US3907504A - Blood oxygenation system including automatic means for stabilizing the flow rate of blood therethrough - Google Patents
Blood oxygenation system including automatic means for stabilizing the flow rate of blood therethrough Download PDFInfo
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- US3907504A US3907504A US348711A US34871173A US3907504A US 3907504 A US3907504 A US 3907504A US 348711 A US348711 A US 348711A US 34871173 A US34871173 A US 34871173A US 3907504 A US3907504 A US 3907504A
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- blood
- reservoir
- oxygenating
- pump
- hollow chamber
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- 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
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3639—Blood pressure control, pressure transducers specially adapted therefor
-
- 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
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
- A61M1/3621—Extra-corporeal blood circuits
- A61M1/3623—Means for actively controlling temperature of blood
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/03—Heart-lung
Abstract
An apparatus for sensing and signaling changes in the pressure and volume of a fluid passing therethrough, the apparatus comprising: (a) a hollow chamber; (b) a compliant reservoir for holding the fluid, the reservoir being located in the hollow chamber and being fitted with inlets and outlets for the fluid; and (c) a motion actuated means in the chamber for signaling changes in the size of the compliant reservoir. In one embodiment, the apparatus is used in an extracorporeal circuit to sense changes in the pressure and volume of blood and to signal the speed controller on a blood transfer pump in the blood circuit.
Description
United States Patent [191 Hammond et a1.
[ Sept. 23, 1975 Donald R. Ingenito, Scotia; Gunnar E. Walmet, Schenectady, all of NY.
[73] Assignee: General Electric Company,
Milwaukee, Wis.
[22] Filed: Apr. 6, 1973 [21] Appl. No.: 348,711
[52] US. Cl. 23/258.5; 128/DIG. 3; 137/565; 417/36; 417/37; 417/43 [51] Int. Cl. A6lM 1/03 [58] Field of Search 23/258.5; 128/D1G. 3; 417/43, 36, 37; 137/565 [56] References Cited UNITED STATES PATENTS 2,659,368 11/1953 Gibbon et a1. 23/258.5 3,332,746 7/1967 Claff et a1. 23/258.5 3,374,066 3/1968 Farrant 23/258.5 3,413,095 11/1968 Bramson 23/258.5
3,484,211 12/1969 Mon et a1. 23/258.5 3,513,845 5/1970 Chestnut et a1 23/258.5 X 3,533,408 10/1970 Paoli 23/258.5 X 3,717,174 2/1973 DeWall..... 23/258.5 X 3,827,828 8/1974 Edwards 417/43 3,833,013 9/1974 Leonard 23/258.5 X
OTHER PUBLICATIONS General Electric Dialing Instruction Manual; Publication No. 46A209535; Nov. 1972; Sections 4.1.1 to
C. T. Drake et 211.; The Effect of Low During Extracorporeal Circulation; J. Thoracic & Cardiovas. Surg.; Vol. 42; No. 6; 12-61; pp. 735-742.
F. .1. Lewis et al.; Semiautomatic Control Blood Pump; .1. Thoracic & Cardiovas. Surg.; Vol. 43; No. 3; 362; pp. 392-396.
M. Turina et al.; An automatic Infants; .1. Thoracic & Cardiovas. Surg.; Vol. 63; No. 2; 2-72; pp. 263268.
Primary Examiner-Barry S. Richman Attorney, Agent, or Firm-Thomas J. Bird, .lr.; Granville M. Pine; Edward A. Hedman [5 7] ABSTRACT ment, the apparatus is used in an extracorporeal circuit to sense changes in the pressure and volume of blood and to signal the speed controller on a blood transfer pump in the blood circuit.
7 Claims, 8 Drawing Figures Mme/AL PUMP US Patent Sept. 23,1975 Sheet 1 of5 US Patent Sept. 23,1975 Sheet 3 of5 3,907,504
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QDQQQQ tswk QR Sou E BLOOD OXYGENATION SYSTEM INCLUDING AUTOMATIC MEANS FOR STABILIZING THE FLOW RATE OF BLOOD THERETI-IROUGH This invention relates to an apparatus for sensing and signaling changes in the pressure and volume of fluids passing therethrough. More particularly, it is concerned with an apparatus which can sense the amount of liquid in a reservoir, e.g., one used in an extracorporeal fluid circuit and, using this signal, to modulate the speed of a pump in the circuit.
