JPH07178166A - Artificial organ - Google Patents

Abstract

PURPOSE:To obtain an artificial organ having limited side effects on a living body by a method in which a body fluid permeable membrane having a specific solubility parameter delta is used for the artificial organ and vitamin E is coated on the surface of a portion of the body fluid permeable membrane to be in contact with a body fluid so that the body fluid permeable membrane has an improved affinity to vitamin E and does not melt out into blood. CONSTITUTION:Body fluid permeable membranes of hollow fiber membranes 16 having a solubility parameter delta of 13 (cal/cm<3>)<1/2> or less are used for an artificial organ, and coatings 17 of vitamin E are applied essentially to the surfaces of portions of the body fluid permeable membranes to be in contact with a body fluid. Consequently, the body fluid permeable membranes have an improved affinity to vitamin E which is a fat-soluble vitamin, and do not melt out into blood, so that an artificial organ having limited side effects on a living body and improved biocompatibility can be obtained. Further, the obtained artificial organ is capable of reducing the amount of residual blood, preventing generation of activated oxygen and various diseases caused by activated oxygen.

Description

Detailed Description of the Invention

[0001]

FIELD OF THE INVENTION The present invention relates to an artificial organ. More specifically, the present invention relates to artificial organs such as artificial kidneys, artificial lungs, and blood separation devices that suppress activation of white blood cells or platelets and have excellent biocompatibility.

[0002]

2. Description of the Related Art Conventionally, artificial organs such as artificial kidneys, artificial lungs and plasma separators have been used, and synthetic polymer membranes have been widely used in dialysis membranes, gas exchange membranes, blood component separation membranes and the like. . However, for example in artificial kidneys,
Since hemodialysis is frequently performed, activation of white blood cells or platelets causes complications, which is a serious problem for dialysis patients. In particular, it has been confirmed that the blood antioxidant in patients who are on hemodialysis for a long period of time is low, and the value of lipid peroxide is high. Therefore, arteriosclerotic diseases are increasing in long-term dialysis patients.

On the other hand, in order to solve this problem, an artificial organ in which the surface of a dialysis membrane is coated with a vitamin E coating having various physiological actions such as in vivo antioxidant action, biological membrane stabilizing action and platelet aggregation inhibiting action. Has been proposed (Japanese Patent Publication Sho 62
No. 41738). However, when vitamin E is coated on the surface of a hydrophilic material, elution into blood is observed at the time of blood inflow, and it has been confirmed that about 90% of vitamin E elutes into blood 30 minutes after blood circulation. The persistence of the effects of vitamin E is a problem.

Further, the higher the solubility parameter δ, the stronger the hydrophilicity, and when the dialysis membrane is a hydrophilic material, the affinity with the fat-soluble vitamin Vitamin E is poor.
Solubility parameter δ is 15.65 (cal / cm ³ ) ^1/2
The regenerated cellulose, which is, has a problem that elution into blood occurs when the blood enters.

[0005]

SUMMARY OF THE INVENTION It is an object of the present invention to provide an artificial organ which has a good affinity for vitamin E which is a fat-soluble vitamin, suppresses elution into blood, and has few side effects on the living body. It is in.

[0006]

In order to solve the above problems, the artificial organ of the present invention is an artificial organ having a body fluid permeable membrane, and the body fluid permeable membrane has a solubility parameter δ of 13
(Cal / cm ³ ) ^1/2 or less, and at least the surface of the body fluid permeable membrane that can come into contact with body fluid is coated with vitamin E.

Further, the artificial organ of the present invention is preferably formed by coating vitamin E on at least the surface of the body fluid flow region in the artificial organ which is in contact with the body fluid.

In the artificial organ of the present invention, the body fluid permeable membrane is preferably a hollow fiber type membrane.

Further, in the artificial organ of the present invention, the body fluid permeable membrane is preferably a synthetic polymer membrane having hydrophobicity or a hydrophobic portion.

Further, in the artificial organ of the present invention, the body fluid permeable membrane is polyethylene, polymethyl methacrylate, polystyrene, polypropylene, polysulfone, polyhydroxyethyl methacrylate, nylon 66, cellulose acetate, polyacrylonitrile, polyvinyl alcohol, ethylene-vinyl alcohol. A hollow fiber type membrane made of at least one polymer material selected from a copolymer and a polycarbonate is preferable.

