JPS59211447A - Carbonaceous implant material for living body hard tissue and production thereof - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION The invention relates to an implant material for biological hard tissue (implant material: -1) and a method for producing the same. When VC is implanted in a living body as an artificial bone used for prosthesis or as a material for an artificial tooth, there is little biological reaction and good biological tissue density.171
All stains have a strong bonding quality, and are durable: fc excellent fc
The present invention relates to an implant material for biological hard tissue and a method for producing the same.

In the past, materials that have been introduced into living bodies as artificial bones and artificial teeth have been divided into various types, and despite many years of effort, the reality is that many problems still remain.

Ceramics, glass, carbon, and other inorganic materials have recently been developed to replace conventional metals or related materials, and some of them have begun to be used for U"4.

Implant materials have various customization requirements depending on the shape, size, and function of the part to be used, and the design and selection of materials for these are also subject to many extremely difficult conditions, such as multiple glazes and variety.

The conditions necessary for the implant material to function safely in the living body are: (1) There is no surgical procedure and no tissue microscopy, and the occurrence of J+'7
i. It should not cause any problems such as allergies or destructive effects on adjacent tissues.

(2) Do not cause foreign body reactions (actions that attempt to expel them from the living body).

(3) It should not be absorbed (disappeared by decomposition) in the living body.

(4) Do not bathe ionized by the influence of body fluids, etc.

(5) It has good affinity with tissues (called biocompatibility).

(6) High mechanical strength such as bending strength and compressive strength,
Must withstand stress during use and do not deteriorate in strength in biological environments.

(7) Easy to handle and erasable IJ can be applied.

(8) Stiffness and elastic modulus are similar to biological hard tissue or slightly thicker 1
It should be possible to adjust the presentation K and take a state as close to natural as possible when integrated with living tissue.

The following requirements must be met. Even when measuring the material against the above requirements, problems with metal materials (4), (1), (2), (4), and (8) above are improved, and with plastic materials ( 2) ,
Conditions (3) and (6) have many problems. On the other hand, ceramic nanomaterials, which have been attracting a lot of attention recently, have almost no problems with VC (1) to (5), which are conditions specific to living tissues.

The reason why ceramic additives were not used in the past is (6)
)■Is it really mechanical? 7, and the drawback was that the strength deteriorated in a moist in-vivo environment. Regarding this point, the above-mentioned drawbacks have been improved and some of the alumina materials such as artificial sapphire single crystals or polycrystalline materials and sintered hydroxide apaquite have been developed and are now available for commercial use. In the case of the former alumina material, the hardness and bullet survival rate are the same (1″1,1.l<living body vC7), and stress concentrates on the implant material. However, under the condition (8), there are problems such as unreasonable force acting on the surrounding tissue, causing damage to it, or even reaching and damaging the nervous tissue. The latter synthetic hydroxyapatite sintered body is a material that closely resembles the hard tissues of living organisms, and there are fewer problems like those of the alumina materials, but it still has poor mechanical strength. There are problems such as the synthesis of annotite powder and the shaping and sintering technology is insufficient, and the multiple steps are cost-free.The above are the problems related to 12). Furthermore, during the treatment, the implant material is usually fixed to the bone in Step 7 of repairing the broken part of the living body's hard tissue (bones and teeth), implanting an artificial joint, and fixing the artificial 1v1 root. (1) Align the implant material and bone tissue with structural or

Self-locking method that fixes itself by devising the shape.

(2) A method of mechanically fixing using screws or bolt nuts.

(3) Attach the implant material to the bone using an adhesive such as all-medical cement.

Measures such as these have been adopted. However, no matter which method is used, the implant material may become loose over a long period of time, and even if there is no defect in the implant material itself, it may come off and have to be replaced.

-Also, by implanting an implant material as a tooth root into the alveolar bone, and 71. Dental treatment is performed to fix the crown of a tooth, and in this case as well, the various hard implant materials mentioned above are used, and there are many different shapes such as natural tooth root shape, bottle shape, blade shape, screw shape, etc. There are many different types of drugs available, each designed according to the symptoms.

In this case, since it is used across the body and the body surface, contact layering is particularly required at the material-tissue interface. That is, adhesion at the part that protrudes from the inside of the body to the body surface is important. If this is not achieved, unfavorable results may occur due to bacterial infection from outside the body or the infiltration of harmful substances into the body.

