JPH01126977A - Filler for crack or opening of bone - Google Patents
Filler for crack or opening of boneInfo
- Publication number
- JPH01126977A JPH01126977A JP62285462A JP28546287A JPH01126977A JP H01126977 A JPH01126977 A JP H01126977A JP 62285462 A JP62285462 A JP 62285462A JP 28546287 A JP28546287 A JP 28546287A JP H01126977 A JPH01126977 A JP H01126977A
- Authority
- JP
- Japan
- Prior art keywords
- sintered body
- porous sintered
- bone
- tcp
- beta
- 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.)
- Pending
Links
- 210000000988 bone and bone Anatomy 0.000 title claims abstract description 56
- 239000000945 filler Substances 0.000 title abstract description 5
- 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 abstract description 33
- 239000000463 material Substances 0.000 claims abstract description 26
- 229910052588 hydroxylapatite Inorganic materials 0.000 claims abstract description 14
- XYJRXVWERLGGKC-UHFFFAOYSA-D pentacalcium;hydroxide;triphosphate Chemical compound [OH-].[Ca+2].[Ca+2].[Ca+2].[Ca+2].[Ca+2].[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O.[O-]P([O-])([O-])=O XYJRXVWERLGGKC-UHFFFAOYSA-D 0.000 claims abstract description 14
- 210000003205 muscle Anatomy 0.000 claims abstract description 6
- 230000007547 defect Effects 0.000 claims description 18
- 238000011049 filling Methods 0.000 claims description 14
- 239000011800 void material Substances 0.000 claims description 9
- 239000003462 bioceramic Substances 0.000 claims description 7
- 239000008280 blood Substances 0.000 abstract description 4
- 210000004369 blood Anatomy 0.000 abstract description 4
- 210000001519 tissue Anatomy 0.000 abstract description 4
- 230000003387 muscular Effects 0.000 abstract 1
- 239000000919 ceramic Substances 0.000 description 10
- 238000010586 diagram Methods 0.000 description 8
- 239000000843 powder Substances 0.000 description 7
- 239000002002 slurry Substances 0.000 description 7
- 239000004372 Polyvinyl alcohol Substances 0.000 description 4
- 230000017531 blood circulation Effects 0.000 description 4
- 238000004090 dissolution Methods 0.000 description 4
- 229920002451 polyvinyl alcohol Polymers 0.000 description 4
- 239000011148 porous material Substances 0.000 description 4
- 238000001035 drying Methods 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 238000000605 extraction Methods 0.000 description 3
- 210000004195 gingiva Anatomy 0.000 description 3
- 238000002513 implantation Methods 0.000 description 3
- 239000000203 mixture Substances 0.000 description 3
- 210000000963 osteoblast Anatomy 0.000 description 3
- 239000008188 pellet Substances 0.000 description 3
- 239000000126 substance Substances 0.000 description 3
- JOYRKODLDBILNP-UHFFFAOYSA-N Ethyl urethane Chemical compound CCOC(N)=O JOYRKODLDBILNP-UHFFFAOYSA-N 0.000 description 2
- MCMNRKCIXSYSNV-UHFFFAOYSA-N Zirconium dioxide Chemical compound O=[Zr]=O MCMNRKCIXSYSNV-UHFFFAOYSA-N 0.000 description 2
- 239000011324 bead Substances 0.000 description 2
- 239000011230 binding agent Substances 0.000 description 2
- 230000015572 biosynthetic process Effects 0.000 description 2
- 229910052799 carbon Inorganic materials 0.000 description 2
- 238000006243 chemical reaction Methods 0.000 description 2
- 150000001875 compounds Chemical class 0.000 description 2
- 238000010304 firing Methods 0.000 description 2
- 239000006260 foam Substances 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 239000002244 precipitate Substances 0.000 description 2
- 239000000243 solution Substances 0.000 description 2
- 238000005507 spraying Methods 0.000 description 2
- 238000003756 stirring Methods 0.000 description 2
- 239000000725 suspension Substances 0.000 description 2
- 235000019731 tricalcium phosphate Nutrition 0.000 description 2
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 2
- 208000018084 Bone neoplasm Diseases 0.000 description 1
