JPS5847178B2 - Materials for manufacturing intraosseous prostheses and intraosseous prostheses made from said materials - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates generally to medicine, and more particularly to intraosseous prostheses used as implants to replace defective bone fragments in the fields of trauma surgery and orthopedics. It concerns improvements in the structural materials used in manufacturing.

The present invention provides for the treatment of traumatic injuries to large bones of the lower extremities.
It is also applied to permanently or temporarily compensate for bone defects following surgical removal of bony neoplasms, or during spontaneous bluish degeneration, or after significant elongation of the bones of the lower extremity. Most desirable.

In the current state of prosthetic surgery, there are many combinations of various materials used as implants or as materials for manufacturing artificial bone.

All endosteal prosthesis manufacturing materials known to date are divided into three basic groups.

That is, they can be classified into metals, ceramics, and polymers.

Additionally, various combinations of these materials are currently in use.

Metals such as titanium, stainless steel, and cobalt, and the endosteal prostheses made from them, are too heavy and difficult to bond with living bone fragments, and the elastic modulus of these materials is an order of magnitude lower than that of bone. It has been found that the high stiffness results in localized osteoporosis at the junction of the bone tissue and the endosteal prosthesis and also overstresses the endosseous prosthesis due to its excessive stiffness.

Corundum Al2O□ has been most commonly used in animal experiments (L.

C1n1 etc., Chirurgia Org, mov,
, 1972゜vnl, 60, A4, p.
p, 423-430; D., Gedulding et al., Abstracts 5IGOT XnI World
d Con-gress, Copenhagen 1975. p
, 75;S.

Hulbert et al., J. Biomed, Ma.
ter, Res, .

1970, vol, 7. pp, 433-456; G, H
eimke etc., Berichts Dtshr
, Keram, Ges, 1973゜50 Kong
ress, S, 4-8; V, Hall, J, Biome
d.

Mater, Res, 1972, part
I, pp-1-4); Among other commonly used substances, mention may be made of the following:

Monolosic acid glass (J, Ben5on, J, Biome
d.

Mater, Res, 1972, part
I, pp. 41-47; J. Colette et al.
J. Bone Surg., 1971.

vol, 53-A, A4. pp, 799-800;
C, 5tani-ski et al., J. Biomed,
Mater-Res-, 1973°vol, 7. A3
, pp. 97-108); - Calcium aluminate (C, Hall, Biocera-mics E
ngineering in Medicine, J.
Wil-ey and 5ons Inc., 19
72,479p; G, Gra-ves et al., J, Bio
med, Mater, Res., 1972.

part I, pp. 91-115; Hulber, S.
t etc., J.

Biomed, Mater, Res, 1970,
vol, 7. pp.

433-456; Ch, Homsy, etc., C
11nical 0r-thopaed ics, 1
972, A89, pp. 220-235)
; Glass ceramics (B, Blencke, etc., Zs
chr, 0rthop, 1974, Bd, 112
, S, 978980; L, Hench et al., J, Bi
omed, Mater.

Res, 1973, vol, 7. Arashi 3,
pp, 25-42; G.

Diotrowski et al., Proceed, 6th
Annual International Bioma
ter, Sympos, CI-emson, 1974
．． - Pure carbon (Ch, Hom5y, etc., C11nical
Orthopedics, 1972. Arashi 89, p.
p, 220-235; J, Ben5on, J, Biom
ed, Mater, Res, 1972゜paru
I, pp. 41-47).

Porous materials must still be considered promising.

This is because the use of such materials reduces the elastic modulus of the endosseous prosthesis and facilitates its connection with the living bone fragment.

In this case, powder metal compression molding (Nilles
J-, LapitskyM, 2CA, J-Biome
d. Mater.

Res, 1973, vol, 7. Wild goose 3,
(see pp. 63-84) or by sintering short titanium wires in vacuum at high temperature and pressure conditions (Gala
nte J, etc., (A, J, Biomed, Mate
r, Res, 1973. vol.

7. Goose 3. pp. 43-61), an intraosseous prosthesis can be produced.

The elastic strain of the material is in the range of 2-4% of the breaking strain, and its elastic modulus is one-seventh that of dense bone tissue.

Of this type of material, porous compression molded titanium with a specific gravity of 3.4 g/CrrL3 and a porosity of 75 mm was most suitable.

