WO2015008327A1 - Poumon artificiel - Google Patents

Poumon artificiel Download PDF

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Publication number
WO2015008327A1
WO2015008327A1 PCT/JP2013/069272 JP2013069272W WO2015008327A1 WO 2015008327 A1 WO2015008327 A1 WO 2015008327A1 JP 2013069272 W JP2013069272 W JP 2013069272W WO 2015008327 A1 WO2015008327 A1 WO 2015008327A1
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WO
WIPO (PCT)
Prior art keywords
gas
hollow fiber
partition
blood
fiber membrane
Prior art date
Application number
PCT/JP2013/069272
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English (en)
Japanese (ja)
Inventor
喬 齋藤
Original Assignee
テルモ株式会社
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Publication date
Application filed by テルモ株式会社 filed Critical テルモ株式会社
Priority to PCT/JP2013/069272 priority Critical patent/WO2015008327A1/fr
Publication of WO2015008327A1 publication Critical patent/WO2015008327A1/fr

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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
    • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
    • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
    • A61M1/1698—Blood oxygenators with or without heat-exchangers
    • 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
    • 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
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/36—General characteristics of the apparatus related to heating or cooling
    • A61M2205/366—General characteristics of the apparatus related to heating or cooling by liquid heat exchangers

Definitions

  • the present invention relates to an artificial lung.
  • an artificial lung a housing, a heat exchanger that is housed in the housing and adjusts the temperature of blood, and a gas exchanger that is arranged around the heat exchanger and performs oxygenation and decarboxylation of blood (For example, refer patent document 1).
  • the artificial lung described in Patent Document 1 is integrally formed to protrude from a housing, and is provided with a wall interposed between a heat exchanger and a gas exchanger.
  • This wall functions as a partition that partitions the heat exchanger and the gas exchanger supplied to the heat exchanger and the gas exchanger, respectively.
  • An object of the present invention is to provide an artificial lung capable of reliably partitioning a gas exchange part and a heat exchange part while maintaining the gas tightness of the gas exchange part and the liquid tightness of the heat exchange part. is there.
  • a housing into which blood flows A gas exchange part that is housed in the housing and exchanges gas with respect to the blood flowing into the housing; A heat exchange part that is housed in the housing adjacent to the gas exchange part and adjusts the temperature of the blood;
  • An artificial lung having a partition part interposed between the gas exchange part and the heat exchange part and having an elastic part at least at a part facing the gas exchange part and the heat exchange part.
  • the partition portion includes a protruding portion that is formed to protrude toward the inside of the housing and a sheet material that covers the protruding portion, and the sheet material functions as the elastic portion.
  • the gas exchange unit has a gas inlet through which gas flows in, and a gas outlet through which gas flows in via the gas inlet
  • the heat exchanging unit includes a heat medium inlet through which a heat medium flows in, and a heat medium outlet through which the heat medium flowing in through the heat medium inlet flows out
  • the partition part includes a first partition part located between the gas inlet and the heat medium inlet, and a second partition part located between the gas outlet and the heat medium outlet.
  • the gas exchange part has a substantially cylindrical shape as a whole,
  • the heat exchange part is substantially cylindrical in overall shape, and is disposed concentrically inside the gas exchange part,
  • the artificial lung according to any one of (1) to (8), wherein the partition portion is disposed concentrically between the gas exchange portion and the heat exchange portion.
  • each of the gas exchange unit and the heat exchange unit includes a hollow fiber membrane layer in which a plurality of hollow fiber membranes are integrated. Artificial lung.
  • the partition part that partitions the gas exchange part and the heat exchange part is provided with the elastic part at the part facing the gas exchange part and the heat exchange part.
