US3667069A - Jet pump cardiac replacement and assist device and method of at least partially replacing a disabled right heart - Google Patents
Jet pump cardiac replacement and assist device and method of at least partially replacing a disabled right heart Download PDFInfo
- Publication number
- US3667069A US3667069A US23388A US3667069DA US3667069A US 3667069 A US3667069 A US 3667069A US 23388 A US23388 A US 23388A US 3667069D A US3667069D A US 3667069DA US 3667069 A US3667069 A US 3667069A
- Authority
- US
- United States
- Prior art keywords
- nozzle
- driving
- suction
- heart
- suction nozzle
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/20—Type thereof
- A61M60/205—Non-positive displacement blood pumps
- A61M60/211—Non-positive displacement blood pumps using a jet, venturi or entrainment effect for pumping the blood
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/126—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel
- A61M60/148—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable via, into, inside, in line, branching on, or around a blood vessel in line with a blood vessel using resection or like techniques, e.g. permanent endovascular heart assist devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/165—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart
- A61M60/178—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body implantable in, on, or around the heart drawing blood from a ventricle and returning the blood to the arterial system via a cannula external to the ventricle, e.g. left or right ventricular assist devices
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/10—Location thereof with respect to the patient's body
- A61M60/122—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body
- A61M60/196—Implantable pumps or pumping devices, i.e. the blood being pumped inside the patient's body replacing the entire heart, e.g. total artificial hearts [TAH]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/40—Details relating to driving
- A61M60/403—Details relating to driving for non-positive displacement blood pumps
- A61M60/405—Details relating to driving for non-positive displacement blood pumps the force acting on the blood contacting member being hydraulic or pneumatic
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M60/00—Blood pumps; Devices for mechanical circulatory actuation; Balloon pumps for circulatory assistance
- A61M60/50—Details relating to control
- A61M60/508—Electronic control means, e.g. for feedback regulation
- A61M60/577—High-frequency driving
Definitions
- the jet pump device is an elongated tubular structure including an upstream driving nozzle from which a driving flow of arterial blood under pressure is ejected into a suction nozzle creating a zone of reduced pressure to cause venous blood to be sucked into and admixed with the driving flow for. distribution to the pulmonary circulation system.
- the pump may be powered by.
- FIG- 7 DESIGN CRITERIA AORTIC PRESSURE, mm Hg DESIGN POINT DESIGN CRITERIA AORTIC PRESSURE: 100 mm Hg VENOUS PRESSURE: mm Hg PULMONARY ARTERIAL PRESSURE: I7mm H VENOUS FLOW RATE: 6 L/min,
- FIG- 5 En I E E u? AORTIC PRESSURE: 100mm Hg 05 6 VENOUS massuns: o'mm H 3 VENOUS FLOW RATE: 6 L/min. W PULMONARY ARTERIAL PRESSURE: VARIABLE l5 D I: w .A ...J E 5 s u: LU l0 cr 4 E 11 LL! 6 5 l- 3 2 l! J g n. o O .2 u.
- This invention relates to an implantable jet pump cardiac replacement device and more particularly to a jet pump right ventricle replacement device. to work in conjunction with left ventricle support yielding total heart support.
- the present death rate from acute transmural myocardial infarction in coronary care units today is primarily because of power failure of the heart. This includes patients who are in cardiogenic shock and/or congestive heart failure. Although heart transplants ofier some hope, further significant lowering of the mortality rate depends largely on an artificial heart or satisfactory cardiac replacement and assist units.
- the present invention is directed, as an alternative, to a jet pump system to replace, assist, or bypass the right ventricle function, which will couple with any left heart.
- this system constitutes a total heart replacement. Specifically, many of the problems associated with two identical pumps have been eliminated.
- jet pumps have never been applied to the circulation, they have been investigated for over 100 years. Presently, they are used in deep well pumping, in aircraft lubrication systems, as booster pumps, and in many other fields in design configurations not markedly difierent from those of the present invention. Excellent papers are found in the literature that accurately predict the performance of a particular pump design from theoretical considerations.
- FIG. 1 is a schematic representation of a jet pump
- Fig. 2 is a longitudinal section of one jet pump design
- FIG. 3 is a transverse section on the line 33 of FIG. 2 and in the direction of the arrows;
- FIG. 4 is a schematic representation of a jet pump in place in the heart as a replacement for the right heart;
- FIG. 5 is a schematic representation of a jet pump in place in the heart as an assist to the right heart;
- FIG. 6 is a schematic representation of the circulatory system including a jet pump as a right heart replacement
- FIG. 7 is a graphic representation of pulmonary arterial head generated as a function of driving flow rate
- FIG. 8 is a graphic representationof the effect of venous flow rate on pulmonary arterial pressure
- FIG. 9 is a graphic representation of pulmonary arterial head generated as a function of driving head for difl'erent values of venous flow rate.
- FIGS. 10, ll, 12, and 13 are modified forms of jet pump shown in longitudinal section.
- a jet pump is basically a device by means of which one fluid is pumped by the action of mixing with another fluid.
- the pump indicated generally at 10, is so simple that it entails no moving parts.
- the fluid which perfomis the pumping action is termed the driving flow, and the fluid to be pumped is termed the suction flow.
- the driving flow results from the high pressure of an independent source.
- the pump may take a variety of different specific forms.
- High pressure driving fluid from a driving flow line 1] mixes with low pressure suction fluid from a suction plenum or chamber 12 in a mixing chamber 13, resulting in a total head intermediate between the driving and suction heads.
- the suction plenum 12 and mixing chamber 13 are interconnected through a restricted annular orifice 14 between an inner driving nozzle 15 and an outer concentric suction nozzle 16.
- the driving nozzle may be held spaced within the suction nozzle as by means of radial struts 17.
- the pressure energy of the driving flow from flow line 11 is converted into velocity energy by means of the drivingnozzle 15.
- the static pressure is reduced to a value lower than in the suction plenum 12.
- the suction fluid is entrained into the suction nozzle 16.
- the two flows exchange momentum by turbulent mixing in the mixing chamber 13. It is customary to add a diverging tubular diffuser 18 to convert the velocity head in the mixing chamber 13 into pressure head at the diffuser exit 19. g
- the invention includes the application of a jet pump as either (l) a replacement [FIG. 4], or (2) an assist to the right heart [FIG. 5].
- a jet pump as either (l) a replacement [FIG. 4], or (2) an assist to the right heart [FIG. 5].
- the pump when used as a replacement, the pump is placed into the venous circuit so that the suction flow is venous blood taken from the right atrium and the cavae.
- the sole purpose of the jet pump will be to generate the pulmonary arterial pressure and flow.
- the pressure source for the driving fluid of the jet pump is the left heart, or its artificial replacement. There is no limitation in regard to the type of left heart replacement used.
- Oneform of artificial'replacement is a blood pump as described in copending application Ser. No. 816,952 filed Apr. 17, 1969 by Dorman et al., now US. Pat. No.
- FIG. 6 A schematic representation of the jet pump placed into the circulation as a right heart replacement is shown in FIG. 6.
- the driving fluid is realized from the aorta or one of its branches and is mixed with the venous blood in the jet pump.
- the combined flow is then passed into the pulmonary circulation at the proper head.
- the pulmonary flow necessarily exceeds the systemic flow by an amount equal to the driving flow. This increase in pulmonary flow is not a significant factor, since it has been shown by several investigators that pulmonary flow may be increased three to four fold with little or no increase in pulmonary arterial pressure. However, the mag-. nitude of this driving flow is of importance, and is minimized by careful design.
- Shunts such as shown schematically at 20 and 21 may be used to reduce the volume of flow to the pulmonary circulation.
- the pulmonary circulation system may include an artificial lung.
- an optimum pump may be designed, and the driving flow r'ate calculated.
- FIG. 7 represents the pulmonary arterial head generated as a function of driving flow rate. Each location on the curve refers to different optimum pump dimensions. The right ventriele must generate on the average a head of 17 mm Hg. From the graph, it is seen that the driving flow rate must be about 4 liters/min. At flow rates not exceeding about 2.5 liters/min, the operation of the pump is impaired due to low Reynolds numbers.
- the driving flow rate is dependent solely upon the driving pressure and the driving nozzle diameter and profile (shape of nozzle). In fact, the driving nozzle velocity depends only upon the driving pressure and nozzle profile, so that the flow rate is governed by the chosen noule. No control is necessary. At 100 mm Hg, the driving nozzle velocity is about 500 cm/sec.
- FIG. 8 is a graph of the effect of venous flow rate on pulmonary arterial pressure, assuming-the pump is not operated at the design point.
- 17 mm Hg are generated at 6 liters/min.
- the pulmonary pressure is about 22 and 11 mm Hg, respectively. Because the driving 'head is fixed at 100 mm Hg, the driving flow rate can be read from FIG. 7 at a head of 17 mm Hg, giving 4 liters/min.
- FIG. 9 is a plot of pulmonary arterial head generated as a function of driving head (aortic pressure) for different values of venous flow rate.
- the top, middle, and bottom curves correspond to venous flow rates of 3, 6, and 9 liters/min. Because the driving nozzle diameter is fixed, the driving flow rate is dependent only upon driving pressure.
- the three driving flow rates, for pressures of 120, 100, and 80 mm Hg, are about 3.5, 4.0, and 4.4 liters/min, respectively.
- the pulmonary arterial pressure varies-from about 12 to 22 mm Hg, as the driving pressurevaries from 80 to 120 mm Hg (e.g., pulsatile driving pressure).
- FIG. 2 A typical jet pumpdesign for circulation application is illustrated inFIG. 2. It is designed for the specifications:
- the driving nozzle diameter is desirably between about 0.2 and 0.6 cm, with a mixing chamber diameter of between about 0.25 and 2.0 cm.
- the mixing chamber length may be up to mixing chamber diameters.
- the suction nozzle tapers inwardly from a diameter between about 0.5 and 2.5 centimeters to between about 0.25 and 2 centimeters over a length between about 0.2 and l centimeter.
- a difiuser is optional, particularly in the case of infants. When present, it may have a taper between about 6 and 30.
- the diffuser exits with a diameter which matches the pulmonary artery diameter, e.g., about 1 to 2.5 cm.
- the total length of the pump, without tubing connections, is desirably on the order of 8 to '10 cm.
- the maximum outside diameter is desirably no more than 2 cm.
