WO1990013322A1 - Heart-assist balloon pump - Google Patents

Heart-assist balloon pump Download PDF

Info

Publication number
WO1990013322A1
WO1990013322A1 PCT/US1990/002551 US9002551W WO9013322A1 WO 1990013322 A1 WO1990013322 A1 WO 1990013322A1 US 9002551 W US9002551 W US 9002551W WO 9013322 A1 WO9013322 A1 WO 9013322A1
Authority
WO
WIPO (PCT)
Prior art keywords
balloon
ventricular
catheter
heart
inflation
Prior art date
Application number
PCT/US1990/002551
Other languages
French (fr)
Inventor
Jacob Segalowitz
Original Assignee
Jacob Segalowitz
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 Jacob Segalowitz filed Critical Jacob Segalowitz
Priority to EP90908338A priority Critical patent/EP0471029B1/en
Priority to DE69029730T priority patent/DE69029730T2/en
Publication of WO1990013322A1 publication Critical patent/WO1990013322A1/en
Priority to HK98106399A priority patent/HK1008392A1/en

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
    • A61M60/10—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
    • A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
    • A61M60/17—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart inside a ventricle, e.g. intraventricular 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
    • A61M60/10—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
    • A61M60/40—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
    • A61M60/531—Regulation using real-time patient data using blood pressure data, e.g. from blood pressure sensors
    • 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
    • A61M60/562—Electronic control means, e.g. for feedback regulation for making blood flow pulsatile in blood pumps that do not intrinsically create pulsatile flow
    • A61M60/569—Electronic control means, e.g. for feedback regulation for making blood flow pulsatile in blood pumps that do not intrinsically create pulsatile flow synchronous with the native heart beat
    • 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
    • A61M60/841—Constructional details other than related to driving of balloon pumps for circulatory assistance
    • A61M60/843—Balloon aspects, e.g. shapes or materials
    • 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
    • A61M2205/32—General characteristics of the apparatus with radio-opaque indicia