At present, 74% of VCs still have the above-mentioned problems.
The inventor of this application discovered that carbon began to attract attention as a biological material in the early 1960s, and that carbon has excellent antithrombotic properties, no tissue irritation, is highly compatible with living organisms, and is effective under various environments both inside and outside of living organisms. It also has excellent stability and mechanical strength, and as a result, it has been applied to artificial heart valves and many established success stories have been published, as well as ligaments, Focusing on the fact that it has been used for dental root materials and artificial joints, we have conducted further research and have thoroughly investigated materials and structures that have a strong bond with living hard tissue, while maintaining all biological functions. By devising a shape design that provides sufficient strength, we succeeded in creating an excellent implant material for biological hard tissue that has never been seen before. That is, in the present invention, a dense carbon material having high hardness, erodibility, and impermeability is used as the core 2, and the core 2 is made of a dense carbon material having a thickness of 100 μm on the surface of the core.
Constructing the above carbonaceous porous layer f: Characteristically, it is substantially composed only of carbon, and if necessary, vapor-phase pyrolytic carbon is deposited on the surface to coat the metal layer surface. The present invention relates to an implant material for biological hard tissues that facilitates the process and strengthens capture, and a method for manufacturing the same.

The implant material of the present invention is made entirely of a single core of carbon material, which has a smooth surface, has gastric hardness, has excellent mechanical strength such as bending strength and compressive strength, and is impermeable to body fluids. Preferably 100 μm or more on the surface of the core material Ir:L 5
It has a structure in which a porous layer with a diameter of 00 μ711 or more is constructed. This porous structure is extremely important for achieving full-circle and strong bonding with living organisms. The collagen fibers newly generated at the interface between the implant and the implant material are designed to penetrate into the porous tissue on the implant surface and create a state in which they interweave with each other.

Furthermore, it is necessary that the surface porous layer has an appropriate pore distribution so that circulating fluids such as blood can easily penetrate to supply oxygen and nutrients. In other words, it is preferable to have a pore diameter of 50 μm or less, preferably 20 μIn or less in the vicinity of the core material, and with this pore diameter, the collagen fiber tissue that has penetrated into the circular part without capillary infiltration will be calcified and removed from the core. It becomes firmly attached to the dragon face and produces an anchoring effect. In addition, the intermediate layer adjacent to the porous layer with a pore diameter of 100 μm or less preferably has a pore distribution of 100 μm or more, preferably about 200 pm, and in this region, oxygen and nutrients are supplied by capillaries. is sufficiently applied and is fixed in a cartilage state to the collagen delicate 441Nik. Furthermore, the outermost surface (is 20 Q
Itm or more and 600 μm or less, preferably 30 (J/,
It is preferable that the porous layer is constructed of a porous layer having tm pore diameter IJk. On the outermost surface with this pore size distribution, body fluids and blood vessels can freely infiltrate, allowing effective and smooth VCi calyx expansion 16 activity, and the collagen fiber tissue is flexible and strong in the in-plant. The toy and the rest of the living body are combined by a total anchoring effect, and it comes to appear in a state exactly like that in nature.