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- 241000282326 Felis catus Species 0.000 description 1
- 208000005422 Foreign-Body reaction Diseases 0.000 description 1
- 241001465754 Metazoa Species 0.000 description 1
- 238000002441 X-ray diffraction Methods 0.000 description 1
- 230000032683 aging Effects 0.000 description 1
- 239000000956 alloy Substances 0.000 description 1
- 229910045601 alloy 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
- 239000007864 aqueous solution Substances 0.000 description 1
- 230000000975 bioactive effect Effects 0.000 description 1
- 239000012620 biological material Substances 0.000 description 1
- 238000001354 calcination Methods 0.000 description 1
- 239000001506 calcium phosphate Substances 0.000 description 1
- 239000002131 composite material Substances 0.000 description 1
- 238000000354 decomposition reaction Methods 0.000 description 1
- 230000006866 deterioration Effects 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 238000005469 granulation Methods 0.000 description 1
- 230000003179 granulation Effects 0.000 description 1
- 239000012535 impurity Substances 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 239000004615 ingredient Substances 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 230000007774 longterm Effects 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 238000012794 pre-harvesting Methods 0.000 description 1
- 238000001556 precipitation Methods 0.000 description 1
- 239000000047 product Substances 0.000 description 1
- 239000007787 solid Substances 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 231100000331 toxic Toxicity 0.000 description 1
- 230000002588 toxic effect Effects 0.000 description 1
- 231100000419 toxicity Toxicity 0.000 description 1
- 230000001988 toxicity Effects 0.000 description 1
- 238000002054 transplantation Methods 0.000 description 1
- 229940078499 tricalcium phosphate Drugs 0.000 description 1
- 229910000391 tricalcium phosphate Inorganic materials 0.000 description 1
Abstract
Description
【発明の詳細な説明】
Ａ産業上の利用分腎
本発明は、例えば骨腫瘍などによって生ずる生体の骨欠
損部及び空隙部に充填し、該所の新生骨の形成を促進し
、生体の骨組織と一体化する骨欠損部及び空隙部の充填
材に関するものである。DETAILED DESCRIPTION OF THE INVENTION A. Industrial Applications The present invention is intended to fill bone defects and voids in living bodies caused by bone tumors, etc., to promote the formation of new bone at the locations, and to improve the bone structure of living bodies. The present invention relates to a filling material for bone defects and voids that integrates with tissue.
Ｂ発明の概要
主成分を生体親和性があり、孔に骨芽細胞が入り込み、
新生骨が生成されると同時に生体内に溶解吸収され、自
家骨と早急に置換される効果があるβ−リン酸三カルシ
ウムの多孔質焼結体に溶解し難い材質でできた接合体を
接合させ、新生骨ができる前にβ−リン酸三カルシウム
多孔質焼結体が、溶出しない充填材を得たものである。B Overview of the invention The main component is biocompatible, and osteoblasts can enter the pores.
A bonded body made of a material that is difficult to dissolve is bonded to a porous sintered body of β-tricalcium phosphate, which is dissolved and absorbed in the body at the same time new bone is generated, and has the effect of rapidly replacing autologous bone. The β-tricalcium phosphate porous sintered body was obtained as a filler that does not elute before new bone is formed.
Ｃ従来の技術
従来、生体における骨欠損部を補綴する場合、自家骨を
採取して移植することが行われていた。C. Prior Art Conventionally, when prosthesizing a bone defect in a living body, autologous bone has been harvested and transplanted.
しかしながら、自家前採取は、採骨のための手術と移植
のための手術と手術回数が増えること、患者に与える苦
痛が大きいことなどの欠点があった。However, autologous pre-harvesting has disadvantages such as an increased number of surgeries for bone collection and transplantation, and greater pain for the patient.
そこで、生体の硬組織代替物質として、合金及び有機物
が用いられてきた。だが、生体内で溶解、劣化による毒
性、異物反応などの問題点があった。Therefore, alloys and organic substances have been used as hard tissue substitutes for living organisms. However, there were problems such as dissolution in living organisms, toxicity due to deterioration, and foreign body reactions.
