944298A/en
Priority to JP54286698A priority patent/JP2001519865A/ja
Publication of WO1998044969A1 publication Critical patent/WO1998044969A1/fr
Priority to NO994826A priority patent/NO994826D0/no
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Classifications

    • 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
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
    • A61M60/43—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic using vacuum at the blood pump, e.g. to accelerate filling
    • 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
    • A61M60/161—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 mechanically acting upon the outside of the patient's blood vessel structure, e.g. compressive structures placed around a vessel
    • 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
    • A61M60/289—Devices for mechanical circulatory actuation assisting the residual heart function by means mechanically acting upon the patient's native heart or blood vessel structure, e.g. direct cardiac compression [DCC] devices
    • 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
    • A61M60/465—Details relating to driving for devices for mechanical circulatory actuation
    • A61M60/468—Details relating to driving for devices for mechanical circulatory actuation the force acting on the actuation means being hydraulic or pneumatic
    • 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
    • A61M60/424—Details relating to driving for positive displacement blood pumps
    • A61M60/427—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
    • A61M60/435—Details relating to driving for positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic with diastole or systole switching by valve means located between the blood pump and the hydraulic or pneumatic energy source

Definitions

  • the present invention relates to systems for mechanically assisting the heart and more particularly to a drive system capable of controlling the rise time and plateau level of a pressure pulse applied to a cardiac compression apparatus.
  • Heart disease accounts for one of the leading causes of cardiac dysfunction among individuals worldwide.
  • One of the more common heart disorders often associated with heart disease involves substantial weakening of the heart. Left unaided, a critically weakened heart often cannot pump the necessary blood required to sustain bodily functions.
  • An important life-saving technique for individuals diagnosed with weakened hearts includes mechanically assisting the heart to pump blood. Such support ensures an adequate blood pressure for sufficiently supplying blood throughout the body without undue stress on the heart muscle.
  • a device such as a heart compression apparatus carries out the assistance during invasive surgery.
  • An alternative device incorporating cardiopulmonary resuscitation (CPR) techniques externally compresses the chest to rhythmically squeeze the heart area and assist in increasing blood flow.
  • CPR cardiopulmonary resuscitation
  • Patent Application Serial Number 60/028,722 filed on October 18, 1996 and assigned to the assignee of the present invention, carries and supports the heart during invasive surgery while uniformly applying pressure directly to the heart through means of an inflatable liner.
  • the liner is cyclically inflated and deflated by an inflation system to apply pressure to the heart.
  • One conventional inflation system for controlling the rise time and plateau level of a pressure pulse utilizes a single regulator-reservoir configuration.
  • the system includes a compressor connected to a regulator, and a reservoir disposed downstream of the regulator.
  • An outflow valve connects to the reservoir outlet and is placed in fluid communication with an inflation chamber disposed in a cardiac compression apparatus for supporting and assisting a heart.
  • the compressor supplies flow through the regulator, which maintains a desired pressure in the tank. Inflation of the chamber occurs by opening the outflow valve to produce an exponentially increasing pressure transient within the chamber that asymptotically approaches the supply pressure level to define a relatively constant pressure, or plateau level, within a known response time.
  • the configuration provides a relatively accurate adjustment of the plateau level without any independent control over changes in the rise time of the start transient.
  • the waveforms may be expressed as: wherein t represents time, and T represents the system time constant. As illustrated in Fig. 3, regardless of the plateau setting, the time constant T remains unchanged with changes only in the magnitude of the plateau level. Because of this characteristic, control of the rise time using the conventional inflation system is generally possible only by affecting the system resistances, capacitances, or source regulator pressure. As a result, the response of the transient to reach the plateau level is typically of the order of three time constants.
  • the rise time known commonly as the time required to reach the plateau level, generally depends upon system characteristics such as overall resistance and capacitance. Therefore, having the capability of merely controlling the plateau level does not enable independent control over the rise time.
  • the conventional inflation system is often disposed several feet from the inflation chamber.