Definitions

  • This invention relates to heart-assist devices and, more particularly, to such devices incorporating balloon pumps.
  • Heart-assist devices are intended to give the heart muscle the necessary time to rest and optimally to recover.
  • the best known of the circulatory-assist devices is the intra-aortic balloon with its counterpulsation capability. With the development of percutaneous techniques for the balloon insertion (for example, through the femoral artery) it is possible to give immediate response to a critical heart condition. However, with the intra-aortic balloon, the cardiac output is increased by only approximately thirty to forty percent. It is clear that a more effective heart-assist device is necessary, particularly in the first moments of intervention, to prevent deterioration of the circulatory system of the patient.
  • the present invention comprises a cardiac- assist, double balloon catheter for pumping blood from the left ventricle of the heart to the aorta synchron- ically with the left ventricle systole and diastole timing.
  • a flexible catheter having a central hollow passage carries two balloons.
  • the first (distal) balloon, the ventricular balloon is positioned at the distal tip of the catheter.
  • the second (proximal) balloon, the aortic balloon is positioned closer to the proximal end of the catheter.
  • the double balloon pump catheter is introduced percutaneously through a peripheral artery and negotiated into the left ventri ⁇ cle of the heart by means of a flexible cardiac guide wire.
  • the ventricular balloon is larger and longer in size than the aortic balloon, and when inflated fills the chamber of the left ventricle of the heart almost completely.
  • the ventricular balloon preferably has the shape and size of the left ventricle of the heart.
  • the aortic balloon is round or elongated in shape and when inflated fits the size of the aorta.
  • the distal tip of the catheter may have a multiple function sensor for detecting various impor ⁇ tant values such as the electrocardiographic activity, blood pressure values, hemodynamic values, etc. of the heart.
  • That sensor has one or more conductors which may be carried in the wall of the catheter to a connector at the proximal end of the catheter.
  • That connector is adapted for connection to an external inflator-deflator which, in response to the electrical activity of the heart, inflates and deflates the ventricular and aortic balloons in synchronized fashion with the proper phase relationship.
  • the heart-signal for controlling inflation and deflation instead of being derived from the sensor on the catheter, may be derived from standard electrocardiographic devices.
  • Inflation and deflation may also be controlled indepen ⁇ dent of the sensor.
  • the control console assures that the aortic balloon is inflated only during diastole and is deflated during systole. Conversely, the ventricular balloon is inflated during systole and deflated during diastole. When the ventricular balloon is deflated, blood flows into the left ventricle from the left atrium.
  • the timing of the inflation and deflation of each balloon is related to the heart cycle as repre- sented by the electrical signals from the heart.
  • the aortic balloon is inflated immediately after the aortic valve-closes so that during diastole the aortic pressure is increased. This increases coronary perfu- sion.
  • the deflation of the aortic balloon occurs just before the start of systole so that aortic impedance to the left ventricular ejection is decreased.
  • the ventricular balloon is immediately inflated after closure of the mitral valve with the start of systole.
  • the inflation progresses rapidly from the distal end of the ventricular balloon toward its proximal end so that a wave-like "pushing" effect is achieved during the rapid inflation, thus forcing the blood from the left ventricle of the heart through the open aortic valve into the aorta where the aortic balloon at that time is deflated.
  • Deflation of the ventricular balloon begins just before the start of diastole with the closure of the aortic valve (between the left ventricle and the aorta) so that left ventri ⁇ cle impedance to atrial blood flow passing during diastole through the mitral valve (between the left atrium and the left ventricle) is eliminated.
  • the rapid, wave-like "pushing" effect on the left ventricle blood volume has the identical effect of ejecting the blood. Since the ventricular balloon corresponds in shape and volume to the shape and almost to the entire volume of the left ventricle of the heart, the stroke-ejected blood volume (stroke output) pumped out from the left ventricle by the balloon pump effect provides a potential stroke output of nearly 100 percent.
  • Both the ventricular balloon and the aortic balloon are inflatable and deflatable separately and independently, one from the other, from two separated inflation-deflation port connectors positioned at the very proximal end of the balloon pump catheter. Such port connectors are connected to the external inflator- deflator console.
  • the central, open-ended lumen of the catheter is connected to a port connector positioned at the most proximal end of the catheter. Contrast solution may thereby be injected to provide the exact positioning of the balloon-pump catheter in the aorta and the left ventricle of the heart during x-ray inspection. This corresponds to current procedures during heart cathe- terization.
  • the central lumen also aids in adjusting timing and synchronization when monitoring arterial pressure.
  • the ventricular balloon and the aortic balloon may come in different volume sizes, thus making the balloon pump catheter suitable for use with optimal precision in pediatric or adult patients.
  • the intra-aortic balloon by itself assists circulation by approximately twenty percent.
  • the effective ⁇ ness of the circulation support is very close to optimal.
  • a heart-assist device comprising: a catheter having a passage therethrough and having a distal end and a proximal end; a ventricular balloon carried by said catheter near the distal end thereof and having an inflated size and shape approximating the shape of the left ventri ⁇ cle, when filled, of the heart of a patient whose heart is being assisted, said ventricular balloon having a proximal end and a distal end, the ventricular balloon expanding upon inflation from said distal end toward said proximal end of said ventricular balloon to create a wave-like pushing effect on blood within the left ventricle of a patient; and an inflation aperture connected to said ventri ⁇ cular balloon to introduce an inflating medium.
  • a heart-assist device comprising: a catheter having a passage therethrough and having a distal end and a proximal end; a ventricular balloon carried by said catheter near the distal end thereof and having an inflated size and shape approximating the size and shape of the left ventricle, when filled, of a patient whose heart is being assisted, said ventricular balloon having a proximal end and a distal end, the size and shape of said ventricular balloon requiring that inflation process from said distal end toward said proximal end of said ventricular balloon to create a wave-like pushing effect during inflation within the left ventricle of a patient; an aortic balloon carried by said catheter closer to said proximal end of said catheter than said ventricular balloon; and tube means carried by said catheter for indepen ⁇ dently carrying an inflating medium to said ventricular and aortic balloons.
  • a ventricular balloon for a heart-assist device comprising an inflatable balloon having a generally frusto-conical shape when inflated approxi ⁇ mating the shape of the left ventricle of a human heart when filled.
  • Fig. 1 is an elevational view of the heart balloon pump catheter according to this invention
  • Fig. 1A is an elevational view of a portion of the structure of Fig. 1 illustrating an alternate embodiment of a ventricular balloon;
  • Fig. 2 is a schematic view showing the present invention in place in the heart of a patient and coupled to external control means;
  • Fig. 3 is an enlarged view of the invention installed in the heart of a patient. Detailed Description of the Preferred Embodiments
  • catheter 10 has a flexible body 12, which is hollow. At its proximal end 14, catheter 10 has a connector 16 for introduction of a contrast solution helpful in the x-ray observation of the installation location and operation of catheter 10. At distal end 17 of catheter 10 there is a sensor 18 for detecting heart action voltages whereby the synchron ⁇ ized inflation and deflation of the balloons associated with the catheter can be achieved by external inflation and deflation means referred to in connection with Fig. 2. Signals from sensor 18 are carried through conduc ⁇ tor 20, which may be carried within the walls of flexible body 12. Connector 20 ultimately emerges from flexible body 12 at electrical output port 22 in flexible body 12 of catheter 10. Tip 24 of catheter 10 is open, thereby exposing lumen 26. Tip 24 may also carry an opaque marker 28 which makes possible accurate location of tip 24 by x-ray means.
  • Catheter 10 carries thereon, in sealed fashion, left ventricular balloon 30 and aortic balloon 32.
  • Aortic port 34 in flexible body 12 is coupled by means of tube 36 to inflation aperture 38 within the confines of aortic balloon 32.
  • Ventricular port 40 is coupled by means of tube 42 to inflation aperture 44 which is within the confines of ventricular balloon 30.
  • the shape of ventricular balloon 30 is of particular note. When inflated, ventricular balloon 30 has a shape which may be technically described as approximately a frusto- conical shape. However, the shape may more practically be described as the shape of the left ventricle when filled with blood. The shape and size of ventricular balloon 30 is, of course, intended to fully discharge blood from the left ventricle at the appropriate moment in the heart cycle.
  • ventricular balloon 30 commences at narrower distal end 31 of ventricular balloon 30, and progresses toward proximal end 33, terminating in the base or wide end of ventricular balloon 30 with the result that there is a rapid, wave-like "pushing" effect on the left ventricular blood volume and an ejection of blood from the left ventricle to nearly 100 percent of the volume of the left ventricle.
  • ventricular balloon 30 it is within the scope of the invention to vary the construction of ventricular balloon 30 to accom ⁇ plish the progressive inflation process which is referred to as the wave-like pushing effect.
  • inflation aperture 44 is positioned near distal end 31 of ventricular balloon 30 which will, much as in the case of the inflation of an ordinary long elastic balloon, start closest to the source of inflation.
  • ventricular balloon 30 of the invention is preferably not made of elastic material but rather is made of suitable material such as cross-linked polyethylene or like materials known to maintain a predetermined size and shape when inflated.
  • ventricular balloon 30 As shown in Fig. 1A, it is possible to segment ventricular balloon 30 into two or more segments 30A and 3OB. This will ensure the progressive inflation of the overall balloon from distal end 46, to proximal end 48, thus ensuring the aforementioned pushing action upon the blood in the left ventricle.
  • inlet ports 50 and 52 with associated inflating medium input and output tubes 54, 56, respectively, are provided.
  • an additional port With this two-segment con iguration, an additional port will have to be provided on catheter 10, and the control console shown in Fig. 2 will have to have an additional inflation- deflation port with an associated control circuitry, all of which are controlled in response to heart- signals derived either from the sensor 18 or from an independent source of electrical heart-signals.
  • ventricular balloon 30 divided into two or more compartments within a single integral balloon such as by the connection of segments 30A and 30B at 41 wherein the compartments are either sealed from each other and connected to single and/or separate inflation sources, or where the compartments are interconnected and inflated progressively by a single source.
  • segments 30A and 30B at 41 wherein the compartments are either sealed from each other and connected to single and/or separate inflation sources, or where the compartments are interconnected and inflated progressively by a single source.
  • the additional inflation- deflation port discussed with respect to Fig. 2 will not be needed.
  • FIG. 2 the heart balloon pump catheter according to this invention is shown, diagram- matically, in place in a human heart.
  • Aortic ventricu ⁇ lar ports 34, 40 are shown coupled by tubes 58, 60, respectively, to control console 62.
  • Electrocar ⁇ diographic signals are received by control console 62 through conductor 64 and synchronized.
  • High speed inflation and deflation of the respective balloons is achieved by utilizing an inflating medium such as helium which has a very low atomic weight.
  • Control console 62 is an extension of the control console commonly used today in connection with intra- aortic balloons.
  • the console preferably has two or more separate controllers, one for each balloon or balloon segment, as the case may be. Each controller can act independently of another controller, or they can act in sequence, as desired.
  • catheter 10 may be introduced through femoral artery 70 in the groin of the patient. Tube 66 having connector 16 is available for introduc ⁇ tion of contrast fluid.
  • ventricular balloon 30 which is at the distal end of catheter 10
  • ventricular balloon 30 is placed at the apex of left ventricle 72 of the heart.
  • inflation of ventricular balloon 30 begins at the most remote portion of the balloon which is immediately adjacent the apex of left ventricle 72, and inflation progresses toward the base of ventricular balloon 30.
  • blood is pumped out of left ventricle 72 into the aorta.
  • Aortic balloon 32 is collapsed or deflated at the moment ventricular balloon 30 is inflated.
  • the fast, progressive inflation of ventricu ⁇ lar balloon 30 from the ventricle apex toward the aorta correlates exactly with the normal physiological reaction arising from ventricular muscle contraction.
  • the blood is pumped out of the left ventricle into the aorta.
  • the heart balloon pump catheter may have only the ventricular balloon, thus eliminating the aortic balloon from catheter 10.
  • a single, synchronized balloon pump i.e., the ventricular balloon shaped and sized according to this invention.
  • the same wave-like "pushing" ejection of blood from the left ventricle of the heart into the aorta, during systole, is achieved by way of this embodiment of the invention.
  • Ventri ⁇ cular balloon 30 displaces a volume of blood equivalent to the ventricular balloon's volume, and proper syn- chronism is controlled by control console 62.
  • control console 62 may be used to activate control console 62 and to synchronize the inflation-deflation of the balloon pumps.
  • the aortic balloon is inflated during diastole and is deflated during systole.
  • ventricular balloon 30 is inflated during systole and deflated during diastole.
  • blood comes into the left ventricle from the left atrium of the heart for the next cycle of operation.