In the biocompatible artificial organ of the present invention, the body fluid permeable membrane has a vitamin E coating amount of 1 to 1000 mg / m ^3.
Is preferred.

The artificial organ in the present invention means an artificial kidney,
An artificial liver, an artificial lung, a plasma separator, a blood circuit, an artificial blood vessel, etc. that has a body fluid circulation region for circulating body fluid such as blood in an artificial organ. It is preferably a membrane. The artificial organ includes not only a tube and a connector for connecting a living body to the artificial organ, but also other blood circuits and the like.

Further, the solubility parameter δ in the present invention
Represents the degree of affinity with vitamin E, and indicates that when the solubility parameter δ is high, the hydrophilicity is strong, and when the solubility parameter δ is low, the hydrophobicity is strong. Furthermore, when the solubility parameter δ is 13 (cal / cm ³ ) ^1/2 or less, the affinity for vitamin E is good and the hydrophobicity.
For the calculation method of the solubility parameter δ, see, for example, Polymer Handbook (Basic Edition, pages 591 to 59).
It is described in many documents such as page 3).

[0014]

Embodiments of the present invention will be described in detail below with reference to the accompanying drawings.

FIG. 1 shows an example of an artificial kidney, that is, a dialyzer of a hollow fiber type membrane. In this dialyzer 1, a hollow fiber bundle 5 made up of a large number of hollow fibers is inserted into a tubular body 4 which is provided with an inlet pipe 2 and an outlet pipe 3 for dialysate near both ends, and then both ends thereof are made of polyurethane. The potting agents 6 and 7 are used to seal both ends of the cylindrical body 4 together. Further, headers 10 and 11 each having an inflow port 8 and a discharge port 9 for body fluid are respectively brought into contact with both ends of the cylindrical main body 4, and the cap 12,
The headers 10 and 11 and the tubular main body 4 are fixed by 13 respectively. Further, tubes 14 and 15 for connecting to a human body are connected to the body fluid inlet port 8 and the body fluid outlet port 9 at both ends of the tubular body 4.

The hollow fibers constituting the hollow fiber bundle 5 are dialysis membranes and are, for example, polyethylene (δ = 7.70), polymethylmethacrylate (δ = 9.10), polystyrene (δ = 9.15). , Polypropylene (δ = 9.40),
Polysulfone (δ = 9.90), Polyhydroxyethyl methacrylate (δ = 10.00), Nylon 66 (δ
= 11.18), cellulose diacetate (δ = 11.1.
35), polyacrylonitrile (δ = 12.35), polyvinyl alcohol (δ = 12.60), cellulose triacetate, ethylene-vinyl alcohol copolymer,
Solubility parameter δ such as polycarbonate is 13 (ca
Any film may be used as long as it is 1 / cm ³ ) ^1/2 or less.

According to the present invention, a portion of the artificial kidney as described above that comes into contact with body fluid, for example, blood in the blood circulation region, for example, the inner surface of the hollow fiber membrane, the inner surface of the space formed by the header 10 and the potting agent 6, The inner surface of the space formed by the header 11 and the potting agent 7, the inner surface of the blood inlet 8, the inner surface of the blood outlet 9, the inner surfaces of the tubes 14 and 15,
In particular, the inner surface of the hollow fiber membrane is coated with vitamin E. For example, in a hollow fiber type membrane, as shown in FIG. 2, the inner surface of the hollow fiber membrane 16 is coated with a vitamin E coating 17.

The vitamin E used in the present invention is fat-soluble and, for example, tocopherols such as α-tocopherol, β-tocopherol, γ-tocopherol, δ-tocopherol, α-tocotrienol, β-tocotrienol, γ-tocopherol. There are tocotrienols such as tocotrienol and δ-tocotrienol. Also, vitamin E
The film thickness of the film is 0.001 to 1.0 μm, preferably 0.01 to 0.3 μm. When the film thickness is 0.001 μm or less, the biocompatibility effect obtained by coating with vitamin E is unlikely to appear, and the film thickness is 1.0 μm
In the above cases, dialysis performance may decrease.

Further, the coating amount of vitamin E is 1 to 10
The amount is 00 mg / m ³ , preferably 10 to 300 mg / m ³ . When the amount of vitamin E coated is 1 mg / m ³ or less, the vitamin E coating is likely to be uneven and the biocompatibility effect is reduced. Further, when the amount is 1000 mg / m ³ or more, the film thickness of vitamin E becomes thick and the elution of vitamin E and the dialysis performance may decrease.

