JPH03218771A - Blood treating device and its production - Google Patents

Abstract

PURPOSE:To improve the adaptability to blood and the suppression of the generation of a thrombosis by subjecting the blood-contact surfaces of partition walls to a corona discharge treatment, then coating the surfaces with a hydrophilic resin. CONSTITUTION:The blood-contact surfaces of the partition walls 10, 11 of a blood treating device, such as artificial lung, artificial dialyzer or plasma separator, for example, the hollow yarn membrane type artificial lung 1 having a housing 6, a hollow yarn membrane 2 for gas exchange which is the member for blood treatment inserted into the housing 6, the partition walls 10, 11 which liquidtightly fix both ends of the hollow yarn membrane bundle to both ends of the housing 6, a gas inflow port 13 and gas outflow port 14 which are respectively provided near both ends of the housing 6 and communicate with the space (oxygen chamber 12) formed of the outside surface of the hollow yarn membrane 2, the inside surface of the housing 6, and the partition walls, and a blood inflow port 29 and blood outflow port 28 which are respectively mounted to both ends of the housing 6, are subjected to the corona discharge treatment at the blood contact surfaces of the partition walls 10, 11 and are coated with the hydrophilic resin 40.

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] The present invention relates to a blood processing device and a method for manufacturing the same. In detail, there are artificial lungs that circulate blood through blood processing components and perform gas exchange such as adding oxygen and removing carbon dioxide, artificial dialyzers that perform hemodialysis, heat exchangers that exchange heat, and blood The present invention relates to a blood processing device such as a plasma separator that performs separation, and a manufacturing method thereof.

[Prior Art] Conventionally, for example, a hollow fiber membrane type artificial dialyzer has been used as a blood processing device.The general structure thereof is that a large number of dialyzers are placed in a cylindrical housing having an inlet and an outlet for dialysate. A hollow fiber membrane bundle consisting of hollow fiber membranes for dialysis is inserted,
Both ends of this hollow fiber membrane bundle are fluid-tightly fixed to both ends of the cylindrical housing by partition walls formed with a bonoting agent, and a canopy forming a blood inlet and a blood outlet outside the partition wall. Goo is attached to the state of the body. As hollow fiber membranes for dialysis, hollow fiber membranes such as cuprammonium cellulose, regenerated cellulose such as cellulose acetate, and polyacrylic nitrile are used, and polyurethane or the like is used as the potting agent.

In JP-A-58-175567, a thermoplastic polymer coating layer is provided on the blood-contacting surface of the partition wall in order to prevent the formation of blood clots on the blood-contacting surface of the polyurethane forming the partition wall, and further, A hollow fiber membrane type blood treatment device has been disclosed in which heparin is immobilized on this thermoplastic resin via a graft copolymer containing diglycidyl methacrylate as a component.

[Problems to be Solved by the Invention] The thermoplastic resins used in the blood treatment device disclosed in the above-mentioned Japanese Patent Application Laid-Open No. 175567/1982 include hydrophobic resins such as silicone, Teflon, and segmented polyether urethane. It is disclosed that hydrophilic resins such as ethyl cellulose, cellulose diacetate, and ethylene-vinyl acetate copolymers can be used.

However, when a hydrophobic resin is used as the thermoplastic resin, an organic solvent in which the hydrophobic resin can be dissolved is used, and a hydrophobic resin solution containing the organic solvent is brought into contact with the blood contacting surface of the septum by a method such as coating. There must be. However, it is difficult to bring this hydrophobic resin solution into contact with only the blood-contacting surface of the septum, and it also comes into contact with the hollow fiber membrane for blood treatment.
There is a problem that the hollow fiber membrane in the contact portion deteriorates.

