CA1094462A - Membrane fluid diffusion exchange device - Google Patents
Membrane fluid diffusion exchange deviceInfo
- Publication number
- CA1094462A CA1094462A CA277,880A CA277880A CA1094462A CA 1094462 A CA1094462 A CA 1094462A CA 277880 A CA277880 A CA 277880A CA 1094462 A CA1094462 A CA 1094462A
- Authority
- CA
- Canada
- Prior art keywords
- tubes
- blood
- block
- oxygenator
- outlet
- 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
Links
Classifications
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D63/00—Apparatus in general for separation processes using semi-permeable membranes
- B01D63/02—Hollow fibre modules
- B01D63/027—Twinned or braided type modules
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D63/00—Apparatus in general for separation processes using semi-permeable membranes
- B01D63/02—Hollow fibre modules
Abstract
ABSTRACT OF THE DISCLOSURE
The device includes a block of a plurality of layers of woven silastic capillary tubes secured to a peripheral rigid frame; manifolds are attached to the frame to allow a treating fluid to circulate through the tubes and to allow recuperation of waste fluids for exhaustion; means are also provided to allow circulation of blood transversely and exteriorly of the tubes whereby the diffusion process between the treating fluid and the blood takes place. The device may be used as an artificial lung for thoracic implantation or paracorporeal respiratory supplementation.
The device includes a block of a plurality of layers of woven silastic capillary tubes secured to a peripheral rigid frame; manifolds are attached to the frame to allow a treating fluid to circulate through the tubes and to allow recuperation of waste fluids for exhaustion; means are also provided to allow circulation of blood transversely and exteriorly of the tubes whereby the diffusion process between the treating fluid and the blood takes place. The device may be used as an artificial lung for thoracic implantation or paracorporeal respiratory supplementation.
Description
-~ 1094462 FIELD OF THE INVENTION ~-The present invention relates to a membrane fluid diffusion exchange device; more particularly, the invention pertains to a blood treating apparatus of the membrane type.
BACKGROUND OF THE INVENTION
Chronic respiratory insufficiency remains one of the unresolved problems of modern medicine. Medical therapeutics offer little hope and a more determined approach must be envisaged, such as homologous lung transplantation, artificial lung implantation or artificial lung paracorporeal supplemen-tation.
It has been observed that membrane oxygenators or "lungs" are less traumatic to blood components than presently available oxygenators in which there is a direct blood-gas contact. The use of a gas permeable membrane imitates the process of gas exchange in the natural lungs where the blood and gas p'hase are separated by the alveolar capillary wall.
Present membrane oxygenators use silastic silicone rubber or silica free silicone rubber which fulfills many of the basic requirements-for an ideal oxygenator membrane. One example of a blood oxygenator using a silastic membrane is found described in U.S. patent No. 3,893,926 issued July 8, 1975 to John A. Awad.
OBJECTS AND STATEMENT OF THE INVENTION
It is an object of the present invention to provide a fluid diffusion device of the membrane type in which the exchange of gases to and from a fluid to be treated is improved.
It is a further object of the present invention to provide a blood oxygenator wherein the oxygenating surface present to the passage of blood is increased thereby influ-'~
encing the overall efficiency of the blood-gas exchange.
This is achieved by providing in a membrane diffusion device layers of woven capillary tubing assembled in a block.
This type of structure is made to match the flow and pressure characteristics of a normal lung and is a major development towards an implantable artificial lung.
The present invention therefore comprises: a block having impervious walls and a flexible inner part formed of a plurality of layers of woven tubular capillary diffusing membranes, the layers being secured to the walls and the membranes having their opposite ends protruding these wallsi inlet chamber means are provided on one portion of the block and in fluid connection with one end of each membrane; outlet chamber means are provided on another portion of the block and in fluid connection with the opposite end of each membrane; and means are further provided for allowing circulation of a fluid to be treated through the inner part of the block, transversely and exteriorily of the woven membranes whereby this fluid may be treated by diffusion of a treating fluid through the membranes into this fluid and whereby waste fluids from this fluid may be recuperated by diffusion through the capillary tubes for exhaustion.