BACKGROUND OF THE INVENTION Various sensors are known which can detect the amount of liquid in a reservoir used in an extracorporeal circuit and, using this signal, modulate the speed ofa pump in the circuit. If the circuit is used, for exam ple, to oxygenate blood, such sensor-controllers operate almost automatically, considerably simplifying the perfusionists task. In this way, for example, a two pump circuit, generally needed with membrane lungs,
is reduced to the operational simplicity of a one-pump circuit by having an automatically controlled arterial pump. Also, such an automatic pump speed controller can be used to sense a venous reservoir being filled by gravity drainage from the patient and thus control the venous pump.
Among the prior art sensors are those which are weighing devices. These suffer serious disadvantages because they have two to four large tubes and two small tubes connected to a compliant or rigid reservoir, and the preload due to these tubes adversely affects the functioning of the weighing mechanism. Another device is based on the principle of an optical detection of the liquid level in the reservoir. However, the optical technique is complicated, lacks reliability, is applicable mainly only to rigid reservoirs, and generally is adapted to give only onoff rather than modulated pump control signals.
In a novel way, the device of the present invention can sense the amount of liquid in a reservoir, e.g., one used in an extracorporeal circuit and, using this signal, modulate the speed of a. pump in the circuit. The present device provides the stated advantages simply, reliably, and in a method consistent with maintaining sterility in the blood.
BRIEF DESCRIPTION OF THE DRAWINGS In the drawings:
FIG. 1 illustrates a vertical plan view, partially in section, of a compliant reservoir pressure and volume sensing and signalingdevice, which is one embodiment of this invention;
FIGS. 2 ((-11 illustrate semi-diagramatically, the device of FIG. 1 in which the compliant reservoir is shown ,to assume typical configurations under the influence of various fluid pressures and volumes;
FIG. 3 is a schematic, partial plan view, showing how the device of FIG. 1 can be used to keep the pump in a gravity drainage, single pump, extracorporeal circuit at the proper speed;
FIG. 4 is a schematic, partial plan view, showing how the device of FIG. 1 can be used to keep either the venous pump or the arterial pump of a two-pump gravity drainage system automatically at proper speed; and
FIG. 5 is a schematic, partial plan view, showing how the device of FIG. I can automatically control the speed of an arterial pump in a two-pump venous pump suction circuit.
Although FIGS. 3-5 relate specifically to a membrane lung of the type described in the copending application of D. R. Ingenito, W. P. Mathewson, D. R. Ryon and Gunnar E. Walmet, Ser. No. 247,987, filed on Apr. 21, 1972, now US. Pat. No. 3,839,204 issued Oct. 1, 1974, and assigned to the assignee of the present invention, it will be understood that the device of this invention can be used equally effectively with other membrane lungs and even different types of fluid gasexchanger and/or heat-exhanger.
DESCRIPTION OF THE INVENTION In its broadest aspects, the invention contemplates a device for continually sensing changes in reservoir distention/pressure and for signaling the changes to operate an external controller. In a preferred feature, the device will include means for varying the maximum volume of the reservoir. This allows one compliant reservoir to be used in an extracorporeal circuit for a variety of patient sizes.
According to the present invention, there is provided an apparatus for sensing and signaling changes in the pressure and volume of a fluid passing therethrough, said apparatus comprising:
a. a hollow chamber;
b. a compliant reservoir for holding said fluid, said reservoir being disposed within said hollow chamber and including an inlet and an outlet port for said fluid; and
c. motion actuated means in said hollow chamber for signaling changes in the size of said compliant reservoir.
Referring to FIG. 1, there is shown a preferred embodiment of the invention, in the form of a compliant reservoir pump speed controller. The sensor-controller is constructed of hollow chamber 2 comprised of U shaped base 4 of metal, plastic or the like and U shaped cover piece 6 also of metal, plastic or other suitable material of construction. Preferably, cover piece 6 and- /or base 4 will be of transparent material, such as clear plastic to allow the fluid in compliant reservoir 8 to be visually observed for any bubbles, clots, suspended foreign matter, and the like. To facilitate mounting, base 4 can be fitted with holder support 10. Adjustment slots 12 and lock screws 14 are providedin cover 6 and base 4 to permit changing the maximum volume of hollow chamber 2.
Compliant reservoir 8 is constructed of any suitable flexible material, such as metal, plastic and the like, preferably poly(vinyl chloride), silicone rubber, etc., and is fitted with inlet 13 and outlet 15, for fluid. It is desirable to provide that inlet 13 be tubular and that it terminate somewhat high up into the reservoir so that any bubbles in the fluid will be trapped by rising to the top of the reservoir instead of being drawn out of outlet 15. In the embodiment shown in FIG. 1, one or more vents, 16, are provided at the top of reservoir 8, and these can also serve conveniently as a sample port. For convenience, reservoir support 18 can be provided to hold the reservoir within the hollow chamber, eg by grasping a ring or other suitable fixture attached thereto.