  • This elastic part has a buffer function. Therefore, for example, it is possible to prevent separation of the partition portion and the gas exchange portion regardless of the pressure of the supplied gas, and thus it is possible to reliably maintain the gas tightness of the gas exchange portion. In addition, for example, it is possible to prevent separation of the partition portion and the heat exchange portion regardless of the pressure of the supplied heat medium, and thus it is possible to reliably maintain the liquid tightness of the heat exchange portion. it can.
  • gas tightness of the gas exchange part and the liquid tightness of the heat exchange part are maintained in this way, it is possible to prevent the heat medium from flowing into the gas exchange part and the gas from flowing into the heat exchange part.
  • the gas exchange part and the heat exchange part can be reliably partitioned.
  • FIG. 1 is a plan view showing a first embodiment of the oxygenator of the present invention.
  • FIG. 2 is a view of the oxygenator shown in FIG. 1 as viewed from the direction of arrow A.
  • 3 is a cross-sectional view taken along line BB in FIG.
  • FIG. 4 is a view as seen from the direction of arrow C in FIG.
  • FIG. 5 is a sectional view taken along line DD in FIG.
  • FIG. 6 is an enlarged detailed view of the area [A] surrounded by the alternate long and short dash line in FIG.
  • FIG. 7 is a view for sequentially explaining a process of manufacturing the elastic portion in FIG. 6.
  • FIG. 8 is a diagram for sequentially explaining the process of manufacturing the elastic portion in FIG. 6.
  • FIG. 9 is a diagram for sequentially explaining the process of manufacturing the elastic part included in the artificial lung according to the second embodiment.
  • Drawing 10 is a figure for explaining the process in which the elastic part with which the artificial lung of a 2nd embodiment is provided is manufactured in
  • FIG. 1 is a plan view showing a first embodiment of the oxygenator of the present invention
  • FIG. 2 is a diagram of the oxygenator shown in FIG. 1 as viewed from the direction of arrow A
  • FIG. 3 is a line BB in FIG. 4 is a cross-sectional view taken along the direction of arrow C in FIG. 2
  • FIG. 5 is a cross-sectional view taken along the line DD in FIG. 1
  • FIG. 6 is a region surrounded by a dashed line in FIG.
  • FIG. 7 and FIG. 8 are diagrams for sequentially explaining the process of manufacturing the elastic portion in FIG.
  • the left side is referred to as “left” or “left”, and the right side is referred to as “right” or “right”.
  • 1 to 5 the inside of the oxygenator will be described as “blood inflow side” or “upstream side”, and the outside will be described as “blood outflow side” or “downstream side”.
  • the artificial lung 10 is provided on the inner side, and performs heat exchange with the blood B, that is, a heat exchange unit 10B that adjusts the temperature of the blood B, and an outer peripheral side of the heat exchange unit 10B.
  • the oxygenator 10 includes a housing 2A and an inner structure 11 that is housed in the housing 2A and has an oxygenator 10A and a heat exchanger 10B.
  • the housing 2A includes a cylindrical housing body 21A, a dish-shaped first lid 22A that seals the left end opening of the cylindrical housing body 21A, and a dish-shaped first lid that seals the right end opening of the cylindrical housing body 21A. 2 lids 23A.
  • the cylindrical housing body 21A, the first lid body 22A, and the second lid body 23A are made of a resin material.
  • the first lid body 22A and the second lid body 23A are fixed to the cylindrical housing body 21A by a method such as fusion or bonding with an adhesive.
  • a tubular blood outlet port 28 is formed on the outer peripheral portion of the cylindrical housing body 21A.
  • the blood outflow port 28 protrudes in a substantially tangential direction of the outer peripheral surface of the cylindrical housing body 21A (see FIG. 5).
  • a tubular blood inflow port 201 and a gas outflow port 27 are formed to protrude from the first lid 22A.
  • the blood inflow port 201 is formed on the end surface of the first lid 22A so that the central axis thereof is eccentric with respect to the center of the first lid 22A.
  • the gas outflow port 27 is formed on the outer peripheral portion of the first lid 22A so that the central axis thereof intersects the center of the first lid 22A (see FIG. 2).
  • the gas inflow port 26 is formed at the edge of the end surface of the second lid 23A.
  • the heat medium inflow port 202 and the heat medium outflow port 203 are each formed at substantially the center of the end surface of the second lid 23A.
  • the center lines of the heat medium inflow port 202 and the heat medium outflow port 203 are slightly inclined with respect to the center line of the second lid body 23A.
