Viole, Anthony (Foothill Ranch, CA, US)
Sirimanne, Laksen (Irvine, CA, US)
Bolling, Steven F. (Ann Arbor, MI, US)
O'leary, Shawn (Mission Viejo, CA, US)
Pecor, Robert (Aliso Viejo, CA, US)
Kelly, Ryan (San Diego, CA, US)
Werner, Wolfgang (Carlsbad, CA, US)
Beizai, Masoud (Laguna Hills, CA, US)

Plaque It! Sponsored by: Flash of Genius

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02/19/2008

06/28/2004

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Orqis Medical Corporation (Lake Forest, CA, US)

600/16

A61M1/12

2876769	Apparatus for oxygenating, centrifuging and changing the temperature of blood	March, 1959	Cordova
2935068	Surgical procedure and apparatus for use in carrying out the same	May, 1960	Donaldson
3017885	Blood flow meter	January, 1962	Robicsek
3410263	Blood-pumping apparatus provided with heart synchronizing means	November, 1968	McGinnis
3592184	HEART ASSIST METHOD AND CATHETER	July, 1971	Watkins et al.
3692018	CARDIAC ASSISTANCE DEVICE	September, 1972	Goetz et al.
3835864	INTRA-CARDIAC STIMULATOR	September, 1974	Rasor et al.
3885251	Artificial heart pump or assist	May, 1975	Pedrosa
3938530	Catheter	February, 1976	Santomieri
3939820	Single-chamber, multi-section balloon for cardiac assistance	February, 1976	Grayzel
3964479	Extracorporeal blood circulation system and drip chamber with adjustable blood level	June, 1976	Boag et al.
4000739	Hemostasis cannula	January, 1977	Stevens
4004299	Cardiac replacement and assist devices	January, 1977	Runge
4034742	Apparatus for mechanically assisting circulation of the blood in the human body	July, 1977	Thoma
4047849	Pneumatic pulsator pumping system with pulsator fluid venting valve	September, 1977	Clay
4051840	Dynamic aortic patch	October, 1977	Kantrowitz et al.
4077394	Integral pressure sensor probe for a cardiac assistance device	March, 1978	McCurdy
4080958	Apparatus for aiding and improving the blood flow in patients	March, 1978	Bregman et al.
4134402	Double lumen hemodialysis catheter	January, 1979	Mahurkar
4135496	Extracorporeal circulation apparatus	January, 1979	Chazov et al.
4143616	Process machinery control system and individual safety control systems therefor or the like	March, 1979	Bible
4154227	Method and apparatus for pumping blood within a vessel	May, 1979	Krause et al.
4167046	Blood pumping device	September, 1979	Portner et al.
4240409	Apparatus for assisting circulation of blood	December, 1980	Robinson et al.
4302854	Electrically activated ferromagnetic/diamagnetic vascular shunt for left ventricular assist	December, 1981	Runge
4375941	Method and apparatus for pumping blood	March, 1983	Child
4384829	Pump and actuator mechanism	May, 1983	Conely et al.
4385631	Catheter	May, 1983	Uthmann
4405313	Figure-eight, dual-lumen catheter and method of using	September, 1983	Sisley et al.
4407271	Apparatus for left heart assist	October, 1983	Schiff
4411655	Apparatus and method for percutaneous catheterization	October, 1983	Schreck
4447236	Infusion catheter system	May, 1984	Quinn
4457673	Pump and actuator mechanism	July, 1984	Conley et al.
4459977	Coronary sinus retroperfusion apparatus for the treatment of myocardial ischemia	July, 1984	Pizon et al.
4464164	Flowrate control for a blood flow system	August, 1984	Troutner et al.
4522195	Apparatus for left heart assist	June, 1985	Schiff
4540402	Double perfusion catheter	September, 1985	Aigner
4543087	Double lumen catheter tip	September, 1985	Sommercom et al.
4546759	Method and apparatus for assisting human heart function	October, 1985	Solar
4552552	Pump system for use with dialysis and like apparatus	November, 1985	Polaschegg et al.
4569332	Method and apparatus for treating a heart patient through the coordinating efforts of balloon pumping and dispensing catheters	February, 1986	Schiff et al.
4573997	Right ventricular assist device	March, 1986	Wisman et al.
4611578	Redundant piston pump for the operation of single or multiple chambered pneumatic blood pumps	September, 1986	Heimes
4625712	High-capacity intravascular blood pump utilizing percutaneous access	December, 1986	Wampler
4666443	Biventricular circulatory assist system and method	May, 1987	Portner
4685446	Method for using a ventricular assist device	August, 1987	Choy
4688998	Magnetically suspended and rotated impellor pump apparatus and method	August, 1987	Olsen et al.
4690134	Ventricular assist device	September, 1987	Snyders
4692141	Double lumen catheter	September, 1987	Mahurkar
4697574	Pump for assistance in circulation	October, 1987	Karcher et al.
4719921	Cardiac pacemaker adaptive to physiological requirements	January, 1988	Chirife
4756302	Blood pumping system and method	July, 1988	Portner et al.
4759760	Cardiovascular pump system	July, 1988	Snapp, Jr.
4771765	Heart assist device and method of use	September, 1988	Choy et al.
4798591	Catheter obturator	January, 1989	Okada
4822357	Auxiliary artificial heart	April, 1989	Forster et al.
4838889	Ventricular assist device and method of manufacture	June, 1989	Kolff
4857062	Catheter introducer valve	August, 1989	Russell
4861330	Cardiac assist device and method	August, 1989	Voss
4872874	Method and apparatus for transarterial aortic graft insertion and implantation	October, 1989	Taherin
4883462	Blood extraction assist apparatus and method	November, 1989	Williamson et al.
4895150	Implanted power source	January, 1990	Isaacson et al.
4902272	Intra-arterial cardiac support system	February, 1990	Milder et al.
4902273	Heart assist device	February, 1990	Choy et al.
4906229	High-frequency transvalvular axisymmetric blood pump	March, 1990	Wampler
4908012	Chronic ventricular assist system	March, 1990	Moise et al.
4925452	Multiple conduit drainage device	May, 1990	Melinyshyn et al.
4927407	Cardiac assist pump with steady rate supply of fluid lubricant	May, 1990	Dorman
4944745	Perfusion balloon catheter	July, 1990	Sogand et al.
4957504	Implantable blood pump	September, 1990	Chardack
4968293	Circulatory assist device	November, 1990	Nelson
4976270	Apparatus for continuously sampling plasma	December, 1990	Parl et al.
4985014	Ventricular venting loop	January, 1991	Orejola
4994078	Intraventricular artificial hearts and methods of their surgical implantation and use	February, 1991	Jarvik
4995856	Ventriculostomy reservoir	February, 1991	Heindl et al.
4995857	Left ventricular assist device and method for temporary and permanent procedures	February, 1991	Arnold
4995865	Multi-lumen catheters	February, 1991	Gahara et al.
5011469	Peripheral cardiopulmonary bypass and coronary reperfusion system	April, 1991	Buckberg et al.
5020516	Circulatory assist method and apparatus	June, 1991	Biondi et al.
5041098	Vascular access system for extracorporeal treatment of blood	August, 1991	Loiterman et al.
5059167	Retroperfusion and retroinfusion control apparatus, system and method	October, 1991	Lundquist et al.
5066285	Catheter introducer sheath made of expanded polytetrafluoroethylene	November, 1991	Hillstead
5069662	Cancer treatment	December, 1991	Bodden
5087247	Balloon perfusion catheter	February, 1992	Horn et al.
5089017	Drive system for artificial hearts and left-ventricular assist devices	February, 1992	Young et al.
5092844	Intracatheter perfusion pump apparatus and method	March, 1992	Schwartz et al.
5098370	Heart assist device	March, 1992	Rahat et al.
5114408	Universal hemostasis valve having improved sealing characteristics	May, 1992	Fleischhaker et al.
5116564	Method of producing a closing member having flexible closing elements, especially a heart valve	May, 1992	Jansen et al.
5129878	Auxiliary circulation apparatus and method of its driving	July, 1992	Takano et al.
5129883	Catheter	July, 1992	Black
5131905	External cardiac assist device	July, 1992	Grooters
5133744	Tubular-valued artificial heart	July, 1992	Ramos Martinez
5147281	Biological fluid pumping means and method	September, 1992	Thornton et al.
5147388	Auxiliary artificial heart of the embedded-in-body type	September, 1992	Yamazaki
5169378	Intra-ventricular expansible assist pump	December, 1992	Figuera
5169379	In-series ventricular assist system and method of controlling same	December, 1992	Freed et al.
5171207	Apparatus and method of use for pulsatile blood flow	December, 1992	Whalen
5176619	Heart-assist balloon pump with segmented ventricular balloon	January, 1993	Segalowitz
5211546	Axial flow blood pump with hydrodynamically suspended rotor	May, 1993	Issacson et al.
5211659	Pump system suitable as a heart assist device	May, 1993	Strimling et al.
5250036	Intravenous catheter placement system	October, 1993	Farivar
5263978	Blood pump for pulsating operation	November, 1993	Kaufman et al.
5267940	Cardiovascular flow enhancer and method of operation	December, 1993	Moulder
5273518	Cardiac assist apparatus	December, 1993	Lee et al.
5279551	Trocar catheter	January, 1994	James
5290227	Method of implanting blood pump in ascending aorta or main pulmonary artery	March, 1994	Pasque
5300113	Cardiac ventricular assistance device particularly for compensating for weakened heart muscle function and for maintaining the vital body functions	April, 1994	Arpesella et al.
5318518	Irrigating catheter	June, 1994	Plechinger et al.
5332403	LVAD with t-shape and unidirectional valve	July, 1994	Kolff
5336205	Flow directed catheter	August, 1994	Zenzen et al.
5346458	Electrohydraulic energy converter for cardiac assist devices and artificial hearts	September, 1994	Affeld
5352180	Method and apparatus for regulating the flow rate of a periodic flow heart prosthesis	October, 1994	Candelon et al.
5374239	Arterial shunt with blood flow indicator	December, 1994	Mischenko
5376113	Closing member having flexible closing elements, especially a heart valve	December, 1994	Jansen et al.
5378230	Triple-lumen critical care catheter	January, 1995	Mahurkar
5403291	Catheter with elongated side holes	April, 1995	Abrahamson
5405329	Intravascular multi-lumen catheter, capable of being implanted by "tunnelling"	April, 1995	Durand
5413549	Devices and methods for efficient intra-aortic balloon pumping	May, 1995	Leschinsky
5417705	Obturator with rotating, resettable safety shield	May, 1995	Haber et al.
5429584	Cardiac assist method and apparatus	July, 1995	Chiu
5433731	Mechanical defibrillator and method for defibrillating a heart	July, 1995	Hoegnelid et al.
5437601	Blood conduit and pulsatile cardiopulmonary bypass pump system	August, 1995	Runge
5449342	Apparatus for assisting blood circulation	September, 1995	Hirose et al.
5453076	Internal cardiac assist apparatus	September, 1995	Kiyota et al.
5453084	Vascular graft with internal shunt	September, 1995	Moses
5472417	Triple lumen catheter	December, 1995	Martin et al.
5486159	Multiple-lumen catheter	January, 1996	Mahurkar
5503615	Implantable cardiac ventricular assist device and controller thereof	April, 1996	Goldstein
5505701	Intra-aortic balloon catheter	April, 1996	Anaya Fernandez de Lomana	604/101.03
5505710	Telescoping probe	April, 1996	Dorsey, III
5511958	Blood pump system	April, 1996	Chen et al.
5514073	Intra-aortic balloon catheter	May, 1996	Miyata et al.
5522800	Low profile perfusion catheter	June, 1996	Crocker
5533957	Method of tissue retroperfusion	July, 1996	Aldea
5533958	Intrapericardial assist device and associated method	July, 1996	Wilk
5536250	Perfusion shunt device and method	July, 1996	Klein et al.
5542937	Multilumen extruded catheter	August, 1996	Chee et al.
5554136	Dual lumen infusion/aspiration catheter	September, 1996	Luther
5556390	Catheter with oval or elliptical lumens	September, 1996	Hicks
5562595	Multiple therapy cardiac assist device having battery voltage safety monitor	October, 1996	Neisz
5571093	Multiple-lumen catheter	November, 1996	Cruz et al.
5584804	Brain resuscitation and organ preservation device and method for performing the same	December, 1996	Klatz et al.
5649911	Intravenous catheter and delivery system	July, 1997	Terotola
5672158	Catheter introducer	September, 1997	Okada et al.
5722930	Reciprocating pump circulatory assist arrangement	March, 1998	Larson et al.
5746575	Blood pump as centrifugal pump	May, 1998	Westphal et al.
5746709	Intravascular pump and bypass assembly and method for using the same	May, 1998	Rom et al.
5749855	Catheter pump	May, 1998	Reitan
5776111	Multiple catheter assembly	July, 1998	Tesio
5785686	Cannula system for a biventricular cardiac support system or a cardiopulmonary bypass system	July, 1998	Runge
5795326	Double lumen tubing design for catheter	August, 1998	Siman
5807311	Dialysis catheter having rigid and collapsible lumens and related method	September, 1998	Palestrant
5824070	Hybrid flow blood pump	October, 1998	Jarvik
5851174	Cardiac support device	December, 1998	Jarvik et al.
5868703	Multichannel catheter	February, 1999	Bertolero et al.
5911685	Method and apparatus for cardiac blood flow assistance	June, 1999	Siess et al.
5928181	Cardiac bypass catheter system and method of use	July, 1999	Coleman et al.
5941813	Cardiac assist device	August, 1999	Sievers et al.
5947953	Splittable multiple catheter assembly and methods of inserting the same	September, 1999	Ash et al.
5961486	Clot resistant multiple lumen catheter	October, 1999	Twardowski et al.
5964694	Method and apparatus for cardiac blood flow assistance	October, 1999	Siess et al.
5965089	Circulatory support system	October, 1999	Jarvik
6044845	Methods and systems for treating ischemia	April, 2000	Lewis
6059760	Cannula having reverse flow tip	May, 2000	Sandmore et al.
6083198	Perfusion catheter providing segmented flow regions and methods of use	July, 2000	Afzal
6085754	Cardiac disease treatment method	July, 2000	Alferness et al.
6086527	System for treating congestive heart failure	July, 2000	Talpade	600/18
6135981	Protective aortic occlusion catheter	October, 2000	Dyke
6136025	Endoscopic arterial pumps for treatment of cardiac insufficiency and venous pumps for right-sided cardiac support	October, 2000	Barbut et al.
6167765	System and method for determining the flow rate of blood in a vessel using doppler frequency signals	January, 2001	Weitzel
6183411	External stress reduction device and method	February, 2001	Mortier et al.
6190304	Enhanced intra-aortic balloon assist device	February, 2001	Downey et al.	600/18
6190408	Device and method for restructuring the heart chamber geometry	February, 2001	Melvin
6200260	Implantable heart assist system	March, 2001	Bolling
6221103	Device and method for restructuring heart chamber geometry	April, 2001	Melvin
6224540	Passive girdle for heart ventricle for therapeutic aid to patients having ventricular dilatation	May, 2001	Lederman et al.
6228052	Dilator for introducer system having injection port	May, 2001	Okada et al.
6245045	Combination sheath and catheter for cardiovascular use	June, 2001	Stratienko
6287608	Method and apparatus for treatment of congestive heart failure by improving perfusion of the kidney by infusion of a vasodilator	September, 2001	Levin et al.
6299575	Implantable heart assist system	October, 2001	Bolling
6371935	Aortic catheter with flow divider and methods for preventing cerebral embolization	April, 2002	Macoviak et al.
6387037	Implantable heart assist system and method of applying same	May, 2002	Bolling et al.
6390969	Implantable heart assist system and method of applying same	May, 2002	Bolling et al.
6428464	Implantable heart assist system	August, 2002	Bolling
6488662	Percutaneous catheter assembly	December, 2002	Sirimanne
6508777	Circulatory support system and method of use for isolated segmental perfusion	January, 2003	Macoviak et al.	604/4.01
6514226	Method and apparatus for treatment of congestive heart failure by improving perfusion of the kidney	February, 2003	Levin et al.
6558356	Medical device for flow augmentation in patients with occlusive cerebrovascular disease and methods of use	May, 2003	Barbut
6564805	Less-invasive devices and methods for treatment of cardiac valves	May, 2003	Garrison et al.
6592567	Kidney perfusion catheter	July, 2003	Levin et al.
6610004	Implantable heart assist system and method of applying same	August, 2003	Viole et al.
6685621	Implantable heart assist system and method of applying same	February, 2004	Bolling et al.
6719749	Multilumen catheter assembly and methods for making and inserting the same	April, 2004	Schweikert et al.
6749598	Apparatus and methods for treating congestive heart disease	June, 2004	Keren et al.
6889082	Implantable heart assist system and method of applying same	May, 2005	Bolling et al.
20020111577	Extra-corporeal vascular conduit	August, 2002	Sirimanne et al.
20020169413	Apparatus and methods for treating congestive heart disease	November, 2002	Keren et al.	604/101.03
20020188166	Multilumen catheter for minimizing limb ischemia	December, 2002	Viole et al.
20020188167	Multilumen catheter for minimizing limb ischemia	December, 2002	Viole et al.
20030069468	Implantable heart assist system and method of applying same	April, 2003	Bolling
20030083617	Partial aortic occlusion devices and methods for renal and coronary perfusion augmentation	May, 2003	St. Germain et al.
20030144628	Percutaneous catheter assembly	July, 2003	Sirimanne
20030187367	System for treating tissue swelling	October, 2003	Odland
20040019251	Implantable heart assist system and method of applying same	January, 2004	Viole et al.
20040236172	Implantable heart assist system and method of applying same	November, 2004	Bolling et al.
20050085683	Implantable heart assist system and method of applying same	April, 2005	Bolling et al.