Landscapes

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

Abstract

A heart-assist device which includes a flexible catheter (10) carrying at least a ventricular balloon (30), such balloon (30) corresponding in size and shape to the size and shape of the left ventricle in the heart being assisted, the ventricular balloon (30) being progressively inflated creating a wave-like pushing effect and deflated synchronously and automatically by means of a control console (62) which responds to heart signals from the catheter (10) or elsewhere, the catheter (10) optionally also carrying an aortic balloon (32) inflated and deflated automatically and synchronously (but in opposite phase) with the ventricular balloon (30) by means of the control console (62), helium optionally being used as the inflating medium to ensure high speed inflation-deflation.

Description

HEART-ASSIST BALLOON PUMP
Background of the Invention
Field of the Invention
This invention relates to heart-assist devices and, more particularly, to such devices incorporating balloon pumps.
Prior Art
During the past thirty years there has been an ever-increasing frequency of heart surgery and greater study and knowledge of the functions of the heart. One of the product groups which has resulted from this increased activity in the knowledge of the function of the heart has been what are known as temporary circula- tory-assist devices. The purpose of such devices is to stabilize, hemodynamically, a failing circulatory system resulting from a failure in the pumping action of the heart. Beneficial results have been realized by the use of heart-assist devices in patients with cardiogenic shock and in severe acute myocardial ischemia. Further, in the critical moments before or after a heart transplantation or after open heart surgical procedures, temporary support of the cardio- circulatory system is crucial.
These heart-assist devices are intended to give the heart muscle the necessary time to rest and optimally to recover. The best known of the circulatory-assist devices is the intra-aortic balloon with its counterpulsation capability. With the development of percutaneous techniques for the balloon insertion (for example, through the femoral artery) it is possible to give immediate response to a critical heart condition. However, with the intra-aortic balloon, the cardiac output is increased by only approximately thirty to forty percent. It is clear that a more effective heart-assist device is necessary, particularly in the first moments of intervention, to prevent deterioration of the circulatory system of the patient.
Therefore, it is an object of this invention to provide a heart-assist device which is compact, is easily handled by a single specialist, is completely atrau atic both to the ventricular chamber and to the blood volume constituents, and is highly effective so as to achieve nearly normal physiological conditions during its use.
Summary of the Invention
The present invention comprises a cardiac- assist, double balloon catheter for pumping blood from the left ventricle of the heart to the aorta synchron- ically with the left ventricle systole and diastole timing.
A flexible catheter having a central hollow passage carries two balloons. The first (distal) balloon, the ventricular balloon, is positioned at the distal tip of the catheter. The second (proximal) balloon, the aortic balloon, is positioned closer to the proximal end of the catheter. The double balloon pump catheter is introduced percutaneously through a peripheral artery and negotiated into the left ventri¬ cle of the heart by means of a flexible cardiac guide wire.
The ventricular balloon is larger and longer in size than the aortic balloon, and when inflated fills the chamber of the left ventricle of the heart almost completely. The ventricular balloon preferably has the shape and size of the left ventricle of the heart. The aortic balloon is round or elongated in shape and when inflated fits the size of the aorta.
The distal tip of the catheter may have a multiple function sensor for detecting various impor¬ tant values such as the electrocardiographic activity, blood pressure values, hemodynamic values, etc. of the heart. That sensor has one or more conductors which may be carried in the wall of the catheter to a connector at the proximal end of the catheter. That connector is adapted for connection to an external inflator-deflator which, in response to the electrical activity of the heart, inflates and deflates the ventricular and aortic balloons in synchronized fashion with the proper phase relationship. The heart-signal for controlling inflation and deflation, instead of being derived from the sensor on the catheter, may be derived from standard electrocardiographic devices.
Inflation and deflation may also be controlled indepen¬ dent of the sensor.
The control console assures that the aortic balloon is inflated only during diastole and is deflated during systole. Conversely, the ventricular balloon is inflated during systole and deflated during diastole. When the ventricular balloon is deflated, blood flows into the left ventricle from the left atrium.
The timing of the inflation and deflation of each balloon is related to the heart cycle as repre- sented by the electrical signals from the heart. The aortic balloon is inflated immediately after the aortic valve-closes so that during diastole the aortic pressure is increased. This increases coronary perfu- sion. The deflation of the aortic balloon occurs just before the start of systole so that aortic impedance to the left ventricular ejection is decreased.
The ventricular balloon is immediately inflated after closure of the mitral valve with the start of systole. The inflation progresses rapidly from the distal end of the ventricular balloon toward its proximal end so that a wave-like "pushing" effect is achieved during the rapid inflation, thus forcing the blood from the left ventricle of the heart through the open aortic valve into the aorta where the aortic balloon at that time is deflated. Deflation of the ventricular balloon begins just before the start of diastole with the closure of the aortic valve (between the left ventricle and the aorta) so that left ventri¬ cle impedance to atrial blood flow passing during diastole through the mitral valve (between the left atrium and the left ventricle) is eliminated.
The rapid, wave-like "pushing" effect on the left ventricle blood volume has the identical effect of ejecting the blood. Since the ventricular balloon corresponds in shape and volume to the shape and almost to the entire volume of the left ventricle of the heart, the stroke-ejected blood volume (stroke output) pumped out from the left ventricle by the balloon pump effect provides a potential stroke output of nearly 100 percent.
Both the ventricular balloon and the aortic balloon are inflatable and deflatable separately and independently, one from the other, from two separated inflation-deflation port connectors positioned at the very proximal end of the balloon pump catheter. Such port connectors are connected to the external inflator- deflator console.
The central, open-ended lumen of the catheter is connected to a port connector positioned at the most proximal end of the catheter. Contrast solution may thereby be injected to provide the exact positioning of the balloon-pump catheter in the aorta and the left ventricle of the heart during x-ray inspection. This corresponds to current procedures during heart cathe- terization. The central lumen also aids in adjusting timing and synchronization when monitoring arterial pressure. The ventricular balloon and the aortic balloon may come in different volume sizes, thus making the balloon pump catheter suitable for use with optimal precision in pediatric or adult patients.
The intra-aortic balloon by itself assists circulation by approximately twenty percent. When combined with the ventricular balloon, the effective¬ ness of the circulation support is very close to optimal.
The manipulation of the balloon pump catheter of the present invention is simple and does not require training or equipment different from current heart catheterization techniques or equipment. Thus, the present balloon pump can be applied immediately. In one aspect of the invention there is provided a heart-assist device comprising: a catheter having a passage therethrough and having a distal end and a proximal end; a ventricular balloon carried by said catheter near the distal end thereof and having an inflated size and shape approximating the shape of the left ventri¬ cle, when filled, of the heart of a patient whose heart is being assisted, said ventricular balloon having a proximal end and a distal end, the ventricular balloon expanding upon inflation from said distal end toward said proximal end of said ventricular balloon to create a wave-like pushing effect on blood within the left ventricle of a patient; and an inflation aperture connected to said ventri¬ cular balloon to introduce an inflating medium.
In another aspect of the invention there is provided a heart-assist device comprising: a catheter having a passage therethrough and having a distal end and a proximal end; a ventricular balloon carried by said catheter near the distal end thereof and having an inflated size and shape approximating the size and shape of the left ventricle, when filled, of a patient whose heart is being assisted, said ventricular balloon having a proximal end and a distal end, the size and shape of said ventricular balloon requiring that inflation process from said distal end toward said proximal end of said ventricular balloon to create a wave-like pushing effect during inflation within the left ventricle of a patient; an aortic balloon carried by said catheter closer to said proximal end of said catheter than said ventricular balloon; and tube means carried by said catheter for indepen¬ dently carrying an inflating medium to said ventricular and aortic balloons.