In addition, when a hydrophilic resin is used, an aqueous liquid (water, alcohol, or a mixture thereof) can be used as the solvent, so the hollow fiber membrane will not be degraded by the organic solvent as described above. On the other hand, since the resin used is hydrophilic, it is not possible to uniformly coat the blood-contacting surface of the partition wall, which is made of polyurethane and has a water-repellent surface, with the hydrophilic resin. For this reason, the hydrophilic resin can only be partially attached, and instead, minute irregularities are formed on the blood contact surface of the septum, resulting in the problem that blood compatibility cannot be improved and thrombus formation cannot be suppressed. .

Therefore, the present invention solves the above problems and eliminates the use of hydrophobic resins that require the use of organic solvents that may deteriorate the hollow fiber membrane, which is a blood processing member, and uses hydrophilic resins. An object of the present invention is to provide a blood processing device in which the blood contacting surface of a partition wall for fixing a blood processing member to a housing is uniformly coated, thereby improving blood compatibility and thrombus occurrence, and a method for manufacturing the same.

Means for Solving Problem L] The object of the present invention described above is achieved by a housing, a blood processing member inserted into the housing, and both ends of the blood processing member being connected to both ends of the housing. a first fluid provided near both ends of the housing and communicating with a space formed by one surface of the blood processing member, the inner surface of the housing, and the partition; A blood processing device having an inlet and an outlet, and a blood inlet and a blood outlet respectively attached to both ends of the housing, wherein the blood contacting surface of the partition wall is corona discharge treated and hydrophilic. This is a blood processing device coated with resin.

Preferably, heparin is immobilized on the surface of the hydrophilic resin. Furthermore, the hydrophilic resin is
It is preferable that the blood contact surface of the blood processing member that is in contact with the partition wall is also coated. Further, the blood processing member is, for example, a porous blood processing membrane or a hemodialysis membrane. Moreover, the porous membrane for blood treatment or the membrane for hemodialysis is, for example, a hollow fiber membrane or a flat membrane. Furthermore, the hydrophilic resin has a hydroxyl group, an amino group,
Contains or can be easily converted into a carboxyl group, an epoxy group, an incyanate group, an epoxy group, a thiocyanate group, an acid chloride group, an aldehyde group, and a carbon-carbon double bond It is preferable that it has a group.

Further, what achieves the above object includes a housing, a blood processing member inserted into the housing, and a partition wall that liquid-tightly fixes both ends of the blood processing member to both ends of the nozzling. , a first fluid inlet and an outlet that are respectively provided near both ends of the housing and communicate with a space formed by one surface of the blood processing member, the inner surface of the housing, and a partition; In the method for manufacturing a blood processing device having a blood inlet and a blood outlet respectively attached to both ends of the nozzing, the blood contacting surface of the partition wall of the blood processing device is subjected to a corona discharge treatment, and then This is a method for manufacturing a blood treatment device, in which the corona discharge treated blood contact surface is brought into contact with a hydrophilic resin solution dissolved in an aqueous solvent.

Preferably, the corona discharge treatment and the contact with the hydrophilic resin solution are also carried out on the blood contacting surface of the blood processing member that is in contact with the partition wall. Furthermore, after contacting with the hydrophilic solution, it is preferable to contact with a heparin solution to fix heparin.

Therefore, an embodiment in which the blood processing device of the present invention is applied to a hollow fiber membrane oxygenator will be described with reference to the drawings.

A hollow fiber membrane oxygenator 1 to which the blood processing device of the present invention is applied is as follows:
A housing 6, a hollow fiber membrane 2 for gas exchange which is a blood processing member inserted into the housing 6, and a partition wall 10 that fixes both ends of the hollow fiber membrane bundle to both ends of the housing 6 in a fluid-tight manner.
．． 11 and a space (oxygen chamber 12
) and a blood inlet 2 attached to both ends of the housing 6, respectively.
9 and a blood outlet 28, and furthermore, the blood contacting surface of the partition 10.11 is treated with corona discharge and coated with a hydrophilic resin.