- the driving nozzle is permanently attached to the mixing chamber, the mixing chamber and diffuser being of uni-construction.
- FIGS. 10 through 13 there are shown in longitudinal section modified forms of jet pump which are illustrative of the wide variety of specific jet pump design which may be utilized in the practice of the present invention.
- the parts are numbered to correspond to those of FIGS. 1 and 2 with suffix'es A through D added.
- suffix'es A through D added.
- the driving flow line 11A extends along the longitudinal axis through the end of the housing enclosing the suction chamber 12A.
- the mixing chamber. 13C, restricted orifice 14A, driving nozzle 15A, suction nozzle 16A and diffuser 18A are all as previously described.
- FIG. 11 there is shown a Coanda type jet pump 108 in which the driving fluid is introduced through a flow line 1 1B and radial port into an annular channel 21 whose inner annular opening forms a jet driving nozzle 158.
- the opening tapers radially inwardly and extends downstream.
- the driving fluid under high pressure exits from the driving nozzle and is diverted in a downstream direction by the -Coanda effect creating the zone of lower pressure to draw fluid from the upstream suction chamber 12B through suction nozzle 16B.
- the mixing chamber 13B and difiuser 18B are as already described.
- FIG. 12 there is shown a somewhat similar type of pump 10C in which the driving fluid enters an annular chamber 22 in the housing through a radially extending port from driving flow line 11C.
- the driving fluid is ejected radially inwardly and is diverted downstream from the annular jet driving nozzle 15C to draw fluid through the suction nozzle 16C from the suction chamber 12C, which inrthe case of a circulation application may be the heart or a tube connecting to the heart.
- the mixing chamber 13C and diffuser 18C are as alread described.
- FIG. 13 there is shown a further modified form of jet pump 10D.
- the driving flow line' llD, orifice 14D, driving nozzle 15D and suction nozzle 16D are generally as described in connection with FIGS. 1 and 2.
- this form of pump has no diffuser as such. Instead, the upstream end of mixing chamber 13D is provided with an annular cavity 23 of enlarged diameter surrounding the end of suction nozzle 16D.
- jet pump The advantages of a jet pump are numerous. There are no moving parts, or mechanical drive-train, as with conventional pumps. No valves are needed. It can be lightweight, as rugged as desired, and small. Since the device is made of substantially rigid, substantially non-flexing material, there are no parts to wear out, dictating long tenn, dependability. Of prime. consideration is that the pump characteristics can be predicted successfully. The efficiencies are high due to all energy losses being confined to fluid friction and mixing losses.
- the jet pump is a device that can take advantage, in regard to size, of the small work output of theright heart, whereas ventricular type pumps may not.
- the jet pump is small and can be used with any left ventricular pump, including the natural left heart.
- the right heart need not be excised.
- the absence of valves and moving parts is ideal. Surgical installation techniques are simple.
- a total heart replacement is realized. External power is only to the left heart pump. If necessary, the right heart jet pump may be controlled, either through left heart control or by means of a valve in the driving flow. The latter involves regulating the driving flow.
- jet pump Further advantages of the jet pump include: (1) minimal construction costs, (2) construction from almost any material, (3) disposability, (4) ease in sterilization, (5) can be coated with non-thrombogenic material, (6) high efficiency, (7) no service necessary, (8) simple and reproducible calibration, and (9) no heat transfer involvement.
- Hemolysis may be important in two parts of the pump-the driving noule and the mixing chamber.
- the driving noale jets blood at a velocity of about 500 cm/sec, and the flow is turbulent.
- the average velocity is reduced to about 200 cm/sec. prior to the diffuser, but the flow is also turbulent.
- Cavitation is often a concern in the mixing chamber of water jet pumps.
- the minimum mixing chamber pressure is about 20 mm Hg. At least 350 mm Hg of negative pressure is needed to induce blood cavitation. Thus, no cavitation is expected in the jet pump.
- Blood clotting has been a continual problem in extracorporeal circuits.
- a jet pump has no dead spaces or stagnation regions, the difiuser being designed for no flow separation. Clotting is thus retarded, and the problem is of the same, or of a smaller, order of magnitude as in all other heart pumps.
- the pump may be made of any of a variety of rigid and semi-rigid materials which are capable of maintaining the shape and alignment of the parts and are compatible with blood.
- the pump may be electroformed by electroplating nickel over an expendable core and after removal of the core plated with gold or coated with a synthetic resin. It may be formed from polycarbonate.
- the pump must be made of, or coated with, an anti-thrombogenic and anti-hemolytic material.
- the entire pump may I desirably be manufactured from low energy materials, examples of which include fluorinated carbon based resins and fluorinated silicone rubbers.
- An implantable jet pump cardiac replacement and assist device comprising:
- a suction plenum upstream from and in fluid communication with said suction nozzle, said plenum including means for connection to receive venous blood of the recipient living being,
- G a discharge outlet downstream from said mixing chamber
- H means for connecting said discharge outlet to the pulmonary circulation system of the recipient living being.
- a device according to claim 1 further characterized in that:
- said driving nonle is of lesser diameter than and upstream from the suction nozzle
- a device according to claim 1 further characterized in that:
- said driving noule is an annular orifice tapering radially inwardly and encircling the downstream end of said suction nonle
- annular chamber of greater diameter and greater cross-sectional area surrounds said driving nozzle
- said driving nozzle is in direct fluid communication with said annular chamber and said annular chamber is in direct fluid communication with said means for connection with a source of arterial blood.
- a device further characterized in that said discharge outlet comprises an outwardly tapered diffuser.
- a device further characterized in that the blood contacting surfaces of the inside of the housing, the inside of the suction nozzle, the inside and outside of the drive nonle, the inside of the suction plenum, the inside of the mixing chamber and the inside of said connecting means and discharge outlet are comprised of an anti-thrombogenic and anti-hemolytic material.
- a jet pump cardiac replacement and assist device comprising:
- suction nozzle inlet adjacent to the upstream end of said housing, said suction nozzle tapering inwardly from a diameter between about 0.5 to 2.5 cen timeters to between about 0.25 to 2 centimeters over a length between about 0.2 to l centimeter,
- G means for connecting said driving nozzle to a source of arterial blood
- a mixing chamber within said housing downstream from said suction and driving nozzles and in fluid communication therewith, the diameter of said mixing chamber being between about 0.25 to 2 centimeters and its length being up to ten times its diameter
- J. means for connecting said discharge outlet to the pulmonary circulation system.
- a device further characterized in that said discharge outlet comprises an outwardly tapered diffuser of between about 6 and 30 and an exit diameter between about 1 to 2.5 centimeters corresponding to the diameter of the pulmonary artery.
- a method of at least partially replacing a disabled right heart in a living being which comprises:
- A. connecting to a source of arterial blood under pressure the upstream end of the driving noule of a jet pump comprising:
- a method according to claim 8 further characterized in that the driving nonle is connected to the aorta.
- a method according to claim 8 mrther characterized in that the driving nozzle is connected to an artificial pump replacement for the left heart.
- a method according to claim 8 further characterized in thatthetricuspidandpulmonaryvalveaofaaid rightheartare made incompetent and said jet pump is implanted within the heart between the right ventricle and pulmonary artery as a total replacement of the right heart.
- a method according to claim 8 further characterized in that one end of said jet pump is connected externally of the hearttotherightatriumoftheheartandtheotherendofsaid pump is connected externally of the heart to the pulmonary arteryinparallelwiththerightheartasanassisttotheright heart.
Landscapes
- Health & Medical Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Engineering & Computer Science (AREA)
- Cardiology (AREA)
- Biomedical Technology (AREA)
- Anesthesiology (AREA)
- Mechanical Engineering (AREA)
- Hematology (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Vascular Medicine (AREA)
- External Artificial Organs (AREA)
Abstract
An implantable jet pump cardiac replacement device and method for replacing or assisting the right heart. The jet pump device is an elongated tubular structure including an upstream driving nozzle from which a driving flow of arterial blood under pressure is ejected into a suction nozzle creating a zone of reduced pressure to cause venous blood to be sucked into and admixed with the driving flow for distribution to the pulmonary circulation system. The pump may be powered by blood pumped by the left heart or an artificial replacement for the left heart.
Description
Unite States atent Blackshear et a1.
[ 1 June6, 1972 Paul; Demelre M. Nicoloff, Minneapolis, all of Minn.
[73] Assignee:
The Regents of the University of Minnesota, Minneapolis, Minn.
[22] Filed: Mar. 27, 1970 [21] AppLNo; 23,388
[52] US. Cl ..3/1, 3/DIG. 2, 128/1 R, 417/194, 417/195, 417/196 [51] Int. Cl ..A63f 1/24, F04f 5/00, F04f5/36, F04f 5/44 [58] FieldofSearch ..3/1,DIG.2;128/1R,214, 128/D1G. 3; 417/183, 194, 195, 196
[56] References Cited UNITED STATES PATENTS 2,173,330 9/1939 Gregg ..417/l96 X RIGHT SUBCLAVIAN A R TE RY RIGHT ATRIUM 2,085,361 6/1937 I-Iellmer ..4l7/195 3,526,906 9/1970 De Laszlo ..3/l
OTHER PUBLICATIONS Jet-Pump Theory and Performance With Fluids of High Viscosity" by R. G. Cunningham, Transactions of the ASME, Vol. 79, No. 2, pages 1807- 1820, 1957 Primary Examiner--Da1ton L. Truluck Assistant Examiner-Ronald L. Frinks Attorney-Burd, Braddock and Bartz ABSTRACT An implantable jet pump cardiac replacement device and method for replacing or assisting the right heart. The jet pump device is an elongated tubular structure including an upstream driving nozzle from which a driving flow of arterial blood under pressure is ejected into a suction nozzle creating a zone of reduced pressure to cause venous blood to be sucked into and admixed with the driving flow for. distribution to the pulmonary circulation system. The pump may be powered by.
blood pumped by the left heart or an artificial replacement for the left heart.
