JP2007215992A - Oxygenator - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an oxygenator which helps avoid bubbles in the blood from being discharged through a blood outlet port. <P>SOLUTION: The oxygenator 10 includes a housing 2A, a hollow fiber membrane bundle 3A in the housing 2A and formed by a multiplicity of hollow fiber membranes serving for gas exchange, gas-inlet and gas-outlet ports provided on the upstream side and downstream side of gas passages, respectively, with the lumen of each hollow fiber membrane as the gas passage, a blood-inlet and blood-outlet ports provided on the upstream side and downstream side of a blood passage, respectively, with the outer side of each hollow fiber membrane as the blood passage, and a filter member 41A provided on the blood outlet port side of the hollow fiber membrane bundle 3A and serves to catch bubbles in blood. The blood outlet port is provided with a blood outlet port 28 projecting from a housing 2A, and a passage enlargement part 281 having an increased cross-sectional area of the passage is provided in the vicinity of the end on the side of the housing 2A of the blood outlet port 28. The blood passing through the filter member 41A reaches the blood outlet port 28 by being decelerated in the passage enlargement part 281. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to an artificial lung.

  Conventionally, as an artificial lung, one having a structure in which gas exchange is performed using a large number of hollow fiber membranes is known (see, for example, Patent Document 1).

  The artificial lung has a housing, a bundle of hollow fiber membranes housed in the housing, a blood inlet and a blood outlet, a gas inlet and a gas outlet, and blood and the blood through each hollow fiber membrane. Gas exchange with the gas, that is, oxygenation and decarbonation gas are performed.

  By the way, in the artificial lung having such a configuration, air bubbles may be mixed in the blood flowing in from the blood inlet, but in this case, the air bubbles are preferably removed by the hollow fiber membrane bundle.

  However, since the hollow fiber membrane bundle is designed so that gas exchange can be performed efficiently and is not originally intended to remove bubbles, the hollow fiber membrane bundle does not sufficiently remove bubbles. In addition, there is a problem that the blood flows out from the blood outlet while being mixed with bubbles and is transferred downstream of the oxygenator. Therefore, an arterial filter is provided in the blood circuit (arterial line) between the oxygenator and the patient for the purpose of removing bubbles.

JP 11-47268 A

  An object of the present invention is to provide an artificial lung capable of preventing bubbles in blood from flowing out from a blood outflow portion.

Such an object is achieved by the present inventions (1) to (7) below.
(1) a housing;
A hollow fiber membrane bundle in which a plurality of hollow fiber membranes housed in the housing and having a gas exchange function are integrated,
Using the lumen of each hollow fiber membrane as a gas flow path, a gas inflow part and a gas outflow part respectively provided on the upstream side and the downstream side of the gas flow path,
With the outside of each hollow fiber membrane as a blood flow path, a blood inflow portion and a blood outflow portion provided on the upstream side and the downstream side of the blood flow path,
An artificial lung having air bubble removing means provided on the blood outflow portion side of the hollow fiber membrane bundle and provided with a filter member having a function of capturing air bubbles in blood,
The blood outflow portion has a tubular blood outlet that protrudes from the housing, and has a flow passage enlargement portion that increases the cross-sectional area of the flow passage in the vicinity of the housing side end of the blood outlet. The artificial lung, wherein the blood that has passed through the filter member is configured to decelerate the flow velocity at the flow channel enlargement portion and reach the blood outlet.

  (2) The artificial lung according to (1), wherein the filter member has a mesh shape.

  (3) The blood outflow portion has a blood outflow side opening formed between an inner surface of the housing and the filter member, and the blood outflow side opening and the blood outflow port are expanded in the flow path. The oxygenator as described in said (1) or (2) which is connected via the part.

  (4) The oxygenator as described in (3) above, which has a portion where the gap distance between the inner surface of the housing and the filter member increases continuously or stepwise on the downstream side of the blood outflow side opening.

  (5) The artificial lung according to any one of (1) to (4), wherein the flow path enlargement section includes an upstream first expansion section and a second expansion section that follows the first expansion section.

  (6) The artificial lung according to (5), wherein the first enlarged portion includes a groove formed over substantially the entire length in the longitudinal direction of the housing.

  (7) The artificial passage according to any one of (1) to (4), wherein the flow path enlarged portion has a first enlarged portion constituted by a groove formed over substantially the entire length in the longitudinal direction of the housing. lung.

  It is preferable that a gap through which blood that has passed through the filter member flows is formed between the filter member and the housing.

  It is preferable that the gap has a portion where the gap distance increases toward the flow path enlarged portion.

Preferably, the housing has a cylindrical body part, and the blood outlet port protrudes in a tangential direction of the circumference of the body part.
It is preferable that the housing has a cylindrical body part, and the flow path expanding part is formed in a part of the inner peripheral surface of the body part in the circumferential direction.

  The bubble removing means preferably further includes an exhaust hollow fiber membrane layer in which a large number of exhaust hollow fiber membranes having a function of permeating and discharging the gas constituting the bubbles are integrated.

  The exhaust hollow fiber membrane layer is preferably located between the hollow fiber membrane bundle and the filter member.

  It is preferable that the filter member is provided in contact with the surface of the hollow fiber membrane bundle or the exhaust hollow fiber membrane layer on the blood outflow portion side and covers almost the entire surface.

  The hollow fiber membranes constituting the hollow fiber membrane bundle and the hollow fiber membranes constituting the exhaust hollow fiber membrane layer are different in at least one of their constituent materials, characteristics, and arrangement conditions. preferable.

The filter member is preferably hydrophilic.
It is preferable that the filter member is composed of one sheet or two or more sheets.

The opening of the filter member is preferably 50 μm or less.
The bubble removing means preferably further comprises an exhaust port for exhausting the gas constituting the bubble out of the housing.

  According to the present invention, the blood that has passed through the filter member has its flow velocity reduced at the flow path enlarged portion, and thus, the bubbles trapped by the filter member are prevented from riding on the bloodstream and reaching the blood outlet. That is, it is possible to prevent bubbles in the blood from flowing out from the blood outflow portion.

Hereinafter, an artificial lung of the present invention will be described in detail based on preferred embodiments shown in the accompanying drawings.
<First Embodiment>
1 is a perspective view showing a first embodiment of the oxygenator according to the present invention, FIG. 2 is a cross-sectional view taken along the line AA in FIG. 1 (cross-sectional side view), and FIG. 3 is the oxygenator shown in FIG. FIG. 4 is an enlarged cross-sectional view of the lower right portion (fixing portion of the hollow fiber membrane bundle, filter member, and exhaust hollow fiber membrane layer) in FIG. 2. 1 and 2, the upper side is “upper” or “upper”, the lower side is “lower” or “lower”, the left side is “blood inflow side” or “upstream side”, and the right side is “blood outflow side”. Or, it will be described as “downstream”.

  The oxygenator 1 of the illustrated embodiment is an oxygenator with a heat exchanger that includes an oxygenator 1A that performs gas exchange with blood and a heat exchanger (heat exchanger) 1B that performs heat exchange with blood. For example, it is installed in a blood extracorporeal circuit.

  The oxygenator 1 includes a housing 2 on the oxygenator portion 1A side and a heat exchanger housing 5 on the heat exchanger 1B side, which are connected (joined) or integrated. First, the oxygenator 1A will be described.

  The housing 2 has a rectangular tube shape, that is, a cylindrical housing main body (hereinafter referred to as a “square cylindrical housing main body”) 21 having a quadrangular (rectangular or square) cross section, and an upper end opening of the rectangular cylindrical housing main body 21. It consists of a dish-shaped first header (upper lid) 22 to be sealed and a dish-shaped second header (lower lid) 23 that seals the lower end opening of the rectangular tubular housing body 21. .

  The rectangular tubular housing body 21, the first header 22 and the second header 23 are, for example, polyolefins such as polyethylene and polypropylene, ester resins (for example, polyesters such as polyethylene terephthalate and polybutylene terephthalate), and styrene. Resin (for example, polystyrene, MS resin, MBS resin), resin materials such as polycarbonate, various ceramic materials, metal materials, and the like are used. The first header 22 and the second header 23 are fixed to the rectangular cylindrical housing body 21 in a liquid-tight manner by a method such as fusion or bonding with an adhesive.

  A tubular blood outflow port (blood outflow port) 28 protrudes from the lower part of the rectangular tubular housing body 21 on the blood outflow side. On the side of the rectangular tube-shaped housing body 21 (housing 2) of the blood outflow port 28, that is, in the vicinity of the upstream end portion, a box-shaped flow passage expanding portion 281 is provided. The lumen of the blood outflow port 28 and the lumen of the flow path expanding portion 281 are in communication, and constitute a flow path through which blood that has passed through a filter member 41 described later passes. As shown in FIGS. 2 and 3, the flow path expanding portion 281 is a portion where the cross-sectional area of the flow path is increased.

  In the artificial lung 1, when the blood that has passed through the filter member 41 flows into the flow channel expanding portion 281, the flow rate is reduced at a rate that is the reciprocal of the increase rate of the cross-sectional area of the flow channel according to a continuous equation. In the decelerated state, the blood reaches the blood outflow port 28. Here, the “continuity equation” is an equation of the law of conservation of mass in hydrodynamics.

  A tubular gas inflow port 26 protrudes from the upper portion of the first header 22. In addition, a tubular gas outflow port 27 and a tubular exhaust port (exhaust port) 29 are formed to project from the lower portion of the second header 23. The gas inflow port 26 is bent at a substantially right angle in the middle thereof, and the tip portion is directed in a direction parallel to the blood outflow port 28.

  In the present invention, the entire shape of the housing 2 is not necessarily a complete rectangular parallelepiped shape. For example, all or part of the corners may be chamfered or rounded. A shape in which a portion is missing, a shape to which a deformed portion is added, or the like may be used.