Another important element in the device of this invention is the means for sensing the amount of liquid in reservoir 8. This can comprise a plate adjacent the reservoir, the plate being movable with changes in reservoir shape induced by fluid pressure and volume changes and a transducer actuated by motion from the sensor plate for supplying a signal to an external .recorder or controller. The sensor plate can be of the linear translating or, preferably, a pivoting type, and preferably is biased, e.g., with a spring, against the reservoir. Many different transducers can be used to convert the motion of the sensor plate to a different form of signal energy, but when used as a pump controller, it is preferred to use a linear motion actuated potentiometer or a linear motion actuated autotransformer.
Referring again to FIG. 1, sensor plate is shown hinged to base 4 at hinge point 22 and is seen to contact compliant reservoir 8 along a fairly substantial area of contact. Leaf spring 24 biases sensor plate 20 against reservoir 8. The transducer comprises linear potentiometer 26 having rod 28, of metal, strategically located to transmit changes in the position of sensor plate 20 to the potentiometer;
In operation, as compliant reservoir 8 fills up with fluid, sensor plate 20 deflects against spring 24. Conversely as reservoir 8 empties, sensor plate 20 follows it and moves out. As sensor plate 20 moves, metal rod 28 connected to linear motion actuated potentiometer 26 has its resistance varied. The resistance is the speed controlling signal in a suitable pump motor speed controller (not shown in FIG. 1).
If it is desired to change the maximum volume of the reservoir, cover plate 6 can be moved with respect to base 4 and locked in the new position with screws 14. This is shown, along with typical pressures and volumes in the reservoir (pressures measured near the top of the reservoir to avoid hydrostatic head contributions), at
various positions in FIG. 2.
For medical use, it is desirable that all parts of the device be'made of plastic. This increases the electrical resistance between the blood and any electrical components used in the sensor to insure patient safety in the event of anelectrical failure. Alternately, metal parts, if used, can be covered with an insulator. The materials in contact with blood should be easily sterilizable and be biocompatible.
DESCRIPTION OF THE PREFERRED EMBODIMENTS FIGS. 3-5 show how the device of this invention can be used as a reservoir sensing pump speed controller in extracorporeal circuits for oxygenating or otherwise treating body fluids, e.g., blood, and the like, before their return to the patient.
Referring to FIG. 3, reservoir sensing pump controller 30 is used in a gravity drainage, single pump, extracorporeal circuit to keep the pump at the proper speed. Blood from the patient (not shown) passes by gravity through conduit 32 into inlet port 13 on sensor device 30. The blood leaves through port 15 and is pumped, e.g., with roller type pump 34 (Sarns Corp., Ann Arbor, Mich, or the like) through conduit 36 past pressure monitoring gauge 38 to the inlet port of membrane type blood-gas exchanger 40 (GE-DUALUNG, General Electric Co., Schenectady, N.Y., or the like) which is fitted with inlet 42 and outlet 44 for heat exchange fluid and inlet conduit 46 for oxygen. The oxygenated blood exits the membrane lung through conduit 48 and, after being led to bubble trap 50, is returned to the patient through conduit 52. Shown schematically in combination with reservoir 8 are hinged sensor plate 20 and linear potentiometer 26 which supplies a pump speed varying signal through conductor 54 to pump 34. As changes in volume or pressure in the system expand or contract reservoir 8, the pumpspeed is varied automatically to compensate,
. Referring to FIG. 4, reservoir sensing pump controller 30 is used to keep either the venous pump or, preferably, the arterial pump of a two-pump gravity drainage system automatically at proper speed. Blood from the patient (not shown) passes by gravity through conduit 56 into inlet port 17 on sensor device 30. The blood leaves through port 15 and is. ,pumped by roller type venous pump 34 through conduit 36 past pressure monitoring gauge 38 to an inlet port of membrane type blood-gas exchanger40. oxygenated blood exits the exchanger through conduit 58 and is split into two streams, one being recycled to controller 30 through conduit 60 and entrance port 13. Complaint reservoir 8 is fitted with one vent tube 16 and a second vent tube includes filter 62 and cardiotomy reservoir 64. The other oxygenated blood stream istransferred through conduit 66and pumped by roller type arterial pump 68 to bubble trap 70 before being returned to the patient. Shown schematically in combination with reservoir 8 are hinged sensor plate 20 and linear potentiometer 26 which supplies a pump speed varying signal. If venous pump 34 is controlled, signal conductor 54 is used. Alternatively, and preferably, if arterial pump 68 is controlled, signal conductor 55 is used. In either case the pump speed is varied automatically to compensate for changes in blood pressure and volume within reservoir 8.