  • the entire shape of the housing 2A does not necessarily have a complete columnar shape, and may be, for example, a partially missing shape or a shape with a deformed portion added.
  • a cylindrical lung 10 ⁇ / b> A is housed inside the housing 2 ⁇ / b> A along the inner peripheral surface thereof.
  • the artificial lung portion 10A includes a cylindrical hollow fiber membrane layer 3A and a filter member 41A provided on the outer peripheral side (blood outflow portion side) of the hollow fiber membrane layer 3A.
  • the hollow fiber membrane layer 3A and the filter member 41A are arranged in the order of the hollow fiber membrane layer 3A and the filter member 41A from the blood inflow side.
  • the hollow fiber membrane layer 3A is composed of a large number of hollow fiber membranes 31A having a gas exchange function, and these hollow fiber membranes 31A are integrated.
  • the hollow fiber membrane 31A is composed of a tubular member having both ends opened.
  • One end (right end) of the tubular hollow fiber membrane 31A is a gas inlet 321A into which the gas G from the gas inlet port 26 flows.
  • the other end (left end) of the hollow fiber membrane 31A is a gas outlet 322A through which the gas G in the hollow fiber membrane 31A flows out to the gas outlet port 27.
  • the lumen of the tube of the hollow fiber membrane 31A constitutes a flow path 32A (gas flow path) through which the gas G flows.
  • each hollow fiber membrane 31A is preferably a polyolefin-based resin, and more preferably polypropylene. Further, the hollow fiber membrane 31A is more preferably a porous body in which micropores are formed in the wall portion by a stretching method or a solid-liquid phase separation method, that is, a porous body. Thereby, gas exchange is reliably performed between blood B and hollow fiber membrane 31A.
  • each hollow fiber membrane 31A that is, the left end portion (one end portion) and the right end portion (the other end portion) are fixed to the inner surface of the cylindrical housing body 21A by partition walls 8 and 9, respectively.
  • the partition walls 8 and 9 are made of, for example, a potting material such as polyurethane or silicone rubber, an adhesive, or the like.
  • each hollow fiber membrane 31A between the partition walls 8 and 9 in the housing 2A that is, in the gap between the hollow fiber membranes 31A, the blood B is directed from the inside to the outside of the oxygenator 10 shown in FIG. A flowing blood channel 33 is formed.
  • a blood inflow port A blood inflow side space 24A communicating with 201 is formed (see FIGS. 3 and 5).
  • the blood inflow side space 24A includes a first cylindrical member 241 having a cylindrical shape, and a plate piece 242 that is disposed inside the first cylindrical member 241 and is opposed to a part of the inner peripheral portion thereof. It is a defined space.
  • the blood B that has flowed into the blood inflow side space 24 ⁇ / b> A can flow down over the entire blood flow path 33 through the plurality of side holes 243 formed in the first cylindrical member 241.
  • a cylindrical gap is formed between the outer peripheral surface of the filter member 41A and the inner peripheral surface of the cylindrical housing body 21A, and this gap forms a blood outflow side space 25A.
  • the blood outflow portion is constituted by the blood outflow side space 25A and the blood outflow port 28 communicating with the blood outflow side space 25A. Since the blood outflow part has the blood outflow side space 25A, a space where the blood B that has passed through the filter member 41A flows toward the blood outflow port 28 is secured, and the blood B can be discharged smoothly.
  • the hollow fiber membrane layer 3A, the filter member 41A, and the blood channel 33 are present between the blood inflow side space 24A and the blood outflow side space 25A.
  • the filter member 41A has a function of capturing bubbles present in the blood B flowing through the blood flow path 33.
  • the filter member 41A is composed of a substantially rectangular sheet-like member (hereinafter also simply referred to as “sheet”), and is formed by winding the sheet into a cylindrical shape.
  • the filter member 41A is fixed to the housing 2A by fixing both ends thereof with partition walls 8 and 9, respectively (see FIG. 3). Further, the filter member 41A has an inner peripheral surface provided in contact with a surface on the downstream side (blood outflow portion side) of the hollow fiber membrane layer 3A and covers almost the entire surface.
  • Such a filter member 41A can capture air bubbles even if there are air bubbles in the blood B flowing through the blood flow path 33.
