JPH0414031B2 - - Google Patents
Info
- Publication number
- JPH0414031B2 JPH0414031B2 JP59005729A JP572984A JPH0414031B2 JP H0414031 B2 JPH0414031 B2 JP H0414031B2 JP 59005729 A JP59005729 A JP 59005729A JP 572984 A JP572984 A JP 572984A JP H0414031 B2 JPH0414031 B2 JP H0414031B2
- Authority
- JP
- Japan
- Prior art keywords
- bone
- inducing material
- calcium phosphate
- osteogenesis
- present
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
- 210000000988 bone and bone Anatomy 0.000 claims description 57
- 239000000463 material Substances 0.000 claims description 32
- 230000001939 inductive effect Effects 0.000 claims description 31
- 230000011164 ossification Effects 0.000 claims description 21
- QORWJWZARLRLPR-UHFFFAOYSA-H tricalcium bis(phosphate) Chemical compound [Ca+2].[Ca+2].[Ca+2].[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O QORWJWZARLRLPR-UHFFFAOYSA-H 0.000 claims description 18
- 239000001506 calcium phosphate Substances 0.000 claims description 17
- 229910000389 calcium phosphate Inorganic materials 0.000 claims description 17
- 235000011010 calcium phosphates Nutrition 0.000 claims description 17
- 238000004519 manufacturing process Methods 0.000 claims description 12
- 239000011148 porous material Substances 0.000 claims description 5
- 239000002344 surface layer Substances 0.000 claims 1
- 210000001519 tissue Anatomy 0.000 description 8
- 206010020649 Hyperkeratosis Diseases 0.000 description 7
- 210000003275 diaphysis Anatomy 0.000 description 7
- 210000001185 bone marrow Anatomy 0.000 description 6
- 239000011575 calcium Substances 0.000 description 6
- 239000006104 solid solution Substances 0.000 description 4
- 230000032683 aging Effects 0.000 description 3
- 230000001054 cortical effect Effects 0.000 description 3
- 239000000843 powder Substances 0.000 description 3
- 230000002787 reinforcement Effects 0.000 description 3
- -1 alumina-silica glass Chemical compound 0.000 description 2
- 229910010293 ceramic material Inorganic materials 0.000 description 2
- 239000002131 composite material Substances 0.000 description 2
- 239000007769 metal material Substances 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 239000000203 mixture Substances 0.000 description 2
- 210000002997 osteoclast Anatomy 0.000 description 2
- 239000002245 particle Substances 0.000 description 2
- 239000002994 raw material Substances 0.000 description 2
- 238000001356 surgical procedure Methods 0.000 description 2
- 229920003002 synthetic resin Polymers 0.000 description 2
- 239000000057 synthetic resin Substances 0.000 description 2
- 230000007306 turnover Effects 0.000 description 2
- 206010000372 Accident at work Diseases 0.000 description 1
- 229910014497 Ca10(PO4)6(OH)2 Inorganic materials 0.000 description 1
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 description 1
- 229910019142 PO4 Inorganic materials 0.000 description 1
- 229910004283 SiO 4 Inorganic materials 0.000 description 1
- GWEVSGVZZGPLCZ-UHFFFAOYSA-N Titan oxide Chemical compound O=[Ti]=O GWEVSGVZZGPLCZ-UHFFFAOYSA-N 0.000 description 1
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 description 1
- 229910052782 aluminium Inorganic materials 0.000 description 1
- PNEYBMLMFCGWSK-UHFFFAOYSA-N aluminium oxide Inorganic materials [O-2].[O-2].[O-2].[Al+3].[Al+3] PNEYBMLMFCGWSK-UHFFFAOYSA-N 0.000 description 1
- 229910052788 barium Inorganic materials 0.000 description 1
- 239000011230 binding agent Substances 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 210000002449 bone cell Anatomy 0.000 description 1
- 229910052793 cadmium Inorganic materials 0.000 description 1
- 229910052791 calcium Inorganic materials 0.000 description 1
- 229910052799 carbon Inorganic materials 0.000 description 1
- 150000001875 compounds Chemical class 0.000 description 1
