JPH05103827A - Living body implant member coated with biologically active apatite film - Google Patents

Abstract

PURPOSE:To obtain a living body implant member enhanced in the compatibility with a living body, capable of ensuring sufficient strength and having the large degree of freedom in planning by constituting the adhesive layer of the living implant member of an org. polymer and an inorg. filler satisfying a specific condition. CONSTITUTION:A part of an implant member 11 is dipped in an org. polymer solution 6 containing an inorg. filler 5 wherein 80wt.% or more thereof has a particle size of 3-100mum and the wt. ratio thereof to an org. polymer is 1-30 and having good adhesiveness to the member 11. Next, the member 11 is dried under vacuum and subsequently immersed in a substantially saturated or supersaturated aqueous solution A7 of a hydroxyapatite component to be allowed to stand in a thermostatic tank at predetermined temp. and taken out of the thermostatic tank to be washed with distilled water and dried to form a film 11 of hydroxyapatite similar to a bone on the surface of the region having come into contact with the org. polymer solution 6 of the member 11. By this method, the compatibility with a living body is enhanced and strength can sufficiently be ensured and the planning degree of freedom is increased.

Description

Detailed Description of the Invention

[0001]

[Field of Industrial Application] The present invention is
When injecting a drug for life support and treatment from outside the body using a catheter, etc., when it is embedded in the body or a member located at the connection part that connects the body and the outside of the body, and when the drug solution is injected deep inside the body The present invention also relates to a bioimplant member that serves as an injection port of the above and further to a bioimplant member that substitutes and repairs a defect portion of hard tissue such as bone.

[0002]

2. Description of the Related Art Recent research and development relating to implant members have been remarkable, and new materials have been developed for orthopedic members, artificial tooth roots, etc. as well as artificial organs. Among them, hydroxyapatite is known to be a specific material that has high bioactivity and is integrated with bone, and has been attracting attention. Therefore, many inventions relating to implant materials using this material have been announced, and Japanese Patent Application Laid-Open No. 3-1.
No. 86272 discloses a member in which a ceramic material such as alumina or zirconia, pure titanium, or a titanium alloy is coated with a calcium phosphate-based material such as hydroxyapatite to be implanted in bone.

Further, in Japanese Patent Publication No. 2-13580,
A technique is disclosed in which a biomedical terminal made of a hydroxyapatite sintered body is used in a portion connecting the inside and outside of the body when extracting in-vivo information to the outside. Japanese Utility Model Publication No. 3-19884 also discloses a technique relating to a bioapatite terminal of hydroxyapatite produced from a bone of a living organism.

Japanese Unexamined Patent Publication (Kokai) No. 3-32676 discloses a technique relating to zirconia or a composite of alumina and hydroxyapatite in order to improve the fact that hydroxyapatite has a low strength and hinders its practical use. ing.

Further, Japanese Patent Publication No. 2-13580 discloses a method for producing hydroxyapatite, and Japanese Patent Publication No. 58-50737 discloses a ceramic method for plasma spraying on a metal implant. Regarding the plasma spraying method on the core material, Japanese Patent Publication No. 59-4691
No. 1, JP-A-62-34559, JP-A-62.
-57548, JP-A-63-46165, and the like.

Regarding the sputtering method, Japanese Patent Laid-Open No. 58-58
No. -109049 gazette, and regarding the flame spraying method, the proceedings of the first autumn symposium of the Japan Ceramic Society 1988, P. It is disclosed in P401 to 402. The baking method using glass frit is disclosed in the 9th Biomaterials Society Conference Proceedings (1987, P6).

Further, regarding the electrophoresis method, the Japan Ceramic Society 1988 P. It is disclosed in P417 to 418.

Regarding the method of precipitating hydroxyapatite from an artificial body fluid in which the kind and concentration of ions are the same as that of human plasma, Japanese Patent Publication No. 62-10939, Japanese Patent Publication No. 1-54290, and Japanese Patent Laid-Open No. 54290/1989. It is disclosed in Japanese Patent Publication No. 2-255515.

[0009]

Conventionally, many techniques have been disclosed as described above with respect to a bioimplant member, particularly a bioimplant member coated with a bioactive apatite film and a method for producing the same, but the following techniques A to A are still available. There are many problems as shown in F.