  • a relatively long hose generally couples the inflation system to the compression apparatus liner. Coupled with the effects of overall system resistances and pressure load, the resulting time constant realized by the conventional inflation system substantially degrades system performance.
  • the resistance be lowered through expansion of the tubing diameter, the size, weight and cost for the components required to effect a larger flowrate would render the system undesirable from a practical standpoint.
  • a second proposal solves several of the aforementioned problems by implementing a source pressure substantially higher than the desired plateau pressure.
  • the pressure circuit is similar to the first proposal described above, but includes an additional control valve disposed in series with the outflow valve. Operation of the system depends upon precise timing to initially open both valves simultaneously, exposing the liner to an exponentially increasing pressure characteristic of the source pressure level, then closing the control valve upon reaching a desired plateau pressure and trapping the pressure within the liner for a timed duration.
  • the inflation system of the present invention provides a straightforward means of inflating a cardiac compression apparatus according to a predefined pressure profile and having an independently controllable rise time and plateau level. Additionally, the system incorporates a minimum number of components to minimize size and associated procurement and operating costs.
  • the inflation system of the present invention independently controls the rise time and plateau level of a pressure cycle profile applied to an inflatable chamber.
  • the invention includes a pneumatic source for pressurizing fluid at a predetermined pressure and a pressure path disposed in fluid communication with the source.
  • the pressure path includes a regulation device for establishing respective high and low pressure levels.
  • a supply mechanism disposed at the output of the pressure path is operative to alternately expose the chamber to the high and low pressure levels according to predetermined switchable durations to define the rise time and plateau levels.
  • the present invention comprises a heart assistance system for supporting and assisting the cyclic pumping of a heart.
  • the heart assistance system includes a cardiac compression apparatus having a support cup and an internal inflation chamber for uniformly compressing the heart.
  • An inflation system applies a pressure pulse to the inflation chamber and places the heart in cyclic compression by independently controlling the rise time and the plateau level of the pressure pulse.
  • the inflation system includes a pneumatic source for pressurizing fluid at a predetermined pressure and a pressure path disposed in fluid communication with the source.
  • the pressure path includes a regulation device for establishing respective high and low pressure levels.
  • a supply mechanism disposed at the output of the pressure path is operative to alternately expose the chamber to the high and low pressure levels according to predetermined switchable durations to define the rise time and plateau levels.
  • the invention comprises a method of independently controlling the rise time and the plateau level of a pressure cycle applied to an inflatable chamber.
  • the method includes the steps of exposing the chamber to a first pressure from a pressure reservoir to exponentially increase the pressure within the chamber for a controllable duration defining the rise time; and switching the pressure in the reservoir following expiration of the duration to a constant second pressure defining the plateau level.
  • the present invention includes a source pressure substantially higher than the desired plateau pressure.
  • the pressure circuit includes two outlet lines from the tank. One outlet line has a switching valve that switches between a first regulated high pressure line and a second regulated plateau pressure line.
  • the second output line is connected to the compression apparatus liner through a supply valve. Operation of the system depends upon precise timing of the switching valve to, first, expose the liner to the high pressure level which is greater than the plateau pressure level, then switching the valve upon reaching a desired predetermined percentage of the plateau pressure, thereby fluidly connecting the liner to the plateau pressure.
  • the supply valve is then switched to close (to vent the liner to atmosphere) at the end of the systolic cycle.
  • FIG. 1 is a cross-sectional view of a non-limiting example of a cardiac assistance apparatus aiding a heart to illustrate an important application for the inflation system of the present invention
  • FIGS. 2 A and 2B are block diagrams of a conventional inflation system
  • FIGS. 3 A and 3B are timing diagrams for the conventional inflation system of Figs. 2 A and 2B, respectively;
  • FIG. 4 is a graphical representation of an undesirable response for the conventional inflation system of Fig. 2B;
  • FIG. 5 is a block diagram of an inflation system according to a first embodiment of the present invention
  • FIG. 6 is a timing diagram for the inflation system of Fig. 5 illustrated with respect to a portion of a pressure profile
  • FIG. 7 is a block diagram of an inflation system according to a second embodiment of the present invention.
  • FIG. 8. is a timing diagram for the inflation system of Fig. 7 illustrated with respect to a portion of a pressure profile
  • FIG. 9 is a block diagram of an inflation system according to a third embodiment of the present invention.