The porous layer referred to here is a general term for a surface structure with a designed pore size distribution and high porosity, and is generally made of an organic polymer material with a controlled particle size distribution. A carbonaceous porous body composed of microparticles VC, which is formed by point adhesion or point fusion between each particle, and is strongly sintered and carbonized, and which has three-dimensional voids. It is. As described above, the implant material according to the present invention, which has a significant function, has a three-dimensional point sintered porous layer on the surface of the core material. Ideally, it would be ideal to coat the surface by depositing vapor-phase pyrolytic carbon for the purpose of strengthening the harvest and making the surface condition more pure and making it easier to complete one cycle of cells. It is true. This vapor phase pyrolytic carbon post-treatment is carried out at an IA degree of 600°C or higher, preferably 700°C, of the object to be treated (core material surface [I] VC carbon-sintered carbonized porous layer). Keep at ~1,100℃,
Hydrocarbon compounds such as benzene and naphthalene, and halogenated hydrocarbons such as dichloroethylene and trichloroethane can be used as pyrolysis carbon raw materials.
In particular, when logenated hydrocarbons are used, there is an advantage that they can be processed at lower temperatures. Vapor phase heat fraction jII a precipitation of carbon,
The time required for the deposition process varies depending on the conditions VC,l:
It is usually carried out in 1 to 10 hours. Above, we have described the structure of the carbonaceous three-dimensional porous material used in this application and the coating treatment with vapor phase pyrolytic carbon, focusing on the cell proliferation function and biocompatibility, which are essential requirements for a biological implant material. A general method for producing a three-dimensional carbonaceous porous body in the present application will be explained. In principle, the organic polymer substance used as a raw material for the porous body may be any substance that is solid and granular and can be carbonized in an inert gas phase atmosphere, but post-chlorinated polyvinyl chloride is preferable. Resin, polyacrylonitrile resin, polyvinyl chloride resin, polyvinyl alcohol,
) Thermoplastic resins such as phenylene ether resin, 4-aryamide-imide resin, polyimide resin, aromatic polyamide resin, and polydivinylbenzene resin, and thermosetting 1'&41A resins such as furan resin, phenol resin, and bismaleimide-triazine resin. Particles obtained by lightly curing a monomer or an initial condensation polymer into a shape that can be thermally deformed or bath-dissolved in a solvent, or gum tragacanth,
Natural polymer particles, such as gum arabic and polysaccharides, have fused polycyclic aromatics as the basic structure of the molecule (1), and synthetic polymer particles that have fused polycyclic aromatics not included in the basic structure of the molecule, such as gum arabic and polysaccharides. Molecular particles, i.e. formalin condensate of naphthalene sulfonic acid, threne dyes and their intermediates, petroleum asphalt, coal tar, synthetic resins, etc. all at 300°C to 500°C
C
Seed or mixture particles of two or more species are suitable. Also, ko\
(This may be used; 1) There are no particular restrictions on the shape of the molecular particles, but it is preferable that they be spherical.

Regarding the size of the particles, (1) particles preferably have a diameter or maximum side of 1 mm or less, and it is preferable that 90 or more of the particles have a diameter or maximum side of 30 μm or more.

To increase the porosity (porosity) of a carbon porous material, select one with a large particle size, and conversely, to obtain one with a small porosity, select all the particles with a small particle size. In order to make the organic polymer particles uniform, it is achieved by pre-classifying the organic polymer particles using a sieve, elutriation, water elutriation, etc. to make the particle size uniform. K, which has a multilayer three-dimensional structure with a VC-shaped porosity distribution, is prepared by preparing fine particles, intermediate particles, and coarse particles that have been classified into uniform diameters in advance, and heating a flat mold for molding. This is achieved by adding fine particles and melting them lightly (melting M), then melting the intermediate particles and then coarse particles into a melting layer (or melt layer) to unify the whole. V
C. Filling a mold having these shapes with particles and melting with N (melting 7k) - C1. A molded article that maintains the entire shape of the mold can be obtained. The power of the above mold
The heating temperature is at least above the softening point of the organic polymer particles used and below the melting point, and adjusted so that the organic polymer particles soften and point fusion occurs between the surface layers of the particles.
Ru. In this case, if the temperature is too low, the fluidity due to softening will be reduced and point melting will not occur.On the other hand, if the temperature is too low, the fluidity due to softening will become too thick and the resulting porous body will This is undesirable since the pores may be closed or even disappear. Although it depends on the solubility of all the solvents in which the K-boad organic polymer particles can be soluble, in general, 10% by weight or less of the particles (-15% by weight or less) is used for spot bonding. The entire particle surface is uniformly wetted using a high-speed J-forming frame machine such as a Henschel mixer, and then the whole particle is placed in the same molding mold as above.In this case, the solvent (only the surface of the organic polymer particle is It is important to add the necessary amount to dissolve and point-bond the material.The formed porous material is dried to release the solvent J',n.
A porous polymer material is obtained. The organic molecular porous material obtained by any of the above methods VCX is then subjected to a hardening treatment, oxidative crosslinking with heated air VC, or immersed in an acid such as Jukucho's sulfuric acid to perform a dehydrogenation reaction to make it insoluble. It is made into a carbon precursor by performing an infusible treatment.

