US3898045A - Blood oxygenator - Google Patents

Blood oxygenator Download PDF

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Publication number
US3898045A
US3898045A US295724A US29572472A US3898045A US 3898045 A US3898045 A US 3898045A US 295724 A US295724 A US 295724A US 29572472 A US29572472 A US 29572472A US 3898045 A US3898045 A US 3898045A
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United States
Prior art keywords
blood
oxygen
chamber
outlet
oxygenator
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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
Application number
US295724A
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English (en)
Inventor
Wallace W Bowley
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
BWXT Intech Inc
Original Assignee
Intech Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Intech Corp filed Critical Intech Corp
Priority to US295724A priority Critical patent/US3898045A/en
Priority to IT52907/73A priority patent/IT997864B/it
Priority to FR7335528A priority patent/FR2201904B1/fr
Priority to IL43375A priority patent/IL43375A0/xx
Priority to AU61033/73A priority patent/AU6103373A/en
Priority to ZA00737801A priority patent/ZA737801B/xx
Priority to BR7770/73A priority patent/BR7307770D0/pt
Priority to DD173900A priority patent/DD114754A5/xx
Priority to SU1964837A priority patent/SU559624A3/ru
Priority to JP48111561A priority patent/JPS523236B2/ja
Priority to NL7313746A priority patent/NL7313746A/xx
Priority to BE136413A priority patent/BE805745A/xx
Priority to ES419384A priority patent/ES419384A1/es
Priority to DE19732350379 priority patent/DE2350379A1/de
Priority to LU68569A priority patent/LU68569A1/xx
Priority to FR7433206A priority patent/FR2252117A1/fr
Priority to DE19742447623 priority patent/DE2447623A1/de
Priority to JP50062580A priority patent/JPS5148758A/ja
Priority to US05/581,971 priority patent/US4017279A/en
Priority to US05/598,630 priority patent/US3960657A/en
Application granted granted Critical
Publication of US3898045A publication Critical patent/US3898045A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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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
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/32—Oxygenators without membranes
    • 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
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/32—Oxygenators without membranes
    • A61M1/322—Antifoam; Defoaming
    • A61M1/325—Surfactant coating; Improving wettability
    • 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
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D19/00—Degasification of liquids
    • B01D19/0031—Degasification of liquids by filtration
    • 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
    • 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
    • Y10S261/00—Gas and liquid contact apparatus
    • Y10S261/26—Foam
    • 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
    • Y10S261/00—Gas and liquid contact apparatus
    • Y10S261/28—Blood oxygenators