Therefore, a specific explanation will be given using FIGS. 1 to 3.

This hollow fiber membrane oxygenator 1 includes a cylindrical housing 6,
60,000 hollow fiber membranes 2 for gas exchange are housed throughout the housing 6.

This hollow fiber membrane 2 for gas exchange is a porous membrane and has a large number of micropores 3 passing through it. The hollow fiber membrane for gas exchange has an inner diameter of 100 to 1000 μm, preferably 100 μm.
~300μl3 wall thickness 5-80μ shoulder, preferably lO~6
0μ shoulder, porosity 20-80%, preferably 30-60%
, and the pore diameter of the micropores is 0.01 to 5μ, preferably 0.
．． A material having a diameter of about 0.01 to 1 μm is preferably used. Also,
The membrane is not limited to a hollow fiber membrane, but may be a flat membrane.

As the material of the hollow fiber membrane 2 for gas exchange, hydrophobic polymers such as polypropylene, polyethylene, polytetrafluoroethylene, polysulfone, polyacrylonitrile, and cellulose acetate can be used. Hydrophobic polymers are preferable, and particularly Preferably, it is a polyolefin resin, more preferably polypropylene, and preferably polypropylene in which micropores are formed by a stretching method or a solid-liquid phase separation method.

To specifically describe the structure of the hollow fiber membrane oxygenator of this embodiment, both ends of the hollow fiber membrane are fluid-tightly fixed to the housing 6 by partition walls 10 and 11 with their respective openings not being closed. .

Due to the partition wall 10.11, the inside of the housing 6 has an oxygen chamber 12, which is a first mass transfer chamber formed by the outer wall of the hollow fiber membrane, the inner wall of the housing 6, and the partition wall, and an oxygen chamber 12 formed inside the hollow fiber membrane. It is divided into a blood circulation space which is a second mass transfer chamber.

The housing 6 is provided with an inflow port 13 for a gas containing oxygen near one end thereof, and an outflow port 14 near the other end thereof.

Furthermore, a flow path forming member 19 having a blood inflow port 29 and an annular convex portion 25 is fixed to the outside of the partition wall 11 with a sealing ring 23, and a blood flow path forming member 19 having a blood outflow port 28 and an annular convex portion is fixed to the outside of the partition wall 10. A flow path forming member 18 having a portion 24 is fixed by a screw ring 22 .

Then, the convex portion 24 of the flow path forming member I8, 19. 25 is the partition wall 10. 11, and this convex portion 24.
At the outer periphery of the ring 22. At least two holes 30, 31, 3 provided in each of 23
The sealing agent is filled from one of the flow path forming members 18. 19 is fixed in a liquid-tight manner to the partition wall 10.11.

In the above explanation, the threaded ring is used, but the flow path forming member may be directly fused to the housing using high frequency waves, ultrasonic waves, etc., or may be bonded using an adhesive or the like. You may. Further, instead of the above sealant, an O-ring made of silicone rubber or the like may be used to liquid-tightly seal the flow path forming member to the partition wall. The partition wall 10.11 is formed of a polymeric ponoting agent, such as polyurethane, silicone, or epoxy resin.

In addition, the forms of membrane oxygenators are limited to the above-mentioned hollow fiber membranes, one in which flat membrane-shaped gas exchange membranes are laminated, and one in which one flat membrane-shaped hollow fiber membrane for gas exchange is wound into a coil shape. It may be a flat-membrane oxygenator, such as a double-layered oxygenator or a zigzag-folded oxygenator.

The partition wall portion of the hollow fiber membrane oxygenator shown in FIG. 1 has been subjected to corona discharge treatment. ), hydroxyl group, carbonyl group,
Carboxyl groups etc. are formed. Then, by introducing the above-mentioned hydrophilic groups onto the surface of the partition wall, the surface of the partition wall becomes hydrophilic, albeit temporarily.