DE9111200	November, 1991
EP0232074	January, 1987			Medical tube
EP0411605	January, 1990			Catheter and assembly for extracorporeal circulation
EP0405749	May, 1990			Ventricular assist device cannulae.
EP0533432	March, 1993			Catheter device.
EP0711574	May, 1996			Catheter with dual round lumens
FR2201908	May, 1974
GB2174151	January, 1985
JP6355943S	November, 1988
JP02286170H	November, 1990			EXOCIRCULATING DEVICE
JP08257001	October, 1996
SU1303165	January, 1985
WO/1986/001416	March, 1986			FULLY PORTABLE SEMI-AUTOMATIC MECHANICAL HEART-LUNG SUBSTITUTION SYSTEM AND METHOD
87	October, 1987
WO/1994/005347	March, 1994			CATHETER PUMP
WO/1996/018358	June, 1996			HIGH RELIABILITY CARDIAC ASSIST SYSTEM
WO/1998/014225	March, 1997			CIRCULATORY SUPPORT SYSTEM
WO/1997/015228	May, 1997			PRESSURE MEASUREMENT IN BLOOD TREATMENT
WO/1998/034676	August, 1998			VASCULAR ACCESS SYSTEMS FOR HEMODIALYSIS
WO/1999/016498	April, 1999			PERCUTANEOUS CATHETER WITH SLIP HUB
WO/1999/019010	April, 1999			IMPLANTABLE HEART ASSIST SYSTEM
WO/1999/021605	May, 1999			CATHETER INTRODUCER
WO/1999/042156	August, 1999			HIGH FLOW RATE DIALYSIS CATHETERS AND RELATED METHODS
WO/1999/059652	November, 1999			PULMONARY AND CIRCULATORY BLOOD FLOW SUPPORT DEVICES AND METHODS FOR HEART SURGERY PROCEDURES
WO/2000/041612	July, 2000			APPARATUS AND METHODS FOR TREATING CONGESTIVE HEART DISEASE
WO/2000/061207	October, 2000			HEART ASSIST SYSTEM
00	December, 2000
WO/2001/074419	October, 2001			PARACARDIAL BLOOD PUMP
WO/2002/064204	September, 2002			EXTRA-CORPOREAL VASCULAR CONDUIT
WO/2002/070039	September, 2002			INTRAVASCULAR DEVICE FOR TREATMENT OF HYPERTENSION
WO/2003/070299	August, 2003			IMPLANTABLE HEART ASSIST SYSTEM