Definitions

  • bubble type oxygenators there is a relationship be tween bubble surface area and film resistance to diffusion which should be optimized in order to maximize the diffusion rate. For a given gas flow rate a small number of large bubbles has too small a mass transfer area for efficient diffusion, whereas a large number of very small bubbles has sufficient interface area but inefficient diffusion characteristics. As might be expected, there exists an optimum size bubble for most efficient diffusion. Certain well known physical proper ties have a bearing upon diffusion rate, an important one being surface film resistance. At the surface of each oxygen bubble there exists a layer of oxygen saturated blood. This is an effective boundary layer which reduces the rate at which the remainder of the oxygen bubble diffuses into the blood thereby reducing the overall oxygenation rate for a given gas flow rate.
  • This boundary layer is more effective for reducing diffusion of small bubbles than of large bubbles.
  • Diffusion rate also relates to the speed at which bubbles rise through the blood. It may thus be appreciated that attempts have been made to produce bubbles of relatively precise size in prior bubble type oxygenators. This gives rise to the present necessity of manufacturing the oxygen bubble diffuser to very close tolerances, a difficult and expensive task at best.
  • Apparatus has alsobeen devised where the diffusion chamber is filled withspherical bodies in order to provide a sufficient agitation for enhanced oxygenation ( Russian Pat. No. 302,125).
  • the blood is made to flow in one direction and the oxygen in the opposite direction through the oxygenator for the stated reason of increasing the rate of diffusion.
  • turbulence will likely occur when the oxygen and the blood travel in opposite directions and a significant amount of hemolysis may thereby result.
  • That invention does notprovide a means for preventing hemolysis due to the movement or vibration of the spherical bodies in the chamber as the oxygen and blood move through. nor does it provide for a means to control bubble size.
  • the bubble-type oxygenators have additional provisions for. defoaming the blood after it has been oxygenated because at that point the blood is in the form of a foam.
  • Several previous devices employ a cylinder packed with chips or fibers soaked in a conventional chemical defoaming or non-wetting agent to break down the bubbles. These structures do not have a uniform density defoamer so that defoaming action is different at different locations within the defoamer. Serious danger to the patient has resulted from this type of defoamer fortwo primary reasons.
  • the invention herein disclosed is an improved blood oxygenator for use as a substitute for the lungs of a patient during cardiac and related surgery. It comprises a diffuser from which oxygen bubblesof relatively uniform predetermined size flow into an ejector filled with blood to make a mixture of blood and oxygen. This mixture flows through a chamber filled with spherical hard beads of uniform size forming L a lattice structure. As the oxygen bubbles and the blood move through the bead lattice, oxygen is diffused into the'blood and carbon dioxide is removed therefrom. This reaction is facilitated by frictional contact between the beads and the bubbles in the blood as they pass through the bead lattice.
  • the resulting action may .properly be termed a wiped film bubble oxygenation process.
  • the oxygenated blood foam thus generated leaves the lattice chamber and enters a defoaming section which has radially and axially uniform defoaming properties.
  • defoamer embodiments are set forth in the detailed description hereinbelow.
  • the oxygenated defoamed blood flowsover aheat exchanger in order to effect whatever' temperature changes are desired and from there it flows into a calibrated blood reservoir, ready to return to the arterial system of the patient.
  • the object of this invention is to provide a simple, relatively inexpensive, disposable blood oxygenator having significantly improved blood flow rate and oxygenation efficiency. Additionally, this'oxygenator includes a reliable and constant defoamer which substantially reduces the possibility of dangerous contamination of the blood by chemical antLfoaming agents.
  • an oxygenator 11 preferably of cylindrical configuration, which comprises ejector 12, a diffuser 13 within the ejector, a lattice chamber 14 formed of a bed of rigid beads 15 in a cylinder 16, a diverter 17, a defoamer 18, a heat exchanger 21 having a core 22 supported by rings 23 therein, and a graduated reservoir 24.
  • Ejector 12 is essentially a mixing chamber and bubv.ble pump having side walls 25 which are concave inward.
  • Oxygen is supplied through conduit 26 to the oxygenator from an outside source (not shown), entering gdiffuser 13.
  • the fabric may be Dacron (a registered trademark) or other suitable materiaI-having relatively uniform openings approximately forty microns across.
  • Retaining ring 29 may be any non-corrosive relatively rigid material such as Lucite (a duPont trademark) or stainless steel. Since a relatively inexpensive, disposable yet sturdy structure is contemplated, a rigid plastic retaining ring is preferred.
  • the oxygenator of this invention is not limited to being disposable and the materials used may vary due to different requirements of the users.
  • oxygen depleted venous blood enters the ejector through conduits 31.
  • the ejector is normally full of blood and at the beginning of an operation must be primed with blood or a saline solution in the normal manner.
  • Oxygen is released from diffuser head.2'7 forming bubbles of substantially uniform size in the blood.
  • the preciseness of bubble size is not critical.
  • the ejector with its concave walls 25 acts as a bubble pump. This structure not only moves the blood through the oxygenator, but effectively causes the oxygen bubbles to be mixed throughout the blood at the top of the ejector, as the mixture enters the lattice chamber.
  • the beads in the lattice chamber are tightly packed and are of uniform size. These beads are preferably 6 mm in diameter but beads ranging from 3 mm to lo mm may be used.
  • the beads may be made of any suitable material which provide a relatively smooth, hard surface. While glass is the substance normally preferred, many other materials such as polyethylene and polytetrafluoroethylene may be used.
  • a coarse mesh cloth 33 separates the bead bed from the ejector and may be mounted to the bottom of cylinder 16 by a conventional retaining ring or other suitable means.
  • Cloth 33 has a mesh opening sufficiently small so as to prevent any of the beads from escaping from the lattice chamber while permitting free flow of the blood/oxygen mixture from the ejector to the lattice chamber.
  • the top of the lattice chamber is also fitted with a similar coarse mesh cloth 33 to prevent any of the beads from escaping into the defoamer.
  • the beads in the chamber are preferably secured together to prevent any vibration or movement within the lattice network. Ultrasonic welding is one good way of accomplishing this desired result Even with the beads secured together, mesh elements 33 are employed at eitherend of the cylinder 16 in case one of the beads should come loose.