As shown in FIG. 2, which is an enlarged sectional view of the partition wall portion of the hollow fiber membrane oxygenator in FIG. The end face is coated with a hydrophilic resin 40. More specifically, as shown in FIG.
The resin (for example, polyurethane) forming the partition wall is mixed in the pores of the hollow fiber membrane 2 in the portion that is in contact with the inner surface of the hollow fiber membrane 2 or the vicinity thereof is exposed. Therefore, on the inner surface of the portion that contacts the partition wall 10, the resin forming the partition wall 10 comes into contact with blood. In the present invention, it is preferable that the hydrophilic resin 40 is also coated on the end face of the partition wall 1O and the partition wall portion that contacts the hollow fiber membrane 2 and is exposed near the inner surface of the hollow fiber membrane 2. This improves blood compatibility throughout the septum.

Furthermore, as shown in FIGS. 2 and 3, it is preferable that the hydrophilic resin coats the end face of the partition wall 1O and the entire inner surface of the partially hollow fiber membrane 2 that contacts the partition wall 1o.

Hydrophilic resins include polyalkyl sulfone, ethyl cellulose, acrylic ester polymers, methacrylic ester polymers (for example, polyHEMA [polyhydroxyethyl methacrylate]), and both hydrophobic and hydrophilic segments. (e.g. block copolymers of HEMA-styrene-HEMA, HEMA-MMA [block copolymers of methyl methacrylate, HEMA-LMA])
[Lauryl methacrylate] Nofloc copolymer, P
A block copolymer of VP [polyvinylpyrrolidone]-MMA, a blend polymer obtained by mixing this block copolymer with a polymer having 7 amino groups), a fluorine-containing resin, and the like can be used. Preferably HEMA-
Styrene-HEMA block copolymer, HEMA-M
MA is a block copolymer of methyl methacrylate, and a blend polymer in which this block copolymer is further mixed with a polymer having an amino group. In addition, as a polymer having an amino group, polyamino, especially PE
I [polyethinimine] is preferred.

In order to fix heparin, which is an anticoagulant described later, on the surface of this hydrophilic resin, the hydrophilic resin must contain hydroxyl groups, amine 7 groups, carboxyl groups, epoxy groups, incyanate groups, epoxy groups, and thiocyanate groups. , an acid chloride group, an aldehyde group, and a carbon-carbon double bond, or a group that can be easily converted into these groups.

Then, an anticoagulant 4 is applied to the surface of the hydrophilic resin 40.
2. For example, it is preferable that heparin is immobilized. This heparin fixation is carried out by bringing an aqueous heparin solution into contact with the surface of the hydrophilic resin 40, and then adding aldehydes such as glutaraldehyde, terephthalaldehyde, and formaldehyde, diphenylmethane diisocyanate, 2,4
Tolylene diisocyanate, carbodiimide modified diphenylmethane diisocyanate, shrimp chlorohydrin, 1
, 4-butanediol diglycidyl ether, polyethylene glycol diglycidyl ether, or the like, and is easily immobilized by covalent bonding to the above-mentioned hydrophilic resin.

This hollow fiber membrane oxygenator 1 is then sterilized before use. For sterilization, known methods such as ethylene oxide gas sterilization and radiation sterilization are used.

In the above explanation, the blood processing device of the present invention was explained using an example in which the blood processing device of the present invention was applied to an artificial lung. A processing member (a dialysis membrane in an artificial dialysis machine, a plasma separation membrane in a plasma separator, and a heat exchange tube in a heat exchanger) is fixed to the housing by a partition wall made of synthetic resin, and the partition wall is It can be applied to any blood processing device that has a contact surface.

Next, a method for manufacturing a blood processing device of the present invention will be explained using the above-mentioned hollow fiber membrane oxygenator.