  • FIG. 10 is a timing diagram for the inflation system of Fig. 9 illustrated with respect to a portion of a pressure profile
  • FIG. 11 is a block diagram of an inflation system according to a fourth embodiment of the present invention.
  • FIG. 12 is a timing diagram for the inflation system of Fig. 1 1 illustrated with respect to a portion of a pressure profile.
  • the inflation system of the present invention independently controls the rise time and plateau level of a pressure profile by switching between first and second pressure levels with a minimum number of components.
  • the control of the rise time and plateau level is important to provide a satisfactory response time to properly match the pressure pulses of a mechanical heart assistance system with the natural pulses of the pumping heart.
  • Figure 1 illustrates a cardiac compression apparatus 12 for assisting a heart 13 to pump blood through a vasculature by substantially uniformly compressing the heart ventricle during the systolic phase.
  • An example of such an apparatus is disclosed in pending U.S. Patent Application Serial No. 60/028,722, filed on October 18, 1996, the disclosure of which is hereby incorporated by reference.
  • the heart is placed into the apparatus which is lined with an internal inflation chamber or liner 16 that includes a port 18 for connecting to an inflation system according to the present invention.
  • a first conventional inflation system for generating a pressure profile in synchronous relation with the pumping heart 13, and generally designated 34 includes a pneumatic compressor 36 having an output coupled to a regulator 38, and a reservoir or tank 40 disposed downstream of the regulator.
  • a first control valve 43 connects to the reservoir outlet.
  • Control valve 43 is a two-way valve and has its output directed to the inflation chamber disposed in the cardiac compression apparatus 12 of the type shown in Fig. 1.
  • a controller (not shown) controls the actuation of control valve 43 according to relatively precise timing such as that illustrated in Fig. 3 A.
  • the compressor supplies flow through the regulator, which maintains a desired pressure in the tank.
  • Inflation of the liner 16 occurs by opening the first control valve 43 to produce an asymptotically increasing pressure transient within the chamber.
  • the source pressure maintained within tank 40 is the desired plateau pressure.
  • control valve 43 is switched so that inflatable chamber port 19 of apparatus 12 is now in fluid communication with reservoir 44. Chamber 44 is simply a vent to atmosphere.
  • a second conventional inflation system for generating a pressure profile in synchronous relation with the pumping heart 13, and generally designated 34 includes a pneumatic compressor 36 having an output coupled to a regulator 38, and a reservoir or tank 40 disposed downstream of the regulator.
  • a first control valve 42 connects to the reservoir outlet.
  • a three-way two position distribution valve 43 is placed in downstream fluid communication with the first control valve and has its output directed to the inflation chamber disposed in the cardiac compression apparatus 12 of the type shown in Fig. 1.
  • a controller (not shown) controls actuation of the control valves
  • the compressor supplies flow through the regulator, which maintains a desired pressure in the tank.
  • Inflation of the liner 16 occurs by simultaneously opening both the first control valve 42 and the distribution valve 43 to produce an asymptotically increasing pressure transient within the chamber.
  • the control valve 42 is closed while the pressure circuit traps the pressurized gas in the liner.
  • the distribution valve is actuated to vent the liner to atmosphere.
  • Fig. 4 illustrates the effect of a slight inaccuracy of the aforedescribed timing resulting in an undesirable overshoot of the desired plateau level . Such effects are often undesirable in cardiac compression applications due to higher pressure applied to the heart than are desired and, additionally, unexpected stresses placed upon the inflatable liner 16.
  • the inflation system according to a first embodiment of the present invention and generally designated 50, provides the capability of independently controlling the rise time and plateau level of an applied pressure pulse.
  • the system includes a pair of pressure paths 52 and 54 disposed in parallel fluid communication with a pneumatic source 56.
  • the pneumatic source 56 typically comprises a controllable compressor or pump capable of producing pressurized gas at pressures between the range of 6 psi to 60 psi (300 to 3000 mmHg).
  • An additional source suitable for this application includes a pressurized pneumatic cylinder with appropriate plumbing to step down the bottled pressure or pressure from gas distribution lines frequently supplied in hospitals to a controllable level.
  • the pressure paths 52 and 54 include respective regulators 58 and 60 disposed downstream of the pressure source 56 and connected to respective tanks or reservoirs 62 and 64.
  • the regulators are configured to maintain respective high and low pressure levels within the tanks.
  • the high pressure level is typically set within the range of approximately 150 to 300 mmHg while the low range often approximates 60 to 150 mmHg.
  • Respective control valves 66 and 68 together comprise a supply mechanism and are disposed at the tank outlets 70 and 72 and plumbed into a common supply manifold 74.
  • the manifold connects to the a venting mechanism 73.