In yet another aspect of the invention there is provided a ventricular balloon for a heart-assist device comprising an inflatable balloon having a generally frusto-conical shape when inflated approxi¬ mating the shape of the left ventricle of a human heart when filled.
Brief Description of the Drawing
The invention herein and the means by which it achieves the original, new and unobvious results, can best be understood by referring to the detailed description which follows, taken in conjunction with the drawing herein, in which:
Fig. 1 is an elevational view of the heart balloon pump catheter according to this invention;
Fig. 1A is an elevational view of a portion of the structure of Fig. 1 illustrating an alternate embodiment of a ventricular balloon;
Fig. 2 is a schematic view showing the present invention in place in the heart of a patient and coupled to external control means; and
Fig. 3 is an enlarged view of the invention installed in the heart of a patient. Detailed Description of the Preferred Embodiments
In Fig. 1, catheter 10 has a flexible body 12, which is hollow. At its proximal end 14, catheter 10 has a connector 16 for introduction of a contrast solution helpful in the x-ray observation of the installation location and operation of catheter 10. At distal end 17 of catheter 10 there is a sensor 18 for detecting heart action voltages whereby the synchron¬ ized inflation and deflation of the balloons associated with the catheter can be achieved by external inflation and deflation means referred to in connection with Fig. 2. Signals from sensor 18 are carried through conduc¬ tor 20, which may be carried within the walls of flexible body 12. Connector 20 ultimately emerges from flexible body 12 at electrical output port 22 in flexible body 12 of catheter 10. Tip 24 of catheter 10 is open, thereby exposing lumen 26. Tip 24 may also carry an opaque marker 28 which makes possible accurate location of tip 24 by x-ray means.
Catheter 10 carries thereon, in sealed fashion, left ventricular balloon 30 and aortic balloon 32. Aortic port 34 in flexible body 12 is coupled by means of tube 36 to inflation aperture 38 within the confines of aortic balloon 32. Ventricular port 40 is coupled by means of tube 42 to inflation aperture 44 which is within the confines of ventricular balloon 30. The shape of ventricular balloon 30 is of particular note. When inflated, ventricular balloon 30 has a shape which may be technically described as approximately a frusto- conical shape. However, the shape may more practically be described as the shape of the left ventricle when filled with blood. The shape and size of ventricular balloon 30 is, of course, intended to fully discharge blood from the left ventricle at the appropriate moment in the heart cycle. By reason of its tapered shape, the inflation of ventricular balloon 30 commences at narrower distal end 31 of ventricular balloon 30, and progresses toward proximal end 33, terminating in the base or wide end of ventricular balloon 30 with the result that there is a rapid, wave-like "pushing" effect on the left ventricular blood volume and an ejection of blood from the left ventricle to nearly 100 percent of the volume of the left ventricle.
It is within the scope of the invention to vary the construction of ventricular balloon 30 to accom¬ plish the progressive inflation process which is referred to as the wave-like pushing effect. In addition to the tapered shape of ventricular balloon 30, it can be seen that inflation aperture 44 is positioned near distal end 31 of ventricular balloon 30 which will, much as in the case of the inflation of an ordinary long elastic balloon, start closest to the source of inflation. It is understood that ventricular balloon 30 of the invention is preferably not made of elastic material but rather is made of suitable material such as cross-linked polyethylene or like materials known to maintain a predetermined size and shape when inflated. Other design expedients such as varying the thickness, strength or the flexibility of the wall of ventricular balloon 30, providing multiple inflation apertures of decreasing size shown in phantom at 35, 37 and 39, etc. are also considered to be within the scope of the invention requiring inflation expan- sion from distal end 31 toward proximal end 33 to create the wave-like pushing effect on blood within the left ventricle.
As shown in Fig. 1A, it is possible to segment ventricular balloon 30 into two or more segments 30A and 3OB. This will ensure the progressive inflation of the overall balloon from distal end 46, to proximal end 48, thus ensuring the aforementioned pushing action upon the blood in the left ventricle. For full control, separate inlet ports 50 and 52 with associated inflating medium input and output tubes 54, 56, respectively, are provided. With this two-segment con iguration, an additional port will have to be provided on catheter 10, and the control console shown in Fig. 2 will have to have an additional inflation- deflation port with an associated control circuitry, all of which are controlled in response to heart- signals derived either from the sensor 18 or from an independent source of electrical heart-signals.
It is within the meaning of a "segmented" balloon to have ventricular balloon 30 divided into two or more compartments within a single integral balloon such as by the connection of segments 30A and 30B at 41 wherein the compartments are either sealed from each other and connected to single and/or separate inflation sources, or where the compartments are interconnected and inflated progressively by a single source. In the case of a single source, the additional inflation- deflation port discussed with respect to Fig. 2 will not be needed.
Turning to Fig. 2, the heart balloon pump catheter according to this invention is shown, diagram- matically, in place in a human heart. Aortic ventricu¬ lar ports 34, 40 are shown coupled by tubes 58, 60, respectively, to control console 62. Electrocar¬ diographic signals are received by control console 62 through conductor 64 and synchronized. High speed inflation and deflation of the respective balloons is achieved by utilizing an inflating medium such as helium which has a very low atomic weight. The use of other gases is also within the scope of the invention. Control console 62 is an extension of the control console commonly used today in connection with intra- aortic balloons. The console preferably has two or more separate controllers, one for each balloon or balloon segment, as the case may be. Each controller can act independently of another controller, or they can act in sequence, as desired.
The manipulation and insertion of the balloon pump catheter according to this invention is simple and does not require training or equipment different from that currently in use. Catheter 10 may be introduced through femoral artery 70 in the groin of the patient. Tube 66 having connector 16 is available for introduc¬ tion of contrast fluid. As can be seen in Fig. 3, when catheter 10 is fully inserted, ventricular balloon 30, which is at the distal end of catheter 10, is placed at the apex of left ventricle 72 of the heart. As has been indicated, inflation of ventricular balloon 30 begins at the most remote portion of the balloon which is immediately adjacent the apex of left ventricle 72, and inflation progresses toward the base of ventricular balloon 30. Thus blood is pumped out of left ventricle 72 into the aorta. Aortic balloon 32 is collapsed or deflated at the moment ventricular balloon 30 is inflated. The fast, progressive inflation of ventricu¬ lar balloon 30 from the ventricle apex toward the aorta correlates exactly with the normal physiological reaction arising from ventricular muscle contraction. Thus, the blood is pumped out of the left ventricle into the aorta.
According to this invention, the heart balloon pump catheter may have only the ventricular balloon, thus eliminating the aortic balloon from catheter 10. With this structure there is a single, synchronized balloon pump, i.e., the ventricular balloon shaped and sized according to this invention. The same wave-like "pushing" ejection of blood from the left ventricle of the heart into the aorta, during systole, is achieved by way of this embodiment of the invention. Ventri¬ cular balloon 30 displaces a volume of blood equivalent to the ventricular balloon's volume, and proper syn- chronism is controlled by control console 62.
Experiments have shown that the inflation- deflation sequence of either ventricular balloon 30 by itself or the combination of ventricular balloon 30 and aortic balloon 32 can be achieved in approximately 0.025 seconds, i.e., in synchrony with the heart action.
It should be understood that while the captive control console has been shown as deriving its control signal from a sensor at the distal end of the catheter, other sources of the cyclical heart signals may be used to activate control console 62 and to synchronize the inflation-deflation of the balloon pumps.
Thus, the aortic balloon is inflated during diastole and is deflated during systole. Conversely, ventricular balloon 30 is inflated during systole and deflated during diastole. When ventricular balloon 30 is deflated, blood comes into the left ventricle from the left atrium of the heart for the next cycle of operation.
While particular embodiments of the invention have been shown and described, it will be apparent to those skilled in the art that variations and modifica- tions may be made therein without departing from the true scope and spirit of the invention. It is the purpose of the appended Claims to cover all such variations and modifications.