(A) The plasma spraying method requires a complicated and expensive apparatus, it is difficult to form a dense film, and since the raw material hydroxyapatite is once melted at a high temperature, it is different from the apatite in the living body. The formation of an apatite film may be mentioned.

(B) The sputtering method requires complicated and expensive equipment, and since the raw material hydroxyapatite is once melted at a high temperature, an apatite film of a different type from the apatite in the living body is formed. Can be mentioned.

(C) The sintering method and the glass frit method are 85
Since it needs to be heat-treated at a temperature of 0 ° C. or higher, it can be applied only to a highly heat-resistant substrate, and since the raw material hydroxyapatite is once treated at a high temperature, it is a kind of apatite film different from that in vivo. Is formed. Further, when a terminal is made of a sintered body, the strength of hydroxyapatite is low, so that the structure and shape are greatly restricted.

(D) Since the electrophoretic method uses the substrate itself as an electrode, it can be applied only to a metal substrate of good conductivity, and since sintered apatite is used as a raw material, it is also apatite in vivo. Films of different apatite are formed.

(E) In the method of depositing from artificial body fluid, the substrate that adheres well to the produced hydroxyapatite is CaO /
There is a problem that it has not been found other than SiO ₂ glass. (F) As a measure for solving some of the problems described above, it has been conventionally known that an epoch-making implant member can be produced by coating an organic polymer with hydroxyapatite having substantially the same composition as that of a living body. However, since the problem that the hydroxyapatite and the organic polymer cannot obtain sufficient adhesive strength has not been solved, this attempt has not been realized.

The present invention has been made by the present inventors as a result of extensive studies to solve the above problems, particularly the problem of the term F, and has excellent compatibility with living organisms and sufficient strength is secured. It is an object of the present invention to provide a bioimplant member that can be manufactured and has a high degree of freedom in design.

[0016]

A bioimplant member coated with a bioactive apatite film according to the present invention is obtained by immersing a substrate coated with an adhesive layer in an aqueous solution of hydroxyapatite component having a substantially saturated or supersaturated concentration. A bioimplant member in which a bone-like hydroxyapatite film is formed on the back surface of the base material by doing, and the adhesive layer contains an organic polymer and an inorganic filler powder as main components,
This inorganic filler has a diameter within the range of 3 to 100 μm.
It is contained in an amount of 1% to 30 by weight, and the weight ratio to the organic polymer is 1 to 30.

As a concrete constitution of the invention, several means shown below are effective for achieving the above-mentioned object.
That is, the film thickness of hydroxyapatite formed on the surface of the base material is preferably 3 to 100 μm. The inorganic fillers include barium sulfate, lead sulfate, barium carbonate, calcium carbonate,
Silicon dioxide, bismuth tungstate, the main component is CaO
It is convenient to use a glass powder of SiO ₂ and SiO ₂ or a mixture containing them as a main component. Further, it is preferable that the base material and the organic polymer are the same material. Furthermore, the average thickness of the film when dried on an organic polymer substrate containing an inorganic filler and having good adhesiveness to the substrate is 5 to 100 μm.
Is desirable.

The means constituting the present invention as described above can be simply described in terms of manufacturing process as follows. That is, in order to obtain a biomedical implant member having excellent compatibility with a living body, sufficient strength, and a large degree of freedom in design, “80% by weight or more of the material is contained in the range of 3 to 100 μm in diameter. "Inorganic filler powder" is a saturated or supersaturated concentration after dipping the base material in "organic polymer solution that adheres well to the base material" with a weight ratio of 1 to 30 when dried. It suffices to form a bone-like hydroxyapatite film on the surface of the substrate by immersing it in the component aqueous solution.

[0019]

In the present invention, the diameter of the inorganic filler is 3 to 1
80% by weight or more must be contained in the range of 00 μm, but the limit of 3 to 100 μm is that when the size is less than 3 μm, the particles are contained in the organic polymer film which acts as a binder between these inorganic fillers. This is because it is buried and does not work to strongly fix hydroxyapatite. On the other hand, when it exceeds 100 μm, the organic polymer film as a binder cannot fix the inorganic filler on the base material, and even if the hydroxyapatite is strongly fixed, the space between the base material and the inorganic filler is large. This is because peeling will occur and it will not be practical.
The reason for limiting the proportion of the inorganic filler having a diameter of 3 to 100 μm to 80% by weight or more is that sufficient adhesive strength cannot be obtained when the filler which does not contribute to the adhesion between the base material and hydroxyapatite exceeds 20% by weight. Because.