そこで現在、生体材料としてセラミックスが用いられて
いる。生体セラミックスは、アルミナ、カーボン、ジル
コニアなど、生体内で不ｉ３ 性で安定な生体不活性な
ものと、ヒドロキシアパタイト（Ｃａｔｓ （ＰＯ４）
ａ （０１［） ｘ） 、リン酸三カルシウム（Ｃａ
３（ＰＯ４）＊）など、生体内で分解、析出、反応など
を起こす生体活性な、生体親和性のよいものがある。Therefore, ceramics are currently used as biomaterials. Bioceramics include bioinert materials such as alumina, carbon, and zirconia, which are stable and bioinert in the body, and hydroxyapatite (Cats (PO4)).
a (01[) x) , tricalcium phosphate (Ca
There are bioactive and biocompatible substances that cause decomposition, precipitation, reactions, etc. in vivo, such as 3(PO4)*).
しかし、上記の生体セラミックスでは、生体不活性なも
のは言うに及ばず、ヒドロキシアパタイトも生体内で長
期間にわたり異物として存在するという問題点があった
。However, the above-mentioned bioceramics have a problem in that not only hydroxyapatite but also hydroxyapatite exists as a foreign substance in the body for a long period of time.
そこで、ヒドロキシアパタイトに比べ、短期間で吸収さ
れて、自家骨に置換されるβ−リン酸三カルシウム（以
下、β−ＴＣＰと略す）を使って最良の骨欠損部及び空
隙部充填材を得ることにした。つまり、最良の骨欠損部
及び空隙部充填材とは、毒性反応を伴わず、短期間に骨
と一体化され、さらに生体内に吸収されると同時に骨組
織の形成を促進し、最後には全て新生骨に置き換わる骨
欠損部及び空隙部充填材を得ることにした。Therefore, compared to hydroxyapatite, β-tricalcium phosphate (hereinafter abbreviated as β-TCP), which is absorbed in a shorter period of time and replaced by autologous bone, is used to obtain the best filling material for bone defects and voids. It was to be. In other words, the best bone defect and void filling material is one that does not cause toxic reactions, integrates with bone in a short period of time, is absorbed by the body, promotes the formation of bone tissue, and finally We decided to obtain a filling material for bone defects and voids that would be completely replaced with new bone.
そこで、β−ＴＣＰを、骨組織とよくなじませるため、
多孔質焼結体として用いた。Therefore, in order to make β-TCP blend well with bone tissue,
It was used as a porous sintered body.
一般に３次元網状セラミックスの多孔質焼結体は以下の
ようにして作られる。Generally, porous sintered bodies of three-dimensional network ceramics are produced as follows.
■軟質ウレタンフオームにセラミック泥しようを含浸さ
せたものを乾燥した後、焼成する。■ Soft urethane foam impregnated with ceramic slurry is dried and then fired.
■セラミツク泥しようの中にＨＩ３．溶液を一定量入れ
、屁合し、乾燥した後、焼成する。■HI3 in ceramic mud. A certain amount of the solution is added, mixed, dried, and fired.
■セラミツク泥しようの中に有機物のビーズの玉を入れ
混合し、乾燥した後、焼成することにより、有機物の玉
を除去する。■ Organic beads are mixed in ceramic mud, dried, and fired to remove organic beads.
そこで、■の方法でβ−ＴＣＰの多孔質焼結体を作り、
成犬の下顎歯槽骨内に埋入し、ｗｉ織学的に長期にわな
外観察した。第７図は、埋入後すぐに撮ったレントゲン
写真の模式図であり、図において、（１）は歯槽骨、（
２）は歯槽骨（１）の上部にある歯肉、（３）は歯槽骨
に埋入されたβ−ＴＣＰの多孔質焼結体である。第８図
は、埋入後、６力月のレントゲン写真の模式図である。Therefore, we made a porous sintered body of β-TCP using method ①.
It was implanted into the mandibular alveolar bone of an adult dog, and its structure was observed outside the trap over a long period of time. Figure 7 is a schematic diagram of an X-ray photograph taken immediately after implantation. In the figure, (1) is the alveolar bone, (
2) is the gingiva above the alveolar bone (1), and (3) is a porous sintered body of β-TCP embedded in the alveolar bone. FIG. 8 is a schematic diagram of an X-ray photograph of the hexagon after implantation.