  As shown in FIGS. 2 to 4, in the housing 2, a hollow fiber membrane bundle 3 in which a large number of hollow fiber membranes 31 having a gas exchange function are integrated, and a blood outflow port 28 ( The filter member 41 and the exhaust hollow fiber membrane layer 42 as the bubble removing means 4 provided on the blood outflow portion side are accommodated. These layers and members are arranged in the order of the hollow fiber membrane bundle 3, the exhaust hollow fiber membrane layer 42, and the filter member 41 from the blood inflow side.

  As shown in FIG. 4, most of the hollow fiber membranes 31 constituting the hollow fiber membrane bundle 3 are arranged substantially in parallel. In this case, each hollow fiber membrane 31 is arranged such that its longitudinal direction is the vertical direction (vertical direction).

  In addition, the arrangement | positioning pattern, arrangement | positioning direction, etc. of the hollow fiber membrane 31 in the hollow fiber membrane bundle 3 are not limited to what was mentioned above, For example, the structure by which each hollow fiber membrane 31 is arrange | positioned in a horizontal direction, a hollow fiber membrane A configuration in which portions 31 cross each other at an angle (intersection portion), a configuration in which all or a part of the hollow fiber membranes 31 are curved, and a part or all of the hollow fiber membranes 31 are wavy, spiral, spiral The structure etc. which were arrange | positioned at the shape or cyclic | annular form may be sufficient.

  Both end portions (upper end portion and lower end portion) of each hollow fiber membrane 31 are fixed to the inner surface of the rectangular tubular housing body 21 by partition walls 8 and 9, respectively (see FIG. 2). The partition walls 8 and 9 are made of a potting material such as polyurethane and silicone rubber.

  The hollow fiber membrane bundle 3 is fixed (fixed) to the inner surface of the rectangular tubular housing main body 21 by fixing portions 7 at both ends in the width direction (see FIG. 3). The fixing portion 7 is made of the same material (potting material) as the partition walls 8 and 9 or other adhesive.

  A first chamber 221 is defined by the first header 22 and the partition wall 8. The first chamber 221 has a gas inflow chamber 261 on the hollow fiber membrane bundle 3 side and an exhaust hollow by a partition 222 provided at the boundary between the hollow fiber membrane bundle 3 and the exhaust hollow fiber membrane layer 42. It is divided into a small space 223 on the thread membrane layer 42 side. The upper end opening of each hollow fiber membrane 31 opens to and communicates with the gas inflow chamber 261.

  On the other hand, a second chamber 231 is defined by the second header 23 and the partition wall 9. The second chamber 231 is separated from the gas outflow chamber 271 on the hollow fiber membrane bundle 3 side by the partition portion 232 provided at the boundary between the hollow fiber membrane bundle 3 and the exhaust hollow fiber membrane layer 42. It is divided into a small space 233 on the thread membrane layer 42 side. The lower end opening of each hollow fiber membrane 31 opens to and communicates with the gas outflow chamber 271 (see FIG. 4).

  The lumen of each hollow fiber membrane 31 constitutes a gas flow path 32 through which gas flows. The gas inflow port 26 and the gas inflow chamber 261 constitute a gas inflow portion located upstream of the gas flow path 32, and the gas outflow port 27 and the gas outflow chamber 271 constitute a gas located downstream of the gas flow path 32. An outflow section is constructed.

  The hollow fiber membrane bundle 3 is filled in the rectangular tube-shaped housing main body 21 with almost no gap, so that the hollow fiber membrane bundle 3 has a substantially rectangular parallelepiped shape as a whole.

  Each hollow fiber membrane 31 between the partition wall 8 and the partition wall 9 in the housing 2 is exposed, and the outside of each hollow fiber membrane 31 (the same applies to the hollow fiber membrane 421), that is, a gap between the hollow fiber membranes 31. In addition, a blood flow path 33 through which blood flows from the left side to the right side in FIG. 2 is formed.

  The upstream side of the blood flow path 33 (the upstream side of the hollow fiber membrane bundle 3), that is, the connecting portion between the rectangular tubular housing main body 21 and the heat exchanger housing 5, serves as a blood inflow portion in the vertical direction (hollow A band-like or slit-like blood inflow side opening (blood inflow side space) 24 extending in a direction substantially parallel to the arrangement direction of the thread film 31 is formed. The interior of the housing 2 communicates with the interior of the heat exchanger housing 5 through the blood inflow side opening 24. By setting it as such a structure, the blood transfer from the heat exchange part 1B to the oxygenator part 1A can be performed efficiently.

  Is the length (vertical length) of the blood inflow side opening 24 substantially equal to the effective length of each hollow fiber membrane 31 (the length from the lower surface of the partition wall 8 to the upper surface of the partition wall 9) (see FIG. 2)? Or slightly shorter (70% or more of the effective length) is preferable. Thereby, the blood can be efficiently transferred from the heat exchange part 1B to the artificial lung part 1A, and the gas exchange for the blood can be efficiently performed in the blood channel 33.

  Further, at least on the upstream side of the blood flow path 33 (the blood inflow side opening 24 side), the direction of blood flow is a direction substantially orthogonal to the longitudinal direction of each hollow fiber membrane 31. Thereby, efficient gas exchange can be performed on the blood flowing through the blood flow path 33.

  On the downstream side of the blood flow path 33 (on the downstream side of the hollow fiber membrane bundle 3), a gap (gap) is formed between the filter member 41 described later and the inner surface of the rectangular tubular housing body 21, and this The gap is a part through which the blood that has passed through the filter member 41 flows, and forms a blood outflow side opening (blood outflow side space) 25. The blood outflow side opening 25, the flow path enlargement part 281, and the blood outflow port 28 communicating with the blood outflow side opening 25 via the flow path enlargement part 281 constitute a blood outflow part. Further, the gap distance t of the blood outflow side opening 25 is constant.

  Since the blood outflow part has such a blood outflow side opening 25, a space through which the blood that has permeated the filter member 41 flows toward the blood outflow port 28 is secured, and blood can be smoothly discharged.

  Between the blood inflow side opening 24 and the blood outflow side opening 25, the hollow fiber membrane bundle 3, the filter member 41, the exhaust hollow fiber membrane layer 42, and the blood flow path 33 are present.

  As the hollow fiber membrane 31, for example, a porous gas exchange membrane is used. The porous hollow fiber membrane has an inner diameter of about 100 to 1000 μm, a thickness of about 5 to 200 μm, preferably about 10 to 100 μm, a porosity of about 20 to 80%, preferably about 30 to 60%, The thing with a hole diameter of about 0.01-5 micrometers, Preferably about 0.01-1 micrometer can be used.

  Moreover, as a constituent material of the hollow fiber membrane 31, for example, a hydrophobic polymer material such as polypropylene, polyethylene, polysulfone, polyacrylonitrile, polytetrafluoroethylene, and polymethylpentene is used. Polyolefin resins are preferred, polypropylene is more preferred, and those having fine pores formed in the wall by a stretching method or a solid-liquid phase separation method are more preferred.

  The length (effective length) of each hollow fiber membrane 31 in the hollow fiber membrane bundle 3 is not particularly limited, but is preferably about 30 to 150 mm, and more preferably about 50 to 100 mm.

  The thickness of the hollow fiber membrane bundle 3 (the length in the lateral direction in FIG. 2) is not particularly limited, but is preferably about 10 to 100 mm, and more preferably about 20 to 80 mm.

  The width of the hollow fiber membrane bundle 3 (length in the longitudinal direction in FIG. 3) is not particularly limited, but is preferably about 10 to 100 mm, and more preferably about 20 to 80 mm.

  As described above, on the downstream side (blood outflow side) of the hollow fiber membrane bundle 3, the bubble removing means 4 having a function of capturing bubbles in the blood and discharging the trapped bubbles out of the blood channel. is set up. The bubble removing means 4 includes a filter member 41 and an exhaust hollow fiber membrane layer 42 installed on the upstream side of the filter member 41. The filter member 41 has a function of capturing bubbles present in the blood flowing through the blood flow path 33, and the exhaust hollow fiber membrane layer 42 transmits gas constituting the bubbles captured by the filter member 41. A number of exhaust hollow fiber membranes 421 (hereinafter simply referred to as “hollow fiber membranes 421”) having a function of discharging are integrated. Hereinafter, the gas constituting the bubbles captured by the filter member 41 is referred to as “bubble forming gas”.

  The filter member 41 is configured by a flat sheet-like member (hereinafter, also simply referred to as “sheet”) having a substantially rectangular shape, and its edges (four sides) are fixed by the partition walls 8 and 9 and the fixing portions 7. Thus, the housing 2 is fixed.

  One side of the filter member 41 is provided in contact with the downstream surface (blood outflow portion side) of the exhaust hollow fiber membrane layer 42 and covers almost the entire surface. By providing the filter member 41 in this way, the effective area of the filter member 41 can be increased, and the ability to capture air bubbles can be sufficiently exhibited. Further, the increase in the effective area of the filter member 41 prevents the blood flow as a whole from being obstructed even if a part of the filter member 41 is clogged (for example, adhesion of blood clots or the like). (Suppressed).

  Examples of the form of the filter member 41 include a mesh-like (net-like), a woven fabric, a non-woven fabric, or a combination of these. Among these, a mesh-like (net-like) is preferable, In particular, a screen filter is preferable. Thereby, while being able to capture | acquire a bubble more reliably, the blood can pass easily.

  In the case of the filter member 41 having a mesh shape, the mesh opening is not particularly limited, but is usually preferably 80 μm or less, more preferably about 15 to 60 μm, and further preferably 20 to 45 μm. preferable. As a result, relatively fine bubbles can be captured without increasing the blood passage resistance, and the bubble capturing efficiency (removability) is high.

  Examples of the constituent material of the filter member 41 include polyolefins such as polyamide, polyethylene, and polypropylene, polyesters such as polyethylene terephthalate and polybutylene terephthalate, nylon, cellulose, polyurethane, and aramid fibers. In particular, it is preferable to use polyethylene terephthalate, polyethylene, or polyurethane as a constituent material of the filter member 41 in that it is excellent in antithrombogenicity and hardly clogs.