Referring to FIG. 5, reservoir'sensing pump controller 30 is used to keep the arterial pump in a two-pump venous pump suction circuit automatically at the proper speed. Blood from the patient (not shown) flows through conduit 72 into roller type venous pump 34 and pumped through conduit 36 to an inlet port of membrane type blood-gas exchanger 40. Oxygenated blood exits the exchanger through conduit 74 and enters compliant reservoir (arterial) 8 through entrance port 13. Compliant reservoir 8 is fitted with vent tube 16 andwith cardiotomy reservoir 64 coupled to reservoir 8 through filter 62. Part of the oxygenated blood in reservoir 8 exits through port 19 and circulates back through the venous pump circuit via conduit 76. Another part of the volume of oxygenated blood in reservoir 8 exits through port 15 to roller type arterial pump 68 where it is pumped through conduit 78, and, optionally, bubble trap 70, back to the patient. Shown schematically in combination with reservoir 8 are hinged sensor plate 20 and linear potentiometer 26 which supplies a pump speed varying signal through conductor 55 to pump 68, automatically varying the pump speed to compensate for changes in blood pressure and volume within reservoir 8.
Obviously, many other variations are possible in the light of the above specific embodiments. For example, FIGS. 4 and 5 illustrate how the sensor can be located in the venous and arterial two-pump circuits. Several other variations are possible. Illustratively, in FIG. 5.
The above description demonstrates that the present invention discloses a reservoir sensing and signaling de- 'vice which is simple and offers unique advantages over other pre-existing designs meant to serve the same function.
Many variations of the present invention are possible without departing from the spirit or scope of the appended claims.
We claim:
1. An apparatus for extracorporeally oxygenating the blood of a living patient comprising in combination i. at least one pumping means for the blood,
ii. oxygenating means for the blood,
iii. means for sensing and signalling changes in the pressure and volume of blood passing through said apparatus, said sensing and signalling means comprising:
a. a hollow chamber of a selectively fixed and adjustable volume and comprising a base piece and w a' cover piece; b. a compliant reservoir for holding said blood, said reservoir being disposed within said hollow chamber and including an inlet and an outlet port for said blood; said hollow chamber substantially limiting the maximum expansion volume of said complaint reservoir, and 5 c. motion activated means in said hollow chamber for generating an electrical signal proportionate to changes in the size of said compliant reservoir, and d. adjusting means movably attaching said cover piece to said base piece to permit selective adjustment of the volume of said hollow chamber by movement of said cover piece relative to said base piece, and
iv. pump speed controlling means being operatively connected to receive said signal from said motion activated means and to automatically adjust the operation of said pumping means so as to move said blood through said apparatus at a flow rate responsive to said signal.
2. An apparatus as defined in claim 1 wherein two pumping means are utilized, one being a venous pumping means located upstream of said oxygenating means and the other being an arterial pumping means located downstream of said oxygenating means and wherein said pump speed controlling means is operatively connected to said arterial pumping means to automatically adjust the flow rate thereof responsive to said signal.
3. An apparatus as defined in claim 1 wherein said oxygenating means for the blood is a membrane type blood-gas exchanging means.
4. An apparatus as defined in claim 1 wherein a single pumping means is utilized in the apparatus.
5. An apparatus as defined in claim 4 wherein the single pumping means is a venous pumping means located upstream of said oxygenating means.
6. An apparatus as defined in claim 1 which also includes a blood heat exchanging means.
7. An apparatus as defined in claim 6 wherein said oxygenating means for the blood is a membrane type bood-tgas exchanging means and the blood heat exchanging means is integral therewith.