- 238000005520 cutting process Methods 0.000 description 1
- 229940127089 cytotoxic agent Drugs 0.000 description 1
- 239000002254 cytotoxic agent Substances 0.000 description 1
- 231100000599 cytotoxic agent Toxicity 0.000 description 1
- 230000018044 dehydration Effects 0.000 description 1
- 238000006297 dehydration reaction Methods 0.000 description 1
- 238000000280 densification Methods 0.000 description 1
- 230000002542 deteriorative effect Effects 0.000 description 1
- 239000003814 drug Substances 0.000 description 1
- 238000010828 elution Methods 0.000 description 1
- 210000002745 epiphysis Anatomy 0.000 description 1
- 238000010304 firing Methods 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 229910052742 iron Inorganic materials 0.000 description 1
- 238000000462 isostatic pressing Methods 0.000 description 1
- 229910052745 lead Inorganic materials 0.000 description 1
- 229910052749 magnesium Inorganic materials 0.000 description 1
- 229910021645 metal ion Inorganic materials 0.000 description 1
- 238000002156 mixing Methods 0.000 description 1
- 229910052759 nickel Inorganic materials 0.000 description 1
- 230000000399 orthopedic effect Effects 0.000 description 1
- 230000002188 osteogenic effect Effects 0.000 description 1
- 239000011505 plaster Substances 0.000 description 1
- 238000005498 polishing Methods 0.000 description 1
- 229920003229 poly(methyl methacrylate) Polymers 0.000 description 1
- 239000004926 polymethyl methacrylate Substances 0.000 description 1
- 229910052700 potassium Inorganic materials 0.000 description 1
- 230000001737 promoting effect Effects 0.000 description 1
- 238000011084 recovery Methods 0.000 description 1
- 239000011347 resin Substances 0.000 description 1
- 229920005989 resin Polymers 0.000 description 1
- 239000002002 slurry Substances 0.000 description 1
- 229910052708 sodium Inorganic materials 0.000 description 1
- 229910001220 stainless steel Inorganic materials 0.000 description 1
- 239000010935 stainless steel Substances 0.000 description 1
- 229910052712 strontium Inorganic materials 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
- 208000024891 symptom Diseases 0.000 description 1
- 229910052715 tantalum Inorganic materials 0.000 description 1
- GUVRBAGPIYLISA-UHFFFAOYSA-N tantalum atom Chemical compound [Ta] GUVRBAGPIYLISA-UHFFFAOYSA-N 0.000 description 1
- 229910052719 titanium Inorganic materials 0.000 description 1
- 239000010936 titanium Substances 0.000 description 1
- OGIDPMRJRNCKJF-UHFFFAOYSA-N titanium oxide Inorganic materials [Ti]=O OGIDPMRJRNCKJF-UHFFFAOYSA-N 0.000 description 1
- 231100000331 toxic Toxicity 0.000 description 1
- 230000002588 toxic effect Effects 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
- 229910052725 zinc Inorganic materials 0.000 description 1
Description
【発明の詳細な説明】 本発明は、骨生成誘起材に関するものである。[Detailed description of the invention] TECHNICAL FIELD The present invention relates to an osteogenesis inducing material.
整形外科等の外科医療の分野において、老齢化
社会における老人の骨の老化、劣化の補強及び骨
折後の骨の修復機能回復の促進は、今日、ほとん
ど行なわれておらず、患者の回復、リハビリテー
シヨン等に依存しているのが現状である。 In the field of surgical medicine such as orthopedics, there is little work being done today to strengthen the aging and deteriorating bones of elderly people in an aging society and to promote the restoration of bone repair function after fractures. The current situation is that it depends on stations, etc.
従来、骨手術後の骨の補綴材として、ステンレ
ス、チタン、タンタルなどの金属材料やアルミ
ナ、酸化チタン、アルミナ−シリカ系ガラス、炭
素などのセラミツクス材料が用いられているが、
金属材料は生体組織との親和性が悪く、金属イオ
ンの溶出が骨細胞毒として作用し、また従来のセ
ラミツクス材料は骨との親和性が良く、組織と反
応せず、耐久性に富むものではあるが、骨の硬組
織とは全く異質であるために骨組織との固着が良
好でなく、毒性はないものの、生体内で死組織と
して存在する。 Conventionally, metal materials such as stainless steel, titanium, and tantalum, and ceramic materials such as alumina, titanium oxide, alumina-silica glass, and carbon have been used as bone prosthetic materials after bone surgery.