In one preferred embodiment described, the device of the present invention is used as an artificial lung wherein the fluid to be treated is blood and the treating and waste fluids are, respectively, oxygen and carbon dioxide.
The scope of applicability of the present invention will become apparent from the detailed description given hereinafter; it should be understood, however, that this description, while indicating preferred embodiments of the invention, is given by way of illustration only since various ' - lOg~46Z
changes and modifications within the spirit and scope of the invention will become apparent to those skilled in the art from reading the following description. For example, the device of the present invention could be used to simulate a patient's kidney.
IN THE DRAWINGS
Figure 1 is a top perspective view of a fluid diffusion exchange device embodying the present invention;
Figure 2 is a side elevational view thereof;
Figure 3 is a top plan view thereof;
Figure 4 is a greatly enlarged fragmentary view of a woven screen used in the present invention;
Figure 5 is an exemplary illustration of the device used as an implantable artificial lung;
Figures 6 and 7 are diagrammatic illustrations of the operation of an artificial lung; and ~;
Figure 8 is an enlarged partial view of the inlet and outlet ports of the artificial lung illustrated in Figs. 6 and 7.
DESCRIPTION OF PREFERRED EMBODIMENTS
Referring to Figures 1, 2 and 3, one example of a fluid diffusion exchange device 10 is shown enclosed in a transparent casing 12. Device 10 has the shape of a rectangu-lar block that includes a square-shaped wall enclosure 14 and a central area filled with a series of layers of woven capillary tubing screens 16. Referring to Fig. 4, one example of such a screen is shown and consists of a tight rectangular weave of six strands of tubes 18 in one direction for each strand of tubes 20 in the other direction. The tubes are preferably ~ade of silicone rubber, commonly known as silastic tubes having, for example, an inner diameter of 0.3 mm and an outer diameter of 0.6 mm; however, other blood compatible semi-per~eable or .
109~1462 micro-porous materials which may be considered equivalent by persons skilled in the plastic art may also be used.
The structure of block 10 may be better understood by a description of its method of construction. Squares of prede-termined size of the woven material are cut and attached toframes of rigid material, such as plexiglass (trademark) for example, to form grids. A number of these grids are then mounted one above the other to form a block. The open ends of ~-the capillary tubes are then closed by dipping them into a liquid adhesive. The stacked grids are then inserted into a mould and, through a series of successive pressure injection process steps using centrifugal force, impervious walls 14 of the block are formed, so that the ends of the tubes 18, 20 are integral with the wall 14, as shown most clearly in Figure 4 of the drawings. The ends of the capillary tubes projecting beyond the walls of plexiglass (trademark) are then trimmed -off, thus reopening the tubes outside each wall 14 of the block.
The provision of stacked screens of silastic tubing recreates the sponge-like texture of a normal lung; it also matches its elasticity, pulse absorption and resistance to flow.
In Figures 1-3, block 10 is shown enclosed in a transparent casing or housing 12 for when the artificial lung is used paracorporeally. Oppositely disposed side portions 24 and 26 of housing 12 are adhesively affixed to block 10 (with silastic, for example) thereby defining gas inlet and outlet manifolds 28 and 30, each having their respective inlet and outlet ports 32 and 34. Housing 12 further includes pyramidal shaped oppositely disposed end portions sealingly connected to the top and bottom edges of enclosure wall 14 thereby defining liquid inlet and outlet manifolds 40 and 42, ,. . .
`` 1094462 each having their respective inlet and outlet ports 44 and 46.
The artificial lung functions as follows: an oxygenating fluid is blown through port 32 of manifold 28 and into each capillary tube end of chamber 28. Through port 44 of manifold 40, blood is caused to pass and bathes the outside of the capillary tubes. The material of the tubular membranes is permeable to the diffusion of both oxygen and carbon dioxide:
oxygen from the tube lumen diffuses into the blood and carbon dioxide from the blood diffuses into the capillary tubing for exhaustion. Manifold 30 collects, from the opposite ends of the tubes, the exhausted gases which subsequently exit through port 34.