The amount of the inorganic filler needs to be 1 to 30 with respect to the amount of the organic polymer when dried. If it is less than 1, the surface of the inorganic filler is completely covered with the organic polymer. The effect of precipitating and fixing hydroxyapatite is almost lost. On the other hand, if it exceeds 40, the effect as a so-called organic polymer binder for fixing the inorganic filler to the base material cannot be expected. As the organic polymer, it is necessary to select one that strongly adheres to the base material. When the base material is an organic polymer, it is better to use the same organic polymer for the binder. The organic polymer does not have to be a single material, and may be a blend of several kinds, or a polymer obtained by blocking or grafting.

The substantially saturated and supersaturated component aqueous solutions are the aqueous solutions disclosed in Japanese Patent Laid-Open No. 25515/1990.

The hydroxyapatite film has a thickness of 3 to 100.
μm is preferred. This is because if it is less than 3 μm, it may be eroded and disappear while being buried in the living body. If it exceeds 100 μm, the strain due to the difference in expansion coefficient between the base material and hydroxyapatite with respect to temperature and humidity becomes large,
As a result, the hydroxyapatite layer is likely to be cracked, and the crack tends to be peeled off as a nucleus. Further, it takes a long time to form the hydroxyapatite layer, which increases the manufacturing cost, and it is not industrially meaningful to increase the thickness of the film, and the main components are CaO and SiO _2.
The glass powder to be used is CaO and S converted to oxides.
iO ₂ is contained in the range of CaO ₂₀ to 60 mol% SiO ₂ 40 to 80 mol%, and the total amount of CaO and SiO ₂ is 70 mol.
% Or more, and the particle size is 100 to 600 μm
The powder having 80% or more of the particles in the range is.
A disclosure regarding the composition of glass containing CaO and SiO _{2 as} main components is disclosed in JP-A-2-25515.

Further, the average thickness of the film when dried on a substrate of an organic polymer containing an inorganic filler and having good adhesion to the substrate is preferably 5 to 100 μm, which is preferable. If it is less than 5 μm, the effect of fixing the inorganic filler to the substrate cannot be expected, and if it exceeds 100 μm, there is a risk of causing cohesive failure in this coating layer in practical use.

[0024]

EXAMPLES As the inorganic filler used in the present invention, a commercially available particulate reagent was purchased and pulverized with a ball mill to obtain an inorganic filler powder having a predetermined particle size. The substance name of the filler will be described in each example.

The main components used in the present invention are CaO and SiO.
_The glass designated as ₂ was manufactured as follows.

<Amount of glass raw material blended><Glasscomposition> CaCO ₃ …………… 28.431 g CaO …………… 49.87 mol% MgO ………………… 2.289 g SiO ₂ ………… 35.46 mol% β-Ca ₂ P ₂ O ₇ … 14.517g P ₂ O ₅ ……… 7.153 mol% CaF ₂ ……………… 0.249g MgO ………… 7.111 mol% SiO ₂ ……………… 17.015g CaF ₂ ............ 0.399 mol% That is, the above glass raw material mixture was made into a fine powder using a mortar and uniformly mixed, and then placed in a platinum crucible for 1450
Melted at 2 ° C for 2 hours. This was poured onto an iron plate, rapidly cooled, and then crushed using a ball mill. Various glass powders were produced from this using a classification sieve.

An aqueous solution of hydroxyapatite component having a substantially saturated or supersaturated concentration was prepared with the following composition, and the pH value at 36.5 ° C. was adjusted to 7.4 by controlling the amount of hydrochloric acid.

<Components and Composition in 1 L of Aqueous Solution> Aqueous Solution A NaCl ………………………………………… 11.994 g NaHCO ₃ …………………………………… _{... 0.525g KCl ................................................... 0.336g K 2 HPO} 4 · 3H 2 O ........................... 0.342g MgCl 2 · 6H 2 O ……………………………… 0.458g CaCl ₂ ……………………………………… 0.417g Na ₂ SO ₄ ………………………………… … 0.107g 1N HCl ……………………………………………… 68ml Tris (hydroxymethyl) aminomethane… 8.086g And the bioimplant member according to the present invention is called skin button. FIG. 1 showing the shape of an implant member and the surface of this implant member It will be described with reference to FIGS. 2 and 3 which are schematic process diagrams of coating a hydroxyapatite film on the above. In FIG. 1, 11 is an implant member made of polyether sulfone [ICI brand name: PES4100G], 1 is an upper adapter, 2 is connected to a flange portion 3 of the upper adapter 1, and through a through hole 8b. A lower adapter that connects the through holes 8 and 8a. Also, in FIG.
In FIG. 3, 4 and 4a are containers, 5 is the above-mentioned inorganic filler, 6 is an organic polymer solution, and 7 is an aqueous solution A.