Claims (7)
1. AN APPARATUS FOR EXTRACORPOREALLY OXYGENATING THE BLOOD OF A LIVING PATIENT COMPRISING IN COMBINATION I. AT LEAST ONE PUMPING MEANS FOR THE BLOOD II. OXYGENATING MEANS FOR THE BLOOD, III. MEANS FOR SENSING AND SIGNALLING CHANGES IN THE PRESSURE AND VOLUME OF BLOOD PASSING THROUGH SAID APPARATUS, SAID SENSING AND SIGNALLING MEANS COMPRISING: A, A HOLLOW CHAMBER OF A SELECTIVELY FIXED AND ADJUSTALE VOLUME AND COMPRISING A BASE PIECE AND A COVER PIECE, B. A COMPLIANT RESERVOIR FOR HOLDING SAID BLOOD, SAID RESERVOIR BEING DISPOSED WITHIN SAID HOLLOW CHAMBER AND INCLUDING AN INLET AND AN OUTLET PORT FOR SAID BLOOD, SAID HOLLOW CHAMBER SUBSTANTIALLY LIMITING THE MAXIMUM EXPANSION VOLUME OF SAID COMPLAINT RESERVOIR AND C. MOTION ACTIVATED MEANS IN SAID HOLLOW CHAMBER FOR GENERATING AN ELECTRICAL SIGNAL PROPORTIONATE TO CHANGES IN THE SIZE OF SAID COMPLIANT RESERVOIR, AND D. ADJUSTING MEANS MOVABLY ATTACHING SAID COVER PIECE TO SAID BASE PIECE TO PERMIT SELECTIVE ADJUSTMENT OF THE VOLUME OF SAID HOLLOW CHAMBER BY MOVEMENT OF SAID COVER PIECE RELATIVE TO SAID BASE PIECE, AND IV. PUMP SPEED CONTROLLING MEANS BEING OPERATIVELY CONNECTED TO RECEIVE SAID SIGNAL FROM SAID MOTON ACTIVATED MEANS AND TO AUTOMATICALLY ADJUST THE OPERATION OF SAID
2. An apparatus as defined in claim 1 wherein two pumping means are utilized, one being a venous pumping means located upstream of said oxygenating means and the other being an arterial pumping means located downstream of said oxygenating means and wherein said pump speed controlling means is operatively connected to said arterial pumping means to automatically adjust the flow rate thereof responsive to said signal.
3. An apparatus as defined in claim 1 wherein said oxygenating means for the blood is a membrane type blood-gas exchanging means.
4. An apparatus as defined in claim 1 wherein a single pumping means is utilized in the apparatus.
5. An apparatus as defined in claim 4 wherein the single pumping means is a venous pumping means located upstream of said oxygenating means.
6. An apparatus as defined in claim 1 which also includes a blood heat exchanging means.
7. An apparatus as defined in claim 6 wherein said oxygenating means for the blood is a membrane type bood-gas exchanging means and the blood heat exchanging means is integral therewith.
Priority Applications (7)
Application Number | Priority Date | Filing Date | Title |
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US348711A US3907504A (en) | 1973-04-06 | 1973-04-06 | Blood oxygenation system including automatic means for stabilizing the flow rate of blood therethrough |
NL7402161A NL7402161A (en) | 1973-04-06 | 1974-02-15 | |
GB1257874A GB1460116A (en) | 1973-04-06 | 1974-03-21 | Apparatus for extracorporeal |
DE2415528A DE2415528A1 (en) | 1973-04-06 | 1974-03-30 | DEVICE FOR DETERMINING AND DISPLAYING THE PRESSURE AND VOLUME OF LIQUIDS |
IT50018/74A IT1004078B (en) | 1973-04-06 | 1974-04-03 | PRESSURE AND VOLUME DETECTOR AND SIGNAL DEVICE OF A FLUID |
CA196,862A CA1006709A (en) | 1973-04-06 | 1974-04-04 | Blood oxygenation system including automatic means for stabilizing the flow rate of blood therethrough |
FR7412090A FR2238918A1 (en) | 1973-04-06 | 1974-04-05 |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
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US348711A US3907504A (en) | 1973-04-06 | 1973-04-06 | Blood oxygenation system including automatic means for stabilizing the flow rate of blood therethrough |
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US3907504A true US3907504A (en) | 1975-09-23 |
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ID=23369198
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Application Number | Title | Priority Date | Filing Date |
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US348711A Expired - Lifetime US3907504A (en) | 1973-04-06 | 1973-04-06 | Blood oxygenation system including automatic means for stabilizing the flow rate of blood therethrough |
Country Status (7)
Country | Link |
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US (1) | US3907504A (en) |
CA (1) | CA1006709A (en) |
DE (1) | DE2415528A1 (en) |
FR (1) | FR2238918A1 (en) |