  • the trapped bubbles are pushed into the hollow fiber membranes 31 ⁇ / b> A near the filter member 41 ⁇ / b> A by the blood flow and are removed from the blood flow path 33 as a result.
  • an annular rib 291 is formed to protrude inside the first lid 22 ⁇ / b> A.
  • a first chamber 221a is defined by the first lid 22A, the rib 291 and the partition wall 8.
  • the first chamber 221a is a gas outflow chamber from which the gas G flows out.
  • the gas outlet 322A of each hollow fiber membrane 31A is open to and communicates with the first chamber 221a.
  • annular rib 292 is also formed to protrude inside the second lid 23A.
  • a second chamber 231 a is defined by the second lid body 23 ⁇ / b> A, the rib 292, and the partition wall 9.
  • the second chamber 231a is a gas inflow chamber into which the gas G flows.
  • the gas inlet 321A of each hollow fiber membrane 31A is open to and communicated with the second chamber 231a.
  • the heat exchange unit 10B is installed inside the artificial lung unit 10A.
  • the heat exchange part 10B has a hollow fiber membrane layer 3B.
  • This hollow fiber membrane layer 3B is the same as the hollow fiber membrane layer 3A except that it has a function of performing heat exchange instead of gas exchange. That is, the hollow fiber membrane layer 3B having a function of performing heat exchange is also composed of a large number of hollow fiber membranes 31B, like the hollow fiber membrane layer 3A of the artificial lung portion 10A, and these hollow fiber membranes 31B are integrated.
  • the gap between the hollow fiber membranes 31 ⁇ / b> B becomes the blood flow path 33.
  • the hollow fiber membrane layer 3B will be described mainly with respect to the differences from the hollow fiber membrane layer 3A described above, and description of the same matters will be omitted.
  • the hollow fiber membrane 31B is configured by a tubular member having both ends opened.
  • One end (right end) of the tubular hollow fiber membrane 31B is a heat medium inlet 321B into which the heat medium H from the heat medium inflow port 202 flows.
  • the other end (left end) of the hollow fiber membrane 31B is a heat medium outlet 322B through which the heat medium H in the hollow fiber membrane 31B flows out to the heat medium outlet port 203.
  • the lumen of the tube of the hollow fiber membrane 31B constitutes a flow path 32B (heat medium flow path) through which the heat medium H flows.
  • both ends of the hollow fiber membrane layer 3B are formed on the inner surface of the cylindrical housing main body 21A by the partition walls 8 and 9, respectively. It is fixed against. Furthermore, the hollow fiber membrane layer 3 ⁇ / b> B has an inner peripheral portion engaged with an uneven portion 244 formed on the outer peripheral portion of the first cylindrical member 241. By this engagement and fixing by the partition walls 8 and 9, the hollow fiber membrane layer 3B is securely fixed to the cylindrical housing main body 21A, and thus the positional displacement of the hollow fiber membrane layer 3B occurs during use of the artificial lung 10. Can be reliably prevented.
  • a second cylindrical member 245 disposed concentrically with the first cylindrical member 241 is disposed inside the first cylindrical member 241.
  • the heat medium H for example, water
  • the heat medium inflow port 202 flows through each hollow fiber membrane 31 ⁇ / b> B of the hollow fiber membrane layer 3 ⁇ / b> B on the outer peripheral side of the first cylindrical member 241. It passes through the path 32B (heat medium flow path) and the inside of the second cylindrical member 245 in this order, and is discharged from the heat medium outflow port 203.
  • heat exchange heat exchange (heating or cooling) is performed with the blood B in contact with the hollow fiber membrane 31B.
  • the heat exchange unit 10B is installed inside the oxygenator 10A in this way, the oxygenator 10A and the heat exchanger 10B can be efficiently stored in one housing 2A, and dead space Therefore, efficient gas exchange can be performed with the small artificial lung 10.
  • the oxygenator 10A and the heat exchanger 10B are in close proximity to each other, and the blood B that has undergone heat exchange in the heat exchanger 10B is prevented from radiating or absorbing heat as much as possible to the oxygenator 10A. It can flow in quickly.
  • the rib 291 is formed to protrude inside the first lid 22A.
  • a rib 292 protrudes from the inside of the second lid 23A.
  • the rib 291 and the rib 292 are provided so that it may mutually oppose, as shown in FIG.
  • a part of the rib 292 is interposed between the hollow fiber membrane layer 3A and the hollow fiber membrane layer 3B.