In 1971, “Dr.
Stra-umann A,G,'' was granted a patent for Ti-Zr alloy (French Patent No. 2,101,59
No. 9, CZ.

(See A61617100).

In this alloy, both components are used in equal amounts.

Said materials exhibit high corrosion resistance and have a relatively low elastic modulus.

All the materials mentioned above are similar, and with respect to their deformability, comparative energy specifications, elastic modulus and specific gravity, these materials differ significantly from the respective parameters of dense bone tissue.

That is, these materials are far from compatible with the properties of the natural bone material they are intended to replace.

Ceramic materials are notable for their high compressive forces, chemical and biological inertness, and porous structure, but they have low resistance to impact loads in external forces, and are brittle and prone to fracture when subjected to stress.

Apart from the substances mentioned above, certain compounds have been proposed and are being investigated that are gradually being replaced by natural tissue.

Among this type of material, compacted fluorite crystals (S
, Levitt et al., J., Biomed, Mater.

Re51.1969, Vol, 3. pp-683
68), as well as calcium oxide-aluminum oxide complexes (G, Graves et al., J, Biom
ed, Mater.

Res, 1972. part Lpp, 91-115
) or porous calcium phosphate.

The most promising material of this group, aluminum oxide (corundum), which is biologically inert and sufficiently strong when soldered, is brittle and easily destroyed, subject to repeated impact loads on a daily basis. It was found to be unsuitable for repairing large defects in long pipes.

Celsium-type substances provide greater resistance to long tubes (L, Sm1th, etc., Arch
ives of Surg.

1963, vol, 87. pp, 653-661; L,
Sm1th et al., J., Bone It, Surg.
, 1964, vol, 4-A.

A5, p, 1155).

This type of material is actually a more viscous material, namely porous corundum impregnated with epoxy resin.

However, studies have shown that endosseous prostheses made with Celosium lose 45% of their initial hardness after only 6 months in an organism.

This is due to the microporosity of this type of material and its low adhesion to the surrounding tissue.

U.S. Patent No. 3,713,860; C,/, 3-1 and French Patent No. 2.106,242; C1,1A61f
Similar drawbacks are inherent in the bone substitutes described in I/100.

This bone substitute consists of a ceramic substrate impregnated with pure methyl methacrylate and coated with a single layer of polymer.

Polyethylene acrylate is also used as a bone substitute in modern medicine (J.

5cales, 1965, Biomechan
icsand Bioengineering Top
ics, Oxford, pergamon Pr
ess).

However, these substances also turned out to be not powerful enough.

Another process for producing endosteal prosthesis materials by foaming plastisol and repeated heat treatment was developed at the Kiev endosteal prosthesis plant (USSR Patent No. 380,321).
No., 1971).

Many combinations of different endosseous prosthesis materials are currently in use.

A material consisting of a single metal rond with a porous coating applied to at least partially cover the surface (French Patent No. 2,
No. 095,854 “EIJment deprothe
se, chirurgical”, CI, A61
fI/100); Oxides, nitrides,
Materials consisting of titanium or titanium alloys coated with carbide or carbonitride coatings (U.S. Pat. No. 364,6
No. 58 2' Implants of Titaniu
m or Titanium A11oy for t
heSurgical Treatment of B
implants consisting of silicone-coated graphite and boron fibers (French Patent No. 2,104,069, Mati
are the destination a rea
lisation dumps”, CI
, A61 f 110o) ;- Sponge-like ceramic intraosseous prosthesis through which interstitial fluid can flow.

Dual rigidity - characterized by its outer layer as the substrate material (US patent “Re1-offorced Porous
Ceramic Bone Prosth-es i
s'CI, 3-1); - a material consisting of porous alumina impregnated prior to the compression molding process with methyl-methacrylate monomers polymerized under the action of gamma radiation (French Patent No. 2,106.242; C1 ,A61
f110O; U.S. Patent No. 3,713,860, C1,
3-1, British Patent No. 1,314,468; C1, AB
- an implantable intraosseous sleeve formed as a plastic-coated metal rod (see Swiss company 5-u
French Patent No. 2.204,392, C1, A61 f 110, granted to
0); intraosseous prostheses adapted to operate under heavy loading conditions (U.S. Pat. No. 3,683,422; C1,128);
No. 84), this intraosseous prosthesis consists of a 111ill reinforcing element and a fiber or textile material covering the reinforcing element and impregnated with an elastomer.