GB (1) | GB1460116A (en) |
IT (1) | IT1004078B (en) |
NL (1) | NL7402161A (en) |
Cited By (34)
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US4062360A (en) * | 1976-04-02 | 1977-12-13 | Bentley Laboratories, Inc. | Atraumatic fluid handling method and apparatus |
US4140635A (en) * | 1977-04-13 | 1979-02-20 | Esmond William G | Purification device |
US4299705A (en) * | 1979-09-07 | 1981-11-10 | Russell Richard T | Method of treating blood during operative procedures |
US4309993A (en) * | 1980-03-06 | 1982-01-12 | Baxter Travenol Laboratories, Inc. | Liquid flow sensing apparatus |
EP0080610A1 (en) * | 1981-11-13 | 1983-06-08 | Terumo Kabushiki Kaisha | Blood circulating circuit for membrane-type artificial lung, and reservoir for use in blood circulating circuit |
EP0089748A2 (en) * | 1982-02-22 | 1983-09-28 | CD Medical, Inc. | Rigid shell expansible blood reservoir, heater and hollow fibre membrane oxygenator assembly |
US4411786A (en) * | 1979-09-07 | 1983-10-25 | Russell Richard T | Method and apparatus for separating blood from other fluids during operative procedures |
US4416280A (en) * | 1980-04-07 | 1983-11-22 | Minnesota Mining And Manufacturing Company | Cardioplegia delivery system |
US4417884A (en) * | 1981-07-09 | 1983-11-29 | Haemonetics Corporation | Centrifuge timer clamp |
US4451562A (en) * | 1982-04-26 | 1984-05-29 | Cobe Laboratories, Inc. | Blood oxygenator |
DE3247149A1 (en) * | 1982-12-21 | 1984-07-05 | Norbert 6100 Darmstadt Krämer | DEVICE FOR MONITORING THE BLOOD LEVEL IN AN OXYGENATOR |
US4490331A (en) * | 1982-02-12 | 1984-12-25 | Steg Jr Robert F | Extracorporeal blood processing system |
WO1985003879A1 (en) * | 1984-02-27 | 1985-09-12 | Omnis Surgical Inc | Priming system for ultrafiltration unit |
US4568330A (en) * | 1983-06-02 | 1986-02-04 | Minnesota Mining And Manufacturing Company | Cardioplegia delivery system with improved bubble trap |
WO1986001416A1 (en) * | 1984-08-21 | 1986-03-13 | Mehealus Partnership | Fully portable semi-automatic mechanical heart-lung substitution system and method |
US4599093A (en) * | 1982-02-12 | 1986-07-08 | Steg Jr Robert F | Extracorporeal blood processing system |
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US5232439A (en) * | 1992-11-02 | 1993-08-03 | Infusion Technologies Corporation | Method for pumping fluid from a flexible, variable geometry reservoir |
US5342313A (en) * | 1992-11-02 | 1994-08-30 | Infusion Technologies Corporation | Fluid pump for a flexible, variable geometry reservoir |
US5578267A (en) * | 1992-05-11 | 1996-11-26 | Minntech Corporation | Cylindrical blood heater/oxygenator |
EP0766974A2 (en) * | 1995-10-03 | 1997-04-09 | Terumo Kabushiki Kaisha | Blood reservoir, blood delivery instrument, and blood delivery apparatus |
US5693039A (en) * | 1990-06-15 | 1997-12-02 | Cobe Laboratories, Inc. | Venous reservoir bag assembly |
US5770073A (en) * | 1996-03-15 | 1998-06-23 | Minntech Corporation | Combined cardiotomy and venous reservoir |
US6106776A (en) * | 1997-04-11 | 2000-08-22 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer via active mixing |
US6113575A (en) * | 1998-05-14 | 2000-09-05 | Terumo Cardiovascular Systems Corporation | Volume control apparatus for a flexible venous reservoir |
US6123519A (en) * | 1995-10-03 | 2000-09-26 | Terumo Kabushiki Kaisha | Delivery blood storing member-equipped blood reservoir tank and blood delivery instrument for extracorporeal circulation circuit |
US6217826B1 (en) | 1997-04-11 | 2001-04-17 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer, heat transfer and pumping capabilities via active mixing |
US6337049B1 (en) | 1998-08-28 | 2002-01-08 | Yehuda Tamari | Soft shell venous reservoir |
WO2003018088A1 (en) * | 2001-08-23 | 2003-03-06 | Michigan Critical Care Consultants, Inc. | Apparatus for exchanging gases in a liquid |
US6723284B1 (en) | 1997-04-11 | 2004-04-20 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer, heat transfer and pumping capabilities via active mixing |
DE102005029682A1 (en) * | 2005-06-21 | 2006-12-28 | Maquet Cardiopulmonary Ag | Heart/lung bypass, for patients on a heart/lung machine, has a reservoir for priming solution and/or blood |