First, a cylindrical housing 6 having a gas inlet 13 and a gas outlet l4 on its side wall is created, and a hollow fiber membrane bundle 2 made of a large number of hollow fiber membranes for gas exchange, which is a member for blood treatment, is placed inside the housing. insert. After the hollow fiber membranes 2 at both ends of the hollow fiber membrane bundle 2 are uniformly dispersed, a container filled with a filler is fitted onto both ends of the hollow fiber membrane bundle 2, and this container is then It is fixed to the end of the housing 6. Further, a gas inlet 13 and a gas outlet 14 of the housing 6
After centrifugally injecting a potting agent (for example, polyurethane), fixing each end of the hollow fiber membrane bundle to the housing 6, and removing the container, the potting agent portion is sliced and each partition wall 10.11 is form. Then, the formed end face of the partition wall is subjected to a corona discharge treatment using a corona discharge treatment device to make the blood contacting surface of the partition wall hydrophilic. In the corona discharge treatment, for example, as shown in FIG. 4, a metal rotary plate 50 serving as a ground and a wire electrode 52 provided thereon are used.
A high voltage source that outputs a voltage of several tens of kV, for example, a corona generator 62;
A corona discharge treatment device 60 is used, which is connected to a high voltage transformer 63 that converts electric power from the source into high voltage.

Then, as shown in FIG. 4, near the end of the rotary plate 50, the artificial lung 1 formed as described above is placed in an upright state. The rotation speed of the rotating plate is 0.01 to 0.
Approximately 5 rps is preferable, and when the oxygenator 1 is placed,
The distance between the end surface of the partition wall of the oxygenator 1 and the wire electrode 52 is 0.
5-5. OI level is preferable. Furthermore, the processing power when the artificial lung 1 is located directly below the wire electrode 52 is preferably about 50 to 100 W. In addition, processing speed (
The speed at which the oxygenator passes under the wire electrode) is 0.0
1~0. About 11/s is preferable.

This corona discharge treatment may be performed once, but preferably several times, specifically 2 to 20 times. and,
After completing the corona discharge treatment on one partition surface, the oxygenator 1
is reversed and corona discharge treatment is applied to the partition wall on the opposite side.

Next, the corona discharge-treated partition wall portion is immersed in a hydrophilic resin solution, and the end surfaces of the partition wall and the inside of the hollow fiber membrane in the portion that contacts the partition wall are filled with the hydrophilic resin solution, and the excess is removed. The hydrophilic resin solution is removed (for example, air is pumped into the hollow fiber membrane to push it out, and excess resin solution on the end face is also removed with compressed air), dried, and the blood contacting surface of the septum is coated with hydrophilic resin. do. In addition, if the hydrophilic resin solution does not flow into the hollow fiber membrane with the above immersion alone, close the gas inlet and outlet, attach a suction device to the opposite partition wall, and It may also be caused to flow in by suctioning. Moreover, if the hydrophilic resin solution does not adhere to the hollow fiber membrane sufficiently in the above-mentioned one-time operation, the above-mentioned operation may be performed multiple times as appropriate. Then, by performing the same operation on the partition wall portion on the opposite side, the blood contacting surface of each partition wall is coated with a hydrophilic resin. As the hydrophilic resin, those mentioned above can be suitably used. Then, the flow path forming member 18 and the flow path forming member 19 are attached to the outer side of the partition wall 10.11 with a threaded ring 22.
Fix it using 23. and a heparin aqueous solution, preferably at pH 2. 5 to 6.0 is allowed to flow in from the blood inlet 29, the inside of the oxygenator 1 is filled with a heparin aqueous solution, and the blood inlet 29 and the blood outlet 28 are sealed, preferably,
Appropriate time 10 minutes to 24 minutes at room temperature to 70°C
Leave it for a while. Then, after draining the heparin aqueous solution,
A glutaraldehyde solution (preferably one having the same pn as the aqueous heparin solution) is added to the blood inlet 28 of the oxygenator l.
Blood inflow port 29 and blood outflow port 2
8 is sealed and left for an appropriate period of 30 minutes to 24 hours to fix the heparin.