Next, a method for manufacturing a dense carbonaceous core material (υ, lower core material) having high hardness, 1% strength, and impermeability according to the present invention will be explained.

Regarding the manufacturing method of the core material, one of the methods described below is adopted depending on its design and purpose of use.

Method (1), using thermoplastic synthetic resins such as hydrogenated polyvinyl chloride resin, polyvinyl chloride; A mixture containing raw natural graphite powder and carbonaceous powder such as carbon blank or chopped fiber as a filler is made into a strong material using a mixing roll with high shear strength, a pressure kneader, etc. The molding composition is prepared by causing a mechanochemical reaction at the interface between the kneaded matrix resin and the carbon flakes to uniformly disperse the carbonaceous powder, preferably to a state of missing particles. After applying pressure, this composition is extruded into a conventional plunger type or screw type extrusion joint under cylinder pressure using an extrusion die of the desired shape to form a tip rod into the desired shape. (Cylinder)
Core material shaped bodies having a shape, a plate shape, and a prismatic shape were obtained.

Method (2), as a matrix, one or more types of monomers, prepolymers, or low polycondensates of base molecular compounds that can be thermally polycondensed with a substance that exhibits a high carbon residual strain yield after firing and can be relatively easily thermally polycondensed. Add the same carbonaceous powder as in method (1) to this mixture and disperse it uniformly, knead it vigorously using a mixing roll with high shear force or a pressure kneader, and then use a Zeel mill. The -1-c matrix resin is uniformly and physicochemically bonded firmly to the surface of the primary particle of the carbonaceous powder used as an extender by applying a high level of mechanical energy using a mechanochemical cuff to induce a reaction. A powder composition for molding was obtained. Next, this was powder compression molded into a desired shape using a conventional hot press molding machine to obtain a formed body for the core material.

Next, the main feature of the present invention, the method of constructing the entire carbonaceous three-dimensional porous body on the surface of the core material, will be explained.

The first method involves directly embedding the entire formed core material obtained by either method (1) or (2) above in soil granules of an organic polymeric material, which is the raw material for the porous material. Enter (
Insert), heat or solvent is used to cause mutual pressure point fusion and point adhesion between the core material surface and particles to obtain a whole raw implant molded product in which the core material and the three-dimensional porous layer are integrally formed. Ta. This raw implant molded body was heated to 50°C to 300°C.
'C is preferably oxidized and crosslinked in an air bath heated to 150°C to 200'C, or immersed in hot concentrated sulfuric acid to perform a dehydrogenation reaction to make it insoluble and infusible, resulting in a carbon AiJ precursor. Thereafter, the temperature was gradually raised in an inert gas injection phase such as nitrogen gas, and the product was fired to a predetermined temperature of 800° C. or higher, and the carbon content was compared to obtain a finished product.

The second method is to shape the surface of the formed body of the core material obtained by the above method into a three-dimensional porous body by point fusion or point contact 7M IC in advance, and to insoluble it by any of the means described above. A liquid or paste-like sieve molecular composition which had been subjected to an infusibility treatment and had carbonization bonding strength was bonded and integrated using an adhesive to obtain an implant-formed body. In this case, liquid or paste-like materials such as organic polymer compositions, furan resins, and phenol resins used as adhesives have a strong bonding force when carbonized. It is not limited to "Tokuo 1". At this time, carbon powder such as fine graphite or carbon blank is added to these adhesive liquid resins.
~50% by weight is preferably added to the composition by 10 to 20% by weight to form a carbonized bond, J:! l) It is preferable because it makes it stronger. The raw implant molded body in which the core material and the porous layer were bonded together in this manner was fired and carbonized in the same manner as in the first method to obtain a complete finished product.

In the third method, the core material and the porous body are carbonized based on the firing method of Ne2, and then they are bonded together using the carbonized adhesive, and then fired in a rectangular manner, thereby completely carbonizing the core material and the porous body. A carbonized finished product was obtained.

From J-1 No. J, No. 2. 3rd///) As described above, the surface of the non-conforming implant material can be coated by depositing it on the surface of the vapor-phase pyrolytic carbon, if necessary. It is possible to increase surface forgery at the same time as synchronization.

The implant material for biological hard tissue of the present invention is custom-made as follows.

