|Publication number||US3692018 A|
|Publication date||Sep 19, 1972|
|Filing date||Feb 11, 1970|
|Priority date||Feb 11, 1970|
|Publication number||US 3692018 A, US 3692018A, US-A-3692018, US3692018 A, US3692018A|
|Inventors||Lionel J Goetz, Robert H Goetz|
|Original Assignee||Lionel J Goetz, Robert H Goetz|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (5), Non-Patent Citations (1), Referenced by (115), Classifications (8)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United States Patent Goetz et al.
[541 CARDIAC ASSISTANCE DEVICE  Inventors: Robert H. Goetz; Lionel J. Goetz, both of 80 Vernon Drive, Scarsdale, NY. 10583 22 Filed: Feb.ll,1970
21 App1.No.: 10,452
I Coronary Artery Aortic I Volve I ll 1 I l ';-i 7 l 74 :1 1 I [151 3,692,018 51 Sept. 19, 1972 3,505,987 4/l970 Heilman 128/1 R FOREIGN PATENTS OR APPLICATIONS 15,864 7/1912 France ..l28/344 OTHER PUBLICATIONS Laird et al. Trans. Amer. Soc. Artif. Int. Organs. Vol. XIV, 1968 pp. 338- 342 Primary Examiner-Dalton L. Truluck Attorney-Pennie, Edmonds, Morton, Taylor and Adams [5 7 ABSTRACT A cardiac assistance device is disclosed which produces a uni-directional pumping action assisting the heart when the device is activated after it has been introduced into a blood vessel by conventional surgical procedures.
8 Claims, 5 Drawing Figures PATENTED SEP 19 I 3 6 92.018
sum 2 OF 2 Cororid Arrery Femovol Artery INVENTORS ROBERT H. GOETZ BY LIONEL JVGOETZ ATTORNEYS BACKGROUND OF THE INVENTION Heart failure is medically defined, in its broadest sense, as the inability of the heart to pump blood throughout the body. For purposes of describing the present invention a failing heart is defined as one that is not sufficiently healthy to pump blood at the rate needed to maintain adequate blood flow and continued well-being of its owner but which is nevertheless, capable of pumping some blood.
A cardiac assistance device is one that aids a failing heart. One presently known device .used for this purpose comprises a single inflatable balloon which is adapted to be inserted into an appropriate blood vessel, as for example, the aorta. When such a device is inflated and deflated, a pumpingaction within theblood vessel occurs and when the inflation and deflation cycle is appropriately timed to the heartbeat, the device acts to assist the failing heart.
While this type of cardiac assistance device has significantly contributed to the progress of medical science, it is inherently inefficient. This is due to the fact that the balloon acts as an omni-directional pump thus making it impossible to direct its force in a single direction so that blood is pumped only to those regions of h the body where adequate blood flow is most critical as for example, to the brain and the muscles of the heart itself.
SUMMARY OF THE INVENTION In accordance with the teachings of the present invention a cardiac assistance device is provided which is constructed to create an artificially induced unidirectional pumping action, within a blood vessel of the patient to aid the failing heart. In construction, the device includes an inflatable occluding chamber and one or more inflatable pumping chambers disposed on one side of the occluding chamber in communicating relationship therewith. The occluding and pumping chambers are adapted to be inserted into the blood vessel of the patient and both are inflated and deflated on a cyclical basis out of phase with the beat of the failing heart but sequentially with respect to each other by a pneumatic power source positioned externally of the patient.
The occluding chamber has a diameter greater than the diameter of the blood vessel within which it lies so that when inflated it occludes the blood vessel. Since the occluding chamber is inflated before the pumping chamber, the pressure created in the blood vessel when the pumping chamber is later inflated causes the blood to flow in a single direction away from point of occlusion between the inflated occluding chamber and the wall of the blood vessel. Thus the cardiac assistance device of the present invention acts as a uni-directional pump and when properly positioned the direction of blood flow created by the device can be effectively controlled according to the dictates of sound medical practice to be most beneficial to the patient.
BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a cross-sectional view of the cardiac assistance device of this invention disposed within a blood vessel.
FIG. 2 is a cross-sectional view of the cardiac assistance device of this invention disposed within a blood vessel showing an alternative embodiment of the structure within the occluding chamber.
FIGS. 3 and 4 are elevation views of the cardiac assistance device of this invention showing progressive stages of the operation of the device.