PCT International Search Report, App. No. PCT/US 01/42774, App. Date: Oct. 15, 2001, 6 Pages.
PCT International Search Report, App. Date: Jun. 18, 2003 PCT/US/03/04401.
JAMA, Jan. 8, 1968. vol. 203. No. 2, Initial Clinical Experience with Intra-aortic Balloon Pumping in Cardiogenic Shock. pp. 113-118.
Article: A Mechanical Auxiliar Ventricle. pp. M340-M344.
Article: Effect of Stationary Guiding Vanes on Improvement of the Washout Behind the Rotor in Centrifugal Blood Pumps: pp. M220-M224.
Article: An Implantable Seal-less Centrifugal Pump: Comparison of Ultrasonic Transit Time and Ultrasonic Doppler Systems: pp. 808-815.
Article: O.H. Frazier, MD. Long-Term Ventricular Support with the Heartmate in Patients Undergoing Bridge-to-Transplant Operation: 3PP total.
Article: Concepts in the Application of Pneumatic Ventricular Assist Devices for Ischemic Myocardial Injury. pp. 162-168.
Article: Long-Term Left Ventricular Assist Device Use Before Transplantation: pp. M530-M534.
Article: In Vitro Characterization of a Magnetically Suspended Continuous Flow Ventricular Assist Device: pp. M359-M360.
Article: Estimation of Left Ventricular Function In Patients With a Left Ventricular Assist device: M544-M551.
Article: Mechanical Auxiliary Ventricle. pp. M345-M344.
Article: Long Term Follow Up of Survivors of Postcardiotomy Circulatory Support. Ruzevich et al.; 4535, A.S.A.I.O. Transactions 34 (1988) Apr.-Jun., No. 2, Hagerstown, MD, USA. pp. 16-124.
Article: Mechanical Cardiopulmonary Support During Arteriography and Surgical Correction of Coronary Insufficiency Producing Myocardial Infarction with Cardiogenic Shock; Carlson et al. Journal of the Association for the Advancement of Medical Instrumentation. vol. 6, No. 3. May-Jun. 1972; pp. 244-248.
Article: The Sternotomy Hemopump, A Second Generation Intraarterial Assist Device. pp. M218-M220, 223.
Article: Transarterial Closed-Chest Left Ventricular (TaCLV) Bypass. pp. 386-390.
Article: First Clinical Application of transarterial Closed-Chest Left Ventricular (TaCLV) Bypass. pp. 386-391.
Article: Implantable Left Ventricular Assist Device. pp. 1522-1533.
Article: Effects of Partial and Complete Unloading of The Failing Left Ventricle by Transarterial Left Heart Bypass. pp. 865-872.
Article: Hydrodynamic Properties of a New Percutaneous Intra-aortic Axial Flow Pump. Reitan et al. ASAIO Journal 2000. pp. 323-328.
Article: Hemodynamic Effects of the Concomitant Use of Intra-Aortic Balloon Pumping and Venoarterial Bypass without Oxygenation In Cardigenic Shock. Takamoto et al. Intra-Aortic Pumping & Ventroaterial Bypass. vol. 19. No. 6. Nov. 1978. pp. 938-945.
Journal of the Association for the Advancement of Medical Instrumentation, vol. 10, No. 5, Sep.-Oct. 1976, p. 215; Medical Instrumentation Editorial.
Dormandy, Goetz, and Kripke; Surgery, Feb. 1969, vol. 65, No. 2, pp. 311-320; Hemodynamics and coronary blood flow with counterpulsation.
The New England Journal of Medicine, Article: Treatment of Severe Fluid Overload by Ultrafiltration, vol. 291, No. 15, Oct. 10, 1974, pp. 747-751.
Magnetically Suspended Vad. pp. M361. 363, 364.
Magovern, George J. Jr, M.D.; Use of Biomedics Pump in Postoperative Circulatory Support: 6PP total.
Shook, Bruce J., MS Eng.; The Abiomed BVS 5000 Biventricular Support System. 6 PP total.
Jeavanandan, Valluvan, M.D. et al.; TCI Heartmate Left Ventricular Assist System: Results with Bridge to Transplant and Chronic Support: 5 PP total.
Ramasamy, Narayanan, PhD et al.; Novacor LVAS: Results with Bridge Transplant to Chronic Support: 3 PP Total.
Emery, Robert M. M.D., et al; Uses of Mechanical Circulatory Assist Devices at Minneapolis Heart Institute: 5PP total.
McBride, Lawerence R., M.D., et al.; Anticoagulation in Patients with Ventricular Assist Devices: 1 Pg.
Pifarre, Roque, M.D. et al.; Bridge to Transplantation with the total Articical heart: The Loyal Experience 5 PP total.
Khanwiljkar, Pratap S., MS, MBA, et al.; Future Prospects for a totally Implantable Artificial Heart: 8 pp total.
Birtwell, W. et al. The evolution of counterpulsation techniques. Med Instrum 1976; 10(5): 217-23.
Blythe, D. Percutaneous axillary artery insertion of an intra-aortic balloon pump. Annesth and Intensive Care 1995; 23(3): 406-7.
Bonchek, L. et al. Direct Ascending Aortic Insertion of the “Percutaneous” Intraaortic Balloon Catheter in the Open Chest: Advantages and Precautions. Ann Thorac Surg 1981; 32(5): 512-14.
Clark, R. E. et al. Future devices and directions. Progress in Cardiovascular Diseases, 43(1) Jul./Aug. 2000: 95-100.
Cochran, R. et al. Ambulatory Intraaortic Balloon Pump Use as Bridge to Heart Transplant. Ann Thorac Surg 2002; 74: 746-52.
Cook, L. et al. Intra-aortic balloon pump complications: A five-year retrospective study of 283 patients. Heart & Lung 1999; 28(3): 195-202.
Crystal, E. et al. Incidence and Clinical Significance of Bacteremia and Sepsis Among Cardiac Patient Treated with Intra-Aortic Balloon Counterpulsation Pump. Amer J Cardiol 2000; 86: 1281-1284.
Dembitsky, W. Briding from acute to chronic devices. Ann Thorac Surg 1999; 68: 724-28.
Goldstein, A. H. et al. Development of an Implantable Centrifugal Blood Pump. ASAIO 1992; 38(3): M362-5.
Goldstein, A. H. et al. Predictable Reduction in Left Ventricular Stroke Work and Oxygen Utilization With an Implantable Centrifugal Pump. Ann Thorac Surg 1994; 58 (4): 1018-24.
Jaski, B. et al. Anterograde Perfusion in Acute Limb Ischemia Secondary to Vascular Occlusive Cardiopulmonary Support. Cath and Cardiovasc Diag 1995; 35: 373-76.
Magovern, G. Nonpulsatile Circulatory Support: Techniques of Insertion. Ann Thorac Surg 1993; 55: 266-72.
McBride, L. et al. Axillary Artery Insertion of an Intraaortic Balloon Pump. Ann Thorac Surg 1989; 48: 874-5.
Nishimura et al. The enabler cannula pump: a novel circulatory support system. The International Journal of Artificial Organs, vol. 22, No. 5, 1999, pp. 317-323.
Sharony et al. Cardiopulmonary Support and Physiology- The Intra-Aortic Cannula Pump: A Novel Assist Device for the Acutely Failing Heart. The Journal of Thoracic and Cardiovascular Surgery, Nov. 1992, vol. 118, No. 5, pp. 924-929.
Sharony, R. et al. Right heart support during off-pump coronary artery surgert—a multi-center study. Heart Surg Forum. 2002; 5(1): 13-6.
Takagaki et al. A Novel Miniature Ventricular Assist Device for Hemodynamic Support. ASAIO Journal 2001, pp. 412-416.
PCT International Search Report, App. No. PCT/US2004/033575, Feb. 18, 2005.
Champsaur, G. et al. Use of the Abiomed BVS System 5000 as a bridge to cardiac transplantation. J Thorac Cardiovasc Surg 1990; 100: 122-8.
Clark, R. E. et al., Left Ventricular Support With the Implantable AB-180 Centrifugal Pump in Sheep With Acute Myocardial Infarction. ASAIO 1998; 44(6): 804-11.
Clark, R. E. et al., Small, Low-Cost Implantable Centrifugal Pump for Short-Term Circulatory Assistance. Ann Thorac Surg 1996; 61: 452-56.
Clark, R. E., Progress in the clinical application of the AB-180 circulatory support system. Journal of Circulatory Support (1998) vol. 1, No. 1, 21-26.
Griffin, W. P. et al. AB-180 Circulatory Support System: Summary of Development and Phase I Clinical Trial. ASAIO 1998; 44(5): M719-24.
Harmand, M.F. et al., In vitro comparative evaluation under static conditions of the hemocompatibility of four types of tubing for cardiopulmonary bypass, Biomaterials 20 (1999) 1561-1571.
Ide, Hirofumi et al., Hemodynamic Evaluation of a New Left Ventricular Assist Device, Artificial Organs 16 (3): 286-90; 1992.
Ide, Hirofumi et al., Evaluation of the Pulsatility of a New Pulsatile Left Ventricular Assist Device—the Integrated Cardioassist Catheter—in Dogs, J. of Thoracic and Cardiovascular Surgery 107 (2): 569-75; Feb. 1994.
Keldenich, Stephan, et al., Application of a New Dynamic Flow Model for Investigating the Biocompatibility of Modified Surfaces; ASAIO Journal 2000.
Konertz, W. et al. Clinical Experience With the MEDOS HIA-VAD System in Infants and Children: A Preliminary Report. Ann Thorac Surg 1997; 63: 1138-44.
Lamba, Nina M.K., In vitro investigation of the blood response to medical grade PVC and the effect of heparin on the blood response; Biomaterials 21 (2000) 89-96.
Magovern, J. A. et al. Clinical results with the AB-180 left ventricular assist device. Ann Thorac Surg 2001; 71: S121-24.
Martin, J. et al. MEDOS HIA-VAD Biventricular Assist Device for Bridge to Recovery in Fulminant Myocarditis. Ann Thorac Surg 1997; 1145-46.
Mihaylov, D. et al., Evaluation of the Optimal Driving Mode During Left Ventricular Assist with Pulsatile Catheter Pump in Calves, Artificial Organs 23(12): 1117-22; 1999.
Mihaylov, Dimiter et al., Development of a New Introduction Technique for the Pulsatile Catheter Pump, Artificial Organs 21(5): 425-27; 1997.
Murakami, Taiji et al., In Vitro and in Vivo Testing of an Implantable Motor Driven Left Ventricular Device, Artificial Organs 20 (2): 152-55; 1996.
Morsink, PLJ et al., Numerical Modelling of Blood Flow Behaviour in the Valved Catheter of the PUCA Pump, a LVAD, The International Journal of Artificial Organs 20(5): 277-284; 1997.
Ohley, W. et al. Influence of Catheter and Arterial Diameter on Flow Distal to an Intra-Aortic Balloon Insertion Site: A Theoretic Examination and In Vitro Assessment. ASAIO 1998; 44: 786-93.
Pacella, J. J. et al. Modified Fabrication Techniques Lead to Improved Centrifugal Blood Pump Performance. ASAIO 1994; 40: M767-72.
Rakhorst, Gerhard et al., In Vitro Evaluation of the Influence of Pulsatile Intraventricular Pumping on Ventricular Pressure Patterns, Artificial Organs 18(7): 494-99; 1994.
Reddy, R. C. et al. End Organ Function With Prolonged Nonpulsatile Circulatory Support. ASAIO 1995; 41: M547-51.
Reedy, J. et al. Mechanical cardiopulmonary support for refractory cardiogenic shock. Heart & Lung 1990; 19(5): 514-23.
Savage, E. B. et al. The AB-180 Circulatory Support System: Summary of Development and Plans for Phase I Clinical Trial. Ann Thorac Surg 1999; 68: 768-74.
Unknown author: Arterial and Venous Access, The Cardiac Catheterization Notebook, pp. 54-63.
Verkerke, Gijsbertus et al., Numerical Simulation of the Pulsating Catheter Pump: A Left Ventricular Assist Device, Artificial Organs 23(10): 924-31; 1999.
Verkerke, Bart et al., The PUCA Pump: A Left Ventricular Assist Device, Artificial Organs 17(5): 365-68; 1993. cited by other.
Verkerke, CJ et al., Numerical Simulation of the PUCA Pump, A Left Ventricular Assist Device, Abstracts of the XIXth ESAO Congress, The International Journal of Artificial Organs 15(9): 543; 1992.
Wenger, R., et al. Flow dynamics of peripheral venous catheters during extracorporeal membrane oxygenation with a centrifugal pump. J Thora Cardiovasc Surg 1988; 96:478-84.
Westaby, S. et al. Mechanical bridge to recovery in fulminant myocarditis. Ann Thorac Surg 2000; 70: 278-282.
Zwart, H.H.J., et al., Transarterial Closed-Chest Left Ventricular (TaCLV) Bypass; vol. XV Trans. Amer. Soc. Artif. Int. Orangs, 1969, pp. 386-390.
Aranki, S. et al. Femoral Veno-Arterial Extracorporeal Life Support With Minimal or No Heparin. Ann Thorac Surg 1993; 56: 149-55.