  • Venting mechanism 73 is preferably a 3-way valve with manifold 74 and the conduit from tank 75 being the inputs and the conduit lending to the inflatable chamber port 18 (Fig. 1) being the output.
  • Tank 75 may be open to a atmosphere or to a negative pressure (i.e. , a vacuum).
  • venting mechanism 73 preferably defaults to being in communication with the inlet conduit from tank 75.
  • a controller 76 electrically connects to the solenoids of the respective control valves 66 and 68 to sequence the valve states according to a predetermined timing scheme illustrated in Figure 6. Operation of the inflation system 50 involves activating a control signal 77 (Fig. 6) to open the high pressure supply control valve 66 and opening the valve 73 to manifold 74 to pressurize the inflatable chamber 16 according to a higher magnitude transient characteristic of the predetermined high pressure. At the end of a predetermined duration, corresponding to the rise time of the pressure profile, a second control signal 78 closes the high pressure supply valve 66 while simultaneously signaling the low pressure supply valve 68 to open. The regulating action of the low pressure path quickly zeroes in the chamber pressure to that of the desired plateau pressure 79.
  • the controller 76 At the end of the systolic phase, the controller 76 returns the chamber to its pre-pressurized condition by deactivating and closing the low pressure supply control valve 68 and quickly relieving the system with venting mechanism 73 to atmospheric pressure to approximate the release phase of the heart pressure profile.
  • the entire cycle repeats within a relatively short period approximating the range 400 to 1000 milliseconds to correspond with the cyclic activity of the heart.
  • a variation of the present invention according to a second embodiment and generally designated 80 conveniently reduces the number of components necessary to implement the invention. Like the first embodiment illustrated in Fig.
  • the variation includes respective high and low pressure paths 82 and 84 driven by a single compressor P and including respective reservoirs 81 and 83, and respective regulators 85 and 87.
  • the outputs of the tanks terminate in a single switching valve 86 that comprises a supply mechanism and includes a solenoid actuator 88 responsive to a controller 89 to switch the valve output 90 between respective high and low pressure inputs 92 and 94.
  • Output 90 connects to a venting mechanism 101 for introducing pressure from output 90 or atmospheric pressure from tank 103 into the inflatable chamber 16 (Fig. 1).
  • Tank 103 may be open to atmosphere or to a negative pressure.
  • Switching valve 86 and venting mechanism valve 101 together comprise a supply mechanism.
  • the switching valve 86 is expected to be initially set with the low pressure path 84 open through the output 90. Initiation of the pressure profile then begins by actuating the venting mechanism 101 with signal 97 and the switching valve 86 with signal 98, to expose the chamber to the set high pressure. Following a pre-set duration corresponding to the profile rise time, the output of the switching valve 86 switches, with signal 99, back to the normally open position thereby introducing pressurized gas from the low pressure path 84 into the chamber to settle on the pre-set low pressure level corresponding to the plateau level 93. Following the pre-set desired duration for the plateau level, a venting mechanism 101 is actuated by the controller to quickly relieve the system corresponding to the release phase of the heart profile.
  • the system includes a pneumatic source 102 for pressurizing a reservoir 104 having a supply mechanism 106 and a relief mechanism 120.
  • Pneumatic source 102 implemented in the third embodiment of the present invention typically comprises a controllable compressor or pump capable of producing pressurized gas at pressures between the range of 60 to 300 mmHg.
  • An additional source suitable for this application includes a pressurized pneumatic cylinder with appropriate plumbing to step down the bottled pressure to a controllable level.
  • pressurized gas that is frequently supplied by hospitals, in the form of gas distribution lines, may be used as the pressure source.
  • the pneumatic source 102 connects to the tank or reservoir 104 disposed in fluid communication with the supply mechanism 106 and the relief or bypass mechanism 120.
  • the supply mechanism 106 typically comprises a three- way control valve responsive to activation of a solenoid actuator 108, which actuation is controlled by control unit 122.
  • the output of three-way control valve 106 is connected to a pressure output 110, which is connected to the inflatable chamber port 18 ( Figure 1).
  • the input to control valve 106 is either connected to tank 104 or to tank 105.
  • Tank 105 may be open to atmosphere or connected to a negative (i.e., a vacuum) pressure to assist in deflating the liner during the diastolic phase.
  • Bypass mechanism 120 typically comprises a back pressure regulator 1 14 connected to a bypass port on the reservoir and a control valve 116 responsive to a solenoid 118 and positioned at the regulator outlet 120.
  • the respective control valve solenoids 108 and 1 18 electrically connect and are responsive to a controller 122 that sends respective control signals 124 and 126 to the control valves according to a predefined timing scheme, shown in Figure 10.
  • the timing scheme in concert with the pressure levels, conveniently enables independent control of the rise time and the plateau level with a single tank and regulator.