It will be understood that the artificial lung described above forms the inner part of a system that includes gas chambers and non-return valves wh;ch are not shown and which will not be described since they do not, as such, form part of the present invention.
The block device described above can also be built in a system which may be implantable in a thoracic cage in which the normal respiratory movements may be used to propell the respiratory gases through the device. A schematic repre-sentation of an implantable artificial lung is illustrated in Figures 5,6 and 7 occupying almost the entire thoracic volume on one side of a patient. A port 50 in the chest wall 52 allows the inlet and outlet of gas through the artificial lung 54 which is located adjacent the patient's heart 56 and which may be anchored at 58 to the posterior of the thoracic cavity.
A blood inlet tube 60 leading from the patient's pulmonary ; ar~ery is connected to the artificial lung 54; an outlet tube 64 drains blood from the artificial lung 54 into the left atrium. The artificial lung is provided with inlet and outlet ~094~6Z
manifolds 68 and 70. Referring to Figures 6 and 7, the space 72 around the artificial lung 54 fills with oxygenating gas on inspiration and, on expiration, the respiratory gases are chased through lung 54 and outlet chamber 74. A more detailed schematic representation of the inlet and outlet port 50 is shown in Figure 8; it includes a skin and chest button 76, a skin pedicle 78, an inlet valve 80, an outlet valve 82 and an accordeon-like structure 84 separating the gas inlet and outlet chambers 72 and 74.
It should be understood that the above described embodiments of an artificial lung, implantable or paracorporeal, must have gas transfer characteristics (for 2 and C02) and be able to maintain these functions reliably and consistently.
Spac,ng, configuration and size of blood and gas inlet and outlet connections must be adaptable to vascular and cardiac anatomic requirements. All materials contacting blood should be blood compatible, smooth and thromboresistant or easily coatable with thromboresistive coatings without altering gas transfer performance. The spacing in the woven material, the transverse surface area and the number of grids can be adjusted to give the pressure drop characteristics deemed essential in matching the resistance to blood flow found in the remaining lung. Also, the weaving of the capillary tubes must be controlled to prevent preferential flow paths from forming within the lung device.
BACKGROUND OF THE INVENTION
Chronic respiratory insufficiency remains one of the unresolved problems of modern medicine. Medical therapeutics offer little hope and a more determined approach must be envisaged, such as homologous lung transplantation, artificial lung implantation or artificial lung paracorporeal supplemen-tation.
It has been observed that membrane oxygenators or "lungs" are less traumatic to blood components than presently available oxygenators in which there is a direct blood-gas contact. The use of a gas permeable membrane imitates the process of gas exchange in the natural lungs where the blood and gas p'hase are separated by the alveolar capillary wall.
Present membrane oxygenators use silastic silicone rubber or silica free silicone rubber which fulfills many of the basic requirements-for an ideal oxygenator membrane. One example of a blood oxygenator using a silastic membrane is found described in U.S. patent No. 3,893,926 issued July 8, 1975 to John A. Awad.
OBJECTS AND STATEMENT OF THE INVENTION
It is an object of the present invention to provide a fluid diffusion device of the membrane type in which the exchange of gases to and from a fluid to be treated is improved.
It is a further object of the present invention to provide a blood oxygenator wherein the oxygenating surface present to the passage of blood is increased thereby influ-'~
encing the overall efficiency of the blood-gas exchange.
This is achieved by providing in a membrane diffusion device layers of woven capillary tubing assembled in a block.
This type of structure is made to match the flow and pressure characteristics of a normal lung and is a major development towards an implantable artificial lung.
The present invention therefore comprises: a block having impervious walls and a flexible inner part formed of a plurality of layers of woven tubular capillary diffusing membranes, the layers being secured to the walls and the membranes having their opposite ends protruding these wallsi inlet chamber means are provided on one portion of the block and in fluid connection with one end of each membrane; outlet chamber means are provided on another portion of the block and in fluid connection with the opposite end of each membrane; and means are further provided for allowing circulation of a fluid to be treated through the inner part of the block, transversely and exteriorily of the woven membranes whereby this fluid may be treated by diffusion of a treating fluid through the membranes into this fluid and whereby waste fluids from this fluid may be recuperated by diffusion through the capillary tubes for exhaustion.