β−ＴＣＰ多孔質焼結体（３）は骨組織（１）とよく馴
じみ、多孔質体の孔に骨芽細胞が入９込み、β−ＴＣＰ
の表面に直接、新生骨が接している部分と、β−ＴＣＰ
が吸収され、β−ＴＣＰ多孔質焼結体（３）からやや離
れたところに骨組織が形成されて入る部分が認められた
。The β-TCP porous sintered body (3) blends well with the bone tissue (1), and osteoblasts enter the pores of the porous body and the β-TCP
The part where new bone is in direct contact with the surface of β-TCP
was absorbed, and a portion where bone tissue was formed and entered a little distance from the β-TCP porous sintered body (3) was observed.
しかし、第８図に示すように、多孔質焼結体の上部が、
歯肉（２）中の血液により溶は出し、大きくえぐられて
いた。However, as shown in Fig. 8, the upper part of the porous sintered body
The blood in the gums (2) had dissolved and the gums had been greatly gouged out.
すなわち、β−ＴＣＰ多孔質焼結体（３）は、溶解度が
大きいという利点が、欠点として現れたのである。これ
は、多孔質焼結体の断面図から次のように考える。That is, the advantage of high solubility of the β-TCP porous sintered body (3) appeared as a disadvantage. This can be considered as follows from the cross-sectional view of the porous sintered body.
第９図は、多孔質焼結体の断面の模式図である。FIG. 9 is a schematic cross-sectional view of the porous sintered body.
図において、（４）はβ−ＴＣＰの焼結体、（５）は連
続空孔である。図のβ−７ＴＣＰ部分（３）は、セラミ
ック泥しょうが乾燥した後、焼成されたものであり、多
孔質焼結体部分は穴だらけで、密度も低く、表面積が大
きい、そのため溶解度が非常に大きい。In the figure, (4) is a sintered body of β-TCP, and (5) is a continuous pore. The β-7TCP part (3) in the figure is made by drying and firing the ceramic slurry, and the porous sintered part is full of holes, has a low density, and has a large surface area, so it has a very high solubility. .
Ｄ発明が解決しようとする問題点
以上のように、全て新生骨と置き換わる材料として、β
−ＴＣＰ多孔質焼結体が良いが、−ａ的な！Ｉ！！造方
法で、多孔体を作り応用しても、歯肉などの血液の循環
の多い所では、溶解量が多すぎ、使用不可能であるとい
う問題点がある。D Problems to be Solved by the Invention As mentioned above, β
-TCP porous sintered body is good, but -a! I! ! Even if a porous body is made and applied using a manufacturing method, there is a problem that the amount of dissolution is too large in areas where blood circulation is high, such as the gums, making it unusable.
本発明は、かかる問題点を解決するためになされたもの
で、全て新生骨と置き換わる材料であり、歯肉などの血
液の循環の多い所では、溶解し難い骨欠損部及び空隙部
充填材を得ることを目的とする。The present invention has been made to solve these problems, and provides a material for filling bone defects and voids that is completely replaceable with new bone and is difficult to dissolve in areas where there is a lot of blood circulation, such as the gums. The purpose is to
Ｅ問題点を解決するための手段
この発明に係わる骨欠損部及び空隙部充填材では、骨欠
損部や空隙部に埋入する生体セラミックスの多孔質焼結
体の筋組織に接する少なくとも一部分に溶解し難い材質
で出来た接合体を備え、多層状にしたものである。E Means for Solving Problems In the bone defect and void filling material according to the present invention, the material dissolves in at least a portion of the porous sintered body of bioceramics that is in contact with the muscle tissue and is implanted in the bone defect or void. It has a multi-layer structure and is made of a material that is difficult to bond with.
Ｆ作用
本発明においては、充填材は、多孔質焼結体と接合体の
多層になっているので、多孔質焼結体部は生体内に溶解
吸収され、自家骨と早急に置換され、さらに、筋肉など
血液の流れる部分に接している部分は、β−ＴＣＰやハ
イドロキシアパタイトの緻密体となっているので、成分
が溶解しに（（、新生骨ができる前に多孔質焼結体が、
溶解し難い。F action In the present invention, since the filling material is made up of multiple layers of porous sintered bodies and bonded bodies, the porous sintered bodies are dissolved and absorbed in the living body, quickly replaced with autologous bone, and further The parts that are in contact with areas where blood flows, such as muscles, are dense bodies of β-TCP and hydroxyapatite, so the components do not dissolve ((, before new bone is formed, the porous sintered body
Difficult to dissolve.