Layno, Carl

Knobbe, Martens, Olson & Bear LLP

RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No. 10/408,926, filed Apr. 7, 2003, which is a continuation of U.S. application Ser. No. 10/078,260, filed on Feb. 15, 2002, now U.S. Pat. No. 6,610,004, both of which are incorporated herein by reference in their entirety.

What is claimed is:

1. A method for increasing perfusion through a renal artery, the method comprising: providing fluid communication between a conduit and means for pumping blood; advancing the pumping means to a location within the descending aorta and an outlet of the conduit to a location proximate a renal artery; and operating said pumping means to direct blood from the descending aorta to the renal artery at volumetric rates that are on average subcardiac to increase perfusion through the renal artery; wherein advancing further comprises advancing the conduit to a location in the vasculature having a width that is meaningfully larger than the width of the conduit.

2. The method of claim 1, wherein the pumping means further comprises pump driving means and further comprising advancing pump driving means into the vasculature.

3. The method of claim 1, further comprising inserting the pumping means and the conduit into a non-primary vessel subcutaneously in a minimally-invasive procedure.

4. The method of claim 1, further comprising configuring the conduit and pumping means such that blood can flow in the aorta outside the conduit after the conduit is advanced to a location in the aorta.

5. The method of claim 1, wherein blood flows inside the conduit and outside the conduit in the aorta while the pumping means is operating.

6. The method of claim 1, wherein the pumping means comprises an open sided housing that permits blood flow therethrough.

7. The method of claim 1, wherein the pumping means is operated in a pulsatile fashion.

8. The method of claim 1, wherein the pumping means comprises a rotary pump.

9. The method of claim 1, wherein the pumping means comprises an impeller and operating the pumping means comprises rotating the impeller.

10. The method of claim 1, wherein providing fluid communication between a conduit and means for pumping blood comprises positioning the pumping means within the conduit.

11. An intravascular system for increasing perfusion through a renal artery, comprising: means for pumping blood; and a conduit fluidly coupled with the pumping means and configured to direct blood in the descending aorta toward a renal artery to maintain or enhance blood flow to a kidney supplied by the renal artery; whereby the pumping means and the conduit are configured to be insertable into a non-primary vessel subcutaneously in a minimally-invasive procedure; wherein the conduit has a transverse dimension that is meaningfully smaller than the transverse dimension of a location in the descending aorta where the conduit is positioned; and wherein the conduit comprises a first lumen in which at least a portion of the pumping means is housed and a second lumen adjacent and parallel to the first lumen.

12. A method for increasing perfusion through a renal artery, the method comprising: providing fluid communication between a conduit and means for pumping blood; advancing the pumping means to a location within the descending aorta and an outlet of the conduit to a location proximate a renal artery; and operating said pumping means to direct blood from the descending aorta to the renal artery at volumetric rates that are on average subcardiac to increase perfusion through the renal artery; wherein the conduit has a first width and advancing comprises advancing the conduit to a location within the vasculature having a second width, the first width being less than about one-half the second width.

13. A method for increasing perfusion through a renal artery, the method comprising: providing fluid communication between a conduit and means for pumping blood; advancing the pumping means to a location within the descending aorta and an outlet of the conduit to a location proximate a renal artery; operating said pumping means to direct blood from the descending aorta to the renal artery at volumetric rates that are on average subcardiac to increase perfusion through the renal artery; and providing a blood flow path in a side lumen of the conduit adjacent the pumping means.

14. An intravascular system for increasing perfusion through a renal artery, comprising: means for pumping blood; and a conduit fluidly coupled with the pumping means and configured to direct blood in the descending aorta toward a renal artery to maintain or enhance blood flow to a kidney supplied by the renal artery; whereby the pumping means and the conduit are configured to be insertable into a non-primary vessel subcutaneously in a minimally-invasive procedure; wherein the conduit has a first cross-sectional area and a location in the descending aorta where the conduit is positioned has a second cross-sectional area, the first cross-sectional area being less than about one-half the second cross-sectional area; and wherein the pumping means further comprises pump driving means configured to be advanced into the patient's vasculature.

15. The pumping system of claim 14, wherein the conduit comprises an inlet and an outlet, the conduit configured such that when the system is applied within the vasculature the inlet can be positioned at a first location in the descending aorta and the outlet can be positioned at a second location in the descending aorta below the first location.

16. The pumping system of claim 14, further comprising an open sided housing that permits blood flow therethrough and that houses at least a portion of the pumping means.

17. The pumping system of claim 14, wherein the conduit comprises an inlet and an outlet, the conduit configured such that when the system is applied within the vasculature the inlet can be positioned at a first location in the descending aorta and the outlet can be positioned at a second location in the descending aorta downstream of the first location.

18. An intravascular system for increasing perfusion through a renal artery, comprising: means for pumping blood; and a conduit fluidly coupled with the pumping means and configured to direct blood in the descending aorta toward a renal artery to maintain or enhance blood flow to a kidney supplied by the renal artery; whereby the pumping means and the conduit are configured to be insertable into a non-primary vessel subcutaneously in a minimally-invasive procedure; wherein the conduit has a first cross-sectional area and a location in the descending aorta where the conduit is positioned has a second cross-sectional area, the first cross-sectional area being less than about one-half the second cross-sectional area; and wherein the conduit comprises a first lumen in which at least a portion of the pumping means is housed and a second lumen for conveying blood adjacent to the first lumen.

19. The pumping system of claim 18, wherein the pumping means further comprises pump driving means configured to be advanced into the patient's vasculature.

20. An intravascular system for increasing perfusion through a renal artery, comprising: means for pumping blood; and a conduit fluidly coupled with the pumping means and configured to direct blood in the descending aorta toward a renal artery to maintain or enhance blood flow to a kidney supplied by the renal artery; whereby the pumping means and the conduit are configured to be insertable into a non-primary vessel subcutaneously in a minimally-invasive procedure; wherein the conduit has a first cross-sectional area and a location in the descending aorta where the conduit is positioned has a second cross-sectional area, the first cross-sectional area being less than about one-half the second cross-sectional area; and wherein the conduit comprises an inlet and an outlet, the conduit configured such that when the system is applied within the vasculature the inlet can be positioned at a first location in the descending aorta and the outlet can be positioned at a second location in the descending aorta upstream of the first location.

21. An intravascular system for increasing perfusion through a renal artery, comprising: means for pumping blood; and a conduit fluidly coupled with the pumping means and configured to direct blood in the descending aorta toward a renal artery to maintain or enhance blood flow to a kidney supplied by the renal artery; whereby the pumping means and the conduit are configured to be insertable into a non-primary vessel subcutaneously in a minimally-invasive procedure; wherein the conduit has a transverse dimension that is meaningfully smaller than the transverse dimension of a location in the descending aorta where the conduit is positioned; and wherein the conduit comprises an inlet and an outlet, the conduit configured such that when the system is applied within the vasculature the inlet can be positioned at a first location in the descending aorta and the outlet can be positioned at a second location in the descending aorta upstream of the first location.

22. The pumping system of claim 21, wherein the conduit comprises an inlet and an outlet, wherein the pump is positioned at least partially within the conduit at a location between the inlet and the outlet, and wherein the conduit is configured to permit significant flow around the conduit at least from the inlet to the pump.

23. The pumping system of claim 21, wherein the conduit comprises an inlet and an outlet, wherein the pump is positioned at least partially within the conduit at a location between the inlet and the outlet, and wherein the conduit is configured to permit significant flow around the conduit at least from the pump to the outlet.