Metal materials have poor affinity with living tissues, and the elution of metal ions acts as a bone cytotoxic agent, while conventional ceramic materials have good affinity with bones, do not react with tissues, and are highly durable. However, since it is completely different from the hard tissue of bone, it does not adhere well to the bone tissue, and although it is not toxic, it exists as dead tissue in vivo.
本発明は上述の事情に鑑みて開発したものであ
り、人体組織に為害性がなく、新生骨の生成を誘
起し、しかも生体新和性が極めて高いリン酸カル
シウム系焼結体で構成された骨生成誘起材を提供
するものである。 The present invention was developed in view of the above-mentioned circumstances, and is an osteogenic sintered body made of a calcium phosphate-based sintered body that is not harmful to human tissue, induces new bone formation, and has extremely high bionewability. It provides an inducing material.
本発明の骨生成誘起材は、骨髄腔内に達する様
に挿入するため、新生骨の誘起は早く、自ら吸収
され消滅するため、骨癒合後の抜去の必要がない
ので、手術の回数を極力へらす必要がある場合、
特に有効である。特に、先端を多孔質体としたも
のにおいては、骨髄腔に達した部位は、短期間で
すべての新生骨でおきかわり、その後、その形が
いをとどめることなしに骨の補強強化を行なうこ
とができる。 Since the bone production-inducing material of the present invention is inserted so as to reach the bone marrow cavity, new bone is induced quickly and is absorbed and disappears by itself, so there is no need to remove it after bone union, so the number of surgeries can be minimized. If you need to reduce
Particularly effective. In particular, with porous tips, the area that reaches the medullary cavity is completely replaced by new bone in a short period of time, and thereafter the bone can be reinforced and strengthened without losing its shape. can.
本願発明でいうリン酸カルシウム系焼結体は、
リン酸カルシウム化合物及びその固溶体であるも
のの焼結体であり、
CaHPO4、Ca3、（PO4）2、Ca5（PO4）3OH、
Ca4O（PO4）2、Ca10（PO4）6（OH）2、CaP4O11、Ca
（PO3）2、Ca2P2O7、Ca（HPO4）2H2Oのアパタイ
トと呼ばれる１群の化合物を包含し、一般に
M10 2+（Z5+O4）6X2 -で示され、
Ｍ：Ca、Ba、Sr、Mg、Na、Ｋ、Pb、Cd、
Zn、Ni、Fe、Al、ctc
ZO4：PO4、ASO4、VO4、SO4、SiO4、
CO3etc
Ｘ：Ｆ、OH、Cl、Ｏ、Br、
などの一種以上で置換されていてもよい。 The calcium phosphate sintered body referred to in the present invention is
It is a sintered body of calcium phosphate compounds and their solid solutions, including CaHPO 4 , Ca 3 , (PO 4 ) 2 , Ca 5 (PO 4 ) 3 OH,
Ca4O ( PO4 ) 2 , Ca10 ( PO4 ) 6 (OH) 2 , CaP4O11 , Ca
It includes a group of compounds called apatites, including (PO 3 ) 2 , Ca 2 P 2 O 7 , Ca(HPO 4 ) 2 H 2 O, and is generally
M 10 2+ (Z 5+ O 4 ) 6 X 2 - , M: Ca, Ba, Sr, Mg, Na, K, Pb, Cd,
Zn, Ni, Fe, Al, ctc ZO 4 :PO 4 , ASO 4 , VO 4 , SO 4 , SiO 4 ,
CO 3 etc. X: May be substituted with one or more of F, OH, Cl, O, Br, etc.
第１図、第２図、第３図第３−ａ図は、本発明
の骨生成誘起材を例示しているが、先細突出部を
有するものである。 1, 2, and 3-3-a illustrate the bone generation-inducing material of the present invention, which has a tapered protrusion.
先端部を先細突出部となした理由は、該部が容
易に骨髄腔内に挿入、到達されるため、骨髄内で
新生骨の生成を誘起し、ターンオーバー（本発明
材と新生骨との置換）の急速化が達成されるから
である。 The reason for making the tip part a tapered protrusion is that this part can be easily inserted and reached into the bone marrow cavity, which induces the generation of new bone within the bone marrow and reduces turnover (between the material of the present invention and new bone). This is because rapid substitution (replacement) is achieved.