[I] made of polyether sulfone shown in FIG.
CI company: PES4100G], the implant member 11 partially contains the inorganic filler 5 of the present invention as shown in FIG.
It was dipped in an organic polymer solution 6 that adheres well to the substrate 11, dried at room temperature for 24 hours, and then vacuum dried at 60 ° C. for 5 hours. After vacuum drying, the implant member 11 is dipped in the aqueous solution A7 as shown in FIG. The implant member is left for 1 week in a thermostatic layer at 36.5 ° C, taken out, thoroughly washed with distilled water, and then dried at 60 ° C. By the above operation, a bone-like hydroxyapatite film 11a is formed on the surface of the implant member 11 particularly in the region in contact with the organic polymer solution 6 in FIG.

According to the above-mentioned procedure, a total of 29 samples of 23 samples of the example and 6 samples of the comparative example were prepared per condition, two of which were used for the destructive test, and the other one was an adult dog. It was embedded in and evaluated for compatibility with a living body. The evaluation items include the following three items A to C.

A. Measurement of film thickness of hydroxyapatite Cut a part of the flange part of the above implant material,
Scratch the undamaged coating with a knife and use a scanning electron microscope to scan the sample with the electron irradiation direction 5
The thickness of the hydroxyapatite layer at the cut end was measured while tilting at 0 degree.
The tilted portion was corrected by calculation to prepare a list in the table below.

B. Adhesive strength between base material and hydroxyapatite layer Cut a part of the flange part of the above implant material,
A cellophane tape (adhesive tape) was attached to the coating portion which was not damaged, and this was peeled to evaluate whether or not the hydroxyapatite layer peels off.

C. Biocompatibility An implant device as shown in FIG. 4 was produced using the above-mentioned implant member that was not used in the destructive test. After sterilizing this with ethylene oxide gas, it was placed on the chest of an adult dog.
It was buried in place as shown in. 1 day, 3 days, 1 week, 2
The state after one week, three weeks, and one month was observed and biocompatibility was evaluated. In order to evaluate this biocompatibility with high sensitivity, the implant device was embedded so that part of it was outside the body and part of it was inside the body. It was embedded in this way and evaluated by the condition of the interface with the skin surface. 4 and 5, the upper tube 12 is connected to the through hole 8 of the implant member 11, and the lower tube 3 fixed by the fixing system 4 is connected to the through hole 8a. A luer adapter 17 and an intermittent infusion plug 18 are attached to the tip of the upper tube 12 and fixed by a fixture 19. On the other hand, the lower adapter 2 including the flange portion 3 of the implant member 11 is embedded subcutaneously, that is, in the living body as shown in FIG. 5, but the tip of the lower tube 13 is connected to the indwelling catheter 16 via the connector 15. And is extended to a required organ (not shown) in the living body.

The evaluation results will be described below by selecting some examples and comparing them with corresponding comparative examples.

Example 1 Example 1 shows that the implant member of the present invention can strongly adhere hydroxyapatite to an organic polymer to such an extent that there is no problem in practical use and exhibits excellent biocompatibility.

Barium sulphate was used as the inorganic filler, and the particle size of which contained 98% by weight (filler D) in the diameter range of 3 to 100 μm.

As the base material, medical polyurethane (TherMedix: SG65D) was used, and as the base material and good organic polymer, the same medical polyurethane as the base material (Thermedic: SG65D) was used. As a solvent,
Cyclohexanone was used. Therefore, the organic polymer solution which has good adhesion to the substrate has the following constitution.

Medical polyurethane: 0.6 g → inorganic filler / organic polymer = 4.0 Filler D: 2.4 g Cyclohexanone: 27 g As a comparative example, only the base material was used. The same operation as in Example 1 was carried out except that an organic polymer solution containing an inorganic filler and having good adhesion to the substrate was not dipped.