[Example] Next, an embodiment of the blood processing device of the present invention will be described.

[Example 1] A cylindrical housing (inner diameter 58xu, length 120xm) having a gas inflow port and an outflow port near the end and having a shape as shown in FIG. 1 was made of polycarbonate. Then, inside the above housing, an inner diameter of about 200μ is placed.
l1 Wall thickness: approx. 25μ shoulder, porosity: approx. 45%, average pore diameter: approx. 70
Approximately 12,000 polypropylene hollow fiber membranes are inserted into the housing. After the hollow fiber membranes at both ends of the hollow fiber membrane bundle are uniformly dispersed, a container filled with a filler is fitted onto both ends of the hollow fiber membrane bundle, and this container is then placed at the end of the housing. be fixed to the section. Furthermore, polyurethane is centrifugally injected from the gas inlet and gas outlet of the housing, and each end of the hollow fiber membrane bundle is fixed to the housing.
After removing the container, the potting agent portion was sliced to form each partition wall. The thickness (maximum part) of the partition wall was 18 zm. Then, the end face of the partition wall thus formed is placed near the end of the rotating plate 50 of the corona discharge treatment device 60 (HVO5-2 system manufactured by TANTEC AS Co., Ltd.), as shown in FIG. was placed and subjected to corona discharge treatment. Note that the corona discharge treatment conditions are such that the rotation speed of the rotary plate 50 is 0. lrps
, the distance between the end surface of the septum of the oxygenator 1 and the wire electrode 52 is 2.
mm, processing voltage 28kV (corona generator)
62 is converted by the high voltage transformer 63), and the processing power when located directly under the wire electrode 52 is 79W.
The processing was performed 10 times in succession at a processing speed of 0.06 m/s. Then, the oxygenator was turned over, and the other partition wall was similarly subjected to corona discharge treatment. After corona discharge treatment, 2
After a few minutes, the corona discharge-treated partition wall portion was immersed in a hydrophilic resin solution. As the hydrophilic resin solution, P(HEMA
) (average molecular weight 15,000) and polyethyleneimine (average molecular weight 200,000) are each 1.25
A 1.0% by weight mixed methanol/methyl cellosolve/water (10.6/1.0/0.4) solution was used. For immersion in the hydrophilic resin solution, place the above hydrophilic resin solution in a petri dish, and soak the partition wall of the oxygenator for 3 seconds.
The fibers were immersed for 10 seconds, pulled up, and dried by blowing air into the hollow fibers from the opposite side to the end faces of the partition walls. The other partition wall portion was also treated in the same manner. Then, after fixing the flow path forming member to the outside of each partition using a screw ring, pH 4.0 (0.
A 0.5% aqueous heparin solution (1M acetate buffer) was allowed to flow in from the blood inlet, the heparin aqueous solution was filled inside the oxygenator, the blood inlet and outlet were sealed, and the mixture was left at 45°C for 4 hours. , the heparin aqueous solution was drained. Subsequently, the pH
A 2.5% glutaraldehyde aqueous solution of 4.0 (001M acetate buffer) was injected into the oxygenator through the blood inlet, the blood inlet and outlet were sealed, and the oxygenator was incubated at 37°C for 12 hours.
The heparin was fixed by leaving it for an hour.

In this way, the hydrophilic resin is fixed on the blood-contacting surface of the septum and heparin is fixed on the surface of the membrane with a membrane area of 0. 8m”
A hollow fiber membrane oxygenator as shown in Figure 1 was constructed.

(Comparative Example) A hollow fiber membrane oxygenator with a membrane area of 0.8 m' was prepared in the same manner as in the example except that the corona discharge treatment was not performed.