FIG. 5 is a diagrammatic illustration of a human heart showing the placement of thecardiac assistance device within the aorta.
DETAILED DESCRIPTION OF THE INVENTION As shown in FIG. 1, the cardiac assistance device includes a pumping structure indicated generally by reference numeral 10 which is adapted to be inserted within a blood vessel 2 of the patient by conventional surgical procedures. The pumping structure is specially constructed to produce auni-directional flow of blood within the blood vessel. For this purpose the pumping structure operates to first occlude the blood vessel and then to create pressure within the blood vessel on one side of the point of occlusion to thereby cause the blood within the vessel to flow in one direction away from the point of occlusion. In construction, the pumping structure includes expansion means for internally occluding the blood vessel and blood moving means positioned on one side of the expansion means for displacing blood onthat side of the expansion means. As shown, the expansion means comprises an inflatable occluding chamber 3 and the blood moving means comprises one or more inflatable pumping chambers 4 which communicate in series with the occluding chamber. The occluding chamber 3 and the pumping chamber 4 are defined by a balloon structure which consists of a balloon member 5 mounted on a tubular conduit 6 extending longitudinally through the balloon member 5. Each end of the balloon is disposed in fluidgas tight relationship about the tubular conduit by suitable sealing means as for example, silk threads 7 tied tightly about the terminal ends of the balloon member. As shown, an intermediate portion of the balloon member 5 is held against expansion in fluid-gas tight relationship to the tubular conduit 6 by silk threads 7' similar to the ones used for sealing each end of the balloon member. A metallic pellet 13 seals the end of the tubular conduit at a point located near the end of the pumping chamber 4 remote from the occluding chamber. The use of a metallic pellet for this pur pose advantageously permits the position of the pumping structure within the blood vessel to be visually monitored by the use of standard X-ray techniques after it has been introduced into the patient.
The balloon member 5 and the tubular conduit are made of nonthrombogenic material so that the danger of blood clotting is eliminated. Also the silk sealing threads are coated with a nonthrombogenic material and the assembled pumping structure is dipped into a bath of molten nonthrombogenic material. An example of nonthrombogenic material is polyurethane. In addition to being nonthrombogenic, the balloon member is also inelastic or nonstretchable so that the danger of fatigue failure due to stretching when the balloon member is repeatedly inflated and deflated is avoided. In other words, no stretching of the balloon member occurs when it is inflated. Rather the balloon merely expands upon inflation to its natural but relaxed inflated state.
The tubular conduit serves a dual purpose. First, it acts to hold the pumping chamber on one side of the occluding chamber as the balloon structure is introduced into the patient thus preventing the balloon structure from folding back on itself. Secondly, the tubular conduit provides a convenient means for introducing gas or fluid into the balloon structure to inflate the occluding and pumping chambers. For the latter purpose those portions of the tubular conduit which extend through the occluding and pumping chambers are provided with a series of perforations 8 which permit air flow into and out of the occluding and pumping chambers. In the presently preferred embodiment of this invention, the tubular conduit has a diameter of approximately 2-3 millimeters and the perforations are approximately 1 millimeter in diameter.
The occluding chamber of the balloon has a size such as when inflated the blood vessel is internally occluded. The blood vessel is occluded by the inflated occluding chamber in the sense that a complete occlusion of the blood vessel is produced causing stoppage of the blood stream and accumulation of the pressure within the blood vessel. The pumping chamber on the other hand is slightly smaller in size than the occluding chamber and when inflated the pumping chamber acts only to increase the pressure within the blood vessel. In other words, flow of blood past the inflated pumping chamber is not prevented but blood flow past the inflated occluding chamber is prevented. In the construction shown in the drawing, the occluding chamber is substantially spherical in shape while the single pumping chamber shown is substantially cylindrical in shape. Since the construction shown in the drawing is intended for insertion within the aorta of the patient which for the average patient has an inside diameter of approximately 18-22 millimeters, it is preferred that the spherical occluding chamber be slightly greater than 22 millimeters in diameter in its inflated state and that the pumping chamber have an inflated size of approximately 16 millimeters in diameter.