Claims

I Claim:
1. A heart-assist device comprising: a catheter having a passage therethrough and having a distal end and a proximal end; a ventricular balloon carried by said catheter near the distal end thereof and having an inflated size and shape approximating the shape of the left ventri¬ cle, when filled, of the heart of a patient whose heart is being assisted, said ventricular balloon having a proximal end and a distal end, the ventricular balloon expanding upon inflation from said distal end toward said proximal end of said ventricular balloon to create a wave-like pushing effect on blood within the left ventricle of a patient; and an inflation aperture connected to said ventri¬ cular balloon to introduce an inflating medium.
2. Apparatus according to Claim 1 further including an aortic balloon carried by said catheter closer to said proximal end of said catheter than said ventricular balloon; and tube means carried by said catheter for carrying an inflating medium to said aortic balloon.
3. Apparatus according to Claim 1 which includes, in addition, a heart-signal sensor carried by said catheter near the distal end thereof.
4. Apparatus according to Claim 1 wherein said ventricular balloon is frusto-conical in shape and is generally fixed in axial length so that expansion is generally radial in direction.
5. Apparatus according to Claim 4 in which said ventricular balloon is segmented.
6. Apparatus according to Claim 1 which includes, in addition, a heart-signal sensor carried at the distal end of said catheter; an automatic inflation-deflation control console having inflation-deflation ports and a heart-signal electrical input connector; tube means coupled pneumatically between said inflation means carried by said catheter and said inflation-deflation ports; and electrical conductor means coupled between said heart-signal sensor on said catheter and said heart- signal electrical input connector on said automatic inflation-deflation control console.
7. A heart-assist device comprising: a catheter having a passage therethrough and having a distal end and a proximal end; a ventricular balloon carried by said catheter near the distal end thereof and having an inflated size and shape approximating the size and shape of the left ventricle, when filled, of a patient whose heart is being assisted, said ventricular balloon having a proximal end and a distal end, the size and shape of said ventricular balloon requiring that inflation process from said distal end toward said proximal end of said ventricular balloon to create a wave-like pushing effect during inflation within the left ventricle of a patient; an aortic balloon carried by said catheter closer to said proximal end of said catheter than said ventricular balloon; and tube means carried by said catheter for indepen¬ dently carrying an inflating medium to said ventricular and aortic balloons.
8. Apparatus according to Claim 7 which includes, in addition, inflation medium control means coupled pneumatically to said tube means for automa¬ tically supplying to said tube means and exhausting from said tube means an inflating medium for the respective ventricular and aortic balloons.
9. Apparatus according to Claim 7 further including an inflating medium.
10. Apparatus according to Claim 9 wherein said inflating medium is helium.
11. Apparatus according to Claim 7 wherein said ventricular balloon is frusto-conical in shape and is generally fixed in axial length so that expansion is generally radial in direction.
12. Apparatus according to Claim 11 in which said ventricular balloon is segmented.
13. Apparatus according to Claim 11 which includes, in addition, separate tube means for inflat¬ ing and deflating, independently, the separate segments of said segmented ventricular balloon.
14. A ventricular balloon for a heart-assist device comprising an inflatable balloon having a generally frusto-conical shape when inflated approxi¬ mating the shape of the left ventricle of a human heart when filled.
15. A ventricular balloon as in Claim 14 wherein said balloon has a distal end and a proximal end, said distal end being smaller in diameter than said proximal end, said balloon having an inflation aperture near said distal end, said balloon being inflatable through said aperture such that said distal end of said balloon will radially enlarge before said proxima1 end.
16. A ventricular balloon as in Claim 15 wherein said balloon has a plurality of inflation apertures spaced along the length of said balloon.
17. A ventricular balloon as in Claim 16 wherein said apertures are of different size, decreas- ing in size from said distal end.
18. A ventricular balloon as in Claim 14 wherein said balloon is segmented into a plurality of segments, each segment having an inflation aperture.
19. A ventricular balloon as in Claim 14 wherein said balloon has a plurality of compartments contained therein to provide for sequential expansion of the balloon.
20. A ventricular balloon as in Claim 14 further including a catheter body comprising a tube, said balloon positioned over said tube and sealed from said tube, said balloon having an inflation aperture to introduce an inflating medium by means other than said tube.
PCT/US1990/002551 1989-05-05 1990-05-07 Heart-assist balloon pump WO1990013322A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP90908338A EP0471029B1 (en) 1989-05-05 1990-05-07 Heart-assist balloon pump
DE69029730T DE69029730T2 (en) 1989-05-05 1990-05-07 BALLOON PUMP TO HELP THE HEART
HK98106399A HK1008392A1 (en) 1989-05-05 1998-06-24 Heart-assist balloon pump

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US347,674 1989-05-05
US07/347,674 US5176619A (en) 1989-05-05 1989-05-05 Heart-assist balloon pump with segmented ventricular balloon

Publications (1)

Publication Number Publication Date
WO1990013322A1 true WO1990013322A1 (en) 1990-11-15

Family

ID=23364754

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1990/002551 WO1990013322A1 (en) 1989-05-05 1990-05-07 Heart-assist balloon pump

Country Status (7)

Country Link
US (1) US5176619A (en)
EP (1) EP0471029B1 (en)
AU (1) AU5732890A (en)
CA (1) CA2016103C (en)
DE (1) DE69029730T2 (en)
HK (1) HK1008392A1 (en)
WO (1) WO1990013322A1 (en)

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0604803A2 (en) * 1992-12-17 1994-07-06 Shlomo Gabbay Multi purpose perfusion cannula
WO2007090416A1 (en) * 2006-02-07 2007-08-16 Medicor Gmbh Medical vascular lock with blocking function
EP2981208A4 (en) * 2013-06-14 2017-01-04 Perfusion Solutions Pty Ltd Cardiac function evaluation system
US10098644B2 (en) 2010-09-21 2018-10-16 Hocor Cardiovascular Technologies Llc Method and system for balloon counterpulsation during aortic valve replacement
WO2020087125A1 (en) 2018-10-31 2020-05-07 Griffith University Ventricular assistance system and method