12 Claims, 13 Drawing Figures PULMONARY VALVE INTACT Y TRICUSPID VALVE INTACT PATENTEDJUH 6 I972 3. 667, 069
saw 2 or 4 RIGHT SUBCLAVIAN ARTERY MADE INCOMPETENT N RY v CIRCULATION RIGHT ATRIUM //Z0 /0 LEFT TRICUSPID VALVE 4 HEART MADE INCOMPETENT JET PUMP AORTA REPLACEMENT 0F RIGHT HEART RIGHT SUBCLAVIAN ARTERY SYSTEMIC PULMONARY VALVE C'RCULATION INTACT FIG. 5'
RIGHT ATRIUM TRICUSPID VALVE INTACT PATENTEBJUN 6 I912 SHEET 3 BF FIG- 7 DESIGN CRITERIA AORTIC PRESSURE, mm Hg DESIGN POINT DESIGN CRITERIA AORTIC PRESSURE: 100 mm Hg VENOUS PRESSURE: mm Hg PULMONARY ARTERIAL PRESSURE: I7mm H VENOUS FLOW RATE: 6 L/min,
2 I 4 a 8 l0 VENOUS FLOW RATE, LITERS/min.
FIG- 5 En I E E u? AORTIC PRESSURE: 100mm Hg 05 6 VENOUS massuns: o'mm H 3 VENOUS FLOW RATE: 6 L/min. W PULMONARY ARTERIAL PRESSURE: VARIABLE l5 D I: w .A ...J E 5 s u: LU l0 cr 4 E 11 LL! 6 5 l- 3 2 l! J g n. o O .2 u.
o Z u: a
l l I l l O 5 IO I5 20 PULMONARY ARTERIAL PRESSURE, mm Hg 3 LITERS /min. I?
a; VENOUS FLOW RATE 3 g 20 m DESIGN POINT 0: CL 9 .J i l5" 0: LL] u: 4 0- DESIGN CRITERIA cz AORTIC PRESSURE: I00 mm Hg 2 venous PRESSURE OmmHq v O 5 PULMONARY ARTERlAL PRESSURE: n m 5 VENOUS FLOW RATE: 6 L/min. 3 EL 0 v I l J 60 '80 I00 \20 I40 I JET PUMP CARDIAC REPLACEMENT AND ASSIST DEVICE AND IVIETHOD OF AT LEAST PARTIALLY REPLACING A DISABLED RIGHT HEART The invention described herein-was made in the course of work under a grant or award from the Department of Health, Education and Welfare.
This invention relates to an implantable jet pump cardiac replacement device and more particularly to a jet pump right ventricle replacement device. to work in conjunction with left ventricle support yielding total heart support.
The present death rate from acute transmural myocardial infarction in coronary care units today is primarily because of power failure of the heart. This includes patients who are in cardiogenic shock and/or congestive heart failure. Although heart transplants ofier some hope, further significant lowering of the mortality rate depends largely on an artificial heart or satisfactory cardiac replacement and assist units.
In a great number of cases this necessarily means replacement of both the right and left ventricles since the coronary artery disease afi'e'cts power to both ventricles when infarction occurs. Use of one pump to replace the entire heart is complicated by higher. pressure requirements in the systemic circuit than in the pulmonary circuit. Too, exposure of the pulmonary vasculature to such high pressures is detrimental. This is amply demonstrated in patients who have a single ventricle or large ventricular septal defects. Theoretically, it is possible to pull blood through the pulmonary circuit by a negative ressure developed by an artificial left ventricle. However, the physical properties and the geometrical configuration of the pulmonary veins do not allow this, for they are prone to collapse at low negative pressures.
Left ventricular output cannot exceed right ventricular output. So typically,.pump replacements of the right ventricle have been identical to their left ventricle counterpart. This arrangement is necessary when ventricle type pumps are utilized. The precise balancing control of these two units is difficult to achieve. As another limitation, flow and pressure dictate ventricle pump size. Yet, with that system, because the left and right heart flow rates are equal, no advantage can be realized from a right heart work load which is less than percent of the total. Finally, overt hemolysis and delayed red cell damage, as well as the chance of mechanical failure, are at least doubled for two ventricle pumps.
The present invention is directed, as an alternative, to a jet pump system to replace, assist, or bypass the right ventricle function, which will couple with any left heart. In combination with a unit functioning for the left ventricle, this system constitutes a total heart replacement. Specifically, many of the problems associated with two identical pumps have been eliminated.
Although jet pumps have never been applied to the circulation, they have been investigated for over 100 years. Presently, they are used in deep well pumping, in aircraft lubrication systems, as booster pumps, and in many other fields in design configurations not markedly difierent from those of the present invention. Excellent papers are found in the literature that accurately predict the performance of a particular pump design from theoretical considerations.
The invention is illustrated by the accompanying drawings in which:
FIG. 1 is a schematic representation of a jet pump;
Fig. 2 is a longitudinal section of one jet pump design;
FIG. 3 is a transverse section on the line 33 of FIG. 2 and in the direction of the arrows;
FIG. 4 is a schematic representation of a jet pump in place in the heart as a replacement for the right heart;
FIG. 5 is a schematic representation of a jet pump in place in the heart as an assist to the right heart;
FIG. 6 is a schematic representation of the circulatory system including a jet pump as a right heart replacement;
FIG. 7 is a graphic representation of pulmonary arterial head generated as a function of driving flow rate;
FIG. 8 is a graphic representationof the effect of venous flow rate on pulmonary arterial pressure;
FIG. 9 is a graphic representation of pulmonary arterial head generated as a function of driving head for difl'erent values of venous flow rate; and
FIGS. 10, ll, 12, and 13 are modified forms of jet pump shown in longitudinal section.
As seen schematically in FIG. 1, a jet pump is basically a device by means of which one fluid is pumped by the action of mixing with another fluid. The pump, indicated generally at 10, is so simple that it entails no moving parts. The fluid which perfomis the pumping actionis termed the driving flow, and the fluid to be pumped is termed the suction flow. The driving flow results from the high pressure of an independent source. As seen hereafter, the pump may take a variety of different specific forms.
The reason that a jet pump works is quite simple. High pressure driving fluid from a driving flow line 1] mixes with low pressure suction fluid from a suction plenum or chamber 12 in a mixing chamber 13, resulting in a total head intermediate between the driving and suction heads.
The suction plenum 12 and mixing chamber 13 are interconnected through a restricted annular orifice 14 between an inner driving nozzle 15 and an outer concentric suction nozzle 16. The driving nozzle may be held spaced within the suction nozzle as by means of radial struts 17. The pressure energy of the driving flow from flow line 11 is converted into velocity energy by means of the drivingnozzle 15. At the plane of the driving nozzle exit, the static pressure is reduced to a value lower than in the suction plenum 12. Thus, the suction fluid is entrained into the suction nozzle 16. The two flows exchange momentum by turbulent mixing in the mixing chamber 13. It is customary to add a diverging tubular diffuser 18 to convert the velocity head in the mixing chamber 13 into pressure head at the diffuser exit 19. g
The invention includes the application of a jet pump as either (l) a replacement [FIG. 4], or (2) an assist to the right heart [FIG. 5]. As seen in FIG. 4, when used as a replacement, the pump is placed into the venous circuit so that the suction flow is venous blood taken from the right atrium and the cavae. The sole purpose of the jet pump will be to generate the pulmonary arterial pressure and flow. The pressure source for the driving fluid of the jet pump is the left heart, or its artificial replacement. There is no limitation in regard to the type of left heart replacement used. Oneform of artificial'replacement is a blood pump as described in copending application Ser. No. 816,952 filed Apr. 17, 1969 by Dorman et al., now US. Pat. No. 3,608,088. To consistently maintain the driving fluid pressure at a high level, the connection of flow line 11 is made to the aorta or one of its branches rather than to the left ventricle. Used with an artificial left heart, the addition of the jet pump constitutes a total heart replacement. Note that this means that the external power input to the body is only to one pump. As seen in FIG. 5, when used as an assist, the pump 10 encased in a flexible tubular housing 20 or the like is connected in parallel with the right heart.
A schematic representation of the jet pump placed into the circulation as a right heart replacement is shown in FIG. 6. The driving fluid is realized from the aorta or one of its branches and is mixed with the venous blood in the jet pump. The combined flow is then passed into the pulmonary circulation at the proper head. The pulmonary flow necessarily exceeds the systemic flow by an amount equal to the driving flow. This increase in pulmonary flow is not a significant factor, since it has been shown by several investigators that pulmonary flow may be increased three to four fold with little or no increase in pulmonary arterial pressure. However, the mag-. nitude of this driving flow is of importance, and is minimized by careful design. Shunts such as shown schematically at 20 and 21 may be used to reduce the volume of flow to the pulmonary circulation. The pulmonary circulation system may include an artificial lung.
For the application shown in FIG. 4, typical characteristics of the pump are presented, based on the work of Cunningham reported in Jet Pump Theory and Performance with Fluids of High Viscosity, Trans. Amer. Soc. Mech. Eng. 79, 2, 1807,
1957. The design criteria are:
a. Aortic pressure of 100 mm Hg,
, b. Venous pressure of mm Hg, and
c. Venous flow rate of 6 L/min.
Once the pulmonary arterial pressure is dictated, an optimum pump may be designed, and the driving flow r'ate calculated.
FIG. 7 represents the pulmonary arterial head generated as a function of driving flow rate. Each location on the curve refers to different optimum pump dimensions. The right ventriele must generate on the average a head of 17 mm Hg. From the graph, it is seen that the driving flow rate must be about 4 liters/min. At flow rates not exceeding about 2.5 liters/min, the operation of the pump is impaired due to low Reynolds numbers.
The driving flow rate is dependent solely upon the driving pressure and the driving nozzle diameter and profile (shape of nozzle). In fact, the driving nozzle velocity depends only upon the driving pressure and nozzle profile, so that the flow rate is governed by the chosen noule. No control is necessary. At 100 mm Hg, the driving nozzle velocity is about 500 cm/sec.
One pump characteristic for a jet pump is a plot of pulmo nary arterial head generated versus venous flow rate for fixed jet size. .Consider a pump designed for the aforementioned criteria and also a pulmonary arterial pressure of 17 mm Hg. FIG. 8 is a graph of the effect of venous flow rate on pulmonary arterial pressure, assuming-the pump is not operated at the design point. As specified, 17 mm Hg are generated at 6 liters/min. At 4 and 8 liters/min. the pulmonary pressure is about 22 and 11 mm Hg, respectively. Because the driving 'head is fixed at 100 mm Hg, the driving flow rate can be read from FIG. 7 at a head of 17 mm Hg, giving 4 liters/min.