The occluding and pumping chamber of the balloon are alternately inflated and deflated at a cycle which is out of phase with the heartbeat of the patient. That is, when the heart is relaxed, the chambers of the balloon are inflated and when the heart is pumping these chambers are deflated. For this purpose a pneumatic power source indicated diagrammatically by reference numeral 11 in FIG. is provided. The pneumatic power source is of conventional construction having the capability of creating alternating positive and negative pressure as triggered by the electrocardiogram of the patient. As shown, the pumping machine is connected to the balloon structure via the tubular conduit 6. A suitable pumping machine for practicing the teachings of the present invention is the pneumatic pumping machine produced by the Datascope Company of New Jersey.
In order to provide uni-directional pumping action, the occluding chamber of the balloon structure is inflated prior to inflation of the pumping chamber. For this purpose an obstruction member 9 is provided. The obstruction member acts to divert the flow of gas within the balloon structure in a manner which produces sequential inflation of the occluding and pumping chambers. As shown the obstruction member is disposed within that portion of the tubular conduit extending through the occluding chamber 3 at a point located between two adjacent perforations 8' and 8". With this arrangement, gas supplied from the pneumatic power source is temporarily diverted from the tubular conduit into the occluding chamber through the perforations 8" disposed upstream of the obstruction member. This diversion is due to the presence of the obstruction member which prevents uninterrupted flow of gas through the tubular conduit. When the occluding chamber has reached a fully inflated configuration as shown in FIG. 4, the gas reenters the tubular conduit through the perforations 8' disposed downstream of the obstruction member. From this point the gas flows into the pumping chamber through the perforations disposed in the portion of the tubular conduit extending within the pumping chamber. Thereby the pumping chamber is brought to a fully inflated condition as shown in FIG. 1. Thus it will be seen that the occluding chamber and pumping chambers are repeatedly cycled in a sequential fashion from the configuration shown in FIG. 3 where both chambers are collapsed to the configuration shown in FIG. 4 where the occluding chamber is inflated and the pumping chamber deflated and finally to the configuration shown in FIG. 1 wherein both chambers are inflated causing blood within the vessel to flow in the direction of arrows 14 away from the point of occlusion in the vessel created by the inflated occluding chamber. With the solid obstruction member it will be recognized that deflation of the occluding chamber also occurs in a sequential manner. In other words, during the deflation phase a reverse flow of air out of the balloon is created first from the occluding chamber through the perforations 8' and then from the pumping chamber. The path of exit from the pumping chamber leads into the conduit 6 through the perforations disposed in the portion of the conduit 6 located within the pumping chamber and then into the occluding chamber via the perforations 8 and finally back into the tubular conduit through the perforations 8" and out of the balloon structure.
The occluding and pumping chambers may advantageously be deflated substantially simultaneously by replacing the solid obstruction member with a oneway valve such as the ball valve 12 shown in FIG. 2. With this arrangement, the ball valve is closed during the inflation cycle thereby producing the same pattern of air flow as is produced with the solid obstruction member shown in FIG. 1. However, on the deflation cycle, the ball valve is opened thus permitting air to be withdrawn from the occluding and pumping chambers through all the perforations in those portions of the tubular conduit disposed within these chambers at substantially the same time. Simultaneous deflation of the occluding and pumping chambers is advantageous since very little time is consumed between successive beats of the heart. Thus the possibility that the pumping structure will pulsate in appropriate coordination with the heartbeat is thereby greatly enhanced.
One application for the cardiac assistance device of the present invention is sown in FIG. 5. For this application the pumping structure section of the device is inserted into the femoral artery at a point below the bifurcation in the aorta and pushed upward into the aorta to the position shown. In this position the device acts to direct a flow of blood toward the heart into the coronary artery which supplies blood to the heart muscles and also into the carotid arteries which supply blood to the brain. Blood pumped by the cardiac assistance device is prevented from reentering the heart chamber by the aortic valve. It will be recognized that this particular use of the device is particularly beneficial since an adequate supply of blood to these critical organs is insured.
We claim: 1. A cardiac assistance device comprising: a. a pump structure adapted to be inserted into a blood vessel of a patient, said blood structure having an elongated support means with an insertable end;
1. expansion means on said support means for occluding the blood vessel;
2. blood moving means positioned on one side of the expansion means on said support means adjacent said insertable end for displacing blood within the vessel on said one side;
3. means for sequentially activating the expansion means and blood moving means in that order to produce a uni-directional flow of blood within the blood vessel away from the point of occlusion and toward the heart, and
b. means for alternately activating and deactivating the expansion means and to produce moving means on a cycle out of phase with the pumping action of the heart.