  • this invention teaches that the bubble is made to traverse a long and tortuous path through the bead lattice. As the bubble encounters each solid bead, there is a wiping action at the diffusion resistant boundary layer of the bubble which physically dislodges or breaks down the boundary layer and results in decreased resistance to the diffusion of oxygen into the blood.
  • the boundary layer reforms as the bubble retreats from each collision with a bead but as each oxygenbubble makes its way upward through the bead lattice, it has a large number of collisions with beads. In the course of each collision, the boundary layer is temporarily broken down and diffusion is facilitated.
  • the rate of diffusion of oxygen in the venous blood isincreased by the presence of thebeads because of the greatly increased surface area for diffusion which the beads provide and by the wiping effect produced by the bubble-bead collisions. It may thus be appreciated that the terminology wiped film bubble oxygenation process is quite appropriate.
  • the flow of oxygen and venous blood is in the same upward direction through the center of the oxygenator, thus eliminating significant resistance to blood flow in opposite directions.
  • the common directional flow of blood and oxygen bubbles means that blood and oxygen *are in contact tzlfirdughout the tirne thatthe blood is flowing through the lattice chamber, thus increasing the diffusion rate.
  • the co-directional flowof the blood and oxygen avoids the turbulence which would result from the collision of two oppositely directed flows.
  • the uniform spacingsbetween the beads can be designed to permit only bubbles of the desired size to proceed through the bead lattice thereby providing maximim diffusion efficiency. Larger bubbles will be separated as they 'pass through the restricted passageways between the beads, thereby accomplishing the desired effect. Consequently, fabric 28 on diffuser'head 27 need not'be manufactured to extremely close tolerances since the bead bed will reduce bubble size as'the mixture passes'through it.
  • the oxygenated blood foam contacts diverter 17 directly from the top of lattice chamber 14.
  • the diverter consists of a concave conical surface preferably made of clear plastic although other shapes and materials may be used.
  • the foam is directed'outward by the diverter and enters defoamer 18 which surrounds the top portion of the lattice chamber above the heat exchanger. Note that the defoamer fabric extends to the center of the oxygenator between the top of the lattice chamber and the diverter.
  • defoamer 18 With reference not to FIG. 3, a top view of defoamer 18 is shown. It consists of a woven cloth 34 which is wound around the upper portion of the lattice chamber a predetermined number of turns in order to insure radial uniformity and consistency in production. Defoaming may be achieved in the well-known manner wherein bubbles containing carbon dioxide and oxygen collapse on fibers which have been coated by spraying or dipping with a chemical antifoam or nonwetting agent.
  • a preferred embodiment of the defoamer is to wrap the lattice chamber with a material comprising two alternating layers of fabric, one wetting and one nonwetting.
  • the bubbles are pulled apart by being repelled from the non-wetting material and attracted to the wetting material whereon it col lapses and drains to the reservoir 24.
  • An alternative preferred embodiment of the defoamer is to use a cloth woven of wetting fibers running horizontally and nonwetting fibers running vertically. The bubbles are repelled and attracted as stated above, causing the bubbles to collapse in a single vertical plane drain to the reservoir.
  • These two preferred embodiments utilize fibers whose wetting and non-wetting properties are inherent in the materials themselves ratherthan the result of treatment with chemical agents. Examples of nonwetting materials are nylon and polytetrafluoroethylene, while wetting materials may be glass fiber or fibersfrom the polycarbonate family such as Lexan (a registered trademark).
  • Carbon dioxide and excess oxygen released from the blood as it is defoamed is' exhausted from the oxygenator through vent 35 in the top of the defoamer.
  • the vent may be equipped with a'conventional bacteriological filter (not shown) to prevent possible contamination ofthe atmosphere in the operating room..
  • the oxygenated blood drains from the defoamer and is allowed to flow over the heat exchanger 21.
  • the heat exchanger is an annular cylindrical containerwith an annular core 22 of closedcell foam filling the bulk of the interior thereof. The core is held in place by means of rings 23 at the top and bottom of the'container. Heated or cooled water is pumpedthrough the heat exchanger, entering through conduit 36 and leaving through'conduit 37. The bloodis th'e'reby maintained at a predetermined desired temperature. Fluid other than water could be used if desired; This particular configuration for the heat e'xchangerpermits a large surface area for rapid temperature adjustment ofthe blood flowing over its sides while having a reduced interior volume to permit rapid fluid exchange within it. t
  • the oxygenated blood of desired temperature is stored in a reservoir' 24 which preferably has transparent walls.
  • the reservoir is an annular configuration and surrounds the ejector and diffuser and the lower end of the lattice chamber.
  • the reservoir' is calibratedtscale 38) as to volume in order that theamount of blood available can easily be'monitored 'duringthe operation.
  • the oxygenated blood is removed from the reservoir through tubing 40 controlled by conventional ball-type check valve 39 which closes the outlet when insufficient blood is present in the reservoir. This prevents any air from getting into the patients arterial system in an emergency situation when the blood reservoir becomes empty.
  • the heat exchanger resides within the reservoir in order to 'rnaintain the'blood temperature as desired.
  • a ring 41 is secured to the top of the oxygenator to provide for attachment of the unit to a ring stand holder.
  • the main shell and most of the interior parts of this oxygenator are made of substantially rigid transparent plastic so that its proper operation may be observed at all times.
  • the plastic elements may be secured together by adhesive or by other suitable means.
  • By being made'of plastic it is disposable, inex pensive to make and shatter resistant.
  • the overall size of this oxygenator is approximately 18 inches in height and 7 inches in diameter for adults/Because thevolume necessary for babies is much lessfa reduced size oxygenator is available for pediatric purposes.
  • the size specified above is by way of example only and is in no way limiting.
  • the invention herein disclosed is a very compact. vertically hung oxygenator. Installation time and operator training are minimal since the device is presterilized and disposable, while being very simple to set up and operate. Those skilled in the art will readily appreciate that various modifications and improvements to this oxygenator may be made to suit particular requirements which are within the scope of the invention.
  • a blood oxygenator comprising:
  • said mixing and pumping means having at least one blood inlet port at one end and a blood foam outlet at the opposite end;