In one preferred embodiment described, the device of the present invention is used as an artificial lung wherein the fluid to be treated is blood and the treating and waste fluids are, respectively, oxygen and carbon dioxide.
The scope of applicability of the present invention will become apparent from the detailed description given hereinafter; it should be understood, however, that this description, while indicating preferred embodiments of the invention, is given by way of illustration only since various ' - lOg~46Z
changes and modifications within the spirit and scope of the invention will become apparent to those skilled in the art from reading the following description. For example, the device of the present invention could be used to simulate a patient's kidney.
IN THE DRAWINGS
Figure 1 is a top perspective view of a fluid diffusion exchange device embodying the present invention;
Figure 2 is a side elevational view thereof;
Figure 3 is a top plan view thereof;
Figure 4 is a greatly enlarged fragmentary view of a woven screen used in the present invention;
Figure 5 is an exemplary illustration of the device used as an implantable artificial lung;
Figures 6 and 7 are diagrammatic illustrations of the operation of an artificial lung; and ~;
Figure 8 is an enlarged partial view of the inlet and outlet ports of the artificial lung illustrated in Figs. 6 and 7.
DESCRIPTION OF PREFERRED EMBODIMENTS
Referring to Figures 1, 2 and 3, one example of a fluid diffusion exchange device 10 is shown enclosed in a transparent casing 12. Device 10 has the shape of a rectangu-lar block that includes a square-shaped wall enclosure 14 and a central area filled with a series of layers of woven capillary tubing screens 16. Referring to Fig. 4, one example of such a screen is shown and consists of a tight rectangular weave of six strands of tubes 18 in one direction for each strand of tubes 20 in the other direction. The tubes are preferably ~ade of silicone rubber, commonly known as silastic tubes having, for example, an inner diameter of 0.3 mm and an outer diameter of 0.6 mm; however, other blood compatible semi-per~eable or .
109~1462 micro-porous materials which may be considered equivalent by persons skilled in the plastic art may also be used.
The structure of block 10 may be better understood by a description of its method of construction. Squares of prede-termined size of the woven material are cut and attached toframes of rigid material, such as plexiglass (trademark) for example, to form grids. A number of these grids are then mounted one above the other to form a block. The open ends of ~-the capillary tubes are then closed by dipping them into a liquid adhesive. The stacked grids are then inserted into a mould and, through a series of successive pressure injection process steps using centrifugal force, impervious walls 14 of the block are formed, so that the ends of the tubes 18, 20 are integral with the wall 14, as shown most clearly in Figure 4 of the drawings. The ends of the capillary tubes projecting beyond the walls of plexiglass (trademark) are then trimmed -off, thus reopening the tubes outside each wall 14 of the block.
The provision of stacked screens of silastic tubing recreates the sponge-like texture of a normal lung; it also matches its elasticity, pulse absorption and resistance to flow.
In Figures 1-3, block 10 is shown enclosed in a transparent casing or housing 12 for when the artificial lung is used paracorporeally. Oppositely disposed side portions 24 and 26 of housing 12 are adhesively affixed to block 10 (with silastic, for example) thereby defining gas inlet and outlet manifolds 28 and 30, each having their respective inlet and outlet ports 32 and 34. Housing 12 further includes pyramidal shaped oppositely disposed end portions sealingly connected to the top and bottom edges of enclosure wall 14 thereby defining liquid inlet and outlet manifolds 40 and 42, ,. . .
`` 1094462 each having their respective inlet and outlet ports 44 and 46.