  • the rib 292 partitions the gas inlet 321A of each hollow fiber membrane 31A from the heat medium inlet 321B of each hollow fiber membrane 31B.
  • the gas G which flowed in from the gas inflow port 26 surely flows into each hollow fiber membrane 31A via the gas inflow port 321A.
  • the heat medium H flowing in from the heat medium inflow port 202 surely flows into each hollow fiber membrane 31B via the heat medium inlet 321B.
  • the rib 292 functions as a partition (first partition) that partitions the gas inlet 321A and the heat medium inlet 321B.
  • a part of the rib 291 is interposed between the hollow fiber membrane layer 3A and the hollow fiber membrane layer 3B.
  • the ribs 291 separate the gas outlet 322A of each hollow fiber membrane 31A from the heat medium outlet 322B of each hollow fiber membrane 31B.
  • the gas G in each hollow fiber membrane 31A flows out reliably to the gas outflow port 27 through the gas outflow port 322A.
  • the heat medium H in each hollow fiber membrane 31B surely flows out to the heat medium outflow port 203 through the heat medium outlet 322B.
  • the rib 291 functions as a partition (second partition) that partitions the gas outlet 322A and the heat medium outlet 322B.
  • the heat medium H flows into the oxygenator 10A or the gas G flows into the heat exchanger 10B. Can be prevented.
  • the rib 291 and the rib 292 have the same configuration, the rib 291 will be described below as a representative, and the description of the rib 292 will be omitted.
  • the rib 291 has an annular projecting portion 5 that is integrally projected and formed inside the first lid 22 ⁇ / b> A, and a sheet material 6 that covers the top of the projecting portion 5.
  • the projecting portion 5 is configured by a constant thickness portion 52 whose cross-sectional shape is plate-like and whose thickness is constant, and a gradually decreasing portion 51 whose thickness gradually decreases in the direction in which the rib 292 is positioned. .
  • the protruding portion 5 has the gradually decreasing portion 51, when the protruding portion 5 is inserted into the opening 61 of the sheet material 6 in the manufacturing process of the artificial lung 10, the gradually decreasing portion 51 can be easily inserted into the opening 61. Therefore, the oxygenator 10 can be easily assembled, and as a result, the productivity of the oxygenator 10 is improved.
  • the gradually decreasing portion 51 is covered with a sheet material 6 having an annular shape as a whole over its entire circumference.
  • the sheet material 6 is inserted between the hollow fiber membrane layer 3 ⁇ / b> A and the hollow fiber membrane layer 3 ⁇ / b> B together with the gradual decrease portion 51 in a state of covering the gradual decrease portion 51, thereby constituting the insertion portion 50.
  • the insertion portion 50 is located in the partition wall 8. Thereby, it is possible to prevent the blood B flowing down the blood flow path 33 from being inhibited by the insertion portion 50.
  • the sheet material 6 arranged in this way has a first sheet portion 61a sandwiched between the gradually decreasing portion 51 and the hollow fiber membrane layer 3A.
  • the first sheet portion 61a functions as an elastic portion, that is, a buffer portion.
  • the pressure gas pressure
  • the hollow fiber membrane layer 3A is pressed against the first sheet portion 61a by the gas pressure, and the adhesion between the hollow fiber membrane layer 3A and the first sheet portion 61a is improved. Thereby, the airtightness between the rib 291 and the hollow fiber membrane layer 3A can be improved.
  • the sheet material 6 has a second sheet portion 61b sandwiched between the gradually decreasing portion 51 and the hollow fiber membrane layer 3B. Similar to the first sheet portion 61a, the second sheet portion 61b also functions as an elastic portion, that is, a buffer portion. Thereby, for example, even if the pressure (hydraulic pressure) generated when the heat medium H passes through the hollow fiber membrane layer 3 ⁇ / b> B acts toward the gradually decreasing portion 51, the pressure can be relaxed. As a result, it is possible to prevent the gradually decreasing portion 51 from being damaged by the hydraulic pressure.
  • the sheet material 6 is made of an elastic material, so that it functions as a buffer portion and is gradually reduced as compared with a seal structure that is fixed by adhesion or welding. It is possible to prevent 51 (sheet material 6) from being damaged such as cracks.
  • the hollow fiber membrane layer 3B is pressed against the second sheet portion 61b by the hydraulic pressure, and the adhesion between the hollow fiber membrane layer 3B and the second sheet portion 61b is improved. Thereby, the liquid-tightness between the rib 291 and the hollow fiber membrane layer 3B can be improved.