US20070100273A1 (en) * | 2003-12-10 | 2007-05-03 | Jms Co., Ltd. | Extracorporeal blood circulating apparatus, closed-type venous reservoir and extracorporeal blood circulating method |
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US4490135A (en) * | 1982-09-24 | 1984-12-25 | Extracorporeal Medical Specialties, Inc. | Single needle alternating blood flow system |
US4490134A (en) * | 1982-09-24 | 1984-12-25 | Extracorporeal Medical Specialties, Inc. | Dual phase blood flow system and method of operation |
IT8453709V0 (en) * | 1984-08-07 | 1984-08-07 | Hospal Dasco Spa | PERFECTED TYPE EQUIPMENT FOR THE CIRCULATION OF A LIQUID ALONG A TUBULAR LINE |
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1973
- 1973-04-06 US US348711A patent/US3907504A/en not_active Expired - Lifetime
-
1974
- 1974-02-15 NL NL7402161A patent/NL7402161A/xx unknown
- 1974-03-21 GB GB1257874A patent/GB1460116A/en not_active Expired
- 1974-03-30 DE DE2415528A patent/DE2415528A1/en active Pending
- 1974-04-03 IT IT50018/74A patent/IT1004078B/en active
- 1974-04-04 CA CA196,862A patent/CA1006709A/en not_active Expired
- 1974-04-05 FR FR7412090A patent/FR2238918A1/fr not_active Withdrawn
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Cited By (49)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4062360A (en) * | 1976-04-02 | 1977-12-13 | Bentley Laboratories, Inc. | Atraumatic fluid handling method and apparatus |
US4140635A (en) * | 1977-04-13 | 1979-02-20 | Esmond William G | Purification device |
US4411786A (en) * | 1979-09-07 | 1983-10-25 | Russell Richard T | Method and apparatus for separating blood from other fluids during operative procedures |
US4299705A (en) * | 1979-09-07 | 1981-11-10 | Russell Richard T | Method of treating blood during operative procedures |
US4309993A (en) * | 1980-03-06 | 1982-01-12 | Baxter Travenol Laboratories, Inc. | Liquid flow sensing apparatus |
US4416280A (en) * | 1980-04-07 | 1983-11-22 | Minnesota Mining And Manufacturing Company | Cardioplegia delivery system |
US4417884A (en) * | 1981-07-09 | 1983-11-29 | Haemonetics Corporation | Centrifuge timer clamp |
US4765959A (en) * | 1981-11-13 | 1988-08-23 | Terumo Kabushiki Kaisha | Blood circulating circuit for membrane-type artificial lung, and reservoir for use in blood circulating circuit |
EP0080610A1 (en) * | 1981-11-13 | 1983-06-08 | Terumo Kabushiki Kaisha | Blood circulating circuit for membrane-type artificial lung, and reservoir for use in blood circulating circuit |
AU574794B2 (en) * | 1981-11-13 | 1988-07-14 | Terumo Kabushiki Kaisha | Reservoir for use in blood circulating circuit |
US4717377A (en) * | 1981-11-13 | 1988-01-05 | Terumo Kabushiki Kaisha | Blood circulating circuit for membrane-type artificial lung, and reservoir for use in blood circulating circuit |
US4599093A (en) * | 1982-02-12 | 1986-07-08 | Steg Jr Robert F | Extracorporeal blood processing system |
US4490331A (en) * | 1982-02-12 | 1984-12-25 | Steg Jr Robert F | Extracorporeal blood processing system |
EP0089748A3 (en) * | 1982-02-22 | 1984-09-12 | Cd Medical, Inc. | Rigid shell expansible blood reservoir, heater and hollow fibre membrane oxygenator assembly |
EP0089748A2 (en) * | 1982-02-22 | 1983-09-28 | CD Medical, Inc. | Rigid shell expansible blood reservoir, heater and hollow fibre membrane oxygenator assembly |
US4469659A (en) * | 1982-04-26 | 1984-09-04 | Cobe Laboratories, Inc. | Sampling device for blood oxygenator |
US4451562A (en) * | 1982-04-26 | 1984-05-29 | Cobe Laboratories, Inc. | Blood oxygenator |
US4704203A (en) * | 1982-08-27 | 1987-11-03 | Reed Charles C | Cardiotomy reservoir apparatus and method |
DE3247149A1 (en) * | 1982-12-21 | 1984-07-05 | Norbert 6100 Darmstadt Krämer | DEVICE FOR MONITORING THE BLOOD LEVEL IN AN OXYGENATOR |
US4568330A (en) * | 1983-06-02 | 1986-02-04 | Minnesota Mining And Manufacturing Company | Cardioplegia delivery system with improved bubble trap |
WO1985003879A1 (en) * | 1984-02-27 | 1985-09-12 | Omnis Surgical Inc | Priming system for ultrafiltration unit |
US4610656A (en) * | 1984-08-21 | 1986-09-09 | Mehealus Partnership | Fully portable semi-automatic mechanical heart-lung substitution system and method |