Ｇ：ｉｌ！ｉ例
実施例１
第１図は、本発明の一実施例を示す断面図であり、図に
おいて、（３１はβ−ＴＣＰの多孔質焼結体、（６）は
多孔質焼結体（３）に接合された接合体（β−ＴＣＰか
らなる緻密な焼結体、ハイドロキシアパタイトからなる
緻密な焼結体、ハイドロキシアパタイトからなる多孔質
焼結体）である。G:il! Example i Example 1 FIG. 1 is a sectional view showing an example of the present invention. In the figure, (31 is a porous sintered body of β-TCP, (6) is a porous sintered body (3 ) (a dense sintered body made of β-TCP, a dense sintered body made of hydroxyapatite, a porous sintered body made of hydroxyapatite).
なお、各図中同一符号は、同一または相当部分を示す。Note that the same reference numerals in each figure indicate the same or corresponding parts.
以下に、その操作を示す。Ｃａ （Ｏｔ［） 、の懸濁
液にＣａｗ （ＰＯ４） ＊となる量のＨ，ＰＯ４水溶
液を撹拌しながら滴下した後、数日間反応と熟成を行い
、得られた沈殴物をろ過した。その後、乾燥し、その粉
末を６００℃で仮焼した。The operation is shown below. An aqueous solution of H and PO4 in an amount of Caw (PO4)* was added dropwise to the suspension of Ca (Ot[) with stirring, and the mixture was reacted and aged for several days, and the resulting precipitate was filtered. Thereafter, it was dried and the powder was calcined at 600°C.
この粉末はＸ線パターンにより、β−Ｃａ３ （ＰＯａ
） ＊が主成分である（例えば不純物として、Ｃａ ｓ
ｔｓ （ＰＯ４） ｓ （ＯＨ） ｘ、Ｃａ１Ｐ２０
７、α−Ｃａ、（ＰＯ４）、、Ｃａ５Ｈｉ （Ｐｏｔ）
ｓ ５ｔｌｚＯなどのβ−Ｇａｓ （ＰＯａ） ＊
以外のＣａ−Ｐ−０化合物）であった。This powder was determined by the X-ray pattern as β-Ca3 (POa
) * is the main component (for example, as an impurity, Ca s
ts (PO4) s (OH) x, Ca1P20
7, α-Ca, (PO4), Ca5Hi (Pot)
β-Gas (POa) such as s5tlzO*
Ca-P-0 compound).
この仮焼物に結合剤としてポリビニルアルコール（以下
ＰＶＡと略す）を添加し、ボールミルで７時間、微粉砕
した。これを半分に分け１．一方を接合体を作るため、
スプレーで造粒した後、直径φ５．０−１厚み２．５ｍ
ｍのベレット状に金型成形した。Polyvinyl alcohol (hereinafter abbreviated as PVA) was added as a binder to this calcined material, and the material was pulverized in a ball mill for 7 hours. Divide this in half 1. To make one zygote,
After granulation by spraying, diameter φ5.0-1 thickness 2.5m
It was molded into a pellet shape with a diameter of m.
その後、成形したベレットを９００℃で仮焼しな。Thereafter, the formed pellet is calcined at 900°C.
１０００〜１４００℃での本焼成で約２０％収縮するの
に対し、この仮焼では約１）％の収縮率であった。While the main firing at 1000 to 1400°C caused a shrinkage of about 20%, the shrinkage rate in this calcination was about 1)%.
一方、ボールミルで微粉砕したセラミック泥しようの半
分を用い、固体と液体（水）の割合を１：１とした後、
ＰＶＡを一定量添加し、よく混合した。これを軟質ウレ
タンフオームのスポンジに含浸させた。On the other hand, after using half of the ceramic slurry finely ground in a ball mill and adjusting the ratio of solid and liquid (water) to 1:1,
A certain amount of PVA was added and mixed well. A soft urethane foam sponge was impregnated with this.