0.01-20 w of such vitamin E
/ V%, preferably 0.1 to 10 w / v% as an organic solvent solution, and allowed to flow into the body fluid flow region of the artificial organ (blood flow region in the case of the artificial kidney shown in FIGS. 1 and 2) for a predetermined time. , For example, 30 seconds to 60 minutes, preferably by contacting for 1 to 10 minutes, the inner surface of the body fluid flow region, for example,
Inner surface of hollow fiber membrane, inner surface of space formed by header 10 and potting agent 6, inner surface of space formed by header 11 and potting agent 7, inner surface of blood inlet 8 and inner surface of blood outlet 9, tube Inner surface of 14, 15
Especially, the vitamin E is well spread on the inner surface of the hollow fiber membrane. Then, after discharging the solution, a gas inert to the vitamin E, for example, air, nitrogen, carbon dioxide gas or the like is introduced at a temperature of 10 to 80 ° C., preferably 15 to 30 ° C. to introduce an organic solvent. Is removed by evaporation to form a film of vitamin E on the contact surface, and further washed with water if necessary. In this case, the coating operation may be performed without connecting the tubes 14 and 15 to form the vitamin E coating on the main portion, particularly the permeable membrane portion.

The organic solvent used in the present invention is one that is insoluble in the synthetic polymer film, such as methanol, ethanol, n-propanol, isopropanol, n-butanol, isobutanol, sec-butanol, Alcohols such as 2-ethylhexanol, diethyl ether, etc. or, for example, 1,2,2-trichloro-1,2,2-trifluoroethane, trichlorofluoromethane, 1,1,2,2-tetrachloro-1, 2-
Chlorinated fluorohydrocarbons such as difluoroethane or the like, for example, methyl fluoride, carbon tetrafluoride, tetrafluoroethane,
Perfluorocycloalkanes such as tetrafluoroethylene, perfluoromethylpropylcyclohexane and perfluorobutylcyclohexane, and fluorocarbons such as perfluorodecane, perfluoromethyldecalin and perfluoroalkyltetrahydropyran.

Although the artificial kidney, which is mainly a dialyzer, has been described above, other artificial liver, artificial lung,
It can also be used in plasma separators, blood circuits, artificial blood vessels and the like, and if a vitamin E coating is formed on a site having a permeable membrane for body fluids, especially blood, a remarkable effect can be obtained.

Next, embodiments of the present invention will be described in more detail with reference to the accompanying drawings.

(Example 1) Inner diameter of about 200 μm, outer diameter of about 2
80 μm, length about 14 cm, solubility parameter δ9.9
Using 341 0 (cal / cm ³ ) ^1/2 polysulfone hollow fibers, as shown in FIG. 1, inserted into the cylindrical main body 1 and fixed at both ends with polyurethane potting agents 6 and 7, and further at both ends Attach headers 10 and 11 to the cap 1
A dialyzer (artificial kidney) 1 was prepared by fixing with 2 and 13. The internal surface area of the dialyzer 1 is 3
It was 00 cm ³ .

On the other hand, 1.0 g of vitamin E (DL-α-tocopherol) was dissolved in 100 ml of ethanol to adjust the concentration of the ethanol solution of vitamin E to 1 w / v%. Then, a 50 ml syringe was connected to one end of the dialyzer 1, the other end was immersed in a solution of vitamin E, and the plunger of the syringe was operated to fill the dialyzer with the solution of vitamin E. In this state, it was left at room temperature for 2 minutes. Next, after pulling up the dialyzer to discharge the solution of vitamin E, an aspirator was connected, nitrogen gas was blown at a temperature of 25 ° C. to dry, and ethanol was removed.
Furthermore, in order to ensure complete drying, the sample was left in an oven at 60 ° C. overnight. The vitamin E coating amount in the dialyzer thus obtained was 0.63 mg.

(Example 2) Using the same polysulfone hollow fiber as in Example 1, the concentration of vitamin E in the ethanol solution of vitamin E was 5 w / v%, and a dialyzer was manufactured by the same method as in Example 1. . The amount of vitamin E coated in this dialyzer was 3.13 mg.