(1) Appropriate selection and design of the structure and pore size of the carbonaceous three-dimensional porous layer, prevention of infiltration of living tissue and calcification on the surface of the internal core material, r, bone organization (bone ) The speed can be completely changed.

(2) The tip of the collagen fiber tissue that has penetrated into the circular part of the implant material is ossified and integrated on the surface of the core material, and the middle layer becomes cartilage, and the outer surface is ￥ Jl! Treated by the newly generated collagen fiber tissue and integrated with the biological skeleton, the implant material is firmly bonded with the anchoring effect (anchoring), giving it an appearance similar to that of natural bone.

(3) Non-implant materials have antithrombotic properties, have extremely low tissue irritation, and have excellent affinity, so they can be applied anywhere.

(4) Because it is composed entirely of carbon, it does not corrode, and its mechanical properties deteriorate over time in the biological environment.

(5) It is lightweight and has an elastic modulus similar to that of living hard tissues, so it does not burden living bodies with unreasonable forces such as stress concentration.

(6) Since the surface layer has a porous structure, the implant material is self-supporting during the treatment and can be freely adapted to the insertion site, so it can withstand long-term use without loosening like other hard materials.

Next, the present invention will be explained in detail with all its embodiments, but the invention is not limited to the following embodiments.

Example 1 (Round bar-shaped sample) As a material for a composition for forming a core material, post-chlorinated polyvinyl chloride resin (-
Nippon Carnoguito Co., Ltd. NT Q 25) is adopted,
After this, fine natural graphite powder (average particle size 2.0 μnL) was poured into crystals based on 100↓F amount% of chlorinated polyvinyl chloride resin.
70% by weight was added as an extender, fc, and dioctyl phthalate 2 was added as a plasticizer to 100% by weight of the formulation.
After adding the quintuple powder and dispersing it using a Hen/El mixer, mixing was repeated sufficiently using a mixing roll kept at a temperature of 1:30°C until the graphite particles were in a state close to the primary particle state. Continue until the mechanochemical reaction 'z8
A core molding composition subjected to N was obtained.

This molding composition was extruded at a molding temperature of 150° C. while degassing using a vented screw extrusion mill, and the molding composition was extruded to a diameter of 2.
A 5 mm round bar (produced shape) was obtained. This round bar has a length of 2
Diameter 5. after cutting to 0mrrL. In a cylindrical molding mold of Q mm, vertical Vr:,'SL is applied from the bottom of the mold to I.
Post-chlorinated polyvinyl chloride resin (T-025
), this was separated into a sieve, passed through a 30-mesh sieve, and the particles remaining on the 50-mesh sieve were collected and filled, and then placed in an air oven at a temperature of 160°C for 30 min.
After processing for minutes at room temperature (cool down and remove from the mold core part II)
] was point-fused to obtain an integrated implant-formed body. Next, this was placed in hot sulfuric acid heated to 100℃ for 20 minutes.
After being immersed for a minute to carry out hydrogen chloride reaction and dehydrogenation reaction, it was washed with water and dried to make it insoluble and infusible. Furthermore, the temperature was increased to 500℃ in nitrogen gas at 10℃/
The temperature was raised from 500 to 1,000°C at a rate of 50°C/hr, held at 0°C for 3 hours, and then allowed to cool naturally to complete firing and complete carbonization. A completed implant material was obtained.

The pore diameters forming the surface porous layer of this implant material were distributed with a radius of ±50 μm17) centered around 150 μm. The shredded sample has a core diameter of 2. l m, m, maximum outer diameter 3.5 mm, length 18. It has an OTtTTL shape and has a bending strength of 4. OOOkgf/crl, compressive strength 5.50, Okgf7ca, and had sufficient mechanical strength.