In one embodiment of the invention, a cam-shaped reinforced fibrous elastomeric element is attached to one end of the reinforcing element.

A textile covering with open pores that allows intergrowth of human tissue is placed against the elastomer-lined surface of the reinforcing element facing the living bone.

The fibrous and textile components of the endoprosthesis are preferably made of Dacron, and silicone rubber is used as the elastomer and Dacron velvet is used as the textile.

Although the endosteal prosthesis described above is the most complete of the intraosseous prostheses known to date, its elastic modulus is much lower than that of dense bone tissue.

Also known are composite materials for bone defect reinforcement consisting of epoxy resin reinforced with randomly placed gypsum or quartz particles.

Its elastic modulus is of the same order of magnitude as that of living bone under loads applied longitudinally to it.

However, all hitherto known materials and endosseous prostheses made therefrom only partially fulfill the requirements imposed on chemically and biologically inert endosseous prostheses.

Although in a few cases the materials and their endosseous prostheses meet the requirements for compressive strength, many of them have surfaces that are porous enough to allow surrounding tissue to grow into them.

As a rule, when developing endosseous prostheses, the biochemical properties of the natural material of the bone tissue and its loading conditions, as well as the natural structure of the long canal as a whole, are not taken into account.

In external forces, a few other materials have higher specific gravity compared to natural bone, are more brittle, have lower resistance to cyclic loads and impact loads, and have insufficient force capacity under load. There is.

Due to the homogeneity and isotropy of the implantable material, it is difficult to use prior art endosseous prostheses as components of natural biochemical systems, such as the anterior tibia and femur, to behave as normal bone. be.

This requirement is extremely important.

This is because only if this requirement is met, the endosseous prosthesis will be effectively protected by natural adaptive mechanisms when subjected to high cyclic loads.

In principle, none of the previously used endosseous prostheses or bone prosthesis materials exhibit stress or hydrodynamic adaptation properties, and said endosseous prostheses do not exhibit any external active muscle It is not acted upon by muscles lζ as tensor muscles, nor by ligaments and fascia as external passive tensor muscles.

Taking all the above factors into account will help to increase the practical safety limit of the intraosseous prosthesis by a factor of three.

However, this can only be achieved using materials and endosseous prosthesis structures that better match the elastic behavior and deformability of the natural bone tissue and of the entire canal replaced by the artificial bone. It becomes possible.

The aim of the invention is to eliminate the above-mentioned drawbacks.

The object of the present invention is to provide a material for making an endosteal prosthesis, which has mechanical properties that are as close as possible to those of the bone tissue to be replaced, as well as an endosseous prosthesis made of said material.

Hereinafter, the present invention will be described in detail with reference to embodiments shown in the drawings.

In the accompanying figures, Figures 1, 2 and 3 show the material for manufacturing an endosteal prosthesis from a reinforcing base made of three nets 1 and 2, net 1 being a chemical and is interposed between two other nets 2 of a biologically inert metal and of a chemically and biologically inert elastic polymeric material (FIG. 4).

The metal net 1 consists of twisted multi-strand titanium wires with a minimum diameter of 0.25 mm.

The wires constituting these nets are joined at their intersections, for example by sintering at high pressure and temperature.

If it is necessary to further strengthen the material of the metal net 1, other biologically and chemically inert alloys,
For example stainless steel or Mo-Cr-C.

Alloy, can be used.

Conversely, if it is desirable to reduce the strength of the material,
Certain chemically inert alloys characterized by low elastic modulus can be used, such as Ti-Zr alloys.

A similar net 2 is made from twisted polymer fibers.

For this purpose, low modulus, chemically and physiologically inert, polymeric materials such as Capron, Lavsan or Dacron are used.

The respective wires of the metal net and the polymer net form an elemental diamond-shaped mesh with an apex angle of 60°.

A mesh with an apex angle of 90 DEG is further suitable if a flat bone reinforcement is to be made with the material of the invention, for example to reconstruct a defective skull, scapula or ilium.

This makes it possible to impart uniformity in the direction of lateral force to the material on the plane where the nets 1 and 2 are arranged.

The metal net 1 and the polymer net 2 of the above structure are placed on top of each other and are held in transverse force to each other, for example by a triple three-dimensional intersecting network, i.e. by suturing the webs with polymer threads (FIG. 4). ).