Families Citing this family (109)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5879499A (en) * 1996-06-17 1999-03-09 Heartport, Inc. Method of manufacture of a multi-lumen catheter
US6482171B1 (en) 1991-07-16 2002-11-19 Heartport, Inc. Multi-lumen catheter
US5584803A (en) 1991-07-16 1996-12-17 Heartport, Inc. System for cardiac procedures
US5766151A (en) * 1991-07-16 1998-06-16 Heartport, Inc. Endovascular system for arresting the heart
US5769812A (en) 1991-07-16 1998-06-23 Heartport, Inc. System for cardiac procedures
US5795325A (en) * 1991-07-16 1998-08-18 Heartport, Inc. Methods and apparatus for anchoring an occluding member
US6866650B2 (en) 1991-07-16 2005-03-15 Heartport, Inc. System for cardiac procedures
US5433700A (en) * 1992-12-03 1995-07-18 Stanford Surgical Technologies, Inc. Method for intraluminally inducing cardioplegic arrest and catheter for use therein
US5458574A (en) * 1994-03-16 1995-10-17 Heartport, Inc. System for performing a cardiac procedure
US5413558A (en) * 1991-09-09 1995-05-09 New York University Selective aortic perfusion system for use during CPR
US6224619B1 (en) 1991-12-17 2001-05-01 Heartport, Inc. Blood vessel occlusion trocar having size and shape varying insertion body
US5759170A (en) 1993-11-30 1998-06-02 Heartport, Inc. Method for intraluminally inducing cardioplegic arrest and catheter for use therein
US5478309A (en) 1994-05-27 1995-12-26 William P. Sweezer, Jr. Catheter system and method for providing cardiopulmonary bypass pump support during heart surgery
US5772631A (en) * 1995-04-28 1998-06-30 Lepor; Norman E. Procedure for alleviating arterial obstruction
US5863366A (en) * 1995-06-07 1999-01-26 Heartport, Inc. Method of manufacture of a cannula for a medical device
ATE347311T1 (en) * 1996-03-20 2006-12-15 Gen Surgical Innovations Inc COMBINED DISSECTION AND RETRACTION DEVICE
US5820542A (en) * 1996-10-31 1998-10-13 Momentum Medical, Inc. Modified circulatory assist device
US5827171A (en) * 1996-10-31 1998-10-27 Momentum Medical, Inc. Intravascular circulatory assist device
US5755687A (en) 1997-04-01 1998-05-26 Heartport, Inc. Methods and devices for occluding a patient's ascending aorta
US6090096A (en) 1997-04-23 2000-07-18 Heartport, Inc. Antegrade cardioplegia catheter and method
UA56262C2 (en) 1997-10-09 2003-05-15 Орквіс Медікел Корпорейшн Extracardiac pumping system for supplementing blood circulation
US6390969B1 (en) 1997-10-09 2002-05-21 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6610004B2 (en) * 1997-10-09 2003-08-26 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6889082B2 (en) * 1997-10-09 2005-05-03 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6387037B1 (en) 1997-10-09 2002-05-14 Orqis Medical Corporation Implantable heart assist system and method of applying same
US6159178A (en) 1998-01-23 2000-12-12 Heartport, Inc. Methods and devices for occluding the ascending aorta and maintaining circulation of oxygenated blood in the patient when the patient's heart is arrested
US6254525B1 (en) 1998-11-04 2001-07-03 Cardio Technologies, Inc. Cardiac assist system and method thereof
US6245007B1 (en) 1999-01-28 2001-06-12 Terumo Cardiovascular Systems Corporation Blood pump
US20040162519A1 (en) * 1999-04-27 2004-08-19 Helkowski Richard A. Aortic occlusion balloon cannula
US6315768B1 (en) * 1999-06-08 2001-11-13 Richard K. Wallace Perfusion procedure and apparatus for preventing necrosis following failed balloon angioplasty
US6692484B1 (en) * 1999-07-17 2004-02-17 Wilson-Cook Medical Incorporated Devices for extracting biliary or urinary stones
US6406422B1 (en) 2000-03-02 2002-06-18 Levram Medical Devices, Ltd. Ventricular-assist method and apparatus
US6808483B1 (en) * 2000-10-03 2004-10-26 Paul A. Spence Implantable heart assist devices and methods
US6527739B1 (en) 2000-12-29 2003-03-04 Advanced Cardiovascular Systems, Inc. Spiraled balloon arrangement for treatment of a tortuous vessel
US6681773B2 (en) * 2001-02-28 2004-01-27 Chase Medical, Inc. Kit and method for use during ventricular restoration
US20030181940A1 (en) * 2001-02-28 2003-09-25 Gregory Murphy Ventricular restoration shaping apparatus and method of use
US7485088B2 (en) * 2001-09-05 2009-02-03 Chase Medical L.P. Method and device for percutaneous surgical ventricular repair
US20040243170A1 (en) * 2001-09-05 2004-12-02 Mitta Suresh Method and device for percutaneous surgical ventricular repair
EP1581102A4 (en) * 2002-12-11 2006-12-20 Proteus Biomedical Inc Method and system for monitoring and treating hemodynamic parameters
US7204798B2 (en) * 2003-01-24 2007-04-17 Proteus Biomedical, Inc. Methods and systems for measuring cardiac parameters
US8721515B2 (en) * 2003-01-31 2014-05-13 L-Vad Technology, Inc. Rigid body aortic blood pump implant
US8540618B2 (en) 2003-01-31 2013-09-24 L-Vad Technology, Inc. Stable aortic blood pump implant
WO2004082736A2 (en) * 2003-03-14 2004-09-30 Light Sciences Corporation Light generating device to intravascular use
CN2885311Y (en) 2006-01-18 2007-04-04 郑成福 Via urethra prostate therapeutic equipment using photodynamic therapy
US10376711B2 (en) * 2003-03-14 2019-08-13 Light Sciences Oncology Inc. Light generating guide wire for intravascular use
US20080269846A1 (en) * 2003-03-14 2008-10-30 Light Sciences Oncology, Inc. Device for treatment of blood vessels using light
JP4746542B2 (en) * 2003-07-09 2011-08-10 ライト、サイエンシーズ、オンコロジー、インコーポレイテッド Peripheral protection and treatment device for blood
US20050085683A1 (en) * 2003-10-15 2005-04-21 Bolling Steven F. Implantable heart assist system and method of applying same
US20050131385A1 (en) * 2003-12-12 2005-06-16 Bolling Steven F. Cannulae for selectively enhancing blood flow
US7172551B2 (en) * 2004-04-12 2007-02-06 Scimed Life Systems, Inc. Cyclical pressure coronary assist pump
US20050277870A1 (en) * 2004-06-10 2005-12-15 Robert Pecor Cannula having reduced flow resistance
US7445592B2 (en) * 2004-06-10 2008-11-04 Orqis Medical Corporation Cannulae having reduced flow resistance
US7214189B2 (en) * 2004-09-02 2007-05-08 Proteus Biomedical, Inc. Methods and apparatus for tissue activation and monitoring
US20060064059A1 (en) * 2004-09-21 2006-03-23 Mark Gelfand Treatment of infarct expansion by partially occluding vena cava
US20060074483A1 (en) * 2004-10-01 2006-04-06 Schrayer Howard L Method of treatment and devices for the treatment of left ventricular failure