仮焼体とセラミック泥しようを含浸したぬれたままのス
ポンジを結合させ、急速に乾燥して七ビの入らないよう
に室温で乾燥した後、１）５０℃で焼成輸、焼結体第１
図を得た。The calcined body and the wet sponge impregnated with ceramic slurry are combined, and after drying rapidly at room temperature to prevent any dirt from entering, the sintered body is 1) fired at 50°C and exported.
I got the diagram.
第２図は本焼結体を成犬の下顎歯槽骨内に埋入後のレン
トゲン写真の模式図である。長期にわたり、観察した結
果、歯肉（２）との接触部分においても、溶解による大
きなへこみは見られなかった。FIG. 2 is a schematic diagram of an X-ray photograph after the present sintered body was implanted into the mandibular alveolar bone of an adult dog. As a result of long-term observation, no large dents due to dissolution were observed even in the contact area with the gingiva (2).
実施例２
Ｃａ （０■）、の懸濁液にＣａｔ、、 （Ｐｏａ）
ｓ （ＯＨ） ｔとなる量のＩｆ、ＰＯ４水溶液を攪拌
しながら滴下した後、数日間反応と熟成を行い、得られ
た沈陵物をろ過しな。Example 2 A suspension of Ca (0■), (Poa)
After dropping an aqueous If and PO4 solution in an amount of s (OH) t with stirring, reaction and aging were performed for several days, and the resulting precipitate was filtered.
その後、乾燥し、その粉末を６００℃で仮焼した。Thereafter, it was dried and the powder was calcined at 600°C.
コノ粉末はｘｓパターンより、Ｃａｂｓ （ＰＯ４）
＊ （ＯＨ） ＊が主成分であるＣｍ−１’−０化合物
であった。Kono powder is from xs pattern, Cabs (PO4)
*(OH)* was a Cm-1'-0 compound as a main component.
この仮焼物にＰＶＡをバインダー（結合剤）として添加
し、ボールミルで４時間微粉砕後、スプレーで造粒した
。この造粒粉を直径φ４．０−１厚み１．０閣に金型成
形したベレットを９５０℃で仮焼した。PVA was added as a binder to this calcined product, which was finely pulverized in a ball mill for 4 hours, and then granulated by spraying. This granulated powder was molded into a pellet having a diameter of φ4.0-1 and a thickness of 1.0 mm and calcined at 950°C.
一方、実施例１と同様にβ−ＴＣＰの粉体の入った泥し
ようをスポンジに含浸させ、ぬれたままのスポンジを作
った。On the other hand, as in Example 1, a sponge was impregnated with slurry containing β-TCP powder to produce a wet sponge.
仮焼体とスポンジを接合した後、乾燥し、１２００℃で
焼成し、第１図と同様な焼結体を得た。After joining the calcined body and the sponge, it was dried and fired at 1200°C to obtain a sintered body similar to that shown in FIG. 1.
得られた複合体を成人の下顎歯槽骨内に埋入し、長期に
わたり、ＩＩ！察した結果、歯肉との接触部分において
、溶解による大きなへこみは見られなかった。The resulting composite was implanted into the mandibular alveolar bone of an adult and maintained over a long period of time. As a result, no large dents due to dissolution were observed in the area in contact with the gums.
実施例３
β−ＴＣＰが主成分の粉末から成るセラミック泥しよう
を含浸したスポンジに、更に、濃度の濃い（β−ＴＣＰ
：水＝１．５〜Ｇ、８．１）β−ＴＣＩ’が主成分のセ
ラミック泥しようを刷毛で、そのスポンジ表面に塗９乾
燥後、１）５０℃で焼成し、第１図と同様な焼結体を得
た。Example 3 A sponge impregnated with ceramic slurry consisting of powder whose main component is β-TCP is
: Water = 1.5~G, 8.1) Apply ceramic slurry mainly composed of β-TCI' to the sponge surface with a brush.9 After drying, 1) Calculate at 50°C, as shown in Figure 1. A sintered body was obtained.
焼成体の密度の高い緻密な表面は°、厚み（１）が０．
９−であった。The dense and precise surface of the fired body has a thickness (1) of 0.
It was 9-.
本焼結体を成人の下顎歯槽骨内に埋入した結果、長期間
にわたり、多量な材料の溶解がなく、良好であった。When this sintered body was implanted into the mandibular alveolar bone of an adult, the results were good, with no large amount of material dissolving over a long period of time.