When using the material of the invention as an endosteal prosthesis of the diaphysis, the metal net and the polymer net are arranged such that the filaments forming the polymer net 2 form an angle of about lO0 with respect to the respective wires of the metal net 1 in a parallel plane. It is preferable to move them relative to each other so as to achieve the following.

To create a flat bone endoprosthesis, these nets can have other mutual orientations, ie 45° from Oo.

The three-dimensional network created by superposing the nets 1 and 2 on top of each other is filled with a binder containing a preservative, for example an epoxy resin containing a hardener.

These drugs are made using conventional processing techniques.

This embedding operation in binder is carried out at room temperature and then
Air dry for 24 hours.

The binder can be polyethylene with a random distribution of fillers such as ink lead or other suitable substances that are biologically compatible with living bone.

The reinforcing base of the intraosseous reinforcement can use a different number of nets 1 and 2 depending on the elastic modulus of the finishing material and the elastic modulus of the metal from which the net 1 is made.

For example, one metal net to one polymer net, or one metal net to three or four polymer nets can be used.

If the elastic modulus of the metal of the net 1 is higher than that of titanium, the number of polymer nets 2 must be increased.

Basically, when titanium is used as the material of the metal net, the percentage of the metal net with respect to the total volume (or cross-sectional area) of the network structure should be in the range of 20-30%, and the percentage of the polymer net should be 60%. ~40 salary range,
The remainder must be taken up by the binding material.

That is, the approximate ratio of metal/polymer/binder is 1:2.
: Must be set to 1.

The volume ratios of the three main elements of the network material are selected such that the resulting material has an elastic behavior and deformation rate close to that of the bone tissue to be reconstructed, but exceeds it in strength.

Since the reinforcement base nets 1 and 2 each have a specific orientation (depending on the purpose of the endosteal prosthesis)
, the novel endosseous prosthesis material according to the present invention has become significantly heterogeneous, and endosseous prostheses made of this material also have similar properties.

The flat bone endoprosthesis is made by forming a plate with a thickness of 5 to 25 mm from a stock made by compression molding a plurality of layers of metal net 1 and polymer net 2 sutured together with a bonding agent. Obtained by making.

In this case, it is preferable to use polyethylene or polytetrafluoroethylene as filler.

The endosteal prosthesis 3 shown in FIGS. 5, 6 and 7 is
Because it is more complex than the previous one and more resistant to heavy variable mechanical loads, it is more suitable for making human flattened anterior reinforcements as well as large long tube reinforcements.

If you look at it in cross section. The intraosseous prosthesis 3 consists of multiple rows of left-handed and right-handed helices (FIGS. 8 and 9) of the material of the invention.

The helices 4 and 5 of each row are interconnected by elements 6 of the same material, and all rows of helices 4 and 5 are embedded in a bonding agent (not shown).

When creating a flat endosseous prosthesis, adjacent rows of helices 4 and 5 of the endosseous prosthesis 3 are arranged in mutually parallel planes.

To produce a long endosseous prosthesis, all helices 4 and 5 are arranged along the longitudinal axis of the endosseous prosthesis.

In various embodiments, a blade consisting of 1 helical rows is configured as follows: (a) three winding directions of adjacent helical rows alternate (FIGS. 5 and 6); (b) 1 All helices in a row have the same direction of winding (Figure 7): (c) The cross sections of helices 4 and 5 in a row are different (Figure 6)
.

For example, in the case of a left-handed distal endosteal prosthesis, the left-handed helix 4
The cross-sectional area of is 2 to 5 times the cross-sectional area of the right-handed helix 5,
The opposite is true for right-handed distal endosteal prostheses.

Flat bone prostheses consisting of plates of this type are characterized by high resistance to parallel shear forces.

The material for producing the flat bone endoprosthesis consists of making a plurality of plates consisting of helices arranged in rows on top of each other and embedding them in an amorphous bonding agent containing a hardening agent. Obtained by compression molding.

The intraosseous prosthesis of the present invention can also be applied to correct defects in long bones.

In this case, the material consisting of the plate of the type mentioned above has a thickness of 1
~3.5 cIrL, twisted in a helical pattern (not shown) of type 2, ie, left-handed and right-handed.

The helices thus produced are embedded in an amorphous binder containing a sustained-acting preservative.

In this way, blank or finished cylindrical endosteal prostheses for prosthesizing fragments or entire shafts of bones subject to relatively low loads, such as the humerus, ulna, radius, clavicle, as well as the carpus or ulna. You can get things.