  • oxygen diffusing means within said mixing and pumping means, said oxygen diffusing means having an oxygen inlet port and having an oxygen outlet spaced from either end of said mixing and pumping means, said oxygen diffusing means further comprising: means at said oxygen outlet for discharging oxygen into the blood in said mixing and pumping means in the form of bubbles;
  • a lattice bed comprising a multiplicity of hard beads of substantially uniform size being tightly packed within and substantially filling said chamber to thereby provide a relatively large collision surface area within said chamber and a plurality of tortuous paths therethrough, each of which is substantially longer than said chamber, said chamber having an outlet and having an inlet coupled to said blood foam outlet of said mixing and pumping means;
  • defoaming means within said housing adjacent said outlet of said chamber, said blood foam being separated into gases and fluid blood within said defoaming means;
  • fluid blood outlet means mounted in the bottom of said storage means.
  • said means for maintaining said lattice bed in tightly packed configuration comprises a substantially rigid coarse mesh cloth'at each end of said chamber confining said beads therein.
  • said means for discharging oxygen into the blood in the form of bubbles comprises a fabric covering said oxygen outlet of said oxygen diffusing means, said fabric having a multiplicity of openings therethrough of substantially uniform size.
  • said means for adjusting blood temperature is an annular cylindrical container surrounding said mixing and pumping means and wherein said fluid blood storage means is an annular cylindrical chamber surrounding said mixing and pumping means, said temperature adjusting means container being located within said fluid blood storage means chamber.
  • each such layer is in confronting relationship and touches the next adjacent layer, said cloth being formed of a multiplicity of fibers, a first portion of said fibers having nonwetting characteristics relative to blood, and a second portion of said fibers having a lesser degree of non-wetting characteristics relative to blood than said first portion of said fibers.
  • said mixing and pumping means is elongated and has a longitudinal mid-point cross section which is substantially less than the cross section thereof at said outlet end;
  • said oxygen outlet of said oxygen diffusing means is located substantially at said longitudinal mid-point of said mixing and pumping means.
  • a blood oxygenator comprising:
  • said mixing and pumping means having at least one blood inlet port at one end and a blood foam outlet at the opposite end;
  • oxygen diffusing means within said mixing and pumping means, said oxygen diffusing means having an oxygen inlet port and having an oxygen outlet spaced from either end of said mixing and pumping means, said oxygen diffusing means further comprising:
  • a lattice bed comprising a multiplicity of hard beads of substantially uniform size being tightly packed within and substantially filling said chamber to thereby provide a relatively large collision surface area within said chamber and a plurality of tortuous paths therethrough, said chamber having an outlet and having an inlet coupled to said blood foam outlet of said mixing and pumping means; means for maintaining said lattice bed in tightly packed configuration within said chamber; defoaming means within said housing adjacent said outlet of said chamber, said blood foam being separated into gases and fluid blood within said defoaming means, said defoaming means comprising: multiple layers of cloth wherein each such layer is in confronting relationship and touches the next adjacent layer, said cloth being formed of a multiplicity of fibers, a first portion of said fibers having non-wetting characteristics relative to blood, and a second portion of said fibers having a lesser degree of nonwetting characteristics relative to blood than said first portion of said fibers; fluid blood storage means below and in communication with said defoaming means; and fluid blood outlet means mounted in the bottom of said storage
  • first portion of said fibers having non-wetting characteristics comprises first layers of said multiple layers of cloth
  • second portion of said fibers having a lesser degree of non-wetting characteristics comprises second layers of said multiple layers of cloth, one of said first layers of cloth being located between two adjacent confronting second layers of cloth in alternating fashion throughout said defoaming means.
  • each of said layers of cloth is woven wherein said first portion of said fibers having non-wetting characteristics are oriented in one direction and said second portion of said fibers having a lesser degree of non-wetting characteristics are cross woven with said first portion of said fibers.
  • said first portion of said fibers having non-wetting characteristics relative to blood is a member of the group consisting of glass and polycarbonates; and said second portion of said fibers having a lesser degree of non-wetting characteristics relative to blood is a member of the group consisting of nylon and polytetrafluoroethylene.
  • a blood oxygenator comprising:
  • said mixing and pumping means having at least one blood inlet port at one end and a blood foam outlet at the opposite end, said mixing and pumping means being elongated and having a midpoint cross section which is substantially less than the cross section thereof at said outlet end;
  • oxygen diffusing means within said mixing and pumping means, said oxygen diffusing means having an oxygen inlet port and having an oxygen outlet spaced from either end of said mixing and pumping means and located substantially at said mid-point thereof, said oxygen diffusing means further comprising: means at said oxygen outlet for discharging oxygen into the blood in said mixing and pumping means in the form of bubbles, the velocity of the oxygen being converted to a foam pressure at said outlet of said mixing and pumping means due to the expanding cross section thereof from the point of entry of the oxygen bubbles to said outlet;
  • a lattice bed comprising a multiplicity of hard beads of substantially uniform size being tightly packed within and substantially filling said chamber to 7 thereby provide a relatively large collision surface area within said chamber and a plurality of tortuous paths therethrough, said lattice chamber having an outlet and having an inlet coupled to said blood foam outlet of said mixing and pumping means;
  • defoaming means within said housing adjacent said outlet of said lattice chamber, said blood foam being separated into gases and fluid blood within said defoaming means;
  • fluid blood outlet means mounted in the bottom of said storage means.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Emergency Medicine (AREA)
  • Biomedical Technology (AREA)
  • Veterinary Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Public Health (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Urology & Nephrology (AREA)
  • Chemical & Material Sciences (AREA)
  • Cardiology (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • External Artificial Organs (AREA)
  • Degasification And Air Bubble Elimination (AREA)
US295724A 1972-10-06 1972-10-06 Blood oxygenator Expired - Lifetime US3898045A (en)