2. The cardiac assistance device according to claim 1 wherein:
a. the expansion means comprises an inflatable occluding chamber; and
b. the blood moving means comprises at least one inflatable pumping chamber communicating with the occluding chamber.
3. The cardiac assistance device according to claim 2 wherein:
a. the occluding chamber and pumping chamber are troduced into the patient.
4. The cardiac assistance device according to claim 3 wherein:
a. the holding means comprises a tubular conduit extending through the balloon member, said balloon member being held in sealed relationship about said conduit at each end thereof and at said intermediate point along its length; and
b. the means for activating the occluding and pumping chambers comprises a pneumatic power source operatively connected to the: tubular conduit for alternately pressurizing and depressurizing the balloon member to inflate and deflate it respectively;
c. 33: portion of the tubular conduit extending through the balloon member has a series of perforations permitting flow of air into and out of the balloon member during the inflation and deflation I phases respectively.
5. The cardiac assistance device according to claim 4 wherein:
a. the means for sequentially inflating the occluding and pumping chambers comprises means for temporarily diverting the flow of air through the tubu lar conduit into the occluding chamber prior to entrance into the pumping chamber.
6. The cardiac assistance device according to claim 5 wherein:
a. the means for diverting the flow of air through the tubular conduit comprises an obstruction member disposed within the portion of the tubular conduit extending through the occluding chamber at a point located between two adjacent perforations of said conduit portion.
7. The cardiac assistance device according to claim 5 wherein:
a. the means for diverting the flow of air through the
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3266487 *||Jun 4, 1963||Aug 16, 1966||Sundstrand Corp||Heart pump augmentation system and apparatus|
|US3504662 *||May 16, 1967||Apr 7, 1970||Avco Corp||Intra-arterial blood pump|
|US3505987 *||Mar 17, 1967||Apr 14, 1970||Medrad Inc||Intra-aortic heart pump|
|US3592183 *||May 27, 1969||Jul 13, 1971||Watkins David H||Heart assist method and apparatus|
|FR15864E *||Title not available|
|1||*||Laird et al. Trans. Amer. Soc. Artif. Int. Organs. Vol. XIV, 1968 pp. 338 342|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3877838 *||Aug 9, 1973||Apr 15, 1975||Choy Daniel S J||Device for advancing material through a tube|
|US3939820 *||Oct 29, 1974||Feb 24, 1976||Datascope Corporation||Single-chamber, multi-section balloon for cardiac assistance|
|US4015590 *||Apr 12, 1976||Apr 5, 1977||Baylor College Of Medicine||Balloon activated blood pump|
|US4034742 *||Jan 23, 1976||Jul 12, 1977||Thoma Dipl Ing Dr Techn Herwig||Apparatus for mechanically assisting circulation of the blood in the human body|
|US4077394 *||Aug 25, 1976||Mar 7, 1978||Mccurdy Martin D||Integral pressure sensor probe for a cardiac assistance device|
|US4154227 *||Oct 11, 1977||May 15, 1979||Krause Horst E||Method and apparatus for pumping blood within a vessel|
|US4261339 *||Mar 6, 1978||Apr 14, 1981||Datascope Corp.||Balloon catheter with rotatable support|
|US4276874 *||Nov 15, 1978||Jul 7, 1981||Datascope Corp.||Elongatable balloon catheter|
|US4292974 *||Jan 30, 1980||Oct 6, 1981||Thomas J. Fogarty||Dilatation catheter apparatus and method|
|US4327709 *||Oct 18, 1979||May 4, 1982||Datascope Corp.||Apparatus and method for the percutaneous introduction of intra-aortic balloons into the human body|
|US4328811 *||Jul 28, 1980||May 11, 1982||Fogarty Thomas J||Calibrating dilation catheter|
|US4346698 *||May 20, 1980||Aug 31, 1982||Datascope Corp.||Balloon catheter with rotatable support|