  The filter member 41 preferably has hydrophilicity. That is, it is preferable that the filter member 41 is made of a material having hydrophilicity or is subjected to hydrophilic treatment (for example, plasma treatment). This not only facilitates the removal of air bubbles during priming of the artificial lung 1, but also makes it difficult for the air bubbles to pass when blood mixed with air bubbles passes through. It is possible to further improve and prevent the outflow of bubbles from the blood outflow port 28 more reliably.

  As such a filter member 41, one sheet-like (particularly mesh like a screen filter) may be used, or two or more thereof may be used. When two or more sheets are used, each sheet may be used by combining at least one of conditions such as its form, constituent material, mesh opening, flat / non-flat, and planar shape.

  A gap, that is, a blood outflow side opening 25 is formed between the filter member 41 and the housing 2 (see FIGS. 2 to 4). Thereby, the filter member 41 is suppressed from coming into contact with (in close contact with) the inner surface of the housing 2, and the blood that has passed through the filter member 41 easily flows down in the blood outflow side opening 25 and passes through the flow channel enlargement part 281. It can flow smoothly toward the blood outflow port 28.

  In the illustrated embodiment, the planar shape of the filter member 41 is rectangular (or square). However, the planar shape of the filter member 41 is not limited to this, and for example, a trapezoid, a parallelogram, an ellipse, or an oval. The shape is not particularly limited.

  Further, in the illustrated embodiment, the filter member 41 is formed of a flat sheet. However, the filter member 41 is not limited to this, and is not flat. For example, the filter member 41 is deformed into a wave shape or the like that is entirely or partially curved. The thing etc. which were done may be sufficient.

  By installing the filter member 41 configured as described above, even if bubbles exist in the blood flowing through the blood flow path 33, the bubbles can be captured. It can be prevented from flowing out. This eliminates the need for an arterial filter conventionally provided in the arterial line.

  Air bubbles trapped by the filter member 41 are removed from the blood flow path 33 by the exhaust hollow fiber membrane layer 42 located on the upstream side of the filter member 41 (positioned between the filter member 41 and the hollow fiber membrane bundle 3). Removed.

  As shown in FIG. 4, most of the hollow fiber membranes 421 constituting the exhaust hollow fiber membrane layer 42 are arranged substantially parallel to the hollow fiber membranes 31 constituting the hollow fiber membrane bundle 3. In addition, both end portions (upper end portion and lower end portion) of each hollow fiber membrane 421 are fixed to the inner surface of the rectangular tubular housing body 21 by the partition walls 8 and 9 in the same manner as each hollow fiber membrane 31 ( (See FIG. 2).

  Thereby, the both ends of each hollow fiber membrane 421 and each hollow fiber membrane 31 can be collectively fixed by the partition walls 8 and 9, respectively. That is, the number of manufacturing steps for manufacturing the artificial lung 1 can be suppressed. Further, each hollow fiber membrane 421 can be filled into the rectangular tubular housing body 21 with almost no gap, that is, high filling efficiency of the hollow fiber membrane 421 can be obtained with respect to the rectangular tubular housing body 21 (dead space). Less). Therefore, it contributes to miniaturization and high performance of the artificial lung part 1A.

  Further, as shown in FIG. 3, the exhaust hollow fiber membrane layer 42 is fixed (fixed) to the inner surface of the rectangular tubular housing body 21 by fixing portions 7 at both ends in the width direction.

  The lumen of each hollow fiber membrane 421 constitutes a gas flow path 422 through which the bubble-constituting gas that flows in through a large number of pores formed in the wall portion of the hollow fiber membrane 421 flows.

  The upper end opening of each gas flow path 422 (each hollow fiber membrane 421) is open to and communicates with the small space 223. Thereby, the small space 223 can function as a bubble storage unit that temporarily stores the bubble constituent gas that has risen through the gas flow paths 422.

  Moreover, the lower end opening of each gas flow path 422 is open | released and connected to the small space 233 (refer FIG. 4). The small space 233 communicates with the exhaust port 29.

  With such a configuration, the bubble constituent gas that has flowed out from the lower end opening of each gas flow path 422 passes through the small space 233 and further passes through the exhaust port 29 to be reliably exhausted from the artificial lung 1 (housing 2). The Thereby, it is possible to prevent bubbles in the blood passing through the blood flow path 33 from flowing out from the blood outflow portion. It can be said that the exhaust port 29 functions as a part of the bubble removing means 4.

  The hollow fiber membrane 421 constituting the exhaust hollow fiber membrane layer 42 and the hollow fiber membrane 31 constituting the hollow fiber membrane bundle 3 may be the same or different. .

  When each hollow fiber membrane 421 and each hollow fiber membrane 31 are different, it is preferable that at least one of the constituent materials, characteristics, and arrangement conditions is different.

  For example, the thickness (length in the lateral direction in FIG. 2) of the exhaust hollow fiber membrane layer 42 can be about 10 to 50 mm.

  Moreover, the width | variety (length of the vertical direction in FIG. 3) of the exhaust hollow fiber membrane layer 42 can be about 10-80 mm.

  The arrangement pattern and arrangement direction of the hollow fiber membranes 421 in the exhaust hollow fiber membrane layer 42 include, for example, a configuration in which the hollow fiber membranes 421 are arranged in a horizontal direction, and the hollow fiber membranes 421 are oblique to each other. A configuration having intersecting portions (intersection portions), a configuration in which all or a part of the hollow fiber membranes 421 are curved and arranged, or a part or all of the hollow fiber membranes 421 are arranged in a wave shape, a spiral shape, a spiral shape or an annular shape The structure etc. which were made are mentioned.

  Thus, the following effects are produced by various conditions. That is, first of all, gas is reliably exchanged with respect to the blood by the hollow fiber membrane bundle 3, and bubbles in the blood after the gas exchange are surely discharged by the hollow fiber membrane layer 42 for exhaust. Second, conditions suitable for gas exchange can be selected for the hollow fiber membrane bundle 3, and conditions suitable for exhaust can be selected for the hollow fiber membrane layer 42 for exhaust. Therefore, high performance can be exhibited for both gas exchange and exhaust. Thirdly, each of the structures having two performances of gas exchange and exhaust can be accommodated in one housing 2 without waste, and thus the interval (filling amount) of the blood flow path 33 is kept low. be able to.

  The filter member 41 is not limited to a configuration provided so as to cover substantially the entire downstream surface of the exhaust hollow fiber membrane layer 42. For example, the downstream surface of the exhaust hollow fiber membrane layer 42 is provided. It may be configured such that a part of the cover is covered and the remaining part is installed through a gap. In this case, the gap functions as a bubble storage part.

  Air bubbles in blood containing bubbles (hereinafter, this blood is referred to as “bubble-containing blood”) on the upstream side of the filter member 41 are captured by the filter member 41. On the other hand, blood that has passed through the filter member 41 and from which bubbles have been removed flows along the filter member 41 toward the blood outflow port 28. When the flow velocity of the blood flowing into the flow path expanding portion 281 is sufficiently decelerated, the blood flow toward the blood outflow port 28 draws bubbles captured by the filter member 41 through the filter member 41 (Venturi effect). Stop. Thereby, it is possible to reliably prevent bubbles in the blood from flowing out from the blood outflow port 28 (blood outflow portion).

  Next, the heat exchange part (heat exchanger) 1B will be described. The heat exchanger 1 </ b> B has a heat exchanger housing 5. The heat exchanger housing 5 has a substantially cylindrical shape, and its upper end and lower end are closed. A blood chamber 50 is formed in the heat exchanger housing 5. A tubular heat medium inflow port 52 and a heat medium outflow port 53 project from the lower end (lower surface) of the heat exchanger housing 5. Further, a tubular blood inlet port 51 protrudes from the lower portion of the heat exchanger housing 5 on the left side in FIG. The lumen of the blood inflow port 51 communicates with the blood chamber 50.

  Inside the heat exchanger housing 5, a heat exchange body 54 whose overall shape is cylindrical, and a cylindrical heat medium chamber forming member (cylindrical wall) 55 disposed along the inner periphery of the heat exchange body 54, A partition wall 56 that divides the inner space of the heat medium chamber forming member 55 into an inflow side heat medium chamber 57 and an outflow side heat medium chamber 58 is provided. The heat medium chamber forming member 55 has a function of forming a heat medium chamber in which the heat medium is temporarily stored inside the heat exchanger 54 and a function of regulating deformation of the cylindrical heat exchanger. .

  The heat medium chamber forming member 55 and the partition wall 56 are fixed to the heat exchanger housing 5 by a method such as fusion or bonding with an adhesive. The heat medium chamber forming member 55 and the partition wall 56 may be separate members or integrally formed.

  Further, the heat medium chamber forming member 55 is formed with strip-shaped openings 59a and 59b extending in the vertical direction penetrating the wall portion. The opening 59a and the opening 59b are disposed at positions facing each other through the partition wall 56 (see FIG. 3). The opening 59 a communicates with the inflow side heat medium chamber 57, and the opening 59 b communicates with the outflow side heat medium chamber 58.

  As the heat exchanger 54, a so-called bellows type heat exchanger (bellows tube) as shown in FIG. 2 can be used. The bellows-type heat exchange element 54 includes a bellows forming portion having a large number of hollow annular protrusions formed substantially parallel to the side surface of the central portion in the axial direction, and is formed at both ends (upper and lower ends) of the bellows type heat exchanger 54. A substantially equal cylindrical portion. The heat exchanger 54 is made of a metal material such as stainless steel or aluminum, or a resin material such as polyethylene or polycarbonate. A metal material such as stainless steel or aluminum is preferable in terms of strength and heat exchange efficiency. In particular, it is preferable that the heat exchanger 54 is made of a metal bellows tube having a wave shape in which a large number of irregularities substantially orthogonal to the axial direction (center axis) of the heat exchanger 54 are repeated.