Cylindrical blanks for endosseous prostheses are
It can be machined or ground to obtain a predetermined length or cross-sectional area.

Large long endosseous prostheses of the lower limb, such as the femur or tibia, are made of the material according to the invention and correspond by their biochemical properties to the natural prototypes, namely the human femur and tibia; In terms of strength, it is several times stronger than this.

FIG. 10 shows one possible embodiment of a trabecular endofemoral prosthesis.

The endosseous prosthesis γ of the femoral shaft is formed as a helical sheath 8 with a central bearing rod 9, said rod 9 being made of titanium, for example, and extending to the endosseous prosthesis 7 to provide greater stiffness. The distal attachment of the intraosseous prosthesis for connection with the epiphyseal midsection is associated with an assembly (not shown).

The internal space of the exterior part 8 accommodates a plurality of helices 10, 11, which are made of the material of the invention and have a smaller outer circumference.

Exterior part 8 and each helix 10 and 11 arranged inside it
consists of rows of helices 4 and 5, and these helices are
They are made of the reticular material mentioned above and are interconnected by elements 6 (FIGS. 5 and 6) of the same material.

In the case of a left-handed lower extremity endoprosthesis, these helices are made by wrapping the plate made as in paragraph 1a1 above into a cylindrical rond of diameter 1-1.5 cfrL; The two helices 10 placed at the front and rear of the shape are left-handed helices.

In the middle, two helices 11 placed lateral to the center of the endosteal prosthesis have a diameter of up to 1.5 cm, are right-handed, and are separated from the plate as described in paragraph Icf.

In this case, the diameter of the left-handed helix 4 in the lateral force direction is smaller than the diameter of the right-handed helix 5 in the lateral force direction (FIG. 6).

A left-handed helical body 12 having a small cross section and consisting of a "b1" type plate (FIG. 7) including a right-handed helix 5 is interposed between the four helices 10 and 11.

The number of helical bodies 12 is variable.

More specifically, in the case of a right-handed lower limb endoprosthesis, the winding directions of all the helices 10, 11, 12 are reversed.

That is, the right-handed lower limb intraosseous prosthesis has the following structure:
It is a mirror image of the left-handed lower limb intraosseous prosthesis 7.

The entire hollow space of the prosthesis 7 is occupied by a binder such as an epoxy resin containing a filler.

One example of a human endotibial prosthesis is shown in Figures 11 and 12.
Illustrated in the figure.

In the endosteal prosthesis of the tibial diaphysis shown in FIGS. 11 and 12, the outer helical sheath 8 has a cross-sectional shape close to an isosceles triangle.

At the vertices of this triangle there are arranged helical bodies 10 and 11 made of the material of the invention, whereas in the center of the triangle there is arranged a metal bearing rod, for example made of titanium. .

This rod 9 is also used for the connection of the endosseous prosthesis 7 to the patient's bone.

FIG. 11 shows a left-handed lower limb intraosseous prosthesis 7.

The helix 10 placed at the apex of the small bevel is left-handed.

In order to make this spiral 10, 'a1 type or 1c1 type
It is desirable to use a type plate in which the helix 4 having a large cross-sectional area is left-handed and the helical 5 having a small cross-sectional area is right-handed.

The helical body 11 disposed at the other apex of the triangle and the helical body of the exterior portion 8 are right-handed, and are similarly made of a″-type or C″-type plates.

In order to make this intraosseous prosthesis even more compact, a plurality of left-handed helices of much smaller cross-section made of "a" type plates consisting of right-handed helices 5 are used.
and 11 can be filled in.

The structure of the right-handed lower limb intraosseous prosthesis (Fig. 12) is similar to the structure described above, except that the winding direction of all helices 9, 10, 11 of the intraosseous prosthesis 7 is reversed. Similar.

FIG. 13 shows an embodiment of the helical body 12 of the intraosseous prosthesis 7, which is formed by twisting small-section helical elements 10 made of 1c'' type plates into a rope shape.