Priority Applications (20)

Application Number Priority Date Filing Date Title
US295724A US3898045A (en) 1972-10-06 1972-10-06 Blood oxygenator
IT52907/73A IT997864B (it) 1972-10-06 1973-10-03 Perfezionamento nei dispositivi ossigenatori di sangue
IL43375A IL43375A0 (en) 1972-10-06 1973-10-04 A blood oxygenator
AU61033/73A AU6103373A (en) 1972-10-06 1973-10-04 Blood oxygenator
FR7335528A FR2201904B1 (en)van) 1972-10-06 1973-10-04
BE136413A BE805745A (fr) 1972-10-06 1973-10-05 Dispositif pour oxygener le sang
DD173900A DD114754A5 (en)van) 1972-10-06 1973-10-05
SU1964837A SU559624A3 (ru) 1972-10-06 1973-10-05 Оксигенатор
JP48111561A JPS523236B2 (en)van) 1972-10-06 1973-10-05
NL7313746A NL7313746A (en)van) 1972-10-06 1973-10-05
ZA00737801A ZA737801B (en) 1972-10-06 1973-10-05 Blood oxygenators
ES419384A ES419384A1 (es) 1972-10-06 1973-10-05 Un oxigenador de sangre del tipo de burbuja.
BR7770/73A BR7307770D0 (pt) 1972-10-06 1973-10-05 Oxigenador do sangue aperfeicoado
DE19732350379 DE2350379A1 (de) 1972-10-06 1973-10-08 Blut-oxygenator
LU68569A LU68569A1 (en)van) 1972-10-06 1973-10-08
FR7433206A FR2252117A1 (en)van) 1972-10-06 1974-10-02
DE19742447623 DE2447623A1 (de) 1972-10-06 1974-10-05 Schaumvernichter
JP50062580A JPS5148758A (en)van) 1972-10-06 1975-05-27
US05/581,971 US4017279A (en) 1972-10-06 1975-05-29 Defoamer apparatus
US05/598,630 US3960657A (en) 1972-10-06 1975-07-24 Method for oxygenating blood