Example 3 Inner diameter about 250 μm, outer diameter about 3
Using 273 hollow polyacrylonitrile (hereinafter, simply referred to as PAN) 20 μm and a length of about 14 cm,
Adjust the concentration of vitamin E in the ethanol solution of vitamin E to 5
A w / v% was set and a dialyzer was manufactured by the same method as in Example 1. The membrane surface area of this dialyzer is 300c
At m ³ , the vitamin E coating amount in the dialyzer is 4.1.
It was 9 mg.

Example 4 10 g of polysulfone was dissolved in 20 ml of dichloromethane and precipitated in 200 ml of methanol for purification. The resulting precipitate was filtered and dried at 60 ° C. 4.5 g of purified polysulfone and 0.25 g of polyvinylpyrrolidone are added to 25 ml of dimethylacetamide.
After being dissolved in a glass plate, 100μ on a glass plate of 10 × 10cm
It was cast at a thickness of m and solidified in a water bath. The obtained flat membrane of polysulfone was thoroughly washed with water and then dried at 60 ° C. Then, the flat membrane of polysulfone was immersed in an ethanol solution containing 5 w / v% of vitamin E for 5 minutes, and then the flat membrane was pulled up and blow-dried at a temperature of 25 ° C. further,
To ensure complete drying, it was left in an oven at 60 ° C overnight. The amount of vitamin E coated in the dialyzer thus obtained was 0.72 mg at 50 cm ³ .

(Comparative Example 1) For comparison, an inner diameter of about 2
A dialyzer was manufactured by the same method as in Example 1, using 341 regenerated cellulose hollow fibers having a diameter of 00 μm, an outer diameter of about 240 μm, and a length of about 14 cm, and the concentration of vitamin E in the ethanol solution of vitamin E was 5 w / v%. did. The membrane surface area of this dialyzer was 300 cm ³ , and the amount of vitamin E coating in the dialyzer was 3.25 mg.

Comparative Example 2 For comparison and comparison, Example 1 was used.
Using a polysulfone hollow fiber similar to that described above, a dialyzer was produced by the same method as in Example 1 without treatment with an ethanol solution of vitamin E.

(Comparative Example 3) As a comparative control, Example 4 was used.
A polysulfone flat membrane was produced in the same manner as in Example 4, except that the same polysulfone as in Example 1 was used and the solution was not treated with an ethanol solution of vitamin E.

(Experimental Example 1) Examples 1 to 3 and Comparative Example 1
The amount of vitamin E eluted in plasma was examined using a dialyzer of No.

First, 500 ml of bovine blood was dispensed into a 50 ml polypropylene test tube and centrifuged at 3000 rpm for 15 minutes to obtain 200 ml of bovine plasma. Furthermore, 50
50 ml of bovine plasma was dispensed into a polypropylene test tube of ml, and the test tube containing bovine plasma was connected to the blood inlet 8 of the dialyzer 1 with a vinyl chloride tube 14 via a pump, and the blood outlet of the dialyzer 1 was connected. 9 and the test tube containing bovine plasma are connected by a vinyl chloride tube 15,
An experimental circuit was prepared. And the test tube containing bovine plasma is 37
Keep in a constant temperature bath at ℃, pump 10 ml / m of bovine plasma
The amount of vitamin E eluted into bovine plasma after 4 hours was measured by circulating the dialyzer at a flow rate of in for 4 hours.

The amount of vitamin E eluted in plasma was measured as follows.

First, 1 ml of bovine plasma after the end of circulation was collected, and 1 ml of ethanol was added thereto and mixed for 30 seconds to remove the protein in bovine plasma. Next, 5 ml of hexane was added and mixed for 1 minute to transfer vitamin E in bovine plasma to the hexane layer. This was centrifuged at 1500 rpm for 10 minutes, and the amount of vitamin E in the upper hexane layer was quantified by liquid chromatography. The measurement conditions for liquid chromatography are:
Column: Amide-80, 4.6 x 25 cm (Tosoh T
SK gel), n-hexane: i-propanol = 98: 2 as a moving layer, flow rate: 1.5 ml / min, injection amount: 10 μl, detection: UV monitor 292 nm
I went there.

Table 1 shows the measurement results of the amount of vitamin E eluted in plasma of Experimental Example 1.

[0037]

[Table 1]

Experimental Example 2 Examples 1 and 2 and Comparative Example 2
In order to evaluate the biocompatibility of vitamin E using the dialyzer of No. 3, a rabbit extracorporeal circulation experiment was performed, and the number of hollow fibers in which blood remained in the hollow fibers after completion of extracorporeal circulation was examined.