A third characteristic is the effect of aortic pressure for a pump optimally designed to the above specifications. The aortic pressure is now allowed to assume values other than 100 mm Hg. FIG. 9 is a plot of pulmonary arterial head generated as a function of driving head (aortic pressure) for different values of venous flow rate. The top, middle, and bottom curves correspond to venous flow rates of 3, 6, and 9 liters/min. Because the driving nozzle diameter is fixed, the driving flow rate is dependent only upon driving pressure. The three driving flow rates, for pressures of 120, 100, and 80 mm Hg, are about 3.5, 4.0, and 4.4 liters/min, respectively. Referring to he graph, at avenous flow rate of 6 liters/min, the pulmonary arterial pressure varies-from about 12 to 22 mm Hg, as the driving pressurevaries from 80 to 120 mm Hg (e.g., pulsatile driving pressure).
A typical jet pumpdesign for circulation application is illustrated inFIG. 2. It is designed for the specifications:
a. Aortic Pressure of 100 mm Hg b. Venous pressure of 0 mm Hg c. Pulmonary arterial pressure of 17 mm Hg d. Venous flow rate of 6 liters/min.
The driving nozzle diameter is desirably between about 0.2 and 0.6 cm, with a mixing chamber diameter of between about 0.25 and 2.0 cm. The mixing chamber length may be up to mixing chamber diameters. The suction nozzle tapers inwardly from a diameter between about 0.5 and 2.5 centimeters to between about 0.25 and 2 centimeters over a length between about 0.2 and l centimeter. A difiuser is optional, particularly in the case of infants. When present, it may have a taper between about 6 and 30. The diffuser exits with a diameter which matches the pulmonary artery diameter, e.g., about 1 to 2.5 cm.
The total length of the pump, without tubing connections, is desirably on the order of 8 to '10 cm. The maximum outside diameter is desirably no more than 2 cm. Thus, the pump is quite small and compact. The driving nozzle is permanently attached to the mixing chamber, the mixing chamber and diffuser being of uni-construction.
In FIGS. 10 through 13, there are shown in longitudinal section modified forms of jet pump which are illustrative of the wide variety of specific jet pump design which may be utilized in the practice of the present invention. In each instance, the parts are numbered to correspond to those of FIGS. 1 and 2 with suffix'es A through D added. In the embodiment of FIG.
10, the driving flow line 11A extends along the longitudinal axis through the end of the housing enclosing the suction chamber 12A. The mixing chamber. 13C, restricted orifice 14A, driving nozzle 15A, suction nozzle 16A and diffuser 18A are all as previously described.
In FIG. 11, there is shown a Coanda type jet pump 108 in which the driving fluid is introduced through a flow line 1 1B and radial port into an annular channel 21 whose inner annular opening forms a jet driving nozzle 158. The opening tapers radially inwardly and extends downstream. The driving fluid under high pressure exits from the driving nozzle and is diverted in a downstream direction by the -Coanda effect creating the zone of lower pressure to draw fluid from the upstream suction chamber 12B through suction nozzle 16B. The mixing chamber 13B and difiuser 18B are as already described.
In FIG. 12, there is shown a somewhat similar type of pump 10C in which the driving fluid enters an annular chamber 22 in the housing through a radially extending port from driving flow line 11C. The driving fluid is ejected radially inwardly and is diverted downstream from the annular jet driving nozzle 15C to draw fluid through the suction nozzle 16C from the suction chamber 12C, which inrthe case of a circulation application may be the heart or a tube connecting to the heart. The mixing chamber 13C and diffuser 18C are as alread described.
In FIG. 13, there is shown a further modified form of jet pump 10D. The driving flow line' llD, orifice 14D, driving nozzle 15D and suction nozzle 16D are generally as described in connection with FIGS. 1 and 2. However, this form of pump has no diffuser as such. Instead, the upstream end of mixing chamber 13D is provided with an annular cavity 23 of enlarged diameter surrounding the end of suction nozzle 16D. It is believed that eddy currents created by the flow into cavity 23 function to convert the velocity head into a pressure head at the exit from mixing chamber 13D and thus the modified structure performs a function similar to that of a diffuserfAltematively, that portion of the pump housing downstream from the suction noule may be simply a straight segment of tubing, particularly where the pump is to be used to assist or replace the right heart of an infant.
The advantages of a jet pump are numerous. There are no moving parts, or mechanical drive-train, as with conventional pumps. No valves are needed. It can be lightweight, as rugged as desired, and small. Since the device is made of substantially rigid, substantially non-flexing material, there are no parts to wear out, dictating long tenn, dependability. Of prime. consideration is that the pump characteristics can be predicted successfully. The efficiencies are high due to all energy losses being confined to fluid friction and mixing losses.
The jet pump is a device that can take advantage, in regard to size, of the small work output of theright heart, whereas ventricular type pumps may not. The jet pump is small and can be used with any left ventricular pump, including the natural left heart. The right heart need not be excised. The absence of valves and moving parts is ideal. Surgical installation techniques are simple.
In combination with a replacement left heart, a total heart replacement is realized. External power is only to the left heart pump. If necessary, the right heart jet pump may be controlled, either through left heart control or by means of a valve in the driving flow. The latter involves regulating the driving flow.
Further advantages of the jet pump include: (1) minimal construction costs, (2) construction from almost any material, (3) disposability, (4) ease in sterilization, (5) can be coated with non-thrombogenic material, (6) high efficiency, (7) no service necessary, (8) simple and reproducible calibration, and (9) no heat transfer involvement.
Some disadvantages are present in a circulation application. The mixing process involves turbulent flow, and the velocities are modestly high. An independent pressure supply is needed for the driving flow, and this source is not considered as part of the jet pump.
Hemolysis may be important in two parts of the pump-the driving noule and the mixing chamber. At an aortic pressure of 100 mm Hg, the driving noale jets blood at a velocity of about 500 cm/sec, and the flow is turbulent. In the mixing chamber, the average velocity is reduced to about 200 cm/sec. prior to the diffuser, but the flow is also turbulent.
We have shown that by jetting plasma into. whole blood at turbulent jet velocities not exceeding 1,700 cm/sec., no hemolysis is detectable. We similarly jetted whole blood through an orifice into whole blood, and detected no hemolysis at orifice velocities less than 1,000 cm/sec. Thus, hemolysis does not appear to be significant under the conditions that exist in a jet pump.
Further evidence that the jet pump will not be excessively hemolytic is found in work by Dorman et al who tested for hemolysis a centrifugal artificial left heart pump of the type described in the aforesaid application Ser. No. 816,952. The pump turbine produced turbulent velocities of 500 cm/sec., and exited the blood through a diffuser of dimensions about equal to a jet pump diffuser. Index of hemolysis of less than 0.01 (grams per 100 liters) was measured. The jet pump hemolysis should not exceed the rate found in this centrifugal pump.
Cavitation is often a concern in the mixing chamber of water jet pumps. In a circulation application, the minimum mixing chamber pressure is about 20 mm Hg. At least 350 mm Hg of negative pressure is needed to induce blood cavitation. Thus, no cavitation is expected in the jet pump.
Blood clotting has been a continual problem in extracorporeal circuits. A jet pump has no dead spaces or stagnation regions, the difiuser being designed for no flow separation. Clotting is thus retarded, and the problem is of the same, or of a smaller, order of magnitude as in all other heart pumps.
The pump may be made of any of a variety of rigid and semi-rigid materials which are capable of maintaining the shape and alignment of the parts and are compatible with blood. For example, the pump may be electroformed by electroplating nickel over an expendable core and after removal of the core plated with gold or coated with a synthetic resin. It may be formed from polycarbonate. For long tenn support, the pump must be made of, or coated with, an anti-thrombogenic and anti-hemolytic material. The entire pump may I desirably be manufactured from low energy materials, examples of which include fluorinated carbon based resins and fluorinated silicone rubbers.
It is apparent that many modifications and variations of this invention as hereinbefore set forth may be made without departing from the spirit and scope thereof. The specific embodiments described are given by way of example only and the invention is limited only by the tenns of the appended claims.
The embodiments of the invention in which an exclusive property or privilege is claimed are defined as follows:
1. An implantable jet pump cardiac replacement and assist device comprising:
A. an elongated tubular housing, said housing being of a size adapted to implantation in a living being and of lightweight material compatible with body fluids,
B. an inwardly tapering suction nozzle inlet adjacent to the upstream end of said housing,
C. an inwardly tapering concentric driving nozzle within said tubular housing, the downstream end of said driving nozzle being in fluid communication with said suction nozzle and associated with said suction noale to create a zone of reduced pressure therein,
D. a suction plenum upstream from and in fluid communication with said suction nozzle, said plenum including means for connection to receive venous blood of the recipient living being,
E. means for connecting said driving nozzle to a source of arterial blood of the recipient living being,
F. a mixing chamber within said housing downstream from said suction and driving nozzles and in fluid communication therewith,
G. a discharge outlet downstream from said mixing chamber, and
H. means for connecting said discharge outlet to the pulmonary circulation system of the recipient living being.
2. A device according to claim 1 further characterized in that:
A. said driving nonle is of lesser diameter than and upstream from the suction nozzle,
B. an annular orifice exists between said driving nozzle and said suction nozzle,
C. means are provided to hold said nozzles concentric.
3. A device according to claim 1 further characterized in that:
A. said driving noule is an annular orifice tapering radially inwardly and encircling the downstream end of said suction nonle,
B. an annular chamber of greater diameter and greater cross-sectional area surrounds said driving nozzle, and
C. said driving nozzle is in direct fluid communication with said annular chamber and said annular chamber is in direct fluid communication with said means for connection with a source of arterial blood.
4. A device according to claim 1 further characterized in that said discharge outlet comprises an outwardly tapered diffuser.
5. a device according to claim 1 further characterized in that the blood contacting surfaces of the inside of the housing, the inside of the suction nozzle, the inside and outside of the drive nonle, the inside of the suction plenum, the inside of the mixing chamber and the inside of said connecting means and discharge outlet are comprised of an anti-thrombogenic and anti-hemolytic material.