|US4522195 *||Jun 13, 1983||Jun 11, 1985||Peter Schiff||Apparatus for left heart assist|
|US4527549 *||Sep 30, 1982||Jul 9, 1985||Shelhigh Inc.||Method of and means for intraaortic assist|
|US4531936 *||Jan 12, 1983||Jul 30, 1985||Gordon Robert T||Device and method for the selective delivery of drugs to the myocardium|
|US4546759 *||Jul 29, 1983||Oct 15, 1985||Mladen Solar||Method and apparatus for assisting human heart function|
|US4697574 *||Feb 20, 1986||Oct 6, 1987||Medicorp Research Laboratories Corp.||Pump for assistance in circulation|
|US4733652 *||Jul 15, 1987||Mar 29, 1988||Aisin Seiki Kabushiki Kaisha||Intra-aortic balloon|
|US4861330 *||Mar 12, 1987||Aug 29, 1989||Gene Voss||Cardiac assist device and method|
|US4896670 *||Apr 19, 1988||Jan 30, 1990||C. R. Bard, Inc.||Kissing balloon catheter|
|US4902272 *||Jun 17, 1987||Feb 20, 1990||Abiomed Cardiovascular, Inc.||Intra-arterial cardiac support system|
|US4934996 *||Jan 31, 1986||Jun 19, 1990||Boston Scientific Corporation||Pressure-controlled intermittent coronary sinus occlusion apparatus and method|
|US4969470 *||Oct 4, 1989||Nov 13, 1990||Boston Scientific Corporation||Heart analysis using pressure-controlled intermittent coronary sinus occlusion|
|US5100382 *||Oct 24, 1988||Mar 31, 1992||Valtchev Konstantin L||Single channel balloon uterine injector|
|US5222980 *||Sep 27, 1991||Jun 29, 1993||Medtronic, Inc.||Implantable heart-assist device|
|US5395330 *||Sep 4, 1992||Mar 7, 1995||Dlp, Inc.||Auto-inflating catheter cuff|
|US5738652 *||Jan 17, 1997||Apr 14, 1998||Heartport, Inc.||Retrograde delivery catheter and method for inducing cardioplegic arrest|
|US5755687 *||Apr 1, 1997||May 26, 1998||Heartport, Inc.||Methods and devices for occluding a patient's ascending aorta|
|US5765568 *||Dec 1, 1995||Jun 16, 1998||Heartport, Inc.||Catheter system and method for venting the left ventricle|
|US5769812 *||Oct 16, 1996||Jun 23, 1998||Heartport, Inc.||System for cardiac procedures|
|US5792094 *||Sep 28, 1995||Aug 11, 1998||Heartport, Inc.||Method of delivering cardioplegic fluid to a patient's heart|
|US5800375 *||Dec 20, 1995||Sep 1, 1998||Heartport, Inc.||Catheter system and method for providing cardiopulmonary bypass pump support during heart surgery|
|US5810757 *||Dec 1, 1995||Sep 22, 1998||Heartport, Inc.||Catheter system and method for total isolation of the heart|
|US5885238 *||May 30, 1995||Mar 23, 1999||Heartport, Inc.||System for cardiac procedures|
|US5913842 *||Feb 11, 1998||Jun 22, 1999||Heartport, Inc.||Retrograde delivery catheter and method for inducing cardioplegic arrest|
|US5980448 *||Jan 28, 1998||Nov 9, 1999||Vascor, Inc.||Single chamber blood pump|
|US6056723 *||May 22, 1998||May 2, 2000||Heartport, Inc.||Methods and devices for occluding a patient's ascending aorta|
|US6066085 *||Jul 22, 1999||May 23, 2000||Vascor, Inc.||Single chamber blood pump|
|US6159178 *||Jan 23, 1998||Dec 12, 2000||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|
|US6190304||Jul 13, 1999||Feb 20, 2001||University Of North Texas Health Science Center At Fort Worth||Enhanced intra-aortic balloon assist device|
|US6200260||Oct 2, 1998||Mar 13, 2001||Fore Flow Corporation||Implantable heart assist system|
|US6248086||Feb 23, 1998||Jun 19, 2001||Heartport, Inc.||Method for cannulating a patient's aortic arch and occluding the patient's ascending aortic arch|
|US6293920||Oct 7, 1998||Sep 25, 2001||Heartport, Inc.||Catheter system and method for providing cardiopulmonary bypass pump support during heart surgery|
|US6299575||Apr 25, 2000||Oct 9, 2001||Orqis Medical Corporation||Implantable heart assist system|