(Example 2) Length 198I, end inner diameter 441l shoulder, middle inner diameter 32m
Inside the housing made of polycarbonate, the inner diameter is approximately 200 mm.
Approximately 7,100 dialysis hollow fiber membranes made of copper ammonia cellulose with μ shoulders and a wall thickness of approximately 12 μm were inserted, and their ends were fixed using polyurethane to form a partition wall. The length of the longest part of the partition wall (the part that contacts the housing) is 15131
Met. Then, corona discharge treatment as in Example 1,
A hydrophilic resin coating and heparin fixation were performed to create an artificial dialysis machine with a membrane area of approximately 08 m'.

[Experiment 1] The partition wall portions of the hollow fiber membrane oxygenators of Example 1 and Comparative Example and the artificial dialyzer of Example 2 were made to a thickness of approximately 2.5 mm. The membrane was sliced into 5xx pieces, and the partition wall portion thus sliced was then cut vertically to expose the inner surface of the hollow fiber membrane. A staining test was conducted using them. As a dye... Basic dye (toluidine blue, Mw:
305.8) was used to prepare a 0.04 w/v% toluidine blue solution, and the slices sliced at the partition wall were immersed in the solution for 3 minutes. After that, they were thoroughly washed with water. Observation was made using -2-T. A slice of the septum of an artificial lung in a comparative example shows
It was dyed purple in spots, and the hydrophilic resin was not evenly coated over the entire surface. Furthermore, the inner surface of the hollow fiber membrane in the portion that was in contact with the polyurethane was hardly colored and was hardly coated with the hydrophilic resin.

In contrast, in the slices of the septum of the artificial lung of Example 1 and the artificial dialysis machine of Example 2, the entire end surface of the septum is uniformly dyed purple, and the hydrophilic resin is uniformly dyed over the entire end surface of the septum. It was found that it was covered with Furthermore, the inner surface of the hollow fiber membrane in the portion in contact with polyurethane was also almost uniformly colored, indicating that the hydrophilic resin was also coated on the inner surface of the hollow fiber membrane in the portion in contact with polyurethane.

[Experiment 2] The partition walls of the hollow fiber membrane oxygenator of Example 1, the comparative example, and the artificial dialyzer of Example 2 were sliced to a thickness of approximately 51 cm, and the surface condition of the end surface of the partition was determined as follows: Observation was made using a scanning electron microscope (JSM 803, manufactured by JEOL Ltd.). As a result, roughness due to slicing was observed on the end face of the partition wall in the comparative example, but in Examples 1 and 2, the surface was smooth.

[Effects of the Invention] The liquid treatment device of the present invention includes a housing, a blood processing member inserted into the housing, and a partition wall that liquid-tightly fixes both ends of the blood processing member to both ends of the housing. and a first fluid inlet and an outlet, which are respectively provided near both ends of the housing and communicate with a space formed by one surface of the blood processing member, the inner surface of the housing, and the partition wall; A blood processing device having a blood inlet and a blood outlet respectively attached to both ends of the housing, wherein the blood contacting surface of the partition wall is corona discharge treated and coated with a hydrophilic resin. Therefore, it is not necessary to use hydrophobic resins that require the use of organic solvents that may cause deterioration of the blood processing member.Furthermore, hydrophilic resins are used on the blood contacting surface of the partition wall that fixes the blood processing member to the housing. Because it is uniformly coated on the skin, it has excellent blood compatibility and inhibits thrombosis.

Further, the method for manufacturing a blood processing device of the present invention includes a housing, a blood processing member inserted into the housing, and a partition wall that liquid-tightly fixes both ends of the blood processing member to both ends of the housing. a first fluid inlet and a first fluid outlet, which are provided near both ends of the housing and communicate with a space formed by one surface of the blood processing member, the inner surface of the housing, and the partition; 4. In the method for manufacturing a blood processor having a blood inlet and a blood outlet respectively attached to both ends of the housing, the blood contacting surface of the partition wall of the blood processor is subjected to a corona discharge treatment, and then the Since the blood contacting surface treated with corona discharge is brought into contact with a hydrophilic resin solution dissolved in an aqueous solvent, a blood processing device having excellent blood compatibility and thrombus generation prevention as described above can be easily produced. be able to.