6. A jet pump cardiac replacement and assist device comprising:
A. an elongated tubular housing,
B. an inwardly tapering suction nozzle inlet adjacent to the upstream end of said housing, said suction nozzle tapering inwardly from a diameter between about 0.5 to 2.5 cen timeters to between about 0.25 to 2 centimeters over a length between about 0.2 to l centimeter,
C. an inwardly tapering concentric driving nozzle within said tubular housing, the downstream end of said driving nozzle being in fluid communication with said suction nonle and associated with said suction nozzle to create a zone of reduced pressure therein, said driving nozzle being of lesser diameter than and upstream from the suction nozzle, the diameter of said driving nozzle being between about 0.2 to 0.6 centimeter,
D. an annular orifice between said driving nozzle and said suction noule,
E. means to hold said nozzles concentric,
F. a suction plenum upstream from and in fluid communication with said suction nozzle,
G. means for connecting said driving nozzle to a source of arterial blood,
H. a mixing chamber within said housing downstream from said suction and driving nozzles and in fluid communication therewith, the diameter of said mixing chamber being between about 0.25 to 2 centimeters and its length being up to ten times its diameter,
I. a discharge outlet downstream from said mixing chamber,
and
J. means for connecting said discharge outlet to the pulmonary circulation system.
7. A device according to claim 6 further characterized in that said discharge outlet comprises an outwardly tapered diffuser of between about 6 and 30 and an exit diameter between about 1 to 2.5 centimeters corresponding to the diameter of the pulmonary artery.
8. A method of at least partially replacing a disabled right heart in a living being which comprises:
A. connecting to a source of arterial blood under pressure the upstream end of the driving noule of a jet pump comprising:
1. an elongated tubular housing, 2. an inwardly tapering suction noule inlet adjacent to the upstream end of said housing,
7 3. an inwardly tapering concentric driving nozzle within said tubular housing, the downstream end of said driving nonle being in fluid communication with said suction nozzle and associated with said suction nozzle to create a zone of reduced pressure therein,
4. a suction plenum upstream from and in fluid communication with said suction noble,
5. means for connecting said driving nozzle to a source of arterial blood,
6. a chamber within said housing downstream from said suction and driving nozzles and in fluid communication therewith,
7. a discharge outlet downstream from said chamber, and
8. means for connecting said discharge outlet to the pulmonary circulation system.
B. connecting the suction plenum of said jet pump to receive venous blood from the right atrium of the heart, and
C. connecting the discharge outlet from said jet pump to the pulmonary circulation system.
9. A method according to claim 8 further characterized in that the driving nonle is connected to the aorta.
10. A method according to claim 8 mrther characterized in that the driving nozzle is connected to an artificial pump replacement for the left heart.
11. A method according to claim 8 further characterized in thatthetricuspidandpulmonaryvalveaofaaid rightheartare made incompetent and said jet pump is implanted within the heart between the right ventricle and pulmonary artery as a total replacement of the right heart.
12. A method according to claim 8 further characterized in that one end of said jet pump is connected externally of the hearttotherightatriumoftheheartandtheotherendofsaid pump is connected externally of the heart to the pulmonary arteryinparallelwiththerightheartasanassisttotheright heart.
Claims (19)
1. An implantable jet pump cardiac replacement and assist device comprising: A. an elongated tubular housing, said housing being of a size adapted to implantation in a living being and of lightweight material compatible with body fluids, B. an inwardly tapering suction nozzle inlet adjacent to the upstream end of said housing, C. an inwardly tapering concentric driving nozzle within said tubular housing, the downstream end of said driving nozzle being in fluid communication with said suction nozzle and associated with said suction nozzle to create a zone of reduced pressure therein, D. a suction plenum upstream from and in fluid communication with said suction nozzle, said plenum including means for connection to receive venous blood of the recipient living being, E. means for connecting said driving nozzle to a source of arterial blood of the recipient living being, F. a mixing chamber within said housing downstream from said suction and driving nozzles and in fluid communication therewith, G. a discharge outlet downstream from said mixing chamber, and H. means for connecting said discharge outlet to the pulmonary circulation system of the recipient living being.
2. A device according to claim 1 further characterized in that: A. said driving nozzle is of lesser diameter than and upstream from the suction nozzle, B. an annular orifice exists between said driving nozzle and said suction nozzle, C. means are provided to hold said nozzles concentric.
2. an inwardly tapering suction nozzle inlet adjacent to the upstream end of said housing,
3. an inwardly tapering concentric driving nozzle within said tubular housing, the downstream end of said driving nozzle being in fluid communication with said suction nozzle and associated with said suction nozzle to create a zone of reduced pressure therein,
3. A device according to claim 1 further characterized in that: A. said driving nozzle is an annular orifice tapering radially inwardly and encircling the downstream end of said suction nozzle, B. an annular chamber of greater diameter and greater cross-sectional area surrounds said driving nozzle, and C. said drivIng nozzle is in direct fluid communication with said annular chamber and said annular chamber is in direct fluid communication with said means for connection with a source of arterial blood.
4. A device according to claim 1 further characterized in that said discharge outlet comprises an outwardly tapered diffuser.
4. a suction plenum upstream from and in fluid communication with said suction nozzle,
5. means for connecting said driving nozzle to a source of arterial blood,
5. a device according to claim 1 further characterized in that the blood contacting surfaces of the inside of the housing, the inside of the suction nozzle, the inside and outside of the drive nozzle, the inside of the suction plenum, the inside of the mixing chamber and the inside of said connecting means and discharge outlet are comprised of an anti-thrombogenic and anti-hemolytic material.
6. A jet pump cardiac replacement and assist device comprising: A. an elongated tubular housing, B. an inwardly tapering suction nozzle inlet adjacent to the upstream end of said housing, said suction nozzle tapering inwardly from a diameter between about 0.5 to 2.5 centimeters to between about 0.25 to 2 centimeters over a length between about 0.2 to 1 centimeter, C. an inwardly tapering concentric driving nozzle within said tubular housing, the downstream end of said driving nozzle being in fluid communication with said suction nozzle and associated with said suction nozzle to create a zone of reduced pressure therein, said driving nozzle being of lesser diameter than and upstream from the suction nozzle, the diameter of said driving nozzle being between about 0.2 to 0.6 centimeter, D. an annular orifice between said driving nozzle and said suction nozzle, E. means to hold said nozzles concentric, F. a suction plenum upstream from and in fluid communication with said suction nozzle, G. means for connecting said driving nozzle to a source of arterial blood, H. a mixing chamber within said housing downstream from said suction and driving nozzles and in fluid communication therewith, the diameter of said mixing chamber being between about 0.25 to 2 centimeters and its length being up to ten times its diameter, I. a discharge outlet downstream from said mixing chamber, and J. means for connecting said discharge outlet to the pulmonary circulation system.
6. a mixing chamber within said housing downstream from said suction and driving nozzles and in fluid communication therewith,
7. a discharge outlet downstream from said mixing chamber, and
7. A device according to claim 6 further characterized in that said discharge outlet comprises an outwardly tapered diffuser of between about 6* and 30* and an exit diameter between about 1 to 2.5 centimeters corresponding to the diameter of the pulmonary artery.
8. A method of at least partially replacing a disabled right heart in a living being which comprises: A. connecting to a source of arterial blood under pressure the upstream end of the driving nozzle of a jet pump comprising:
8. means for connecting said discharge outlet to the pulmonary circulation system. B. connecting the suction plenum of said jet pump to receive venous blood from the right atrium of the heart, and C. connecting the discharge outlet from said jet pump to the pulmonary circulation system.
9. A method according to claim 8 further charactErized in that the driving nozzle is connected to the aorta.
10. A method according to claim 8 further characterized in that the driving nozzle is connected to an artificial pump replacement for the left heart.
11. A method according to claim 8 further characterized in that the tricuspid and pulmonary valves of said right heart are made incompetent and said jet pump is implanted within the heart between the right ventricle and pulmonary artery as a total replacement of the right heart.
12. A method according to claim 8 further characterized in that one end of said jet pump is connected externally of the heart to the right atrium of the heart and the other end of said pump is connected externally of the heart to the pulmonary artery in parallel with the right heart as an assist to the right heart.