24. The pumping system of claim 21, wherein the conduit comprises an inlet and an outlet, wherein the pump is positioned at least partially within the conduit at a location between the inlet and the outlet, and wherein the conduit is configured to permit significant flow around the conduit from the inlet to the outlet.

FIELD OF THE INVENTION

The present invention relates generally to a system for assisting the heart and, in particular, to an extracardiac pumping system and a method for both supplementing the circulation of blood through the patient and for enhancing vascular blood mixing using a minimally invasive procedure.

BACKGROUND OF THE INVENTION

During the last decade, congestive heart failure (CHF) has burgeoned into the most important public health problem in cardiovascular medicine. As reported in Gilum, R. F., Epidemiology of Heart Failure in the U.S ., 126 Am. Heart J. 1042 (1993), four hundred thousand (400,000) new cases of CHF are diagnosed in the United States annually. The disorder is said to affect nearly 5 million people in this country and close to 20 million people worldwide. The number of hospitalizations for CHF has increased more than three fold in the last 15 years. Unfortunately, nearly 250,000 patients die of heart failure annually. According to the Framingham Heart Study, the 5-year mortality rate for patients with congestive heart failure was 75 percent in men and 62 percent in women (Ho, K. K. L., Anderson, K. M., Kannel, W. B., et al., Survival After the Onset of Congestive Heart Failure in Framingham Heart Study Subject , 88 Circulation 107 (1993)). This disorder represents the most common discharge diagnosis for patients over 65 years of age. Although the incidence of most cardiovascular disorders has decreased over the past 10 to 20 years, the incidence and prevalence of congestive heart failure has increased at a dramatic rate. This number will increase as patients who would normally die of an acute myocardial infarction (heart attack) survive, and as the population ages.

CHF manifests itself primarily by exertional dyspnea (difficult or labored breathing) and fatigue. Three paradigms are used to describe the causes and therapy of CHF. The first views this condition in terms of altered pump function and abnormal circulatory dynamics. Other models describe it largely in terms of altered myocardial cellular performance or of altered gene expression in the cells of the atrophied heart. In its broadest sense, CHF can be defined as the inability of the heart to pump blood throughout the body at the rate needed to maintain adequate blood flow, and many of the normal functions of the body.

To address CHF, many types of cardiac assist devices have been developed. A cardiac or circulatory assist device is one that aids the failing heart by increasing its pumping function or by allowing it a certain amount of rest to recover its pumping function. Because congestive heart failure may be chronic or acute, different categories of heart assist devices exist. Short of a heart transplant, at least two types of chronic heart assist systems have been developed. One type employs a full or partial prosthetic connected between the heart and the aorta, one example of which is commonly referred to as a LVAD—Left Ventricular Assist Device. With reference to FIG. 1 herein, one example of a LVAD 2 is shown. The LVAD comprises a pump and associated valves 4 that draws blood directly from the apex of the left ventricle 6 and directs the blood to the aortic arch 8 , bypassing the aortic valve. In this application, the left ventricle stops functioning and does not contract or expand. The left ventricle becomes, in effect, an extension of the left atrium, with the LVAD 2 taking over for the left ventricle. The ventricle, thus, becomes a low-pressure chamber. Because the intent is to take over for the left ventricle, the LVAD operates by pumping blood at cardiac rates. With an LVAD, oxygenated blood circulation is established sufficient to satisfy the demand of the patient's organs. Under these circumstances, however, continuous flow may not be desired because the patient's arterial system is deprived of pulsatile wave flow, which is beneficial to certain parts of the patient.

Another type of chronic heart assist system is shown in U.S. Pat. No. 5,267,940 to Moulder. Moulder describes a pump implanted into the proximal descending aorta to assist in the circulation of blood through the aorta. Because it is intended to pump blood flowing directly out of the heart, it is important that the Moulder device operate in a properly timed, pulsatile fashion. If it is not operated in direct synchronization with the patient's heart, there is a risk that the pump might cause “carotid steal phenomenon” where blood is drawn away from the patient's brain through the carotid arteries when there is insufficient blood in the left ventricle.

In addressing acute CHF, two types of heart assist devices have been used. One is counterpulsatory in nature and is exemplified by an intra-aortic balloon pump (IABP). With an IABP, the balloon is collapsed during isovolumic contraction, providing a reduced pressure against which the heart must pump blood, thereby reducing the load on the heart during systole. The balloon is then expanded, forcing blood omnidirectionally through the arterial system. Another example of this first type employs one or more collapsible chambers in which blood flows passively into the chamber during systole, as is shown in U.S. Pat. No. 4,240,409 to Robinson et al. The chamber is then collapsed and the blood forcibly returned to the aorta. These devices simulate a chamber of the heart and depend upon an inflatable bladder to effectuate pumping action, requiring an external pneumatic driver. Moreover, they do not operate as a continuous flow system, operating exclusively in pulsatile fashion.

A second type of acute assist device utilizes an extracorporeal pump, such as the Biomedicus centrifugal pump, to direct blood through the patient while surgery is performed on the heart. In one example, described in U.S. Pat. No. 4,968,293 to Nelson, the heart assist system employs a centrifugal pump in which the muscle of the patient is utilized to add pulsatility to the blood flow. The Nelson device is used to bypass a portion of the descending aorta.

Another device, shown in U.S. Pat. No. 4,080,958 to Bregman et al., utilizes an inflatable and collapsible bladder to assist in blood perfusion during heart trauma and is intended to supplement a conventional heart-lung machine by imparting pulsatile actuation. In the primary embodiment disclosed in Bregman, the balloon is controlled to maintain sufficient pressure at the aortic root during diastole to ensure sufficient blood perfusion to the coronary arteries. In an alternative embodiment, a low resistance outlet from the aorta to the inferior vena cava is provided to reduce the aortic pressure during systole, thus, reducing the hemodynamic load on the left ventricle.

Other devices, such as that shown in U.S. Pat. No. 4,034,742 to Thoma, depend upon interaction and coordination with a mechanical pumping chamber containing a movable pumping diaphragm. These devices are intended primarily for application proximate the heart and within the patient's thorax, requiring major invasive surgery.

Many CHF devices are acutely used in the perioperative period. For example, U.S. Pat. No. 4,995,857 to Arnold discloses a perioperative device to pump blood at essentially cardiac rates during surgery when the heart has failed or has been stopped to perform cardiac surgery. The Arnold system temporarily replaces the patient's heart and lung and pumps blood at cardiac rates, typically 5 to 6 liters/min. Like all systems that bypass the heart and the lungs, an oxygenator is required. Of course, with any system that includes an oxygenator, such as the conventional heart-lung machine, the patient cannot be ambulatory.

With early IABP devices, a polyurethane balloon was mounted on a vascular catheter, inserted into the femoral artery, and positioned in the descending aorta just distal to the left subclavian artery. The balloon catheter was connected to a pump console that pumped helium or carbon dioxide into the balloon during diastole to inflate it. During isovolumic contraction, i.e., during the brief time that the aortic valve is closed and the left ventricle continues to contract, the gas used to actuate the balloon was rapidly withdrawn to deflate the balloon. This reduced the pressure at the aortic root when the aortic valve opened. In contrast, during diastole, the balloon was inflated, causing the diastolic pressure to rise and pushing the blood in the aorta distally towards the lower part of the body (on one side of the balloon) and proximally toward the heart and into the coronary arteries (on the other).

The major advantage in such a counterpulsation device was systolic deflation, which lowered the intra-aortic volume and pressure, reducing both afterload and myocardial oxygen consumption. In other words, when the balloon is inflated, it creates an artificially higher pressure in the aorta, which has the ancillary benefit of greater perfusion through the coronary arteries. When the balloon deflates, just before the aortic valve opens, the pressure and volume of the aorta decrease, relieving some of the hemodynamic burden on the heart. These physiologic responses improved the patient's cardiac output and coronary circulation, temporarily improving hemodynamics. In general, counterpulsation with an IABP can augment cardiac output by about 15%, this being frequently sufficient to stabilize the patient's hemodynamic status, which might otherwise rapidly deteriorate. When there is evidence of more efficient pumping ability by the heart, and the patient has moved to an improved class of hemodynamic status, counterpulsation can be discontinued, by slowly weaning while monitoring for deterioration.

Until 1979, all IABP catheters were inserted via surgical cutdown, generally of the femoral artery. Since then, the development of a percutaneous IABP catheter has allowed quicker, and perhaps safer, insertion and has resulted in more expeditious institution of therapy and expansion of clinical applications. Inflation and deflation of the balloon, however, requires a pneumatic pump that is sufficiently large that it must be employed extracorporeally, thereby restricting the patient's movements and ability to carry out normal, daily activities. IABP devices are, thus, limited to short term use, on the order of a few days to a few weeks.

As discussed above, a variety of ventricular assist pumping mechanisms have been designed. Typically associated with LVADs are valves that are used in the inlet and outlet conduits to insure unidirectional blood flow. Given the close proximity of the heart, unidirectional flow was necessary to avoid inadvertent backflow into the heart. The use of such valves also minimized the thrombogenic potential of the LVAD device.

Typically, the pump associated with older LVADs was a bulky pulsatile flow pump, of the pusher plate or diaphragm style, such as those manufactured by Baxter Novacor or TCI, respectively. Given that the pump was implanted within the chest and/or abdominal cavity, major invasive surgery was required. The pumps were typically driven through a percutaneous driveline by a portable external console that monitors and reprograms functions.

Alternatively, rotary pumps, such as centrifugal or axial pumps, have been used in heart assist systems. With centrifugal pumps, the blood enters and exits the pump practically in the same plane. An axial pump, in contrast, directs the blood along the axis of rotation of the rotor. Inspired by the Archimedes screw, one design of an axial pump has been miniaturized to about the size of a pencil eraser, although other designs are larger. Despite its small size, an axial pump may be sufficiently powerful to produce flows that approach those used with older LVADs. Even with miniaturized pumps, however, the pump is typically introduced into the left ventricle through the aortic valve or through the apex of the heart, and its function must be controlled from a console outside the body through percutaneous lines.

All of these heart assist systems referred to above serve one or both of two objectives: (1) to improve the performance of a patient's operative-but-diseased heart from the minimum, classified as NYHAC Class IV, to practically normal, classified as I or 0; or (2) to supplement oxygenated blood circulation through the patient to satisfy organ demand when the patient's heart is suffering from CHF. With such systems, extreme pumping and large amounts of energy, volume, and heat dissipation are required.