  • the constituent material of the sheet material 6 examples include elastic materials such as various thermoplastic elastomers (for example, silicone rubber, polyurethane, etc.).
  • elastic materials such as various thermoplastic elastomers (for example, silicone rubber, polyurethane, etc.).
  • the sheet material 6 is formed of such an elastic material, blocking occurs between the sheet material 6 and the partition wall 8 and the mutual adhesion can be improved. Moreover, blocking also arises between the sheet material 6 and the gradual reduction part 51, and mutual adhesiveness can be improved. Due to the synergistic effect of the adhesiveness due to such blocking and the adhesiveness due to gas pressure or hydraulic pressure as described above, the airtightness between the rib 291 and the hollow fiber membrane layer 3A, the rib 291 and the hollow fiber membrane layer 3B, The liquid tightness can be improved. This further prevents the heat medium H from flowing into the oxygenator 10A and the gas G from flowing into the heat exchanger 10B.
  • Such a sheet material 6 is manufactured as follows.
  • an annular base material 65 as shown in FIG. 7 is prepared.
  • the base material 65 is bent so that the back surface side of the second sheet portion 61b overlaps the back surface side of the first sheet portion 61a. In this way, a sheet material 6 as shown in FIG. 8 can be obtained.
  • the blood B flowing in from the blood inflow port 201 sequentially passes through the blood inflow side space 24A and the side hole 243 and flows into the heat exchange unit 10B.
  • the blood B flows through the blood flow path 33 in the downstream direction, and contacts the surface of each hollow fiber membrane 31B to exchange heat (warming or cooling).
  • the blood B thus heat-exchanged flows into the artificial lung 10A.
  • the blood B flows through the blood channel 33 in the downstream direction.
  • the gas G gas containing oxygen
  • the gas inflow port 26 is distributed from the second chamber 231a to the flow paths 32A of the hollow fiber membranes 31A, and flows through the flow paths 32A.
  • the gas is accumulated in the room 221a and discharged from the gas outflow port 27.
  • the blood B flowing through the blood flow path 33 contacts the surface of each hollow fiber membrane 31A, and gas exchange (oxygenation, decarbonation gas) is performed with the gas G flowing through the flow path 32A.
  • the gas G flowing from the gas inflow port 26 is prevented from flowing into the heat exchange unit 10B by the rib 292. Further, the gas G flowing out from the flow path 32A to the gas outflow port 27 is prevented from flowing into the heat exchange unit 10B by the rib 291.
  • the blood B from which gas has been exchanged and bubbles have been removed flows out from the blood outflow port 28.
  • the hollow fiber membrane 31B is wound around the outer side of the first cylindrical member 241 in which the second cylindrical member 245 is disposed inside to form the hollow fiber membrane layer 3B.
  • the sheet material 6 is attached to the outer periphery of the left end side and the right end side of the hollow fiber membrane layer 3B, respectively.
  • the hollow fiber membrane layer 3A is provided by winding the hollow fiber membrane 31A around the outer periphery of the hollow fiber membrane layer 3B provided with the sheet material 6 so as to cover the sheet material 6 together.
  • the filter member 41A is wound around the outer peripheral surface of the hollow fiber membrane layer 3B so as to cover almost the entire outer peripheral surface of the hollow fiber membrane layer 3A. Thereby, the inner structure 11 is obtained.
  • cylindrical housing body 21 ⁇ / b> A is mounted on the outer peripheral surface side of the inner structure 11.
  • both end portions of the inner structure 11 are cut so that both end portions of the hollow fiber membranes 31A and 31B, the right end portion of the right sheet material 6, and the left end portion of the left sheet material 6 are opened. . Note that the cut portion is discarded.
  • the first lid body 22A and the second lid body 23A are mounted on the cylindrical housing body 21A in which the inner structure 11 is accommodated.
  • the first lid 22A is attached to the cylindrical housing main body 21A so that the protruding portion 5 on the first lid 22A side is inserted into the opening 61 of the sheet material 6 on the same side.
  • the second lid body 23A is attached to the cylindrical housing body 21A so that the protruding portion 5 on the second lid body 23A side is inserted into the opening 61 of the sheet material 6 on the same side.