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US2338870A | 1970-03-27 | 1970-03-27 |
Publications (1)
Publication Number | Publication Date |
---|---|
US3667069A true US3667069A (en) | 1972-06-06 |
Family
ID=21814797
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US23388A Expired - Lifetime US3667069A (en) | 1970-03-27 | 1970-03-27 | Jet pump cardiac replacement and assist device and method of at least partially replacing a disabled right heart |
Country Status (1)
Country | Link |
---|---|
US (1) | US3667069A (en) |
Cited By (62)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3818511A (en) * | 1972-11-17 | 1974-06-25 | Medical Prod Corp | Medical prosthesis for ducts or conduits |
US3962960A (en) * | 1973-12-26 | 1976-06-15 | Tempmaster Corporation | Vertical discharge slot diffuser with high induction ratio |
WO1984002266A1 (en) * | 1982-12-13 | 1984-06-21 | Possis Medical Inc | Vascular graft and blood supply method |
US4625712A (en) * | 1983-09-28 | 1986-12-02 | Nimbus, Inc. | High-capacity intravascular blood pump utilizing percutaneous access |
JPS62500792A (en) * | 1984-11-14 | 1987-04-02 | ナウチノ−イススレドバテルスキ インステイテユト プリクラドニフ フイジチエスキフ プロブレム イメニ ア−.エヌ.セブチエンコ | Liquid crystal material consisting of 4-(4'-cyanodiphenyl) ester of trans-4''-n-alkylcyclohex-2-enecarboxylic acid and liquid crystal composition using the same |
US4927407A (en) * | 1989-06-19 | 1990-05-22 | Regents Of The University Of Minnesota | Cardiac assist pump with steady rate supply of fluid lubricant |
US4964864A (en) * | 1988-09-27 | 1990-10-23 | American Biomed, Inc. | Heart assist pump |
US4969865A (en) * | 1989-01-09 | 1990-11-13 | American Biomed, Inc. | Helifoil pump |
US5108417A (en) * | 1990-09-14 | 1992-04-28 | Interface Biomedical Laboratories Corp. | Anti-turbulent, anti-thrombogenic intravascular stent |
US5112292A (en) * | 1989-01-09 | 1992-05-12 | American Biomed, Inc. | Helifoil pump |
US5344425A (en) * | 1990-09-14 | 1994-09-06 | Interface Biomedical Laboratories, Corp. | Intravascular stent and method for conditioning the surfaces thereof |
US6026814A (en) * | 1997-03-06 | 2000-02-22 | Scimed Life Systems, Inc. | System and method for percutaneous coronary artery bypass |
US6035856A (en) * | 1997-03-06 | 2000-03-14 | Scimed Life Systems | Percutaneous bypass with branching vessel |
US6092526A (en) * | 1997-06-19 | 2000-07-25 | Scimed Life Systems, Inc. | Percutaneous chamber-to-artery bypass |
US6155264A (en) * | 1997-03-06 | 2000-12-05 | Scimed Life Systems, Inc. | Percutaneous bypass by tunneling through vessel wall |
US6213126B1 (en) | 1997-06-19 | 2001-04-10 | Scimed Life Systems, Inc. | Percutaneous artery to artery bypass using heart tissue as a portion of a bypass conduit |
US6217541B1 (en) | 1999-01-19 | 2001-04-17 | Kriton Medical, Inc. | Blood pump using cross-flow principles |
US6250890B1 (en) * | 1997-10-14 | 2001-06-26 | Serguei A. Popov | Liquid-gas jet apparatus |
US6325813B1 (en) | 1998-08-18 | 2001-12-04 | Scimed Life Systems, Inc. | Method and apparatus for stabilizing vascular wall |
US20020077696A1 (en) * | 1997-09-16 | 2002-06-20 | Gholam-Reza Zadno-Azizi | Body fluid flow control device |
US20020103413A1 (en) * | 1999-06-23 | 2002-08-01 | Mogens Bugge | Implantable device for utilisation of the hydraulic energy of the heart |
US6443158B1 (en) | 1997-06-19 | 2002-09-03 | Scimed Life Systems, Inc. | Percutaneous coronary artery bypass through a venous vessel |
EP1078646A3 (en) * | 1999-08-24 | 2002-09-18 | DHD Healthcare Corporation | Continuous positive airway pressure therapy device |
US6464655B1 (en) | 1999-03-17 | 2002-10-15 | Environmental Robots, Inc. | Electrically-controllable multi-fingered resilient heart compression devices |
US20040059179A1 (en) * | 2002-09-20 | 2004-03-25 | Mark Maguire | Intra-aortic renal delivery catheter |
US20040064089A1 (en) * | 2000-11-28 | 2004-04-01 | Kesten Randy J. | Intra-aortic renal drug delivery catheter |
US20040064091A1 (en) * | 1999-01-11 | 2004-04-01 | Gad Keren | Apparatus and methods for treating congestive heart disease |
US20040258535A1 (en) * | 2003-06-23 | 2004-12-23 | George Tash | Automatically deformable nozzle regulator for use in a venturi pump |
US20050178389A1 (en) * | 2004-01-27 | 2005-08-18 | Shaw David P. | Disease indications for selective endobronchial lung region isolation |
US20050196344A1 (en) * | 2004-02-27 | 2005-09-08 | Mccutcheon John | Methods and devices for blocking flow through collateral pathways in the lung |
US20050197624A1 (en) * | 2004-03-04 | 2005-09-08 | Flowmedica, Inc. | Sheath for use in peripheral interventions |
US20050245892A1 (en) * | 2002-09-20 | 2005-11-03 | Flowmedica, Inc. | Apparatus and method for inserting an intra-aorta catheter through a delivery sheath |
US20050245882A1 (en) * | 2002-09-20 | 2005-11-03 | Flowmedica, Inc. | Method and apparatus for intra-aortic substance delivery to a branch vessel |
US20050267010A1 (en) * | 2004-05-14 | 2005-12-01 | Flowmedica, Inc. | Bi-lateral local renal delivery for treating congestive heart failure and for BNP therapy |
US20060020347A1 (en) * | 2004-03-08 | 2006-01-26 | Michael Barrett | Implanted bronchial isolation devices and methods |
US20060030863A1 (en) * | 2004-07-21 | 2006-02-09 | Fields Antony J | Implanted bronchial isolation device delivery devices and methods |
US20060069323A1 (en) * | 2004-09-24 | 2006-03-30 | Flowmedica, Inc. | Systems and methods for bi-lateral guidewire cannulation of branched body lumens |
US20060107956A1 (en) * | 2004-11-19 | 2006-05-25 | Hendricksen Michael J | Bronchial flow control devices and methods of use |
US20060149350A1 (en) * | 2003-06-05 | 2006-07-06 | Flowmedica, Inc. | Systems and methods for performing bi-lateral interventions or diagnosis in branched body lumens |
US20060167437A1 (en) * | 2003-06-17 | 2006-07-27 | Flowmedica, Inc. | Method and apparatus for intra aortic substance delivery to a branch vessel |
US20060189960A1 (en) * | 1999-01-11 | 2006-08-24 | Flowmedica, Inc. | Intra-aortic renal drug delivery catheter |
US7122019B1 (en) | 2000-11-28 | 2006-10-17 | Flowmedica Inc. | Intra-aortic renal drug delivery catheter |
US20070167913A1 (en) * | 2005-10-11 | 2007-07-19 | Flowmedica, Inc. | Vascular sheath with variable lumen construction |
US20070213686A1 (en) * | 2003-08-05 | 2007-09-13 | Flowmedica, Inc. | System and method for prevention of radiocontrast induced nephropathy |
US20070217922A1 (en) * | 2004-02-14 | 2007-09-20 | Hans-Peter Braun | Device For Pumping Fuel |
US20070249997A1 (en) * | 2002-09-20 | 2007-10-25 | Flowmedica, Inc. | Method and apparatus for selective material delivery via an intra-renal catheter |
US20070287967A1 (en) * | 2006-06-08 | 2007-12-13 | Flowmedica, Inc. | Selective renal cannulation and infusion systems and methods |
US20080221551A1 (en) * | 2007-03-09 | 2008-09-11 | Flowmedica, Inc. | Acute kidney injury treatment systems and methods |
US20090105799A1 (en) * | 2007-10-23 | 2009-04-23 | Flowmedica, Inc. | Renal assessment systems and methods |
US7780628B1 (en) | 1999-01-11 | 2010-08-24 | Angiodynamics, Inc. | Apparatus and methods for treating congestive heart disease |
US20100236551A1 (en) * | 2007-03-16 | 2010-09-23 | Dolphys Technologies B.V. | Gas flow reversing element |
US7993325B2 (en) | 2002-09-20 | 2011-08-09 | Angio Dynamics, Inc. | Renal infusion systems and methods |
US20110226238A1 (en) * | 2000-03-04 | 2011-09-22 | Pulmonx Corporation | Implanted bronchial isolation devices and methods |
US20150285271A1 (en) * | 2014-04-04 | 2015-10-08 | Caltec Limited | Jet pump |
US9211181B2 (en) | 2004-11-19 | 2015-12-15 | Pulmonx Corporation | Implant loading device and system |
US9486562B2 (en) | 2014-10-24 | 2016-11-08 | Integrated Surgical, Llc | Suction device for surgical instruments |
US20160354524A1 (en) * | 2011-08-11 | 2016-12-08 | Abiomed, Inc. | Devices, methods and systems for counterpulsation and blood flow conduit connection |
WO2017011024A1 (en) * | 2015-07-13 | 2017-01-19 | Noah Mark Minskoff | Surgical suction device that uses positive pressure gas |
US20170274125A1 (en) * | 2015-07-13 | 2017-09-28 | Integrated Surgical LLC | Surgical suction device that uses positive pressure gas |
US10463508B2 (en) | 2012-08-10 | 2019-11-05 | Abiomed, Inc. | Graft anchor devices, systems and methods |
US10500323B2 (en) * | 2012-03-26 | 2019-12-10 | Procyrion, Inc. | Systems and methods for fluid flows and/or pressures for circulation and perfusion enhancement |
US11596783B2 (en) * | 2018-03-06 | 2023-03-07 | Indiana University Research & Technology Corporation | Blood pressure powered auxiliary pump |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2085361A (en) * | 1935-10-05 | 1937-06-29 | Schutte & Koerting Company | Steam jet exhauster |
US2173330A (en) * | 1936-06-25 | 1939-09-19 | Gregg Tresham Dames | Fluid compressing and exhausting device |
US3526906A (en) * | 1965-11-05 | 1970-09-08 | Lorraine Carbone | Prosthetic implants made from carbonaceous materials |
-
1970
- 1970-03-27 US US23388A patent/US3667069A/en not_active Expired - Lifetime
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2085361A (en) * | 1935-10-05 | 1937-06-29 | Schutte & Koerting Company | Steam jet exhauster |
US2173330A (en) * | 1936-06-25 | 1939-09-19 | Gregg Tresham Dames | Fluid compressing and exhausting device |
US3526906A (en) * | 1965-11-05 | 1970-09-08 | Lorraine Carbone | Prosthetic implants made from carbonaceous materials |
Non-Patent Citations (1)
Title |