Many of these heart assist systems have several general features in common: 1) the devices are cardiac in nature; i.e., they are placed directly within or adjacent to the heart, or within one of the primary vessels associated with the heart (aorta), and are often attached to the heart and/or aorta; 2) the devices attempt to reproduce pulsatile blood flow naturally found in the mammalian circulatory system and, therefore, require valves to prevent backflow; 3) the devices are driven from external consoles, often triggered by the electrocardiogram of the patient; and 4) the size of the blood pump, including its associated connectors and accessories, is generally unmanageable within the anatomy and physiology of the recipient. Due to having one or more of these features, the prior art heart assist devices are limited in their effectiveness and/or practicality.

Many of the above identified prior art systems, generally referred to as Mechanical Circulatory Assist Devices, are not the only means, however, used to treat patients with congestive heart failure (CHF). Most CHF patients are prescribed as many as five to seven different drugs to ameliorate their signs and symptoms. These drugs may include diuretics, angiotensin converting enzyme (ACE) inhibitors, beta-blockers, cardiac glycosides, and peripheral vasodilators. The rationale for pharmacological intervention in heart failure include minimizing the load on the heart, improving the pumping action of the heart by enhancing the contractility of the muscle fibers, and suppression of harmful neurohormonal compensatory mechanisms that are activated because of the decreased pumping function of the heart.

Noncompliance with what is often a complex drug regime may dramatically adversely affect the recovery of a CHF patient leading to the need for hospitalization and possibly morbidity and mortality. In addition, ACE inhibitors and diurectics can cause hypotension, which leads to decreased organ perfusion or an increasing demand on the heart to pump more blood. This leads to an inability, in many cases, to prescribe the most effective dosage of ACE inhibitors and a less than optimum outcome for the patient. Patients suffering from CHF with the underlying cause of mitral valve insufficiency have been able to have their diuretics reduced following surgical repair of their mitral valve. This is due to an increased cardiac output and arterial pressures (as a result of the correction of the problem) resulting in more effective organ perfusion. With the reduction in the use of diuretics and the resultant hypotension, more effective dosages of ACE inhibitors can be used with more favorable outcomes. In addition, it is easier for the patient to follow a less complex drug regime, eliminating the costly and life threatening risks associated with noncompliance.

When blood flow through the coronary arteries falls below the level needed to provide the energy necessary to maintain myocardial function, due often to a blockage in the coronary arteries, a myocardial infarction or heart attack occurs. This is a result of the blockage in the coronary arteries preventing blood from delivering oxygen to tissues downstream of the blockage. The closer the blockage is to the coronary ostia, however, the more severe and life threatening the myocardial infarction. The farther the location of the blockage is from the coronary ostia, the smaller the area of tissue or myocardium that is at risk. As the energy stored in the affected area decreases, myocardial cells begin to die. The larger the area that dies due to the loss of oxygen, the more devastating the infarction. To reduce the area at risk, at least two known options are to either increase the oxygen supply to the affected area or decrease the energy demands of the heart to prolong energy stores until the blockage can be removed or reduced. One particular method to increase blood flow, thereby increasing delivery of oxygen to the affected area, is through a technique called retroperfusion. This is accomplished by passing a cannula into either the right or left ventricle (depending on the area of the blockage) and perfusing oxygenated blood retrograde up the coronary artery on the downstream side of the blockage. Another method is to use drugs to increase the force of contraction of the myocardium, creating increased blood flow across the blocked area. Yet another method is to use drugs, such as pentoxifylline, aspirin, or TPA (tissue plaminogen activator), to reduce the viscosity of (thin out) the blood, inhibit platelet aggregation, or lyse thrombi (clots), respectively, thus, allowing more blood to pass by the blockage. The goal of all of these methods is to increase the delivery of oxygen to the tissue at risk.

The alternative option mentioned above is to reduce the energy demands of the myocardium and increase the amount of time before irreversible damage occurs. This can be accomplished by reducing the workload of the left ventricle (which is the largest energy-consuming portion of the heart). An IABP is placed into the aorta and used as described above, resulting in a decreased afterload on the heart and increased perfusion of the coronary arteries and peripheral organs. An alternative way to reduce myocardial oxygen demand is to reduce the volume of blood the left ventricle must pump. This can be accomplished by reducing the load on the left ventricle, such as in a cardiopulmonary bypass or use of an LVAD. Unloading the left ventricle decreases the energy requirements of the myocardium and increases the amount of time before irreversible damage occurs. This provides an opportunity to more effectively remove or decrease the blockage and salvage myocardial function. To be successful, each of these techniques must be implemented within a short amount of time after the onset of a myocardial infarction. The disadvantage, however, is that each of these techniques can only be performed in an emergency room or hospital setting. Unless the patient is already in the hospital when the myocardial infarction occurs, there is usually some level of irreversible damage and subsequent loss of myocardial function.

It would be advantageous, therefore, to employ a heart assist system that avoids major invasive surgery and also avoids the use of peripheral equipment that severely restricts a patient's movement. It would also be advantageous to have such a heart assist system that can be employed in a non-hospital setting for ease of treating acute heart problems under emergency conditions.

SUMMARY OF THE INVENTION

The object of the present invention is to address the aspect of CHF that results from altered pump function and abnormal circulatory dynamics while overcoming the limitations of prior art heart assist systems. Without functioning as a bypass to one or more of a patient's organs, the present invention comprises an extracardiac pumping system for supplementing the circulation of blood through the patient without any component thereof being connected to the patient's heart or primary vessels. Thus, it is extracardiac in nature. With the ability to be applied within a minimally invasive procedure, the present invention significantly improves the condition of the patient suffering from CHF, resulting in the patient feeling much better, even where CHF continues. By supplementing the pumping action of the heart, in lieu of replacing it, the various embodiments of the present invention take advantage of the pulsatile action of the heart, despite its weakened condition, to effectively deliver blood to body organs that benefit from pulsatile delivery of oxygenated blood. As a result, the present invention is capable of being operated in a continuous flow fashion or, if desired, in a pulsatile flow fashion.

An ancillary but important benefit of the present invention is the ability to apply the present invention in such a way as to also reduce the pumping load on the heart, thereby potentially permitting the heart to recover during use. With the present invention, no bulky pump, valves or oxygenator are required, and no thoracic invasion with major cardiac surgery is required. Indeed, a significant advantage of the present invention is its simplicity while achieving extraordinary results in improving the condition of a patient suffering from CHF. It is contemplated that the present invention be applied such that the heart experiences a reduced pressure at the aortic root during systole (afterload) and/or a reduced left ventricular end diastolic pressure (pre-load), thus reducing the hemodynamic burden or workload on the heart and, thus, permitting the heart to recover.

The extracardiac system of the present invention preferably comprises, in several embodiments, a rotary pump configured to pump blood through the patient at subcardiac rates; i.e., at a flow rate significantly below that of the patient's heart. Other types of pumps or flow generating mechanisms may be effective as well, including but not limited to rotating means, e.g., an Archimedes screw or impeller housed within an open or closed housing, either of which may be cable driven or shaft driven. Pumping the blood tends to revitalize the blood to a certain extent by imparting kinetic and potential energy to the blood discharged from the pump. Importantly, the preferred pump for the present invention pumping system is one that requires a relatively low amount of energy input, when compared to prior art pumps designed to pump at cardiac rates. The pump may be implanted corporeally or more specifically intravascularly, or it may be positioned extracorporeally, depending upon the capability, practicality, or need of the patient to be ambulatory.

The present invention also comprises, in several embodiments, an inflow conduit fluidly coupled to the pump, to direct blood to the pump from a first blood vessel, either the aorta or a first peripheral or non-primary vessel, either directly or indirectly through another blood vessel, wherein insertion of the pump and/or inflow conduit is through a non-primary blood vessel. The invention further comprises an outflow conduit fluidly coupled to the pump, to direct blood from the pump to a second blood vessel, either the aorta or a second peripheral or non-primary blood vessel, whether directly to the second vessel or indirectly through the first or other peripheral or non-primary blood vessel. The connection of the inflow and outflow conduits to the respective blood vessels is performed subcutaneously; not so deep as to involve major invasive surgery. In other words, minimally subdermal. This permits application of the connections in a minimally-invasive procedure. Preferably, the connections to the blood vessels are just below the skin or just below the first layer of muscle, depending upon the blood vessels at issue or the location of the connection, although slightly deeper penetrations may be necessary for some patients or for some applications.

In one embodiment, the present invention is configured so that it may be applied at a single cannulated site and comprises, for example, a multi-lumen catheter having at least one lumen as an inflow lumen and a second lumen as an outlet lumen. The multi-lumen catheter has an inflow port in fluid communication with the inflow lumen. With this embodiment, blood may be drawn into the inflow port of the first lumen from a first peripheral or non-primary blood vessel site, either the blood vessel into which the multi-lumen catheter is inserted or a different blood vessel. The output of the pump directs blood through a second (outlet) port at the distal end of the second lumen that may be located in a second peripheral or non-primary vessel site. This method accomplishes the same beneficial results achieved in the previously described embodiments, but requires only a single cannulated site, rather than two such sites. It should be appreciated that the multi-lumen catheter could be used in a manner where the outflow of the cannula is directed to the first vessel, while the inflow is drawn from the second vessel. Further still, it should be appreciated that in one application the inflow lumen could be positioned to draw blood from a peripheral or non-primary vessel at the site of entry into the patient while the outflow could be positioned in the aorta, proximate an arterial branch.

The pump of the present invention may be a continuous flow pump, a pulsatile pump, and/or a hybrid pump that is configured to generate flow in both a continuous and pulsatile format. The pump may be implantable and is used to fluidly connect two blood vessels, such as the femoral artery at the inflow and the left axillary artery at the outflow, although other peripheral or non-primary arterial and venous blood vessels are contemplated, as well as any singular and/or cumulative combination thereof. An alternative embodiment employs both a continuous flow and a pulsatile flow pump connected in parallel or in series and operating simultaneously or in an alternating fashion. Yet another alternative embodiment employs a rotary pump that is controllable in a synchronous copulsating or counterpulsating fashion, or in some out-of-phase intermediate thereof.