|US6387037||Dec 23, 1999||May 14, 2002||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US6390969||Apr 21, 2000||May 21, 2002||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US6398752||Jun 5, 1998||Jun 4, 2002||William P. Sweezer, Jr.||Method of occluding a patient's ascending aorta and delivery cardioplegic fluid|
|US6423031||Nov 1, 1999||Jul 23, 2002||Brian S. Donlon||Methods and devices for occluding a patient's ascending aorta|
|US6428464||Apr 9, 1999||Aug 6, 2002||Orqis Medical Corporation||Implantable heart assist system|
|US6468200 *||Mar 6, 2000||Oct 22, 2002||Michael C. Fischi||Segmented peristaltic intra-aortic balloon pump|
|US6482171||Jan 13, 1997||Nov 19, 2002||Heartport, Inc.||Multi-lumen catheter|
|US6589206||Oct 10, 2000||Jul 8, 2003||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|
|US6610004||Feb 15, 2002||Aug 26, 2003||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US6635046 *||Mar 20, 2000||Oct 21, 2003||Coaxia, Inc.||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US6685621||Jun 11, 2002||Feb 3, 2004||Orois Medical Corporation||Implantable heart assist system and method of applying same|
|US6743196||Apr 24, 2001||Jun 1, 2004||Coaxia, Inc.||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US6767345||Nov 8, 2002||Jul 27, 2004||Coaxia, Inc.||Partial aortic occlusion devices and methods for renal and coronary perfusion augmentation|
|US6796992||Apr 11, 2003||Sep 28, 2004||Coaxia, Inc.||Cerebral perfusion augmentation|
|US6889082||Nov 6, 2002||May 3, 2005||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US6902556||Jun 5, 2002||Jun 7, 2005||Heartport, Inc.||Methods and devices for occluding the ascending aorta and maintaining circulation oxygenated blood in the patient when the patient's heart is arrested|
|US7125376||Apr 7, 2003||Oct 24, 2006||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US7144365||Dec 5, 2003||Dec 5, 2006||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US7150736||Jan 24, 2005||Dec 19, 2006||Coaxia, Inc.||Cerebral perfusion augmentation|
|US7166097||Sep 22, 2004||Jan 23, 2007||Coaxia, Inc.||Cerebral perfusion augmentation|
|US7331921||Jun 28, 2004||Feb 19, 2008||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US7445592||Jun 10, 2004||Nov 4, 2008||Orqis Medical Corporation||Cannulae having reduced flow resistance|
|US7458929||May 3, 2005||Dec 2, 2008||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US7468027||Oct 21, 2005||Dec 23, 2008||Coaxia, Inc.||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US7468050 *||Dec 24, 2003||Dec 23, 2008||L. Vad Technology, Inc.||Long term ambulatory intra-aortic balloon pump|
|US7513863||Jun 28, 2004||Apr 7, 2009||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US7588530||Jul 19, 2005||Sep 15, 2009||Marlin Stephen Heilman||Devices, systems and methods for assisting blood flow|
|US7588531||May 3, 2006||Sep 15, 2009||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US7591778||May 3, 2006||Sep 22, 2009||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US7614997||May 3, 2006||Nov 10, 2009||Orqis Medical Corporation||Implantable heart assist system and method of applying same|
|US7867195||Jan 24, 2005||Jan 11, 2011||Coaxia, Inc.||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US7927268||Oct 16, 2007||Apr 19, 2011||Coaxia, Inc.||Counterpulsation device with increased volume-displacement efficiency and methods of use|
|US7993260||Nov 10, 2009||Aug 9, 2011||Thoratec Corporation||Implantable heart assist system and method of applying same|
|US7993324||Jun 3, 2009||Aug 9, 2011||Coaxia, Inc.||Cerebral perfusion augmentation|
|US8066628||Oct 22, 2010||Nov 29, 2011||Nupulse, Inc.||Intra-aortic balloon pump and driver|
|US8323174||Nov 18, 2011||Dec 4, 2012||Nupulse, Inc.||Skin interface for ventricular assist device|
|US8326421||Feb 21, 2012||Dec 4, 2012||Nupulse, Inc.||Ventricular assist device|
|US8608637||Jan 12, 2012||Dec 17, 2013||Nupulse, Inc.||Internal drive line for ventricular assist device|