[Brief explanation of the drawing]

Fig. 1 shows a metal net forming the reinforcing base of the material of the intraosseous prosthesis according to the invention, Fig. 2 shows a polymer net constituting the reinforcing base of the same material, and Fig. 3 shows the net in the material of the invention. 4 is a plan view of an embodiment of the arrangement, FIG. 4 is a sectional view of an embodiment of the reinforcing base of the material according to the invention, FIGS. 5, 6 and 7 are each made of the material according to the invention. FIGS. 8 and 9 show the winding direction of the helical body made of the material of the invention, FIGS. 10, 11 and 12. 13 is a cross-sectional view showing an embodiment of an intraosseous prosthesis for reconstructing a main bone, and FIG. 13 is a perspective view showing a helical cross-section of the intraosseous prosthesis according to the present invention. 1.2...Net, 3...Intraosseous prosthesis material, 4,5
... Helical body, 6... Surrounding element, 8... Exterior part helical body, 10.11... Internal helical body, 12... Helical body.

Claims (1)

[Scope of Claims] 1. In a material for producing an intraosseous prosthesis as a reinforcing base filled with a binder containing a preservative, the reinforcing base has a layered structure and includes two types of nets 1 and 2. the force net 2 is made of a chemically and biologically inert metal, the other net 2 is made of a chemically and biologically inert elastic polymeric material, and the net 1, 2 is filled with a binder, and the volume ratio of said metal net 1 to the total material is chosen such that the elastic modulus of the material approximates that of the bone tissue to be replaced. Characteristic materials for manufacturing intraosseous prostheses. 2. Material according to claim 1, characterized in that the wires of the nets 1, 2 have a parallelogram mesh with an acute angle of 60°. 3. The wires of the nets 1, 2 are arranged in parallel planes, separated from each other and offset from each other by a maximum angle of 10°. material. 4. The material according to any one of claims 1 to 3, wherein the volume ratio of the metal net 1 to the entire material is within a range of 1:5 to 1:3. 5. Material according to claim 1, characterized in that the binder is essentially an epoxy resin containing a curing agent. 6. Material according to claim 1, characterized in that the binder is essentially polyethylene containing graphite filler. 7 A chemically and biologically inert metal net 1 and a chemically and biologically inert elastic polymer net 2 have a layered structure, and the space between both nets 1 and 2 is filled with a bond containing a preservative. In addition, a reinforcing base selected such that the volume ratio between the metal net 1 and the entire material approximates the elastic modulus of the material to the elastic modulus of the bone tissue to be replaced is inserted into the bone. The reinforcing base is prepared as a material for a shape, and a plurality of helical bodies formed by winding this reinforcing base are arranged in parallel, and the reinforcing base is arranged to meander between the helical bodies to wrap each helical body, and the helical body 4 , 5 are all embedded in a binding agent to form a flat bone prosthesis. 8 The winding force of the helical bodies 4 and 5 adjacent to each other is right-handed and the winding force of the other force is left-handed. 8. Intraosseous prosthesis according to claim 7, characterized in that it has a shape. 9 A layered structure of a chemically and biologically inert metal net and a chemically and biologically inert elastic polymer net, and the space between both nets is filled with a binder containing a preservative. , a reinforcing base was prepared in which the volume ratio of the metal net to the entire material was selected such that the elastic modulus of the material approximated the elastic modulus of the bone tissue to be replaced, and this reinforcing base was wound to form A flat intraosseous prosthesis is formed by arranging a plurality of helical bodies in parallel, wrapping the reinforcing base in a meandering manner between the helical bodies, and embedding all of the helical bodies in a bonding agent. The shape is used as a material for a columnar intraosseous prosthesis,
The flat material is formed into a cylindrical shape to form a helical exterior portion 8,
In the internal space of the exterior part 8, a plurality of helical bodies 10, 11 are arranged in the longitudinal force direction of the exterior part 8, and a helical body 12 is formed by twisting a plurality of small-diameter helical bodies. The outer circumference of each helical body is smaller than the outer circumference of the exterior part 8, and a support rod 9 is provided in the center of the exterior part 8 in the longitudinal direction thereof. A trabecular endosseous prosthesis characterized in that all these endosseous prosthesis components are embedded in a bonding agent. 10. The columnar intraosseous prosthesis according to claim 9, wherein the cross-sectional shape of the exterior portion 8 approximates a triangle, and the helical bodies 10 and 11 are arranged at the vertices of the triangle. 11 A helical body located at one vertex of the triangle 10.
11. The trabecular intraosseous prosthesis according to claim 10, wherein the winding direction of the helical body 11 is opposite to the winding direction of the helical bodies 10, 11 located at the other vertices of the triangle.