---|
Jet Pump Theory and Performance With Fluids of High Viscosity by R. G. Cunningham, Transactions of the ASME, Vol. 79, No. 2, pages 1807 1820, 1957 * |
Cited By (133)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3818511A (en) * | 1972-11-17 | 1974-06-25 | Medical Prod Corp | Medical prosthesis for ducts or conduits |
US3962960A (en) * | 1973-12-26 | 1976-06-15 | Tempmaster Corporation | Vertical discharge slot diffuser with high induction ratio |
WO1984002266A1 (en) * | 1982-12-13 | 1984-06-21 | Possis Medical Inc | Vascular graft and blood supply method |
GB2141939A (en) * | 1982-12-13 | 1985-01-09 | Possis Medical Inc | Vascular graft and blood supply method |
US4546499A (en) * | 1982-12-13 | 1985-10-15 | Possis Medical, Inc. | Method of supplying blood to blood receiving vessels |
US4562597A (en) * | 1982-12-13 | 1986-01-07 | Possis Medical, Inc. | Method of supplying blood to blood receiving vessels |
US4601718A (en) * | 1982-12-13 | 1986-07-22 | Possis Medical, Inc. | Vascular graft and blood supply method |
DE3390385C2 (en) * | 1982-12-13 | 1994-07-07 | Possis Medical Inc | Vascular implants |
US4625712A (en) * | 1983-09-28 | 1986-12-02 | Nimbus, Inc. | High-capacity intravascular blood pump utilizing percutaneous access |
JPS62500792A (en) * | 1984-11-14 | 1987-04-02 | ナウチノ−イススレドバテルスキ インステイテユト プリクラドニフ フイジチエスキフ プロブレム イメニ ア−.エヌ.セブチエンコ | Liquid crystal material consisting of 4-(4'-cyanodiphenyl) ester of trans-4''-n-alkylcyclohex-2-enecarboxylic acid and liquid crystal composition using the same |
JPH0158237B2 (en) * | 1984-11-14 | 1989-12-11 | Nauchino Isusuredo* Inst Purikuradonifu Fuijichesukifu Puroburemu Imeni Aa Enu Sebuchenko | |
US4964864A (en) * | 1988-09-27 | 1990-10-23 | American Biomed, Inc. | Heart assist pump |
EP0480101A1 (en) * | 1988-09-27 | 1992-04-15 | American Biomed, Inc. | Heart assist pump |
US4969865A (en) * | 1989-01-09 | 1990-11-13 | American Biomed, Inc. | Helifoil pump |
US5112292A (en) * | 1989-01-09 | 1992-05-12 | American Biomed, Inc. | Helifoil pump |
US4927407A (en) * | 1989-06-19 | 1990-05-22 | Regents Of The University Of Minnesota | Cardiac assist pump with steady rate supply of fluid lubricant |
US5108417A (en) * | 1990-09-14 | 1992-04-28 | Interface Biomedical Laboratories Corp. | Anti-turbulent, anti-thrombogenic intravascular stent |
US5344425A (en) * | 1990-09-14 | 1994-09-06 | Interface Biomedical Laboratories, Corp. | Intravascular stent and method for conditioning the surfaces thereof |
US6026814A (en) * | 1997-03-06 | 2000-02-22 | Scimed Life Systems, Inc. | System and method for percutaneous coronary artery bypass |
US6035856A (en) * | 1997-03-06 | 2000-03-14 | Scimed Life Systems | Percutaneous bypass with branching vessel |
US6155264A (en) * | 1997-03-06 | 2000-12-05 | Scimed Life Systems, Inc. | Percutaneous bypass by tunneling through vessel wall |
US7004175B2 (en) | 1997-03-06 | 2006-02-28 | Scimed Life Systems, Inc. | System and method for percutaneous coronary artery bypass |
US6253769B1 (en) | 1997-03-06 | 2001-07-03 | Scimed Life Systems, Inc. | Method for percutaneous coronary artery bypass |
US20030195457A1 (en) * | 1997-03-06 | 2003-10-16 | Scimed Life Systems, Inc. | System and method for percutaneous coronary artery bypass |
US6390098B1 (en) | 1997-03-06 | 2002-05-21 | Scimed Life Systems, Inc. | Percutaneous bypass with branching vessel |
US6575168B2 (en) | 1997-03-06 | 2003-06-10 | Scimed Life Systems, Inc. | System and method for percutaneous coronary artery bypass |
US6092526A (en) * | 1997-06-19 | 2000-07-25 | Scimed Life Systems, Inc. | Percutaneous chamber-to-artery bypass |
US6213126B1 (en) | 1997-06-19 | 2001-04-10 | Scimed Life Systems, Inc. | Percutaneous artery to artery bypass using heart tissue as a portion of a bypass conduit |
US6443158B1 (en) | 1997-06-19 | 2002-09-03 | Scimed Life Systems, Inc. | Percutaneous coronary artery bypass through a venous vessel |
US20020077696A1 (en) * | 1997-09-16 | 2002-06-20 | Gholam-Reza Zadno-Azizi | Body fluid flow control device |
US20030199972A1 (en) * | 1997-09-16 | 2003-10-23 | Gholam-Reza Zadno-Azizi | Body fluid flow control device |
US20020095209A1 (en) * | 1997-09-16 | 2002-07-18 | Gholam-Reza Zadno-Azizi | Body fluid flow control device |
US7276077B2 (en) | 1997-09-16 | 2007-10-02 | Emphasys Medical, Inc. | Body fluid flow control device |
US7033387B2 (en) | 1997-09-16 | 2006-04-25 | Emphasys Medical, Inc. | Body fluid flow control device |
US6250890B1 (en) * | 1997-10-14 | 2001-06-26 | Serguei A. Popov | Liquid-gas jet apparatus |
US6325813B1 (en) | 1998-08-18 | 2001-12-04 | Scimed Life Systems, Inc. | Method and apparatus for stabilizing vascular wall |
US6749598B1 (en) * | 1999-01-11 | 2004-06-15 | Flowmedica, Inc. | Apparatus and methods for treating congestive heart disease |
US7780628B1 (en) | 1999-01-11 | 2010-08-24 | Angiodynamics, Inc. | Apparatus and methods for treating congestive heart disease |
US20060189960A1 (en) * | 1999-01-11 | 2006-08-24 | Flowmedica, Inc. | Intra-aortic renal drug delivery catheter |
US20070100314A1 (en) * | 1999-01-11 | 2007-05-03 | Flowmedica, Inc. | Apparatus and methods for treating congestive heart disease |
US20040064091A1 (en) * | 1999-01-11 | 2004-04-01 | Gad Keren | Apparatus and methods for treating congestive heart disease |
US20040097900A1 (en) * | 1999-01-11 | 2004-05-20 | Gad Keren | Apparatus and methods for treating congestive heart disease |
US7329236B2 (en) | 1999-01-11 | 2008-02-12 | Flowmedica, Inc. | Intra-aortic renal drug delivery catheter |
US7335192B2 (en) | 1999-01-11 | 2008-02-26 | Flowmedica, Inc. | Apparatus and methods for treating congestive heart disease |
US7341570B2 (en) | 1999-01-11 | 2008-03-11 | Flowmedica, Inc. | Apparatus and methods for treating congestive heart disease |
US6217541B1 (en) | 1999-01-19 | 2001-04-17 | Kriton Medical, Inc. | Blood pump using cross-flow principles |
US6464655B1 (en) | 1999-03-17 | 2002-10-15 | Environmental Robots, Inc. | Electrically-controllable multi-fingered resilient heart compression devices |
USRE41394E1 (en) * | 1999-06-23 | 2010-06-22 | Mogens Bugge | Implantable device for utilization of the hydraulic energy of the heart |
US6827682B2 (en) * | 1999-06-23 | 2004-12-07 | Mogens Bugge | Implantable device for utilization of the hydraulic energy of the heart |
US20020103413A1 (en) * | 1999-06-23 | 2002-08-01 | Mogens Bugge | Implantable device for utilisation of the hydraulic energy of the heart |
EP1078646A3 (en) * | 1999-08-24 | 2002-09-18 | DHD Healthcare Corporation | Continuous positive airway pressure therapy device |
US20110226238A1 (en) * | 2000-03-04 | 2011-09-22 | Pulmonx Corporation | Implanted bronchial isolation devices and methods |
US8474460B2 (en) | 2000-03-04 | 2013-07-02 | Pulmonx Corporation | Implanted bronchial isolation devices and methods |
US7481803B2 (en) | 2000-11-28 | 2009-01-27 | Flowmedica, Inc. | Intra-aortic renal drug delivery catheter |
US20040064089A1 (en) * | 2000-11-28 | 2004-04-01 | Kesten Randy J. | Intra-aortic renal drug delivery catheter |
US7122019B1 (en) | 2000-11-28 | 2006-10-17 | Flowmedica Inc. | Intra-aortic renal drug delivery catheter |
US8585678B2 (en) | 2002-09-20 | 2013-11-19 | Angiodynamics, Inc. | Method and apparatus for intra-aortic substance delivery to a branch vessel |
US7364566B2 (en) | 2002-09-20 | 2008-04-29 | Flowmedica, Inc. | Method and apparatus for intra-aortic substance delivery to a branch vessel |
US7063679B2 (en) | 2002-09-20 | 2006-06-20 | Flowmedica, Inc. | Intra-aortic renal delivery catheter |
US7563247B2 (en) | 2002-09-20 | 2009-07-21 | Angiodynamics, Inc. | Intra-aortic renal delivery catheter |
US7914503B2 (en) | 2002-09-20 | 2011-03-29 | Angio Dynamics | Method and apparatus for selective material delivery via an intra-renal catheter |
US20040059179A1 (en) * | 2002-09-20 | 2004-03-25 | Mark Maguire | Intra-aortic renal delivery catheter |
US7104981B2 (en) | 2002-09-20 | 2006-09-12 | Flowmedica, Inc. | Apparatus and method for inserting an intra-aorta catheter through a delivery sheath |
US20040059276A1 (en) * | 2002-09-20 | 2004-03-25 | Flomedica, Inc. | Intra-aortic renal delivery catheter |
US6994700B2 (en) | 2002-09-20 | 2006-02-07 | Flowmedica, Inc. | Apparatus and method for inserting an intra-aorta catheter through a delivery sheath |
US7241273B2 (en) | 2002-09-20 | 2007-07-10 | Flowmedica, Inc. | Intra-aortic renal delivery catheter |
US20050245892A1 (en) * | 2002-09-20 | 2005-11-03 | Flowmedica, Inc. | Apparatus and method for inserting an intra-aorta catheter through a delivery sheath |
US20050245882A1 (en) * | 2002-09-20 | 2005-11-03 | Flowmedica, Inc. | Method and apparatus for intra-aortic substance delivery to a branch vessel |
US7993325B2 (en) | 2002-09-20 | 2011-08-09 | Angio Dynamics, Inc. | Renal infusion systems and methods |
US8012121B2 (en) | 2002-09-20 | 2011-09-06 | Angiodynamics, Inc. | Method and apparatus for selective material delivery via an intra-renal catheter |
US20070249997A1 (en) * | 2002-09-20 | 2007-10-25 | Flowmedica, Inc. | Method and apparatus for selective material delivery via an intra-renal catheter |
US20060149350A1 (en) * | 2003-06-05 | 2006-07-06 | Flowmedica, Inc. | Systems and methods for performing bi-lateral interventions or diagnosis in branched body lumens |
US7766961B2 (en) | 2003-06-05 | 2010-08-03 | Angio Dynamics, Inc. | Systems and methods for performing bi-lateral interventions or diagnosis in branched body lumens |