  • the protrusion 5 has the gradual reduction part 51 as mentioned above. For this reason, the protrusion part 5 can be more easily and reliably inserted into the sheet material 6.
  • the artificial lung 10 as shown in FIG. 3 can be obtained through the above steps.
  • FIG. 9 and FIG. 10 are diagrams for sequentially explaining the process of manufacturing the elastic part included in the oxygenator of the second embodiment.
  • This embodiment is the same as the first embodiment except that the manufacturing method of the elastic portion is different.
  • a groove 63 is formed in the bent portion 62 of the base material 65 using, for example, a cutter.
  • the groove 63 is formed over the entire circumference of the outer peripheral surface of the base material 65.
  • channel 63 is not limited to using a cutter, For example, a laser beam etc. can also be used.
  • the base material 65 is folded so that the groove 63 is a mountain fold mountain side and the back surface side of the second sheet portion 61 b overlaps the back surface side of the first sheet portion 61 a. Thereby, the sheet material 6 as shown in FIG. 10 is obtained.
  • the base material 65 can be easily bent and the bent state can be easily maintained. Further, the first sheet portion 61a and the second sheet portion 61b can be easily bent so that the widths thereof are approximately the same.
  • the oxygenator of the present invention is not limited to this, and each part constituting the oxygenator can be any one that can exhibit the same function. It can be replaced with that of the configuration. Moreover, the arbitrary components may be added to the oxygenator of this invention.
  • each hollow fiber membrane constituting the hollow fiber membrane layer of the artificial lung part and each hollow fiber membrane constituting the hollow fiber membrane layer of the heat exchange part were the same in the above embodiment,
  • one (the former) hollow fiber membrane may be thinner than the other (the latter) hollow fiber membrane, or both hollow fiber membranes may be made of different materials.
  • the partition part that partitions the oxygenator part and the heat exchange part is composed of the projecting part and the elastic part in each of the above embodiments, but is not limited to this.
  • the entire partition part is an elastic part. It may be configured.
  • the sheet material is manufactured using a ring-shaped base material in advance, but is not limited thereto, for example, a belt shape is formed in advance, and ends thereof are joined, that is, You may manufacture using the base material which bonded together and made the annular
  • the groove formed in the base material when the sheet material is manufactured was formed in the center portion in the width direction of the base material in the second embodiment, but is not limited thereto, for example, It may be formed at a position deviating from the central portion.
  • seat material differs in the 1st sheet
  • Such a configuration is preferable because the size can be easily changed when it is desired to have a size relationship between the width of the first sheet portion and the width of the second sheet portion.
  • the sheet material is obtained by bending an annular base material in advance.
  • the sheet material is not limited to this.
  • the sheet material is formed in the central portion in the thickness direction of the annular base material in advance.
  • a slit may be formed along the circumferential direction. And a protrusion part can be inserted in this slit.
  • the oxygenator of the present invention includes a housing into which blood flows, a gas exchange part that is housed in the housing and performs gas exchange with respect to the blood that has flowed into the housing, and is adjacent to the gas exchange part in the housing. And an elastic part at least at a portion facing the gas exchange part and the heat exchange part, inserted between the gas exchange part and the heat exchange part. And a partition part provided. Therefore, it is possible to reliably partition the gas exchange unit and the heat exchange unit while maintaining the gas tightness of the gas exchange unit and the liquid tightness of the heat exchange unit. Therefore, the oxygenator of the present invention has industrial applicability.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
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  • Hematology (AREA)
  • Animal Behavior & Ethology (AREA)
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  • Cardiology (AREA)
  • Emergency Medicine (AREA)
  • Urology & Nephrology (AREA)
  • External Artificial Organs (AREA)