|US8684905||Feb 21, 2012||Apr 1, 2014||Nupulse, Inc.||Intra-aortic balloon pump assembly for ventricular assist device|
|US8876686||Feb 9, 2012||Nov 4, 2014||Vascor, Inc||Control of blood flow assist systems|
|US8888740||Jan 10, 2011||Nov 18, 2014||Zoll Circulation, Inc.||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US8900115||Jul 1, 2011||Dec 2, 2014||Thoratec Corporation||Implantable heart assist system and method of applying same|
|US9387284||Oct 21, 2014||Jul 12, 2016||Vascor, Inc||Control of blood flow assist systems|
|US20020115982 *||Jan 18, 2002||Aug 22, 2002||Coaxia, Inc.||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US20030069468 *||Nov 6, 2002||Apr 10, 2003||Bolling Steven F.||Implantable heart assist system and method of applying same|
|US20040220521 *||May 27, 2004||Nov 4, 2004||Barbut Denise R.||Partial aortic occlusion devices and methods for renal perfusion augmentation|
|US20050085685 *||Sep 22, 2004||Apr 21, 2005||Coaxia, Inc.||Cerebral perfusion augmentation|
|US20050124849 *||Jan 24, 2005||Jun 9, 2005||Barbut Denise R.||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US20050159640 *||Jan 24, 2005||Jul 21, 2005||Coaxia, Inc.||Cerebral perfusion augmentation|
|US20060014999 *||Jul 19, 2005||Jan 19, 2006||Heilman Marlin S||Devices, systems and methods for assisting blood flow|
|US20060047262 *||Oct 21, 2005||Mar 2, 2006||Barbut Denise R||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US20060270892 *||May 3, 2006||Nov 30, 2006||Bolling Steven F||Implantable heart assist system and method of applying same|
|US20060276681 *||May 3, 2006||Dec 7, 2006||Bolling Steven F||Implantable heart assist system and method of applying same|
|US20070118095 *||Jan 19, 2007||May 24, 2007||Coaxia, Inc.||Cerebral perfusion augmentation|
|US20070135793 *||Jan 18, 2007||Jun 14, 2007||Coaxia, Inc.||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|US20070239135 *||Jan 19, 2007||Oct 11, 2007||Coaxia, Inc.||Cerebral perfusion augmentation|
|US20090099516 *||Nov 7, 2005||Apr 16, 2009||Gildoni Zvi M||Apparatus and method for direct organ perfusion|
|US20090247884 *||Jun 3, 2009||Oct 1, 2009||Barbut Denise R||Cerebral perfusion augmentation|
|US20100211008 *||Feb 7, 2006||Aug 19, 2010||Egon Wiest||Medical Vascular Lock With Blocking Function|
|US20110106132 *||Jan 10, 2011||May 5, 2011||Barbut Denise R||Partial aortic occlusion devices and methods for cerebral perfusion augmentation|
|CN104174078B *||Sep 15, 2014||Sep 21, 2016||靳立军||一种左心室辅助装置|
|DE2915089A1 *||Apr 12, 1979||Oct 30, 1980||Datascope Corp||Ballonkatheder|
|DE102005004663B4 *||Feb 2, 2005||Jul 23, 2009||Medicor Gmbh||Medizinische Gefń▀schleuse mit Blockungsfunktion|
|EP0192574A1 *||Feb 19, 1986||Aug 27, 1986||Medicorp Research Laboratories Corporation||Circulatory and coronary intra-aortic balloon assistance pump|
|EP0194338A2 *||Jul 5, 1985||Sep 17, 1986||Shelhigh, Inc.||Method of and means for intraaortic assist|
|EP0209070A2 *||Jul 9, 1986||Jan 21, 1987||ABIOMED, INC. ( a Delaware Corporation)||High frequency intra-arterial cardiac support system|
|EP0209070A3 *||Jul 9, 1986||Jul 20, 1988||ABIOMED, INC. ( a Delaware Corporation)||High frequency intra-arterial cardiac support system|
|WO1980002366A1 *||May 7, 1979||Nov 13, 1980||H Krause||Method and apparatus for pumping blood within a vessel|
|WO1981002110A1 *||Jan 29, 1981||Aug 6, 1981||T Fogarty||Dilatation catheter apparatus and method|
|WO1982000409A1 *||Jul 24, 1981||Feb 18, 1982||T Fogarty||Calibrating dilatation catheter method and apparatus|
|WO2006048883A3 *||Nov 7, 2005||Oct 26, 2006||Drops Ltd||Apparatus and method for direct organ perfusion|
|U.S. Classification||600/18, 417/475, 417/389, 604/914|
|Cooperative Classification||A61M1/1072, A61M2025/1052|