  • valve 116 is preferably set so that when it is open, the pressure within tank 104 is at the plateau pressure ("P plateau "). By merely changing regulator's 114 setpoint, the plateau level can be easily controllable to a relatively high degree of precision.
  • valves 116 and 106 are closed, tank 104 is essentially at the supply pressure of source 102 ("P supply ").
  • valve 116 While still maintaining valve 106 closed, valve 116 is closed causing the pressure within tank 104 to reach P supp ⁇ y , which is greater than P p ⁇ ateau .
  • Controller 122 opens the supply valve 106 and exposes the line 110 connected to the interior of chamber 18 ( Figure 1) to pressurized gas in the range of 150 to 500 mmHg, which is equal to P supp ⁇ y .
  • valve 116 is opened by control signal 126 to cause the pressure within chamber 18 to approach P p ⁇ ateau . without any overshoot.
  • the pressure within chamber 18 increases exponentially toward P supply , until the second control signal 126 is sent by the controller to open the control valve solenoid 118.
  • the timed duration between the control signals corresponds to the rise time of the pressure profile.
  • the controller 122 At the end of the systolic phase, the controller 122 returns the chamber to its pre-pressurized condition by deactivating and closing the supply control valve 106 and quickly venting the system to atmospheric pressure, thereby releasing the pressure in the chamber.
  • the entire cycle repeats within a relatively short period, typically within approximately 400 to 1000 milliseconds, corresponding to the cyclic activity of the heart.
  • a fourth embodiment and generally designated as 160, is illustrated. In this embodiment, only one reservoir 142 is required.
  • the output of pressure source 140 is in direct fluid communication with reservoir 142.
  • a first bypass output path places tank 142 in fluid communication with either a first high pressure path 152 or a second low pressure path 154 through three-way switching valve 148.
  • Regulators 144, 146 are connected to paths 152, 154, respectively.
  • Regulator 144 sets the pressure within line 152 at a predetermined pressure above the plateau pressure.
  • Regulator 146 sets the pressure within line 154 at the plateau pressure.
  • a single switching valve 148 is connected to the inputs of fluid lines 152, 154, respectively.
  • a controller 162 switches valve 148 so that tank 142 is either in fluid communication with high pressure line 152 or plateau pressure line 154.
  • a second output line 150 fluidly connects the output of tank 142 to a supply mechanism or valve 156.
  • Supply valve 156 is similar to supply valve 106 illustrated in Fig. 9. Thus, valve 156 is a three-way valve.
  • the input to control valve 156 is either connected to tank 142 or tank 164.
  • Tank 164 may be open to a atmosphere or to a negative pressure.
  • controller 162 initiates a start control signal 166 to switch valve 148 so that it is in fluid communication with high pressure line 152. Thereafter, control signal 122 initiates start control signal 168 to open supply valve 156 so that the liner is in fluid communication with tank 142 via output line 150. Simultaneously, or after a short delay of between approximately 10 milliseconds to 100 milliseconds, controller 162 initiates a signal to switch valve 148 so that tank 142 is now in fluid communication with plateau line 154. Thus, the pressure within tank 142 will be immediately adjusted to the plateau pressure so that the pressure within chamber 18 approaches P plateau , without any over shoot.
  • the pressure within chamber 18 exponentially rises towards the pressure set within high pressure line 152, until a signal is sent by the controller to switch valve 148 so that the tank is now in fluid communication with the plateau pressure line 154.
  • the controller 162 returns the chamber to its prepressurized position by switching supply valve 156 and quickly venting chamber 18 to either atmospheric pressure or to a negative pressure, as desired.
  • the inflation system of the present invention will appreciate the many advantages afforded by the inflation system of the present invention. Of particular significance is the capability of independently controlling the rise time and plateau level of the pressure profile. With this feature, the pressure pulse can be customized to substantially match a patient's pressure profile to place the system in a more synchronous rhythm with the natural cyclic pumping of the heart. As a result, instances of destructive interference between the assistance apparatus and the heart itself are minimized, thereby maximizing the effective assistance provided to the heart.
  • the present invention also provides the benefit of incorporating a straightforward design to carry out the functionality with a minimum number of mechanical components.
  • costs involved in the purchase and operation of the system are dramatically reduced.
  • minimizing the number of mechanical components also serves to reduce the overall size and complexity of the inflation system, making the system highly desirable for portable applications. Because of the relatively few high maintenance components and corresponding plumbing lines, system reliability is substantially improved.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Anesthesiology (AREA)
  • Mechanical Engineering (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Vascular Medicine (AREA)
  • External Artificial Organs (AREA)