  Examples of the constituent material of the heat exchanger housing 5, the heat medium chamber forming member 55, and the partition wall 56 include polyolefins such as polyethylene and polypropylene, ester resins (for example, polyesters such as polyethylene terephthalate and polybutylene terephthalate), and styrene. Examples thereof include resins (for example, polystyrene, MS resin, MBS resin), resin materials such as polycarbonate, various ceramic materials, and metal materials.

  Hereinafter, the flow of the heat medium in the heat exchange unit 1B of the artificial lung 1 will be described with reference to FIGS.

  The heat medium flowing in from the heat medium inflow port 52 first enters the inflow side heat medium chamber 57, flows into the outer peripheral side of the heat medium chamber forming member 55 through the opening 59 a, and almost the entire outer periphery of the heat medium chamber forming member 55. It spreads around the circumference and enters a large number of concave portions (inside the hollow annular projection) of the bellows of the heat exchanger 54. As a result, the heat exchanger 54 in contact with the heat medium is heated or cooled. Then, heat exchange (heating or cooling) is performed with the blood flowing on the outer peripheral side of the heat exchanger 54.

  The heat medium used for heating or cooling the heat exchanger 54 enters the outflow side heat medium chamber 58 through the opening 59 b and is discharged from the heat medium outflow port 53.

  Note that, unlike the illustrated embodiment, in the present invention, the heat exchanging portion 1B may not exist.

  Next, the flow of blood in the oxygenator 1 of this embodiment will be described with reference to FIGS.

  In the oxygenator 1, blood flowing from the blood inflow port 51 flows between the blood chamber 50, that is, between the inner peripheral surface of the heat exchanger housing 5 and the heat exchanger 54. Heat exchange (heating or cooling) is performed in contact with the outer surface of the protrusion. The blood thus heat-exchanged gathers on the downstream side of the blood chamber 50 and flows into the housing 2 of the artificial lung portion 1A through the blood inflow side opening 24.

  The blood that has passed through the blood inflow side opening 24 flows in the blood flow path 33 in the downstream direction. On the other hand, the gas (gas containing oxygen) supplied from the gas inflow port 26 is distributed from the gas inflow chamber 261 to the gas flow paths 32 that are the lumens of the hollow fiber membranes 31, and flows through the gas flow paths 32. Thereafter, the gas is accumulated in the gas outflow chamber 271 and discharged from the gas outflow port 27. The blood flowing through the blood flow path 33 contacts the surface of each hollow fiber membrane 31, and gas exchange (oxygenation, decarbonation gas) is performed with the gas flowing through the gas flow path 32.

  When bubbles are mixed in the blood that has undergone gas exchange, the bubbles are captured by the filter member 41. Bubbles captured by the filter member 41 (bubble constituent gas) pass through a large number of pores in the wall of each hollow fiber membrane 421 of the exhaust hollow fiber membrane layer 42 adjacent to the upstream side of the filter member 41, and It enters the lumen (gas flow path 422) of the hollow fiber membrane 31. The bubble constituent gas that has entered the lumen of the hollow fiber membrane 31 is discharged from the exhaust port 29 through the small space 233.

  The blood after the gas exchange and the removal of the bubbles as described above flows out from the blood outflow port 28.

  In the artificial lung 1 of the present embodiment, a surface that comes into contact with blood (for example, the inner surface of the housing 2, the inner surface of the heat exchanger housing 5, the surface of the heat medium chamber forming member 55, the surface of the partition wall 56, the fixing portion 7, the partition wall) The surfaces facing the blood flow paths 33 of 8 and 9 are preferably antithrombogenic surfaces. The antithrombogenic surface can be formed by coating the surface with an antithrombogenic material and further fixing. Examples of the antithrombotic material include heparin, urokinase, HEMA-St-HEMA copolymer, and poly-HEMA.

  In the artificial lung 1, the flow rate of blood flowing from the blood inflow port 51 is not particularly limited because it varies depending on the patient's physique and surgical method (surgical method). About 2.0 L / min is preferable, about 2.0 to 5.0 L / min is preferable for middle-aged people, and about 3.0 to 7.0 L / min is preferable for adults.

  In the oxygenator 1, the flow rate of the gas supplied from the gas inflow port 26 is not particularly limited because it varies depending on the patient's physique and technique, but generally 0.05 to 4.0 L / in for infants to children. For example, about 1.0 to 10.0 L / min is preferable for middle-aged persons, and about 1.5 to 14.0 L / min is preferable for adults.

  Moreover, since the oxygen concentration in the gas supplied from the gas inflow port 26 varies depending on the metabolic amount of oxygen / carbon dioxide gas of the patient during the operation, it is not particularly limited, but can be 40 to 100%.

  Further, the maximum continuous operation time of the oxygenator 1 is not particularly limited because it varies depending on the patient's condition and surgical technique, but can generally be about 2 to 6 hours. In addition, the maximum continuous operation time of the oxygenator 1 may rarely be as long as about 10 hours.

Second Embodiment
FIG. 5 is a longitudinal sectional view (sectional side view) showing a second embodiment of the oxygenator of the present invention.

  Hereinafter, the second embodiment of the oxygenator according to the present invention will be described with reference to this drawing, but the description will focus on the differences from the first embodiment described above, and the same matters will not be described and illustrated. .

This embodiment is the same as the first embodiment except that the shape of the housing is different.
In the artificial lung 1 ′ shown in FIG. 5, the downstream wall portion 211 of the rectangular tubular housing body 21 (housing 2) is inclined with respect to the central axis of the rectangular tubular housing body 21. That is, in the artificial lung 1 ′, the cross-sectional area of the rectangular tube-shaped housing body 21 is gradually increased toward the lower side (flow channel expanding portion 281) in FIG. 5. For this reason, the gap distance of the gap formed between the inner surface (wall portion 211) of the rectangular tubular housing body 21 and the filter member 41, that is, the gap distance t of the blood outflow side opening 25 is the flow path expanding portion 281. It gradually increases (increases) toward (downstream).

As the gap distance t gradually increases in this way, the flow rate of the blood flowing down the blood outflow side opening 25 is further decelerated until it reaches the flow path expanding portion 281. By slowing down the flow rate in this manner, the flow of blood is not unreasonable, the flow rate distribution of the flow in the blood flow path 33 is uniform, and as a result, the pressure loss when the blood flows is kept low. Can do.
The gap distance t may increase stepwise toward the downstream side (downward).
Such a portion (lower portion) where the gap distance t of the blood outflow side opening 25 is increased is a portion where the channel cross-sectional area of the blood outflow side opening 25A is enlarged. The same function as the 1st expansion part 282A in an embodiment is exhibited.

<Third Embodiment>
FIG. 6 is a plan view showing a third embodiment of the oxygenator of the present invention, FIG. 7 is a diagram (left side view) of the oxygenator shown in FIG. 6 viewed from the arrow B side, and FIG. 9 is a cross-sectional view taken along the line D-D in FIG. 7, FIG. 10 is a cross-sectional view taken along the line E-E in FIG. 6, and FIG. It is an expanded sectional view of a thread membrane bundle, a filter member, and a hollow fiber membrane layer for exhaust). 6, 8, and 9 are referred to as “left” or “left”, and the right side is referred to as “right” or “right”. Moreover, the upper side in FIGS. 6-8, 10 and 11 is called "upper" or "upper", and the lower side is called "lower" or "lower". Further, in FIGS. 6 to 11, the inside of the artificial lung will be described as “blood inflow side” or “upstream side”, and the outside will be described as “blood outflow side” or “downstream side”.
Hereinafter, the third embodiment of the oxygenator according to the present invention will be described with reference to these drawings. The description will focus on the differences from the above-described embodiments, and the same matters will not be described and illustrated. .

This embodiment is the same as the first embodiment except that the overall shape of the oxygenator is different.
The oxygenator 10 of the illustrated embodiment has a substantially cylindrical shape as a whole (outer shape). The artificial lung 10 is provided on the inner side, provided on the outer peripheral side of the heat exchanging part (heat exchanger) 10B having substantially the same configuration as the heat exchanging part 1B of the first embodiment, and the blood exchanging part 10B. This is an oxygenator with a heat exchanger and an oxygenator 10A that performs gas exchange.

  The oxygenator 1 has a housing 2A, and an oxygenator 10A and a heat exchanger 10B are accommodated in the housing 2A. As shown in FIG. 10, the oxygenator 10A and the heat exchanger 10B are installed concentrically with the housing 2A.

  Moreover, the heat exchange part 10B is further accommodated in the heat exchanger housing 5A in the housing 2A. With this heat exchanger housing 5A, both end portions of the heat exchanging portion 10B are fixed to the housing 2A, respectively.

  The housing 2A includes a cylindrical housing main body (hereinafter referred to as “cylindrical housing main body”) 21A and a dish-shaped first header (upper lid) that seals the left end opening of the cylindrical housing main body (body portion) 21A. ) 22A and a dish-shaped second header (lower lid) 23A for sealing the right end opening of the cylindrical housing body 21A.

  The cylindrical housing main body 21A, the first header 22A, and the second header 23A are, for example, polyolefins such as polyethylene and polypropylene, ester resins (for example, polyesters such as polyethylene terephthalate and polybutylene terephthalate), and styrene resins. (For example, polystyrene, MS resin, MBS resin), resin materials such as polycarbonate, various ceramic materials, metal materials, and the like. The first header 22A and the second header 23A are liquid-tightly 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 substantially in the tangential direction of the outer peripheral surface (circumference) of the cylindrical housing body 21A (see FIGS. 7 and 10). In the configuration shown in FIG. 10, the inner surface (hereinafter referred to as “outer inner surface 280”) of the outer side of the blood outflow port 28 (the side far from the center of the cylindrical housing body 21A) is the inner peripheral surface (accurately) of the cylindrical housing body 21A. Is located on the outer peripheral side of the inner peripheral surface on the surface extending into the blood outflow port 28). In this case, the distance (offset) C between the outer inner surface 280 of the blood outflow port 28 and the surface obtained by extending the inner peripheral surface of the cylindrical housing body 21A into the blood outflow port 28 is, for example, about 0.5 to 4 mm. Is done.