The artificial lung functions as follows: an oxygenating fluid is blown through port 32 of manifold 28 and into each capillary tube end of chamber 28. Through port 44 of manifold 40, blood is caused to pass and bathes the outside of the capillary tubes. The material of the tubular membranes is permeable to the diffusion of both oxygen and carbon dioxide:
oxygen from the tube lumen diffuses into the blood and carbon dioxide from the blood diffuses into the capillary tubing for exhaustion. Manifold 30 collects, from the opposite ends of the tubes, the exhausted gases which subsequently exit through port 34.
It will be understood that the artificial lung described above forms the inner part of a system that includes gas chambers and non-return valves wh;ch are not shown and which will not be described since they do not, as such, form part of the present invention.
The block device described above can also be built in a system which may be implantable in a thoracic cage in which the normal respiratory movements may be used to propell the respiratory gases through the device. A schematic repre-sentation of an implantable artificial lung is illustrated in Figures 5,6 and 7 occupying almost the entire thoracic volume on one side of a patient. A port 50 in the chest wall 52 allows the inlet and outlet of gas through the artificial lung 54 which is located adjacent the patient's heart 56 and which may be anchored at 58 to the posterior of the thoracic cavity.
A blood inlet tube 60 leading from the patient's pulmonary ; ar~ery is connected to the artificial lung 54; an outlet tube 64 drains blood from the artificial lung 54 into the left atrium. The artificial lung is provided with inlet and outlet ~094~6Z
manifolds 68 and 70. Referring to Figures 6 and 7, the space 72 around the artificial lung 54 fills with oxygenating gas on inspiration and, on expiration, the respiratory gases are chased through lung 54 and outlet chamber 74. A more detailed schematic representation of the inlet and outlet port 50 is shown in Figure 8; it includes a skin and chest button 76, a skin pedicle 78, an inlet valve 80, an outlet valve 82 and an accordeon-like structure 84 separating the gas inlet and outlet chambers 72 and 74.
It should be understood that the above described embodiments of an artificial lung, implantable or paracorporeal, must have gas transfer characteristics (for 2 and C02) and be able to maintain these functions reliably and consistently.
Spac,ng, configuration and size of blood and gas inlet and outlet connections must be adaptable to vascular and cardiac anatomic requirements. All materials contacting blood should be blood compatible, smooth and thromboresistant or easily coatable with thromboresistive coatings without altering gas transfer performance. The spacing in the woven material, the transverse surface area and the number of grids can be adjusted to give the pressure drop characteristics deemed essential in matching the resistance to blood flow found in the remaining lung. Also, the weaving of the capillary tubes must be controlled to prevent preferential flow paths from forming within the lung device.
Claims (6)
1. A membrane blood oxygenator comprising:
a block formed of a unitary peripheral continuous wall portion and of a flexible inner portion mounted to and inside said wall portion; said flexible inner portion consisting of a plurality of closely stacked adjacent layers of woven silastic capillary tubes having their opposite ends integral with and extending through said wall portion so that leak-proof separation is provided between the inside and the outside of said block;
gas inlet chamber means on one side of said block and in fluid connection with one end of said tubes for allowing oxygen to circulate in said tubes;
gas outlet chamber means on an opposite side of said block as said gas inlet chamber means and in fluid connection with the opposite end of said tubes as said gas inlet chamber means, for allowing recuperation of oxygen and carbon dioxide from said tubes; and means for circulating blood through said flexible inner portion transversely and exteriorly of said woven tubes so that blood is treated by diffusion of said oxygen from said tubes into said blood and by diffusion of oxygen and carbon dioxide from the blood into said tubes for exhaustion through said outlet chamber means.
a block formed of a unitary peripheral continuous wall portion and of a flexible inner portion mounted to and inside said wall portion; said flexible inner portion consisting of a plurality of closely stacked adjacent layers of woven silastic capillary tubes having their opposite ends integral with and extending through said wall portion so that leak-proof separation is provided between the inside and the outside of said block;
gas inlet chamber means on one side of said block and in fluid connection with one end of said tubes for allowing oxygen to circulate in said tubes;
gas outlet chamber means on an opposite side of said block as said gas inlet chamber means and in fluid connection with the opposite end of said tubes as said gas inlet chamber means, for allowing recuperation of oxygen and carbon dioxide from said tubes; and means for circulating blood through said flexible inner portion transversely and exteriorly of said woven tubes so that blood is treated by diffusion of said oxygen from said tubes into said blood and by diffusion of oxygen and carbon dioxide from the blood into said tubes for exhaustion through said outlet chamber means.