Abstract

L'invention concerne un système (50) de gonflage permettant de régler de manière indépendante le profil de pression, c'est-à-dire le temps de montée et le niveau plateau d'un fluide envoyé dans une chambre (18) gonflable par une source (56) de fluide, via des passages (52, 54) conduisant à des régulateurs (58, 60) haute et basse pression, et des réservoirs (62, 64) dont les sorties sont commandées par des soupapes (66, 68) permettant de produire les hautes et basses pressions requises à des moments spécifiques, afin de déterminer le profil de pression.
PCT/US1998/006353 1997-04-04 1998-03-30 Systeme de transmission pour regler la compression cardiaque Ceased WO1998044969A1 (fr)

Priority Applications (6)

Application Number Priority Date Filing Date Title
EP98915200A EP1021217A4 (fr) 1997-04-04 1998-03-30 Systeme de transmission pour regler la compression cardiaque
BR9807926-3A BR9807926A (pt) 1997-04-04 1998-03-30 Sistema de acionamento e método para controlar a compressão cardìaca.
CA002285231A CA2285231A1 (fr) 1997-04-04 1998-03-30 Systeme de transmission pour regler la compression cardiaque
AU69442/98A AU6944298A (en) 1997-04-04 1998-03-30 Drive system for controlling cardiac compression
JP54286698A JP2001519865A (ja) 1997-04-04 1998-03-30 心臓圧迫制御用駆動装置
NO994826A NO994826D0 (no) 1997-04-04 1999-10-04 Drivsystem for styring av hjertekompresjon

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US4446097P 1997-04-04 1997-04-04
US60/044,460 1997-04-04

Publications (1)

Publication Number Publication Date
WO1998044969A1 true WO1998044969A1 (fr) 1998-10-15

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Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1998/006353 Ceased WO1998044969A1 (fr) 1997-04-04 1998-03-30 Systeme de transmission pour regler la compression cardiaque

Country Status (7)

Country Link
EP (1) EP1021217A4 (fr)
JP (1) JP2001519865A (fr)
AU (1) AU6944298A (fr)
BR (1) BR9807926A (fr)
CA (1) CA2285231A1 (fr)
NO (1) NO994826D0 (fr)
WO (1) WO1998044969A1 (fr)

Cited By (15)