As the base material of Example 1 and Comparative Example 1, medical polyurethane [SG65D manufactured by TherMedix Inc.] was used. The evaluation results are shown in Table 1.

[0040]

[Table 1]

In Example 1, after one month, the hydroxyapatite layer was observed using a scanning electron microscope. No adhesion with the soft tissue was observed, but there was no change in the hydroxyapatite layer itself. There wasn't.

Downgrowth is a phenomenon in which the skin sinks downward at the interface between the skin and the implant member if the biocompatibility is not good. It is judged that the biocompatibility is better as there is no downulose. Further, if the biocompatibility is good, it is considered that the resistance of the living tissue to the bacteria from the outside does not decrease, so that infection is difficult.

In summary of the above, it can be said that, in the implant member of the present invention, infection did not occur even after disinfection was stopped, which is an epoch-making result.

Examples 2-3: In Examples 2-3, the diameters of the inorganic fillers A, B, C and D shown in Table 2 were 3 to 3, respectively.
It indicates that 80% by weight or more must be contained in the range of 100 μm. Barium sulfate was used as the inorganic filler. As the base material, medical polyurethane (SG65D)
It was used.

[0045]

[Table 2]

Otherwise in the same manner as in Example 1, the hydroxyapatite was coated. The evaluation results are shown in Table 3.

[0047]

[Table 3]

From the above, the particle size of the filler is 3 to 100 μm.
It can be seen that the proportion in the range of is very critical between 75% and 80%.

Examples 4-6: Examples 4-6 show that the ratio of the inorganic filler to the organic polymer is limited to 1-30.

[0050]

[Table 4]

The organic polymer solution for dipping the substrate is shown in Table 4.
After that, the hydroxyapatite was coated by the same procedure as in Example 1. The evaluation results are shown in Table 5.

[0052]

[Table 5]

From the results of this example, it was confirmed that when the filler / organic polymer was less than 1.0 and 30 or more, the hydroxyapatite film could not be used or was unsuitable.

Examples 7 to 12: Examples 7 to 12 show that the bioimplant members of the present invention can be obtained with various inorganic fillers composed of different substances shown in Table 6.

[0055]

[Table 6]

Other operations are performed only by changing the kind of filler.
This is the same as in the first embodiment. Table 7 shows the evaluation results.

[0057]

[Table 7]

From the results shown in Table 7, it is not particularly systematic as a substance suitable for the inorganic filler, and titanium dioxide, zinc oxide and zinc sulfide of Comparative Examples 5, 6 and 7 are completely unsuitable. However, good results have been obtained with the substances used in Examples 7 to 12.

Examples 13 to 17: In Examples 13 to 17, the average thickness of the film when dried on a substrate of an organic polymer containing an inorganic filler and having good adhesion to the substrate is preferred. Indicates 5 to 100 μm.

The thickness of the coating film was controlled by changing the concentration of the organic polymer solution and the number of dips.
5 samples shown in were prepared. Subsequent operations are described in Example 1.
It was carried out according to. By the way, the film thickness of Example 1 is 12
was μm. The evaluation results are shown in Table 8.

[0061]

[Table 8]

Although biocompatibility was omitted in the above evaluation, satisfactory results were obtained with a film thickness of 5 to 100 μm.

Examples 18 to 23: Only the time for immersing the substrate in the aqueous solution A was changed, and the other conditions were the same as in Example 1. By this method, the film thickness of hydroxyapatite was changed as shown in Table 9.

[0064]

[Table 9]

When the surface of the sample of Example 18 was observed after 3 weeks, the hydroxyapatite layer had disappeared. When the surface of the sample of Example 23 was observed one month later, the hydroxyapatite layer was partially disappeared. From the results shown in Table 9 above, the thickness of the hydroxyapatite layer in the present invention is preferably 3
It can be seen that the thickness is -100 μm, and more preferably 10-60 μm.

Example 24: In Example 24, a radius of 8 m
m, height 15 mm cylindrical polyether sulfone [I
CI Japan: PES4100G] implant base material is dipped in the following organic polymer solution.