実施例４
今度は歯槽骨だけではな（、−段的な骨組織での応用例
を考えてみた。Example 4 This time, we considered an example of application not only to alveolar bone but also to graded bone tissue.
第３図は多孔体の２面を緻密体で形成した焼結体を生体
内に内入した時の模式図、第４図は多孔体の両面を緻密
体で形成した焼結体を生体内に埋入した時の模式図であ
る。図において（７）は骨組織、（８）は筋組織を示し
ている。第５図は緻密体の周りを多孔質焼結体とした模
式図である。Figure 3 is a schematic diagram of a porous body in which a sintered body with two sides made of dense material is injected into a living body. It is a schematic diagram when it is embedded in. In the figure, (7) shows bone tissue and (8) shows muscle tissue. FIG. 5 is a schematic diagram of a dense body surrounded by a porous sintered body.
これら全ての材料について、動物実験をした結果、長期
にわたり、多量な材料の溶解がな（、良好であった。Animal experiments on all of these materials showed that large amounts of the materials did not dissolve over a long period of time.
実施例５
第６図は抜歯形状に加工した焼結体を生体内に埋入した
時の模式図である。図に示した焼結体を抜歯後、歯肉（
２）で抜歯孔が埋められる前に、埋入した。その結果、
良好な結果を得た。Example 5 FIG. 6 is a schematic diagram when a sintered body processed into a tooth extraction shape is implanted in a living body. After removing the sintered body shown in the figure, the gingiva (
It was placed before the tooth extraction hole was filled in step 2). the result,
Good results were obtained.
また、抜歯形状の加工は、多孔質焼結体であるので加工
が容易で、ヤスリ等で加工ができる利点がある。Further, since it is a porous sintered body, it is easy to process it into a tooth-extracted shape, and it has the advantage that it can be processed with a file or the like.
本実施例では、多孔質焼結体にβ−ＴＣＰ、接合体にβ
−ＴＣＰの緻密な焼結体、またはハイドロキシアパタイ
トの緻密な焼結体、またはハイドロキシアパタイトの多
孔質焼結体を使ったが、適当な溶解度を持った生体セラ
ミックスであれば、同様な効果を得られる。In this example, β-TCP is used for the porous sintered body, and β-TCP is used for the joined body.
-We used a dense sintered body of TCP, a dense sintered body of hydroxyapatite, or a porous sintered body of hydroxyapatite, but the same effect can be obtained if it is a bioceramic with an appropriate solubility. It will be done.
Ｈ発明の効果
本発明は、多孔質焼結体部と接合体部の多層になってい
るので、骨と接している部分は、β−ＴＣＰの多孔質焼
結体となり、骨欠損部及び空隙部に充填材として生体内
に用いた場合、生体親和性があり、孔に骨芽細胞が入り
込み、新生骨が生成されると同時に生体内に溶解吸収さ
れ、自家骨と早急に置換され、さらに、筋肉など血液の
流れる部分に接している部分は、β−ＴＣＰやハイドロ
キシアパタイトの緻密体となっているので、成分が溶解
し難く、新生骨ができる前に充填材が溶解して、充填材
の構造が損なわれることはない。H Effects of the Invention The present invention has multiple layers of a porous sintered body part and a bonded body part, so the part in contact with the bone becomes a porous sintered body of β-TCP, eliminating bone defects and voids. When used as a filler in the body, it has biocompatibility, osteoblasts enter the pores, new bone is generated, and at the same time it is dissolved and absorbed in the body, rapidly replacing autologous bone, and The areas that are in contact with areas where blood flows, such as muscles, are dense bodies of β-TCP and hydroxyapatite, so these ingredients are difficult to dissolve, and the filling material dissolves before new bone is formed. structure is not damaged.