第１図において１１は、リン酸カルシウム系焼
結体だけから成るものであるが、これは、新生骨
の誘起が緩慢であるが、骨の補強促進を長期にわ
たり行なうようには有効なものである。この様
な、骨生成誘起材１の製造方法としては、たとえ
ば、リン酸カルシウム粉末原料を水及び有機バイ
ンダーと混合した泥しようを、石膏型枠に流し込
み、脱水後取り出し、1000〜1450℃で焼成するこ
とにより造られる。 In FIG. 1, reference numeral 11 is composed only of a calcium phosphate sintered body, which is slow in inducing new bone formation, but is effective in promoting bone reinforcement over a long period of time. As a method for producing the bone formation inducing material 1, for example, a slurry prepared by mixing calcium phosphate powder raw materials with water and an organic binder is poured into a plaster mold, taken out after dehydration, and fired at 1000 to 1450°C. built by.
第２図は骨生成誘起材の上部２１が、リン酸カ
ルシウム系焼結体であり、先端部２２が30〜90％
の空孔を有するリン酸カルシウム多孔体から成る
ものである。この多孔体の孔径は、１〜600μで
あり、好ましくは50〜300μであるが、骨細胞が
進入可能で、連続した空孔を有していれば良い。
この様な骨生成誘起材の製造法としては、たとえ
ば、リン酸カルシウム粉末原料100重量部に１〜
600μの粒径をもつ有機合成樹脂たとえばポリメ
チルメタクリレート樹脂30〜80重量部加え、アル
コールを媒体として、混合乾燥し、この混合物を
ゴム風船につめ、最後にリン酸カルシウム粉末だ
けを充填した後、50〜2000Kg／cm3で静水圧プレス
を行ない成形体を作り、この成形体を室温から
300〜500℃に徐々に加熱し、有機合成樹脂粒子を
熱分解、除去し、その後、電気炉で800〜1450℃
に加熱焼成することによつて、リン酸カルシウム
及びその固溶体と、リン酸カルシウム多孔体の複
合体を製造することができる。この複合体を切
削、研摩加工ののち第２図に示す骨生成誘起材が
製造される。 In Fig. 2, the upper part 21 of the osteogenesis inducing material is a calcium phosphate-based sintered body, and the tip part 22 is 30 to 90%
It is made of a calcium phosphate porous material having pores of. The pore diameter of this porous body is 1 to 600 μm, preferably 50 to 300 μm, but it is sufficient that the pores are continuous and allow bone cells to enter.
As a method for producing such a bone production-inducing material, for example, 1 to 100 parts by weight of calcium phosphate powder raw material is added.
Add 30 to 80 parts by weight of an organic synthetic resin such as polymethyl methacrylate resin with a particle size of 600μ, mix and dry using alcohol as a medium, fill this mixture into a rubber balloon, and finally fill it with only calcium phosphate powder. A molded body is made by isostatic pressing at 2000Kg/ cm3 , and this molded body is heated from room temperature.
Gradually heated to 300-500℃ to thermally decompose and remove organic synthetic resin particles, then heated to 800-1450℃ in an electric furnace.
By heating and firing, a composite of calcium phosphate and its solid solution and a calcium phosphate porous body can be produced. After cutting and polishing this composite, the bone production-inducing material shown in FIG. 2 is manufactured.
さらに第３図は、リン酸カルシウム系焼結体に
骨と強固に保持される様にネジ切りを行なつたも
のである。したがつて、骨に埋植後、骨生成誘起
材が抜けることなくターンオーバーが終るまで骨
と一体化される。 Further, in FIG. 3, threads are cut into the calcium phosphate sintered body so that it can be firmly attached to the bone. Therefore, after being implanted in the bone, the osteogenesis-inducing material does not come off and is integrated with the bone until the turnover is completed.
この様な骨生成誘起材の製造方法は、第２図に
示す骨生成誘起材を製造後、リン酸カルシウム系
焼結体即ち第３図の３１部にネジ切り加工をほど
こし製造される。第３−ａ図は、本発明骨生成誘
起材の偏形くさび形に形成した例を示す。 The method for manufacturing such an osteogenesis inducing material is as follows: After producing the osteogenesis inducing material shown in FIG. 2, the calcium phosphate sintered body, that is, the portion 31 in FIG. 3, is threaded. Fig. 3-a shows an example of the osteogenesis-inducing material of the present invention formed into a deformed wedge shape.