  A blood outflow side opening 25A, which will be described later, has a cylindrical shape concentric with the cylindrical housing body 21A. As a result, the blood outflow port 28 protrudes in a substantially tangential direction of the circumference of the blood outflow side opening 25A. Will be. Thereby, the blood that has passed through the blood outflow side opening 25A can flow into the blood outflow port 28 smoothly and easily.

  Near the cylindrical housing body 21A (housing 2) side of the blood outflow port 28 (in the vicinity of the end on the upstream side), that is, at the root of the blood outflow port 28, a flow path expanding portion 281 having a box shape (or groove shape). Is provided. The lumen of the blood outflow port 28 and the lumen of the flow path expanding portion 281 are in communication, and constitute a flow path through which blood that has passed through a filter member 41A described later passes. As shown in FIGS. 8 and 10, the flow path expanding portion 281 is a portion where the cross-sectional area of the flow path is increased.

  In the artificial lung 1, when the blood that has passed through the filter member 41 </ b> A flows into the flow channel enlargement unit 281, the flow rate is reduced at a rate that is the reciprocal of the increase rate of the flow channel cross-sectional area according to the continuous equation. The blood reaches the blood outflow port 28 in a state where is decelerated.

  A tubular blood inflow port 201 and a gas outflow port 27 are formed to protrude from the first header 22A. The blood inflow port 201 is formed on the end face of the first header 22A so that the central axis thereof is eccentric with respect to the center of the first header 22A. The gas outflow port 27 is formed on the outer peripheral portion of the first header 22A so that its central axis intersects the center of the first header 22A (see FIG. 7).

  A tubular gas inflow port 26, an exhaust port (exhaust port) 29, a heat medium inflow port 202, and a heat medium outflow port 203 are formed in the second header 23A so as to protrude. The gas inflow port 26 and the exhaust port 29 are each formed at the edge of the end face of the second header 23A. The heat medium inflow port 202 and the heat medium outflow port 203 are each formed at substantially the center of the end face of the second header 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 header 23A.

  In the present invention, the entire shape of the housing 2A does not necessarily have a complete columnar shape, and may be, for example, a shape in which a part is missing or a shape in which a deformed part is added.

  As shown in FIGS. 8 to 10, a cylindrical artificial lung portion 10 </ b> A having a cylindrical shape along the inner peripheral surface is concentrically disposed (contained) inside the housing 2 </ b> A. The artificial lung portion 10A includes a cylindrical hollow fiber membrane bundle 3A, a filter member 41A as an air bubble removing means 4A provided on the outer peripheral side (blood outflow portion side) of the hollow fiber membrane bundle 3A, and an exhaust hollow fiber membrane layer. 42A. These layers and members are arranged (laminated) in the order of the hollow fiber membrane bundle 3A, the exhaust hollow fiber membrane layer 42A, and the filter member 41A from the blood inflow side.

  As shown in FIG. 11, the hollow fiber membrane bundle 3 </ b> A is obtained by integrating a large number of hollow fiber membranes 31 having a gas exchange function. Most of the hollow fiber membranes 31 constituting the hollow fiber membrane bundle 3A are arranged substantially parallel to the central axis of the housing 2A, or are inclined at a predetermined angle with respect to the central axis of the housing 2A. Yes. When the hollow fiber membrane 31 is wound, for example, spirally around the central axis of the housing 2A, the latter is the latter.

  The arrangement pattern, the arrangement direction, and the like of the hollow fiber membranes 31 in the hollow fiber membrane bundle 3A are not limited to those described above. For example, each hollow fiber membrane 31 is in a direction perpendicular to the central axis of the housing 2A. Arranged configuration, configuration in which the hollow fiber membrane 31 is wound around the central axis of the housing 2A, and the hollow fiber membranes 31 have a portion (intersection) where the hollow fiber membranes 31 obliquely intersect each other, or all or some of the hollow fiber membranes 31 are curved A configuration in which all or a part of the hollow fiber membranes 31 are arranged in a wave shape, a spiral shape, a spiral shape, or an annular shape may be used.

  Both end portions (left end portion and right end portion) of each hollow fiber membrane 31 are fixed to the inner surface of the cylindrical housing main body 21A by partition walls 8 and 9, respectively (see FIGS. 9 and 10).

  Further, the hollow fiber membrane bundle 3A is filled between the cylindrical housing main body 21A and the heat exchanging portion 10B with almost no gap, so that the hollow fiber membrane bundle 3A has a substantially cylindrical shape as a whole. There is no. Thereby, the high filling efficiency of the hollow fiber membrane 31 is obtained with respect to the cylindrical housing body 21A having the same shape (the dead space is small), which contributes to the miniaturization and high performance of the oxygenator 10A.

  Each hollow fiber membrane 31 between the partition wall 8 and the partition wall 9 in the housing 2A is exposed, and the outside of each hollow fiber membrane 31 (the same applies to the hollow fiber membrane 421 of the exhaust hollow fiber membrane layer 42A), that is, A blood flow path 33 in which blood flows from the left side to the right side in FIG. 2 is formed in the gap between the hollow fiber membranes 31.

  As an inflow portion of blood flowing from the blood inflow port 201 between the upstream side of the blood flow path 33 (the upstream side of the hollow fiber membrane bundle 3A), that is, between the artificial lung portion 10A and the heat exchange portion 10B. A cylindrical blood inlet side opening (blood inlet side space) 24A is formed.

  The blood that has flowed into the blood inflow side opening 24A flows along the circumferential direction and the longitudinal direction of the blood inflow side opening 24A, and thus reaches the entire blood inflow side opening 24A. Thereby, the blood can be efficiently transferred from the heat exchange unit 10B to the oxygenator 10A.

  On the downstream side of the blood flow path 33 (on the downstream side of the hollow fiber membrane bundle 3A), 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. The gap is a portion where blood that has passed through the filter member 41A flows, and forms a blood outflow side opening (blood outflow side space) 25A. The blood outflow portion is constituted by the blood outflow side opening portion 25A, the flow channel enlargement portion 281 and the blood outflow port 28 communicating with the blood outflow side opening portion 25A via the flow passage enlargement portion 281. Further, the gap distance t of the blood outflow side opening 25 is constant in the circumferential direction of the blood outflow side opening 25.

  Since the blood outflow part has such a blood outflow side opening 25A, a space through which the blood that has passed through the filter member 41A flows toward the blood outflow port 28 is secured, and the blood can be smoothly discharged.

  The hollow fiber membrane bundle 3A, the filter member 41A, the exhaust hollow fiber membrane layer 42A, and the blood flow path 33 are present between the blood inflow side opening 24A and the blood outflow side opening 25A.

  In addition, the thickness (length in the radial direction in FIG. 10) of the hollow fiber membrane bundle 3A is not particularly limited, but is preferably about 2 to 100 mm, and more preferably about 3 to 30 mm.

  As described above, on the downstream side (blood outflow portion side) of the hollow fiber membrane bundle 3A, the bubble removing means 4A having a function of capturing bubbles in the blood and discharging the captured bubbles out of the blood channel. is set up. The bubble removing means 4A includes a filter member 41A and an exhaust hollow fiber membrane layer 42A installed on the upstream side of the filter member 41A.

  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 columnar shape. The filter member 41A is fixed to the housing 2A by fixing both ends thereof with partition walls 8 and 9, respectively (see FIGS. 8 and 9).

  The filter member 41A is provided so that its inner peripheral surface is in contact with the downstream surface (blood outflow portion side) of the exhaust hollow fiber membrane layer 42A and covers almost the entire surface. By providing the filter member 41A in this manner, the effective area of the filter member 41A can be increased, and the ability to capture air bubbles can be sufficiently exhibited. Further, the increase in the effective area of the filter member 41A prevents the blood flow as a whole from being obstructed even if a part of the filter member 41A is clogged (for example, adhesion of blood clots or the like). (Suppressed).

  In addition, as a form of the filter member 41A, for example, a form similar to the filter member 41 of the first embodiment, that is, a mesh-like (net-like) form, a woven cloth, a non-woven cloth, or a combination thereof is used. be able to.

  Further, as the constituent material of the filter member 41A, for example, the same material as that of the filter member 41 of the first embodiment can be used.

  In the illustrated embodiment, the filter member 41A has a substantially constant outer diameter. However, the filter member 41A is not limited thereto. For example, the filter member 41A has a part in which a part of the outer diameter is enlarged or reduced. May be.

  By installing the filter member 41A having the above-described configuration, even if bubbles are present in the blood flowing through the blood flow path 33, the bubbles can be captured. It can be prevented from flowing out.

  Bubbles captured by the filter member 41A are removed from the blood flow path 33 by the exhaust hollow fiber membrane layer 42A located on the upstream side of the filter member 41A.

As shown in FIG. 11, most of the hollow fiber membranes 421 constituting the exhaust hollow fiber membrane layer 42A are disposed substantially parallel to the central axis of the housing 2A (the hollow fibers constituting the hollow fiber membrane bundle 3A). Or arranged so as to be inclined at a predetermined angle with respect to the central axis of the housing 2A. When the hollow fiber membrane 421 is wound, for example, spirally around the central axis of the housing 2A, the latter is the latter.
Further, both end portions (upper end portion and lower end portion) of each hollow fiber membrane 421 are fixed to the inner surface of the cylindrical housing main body 21A by the partition walls 8 and 9 as in the case of each hollow fiber membrane 31 (FIG. 8 and FIG. 9).