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WO1999022784A1 (fr) 1997-11-03 1999-05-14 Cardio Technologies, Inc. Procede et appareil servant a aider un coeur a pomper du sang
US6572650B1 (en) 1998-06-05 2003-06-03 Organogenesis Inc. Bioengineered vascular graft support prostheses
US6890351B2 (en) 1994-02-18 2005-05-10 Organogenesis Inc. Method for treating diseased or damaged organs
US6986735B2 (en) 1998-06-05 2006-01-17 Organogenesis Inc. Method of making a bioremodelable vascular graft prosthesis
US7060103B2 (en) 1995-04-07 2006-06-13 Organogenesis Inc. Tissue repair fabric
US7077862B2 (en) 2002-01-09 2006-07-18 Myocor, Inc. Devices and methods for heart valve treatment
US7121999B2 (en) 1998-06-05 2006-10-17 Organogenesis Inc. Method of preparing layered graft prostheses
US7189199B2 (en) 1997-01-02 2007-03-13 Myocor, Inc. Methods and devices for improving cardiac function in hearts
US7214242B2 (en) 1998-06-05 2007-05-08 Organogenesis, Inc. Bioengineered tubular graft prostheses
US7666224B2 (en) 2002-11-12 2010-02-23 Edwards Lifesciences Llc Devices and methods for heart valve treatment
US7722523B2 (en) 1998-07-29 2010-05-25 Edwards Lifesciences Llc Transventricular implant tools and devices
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US8092367B2 (en) 2001-09-07 2012-01-10 Mardil, Inc. Method for external stabilization of the base of the heart
US8226711B2 (en) 1997-12-17 2012-07-24 Edwards Lifesciences, Llc Valve to myocardium tension members device and method
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US7060103B2 (en) 1995-04-07 2006-06-13 Organogenesis Inc. Tissue repair fabric
US7189199B2 (en) 1997-01-02 2007-03-13 Myocor, Inc. Methods and devices for improving cardiac function in hearts
WO1999022784A1 (fr) 1997-11-03 1999-05-14 Cardio Technologies, Inc. Procede et appareil servant a aider un coeur a pomper du sang
US8226711B2 (en) 1997-12-17 2012-07-24 Edwards Lifesciences, Llc Valve to myocardium tension members device and method
US7041131B2 (en) 1998-06-05 2006-05-09 Organogenesis, Inc. Bioengineered vascular graft support prostheses
US7121999B2 (en) 1998-06-05 2006-10-17 Organogenesis Inc. Method of preparing layered graft prostheses
US6986735B2 (en) 1998-06-05 2006-01-17 Organogenesis Inc. Method of making a bioremodelable vascular graft prosthesis
US7214242B2 (en) 1998-06-05 2007-05-08 Organogenesis, Inc. Bioengineered tubular graft prostheses
US6572650B1 (en) 1998-06-05 2003-06-03 Organogenesis Inc. Bioengineered vascular graft support prostheses
US7722523B2 (en) 1998-07-29 2010-05-25 Edwards Lifesciences Llc Transventricular implant tools and devices
US7981020B2 (en) 1998-07-29 2011-07-19 Edwards Lifesciences Llc Transventricular implant tools and devices
US8579798B2 (en) 1998-09-21 2013-11-12 Edwards Lifesciences, Llc External cardiac stress reduction method
US9198757B2 (en) 2000-10-06 2015-12-01 Edwards Lifesciences, Llc Methods and devices for improving mitral valve function
US7766812B2 (en) 2000-10-06 2010-08-03 Edwards Lifesciences Llc Methods and devices for improving mitral valve function
US9289298B2 (en) 2001-09-07 2016-03-22 Mardil, Inc. Method and apparatus for external stabilization of the heart
US8092367B2 (en) 2001-09-07 2012-01-10 Mardil, Inc. Method for external stabilization of the base of the heart
US8128553B2 (en) 2001-09-07 2012-03-06 Mardil, Inc. Method and apparatus for external stabilization of the heart
US8070805B2 (en) 2002-01-09 2011-12-06 Edwards Lifesciences Llc Devices and methods for heart valve treatment
US7678145B2 (en) 2002-01-09 2010-03-16 Edwards Lifesciences Llc Devices and methods for heart valve treatment
US7077862B2 (en) 2002-01-09 2006-07-18 Myocor, Inc. Devices and methods for heart valve treatment
US7666224B2 (en) 2002-11-12 2010-02-23 Edwards Lifesciences Llc Devices and methods for heart valve treatment

Also Published As

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CA2285231A1 (fr) 1998-10-15
EP1021217A4 (fr) 2000-09-27
NO994826D0 (no) 1999-10-04
BR9807926A (pt) 2000-02-22
AU6944298A (en) 1998-10-30
EP1021217A1 (fr) 2000-07-26
JP2001519865A (ja) 2001-10-23

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