First, the rabbit was fixed on its back on a Kitajima type fixed base, the hair of the surgical field was shaved with an electric hair clipper, and wiped with alcoholic cotton. Then, make an incision along the midline from below the jaw to the clavicle with scissors and open the fascia, taking care not to damage the nerves, branch vessels, and surrounding tissues.
The common carotid artery was dissected. The left (right) facial vein was then carefully removed as well. Then, with the blood vessel clamped, a Surflow (registered trademark of Terumo Corp.) indwelling needle made by Terumo Corp. with a mixed rubber cap filled with physiological saline was inserted into the vein and fixed by ligation. further,
One side (venous side) of the circuit was connected to the venous side of a dialyzer filled with physiological saline by a vinyl chloride tube filled with physiological saline. Similarly, an indwelling needle was inserted into the artery, fixed by ligation, and then connected to the arterial side of the dialyzer via a pump using a vinyl chloride tube filled with physiological saline.

Using the rabbit extracorporeal circuit, an extracorporeal circulation experiment was conducted as follows.

First, the blood vessel was unclamped, and the pump was kept at a flow rate of 10 ml / min to perform extracorporeal circulation for 2 hours. After the circulation is completed, the arteriovenous blood vessels are clamped again,
The arterial side circuit and the venous side circuit were cut at a portion near the indwelling needle. Then, 50 ml of physiological saline is pumped for 10 m.
The inside of the circuit and the dialyzer was cleaned by making a single pass at a flow rate of 1 / min. After cleaning, cut the hollow fibers at the center of the dialyzer, count the number of hollow fibers with residual blood with a microscope, and determine the residual blood ratio by the total number of hollow fibers in the dialyzer and the number of hollow fibers with residual blood. It was calculated.

Table 2 shows the calculation results of the residual blood rate after the end of extracorporeal circulation in Experimental Example 2.

[0043]

[Table 2]

(Experimental Example 3) Using the flat membranes of Example 4 and Comparative Example 3 made of polysulfone, the emission intensity integrated value was measured to evaluate the amount of active oxygen produced.

First, 20 U / ml heparinized human blood was treated with 6% dextran T-70 in a physiological saline solution at a ratio of 9: 1.
The mixture was gently mixed at a ratio of 2 and left standing upside down for about 2 hours. Then, the supernatant was gently collected and leukocyte phagocytic cells in this supernatant were treated with Hank's ballance salt solution at 1 × 10 ⁶ ce.
It was adjusted to 11 / ml and used as a test solution. Then, a 40 cm ² flat membrane and 1.2 ml of the test solution were added to the cuvette so that the entire membrane was immersed in the test solution. The cuvette was made of glass and was previously silicone-coated with NCT-911 (Toshiba Silicone).
Furthermore, 0.1 mM 2-methyl-6 (-
10 μl of p-methoxyphenol) -3,7-dihydroimidazo (-1,2-a) -pyrazin-3-one was added, and the integrated value of luminescence intensity was immediately measured with a luminescence reader at 37 ° C. for 15 minutes. Further, the integrated value of the emission intensity of only the cuvette was measured for comparison and control.

Table 3 shows the measurement results of the integrated value of the emission intensity for evaluating the active oxygen production amount of Experimental Example 3.

[0047]

[Table 3]

Table 1 showing the experimental results of the above Experimental Examples 1 to 3.
It can be seen from Table 3 that in Table 1, the cellulose membrane of Comparative Example 1 has a solubility parameter δ of 15.70 (cal / cal).
cm ³ ) ^1/2 and high hydrophilicity, 88% of vitamin E coating amount was eluted in plasma circulation. On the other hand, the polysulfone membranes of Example 1 and Example 2 have a solubility parameter δ of 9.90 (cal / cm ³ ) ^1/2 and also have a hydrophobic portion, so that elution of vitamin E into plasma is completely observed. However, it is strongly immobilized by a hydrophobic-hydrophobic bond with vitamin E. The solubility parameter δ of the PAN membrane of Example 3 is 12.35 (cal / cm ³ ) ^1/2 , but the elution rate of vitamin E is about 1%, which is a slight elution rate compared to the cellulose membrane. there were.