JPS62500006A (en) * | 1984-08-21 | 1987-01-08 | カーディオパルモニックス・インコーポレーテッド | Fully portable, semi-automatic mechanical cardiopulmonary function device and method thereof |
WO1986001416A1 (en) * | 1984-08-21 | 1986-03-13 | Mehealus Partnership | Fully portable semi-automatic mechanical heart-lung substitution system and method |
US4643713A (en) * | 1984-11-05 | 1987-02-17 | Baxter Travenol Laboratories, Inc. | Venous reservoir |
US4832689A (en) * | 1986-11-06 | 1989-05-23 | B. Braun Melsungen Ag | Infusion means |
US5693039A (en) * | 1990-06-15 | 1997-12-02 | Cobe Laboratories, Inc. | Venous reservoir bag assembly |
US5720741A (en) * | 1990-06-15 | 1998-02-24 | Cobe Laboratories, Inc. | Venous reservoir bag assembly |
US5578267A (en) * | 1992-05-11 | 1996-11-26 | Minntech Corporation | Cylindrical blood heater/oxygenator |
US5232439A (en) * | 1992-11-02 | 1993-08-03 | Infusion Technologies Corporation | Method for pumping fluid from a flexible, variable geometry reservoir |
US5342313A (en) * | 1992-11-02 | 1994-08-30 | Infusion Technologies Corporation | Fluid pump for a flexible, variable geometry reservoir |
EP0766974A3 (en) * | 1995-10-03 | 1997-11-05 | Terumo Kabushiki Kaisha | Blood reservoir, blood delivery instrument, and blood delivery apparatus |
US6123519A (en) * | 1995-10-03 | 2000-09-26 | Terumo Kabushiki Kaisha | Delivery blood storing member-equipped blood reservoir tank and blood delivery instrument for extracorporeal circulation circuit |
US5931646A (en) * | 1995-10-03 | 1999-08-03 | Terumo Kabushiki Kaisha | Blood delivery instrument for regulating the amount of blood stored in an accumulator independent of the pumping operation |
EP0766974A2 (en) * | 1995-10-03 | 1997-04-09 | Terumo Kabushiki Kaisha | Blood reservoir, blood delivery instrument, and blood delivery apparatus |
US5770073A (en) * | 1996-03-15 | 1998-06-23 | Minntech Corporation | Combined cardiotomy and venous reservoir |
US20040219061A1 (en) * | 1997-04-11 | 2004-11-04 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer, heat transfer and pumping capabilities via active mixing |
US6217826B1 (en) | 1997-04-11 | 2001-04-17 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer, heat transfer and pumping capabilities via active mixing |
US6348175B1 (en) | 1997-04-11 | 2002-02-19 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer via active mixing |
US6723284B1 (en) | 1997-04-11 | 2004-04-20 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer, heat transfer and pumping capabilities via active mixing |
US6106776A (en) * | 1997-04-11 | 2000-08-22 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer via active mixing |
US7122151B2 (en) | 1997-04-11 | 2006-10-17 | University Of Pittsburgh | Membrane apparatus with enhanced mass transfer, heat transfer and pumping capabilities via active mixing |
US6113575A (en) * | 1998-05-14 | 2000-09-05 | Terumo Cardiovascular Systems Corporation | Volume control apparatus for a flexible venous reservoir |
US6337049B1 (en) | 1998-08-28 | 2002-01-08 | Yehuda Tamari | Soft shell venous reservoir |
US6773426B2 (en) | 1998-08-28 | 2004-08-10 | Yehuda Tamari | Soft shell venous reservoir with improved air handling |
WO2003018088A1 (en) * | 2001-08-23 | 2003-03-06 | Michigan Critical Care Consultants, Inc. | Apparatus for exchanging gases in a liquid |
US20070100273A1 (en) * | 2003-12-10 | 2007-05-03 | Jms Co., Ltd. | Extracorporeal blood circulating apparatus, closed-type venous reservoir and extracorporeal blood circulating method |
US7651473B2 (en) * | 2003-12-10 | 2010-01-26 | Jms Co., Ltd. | Extracorporeal blood circulating apparatus, closed-type venous reservoir and extracorporeal blood circulating method |
DE102005029682A1 (en) * | 2005-06-21 | 2006-12-28 | Maquet Cardiopulmonary Ag | Heart/lung bypass, for patients on a heart/lung machine, has a reservoir for priming solution and/or blood |
Also Published As
Publication number | Publication date |
---|---|
FR2238918A1 (en) | 1975-02-21 |
IT1004078B (en) | 1976-07-10 |
CA1006709A (en) | 1977-03-15 |
NL7402161A (en) | 1974-10-08 |
DE2415528A1 (en) | 1974-10-24 |
GB1460116A (en) | 1976-12-31 |
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