[Brief Description of the Drawings] Fig. 1 is a partial sectional view of an embodiment in which the blood processing device of the present invention is applied to a hollow fiber membrane oxygenator, and Fig. 2 is a partial cross-sectional view of an embodiment of the hollow fiber membrane type oxygenator shown in Fig. 1. FIG. 3 is an enlarged sectional view of the partition wall portion of the hollow fiber membrane type artificial dialyzer shown in FIG. It is a diagram showing an example of a corona discharge treatment device used for manufacturing. ■...Blood processing device, 2...Hollow fiber membrane, 6...
Housing, 10.11... Partition wall l3... Gas inlet, l4... Gas outlet, 28... Blood outlet,
29...Blood inlet, 40...Hydrophilic resin, 4
2... Anticoagulant, 50... Rotating plate, 52...
・Wire electrode, 60...Corona discharge treatment device, 62...Corona generator 63...High voltage transformer Fig. 2 Fig. 8

Claims (9)

[Claims] (1) A housing, a blood processing member inserted into the housing, a partition wall that liquid-tightly fixes both ends of the blood processing member to both ends of the housing, and a partition wall provided near both ends of the housing, respectively. a first fluid inlet and an outlet, which are provided and communicate with a space formed by one surface of the blood processing member, an inner surface of the housing, and a partition; and a first fluid inlet and an outlet, which are attached to both ends of the housing, respectively. 1. A blood processing device having an inlet and a blood outlet, wherein the blood contacting surface of the partition wall is subjected to a corona discharge treatment and coated with a hydrophilic resin. (2) The blood treatment device according to claim 1, wherein heparin is immobilized on the surface of the hydrophilic resin. (3) The blood processing device according to claim 1 or 2, wherein the hydrophilic resin is also coated on a blood contacting surface of the blood processing member that is in contact with the partition wall. (4) The blood processing device according to any one of claims 1 to 3, wherein the blood processing member is a porous membrane for blood processing or a membrane for hemodialysis. (5) The porous membrane for blood processing or the membrane for hemodialysis,
The blood processing device according to any one of claims 1 to 4, which is a hollow fiber membrane or a flat membrane. (6) The hydrophilic resin includes a hydroxyl group, an amino group, a carboxyl group, an epoxy group, an isocyanate group, an epoxy group,
Any one of claims 1 to 5, which has any one of a thiocyanate group, an acid chloride group, an aldehyde group, and a carbon-carbon double bond, or a group that can be easily converted into these groups. Blood processing equipment. (7) a housing, a blood processing member inserted into the housing, a partition wall that liquid-tightly fixes both ends of the blood processing member to both ends of the housing, and a partition wall provided near both ends of the housing, respectively; a first fluid inlet and an outlet, which are provided and communicate with a space formed by one surface of the blood processing member, an inner surface of the housing, and a partition; and a first fluid inlet and an outlet, which are attached to both ends of the housing, respectively. In a method for manufacturing a blood processing device having an inlet and a blood outflow port, the blood contacting surface of the partition wall of the blood processing device is subjected to a corona discharge treatment, and then the corona discharge treated blood contacting surface is soaked in an aqueous solvent. 1. A method for producing a blood treatment device, which comprises bringing it into contact with a dissolved hydrophilic resin solution. (8) The method for manufacturing a blood processing device according to claim 7, wherein the corona discharge treatment and the contact with the hydrophilic resin solution are also performed on a blood contacting surface of the blood processing member that is in contact with the partition wall. (9) The method for manufacturing a blood processing device according to claim 7 or 8, wherein after contacting with the hydrophilic solution, contacting with a heparin solution is performed to fix heparin.