  The arrangement pattern, arrangement direction, and the like of the hollow fiber membrane 421 in the exhaust hollow fiber membrane layer 42A are not limited to those described above. For example, each hollow fiber membrane 421 is perpendicular to the central axis of the housing 2A. A configuration arranged in a direction, a configuration in which the hollow fiber membrane 421 is wound around the central axis of the housing 2A, and a portion (intersection) where the hollow fiber membranes 31 obliquely intersect each other (intersection), all or part of the hollow fiber membranes 31 May be a configuration in which all or a part of the hollow fiber membranes 421 are arranged in a wave shape, a spiral shape, a spiral shape, or an annular shape.

  Further, the thickness (length in the radial direction in FIG. 10) of the exhaust hollow fiber membrane layer 42A is not particularly limited, but is preferably about 1 to 50 mm, and more preferably about 1 to 30 mm.

  As shown in FIG. 9 (also in FIG. 8), the first chamber 221a is defined by the first header 22A, the partition wall 8, the heat exchanger housing 5A of the heat exchange unit 10B, and the heat medium chamber forming member 55. Has been. This first chamber 221a is divided into a gas outflow chamber 271 on the hollow fiber membrane bundle 3A side and an exhaust hollow by a partition 222 provided at the boundary between the hollow fiber membrane bundle 3A and the exhaust hollow fiber membrane layer 42A. It is divided into a small space 223 on the thread membrane layer 42A side. The left end opening of each hollow fiber membrane 31 is open to and communicated with the gas outflow chamber 271.

  On the other hand, a second chamber 231a is defined by the second header 23A, the partition wall 9, the heat exchanger housing 5A of the heat exchange unit 10B, and the heat medium chamber forming member 55. The second chamber 231a is divided into a gas inflow chamber 261 on the hollow fiber membrane bundle 3A side and a hollow for exhaust by a partition 232 provided at the boundary between the hollow fiber membrane bundle 3A and the exhaust hollow fiber membrane layer 42A. It is divided into a small space 233 on the thread membrane layer 42A side. The right end opening of each hollow fiber membrane 31 is open to and communicated with the gas inflow chamber 261 (see FIG. 11).

  The lumen of each hollow fiber membrane 31 constitutes a gas flow path 32 through which gas flows. The gas inflow port 26 and the gas inflow chamber 261 constitute a gas inflow portion located upstream of the gas flow path 32, and the gas outflow port 27 and the gas outflow chamber 271 constitute a gas located downstream of the gas flow path 32. An outflow section is constructed.

  In addition, the lumen of each hollow fiber membrane 421 constitutes a gas flow path 422 through which the bubble-constituting gas that flows in through a large number of pores formed in the wall portion of the hollow fiber membrane 421 flows.

  The left end opening of each gas flow path 422 (each hollow fiber membrane 421) is open to and communicates with the small space 223. Thereby, the small space 223 can function as a bubble storage section that temporarily stores the bubble constituent gas that has flowed out of each gas flow path 422.

  Further, the right end opening of each gas flow path 422 is open to and communicates with the small space 233 (see FIG. 11). The small space 233 communicates with the exhaust port 29.

  With such a configuration, the bubble constituent gas flowing out from the right end opening of each gas flow path 422 passes through the small space 233 and further passes through the exhaust port 29 and is reliably exhausted from the artificial lung 10 (housing 2A). The Thereby, it is possible to reliably prevent bubbles in the blood passing through the blood flow path 33 from flowing out from the blood outflow portion.

  Air bubbles in the bubble-containing blood upstream of the filter member 41A are captured by the filter member 41A. On the other hand, blood that has passed through the filter member 41A and from which bubbles have been removed flows along the filter member 41A toward the blood outflow port 28. By sufficiently slowing down the flow velocity of the blood flowing into the flow path expanding portion 281, the blood flow toward the blood outflow port 28 draws bubbles captured by the filter member 41 </ b> A through the filter member 41 </ b> A (Venturi effect). Stop. Thereby, it is possible to reliably prevent bubbles in the blood from flowing out from the blood outflow port 28 (blood outflow portion).

  As described above, the heat exchanging unit 10B is installed inside the artificial lung unit 10A. Since this heat exchanging part 10B has substantially the same configuration as the heat exchanging part 1B, its description is omitted.

  In addition, since the heat exchanging part 10B is installed inside the artificial lung part 10A as described above, the following effects can be obtained. That is, first, the oxygenator 10A and the heat exchanger 10B can be efficiently stored in one housing 2A, and the dead space is small. Therefore, efficient gas exchange is performed with the small oxygenator 10. be able to. Second, the oxygenator 10A and the heat exchanger 10B are in a state closer to that of the first embodiment, so that the blood exchanged by the heat exchanger 10B can quickly flow into the oxygenator 10A. Therefore, the filling amount of blood in the blood inflow side opening 24A (blood channel 33) connecting the heat exchange part 10B and the artificial lung part 10A can be minimized. Thirdly, the blood heat-exchanged by the heat exchange unit 10B can quickly flow into the oxygenator 10A without being dissipated or absorbed.

  Next, the flow of blood in the oxygenator 10 of this embodiment will be described with reference to FIGS.

  In the oxygenator 10, the blood flowing in from the blood inflow port 201 flows between the blood chamber 50, that is, between the inner peripheral surface of the heat exchanger housing 5 </ b> A and the heat exchanger 54. Heat exchange (heating or cooling) is performed in contact with the outer surface of the protrusion. The blood thus heat-exchanged sequentially passes through the opening 59c formed in the upper part of the heat exchanger housing 5A and the blood inflow side opening 24A and flows into the housing 2A of the oxygenator 10A.

  The blood that has passed through the blood inflow side opening 24A flows in the blood flow path 33 in the downstream direction. On the other hand, the gas (gas containing oxygen) supplied from the gas inflow port 26 is distributed from the gas inflow chamber 261 to the gas flow paths 32 that are the lumens of the hollow fiber membranes 31, and flows through the gas flow paths 32. Thereafter, the gas is accumulated in the gas outflow chamber 271 and discharged from the gas outflow port 27. The blood flowing through the blood flow path 33 contacts the surface of each hollow fiber membrane 31, and gas exchange (oxygenation, decarbonation gas) is performed with the gas flowing through the gas flow path 32.

  When bubbles are mixed in the blood that has undergone gas exchange, the bubbles are captured by the filter member 41A. Bubbles (bubble constituent gas) trapped by the filter member 41A pass through a large number of pores in the wall portions of the hollow fiber membranes 421 of the exhaust hollow fiber membrane layer 42A adjacent to the upstream side of the filter member 41A. It enters the lumen (gas flow path 422) of the hollow fiber membrane 31. The bubble constituent gas that has entered the lumen of the hollow fiber membrane 31 is discharged from the exhaust port 29 through the small space 233.

  The blood after the gas exchange and the removal of the bubbles as described above flows out from the blood outflow port 28.

<Fourth embodiment>
FIG. 12 is a cross-sectional view showing a fourth embodiment of the oxygenator of the present invention.

  Hereinafter, the fourth embodiment of the oxygenator according to the present invention will be described with reference to this drawing. However, the differences from the above-described embodiments will be mainly described, and the description and illustration of the same matters will be omitted.

  This embodiment is the same as the third embodiment except that the oxygenator is stored eccentrically with respect to the housing.

In the artificial lung 10 ′ shown in FIG. 12, the artificial lung portion 10A is arranged eccentrically upward with respect to the housing 2A (cylindrical housing body 21A). Therefore, the gap distance of the gap formed between the inner peripheral surface of the cylindrical housing body 21A and the outer peripheral surface of the filter member 41A, that is, the gap distance t of the blood outflow side opening 25A is downstream along the circumferential direction. It gradually increases (increases) toward the side, that is, toward the flow path expanding portion 281. In the blood outflow side opening 25A, the gap distance t is the minimum gap distance t _min above and the maximum gap distance t _max below (downstream).

The blood outflow side opening 25A in the vicinity of the maximum gap distance _tmax has an enlarged flow passage cross-sectional area of the blood outflow side opening 25A. Therefore, the first enlarged portion in the seventh embodiment to be described later. It corresponds to 282A and exhibits the same function as the first enlarged portion 282A.

  As the gap distance t gradually increases in this way, the flow rate of the blood passing through the blood outflow side opening 25A is further decelerated until it reaches the flow path expanding portion 281. In addition, since the flow velocity is gradually reduced in this way, there is no difficulty in blood flow, the flow velocity distribution in the blood flow path 33 is uniform, and as a result, the pressure loss when blood flows is reduced. Can be suppressed.

<Fifth Embodiment>
FIG. 13: is a longitudinal cross-sectional view (cross-sectional side view) which shows 5th Embodiment of the oxygenator of this invention.
Hereinafter, the fifth embodiment of the oxygenator according to the present invention will be described with reference to this drawing. However, the description will focus on the differences from the first embodiment described above, and the same matters will not be described and illustrated. .

  The oxygenator 1 of the present embodiment is the same as that of the first embodiment except that the exhaust hollow fiber membrane layer 42 and the exhaust port (exhaust port) 29 are not present. That is, the bubble removing means 4 in this embodiment is configured by the filter member 41.

  Further, in the present embodiment, since the exhaust port 29 does not exist, the partition portions 222 and 232 are not provided.

<Sixth Embodiment>
FIG. 14 is a longitudinal sectional view (sectional side view) showing a sixth embodiment of the oxygenator of the present invention.
Hereinafter, the sixth embodiment of the oxygenator according to the present invention will be described with reference to this drawing, but the description will focus on the differences from the second embodiment described above, and the same matters will not be described and illustrated. .

  The oxygenator 1 ′ of this embodiment is the same as that of the second embodiment except that the exhaust hollow fiber membrane layer 42 and the exhaust port (exhaust port) 29 are not present. That is, the bubble removing means 4 in this embodiment is configured by the filter member 41.