It is contemplated that, where the entire system of the present invention is implanted, that it be implanted subcutaneously without the need for major invasive surgery and, preferably, extrathoracically. For example, the pump may be implanted in the groin area, with the inflow conduit attached to the femoral or iliac artery proximate thereto and the outflow conduit attached to the axillary artery proximate the shoulder. It is contemplated that the outflow conduit be applied by tunneling it under the skin from the pump to the axillary artery. Alternatively, the pump and conduits may be applied intravascularly through a non-primary blood vessel in a subcutaneous application. In such an embodiment, the pump is sized and configured to be positioned within or pass through a non-primary vessel and introduced via a percutaneous insertion or a surgical cutdown with or without accompanying inflow and outflow conduits. The pump may be enclosed within a conduit through which blood may be directed, an open housing having a cage-like arrangement to shield the pump blades from damaging the endothelial lining, or a closed housing having an inlet and outlet to which inflow and outflow conduits may be respectively attached.

Where implanted, the pump is preferably powered by an implantable power source, such as for example a battery, that may be regenerated externally by an RF induction system or be replaced periodically, and/or a self-generating power source that, for example, draws energy from the human body (e.g., muscles, chemicals, heat). The pump may alternatively be powered by a rotatably driven cable extending and controlled extracorporeally.

The present invention also comprises a method for supplementing the circulation of blood in the patient and potentially reducing the workload on the heart of a patient without connecting any component to the patient's heart. The inventive method comprises the steps of implanting a pump configured to generate blood flow at volumetric rates that are on average subcardiac, wherein the pump may have an inflow and outflow conduit attached thereto and may be enclosed in an open or closed housing; fluidly connecting a distal end of the inflow conduit to a first peripheral or non-primary blood vessel with a minimally-invasive surgical procedure to permit the flow of blood to the pump from the first peripheral or non-primary blood vessel of the patient; implanting the inflow conduit subcutaneously; fluidly connecting a distal end of the outflow conduit to a second peripheral or non-primary blood vessel with a minimally-invasive surgical procedure to permit the flow of blood away from the pump to the second blood vessel of the patient; and operating said pump to perfuse blood through the patient's circulatory system. Where the peripheral blood vessel is the axillary artery, the step of connecting the distal end of the outflow conduit may be performed in such a manner that a sufficient flow of blood is directed toward the hand to avoid limb ischemia while ensuring that sufficient flow is directed toward the aorta without damaging the endothelial lining of the axillary vessel. The same concerns for avoiding limb ischemia and damage to the endothelial lining would apply, however, regardless of the selection of second peripheral or non-primary blood vessel.

In one specific application, the pump is capable of synchronous control wherein the step of operating the pump includes the steps of beginning discharge of blood out of the pump during isovolumic contraction and discontinuing discharge of blood when the aortic valve closes following systole. Depending upon the patient and the specific arrangement of the present system, this specific method results in reduced afterload and/or preload on the heart while also supplementing circulation. For example, in one application, the first and second blood vessels are the femoral and axillary arteries, respectively; or the femoral artery and the aorta, respectively. Numerous other combinations may be equally effective to achieve the benefits of the present invention.

In an alternative method of applying the present invention, the pump is not implanted and the inflow and outflow conduits are fluidly coupled to the first and second blood vessels percutaneously, using a readily-removable connector, such as a cannula, to connect the distal ends of each conduit to the blood vessels.

An important advantage of the present invention is that it utilizes the benefits of an IABP, without the requirement of extracorporeal equipment or the need to have a balloon or similar implement partially obstructing a blood vessel. In addition to the benefits of an IABP, it also offers the benefit of reducing the preload on the heart. The present invention thus offers simplicity and long-term use.

Another important advantage of the present invention is its potential to enhance mixing of systemic arterial blood, particularly in the aorta, and thereby deliver blood with a higher oxygen-carrying capacity to organs supplied by arterial side branches off of the aorta. This overcomes the problem of blood streaming in the descending aorta that may sometimes occur in patients suffering from low cardiac output or other ailments resulting in low blood flow. The lack of mixing of the blood within the descending aorta that may result from blood streaming could lead to a higher concentration of red blood cells and nutrients in the central region of the aorta and a decreasing concentration of red blood cells closer to the aortic wall. This could result in lower hematocrit blood flowing into branch arteries from the aorta. Where it is desired to address the potential problem of blood streaming, a method of utilizing the present invention may include taking steps to assess certain parameters of the patient and then to determine the minimum output of the pump that ensures turbulent flow in the aorta, thereby enhancing blood mixing. One embodiment of that method includes the step of determining the Reynolds number and the average Womersley number for the flow through the descending aorta before and/or after applying the present inventive system to the patient and adjusting the pump accordingly.

BRIEF DESCRIPTION OF THE DRAWINGS

These and other features and advantages of the invention will now be described with reference to the drawings, which are intended to illustrate and not to limit the invention.

FIG. 1 is a schematic view of a cardiac assist device, known as a left ventricular assist device, showing a bypass from the apex of the left ventricle to the aortic arch;

FIG. 2 is a schematic view of a first embodiment of the present invention, shown applied to a patient's circulatory system.

FIG. 3 is a schematic view of a second embodiment of the present invention, shown applied to a patient's circulatory system.

FIG. 4 is a schematic view of a variation of the first embodiment of FIG. 2 shown implanted into a patient;

FIG. 5 is a schematic view of a third embodiment of the present invention, shown applied to a patient's circulatory system.

FIG. 6 is a schematic view of a fourth embodiment of the present invention, shown applied to a patient's circulatory system.

FIG. 7 is a schematic view of an inflow L-shaped connector, shown inserted within a blood vessel.

FIG. 8 is a schematic view of a fifth embodiment of the present invention employing a multi-lumen catheter for single site application to a patient.

FIG. 9 is a schematic view of a sixth embodiment of the present invention showing a reservoir and a portable housing for carrying a portion of the invention directly on the patient.

FIG. 10 is a schematic view of a variation of the third embodiment of FIG. 5, shown applied to a patient's circulatory system.

FIG. 11 is a schematic view of an application of the embodiment of FIG. 2 in which the inflow conduit and outflow conduit are applied to the same non-primary blood vessel.

FIG. 12 is a schematic view of a seventh embodiment of the present invention employing an intravascular pump inserted through a non-primary vessel in which the pump is enclosed in a protective housing without inflow and outflow conduits.

FIG. 13 is a schematic view of an eighth embodiment of the present invention employing an intravascular pump inserted through a non-primary vessel in which the pump is housed within a conduit having an inlet and an outlet.

FIG. 13A is a schematic view of the pumping system of FIG. 13 wherein the pump is operated in a reverse direction;

FIG. 14 is a schematic view of a variation of the eighth embodiment of FIG. 13 in which an additional conduit is shown adjacent the conduit housing the pump, and in which the pump comprises a shaft mounted helical thread.

FIG. 14A is a schematic view of the pumping system of FIG. 14 wherein the pump is operated in a reverse direction.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Turning now to the drawings provided herein, a more detailed description of the embodiments of the present invention is provided below. It should be noted, however, that while some embodiments have all of the advantages identified herein, other embodiments may only realize some but not all of the advantages.

The present invention provides a heart assist system that is extracardiac in nature. In other words, the present invention supplements blood perfusion, without the need to interface directly with the heart and aorta. Thus, no major invasive surgery is necessary to use the present invention. The present invention also lessens the hemodynamic burden or workload on the heart by reducing the pressure at the aortic root during systole (afterload) and/or reducing left ventricular end diastolic pressure and volume (preload).

With reference to FIG. 2, a first embodiment of the present invention 10 is shown applied to a patient 12 having an ailing heart 14 and an aorta 16 , from which peripheral brachiocephalic blood vessels extend, including the right subclavian 18 , the right carotid 20 , the left carotid 22 , and the left axillary 24 . Extending from the descending aorta is another set of peripheral blood vessels, the left and right femoral arteries 26 , 28 .

The first embodiment 10 comprises a pump 32 , having an inlet 34 and an outlet 36 for connection of flexible conduits thereto. The pump 32 is preferably a rotary pump, either an axial type or a centrifugal type, although other types of pumps may be used, whether commercially-available or customized. In either case, the pump should be sufficiently small to be implanted subcutaneously and preferably extrathoracically, for example in the groin area of the patient, without the need for major invasive surgery. Because the present invention is an extracardiac system, no valves are necessary. Any inadvertent backflow through the pump and/or through the inflow conduit would not harm the patient.

Regardless of the style or nature chosen, the pump 32 of the present invention is sized to generate blood flow at subcardiac volumetric rates, less than about 50% of the flow rate of an average healthy heart, although flow rates above that may be effective. Thus, the pump 32 of the present invention is sized and configured to discharge blood at volumetric flow rates anywhere in the range of 0.1 to 3 liters per minute, depending upon the application desired and/or the degree of need for heart assist. For example, for a patient experiencing advanced congestive heart failure, it may be preferable to employ a pump that has an average subcardiac rate of 2.5 to 3 liters per minute. In other patients, particularly those with minimal levels of heart failure, it may be preferable to employ a pump that has an average subcardiac rate of 0.5 liters per minute or less. In yet other patients it may be preferable to employ a pump that is a pressure wave generator that uses pressure to augment the flow of blood generated by the heart.

In one embodiment, the pump selected is a continuous flow pump so that blood perfusion through the circulation system is continuous. In an alternative embodiment, the pump selected has the capability of synchronous actuation; i.e., it may be actuated in a pulsatile mode, either in copulsating or counterpulsating fashion.

For copulsating action, it is contemplated that the pump 32 would be actuated to discharge blood generally during systole, beginning actuation, for example, during isovolumic contraction before the aortic valve opens or as the aortic valve opens. The pump would be static while the aortic valve is closed following systole, ceasing actuation, for example, when the aortic valve closes.

For counterpulsating actuation, it is contemplated that the pump 32 would be actuated generally during diastole, ceasing actuation, for example, before or during isovolumic contraction. Such an application would permit and/or enhance coronary blood perfusion. In this application, it is contemplated that the pump would be static during the balance of systole after the aortic valve is opened, to lessen the burden against which the heart must pump. The aortic valve being open encompasses the periods of opening and closing, wherein blood is flowing therethrough.