US20060167437A1 (en) * | 2003-06-17 | 2006-07-27 | Flowmedica, Inc. | Method and apparatus for intra aortic substance delivery to a branch vessel |
US20040258535A1 (en) * | 2003-06-23 | 2004-12-23 | George Tash | Automatically deformable nozzle regulator for use in a venturi pump |
US7789633B2 (en) * | 2003-06-23 | 2010-09-07 | George Tash and Debra B. Tash | Automatically deformable nozzle regulator for use in a venturi pump |
US20070213686A1 (en) * | 2003-08-05 | 2007-09-13 | Flowmedica, Inc. | System and method for prevention of radiocontrast induced nephropathy |
US20050178389A1 (en) * | 2004-01-27 | 2005-08-18 | Shaw David P. | Disease indications for selective endobronchial lung region isolation |
US20090255537A1 (en) * | 2004-01-27 | 2009-10-15 | Pulmonx | Disease indications for selective endobronchial lung region isolation |
US20070217922A1 (en) * | 2004-02-14 | 2007-09-20 | Hans-Peter Braun | Device For Pumping Fuel |
US7874812B2 (en) * | 2004-02-14 | 2011-01-25 | Robert Bosch Gmbh | Suction jet pump with ribs for guiding the flow of fuel |
US8206684B2 (en) | 2004-02-27 | 2012-06-26 | Pulmonx Corporation | Methods and devices for blocking flow through collateral pathways in the lung |
US20050196344A1 (en) * | 2004-02-27 | 2005-09-08 | Mccutcheon John | Methods and devices for blocking flow through collateral pathways in the lung |
US20050197624A1 (en) * | 2004-03-04 | 2005-09-08 | Flowmedica, Inc. | Sheath for use in peripheral interventions |
US20090318857A1 (en) * | 2004-03-04 | 2009-12-24 | Flowmedica, Inc. | Sheath for use in peripheral interventions |
US8518011B2 (en) | 2004-03-04 | 2013-08-27 | Angiodynamics, Inc. | Sheath for use in peripheral interventions |
US20060020347A1 (en) * | 2004-03-08 | 2006-01-26 | Michael Barrett | Implanted bronchial isolation devices and methods |
US20050267010A1 (en) * | 2004-05-14 | 2005-12-01 | Flowmedica, Inc. | Bi-lateral local renal delivery for treating congestive heart failure and for BNP therapy |
US7585836B2 (en) | 2004-05-14 | 2009-09-08 | Goodson Iv Harry Burt | Bi-lateral local renal delivery for treating congestive heart failure and for BNP therapy |
US20060030863A1 (en) * | 2004-07-21 | 2006-02-09 | Fields Antony J | Implanted bronchial isolation device delivery devices and methods |
US20060069323A1 (en) * | 2004-09-24 | 2006-03-30 | Flowmedica, Inc. | Systems and methods for bi-lateral guidewire cannulation of branched body lumens |
US12064331B2 (en) | 2004-11-19 | 2024-08-20 | Pulmonx Corporation | Implant loading device and system |
US11083556B2 (en) | 2004-11-19 | 2021-08-10 | Pulmonx Corporation | Implant loading device and system |
US20110010910A1 (en) * | 2004-11-19 | 2011-01-20 | Pulmonx Corporation | Bronchial flow control devices and methods of use |
US20060107956A1 (en) * | 2004-11-19 | 2006-05-25 | Hendricksen Michael J | Bronchial flow control devices and methods of use |
US9872755B2 (en) | 2004-11-19 | 2018-01-23 | Pulmonx Corporation | Implant loading device and system |
US7771472B2 (en) | 2004-11-19 | 2010-08-10 | Pulmonx Corporation | Bronchial flow control devices and methods of use |
US9211181B2 (en) | 2004-11-19 | 2015-12-15 | Pulmonx Corporation | Implant loading device and system |
US8388682B2 (en) | 2004-11-19 | 2013-03-05 | Pulmonx Corporation | Bronchial flow control devices and methods of use |
US20070167913A1 (en) * | 2005-10-11 | 2007-07-19 | Flowmedica, Inc. | Vascular sheath with variable lumen construction |
US20070287967A1 (en) * | 2006-06-08 | 2007-12-13 | Flowmedica, Inc. | Selective renal cannulation and infusion systems and methods |
US7771401B2 (en) | 2006-06-08 | 2010-08-10 | Angiodynamics, Inc. | Selective renal cannulation and infusion systems and methods |
US20080221551A1 (en) * | 2007-03-09 | 2008-09-11 | Flowmedica, Inc. | Acute kidney injury treatment systems and methods |
US10543335B2 (en) | 2007-03-16 | 2020-01-28 | Ventinova Technologies B.V. | Gas flow reversing element |
US20100236551A1 (en) * | 2007-03-16 | 2010-09-23 | Dolphys Technologies B.V. | Gas flow reversing element |
US8950400B2 (en) * | 2007-03-16 | 2015-02-10 | Dolphys Technologies B.V. | Gas flow reversing element |
US20090105799A1 (en) * | 2007-10-23 | 2009-04-23 | Flowmedica, Inc. | Renal assessment systems and methods |
US9919086B2 (en) * | 2011-08-11 | 2018-03-20 | Abiomed, Inc. | Devices, methods and systems for counterpulsation and blood flow conduit connection |
US20160354524A1 (en) * | 2011-08-11 | 2016-12-08 | Abiomed, Inc. | Devices, methods and systems for counterpulsation and blood flow conduit connection |
US10350048B2 (en) | 2011-09-23 | 2019-07-16 | Pulmonx Corporation | Implant loading device and system |
US10500323B2 (en) * | 2012-03-26 | 2019-12-10 | Procyrion, Inc. | Systems and methods for fluid flows and/or pressures for circulation and perfusion enhancement |
US10463508B2 (en) | 2012-08-10 | 2019-11-05 | Abiomed, Inc. | Graft anchor devices, systems and methods |
US11213412B2 (en) | 2012-08-10 | 2022-01-04 | Abiomed, Inc. | Graft anchor devices, systems and methods |
US20150285271A1 (en) * | 2014-04-04 | 2015-10-08 | Caltec Limited | Jet pump |
US9750855B2 (en) | 2014-10-24 | 2017-09-05 | Conmed Corporation | Suction device for surgical instruments |
US10022479B2 (en) | 2014-10-24 | 2018-07-17 | Conmed Corporation | Suction device for surgical instruments |
US10034970B2 (en) | 2014-10-24 | 2018-07-31 | Conmed Corporation | Suction device for surgical instruments |
US9867913B2 (en) | 2014-10-24 | 2018-01-16 | Conmed Corporation | Suction device for surgical instruments |
US9486562B2 (en) | 2014-10-24 | 2016-11-08 | Integrated Surgical, Llc | Suction device for surgical instruments |
US10926007B2 (en) * | 2015-07-13 | 2021-02-23 | Conmed Corporation | Surgical suction device that uses positive pressure gas |
EP3978043A3 (en) * | 2015-07-13 | 2022-04-13 | ConMed Corporation | Surgical suction device that uses positive pressure gas |
US10821212B2 (en) | 2015-07-13 | 2020-11-03 | Conmed Corporation | Surgical suction device that uses positive pressure gas |
US10835649B2 (en) | 2015-07-13 | 2020-11-17 | Conmed Corporation | Surgical suction device that uses positive pressure gas |
US10835648B2 (en) | 2015-07-13 | 2020-11-17 | Conmed Corporation | Surgical suction device that uses positive pressure gas |
US10850012B2 (en) | 2015-07-13 | 2020-12-01 | Conmed Corporation | Surgical suction device that uses positive pressure gas |
US20170274125A1 (en) * | 2015-07-13 | 2017-09-28 | Integrated Surgical LLC | Surgical suction device that uses positive pressure gas |
US10926008B2 (en) | 2015-07-13 | 2021-02-23 | Conmed Corporation | Surgical suction device that uses positive pressure gas |
AU2015402523B2 (en) * | 2015-07-13 | 2019-01-24 | Conmed Corporation | Surgical suction device that uses positive pressure gas |
WO2017011024A1 (en) * | 2015-07-13 | 2017-01-19 | Noah Mark Minskoff | Surgical suction device that uses positive pressure gas |
CN108472419A (en) * | 2016-04-06 | 2018-08-31 | 康曼德公司 | Use the surgical aspiration device of barotropic gas |
EP3307343A4 (en) * | 2016-04-06 | 2019-01-02 | CONMED Corporation | Surgical suction device that uses positive pressure gas |
EP3915606A1 (en) * | 2016-04-06 | 2021-12-01 | CONMED Corporation | Surgical suction device that uses positive pressure gas |
US11596783B2 (en) * | 2018-03-06 | 2023-03-07 | Indiana University Research & Technology Corporation | Blood pressure powered auxiliary pump |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US3667069A (en) | Jet pump cardiac replacement and assist device and method of at least partially replacing a disabled right heart | |
US5688245A (en) | Cannula system for a biventricular cardiac support system or a cardiopulmonary bypass system | |
US5458468A (en) | Diaphragm pump | |
US11311713B2 (en) | Self-propelled venous blood pump | |
EP0157871B1 (en) | High-capacity intravascular blood pump utilizing percutaneous access | |
US8870951B1 (en) | Total artificial heart system for auto-regulating flow and pressure | |
Pennock et al. | Survival and complications following ventricular assist pumping for cardiogenic shock | |
US5928132A (en) | Closed chest intra-aortic balloon based ventricular assist device | |
US6132364A (en) | Heart assist system and method | |
US3955557A (en) | Blood pump for use in an artificial heart or such purpose | |
CN105498002A (en) | Blood pumping impeller | |
US11957820B2 (en) | Blood pump | |
CA2226491A1 (en) | Heart assist system | |
US20210085955A1 (en) | Ventricular decompression and assisting apparatus | |
US3771174A (en) | Artificial heart utilizing blood pulsing fluid oscillators | |
WO1999026677A1 (en) | Heart assist system with cannula pump | |
JPH04176471A (en) | Circulation auxiliary pump | |
US4259988A (en) | Vortex-diode check valve with flexible diaphragm | |
EP1098671A1 (en) | Double-tube heart-assistance system | |
Zhu et al. | Effects of an intra-ventricular assist device on the stroke volume of failing ventricle: Analysis of a mock circulatory system | |
Qian | Low haemolysis pulsatile impeller pump: design concepts and experimental results | |
Ратобильская et al. | Mechanical circulatory support devices and new technologies for the treatment of myocardial infarction | |
JP2023529707A (en) | Blood pump for unidirectional blood flow and blood oxidation system equipped with the same | |
Woodward et al. | A fluid-amplifier artificial heart pump | |
Maul et al. | Principles of Mechanical Cardiopulmonary Support |