PES4100G …………………… 0.3g Calcium carbonate [filler G] …… 2.7g N-methyl-2-pyrrolidone …… 15g Dichloromethane ……………… 15g at room temperature After leaving it for 20 hours, it was vacuum dried at 100 ° C. for 5 hours. This bioimplant member was immersed in the aqueous solution A for 10 days to form a hydroxyapatite layer having a thickness of 18 μm.
After being sterilized with ethylene oxide gas, it was embedded in the femur of a rabbit and extracted after 10 weeks, and the adhesion state between the implant member and the living bone tissue was checked. The living tissue was completely adhered to the hydroxyapatite layer of the implant member.
This material has a bending strength of 1100 kg / cm ² or more,
The elongation at break is 60% or more, which is higher than that of other implant materials such as bio-glass and hydroxyapatite sintered body.
It has been found that it is possible to provide an implant member that is extremely excellent, lightweight, and excellent in biocompatibility.

The bioimplant member according to the present invention has been described above by using several embodiments. Until now, it is well known that hydroxyapatite shows excellent biocompatibility, but due to its low strength, its use as an implant member as a sintered body is limited to the part that does not bear a large force. Came. Metal substrate to improve this,
Alternatively, although a method of coating ceramics has been developed, it has not become a general-purpose implant member due to the high price of the base material itself and poor moldability. Originally, it is ideal to coat on an organic polymer material whose workability and moldability are remarkably superior compared to other materials, and the price is relatively low, but the adhesive strength with hydroxyapatite is low. There wasn't.

Taking these things into consideration, this example shows that an “implant member in which an organic polymer material is coated with hydroxyapatite” having a sufficiently practical level of adhesive strength to an organic polymer has been achieved. Shown and demonstrated to have excellent performance.

[0070]

As described above, according to the present invention, the diameter is 3 to
The weight ratio of the inorganic filler powder containing 80% by weight or more in the range of 100 μm to the organic polymer when dried is 1 to
After dipping the base material in an organic polymer solution that adheres well to the base material of No. 30, the surface of the base material is immersed in an aqueous solution of hydroxyapatite component having a substantially saturated or supersaturated concentration so that the surface of the base material is bone-like Since the bioimplant member formed with the acid apatite film has been developed, the bioimplant member has excellent compatibility with the living body, sufficiently secures strength, and has a large degree of freedom in design, and thus contributes particularly to the medical field. There is expected.

[Brief description of drawings]

FIG. 1 is a shape explanatory view of a living body implant member according to an embodiment of the present invention.

FIG. 2 is a schematic view showing a first step of coating a hydroxyapatite film according to the present invention.

FIG. 3 is a schematic view showing a second step of coating a hydroxyapatite film according to the present invention.

FIG. 4 is a structural explanatory view of an implant device formed by using the biological implant member according to the present invention.

FIG. 5 is an explanatory view showing a state in which the living body implant member of FIG. 4 is embedded and left in a living body.

[Explanation of symbols]

 1 Upper Adapter 2 Lower Adapter 3 Flange Part 4, 4a Container 5 Glass Powder 6 Aqueous Solution (1) 7 Aqueous Solution (2) 8, 8a, 8b Through Hole 11 Implant Member

Claims (5)

[Claims] 1. A film of a hydroxyapatite bone-like material on the surface of a substrate by immersing a base material of a bioimplant member having an adhesive layer on the surface in an aqueous solution of hydroxyapatite component having a substantially saturated or supersaturated concentration. A bioimplant member formed by forming an adhesive layer, wherein the adhesive layer contains an organic polymer having a strong affinity for a base material and an inorganic filler powder as main components, and the inorganic filler has a particle diameter of 3 to 1
A bioimplant member coated with a bioactive apatite film, characterized in that a composite having a weight ratio of 1 to 30 with respect to the organic polymer occupies 80% by weight or more in the range of 00 μm. 2. The film thickness of hydroxyapatite is 3 to 100 μm.
The living body implant member according to claim 1, wherein 3. The inorganic filler is barium sulfate, lead sulfate, barium carbonate, calcium carbonate, silicon dioxide, bismuth tungstate, glass powder containing CaO and SiO ₂ as main components, or a mixture containing these as main components. The living body implant member according to claim 1, wherein: 4. The bioimplant member according to claim 1, wherein the base material and the organic polymer are the same material. 5. An average thickness of a film of an organic polymer which contains an inorganic filler and has good adhesion to a base material when dried on the base material is 5 to 100 μm. 1. The biological implant member according to 1.