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US295724A US3898045A (en) 1972-10-06 1972-10-06 Blood oxygenator

Related Child Applications (2)

Application Number Title Priority Date Filing Date
US05/581,971 Division US4017279A (en) 1972-10-06 1975-05-29 Defoamer apparatus
US05/598,630 Division US3960657A (en) 1972-10-06 1975-07-24 Method for oxygenating blood

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US3898045A true US3898045A (en) 1975-08-05

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US295724A Expired - Lifetime US3898045A (en) 1972-10-06 1972-10-06 Blood oxygenator

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US (1) US3898045A (en)van)
JP (2) JPS523236B2 (en)van)
AU (1) AU6103373A (en)van)
BE (1) BE805745A (en)van)
BR (1) BR7307770D0 (en)van)
DD (1) DD114754A5 (en)van)
DE (1) DE2350379A1 (en)van)
ES (1) ES419384A1 (en)van)
FR (2) FR2201904B1 (en)van)
IL (1) IL43375A0 (en)van)
IT (1) IT997864B (en)van)
LU (1) LU68569A1 (en)van)
NL (1) NL7313746A (en)van)
SU (1) SU559624A3 (en)van)
ZA (1) ZA737801B (en)van)

Cited By (37)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4017279A (en) * 1972-10-06 1977-04-12 Intech, Inc. Defoamer apparatus
DE2704554A1 (de) * 1976-02-03 1977-08-04 Shiley Lab Inc Sauerstoffbehandlungsgeraet fuer blut
US4065264A (en) * 1976-05-10 1977-12-27 Shiley Laboratories, Inc. Blood oxygenator with integral heat exchanger for regulating the temperature of blood in an extracorporeal circuit
US4131431A (en) * 1976-12-27 1978-12-26 Siposs George G Blood shut-off valve
US4138288A (en) * 1976-05-10 1979-02-06 Shiley Scientific Incorporated Method and apparatus for oxygenating and regulating the temperature of blood
US4138464A (en) * 1976-05-10 1979-02-06 Lewin John E Blood oxygenator with integral heat exchanger
US4140635A (en) * 1977-04-13 1979-02-20 Esmond William G Purification device
US4182739A (en) * 1976-02-03 1980-01-08 Shiley Incorporated Blood oxygenator
US4183961A (en) * 1976-02-03 1980-01-15 Shiley Incorporated Method of oxygenating blood
US4224413A (en) * 1975-05-21 1980-09-23 Beecham Group Limited Cell culture method
US4228125A (en) * 1978-06-20 1980-10-14 Cobe Laboratories, Inc. Gas exchange apparatus
US4261951A (en) * 1978-03-02 1981-04-14 Dsd "Metalchim" Apparatus for blood oxygenation
US4268476A (en) * 1975-06-06 1981-05-19 Bentley Laboratories, Inc. Blood oxygenator
US4282180A (en) * 1975-06-06 1981-08-04 Bentley Laboratories, Inc. Blood oxygenator
US4297318A (en) * 1975-06-06 1981-10-27 Bentley Laboratories, Inc. Blood oxygenator
US4336224A (en) * 1979-01-16 1982-06-22 Travenol Laboratories, Inc. Bubble oxygenator
US4372914A (en) * 1975-06-06 1983-02-08 Bentley Laboratories, Inc. Blood oxygenator
US4490331A (en) * 1982-02-12 1984-12-25 Steg Jr Robert F Extracorporeal blood processing system
US4585056A (en) * 1984-04-18 1986-04-29 Norton Company Heat exchanger
US4599093A (en) * 1982-02-12 1986-07-08 Steg Jr Robert F Extracorporeal blood processing system
US4623518A (en) * 1975-06-06 1986-11-18 Baxter-Travenol Laboratories, Inc. Blood oxygenator
US4637917A (en) * 1983-10-14 1987-01-20 Reed Charles C Bubble oxygenator
US4734373A (en) * 1986-06-24 1988-03-29 Bartal Arie H Apparatus for enhancing cell growth, preservation and transport
US4954317A (en) * 1975-06-06 1990-09-04 Baxter International, Inc. Blood oxygenator
US5116308A (en) * 1989-01-13 1992-05-26 Terumo Kabushiki Kaisha Apparatus for processing fluid and method of driving the same
US5166067A (en) * 1988-11-30 1992-11-24 Hitachi, Ltd. Culturing method, system and apparatus for cell culture
US5403388A (en) * 1993-05-12 1995-04-04 Pfiffner; Tim E. Surfactant mediation sparge tube
US5578267A (en) * 1992-05-11 1996-11-26 Minntech Corporation Cylindrical blood heater/oxygenator
US5849186A (en) * 1996-11-15 1998-12-15 C. R. Bard Inc. Integrated cardiotomy and venous blood reservoir
US6001306A (en) * 1996-11-07 1999-12-14 C. R. Bard, Inc. Integrated oxygenator and heat exchanger
US6500394B1 (en) * 1999-06-30 2002-12-31 Cellpoint Scientific, Inc. Dry sterilizer
US6630107B1 (en) * 1998-10-28 2003-10-07 Salvador Merce Vives Blood pumping equipment for extracorporeal circulation and ventricular assistance
US20110137236A1 (en) * 2007-10-01 2011-06-09 Baxter International Inc. Fluid delivery systems and methods having floating baffle aided air removal
US8777832B1 (en) 2013-03-14 2014-07-15 The University Of Kentucky Research Foundation Axial-centrifugal flow catheter pump for cavopulmonary assistance
US8906300B2 (en) 2011-08-11 2014-12-09 The University Of Kentucky Research Foundation Even perfusion pump-integrated blood oxygenator
WO2015007720A1 (en) * 2013-07-18 2015-01-22 Universiteit Gent Oxygenator
US10625009B2 (en) 2016-02-17 2020-04-21 Baxter International Inc. Airtrap, system and method for removing microbubbles from a fluid stream