本発明の骨生成誘起材は、第４図に示す様に、
骨幹部に使用する場合、骨幹部の大きさに応じて
骨生成誘起材の寸法を変化させ、必要な個数だ
け、骨幹部に骨生成誘起材の大きさに応じてドリ
ルで穿孔し、好ましくは、前後左右に交互に穿孔
し、骨生成誘起材の先端４１を骨髄部４３まで達
する様に挿入し、皮質骨４２で固定する。この様
に固定された骨幹部では、外骨膜性仮骨の形成と
ともに、骨髄部に達した先端部から短期間で海綿
骨らしき新生骨の誘起が見られ、さらには、内骨
膜性仮骨を形成し、この内骨膜性仮骨はさらに緻
密骨に変化していく。又、骨髄腔内にできた海綿
骨らしき新生骨及び外骨膜性仮骨は時間の経過と
ともに不必要な部位は、破骨細胞によつて生体内
に吸収され、必要な部位だけの新生骨が残る。こ
の様に、短期間で本発明の骨生成誘起材により、
新生骨の緻密化が進行し、骨組織と同一の組織を
もつ緻密骨になり、骨の補強の促進ならびに強化
を行なうことができる。又、本発明の骨生成誘起
材は、長管骨における骨幹部だけでなく、骨端
部、短骨、扁平骨などにも、同じ形状で寸法を変
えることにより使用することができる。 As shown in FIG. 4, the bone production-inducing material of the present invention has the following properties:
When used on the diaphysis, the dimensions of the osteogenesis-inducing material are changed according to the size of the diaphysis, and the required number of holes are drilled into the diaphysis according to the size of the osteogenesis-inducing material, preferably. , holes are made alternately in the front, back, left and right, and the tip 41 of the osteogenesis inducing material is inserted so as to reach the bone marrow part 43 and fixed with the cortical bone 42. In the diaphysis fixed in this way, along with the formation of an experiosteal callus, new bone resembling cancellous bone is induced in a short period of time from the tip that reaches the medullary region, and furthermore, endoperiosteal callus is formed. This endoperiosteal callus further transforms into compact bone. In addition, over time, new bone that looks like cancellous bone and extraperiosteal callus that are formed in the bone marrow cavity are absorbed into the body by osteoclasts in unnecessary parts, and new bone is created only in the necessary parts. remain. In this way, the osteogenesis inducing material of the present invention can be used in a short period of time.
The densification of the new bone progresses, and it becomes a densified bone with the same tissue as bone tissue, which can promote and strengthen bone reinforcement. Furthermore, the bone production-inducing material of the present invention can be used not only for the diaphysis of long bones, but also for the epiphyses, short bones, flat bones, etc., by changing the dimensions with the same shape.
実施例
第２図に示す骨生成誘起材を前記の方法で製造
し、犬の大髄骨骨幹部に使用した。本発明の骨生
成誘起材の寸法は上部外径２mm、長さ２〜３mmと
し、骨幹部を７mm間隔で２mmの穴を４個あけ、本
発明の骨生成誘起材を先端が骨髄部に達する様に
挿入した。この様に骨生成誘起材を挿入した骨幹
部では、４週経過後、骨生成誘起材を挿入した部
位とその近傍では、外骨膜性仮骨が形成され、骨
髄腔内は海綿骨らしき新生骨の誘起が見られ、さ
らに８週経過後、骨髄腔内は、内骨膜性仮骨が形
成され一部は、緻密骨に変化していた。さらに13
週経過後、外骨膜性仮骨と、骨髄腔内にできた不
必要な新生骨は破骨細胞によつて生体内に吸収さ
れ、必要な部位だけの新生骨が残つており、皮質
骨は新生骨でおおわれ、この新生骨は、骨組織と
同一の組織をも緻密骨になつていた。Example The bone production-inducing material shown in FIG. 2 was produced by the method described above and used on the large medullary bone shaft of a dog. The dimensions of the osteogenesis inducing material of the present invention are 2 mm in the upper outer diameter and 2 to 3 mm in length. Four 2 mm holes are made at 7 mm intervals in the diaphysis, and the tip of the osteogenesis inducing material of the present invention reaches the bone marrow. I inserted it like this. In the diaphysis into which the osteogenesis-inducing material was inserted in this way, after 4 weeks, extraperiosteal callus is formed at the site where the osteogenesis-inducing material was inserted and in its vicinity, and new bone that looks like cancellous bone is formed within the medullary cavity. After 8 weeks had passed, endoperiosteal callus was formed in the medullary cavity, and some of it had changed to compact bone. 13 more
After a week, the extraperiosteal callus and unnecessary new bone formed within the medullary cavity are resorbed into the body by osteoclasts, leaving only the necessary new bone, and cortical bone remains. It was covered with new bone, and this new bone had the same tissue as the bone tissue, which had also become compact bone.