US7347810B2 (en) * 2004-10-01 2008-03-25 Stamos Thomas A Device for draining the coronary sinus
US20060184199A1 (en) * 2005-02-14 2006-08-17 O'leary Shawn Apparatus and methods for reducing bleeding from a cannulation site
US20060224110A1 (en) * 2005-03-17 2006-10-05 Scott Michael J Methods for minimally invasive vascular access
JP5027797B2 (en) * 2005-03-31 2012-09-19 プロテウス バイオメディカル インコーポレイテッド Automatic optimization of multi-electrode pacing for cardiac resynchronization
EP1898999A4 (en) * 2005-07-01 2011-10-19 Proteus Biomedical Inc Deployable epicardial electrode and sensor array
WO2007021804A2 (en) * 2005-08-12 2007-02-22 Proteus Biomedical, Inc. Evaluation of depolarization wave conduction velocity
US7766893B2 (en) * 2005-12-07 2010-08-03 Boston Scientific Scimed, Inc. Tapered multi-chamber balloon
WO2007075974A2 (en) * 2005-12-22 2007-07-05 Proteus Biomedical, Inc. Implantable integrated circuit
WO2007076324A2 (en) * 2005-12-23 2007-07-05 C.R. Bard Inc. Balloon catheter with centralized vent hole
US7914436B1 (en) 2006-06-12 2011-03-29 Abiomed, Inc. Method and apparatus for pumping blood
US7654264B2 (en) 2006-07-18 2010-02-02 Nellcor Puritan Bennett Llc Medical tube including an inflatable cuff having a notched collar
ES2638430T3 (en) * 2006-09-22 2017-10-20 Romano Guerra Tracheostomy device and device
US20080207986A1 (en) * 2007-02-26 2008-08-28 Choy Daniel S J Heart assist device
US9375164B2 (en) 2007-03-08 2016-06-28 Sync-Rx, Ltd. Co-use of endoluminal data and extraluminal imaging
US11197651B2 (en) 2007-03-08 2021-12-14 Sync-Rx, Ltd. Identification and presentation of device-to-vessel relative motion
US9305334B2 (en) 2007-03-08 2016-04-05 Sync-Rx, Ltd. Luminal background cleaning
US9968256B2 (en) 2007-03-08 2018-05-15 Sync-Rx Ltd. Automatic identification of a tool
US9629571B2 (en) 2007-03-08 2017-04-25 Sync-Rx, Ltd. Co-use of endoluminal data and extraluminal imaging
US10716528B2 (en) 2007-03-08 2020-07-21 Sync-Rx, Ltd. Automatic display of previously-acquired endoluminal images
US11064964B2 (en) 2007-03-08 2021-07-20 Sync-Rx, Ltd Determining a characteristic of a lumen by measuring velocity of a contrast agent
US8781193B2 (en) 2007-03-08 2014-07-15 Sync-Rx, Ltd. Automatic quantitative vessel analysis
JP5639764B2 (en) * 2007-03-08 2014-12-10 シンク−アールエックス，リミティド Imaging and tools for use with moving organs
US8473069B2 (en) * 2008-02-28 2013-06-25 Proteus Digital Health, Inc. Integrated circuit implementation and fault control system, device, and method
EP2303385B1 (en) * 2008-06-19 2013-12-11 Sync-RX, Ltd. Stepwise advancement of a medical tool
US20100094074A1 (en) * 2008-10-10 2010-04-15 Hologic Inc. Brachytherapy apparatus and methods employing expandable medical devices comprising fixation elements
US20100094075A1 (en) * 2008-10-10 2010-04-15 Hologic Inc. Expandable medical devices with reinforced elastomeric members and methods employing the same
US9095313B2 (en) 2008-11-18 2015-08-04 Sync-Rx, Ltd. Accounting for non-uniform longitudinal motion during movement of an endoluminal imaging probe
US11064903B2 (en) 2008-11-18 2021-07-20 Sync-Rx, Ltd Apparatus and methods for mapping a sequence of images to a roadmap image
US10362962B2 (en) 2008-11-18 2019-07-30 Synx-Rx, Ltd. Accounting for skipped imaging locations during movement of an endoluminal imaging probe
US8855744B2 (en) 2008-11-18 2014-10-07 Sync-Rx, Ltd. Displaying a device within an endoluminal image stack
US9101286B2 (en) 2008-11-18 2015-08-11 Sync-Rx, Ltd. Apparatus and methods for determining a dimension of a portion of a stack of endoluminal data points
US9974509B2 (en) 2008-11-18 2018-05-22 Sync-Rx Ltd. Image super enhancement
US9144394B2 (en) 2008-11-18 2015-09-29 Sync-Rx, Ltd. Apparatus and methods for determining a plurality of local calibration factors for an image
JP2012510340A (en) * 2008-12-02 2012-05-10 プロテウス バイオメディカル インコーポレイテッド Communication protocol suitable for the analyzer
EP2414036A4 (en) * 2009-04-02 2013-02-20 Proteus Digital Health Inc Method and apparatus for implantable lead
WO2010126503A1 (en) 2009-04-29 2010-11-04 Proteus Biomedical, Inc. Methods and apparatus for leads for implantable devices
WO2011011736A2 (en) 2009-07-23 2011-01-27 Proteus Biomedical, Inc. Solid-state thin film capacitor
US8718770B2 (en) 2010-10-21 2014-05-06 Medtronic, Inc. Capture threshold measurement for selection of pacing vector
US8355784B2 (en) 2011-05-13 2013-01-15 Medtronic, Inc. Dynamic representation of multipolar leads in a programmer interface
EP2863802B1 (en) 2012-06-26 2020-11-04 Sync-RX, Ltd. Flow-related image processing in luminal organs
CA2916140C (en) 2013-06-20 2021-04-20 Constantinos ANAGNOSTOPOULOS Intra-aortic balloon apparatus, assist devices, and methods for improving flow, counterpulsation, and haemodynamics
US20170000935A1 (en) 2014-01-27 2017-01-05 Children's Medical Center Corporation Mechanical assist device
US9623163B1 (en) 2016-02-11 2017-04-18 Michael Fischi Left ventricle heart-assist device
CN107412892B (en) * 2016-02-16 2021-04-16 上海微创医疗器械（集团）有限公司 Catheter sheath and ventricular assist circulation device
US10117982B2 (en) * 2016-04-15 2018-11-06 Guy P. Curtis And Frances L. Curtis Trust System and method for improving a heart muscle response
WO2018039461A1 (en) * 2016-08-24 2018-03-01 Nupulsecv, Inc. Blood pump assembly and method of use thereof
CN107158549A (en) * 2017-06-29 2017-09-15 吴强 For regulating and controlling left ventricle capacity to improve the servicing unit of Cardial pump function
CN109316641A (en) * 2018-11-06 2019-02-12 曾建新 A kind of artificial heart device
US11426563B2 (en) 2018-12-03 2022-08-30 Nxt Biomedical, Llc Blood pump or balloon cycling and venous occlusion
CN110559497B (en) * 2019-09-19 2024-02-09 厦门大学附属第一医院 Heart auxiliary stent balloon system, manufacturing method thereof and heart auxiliary device
JP2023511071A (en) * 2020-01-16 2023-03-16 エヌエックスティー バイオメディカル，エルエルシー Lymph Node Access, Drainage, and Shunting
EP4346670A4 (en) * 2021-06-01 2024-09-18 Mayo Found Medical Education & Res Methods and devices for electroporation for treatment of ventricular fibrillation
CN114681788B (en) * 2022-03-29 2023-08-29 南方医科大学珠江医院 Heart auxiliary circulation device and control method thereof
CN115591106B (en) * 2022-10-19 2024-08-20 北京工业大学 Functional mitral valve pump for relaxing dysfunction heart failure