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DE2757345C2 (de) * 1977-12-22 1986-01-23 Wacker-Chemie GmbH, 8000 München Verfahren zur Schaumzerstörung beim Entfernen von Restmonomer aus Reaktionsgemischen
DE8704467U1 (de) * 1987-01-15 1988-05-26 Quarzlampenfabrik Dr.-Ing. Felix W. Müller GmbH & Co KG, 45239 Essen Gerät zur Herstellung von oxygeniertem Blut

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US3204631A (en) * 1961-05-01 1965-09-07 Louis G Fields Blood oxygenator and pump apparatus
US3291568A (en) * 1964-04-06 1966-12-13 Richard D Santter Cardio-pulmonary by-pass oxygenator unit
US3468631A (en) * 1965-06-21 1969-09-23 Bentley Lab Blood oxygenator with heat exchanger
US3513845A (en) * 1966-09-15 1970-05-26 United Aircraft Corp Bypass heart pump and oxygenator system
US3488158A (en) * 1966-12-12 1970-01-06 Bentley Lab Bubbler assembly for oxygenator
US3547591A (en) * 1968-10-16 1970-12-15 Jose C Torres Bubble film oxygenator
US3578411A (en) * 1969-07-22 1971-05-11 Bentley Lab Bubbler assembly for blood treating apparatus
US3729377A (en) * 1971-03-12 1973-04-24 Baxter Laboratories Inc Envelope oxygenator for blood having inflatable portions and process of using same
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Cited By (40)