It should be recognized that the designations copulsating and counterpulsating are general identifiers and are not limited to specific points in the patient's heart cycle when the pump begins and discontinues actuation. Rather, they are intended to generally refer to pump actuation in which the pump is actuating, at least in part, during systole and diastole, respectively. For example, it is contemplated that the pump might be activated to be out of phase from true copulsating or counterpulsating actuation described herein, and still be synchronous, depending upon the specific needs of the patient or the desired outcome. One might shift actuation of the pump to begin prior to or after isovolumic contraction or to begin before or after isovolumic expansion.

Furthermore, the pulsatile pump may be actuated to pulsate asynchronously with the patient's heart. Typically, where the patient's heart is beating irregularly, there may be a desire to pulsate the pump asynchronously so that the perfusion of blood by the extracardiac pumping system is more regular and, thus, more effective at oxygenating the organs. Where the patient's heart beats regularly, but weakly, synchronous pulsation of the extracardiac pump may be preferred.

The pump 32 is driven by a motor 40 and/or other type of drive means and is controlled preferably by a programmable controller 42 that is capable of actuating the pump in pulsatile fashion, where desired, and also of controlling the speed or output of the pump. For synchronous control, the patient's heart would preferably be monitored with an EKG in which feedback would be provided the controller 42 . The controller 42 is preferably programmed by the use of external means. This may be accomplished, for example, using RF telemetry circuits of the type commonly used within implantable pacemakers and defibrillators. The controller may also be autoregulating to permit automatic regulation of the speed, and/or regulation of the synchronous or asynchronous pulsation of the pump, based upon feedback from ambient sensors monitoring parameters, such as pressure or the patient's EKG. It is also contemplated that a reverse-direction pump be utilized, if desired, in which the controller is capable of reversing the direction of either the drive means or the impellers of the pump. Such a pump might be used where it is desirable to have the option of reversing the direction of circulation between two peripheral blood vessels.

Power to the motor 40 and controller 42 may be provided by a power source 44 , such as a battery, that is preferably rechargeable by an external induction source (not shown), such as an RF induction coil that may be electromagnetically coupled to the battery to induce a charge therein. Alternative power sources are also possible, including a device that draws energy directly from the patient's body; e.g., the patient's muscles, chemicals or heat. The pump can be temporarily stopped during recharging with no appreciable life threatening effect, because the system only supplements the heart, rather than substituting for the heart.

While the controller 42 and power source 44 are preferably pre-assembled to the pump 32 and implanted therewith, it is also contemplated that the pump 32 and motor 40 be implanted at one location and the controller 42 and power source 44 be implanted in a separate location. In one alternative arrangement, the pump 32 may be driven externally through a percutaneous drive line. In another alternative, the pump, motor and controller may be implanted and powered by an extracorporeal power source. In the latter case, the power source could be attached to the side of the patient to permit fully ambulatory movement.

The inlet 34 of the pump 32 is preferably connected to a flexible inflow conduit 50 and a flexible outflow conduit 52 to direct blood flow from one peripheral blood vessel to another. The inflow and outflow conduits 50 , 52 may, for example, be formed from Dacron, Hemashield or Gortex materials, although other synthetic materials may be suitable. The inflow and outflow conduits 50 , 52 may also comprise biologic materials or pseudobiological (hybrid) materials (e.g., biologic tissue supported on a synthetic scaffold). The inflow and outflow conduits are preferably configured to minimize kinks so blood flow is not meaningfully interrupted by normal movements of the patient or compressed easily from external forces. In some cases, the inflow and/or outflow conduits may come commercially already attached to the pump. Where it is desired to implant the pump 32 and the conduits 50 , 52 , it is preferable that the inner diameter of the conduits be less than 25 mm, although diameters slightly larger may be effective.

In one preferred application of the present invention, the first embodiment is applied in an arterial-arterial fashion; for example, as a femoral-axillary connection, as is shown in FIG. 2. It should be appreciated by one of ordinary skill in the art that an axillary-femoral connection would also be effective using the embodiments described herein. Indeed, it should be recognized by one of ordinary skill in the art that the present invention might be applied to any of the peripheral blood vessels in the patient. In an alternative arrangement, as shown in FIG. 11, the first embodiment may be applied so that the inflow conduit and the outflow conduit are applied subcutaneously to the same non-primary vessel, in any manner described herein.

The inflow conduit 50 has a first proximal end 56 that connects with the inlet 34 of the pump 32 and a second distal end 58 that connects with a first peripheral blood vessel, which is preferably the left femoral artery 26 of the patient 12 , although the right femoral artery or any other peripheral artery may be acceptable. In one application, the connection between the inflow conduit 50 and the first blood vessel is via an end-to-side anastomosis, although a side-to-side anastomosis connection might be used mid-stream of the conduit where the inflow conduit were connected at its second end to an additional blood vessel or at another location on the same blood vessel (neither shown).

Similarly, the outflow conduit 52 has a first proximal end 62 that connects to the outlet 36 of the pump 32 and a second distal end 64 that connects with a second peripheral blood vessel, preferably the left axillary artery 24 of the patient 12 , although the right axillary artery, or any other peripheral artery, would be acceptable. In one application, the connection between the outflow conduit 52 and the second blood vessel is via an end-to-side anastomosis, although a side-to-side anastomosis connection might be used mid-stream of the conduit where the outflow conduit were connected at its second end to yet another blood vessel (not shown) or at another location on the same blood vessel. Preferably, the outflow conduit is attached to the second blood vessel at an angle that results in the predominant flow of blood out of the pump proximally toward the aorta and heart, such as is shown in FIG. 2, while still maintaining sufficient flow distally toward the hand to prevent limb ischemia.

It is preferred that application of the present invention to the peripheral or non-primary blood vessels be accomplished subcutaneously; i.e., at a shallow depth just below the skin or first muscle layer so as to avoid major invasive surgery. It is also preferred that the present invention be applied extrathoracically to avoid the need to invade the patient's chest cavity. Where desired, the entire extracardiac system of the present invention 10 may be implanted within the patient 12 , either extravascularly or intravascularly or a hybrid thereof. In the case of an extravascular application, the pump 32 may be implanted, for example, into the groin area, with the inflow conduit 50 fluidly connected subcutaneously to, for example, the femoral artery 26 proximate the pump 32 . The outflow conduit would be tunneled subcutaneously through to, for example, the left axillary artery 24 . In an alternative arrangement, the pump 32 and associated drive and controller could be temporarily fastened to the exterior skin of the patient, with the inflow and outflow conduits 50 , 52 connected percutaneously. In either case, the patient may be ambulatory without restriction of tethered lines.

Referring to FIG. 11, an alternative method of using the present invention comprises the steps of fluidly coupling the inflow conduit 50 , which is fluidly coupled to pump 32 , to a patient subcutaneously to a non-primary blood vessel, either via an anastomosis connection or percutaneously with a cannula 54 , fluidly coupling the outflow conduit 52 to the same blood vessel in a desired manner described herein, directing blood from the blood vessel through the inflow conduit, through the pump and the outflow conduit into the blood vessel. In the application of FIG. 11, the system is positioned at the patient's left femoral artery. Specific applications of this alternative method may further comprise positioning the inflow conduit upstream of the outflow conduit, although the reverse arrangement is also contemplated. It is also contemplated that either the inflow conduit or the outflow conduit may extend through the non-primary blood vessel to a second blood vessel (e.g., through the left femoral to the aorta proximate the renal branch) so that blood may be directed from the first to the second blood vessel or vice versa.

It is contemplated that, where an anastomosis connection is not desired, a special connector may be used to connect the conduits 50 , 52 to the peripheral blood vessels. With reference to FIG. 3, a second embodiment of the present invention is shown, wherein the inflow conduit 50 and outflow conduit 52 are connected to the peripheral blood vessels via first and second connectors 68 , 70 each comprising three-opening fittings. In the preferred embodiment, the connectors 68 , 70 comprise an intra-vascular, generally-tee-shaped fitting 72 having a proximal end 74 , a distal end 76 , and an angled divergence 78 permitting connection to the inflow and outflow conduits 50 , 52 and the blood vessels. The proximal and distal ends 74 , 76 of the fittings 72 permit connection to the blood vessel into which the fitting is positioned. The angle of divergence 78 of the fittings 72 may be 90 degrees or less in either direction from the axis of flow through the blood vessel, as optimally selected to generate the needed flow distally toward the hand to prevent limb ischemia, and to insure sufficient flow and pressure toward the aorta to provide the circulatory assistance and workload reduction needed while minimizing or avoiding endothelial damage to the vessel. In another embodiment, the connectors 68 , 70 are sleeves (not shown) that surround and attach to the outside of the peripheral blood vessel where, within the interior of the sleeve, a port to the blood vessel is provided to permit blood flow from the conduits 50 , 52 when they are connected to the connectors 68 , 70 , respectively.

Other types of connectors having other configurations are contemplated that may avoid the need- for an anastomosis connection or that permit connection of the conduits to the blood vessels. For example, it is contemplated that an L-shaped connector be used if it is desired to withdraw blood more predominantly from one direction of a peripheral vessel or to direct blood more predominantly into a peripheral vessel. Referring to FIG. 7, an inflow conduit 50 is fluidly connected to a peripheral vessel, for example, the left femoral artery 26 , using an L-shaped connector 310 . The connector 310 has an inlet port 312 at a proximal end and an outlet port 314 through which blood flows into the inflow conduit 50 . The connector 310 also has an arrangement of holes 316 within a wall positioned at a distal end opposite the inlet port 312 so that some of the flow drawn into the connector 310 is diverted through the holes 312 , particularly downstream of the connector, as in this application. A single hole in the wall could also be effective, depending upon size and placement. The connector may be a deformable L-shaped catheter percutaneously applied to the blood vessel or, in an alternative embodiment, be connected directly to the walls of the blood vessel for more long term application. By directing some blood flow downstream of the connector during withdrawal of blood from the vessel, ischemic damage downstream from the connector may be avoided. Such ischemic damage might otherwise occur if the majority of the blood flowing into the inflow connector were diverted from the blood vessel into the inflow conduit. It is also contemplated that a connection to the blood vessels might be made via a cannula, wherein the cannula is implanted, along with the inflow and outflow conduits.

The advantage of discrete connectors is their potential application to patients with chronic CHF. A connector eliminates a