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3791374A (en) * 1971-08-09 1974-02-12 Department Of Health Education Programmer for segmented balloon pump
US4685446A (en) * 1984-02-21 1987-08-11 Choy Daniel S J Method for using a ventricular assist device
US4771765A (en) * 1984-02-21 1988-09-20 Choy Daniel S J Heart assist device and method of use
US4809681A (en) * 1986-03-28 1989-03-07 Aisin Seiki Kabushiki Kaisha Electrocardiographic measurement method for controlling an intra-aortic balloon pump
US4861330A (en) * 1987-03-12 1989-08-29 Gene Voss Cardiac assist device and method

Family Cites Families (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US388510A (en) * 1888-08-28 Vaginal syringe
US2687131A (en) * 1952-09-17 1954-08-24 Davol Rubber Co Female incontinence catheter
US3509884A (en) * 1967-09-13 1970-05-05 William Bell Rectal balloon catheter
US3568659A (en) * 1968-09-24 1971-03-09 James N Karnegis Disposable percutaneous intracardiac pump and method of pumping blood
US3720200A (en) * 1971-10-28 1973-03-13 Avco Corp Intra-arterial blood pump
WO1980002366A1 (en) * 1979-05-07 1980-11-13 H Krause Method and apparatus for pumping blood within a vessel
SU1003845A1 (en) * 1981-05-07 1983-03-15 Научно-Исследовательский Институт Трансплантологии И Искусственных Органов Pump for artificial blood circulation
US4430076A (en) * 1982-02-04 1984-02-07 Harris James H Combined uterine injector and manipulative device
US4619247A (en) * 1983-03-31 1986-10-28 Sumitomo Electric Industries, Ltd. Catheter
US4689041A (en) * 1984-01-20 1987-08-25 Eliot Corday Retrograde delivery of pharmacologic and diagnostic agents via venous circulation
US4627837A (en) * 1984-05-30 1986-12-09 German Gonzalo Catheter device
US5021045A (en) * 1988-04-28 1991-06-04 Research Medical, Inc. Retrograde venous cardioplegia catheters and methods of use and manufacture

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3791374A (en) * 1971-08-09 1974-02-12 Department Of Health Education Programmer for segmented balloon pump
US4685446A (en) * 1984-02-21 1987-08-11 Choy Daniel S J Method for using a ventricular assist device
US4771765A (en) * 1984-02-21 1988-09-20 Choy Daniel S J Heart assist device and method of use
US4809681A (en) * 1986-03-28 1989-03-07 Aisin Seiki Kabushiki Kaisha Electrocardiographic measurement method for controlling an intra-aortic balloon pump
US4861330A (en) * 1987-03-12 1989-08-29 Gene Voss Cardiac assist device and method

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP0471029A4 *

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0604803A2 (en) * 1992-12-17 1994-07-06 Shlomo Gabbay Multi purpose perfusion cannula
EP0604803A3 (en) * 1992-12-17 1994-09-28 Shlomo Gabbay Multi purpose perfusion cannula.
WO2007090416A1 (en) * 2006-02-07 2007-08-16 Medicor Gmbh Medical vascular lock with blocking function
US10098644B2 (en) 2010-09-21 2018-10-16 Hocor Cardiovascular Technologies Llc Method and system for balloon counterpulsation during aortic valve replacement
EP2618782B1 (en) * 2010-09-21 2019-06-12 HOCOR Cardiovascular Technologies LLC System for balloon counterpulsation during aortic valve replacement
US10881412B2 (en) 2010-09-21 2021-01-05 Hocor Cardiovascular Technologies, Llc Method and system for balloon counterpulsation during aortic valve replacement
EP2981208A4 (en) * 2013-06-14 2017-01-04 Perfusion Solutions Pty Ltd Cardiac function evaluation system
WO2020087125A1 (en) 2018-10-31 2020-05-07 Griffith University Ventricular assistance system and method
NL2021903B1 (en) * 2018-10-31 2020-05-14 Univ Griffith Ventricular assistance system and method
EP3873555A4 (en) * 2018-10-31 2023-01-11 Griffith University Ventricular assistance system and method

Also Published As

Publication number Publication date
EP0471029A4 (en) 1993-07-28
CA2016103C (en) 2001-02-06
CA2016103A1 (en) 1990-11-05
DE69029730D1 (en) 1997-02-27
AU5732890A (en) 1990-11-29
EP0471029A1 (en) 1992-02-19
HK1008392A1 (en) 1999-05-07
US5176619A (en) 1993-01-05
DE69029730T2 (en) 1997-07-31
EP0471029B1 (en) 1997-01-15

Similar Documents

Publication Publication Date Title
EP0471029B1 (en) Heart-assist balloon pump
US4902272A (en) Intra-arterial cardiac support system
US3791374A (en) Programmer for segmented balloon pump
US3504662A (en) Intra-arterial blood pump
US4240409A (en) Apparatus for assisting circulation of blood
US8221303B2 (en) Intra-ventricular cardiac assist device and related method of use
US4546759A (en) Method and apparatus for assisting human heart function
US4861330A (en) Cardiac assist device and method
US6468200B1 (en) Segmented peristaltic intra-aortic balloon pump
US4690134A (en) Ventricular assist device
US6210318B1 (en) Stented balloon pump system and method for using same
US4531936A (en) Device and method for the selective delivery of drugs to the myocardium
US5308319A (en) Cardio assist system and insertion device therefor
US8784292B2 (en) Double balloon pump cardiac assist device and related method of use
US6669624B2 (en) Temporary heart-assist system
JPS62236532A (en) Electrocardiograph measuring method, balloon pump in aorta used therein and arrangement of said pump in aorta
JPH06510686A (en) Cardiac support device that can be implanted subcutaneously
JPS5867266A (en) Expansion device
US20080207986A1 (en) Heart assist device
WO2009035581A1 (en) Intra-aortic multi-balloon catheter for improving coronary and visceral perfusion
US6149578A (en) Piston-action intra-aortic coronary assist device
WO1999059653A1 (en) Coronary artery counterpulsation device and method
CN114259646A (en) Blood circulation auxiliary device and control system
JPH07265412A (en) Auxiliary circulating device for blood
JPH10174713A (en) Heart assisting device

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AU FI JP KR NO US

AL Designated countries for regional patents

Kind code of ref document: A1

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

WWE Wipo information: entry into national phase

Ref document number: 1990908338

Country of ref document: EP

WWP Wipo information: published in national office

Ref document number: 1990908338

Country of ref document: EP

WWG Wipo information: grant in national office

Ref document number: 1990908338

Country of ref document: EP