2. An oxygenator as defined in Claim 1, said inlet and outlet chamber means comprise inlet and outlet manifolds respectively.
3. An oxygenator as defined in Claim 2, wherein said manifolds are adhesively secured to opposite side portions of said block to thereby define oppositely disposed inlet and outlet chambers.
4. An oxygenator as defined in Claim 1, wherein said means for circulating blood through said flexible inner portion include inlet and outlet manifolds disposed at opposite ends of said block.
5. An oxygenator as defined in Claim 4, wherein said manifolds have outwardly converging side walls for uniform distribution and collection of said blood in and out said inner flexible portion.
6. An oxygenator as defined in Claim 1, wherein said block is so dimensioned, and formed of such materials, so that it is implantable in a patient's body.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA277,880A CA1094462A (en) | 1977-05-06 | 1977-05-06 | Membrane fluid diffusion exchange device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA277,880A CA1094462A (en) | 1977-05-06 | 1977-05-06 | Membrane fluid diffusion exchange device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1094462A true CA1094462A (en) | 1981-01-27 |
Family
ID=4108601
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA277,880A Expired CA1094462A (en) | 1977-05-06 | 1977-05-06 | Membrane fluid diffusion exchange device |
Country Status (1)
| Country | Link |
|---|---|
| CA (1) | CA1094462A (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0374873A2 (en) * | 1988-12-20 | 1990-06-27 | The Dow Chemical Company | Efficient vapor- liquid mass transfer by microporous membrane fibers |
| EP0598909A1 (en) * | 1992-02-12 | 1994-06-01 | Mitsubishi Rayon Co., Ltd. | Hollow yarn membrane module |
| US5922201A (en) * | 1992-02-12 | 1999-07-13 | Mitsubishi Rayon Co., Ltd. | Hollow fiber membrane module |
| WO2011023605A1 (en) * | 2009-08-24 | 2011-03-03 | Dritte Patentportfolio Beteiligungsgesellschaft Mbh & Co. Kg | Three-dimensionally braided hollow fiber module for mass and energy transfer operations |
-
1977
- 1977-05-06 CA CA277,880A patent/CA1094462A/en not_active Expired
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0374873A2 (en) * | 1988-12-20 | 1990-06-27 | The Dow Chemical Company | Efficient vapor- liquid mass transfer by microporous membrane fibers |
| EP0374873A3 (en) * | 1988-12-20 | 1991-01-23 | The Dow Chemical Company | Efficient vapor- liquid mass transfer by microporous membrane fibers |
| EP0598909A1 (en) * | 1992-02-12 | 1994-06-01 | Mitsubishi Rayon Co., Ltd. | Hollow yarn membrane module |
| EP0598909A4 (en) * | 1992-02-12 | 1994-07-20 | Mitsubishi Rayon Co | Hollow yarn membrane module. |
| US5480553A (en) * | 1992-02-12 | 1996-01-02 | Mitsubishi Rayon Co., Ltd. | Hollow fiber membrane module |
| US5922201A (en) * | 1992-02-12 | 1999-07-13 | Mitsubishi Rayon Co., Ltd. | Hollow fiber membrane module |
| WO2011023605A1 (en) * | 2009-08-24 | 2011-03-03 | Dritte Patentportfolio Beteiligungsgesellschaft Mbh & Co. Kg | Three-dimensionally braided hollow fiber module for mass and energy transfer operations |
| EP2708279A1 (en) * | 2009-08-24 | 2014-03-19 | Dritte Patentportfolio Beteiligungsgesellschaft mbH & Co. KG | Three-dimensionally braided hollow fiber module for mass and energy transfer operations |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKEX | Expiry |