In Table 2, the residual blood rate of the polysulfone membrane not treated with vitamin E of Comparative Example 2 was 37.9%, whereas the polysulfone treated with 1 w / v% of vitamin E of Example 1 was used. The residual blood rate was 27.0% in the membrane, and the residual blood rate was 18.6% in the polysulfone membrane treated with 5 w / v% of vitamin E of Example 2, clearly indicating that vitamin E inhibits platelet aggregation. Due to the action, the residual blood rate after extracorporeal circulation in rabbits is reduced, and it shows excellent biocompatibility.

In Experimental Example 3, the hollow fiber shape includes the outer surface (inner surface) of the hollow fiber that does not come into contact with blood. I did this, but this is the inner surface (outer surface) of the hollow fiber membrane
There is no substitute for measuring only. In Table 3,
The emission intensity integrated value of the polysulfone film not treated with vitamin E of Comparative Example 3 was 378 kcpm, while that of Experimental Example 4
The integrated emission value of the polysulfone film treated with Vitamin E is 203 kcpm, and it is clear that the amount of active oxygen produced by the film stimulation is suppressed by coating Vitamin E. Furthermore, the integrated value of the emission intensity of only the cuvette is 192 kcpm.
It can be seen that the difference from the integrated value of the emission intensity of the polysulfone film treated in step 1 is slight. Therefore, it is considered that by coating with vitamin E, production of active oxygen is suppressed, and it is possible to reduce various diseases caused by active oxygen.

Although the present embodiment has been described above using the polysulfone hollow fiber membrane and the polyacrylonitrile (PAN) hollow fiber membrane, the present invention is not limited to this, and the solubility parameter δ is 13 (cal / cm). ³ ) Membranes of ^1/2 or less may be used, and not limited to hollow fiber membranes, flat membranes and the like may be used.

[0052]

As described above, the artificial organ of the present invention is an artificial organ having a body fluid permeable membrane, and the body fluid permeable membrane has a solubility parameter δ of 13 (cal / cm).
³ ) ^1/2 or less, and at least the surface of the body fluid permeable membrane that can come into contact with body fluid is coated with vitamin E. By improving the affinity and suppressing elution into blood, it is possible to provide an artificial organ with few side effects on the living body and improved biocompatibility. Furthermore, the residual blood rate can be reduced. In addition, production of active oxygen is suppressed, and various diseases caused by active oxygen can be reduced.

Further, the artificial organ of the present invention is characterized in that at least the surface of the body fluid flow region in the artificial organ which is in contact with the body fluid is coated with vitamin E, whereby the biocompatibility is further improved. It can improve and reduce the residual blood rate. Furthermore, production of active oxygen is suppressed.

Further, the artificial organ of the present invention is characterized in that the body fluid permeable membrane is a hollow fiber type membrane, so that the effective membrane area is increased and the dialysis property is improved.

Further, the artificial organ of the present invention is characterized in that the body fluid permeable membrane is a hydrophobic or synthetic polymer membrane containing a hydrophobic portion, thereby further improving the affinity with vitamin E and It is possible to suppress the elution to the above and improve the biocompatibility.

In the biocompatible artificial organ of the present invention, the body fluid permeable membrane has a vitamin E coating amount of 1 to 1000 mg / m ^3.
The biocompatibility can be improved without causing unevenness in the vitamin E coating and without lowering the dialysis performance.

[Brief description of drawings]

FIG. 1 is a perspective view showing a part of a dialyzer showing an embodiment of the present invention.

FIG. 2 is a vertical cross-sectional view of a hollow fiber membrane showing an example of the present invention.

[Explanation of symbols]

 1 dialyzer 2 dialysate inlet pipe 3 dialysate outlet pipe 4 tubular body 5 hollow fiber membrane 6,7 potting agent 8 body fluid inlet 9 body fluid outlet 10,11 header 12,13 cap 14,15 tube 16 hollow fiber membrane 17 Film

Front page continued (72) Inventor Hideki Watanabe 1500 Inoguchi, Nakai-cho, Ashigarakami-gun, Kanagawa Terumo Corporation

Claims (1)

[Claims] 1. An artificial organ having a body fluid permeable membrane, wherein the body fluid permeable membrane has a solubility parameter δ of 13 (cal / cal).
cm ³ ) ^1/2 or less, and an artificial organ characterized in that at least the surface of the body fluid permeable membrane that can come into contact with body fluid is coated with vitamin E.