Example 2 (plate-shaped sample) The same material as in the above-mentioned Example V1'1 was adopted as the silk material for core/l-o molding, and the molding temperature was adjusted using hydraulic extrusion molding with a complete plunger equipped with a full degassing device. 130℃, molding pressure cuff 0 kff/csrt, thickness 2.5 nL7a
, 4% 3 Q ntm extrusion molded to length 25
A plate-shaped body (produced shape) was obtained by cutting +nm17. In addition, the porous layer (・11. As a construction material, the average degree of polymerization is 740.
All chlorinated polyvinyl chloride with a chlorine content of 670% (■'J'-870 manufactured by Nippu Carbide Co., Ltd.) was used, and all of this was classified in advance through a sieve to pass through ■200 meso/yu (90% below 45zzm). Fine grain, ■ 100 meso passed through 7 units, 150 meso remained (average particle size 701 tm) intermediate grain, ■ 30 meso/
Passed through 11 units, 50 units remained (average particle size 280μ)
nL) of rice grains were obtained. Next, on a mold with a smooth surface measuring 2 Q Q mm wide x 300 mff1 long (
(After the fine grains of the above (■) were packed down to a thickness of 1 mm and VC, they were cooled to a temperature-controlled room that was kept in a heated air path for 2 minutes in this mold 'ff:l 501:, so that the particles were slightly fused with each other. A finely porous layer was formed.Next, the same operation was repeated sequentially to form a medium grain layer on top of the fine grain 1-, and a coarse grain layer on top of that to form a three-layer structure with a different pore distribution. The integrated transversely porous body was formed into a shape (11).Next, it was treated in the same manner as in Example 1 to make it insoluble.It was further heated at 10°C/hr in an elementary gas. Rapid reaction "T: The temperature was raised to 400°C and then cooled to obtain the three-dimensional porous body.

Separately, prepare all liquid or paste adhesives that have carbonization bonding properties. That is, 80% by weight of furan resin initial condensate (Hitafuran VP-302 manufactured by Nizu Kasei Co., Ltd.) and natural graphite powder (
2 μm) A total of liquid products were prepared by adjusting the formulation and kneading with three cooled rolls.

Next, the surface of the core material plate (2 pieces of the carbon precursor of the porous body cut into length I Q mm x width 3 Q mm) were prepared by adding an appropriate curing agent to the adhesive described above. The two surfaces were bonded and integrated to obtain an implant-formed body.

Next VC1 This is all fired and carbonized under the same conditions as in Example 1 to produce the desired carbonaceous implant material? #Ta.

In order to measure the diameter of the pores that make up the three-dimensional porous layer on the entrance surface, the sample phase was completely cut = 15 thn on average near the core material.
, , Average of 200μyn in the middle part, average of 350 in the outer part
Pore diameters of μm were observed, and the layers were mutually fused. In addition, the surface of the core material and the surface of the porous layer were firmly bonded, and the -C-'e boundary W] could be determined.

For sample 1, J, length 4.8 nun (core part 2.0
+l1lTL l Sen25171171, height 20mm
shape, bending strength 3, 500 kgf/C++
t, compressive strength 5,800 krf/C+d with sufficient V
lly, the mechanical strength was poor.

Example 3 (Brave-F type sample) 4'A (furan) lIIr of the composition for forming the core material
II'#f initial condensate (Hitafuran V F manufactured by Nizu Kasei Co., Ltd.
-302) Furnace blank (MA-100 manufactured by Mitsubishi Chemical Industries, Ltd.) 45 p5 relative to 100% by weight
:im% was added as an extender and was uniformly mixed in a kneader.The mixture was thoroughly kneaded using a Mikinon Krollke kept at 50°C, and the graphite particles were shaped like primary ribs. The mechanochemical reaction 'C'i continues until it approaches 1.
The surface of the graphite particles was coated with furan fat [J: A] and the edges were removed uniformly. Next, this was coarsely crushed, put into a ball mill, and crushed for 50 hours, with an average particle size of 5 μ7 rL.
A core material molding composition powder was obtained. Using this core material molding composition powder, a mold having the shape shown in the figure □ was heated to 150°C.
The powder was compressed under a molding pressure of 1001 ηf/l and r)i to obtain a core material formed body.

Then, the above Example 2 was applied to both the front and back sides of the blade portion of this core material.
The carbon precursor of the three-dimensional porous body having a three-layer 114 structure was cut and bonded to the adhesive prepared in Example 2 described in f4iJ for integration to obtain an implant-formed body. Next, this was heated to 180 CK and treated for 10 hours in an open air conditioner to completely cure it and form a carbon frame.

Next, the fired carbon was purple-purified under the same conditions as in Example 1 to obtain the desired carbonaceous implant material.