以上の如く、本発明によるリン酸カルシウムを
主体とする骨生成誘起材は、寸法を変えることに
より、又、使用本数を変化させることにより、症
状に応じて種々多様に使用でき、しかも、挿入
後、新生骨に誘起は早く、短期間のうちに骨組織
と同一組織になり、骨の補強に促進ならびに強化
に対して有効に作用する。即ち、今日の老齢化社
会における社会福祉、労働災害などの骨折後の機
能回復に対して本発明の骨生成誘起材は、大きく
効果がある。 As described above, the osteogenesis-inducing material based on calcium phosphate according to the present invention can be used in a variety of ways depending on the symptoms by changing the dimensions and the number of pieces used. It is quickly induced in bones, becomes the same tissue as bone tissue in a short period of time, and acts effectively to promote and strengthen bone reinforcement. That is, the bone production-inducing material of the present invention is highly effective for social welfare in today's aging society and for functional recovery after fractures caused by industrial accidents.
第１図、第２図、第３図及び第３−ａ図は本発
明の骨生成誘起材の具体例を示す。
１１，２１……リン酸カルシウム焼結体及びそ
の固溶体、２２，３２……リン酸カルシウム多孔
体、３１……リン酸カルシウム焼結体及びその固
溶体、第４図は本発明の骨生成誘起材の使用例を
示す。４１……本発明の骨生成誘起材、４２……
皮質骨、４３……骨髄腔。
FIG. 1, FIG. 2, FIG. 3, and FIG. 3-a show specific examples of the bone production-inducing material of the present invention. 11, 21... Calcium phosphate sintered body and its solid solution, 22, 32... Calcium phosphate porous body, 31... Calcium phosphate sintered body and its solid solution. FIG. 4 shows an example of use of the bone formation inducing material of the present invention. 41... Osteogenesis inducing material of the present invention, 42...
Cortical bone, 43...Medullary cavity.
Claims (1)
突出部を有し、且つ、少なくとも、前記焼結体の
一部分は多孔質体からなる骨生成誘起材。 ２ その表層の一部にネジ切り部が形成された特
許請求の範囲第１項に記載の骨生成誘起材。[Scope of Claims] 1. A bone formation-inducing material which is mainly composed of a calcium phosphate-based sintered body, has a tapered protrusion, and at least a portion of the sintered body is made of a porous material. 2. The bone production-inducing material according to claim 1, wherein a threaded portion is formed in a part of the surface layer.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP59005729A JPS60150756A (en) | 1984-01-18 | 1984-01-18 | Bone formation inducing material |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP59005729A JPS60150756A (en) | 1984-01-18 | 1984-01-18 | Bone formation inducing material |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS60150756A JPS60150756A (en) | 1985-08-08 |
| JPH0414031B2 true JPH0414031B2 (en) | 1992-03-11 |
Family
ID=11619206
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP59005729A Granted JPS60150756A (en) | 1984-01-18 | 1984-01-18 | Bone formation inducing material |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS60150756A (en) |
Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5766251A (en) * | 1992-03-13 | 1998-06-16 | Tomihisa Koshino | Wedge-shaped spacer for correction of deformed extremities |
| US5868749A (en) * | 1996-04-05 | 1999-02-09 | Reed; Thomas M. | Fixation devices |
| US6008433A (en) * | 1998-04-23 | 1999-12-28 | Stone; Kevin R. | Osteotomy wedge device, kit and methods for realignment of a varus angulated knee |
| JP5138313B2 (en) * | 2007-08-27 | 2013-02-06 | 株式会社パイロットコーポレーション | Biological structure |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS59189841A (en) * | 1983-04-09 | 1984-10-27 | 三菱鉱業セメント株式会社 | Sealing gasket for filling bone carnal |
-
1984
- 1984-01-18 JP JP59005729A patent/JPS60150756A/en active Granted
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS59189841A (en) * | 1983-04-09 | 1984-10-27 | 三菱鉱業セメント株式会社 | Sealing gasket for filling bone carnal |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS60150756A (en) | 1985-08-08 |
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