  Further, in the present embodiment, since the exhaust port 29 does not exist, the partition portions 222 and 232 are not provided.

<Seventh embodiment>
FIG. 15 is a longitudinal sectional view (sectional side view) showing a seventh embodiment of the oxygenator of the present invention, and FIG. 16 is a perspective view of a cylindrical housing body in the oxygenator of the seventh embodiment.

  Hereinafter, the seventh embodiment of the oxygenator according to the present invention will be described with reference to these drawings, but the description will focus on the differences from the third embodiment described above, and the description of the same matters will be omitted. Moreover, about the structure similar to 3rd Embodiment, FIGS. 6-11 shall be substituted.

  The oxygenator 10 ″ of the present embodiment does not include the exhaust hollow fiber membrane layer 42A, the exhaust port (exhaust port) 29, and the partitioning portions 222 and 232, and the first embodiment except that the configuration of the flow path expanding portion is different. This is the same as the third embodiment (FIGS. 6 to 11).

  The bubble removing means 4A in the present embodiment is composed of a filter member 41A and does not have the exhaust hollow fiber membrane layer 42A and the exhaust port 29. Further, since the exhaust port 29 does not exist, the partition portions 222 and 232 (see FIG. 9) are not provided.

  Further, the flow path expanding portion 282 in the present embodiment is composed of an upstream first expanded portion 282A and a second expanded portion 282B following this. Thereby, the effect of preventing the discharge of bubbles from the blood outflow port 28 is more remarkably exhibited.

  In the vicinity of the base portion of the blood outflow port 28 (in the vicinity of the upstream end portion), a groove (groove-shaped recess) having a certain width is formed on the inner peripheral surface of the cylindrical housing body 21A in the axial direction (longitudinal direction) of the cylindrical housing body 21A. ) And this groove constitutes the first enlarged portion 282A. In other words, the first enlarged portion 282A is a portion in which the inner diameter of the cylindrical housing body 21A is partially (locally) enlarged.

  The first advantage 282A is not provided on the entire circumference of the inner peripheral surface of the cylindrical housing main body 21A, but is provided locally on a part of the inner peripheral surface. There is. That is, when the first enlarged portion 282A is provided on the entire inner peripheral surface of the cylindrical housing body 21A, the volume of the blood outflow side opening 25A increases and the blood priming volume increases. When the blood outflow side opening 25A is provided on a part of the inner peripheral surface of the cylindrical housing main body 21A as in the form, the effect of preventing the discharge of the bubbles is obtained while suppressing an increase in the priming volume. be able to.

  The groove constituting the first enlarged portion 282A is formed over substantially the entire axial length (longitudinal direction) of the cylindrical housing body 21A, that is, over the entire axial length of the blood outflow side opening 25A. Preferred (see FIG. 16). This is because the blood flow velocity can be uniformly and reliably reduced at each part in the axial direction of the blood outflow side opening 25A.

The presence of the first enlarged portion 282A increases the gap distance of the blood outflow side opening 25A. That is, when the gap distance t at the portion where the first enlarged portion 282A of the blood outflow side opening 25A does not exist is used as a reference, the gap distance t1 of the portion where the first enlarged portion 282A is formed (in the fourth embodiment). (corresponding to _tmax ) is larger than the gap distance t. t1 / t is preferably about 1.05 to 12, more preferably about 1.05 to 10. Moreover, t1-t is preferably about 0.05 to 20 mm, more preferably about 0.1 to 10 mm.

  When t1 / t or t1-t is within the numerical range as described above, the blood flow is slowly decelerated by the first enlarged portion 282A, and contributes to an improvement in the effect of preventing the discharge of bubbles from the blood outflow port 28. To do.

  Here, the distance t2 between the filter member 41A and the inner surface 280 outside the blood outflow port 28 is the sum (t1 + C) of t1 and the offset C (see FIG. 15).

  The width (groove width) of the first enlarged portion 282A is not particularly limited, but when viewed from the side surface on the side where the blood outflow port 28 of the cylindrical housing body 21A is formed (when viewed from below in FIG. 15) When the width (length of the chord) of the formation region of the first enlarged portion 282A (when viewed from the front of FIG. 16) is W, W is 35 to 99% of the inner diameter (diameter) of the cylindrical housing body 21A. The degree is preferable, and about 45 to 75% is preferable. When W is within such a numerical range, the blood flow is slowly decelerated by the first enlarged portion 282A, which contributes to an improvement in the effect of preventing the discharge of bubbles from the blood outflow port 28.

  On the other hand, the second enlarged portion 282B is the same as the channel enlarged portion 281 (the channel enlarged portion 281 formed at the root of the blood outflow port 28) in the third embodiment.

  In the artificial lung 10 ″ of the present embodiment, the blood flowing toward the downstream side through the blood flow path (gap between the hollow fiber membranes 31 of the hollow fiber membrane bundle 3A) 33 flows into the hollow fiber membranes 31 of the hollow fiber membrane bundle 3A. Gas exchange (oxygenation and decarbonation gas) is performed with the gas flowing through the gas flow path (inner cavity of the hollow fiber membrane 31) 32, and reaches the filter member 41A. The blood that sequentially passes through the membrane bundle 3A and the filter member 41A and enters the blood outflow side opening 25A flows in the blood outflow side opening 25A toward the first enlarged portion 282A along the circumferential direction thereof. At this time, since the width of the blood flow path is increased from t to t1, the blood flow rate is reduced, and the blood that has flowed into the first enlarged portion 282A further flows into the first enlarged portion. 282A toward the center in the longitudinal direction (Towards the second enlarged portion 282B) and flows into the second enlarged portion 282B, at which time the blood flow rate is also reduced, and then the blood flows through the blood outflow port 28 and out of the housing 2A. leak.

When bubbles are mixed in the blood flowing through the blood flow path 33, the bubbles are captured by the filter member 41A. Bubbles (bubble constituent gas) captured by the filter member 41A pass through a large number of pores formed in the wall portion of the hollow fiber membrane 31 on the upstream side (inside) of the filter member 41A, and the hollow fiber membrane 31 Enter the lumen (gas flow path 32). The bubble constituent gas that has entered the lumen of the hollow fiber membrane 31 is discharged from the gas outflow port 27 to the outside of the housing 2A through the first chamber 221a.
In addition, with respect to the gas exchange with respect to the blood as described above, the subsequent blood flow, the action of removing and discharging bubbles in the blood, etc., other embodiments (fifth and sixth) that do not have the hollow fiber membrane layer for exhaustion. The same applies to the eighth, ninth and tenth embodiments).

<Eighth Embodiment>
FIG. 17 is a cross-sectional view showing an eighth embodiment of the oxygenator of the present invention.
Hereinafter, the eighth embodiment of the oxygenator according to the present invention will be described with reference to this drawing. However, the difference from the third embodiment will be mainly described, and the description and illustration of the same matters will be omitted. .

  The oxygenator 1 of the present embodiment is the same as that of the third embodiment except that the exhaust hollow fiber membrane layer 42A and the exhaust port (exhaust port) 29 are not present. That is, the filter member 41A has its inner peripheral surface provided in contact with the downstream surface (blood outflow portion side) of the hollow fiber membrane bundle 3A. In the present embodiment, the bubble removing means 4A is composed of a filter member 41A.

  Further, in the present embodiment, since the exhaust port 29 does not exist, the partition portions 222 and 232 are not provided.

<Ninth Embodiment>
FIG. 18 is a cross-sectional view showing a ninth embodiment of the oxygenator of the present invention.
Hereinafter, the ninth embodiment of the oxygenator of the present invention will be described with reference to this drawing. However, the description will focus on the differences from the fourth embodiment described above, and the description and illustration of the same matters will be omitted. .

  The oxygenator 1 of this embodiment is the same as that of the fourth embodiment except that the exhaust hollow fiber membrane layer 42A and the exhaust port (exhaust port) 29 are not present. That is, the filter member 41A has its inner peripheral surface provided in contact with the downstream surface (blood outflow portion side) of the hollow fiber membrane bundle 3A. In the present embodiment, the bubble removing means 4A is composed of a filter member 41A.

  Further, in the present embodiment, since the exhaust port 29 does not exist, the partition portions 222 and 232 are not provided.

<Tenth Embodiment>
FIG. 19 is a cross-sectional view showing a tenth embodiment of the oxygenator of the present invention.
Hereinafter, the tenth embodiment of the oxygenator according to the present invention will be described with reference to this drawing. However, the description will focus on the differences from the seventh embodiment described above, and the same matters will not be described and illustrated. .

  The oxygenator 100 of the present embodiment is the same as that of the seventh embodiment (FIGS. 15 and 16) except that the configuration of the flow path enlargement unit 282 is different.

That is, the flow path expanding portion 282 in the present example is configured by the first expanded portion 282A similar to that described in the seventh embodiment, and there is no equivalent to the second expanded portion 282B.
Preferred values such as the width W of the first enlarged portion 282A, t1 / t, and t1-t are the same as those described in the seventh embodiment.

  In this embodiment, the distance t2 between the filter member 41A and the inner surface 280 outside the blood outflow port 28 is equal to t1, that is, the offset C (= t2-t1) is 0 (see FIG. 19).

  As described above, the illustrated embodiments of the oxygenator of the present invention have been described. However, the present invention is not limited to these embodiments, and each component constituting the oxygenator may have any configuration that can exhibit the same function. Can be substituted, and arbitrary constituents may be added.

  For example, regarding the structure and shape of the housing and the heat exchanger housing, the formation position and the protruding direction of the gas inflow port, gas outflow port, blood outflow port, blood inflow port, heat medium inflow port and heat medium outflow port for each housing The configuration shown in FIG. Further, the posture (positional relationship of each part with respect to the vertical direction) when using the artificial lung is not limited to the state shown in the figure.