The structure of the obtained surface porous layer was the same as in Example 2. The surface of this sample was hard and glassy, and the bending strength I
K 1, 500 kgf/ca flexural modulus 2X10
51 (rif/ca, 1% pressure to failure at a load of 240 ky), with all the special notes suitable as an implant material for biological rigid structures.

Example 4 (Surface coating by vapor-phase pyrolytic carbon deposition) The charcoal/leaf implant sample prepared in Example 2 was fixed as a base material and electricity was applied directly to the plate-like core material. and heated. The deposition conditions are as follows.

Raw material cloth Cis-1,2-dichloroethylene carrier gas Argon raw material gas concentration 14% by volume Raw material gas flow rate 400 rrre/yu11 Center core material table [11] Temperature 900°C Also, the deposition time is 51 times per hour I finished it in time.

The implant surface is coated with vapor-phase pyrolytic carbon and is extremely robust and hard, with a steel filer 1. IT was in a state with no injuries.

In addition, the surface layer (porous 1111 forming 41Y) is maintained extremely well, and furthermore, according to electron microscopy observation,
The surface of the sintered particles was uniformly scratched, rounded and smoothed. The strength L1 of the plate-shaped body trial 1 is further increased to have a bending strength of 4, 200 hf/crrf,
EEA'g(? rUi sa6.500 kgf /C
It was T7 de.

Although the examples have been explained above, these samples are currently
Injected as an implant material into the alveolus and lower leg bone of a cynomolgus monkey weighing 4 kHz; JA is in charge.

Patent applicant: Mitsubishi Pencil Co., Ltd.

Claims (6)

[Claims] (1) The core material is characterized in that a three-dimensional carbonaceous porous layer with a thickness of 1001 Lrn or more is constructed on the surface of the core material, which is made of a dense carbon material having cylindrical hardness, surface strength, and impermeability. An implant material for biological hard tissues, which is essentially composed of carbon material and is integrally formed with a porous layer. (2) The core material is carbonaceous fine powder such as crystalline graphite or carbon blank, or organic polymer resin material composite reinforced with carbon fiber VC, fully hardened, or carbon treated with fugo, infusible, etc. The implant material for living bone tissue according to claim 1, which is a carbonaceous material obtained by performing a precursor treatment and then firing at a predetermined temperature or higher in an inert gas phase atmosphere. (3) The carbonaceous three-dimensional porous layer is formed by heating the particles of the organic polymer substance or lightly melting the surface with a solvent to cause point fusion or point adhesion between the particles. After forming (produced shaped body), it is subjected to hardening treatment or insoluble and infusible treatment to impart heat-resistant deformation VL (carbon precursor)
The implant material for biological hard tissue according to claim 1, which is a carbon porous body having basically a granular sintered structure, which is obtained by firing at a predetermined temperature in an inert gas phase atmosphere. (4) A molded body of an organic polymer resin material composite reinforced with carbonaceous fine powder such as crystalline graphite or carbon blank or carbon fiber, or a molded body subjected to a carbon precursor treatment such as a hardening treatment or an infusible insolubilization treatment. The molded body or the molded body is further heated at a predetermined temperature or higher in an inert gaseous atmosphere [sintered carbonaceous material 7J
All the raw particles of the organic polymer substance are directly surrounded by a core material consisting of J and heated or treated with a solvent to cause point fusion or point adhesion between the surface of the core material and the particles, or the surface of the core material is A liquid using one or more organic polymer substances that effectively carbonizes the produced form of the organic polymer porous body made of the organic polymer substance, its carbon precursor, or the porous layer surface made of the carbonized substance. Carbonized bonding material made from the composition kfffi
In-blank for biological hard tissues, which consists of bonding in layers and shaping them into one piece, subjecting them to a treatment to make them insoluble or infusible, and then firing them to a predetermined temperature in an inert atmosphere (Note 1). A
−) + Method for producing the material. (5) The method for producing an implant material for biological hard tissue according to Patent Disclaimer * Scope Item 4, wherein the firing comprises heating to a temperature of at least 800° C. or higher. (6) After firing, vapor phase pyrolytic carbon coating treatment 3ii! Precipitate charcoal throughout the process to smooth the light surface and strengthen capture 1. 5. The method for producing an implant material for biological hard tissue according to claim 4, which is characterized in that it can be used in a living body.