Abstract

L'invention concerne un poumon artificiel (10) qui comporte : une enveloppe dans laquelle s'écoule le sang ; une section d'échange de gaz stockée à l'intérieur de l'enveloppe et ayant une couche de membrane de fibre creuse (3A) pour effectuer un échange de gaz dans le sang s'écoulant dans l'enveloppe ; une section d'échange de chaleur stockée de façon adjacente à la section d'échange de gaz à l'intérieur de l'enveloppe et ayant une couche de membrane de fibre creuse (3B) pour régler la température du sang ; et une nervure (291) introduite entre la section d'échange de gaz et la section d'échange de chaleur pour servir de cloison afin de les séparer. Ladite cloison comprend une section saillante (5), qui se présente sous la forme d'une saillie partant de l'enveloppe, et un matériau en feuille (6) pour recouvrir le sommet de la section saillante (5).
PCT/JP2013/069272 2013-07-16 2013-07-16 Poumon artificiel WO2015008327A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
PCT/JP2013/069272 WO2015008327A1 (fr) 2013-07-16 2013-07-16 Poumon artificiel

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/JP2013/069272 WO2015008327A1 (fr) 2013-07-16 2013-07-16 Poumon artificiel

Publications (1)

Publication Number Publication Date
WO2015008327A1 true WO2015008327A1 (fr) 2015-01-22

Family

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PCT/JP2013/069272 WO2015008327A1 (fr) 2013-07-16 2013-07-16 Poumon artificiel

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Country Link
WO (1) WO2015008327A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB2582239A (en) * 2018-11-06 2020-09-23 Spectrum Medical Ltd Oxygenation system
JP2020536637A (ja) * 2017-10-10 2020-12-17 ソリン・グループ・イタリア・ソシエタ・ア・レスポンサビリタ・リミタータＳｏｒｉｎ Ｇｒｏｕｐ Ｉｔａｌｉａ Ｓ．ｒ．ｌ． 熱交換器（ｈｅｘ）内の向流血液／水流路を備えた血液処理ユニット（ｂｐｕ）

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012524626A (ja) * 2009-04-23 2012-10-18 メドトロニック，インコーポレイテッド 熱交換器を有する径方向設計人工肺
JP2012239885A (ja) * 2011-05-17 2012-12-10 Sorin Group Italia Srl 血液クロスフローを有する血液処理ユニット

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2012524626A (ja) * 2009-04-23 2012-10-18 メドトロニック，インコーポレイテッド 熱交換器を有する径方向設計人工肺
JP2012239885A (ja) * 2011-05-17 2012-12-10 Sorin Group Italia Srl 血液クロスフローを有する血液処理ユニット

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2020536637A (ja) * 2017-10-10 2020-12-17 ソリン・グループ・イタリア・ソシエタ・ア・レスポンサビリタ・リミタータＳｏｒｉｎ Ｇｒｏｕｐ Ｉｔａｌｉａ Ｓ．ｒ．ｌ． 熱交換器（ｈｅｘ）内の向流血液／水流路を備えた血液処理ユニット（ｂｐｕ）
US11918719B2 (en) 2017-10-10 2024-03-05 Sorin Group Italia S.R.L. Blood processing unit (BPU) with countercurrent blood/water flow paths in the heat exchanger (HEX)
GB2582239A (en) * 2018-11-06 2020-09-23 Spectrum Medical Ltd Oxygenation system
GB2582239B (en) * 2018-11-06 2022-09-07 Spectrum Medical Ltd Oxygenation system

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