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Publication number Priority date Publication date Assignee Title
US4017279A (en) * 1972-10-06 1977-04-12 Intech, Inc. Defoamer apparatus
US4224413A (en) * 1975-05-21 1980-09-23 Beecham Group Limited Cell culture method
US4297318A (en) * 1975-06-06 1981-10-27 Bentley Laboratories, Inc. Blood oxygenator
US4372914A (en) * 1975-06-06 1983-02-08 Bentley Laboratories, Inc. Blood oxygenator
US4282180A (en) * 1975-06-06 1981-08-04 Bentley Laboratories, Inc. Blood oxygenator
US4268476A (en) * 1975-06-06 1981-05-19 Bentley Laboratories, Inc. Blood oxygenator
US4954317A (en) * 1975-06-06 1990-09-04 Baxter International, Inc. Blood oxygenator
US4623518A (en) * 1975-06-06 1986-11-18 Baxter-Travenol Laboratories, Inc. Blood oxygenator
US4183961A (en) * 1976-02-03 1980-01-15 Shiley Incorporated Method of oxygenating blood
US4182739A (en) * 1976-02-03 1980-01-08 Shiley Incorporated Blood oxygenator
US4067696A (en) * 1976-02-03 1978-01-10 Swiley Laboratories, Inc. Blood oxygenator
DE2704554A1 (de) * 1976-02-03 1977-08-04 Shiley Lab Inc Sauerstoffbehandlungsgeraet fuer blut
US4065264A (en) * 1976-05-10 1977-12-27 Shiley Laboratories, Inc. Blood oxygenator with integral heat exchanger for regulating the temperature of blood in an extracorporeal circuit
US4138464A (en) * 1976-05-10 1979-02-06 Lewin John E Blood oxygenator with integral heat exchanger
US4138288A (en) * 1976-05-10 1979-02-06 Shiley Scientific Incorporated Method and apparatus for oxygenating and regulating the temperature of blood
US4131431A (en) * 1976-12-27 1978-12-26 Siposs George G Blood shut-off valve
US4140635A (en) * 1977-04-13 1979-02-20 Esmond William G Purification device
US4261951A (en) * 1978-03-02 1981-04-14 Dsd "Metalchim" Apparatus for blood oxygenation
US4228125A (en) * 1978-06-20 1980-10-14 Cobe Laboratories, Inc. Gas exchange apparatus
US4336224A (en) * 1979-01-16 1982-06-22 Travenol Laboratories, Inc. Bubble oxygenator
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
US4637917A (en) * 1983-10-14 1987-01-20 Reed Charles C Bubble oxygenator
US4585056A (en) * 1984-04-18 1986-04-29 Norton Company Heat exchanger
US4734373A (en) * 1986-06-24 1988-03-29 Bartal Arie H Apparatus for enhancing cell growth, preservation and transport
US5166067A (en) * 1988-11-30 1992-11-24 Hitachi, Ltd. Culturing method, system and apparatus for cell culture
US5116308A (en) * 1989-01-13 1992-05-26 Terumo Kabushiki Kaisha Apparatus for processing fluid and method of driving the same
US5578267A (en) * 1992-05-11 1996-11-26 Minntech Corporation Cylindrical blood heater/oxygenator
US5403388A (en) * 1993-05-12 1995-04-04 Pfiffner; Tim E. Surfactant mediation sparge tube
US6001306A (en) * 1996-11-07 1999-12-14 C. R. Bard, Inc. Integrated oxygenator and heat exchanger
US5849186A (en) * 1996-11-15 1998-12-15 C. R. Bard Inc. Integrated cardiotomy and venous blood reservoir
US6630107B1 (en) * 1998-10-28 2003-10-07 Salvador Merce Vives Blood pumping equipment for extracorporeal circulation and ventricular assistance
US6500394B1 (en) * 1999-06-30 2002-12-31 Cellpoint Scientific, Inc. Dry sterilizer
US20110137236A1 (en) * 2007-10-01 2011-06-09 Baxter International Inc. Fluid delivery systems and methods having floating baffle aided air removal
US8025716B2 (en) * 2007-10-01 2011-09-27 Baxter International Inc. Fluid delivery systems and methods having floating baffle aided air removal
US8906300B2 (en) 2011-08-11 2014-12-09 The University Of Kentucky Research Foundation Even perfusion pump-integrated blood oxygenator
US9468557B2 (en) 2011-08-11 2016-10-18 The University Of Kentucky Research Foundation Compact heat exchanger for veno-venous perfusion-induced systemic hyperthermia systems
US8777832B1 (en) 2013-03-14 2014-07-15 The University Of Kentucky Research Foundation Axial-centrifugal flow catheter pump for cavopulmonary assistance
WO2015007720A1 (en) * 2013-07-18 2015-01-22 Universiteit Gent Oxygenator
US10625009B2 (en) 2016-02-17 2020-04-21 Baxter International Inc. Airtrap, system and method for removing microbubbles from a fluid stream

Also Published As

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BR7307770D0 (pt) 1974-09-24
DD114754A5 (en)van) 1975-08-20
IT997864B (it) 1975-12-30
SU559624A3 (ru) 1977-05-25
DE2350379A1 (de) 1974-04-11
LU68569A1 (en)van) 1973-12-27
BE805745A (fr) 1974-04-05
FR2201904B1 (en)van) 1977-09-23
FR2201904A1 (en)van) 1974-05-03
JPS523236B2 (en)van) 1977-01-26
IL43375A0 (en) 1974-01-14
JPS4994191A (en)van) 1974-09-06
NL7313746A (en)van) 1974-04-09
ZA737801B (en) 1975-05-28
ES419384A1 (es) 1976-04-01
FR2252117A1 (en)van) 1975-06-20
AU6103373A (en) 1975-04-10
JPS5148758A (en)van) 1976-04-27

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