Next, specific examples of the present invention will be described.
Example 1
FIG. 15 and FIG. 16 are artificial lungs (seventh embodiment) having three types (varieties 1, 2, and 3) having different sizes of a cylindrical housing body (outer cylinder) and a hollow fiber membrane bundle. Lungs were manufactured. Details of the structure of the oxygenator are shown in Table 1.

  As shown in FIG. 15, the outer cylinder of the oxygenator is formed with a second enlarged portion of the flow channel enlarged portion at the base of the blood outflow port, and further, as shown in FIG. In the vicinity of the second enlarged portion, a groove-shaped first enlarged portion extending along the longitudinal direction of the outer cylinder is formed. Hollow fiber membranes are those used in Capiox (“Capiox” is a registered trademark) RX25, RX15, RX05 commercially available from Terumo Corp. (The hollow fiber membrane is spirally wound around the central axis of the housing. The same is applied).

  As the filter member, a sheet-like mesh made of polyester and having a thickness of 70 μm was used.

(Example 2)
Variety 4, which is an artificial lung (tenth embodiment) configured as shown in FIG. 19, was manufactured. Details of the structure of the oxygenator are shown in Table 1.

  As shown in FIG. 19, the outer cylinder of the artificial lung has a groove-shaped first enlarged portion extending along the longitudinal direction of the outer cylinder on the inner peripheral surface of the outer cylinder. The hollow fiber membrane and the filter member constituting the hollow fiber membrane bundle are the same as those in Example 1.

(Comparative Example 1)
Capiox (“Capiox” is a registered trademark) RX25 (variety 5), RX15 (breed 6), RX05 (breed 7) commercially available from Terumo Corp. was used as an artificial lung for comparison. These do not have an exhaust hollow fiber membrane layer and a filter member.

  Further, as shown in FIG. 20, the tangent to the inner peripheral surface of the outer cylinder and the inner surface 280 outside the blood outflow port coincide with each other. That is, each oxygenator of Comparative Example 1 does not have a flow path expanding portion (second expanding portion) and does not have a first expanding portion. Details of the structure of the oxygenator are shown in Table 1.

(Comparative Example 2)
An artificial lung (variety 8) similar to the breed 5 of Comparative Example 1 was produced except that the same filter member as used in Example 1 was installed on the outer peripheral surface of the hollow fiber membrane bundle. The conditions of the artificial lung of Comparative Example 2 are shown in Table 1 below.

<Bubble removal performance test>
The following air bubble removal performance tests were performed on the artificial lungs (types 1 to 8) of Examples 1 and 2 and Comparative Examples 1 and 2.

  Each artificial lung of varieties 1 to 8 was incorporated into a blood extracorporeal circuit, and blood of an experimental animal (bovine blood, hematocrit value = 35%, blood temperature = 37 ° C.) was circulated at a flow rate shown in Table 2 below. A bubble containing various bubbles with different bubble diameters was mixed just before the blood inlet port of the oxygenator, and the amount of bubbles in the blood flowing out from the blood outlet port was measured by the bubble detector under the following conditions. The results are shown in Table 2 below.

Bubble detection time: 1 minute Number of bubbles: Bubbles measured with a bubble detector were divided into ranges of 10 μm bubble diameter, and the number of each bubble was counted.

  As shown in Table 2, it was confirmed that each of the artificial lungs (types 1 to 4) of Examples 1 and 2 had high bubble removal performance. In particular, each artificial lung (variety 1 to 3) of Example 1 in which the flow path expanding portion is configured by the first expanding portion and the second expanding portion has no bubble outflow regardless of the size of the bubble diameter, The bubble removal performance was extremely high.

  On the other hand, in the artificial lung of Comparative Example 1 (variety 5 to 6) in which the filter member and the flow path enlargement portion are not present, the outflow of bubbles having a bubble diameter of 80 μm or less is particularly significant, and the removal of bubbles is larger than in Examples 1 and 2. The performance was inferior.

  In addition, in the artificial lung of the comparative example 2 (variety 8) provided with the filter member but having no flow passage expanding portion, the outflow of bubbles is somewhat suppressed by the presence of the filter member as compared with the breed 5 of the comparative example 1. However, the bubble removal performance is still inferior to Examples 1 and 2.

  From the above, both the filter member and the flow path expanding portion (particularly, those having the first expanded portion and the second expanded portion) are provided rather than the filter member and the flow path expanded portion. In such a case, it was found that the bubble removal performance was remarkably improved by the synergistic effect of combining these.

1 is a perspective view showing a first embodiment of an oxygenator according to the present invention. It is the sectional view on the AA line (cross-sectional side view) in FIG. It is a cross-sectional view (cross-sectional top view) of the oxygenator part in the oxygenator shown in FIG. FIG. 3 is an enlarged cross-sectional view of a lower right portion (a fixing portion of a hollow fiber membrane bundle, a filter member, and an exhaust hollow fiber membrane layer) in FIG. 2. It is a longitudinal cross-sectional view (cross-sectional side view) which shows 2nd Embodiment of the oxygenator of this invention. It is a top view which shows 3rd Embodiment of the oxygenator of this invention. It is the figure (left side view) which looked at the oxygenator shown in FIG. 6 from the arrow B side. It is CC sectional view taken on the line in FIG. It is the DD sectional view taken on the line in FIG. It is the EE sectional view taken on the line in FIG. FIG. 10 is an enlarged cross-sectional view of an upper right portion (a fixing portion of a hollow fiber membrane bundle, a filter member, and an exhaust hollow fiber membrane layer) in FIG. 9. It is a cross-sectional view showing a fourth embodiment of the oxygenator of the present invention. It is a longitudinal cross-sectional view (cross-sectional side view) which shows 5th Embodiment of the oxygenator of this invention. It is a longitudinal cross-sectional view (cross-sectional side view) which shows 6th Embodiment of the oxygenator of this invention. It is a cross-sectional view showing a seventh embodiment of the oxygenator of the present invention. It is a perspective view of the cylindrical housing main body in the oxygenator of 7th Embodiment. It is a cross-sectional view showing an eighth embodiment of the oxygenator of the present invention. It is a cross-sectional view showing a ninth embodiment of the oxygenator of the present invention. It is a cross-sectional view showing a tenth embodiment of the oxygenator of the present invention. It is a cross-sectional view of the cylindrical housing main body in the artificial lung of a comparative example.

Explanation of symbols

1, 1 ', 10, 10', 10 ", 100 Artificial lung 1A, 10A Artificial lung 1B, 10B Heat exchanger (heat exchanger)
2, 2A Housing 21 Square tubular housing main body 21A Cylindrical housing main body 211 Wall portion 22, 22A First header 221, 221a First chamber 222 Partition portion 223 Small space 23, 23A Second header 231, 231a Second Room 232 Partition 233 Small space 24, 24A Blood inflow side opening 25, 25A Blood outflow side opening 26 Gas inflow port 261 Gas inflow chamber 27 Gas outflow port 271 Gas outflow chamber 28 Blood outflow port (blood outflow port)
281 Channel expansion portion 280 Outside inner surface 282 Channel expansion portion 282A First expansion portion 282B Second expansion portion 29 Exhaust port (exhaust port)
DESCRIPTION OF SYMBOLS 201 Blood inflow port 202 Heat medium inflow port 203 Heat medium outflow port 3, 3A Hollow fiber membrane bundle 31 Hollow fiber membrane 32 Gas flow path (luminal of hollow fiber membrane)
33 Blood channel 4, 4A Bubble removing means 41, 41A Filter member 42, 42A Exhaust hollow fiber membrane layer 421 Hollow fiber membrane (exhaust hollow fiber membrane)
422 Gas flow path 5, 5A Heat exchanger housing 50 Blood chamber 51 Blood inflow port 52 Heat medium inflow port 53 Heat medium outflow port 54 Heat exchanger 55 Heat medium chamber forming member 56 Partition wall 57 Inflow side heat medium chamber 58 Outflow side Heat medium chamber 59a Opening 59b Opening 59c Opening 7 Fixed part 8, 9 Partition t Gap distance t1 Gap distance _tmin Minimum gap distance _tmax Maximum gap distance C Offset

Claims (7)

A housing;
A hollow fiber membrane bundle in which a plurality of hollow fiber membranes housed in the housing and having a gas exchange function are integrated,
Using the lumen of each hollow fiber membrane as a gas flow path, a gas inflow part and a gas outflow part respectively provided on the upstream side and the downstream side of the gas flow path,
With the outside of each hollow fiber membrane as a blood flow path, a blood inflow portion and a blood outflow portion provided on the upstream side and the downstream side of the blood flow path,
An artificial lung having air bubble removing means provided on the blood outflow portion side of the hollow fiber membrane bundle and provided with a filter member having a function of capturing air bubbles in blood,
The blood outflow portion has a tubular blood outlet that protrudes from the housing, and has a flow passage enlargement portion that increases the cross-sectional area of the flow passage in the vicinity of the housing side end of the blood outlet. The artificial lung, wherein the blood that has passed through the filter member is configured to decelerate the flow velocity at the flow channel enlargement portion and reach the blood outlet.   The artificial lung according to claim 1, wherein the filter member has a mesh shape.   The blood outflow portion has a blood outflow side opening formed between an inner surface of the housing and the filter member, and the blood outflow side opening and the blood outflow port are interposed via the flow path expanding portion. The oxygenator according to claim 1 or 2, which is in communication with each other.   The artificial lung according to claim 3, further comprising a part where a gap distance between the inner surface of the housing and the filter member is continuously or stepwise increased on the downstream side of the blood outflow side opening.   The artificial lung according to any one of claims 1 to 4, wherein the flow path expanding portion includes a first expanding portion on the upstream side and a second expanding portion subsequent thereto.   The artificial lung according to claim 5, wherein the first enlarged portion is configured by a groove formed over substantially the entire length of the housing in the longitudinal direction.   The artificial lung according to any one of claims 1 to 4, wherein the flow path expanding portion has a first expanded portion configured by a groove formed over substantially the entire length in the longitudinal direction of the housing.

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