第１図は、本発明の一実施例を示す断面図、第２図は本
焼結体を成人の下顎歯槽骨内に埋入後のレントゲン写真
の模式断面図、第３図は多孔質焼結体の２ＷＪを緻密体
で形成した焼結体を生体内に埋入した時の模式断面図、
第４図は多孔質焼結体の両面を緻密体で形成した焼結体
を生体内に埋入した時の模式断面図、第５図はｍＷ！体
の周りを多孔質焼結体とした焼結体の模式断面図、第６
図は抜歯形状に加工した焼結体を生体内に埋入した時の
模式断面図、第７図はβ−ＴＣＰ多孔質体全孔質体すぐ
゛に撮ったレントゲン写真の模式断面図、第８図は埋入
６力月後のレントゲン写真の模式断面図、第９図は多孔
質焼結体の断面の模式図である。
（３）は生体セラミックス多孔質焼結体、（６）は接合
体を示す。Fig. 1 is a cross-sectional view showing one embodiment of the present invention, Fig. 2 is a schematic cross-sectional view of an X-ray photograph after the present sintered body is implanted into the mandibular alveolar bone of an adult, and Fig. 3 is a porous sintered body. A schematic cross-sectional view when a sintered body in which 2WJ of the body is formed of a dense body is implanted in a living body,
Figure 4 is a schematic cross-sectional view of a porous sintered body with both sides made of dense material implanted in a living body, and Figure 5 is mW! Schematic cross-sectional view of a sintered body with a porous sintered body surrounding it, No. 6
The figure is a schematic cross-sectional view of a sintered body processed into a tooth extraction shape and implanted in a living body. Figure 7 is a schematic cross-sectional view of an X-ray photograph taken immediately after the β-TCP porous body. FIG. 8 is a schematic cross-sectional view of an X-ray photograph 6 months after implantation, and FIG. 9 is a schematic cross-sectional view of the porous sintered body. (3) shows a bioceramic porous sintered body, and (6) shows a joined body.
Claims (6)
の多孔質焼結体、該多孔質焼結体の筋組織に接する少な
くとも一部分に接合体を備え、多層状にしたことを特徴
とする骨欠損部及び空隙部充填材。(1) A porous sintered body of β-tricalcium phosphate, which is a bioceramic, and a bone defect characterized by having a bonded body in at least a portion of the porous sintered body in contact with the muscle tissue to form a multilayered structure. and void filling material.
緻密な焼結体、またはハイドロキシアパタイトからなる
緻密な焼結体、またはハイドロキシアパタイトからなる
多孔質焼結体であることを特徴とする特許請求の範囲第
１項記載の骨欠損部及び空隙部充填材。(2) The bonded body is characterized in that it is a dense sintered body made of β-tricalcium phosphate, a dense sintered body made of hydroxyapatite, or a porous sintered body made of hydroxyapatite. A bone defect and void filling material according to claim 1.
体の理論密度は７０％〜１００％とすることを特徴とす
る特許請求の範囲第２項記載の骨欠損部及び空隙部充填
材。(3) The bone defect and void filling material according to claim 2, wherein the dense sintered body made of β-tricalcium phosphate has a theoretical density of 70% to 100%. .
体の理論密度は６０％〜１００％とすることを特徴とす
る特許請求の範囲第２項記載の骨欠損部及び空隙部充填
材。(4) The bone defect and void filling material according to claim 2, wherein the dense sintered body made of hydroxyapatite has a theoretical density of 60% to 100%.
工したことを特徴とする特許請求の範囲第１項記載の骨
欠損部及び空隙部充填材。(5) The bone defect and void filling material according to claim 1, wherein the porous sintered body is processed to have the same shape as the root of an extracted tooth.
きさに合わせ０＜Ｔａ＜５ｍｍとし、生体セラミックス
の多孔質焼結体の厚み（Ｔｂ）は、同様に骨欠損部の穴
の大きさに合わせ０＜Ｔｂ＜３ｍｍしたことを特徴とす
る特許請求の範囲第１項記載の骨欠損部及び空隙部充填
材。(6) The thickness (Ta) of the bonded body is set to 0<Ta<5 mm in accordance with the size of the hole in the bone defect, and the thickness (Tb) of the porous sintered body of bioceramics is similarly adjusted to the size of the hole in the bone defect. The bone defect and void filling material according to claim 1, characterized in that 0<Tb<3 mm in accordance with the size of the hole.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62285462A JPH01126977A (en) | 1987-11-13 | 1987-11-13 | Filler for crack or opening of bone |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62285462A JPH01126977A (en) | 1987-11-13 | 1987-11-13 | Filler for crack or opening of bone |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH01126977A true JPH01126977A (en) | 1989-05-19 |
Family
ID=17691827
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP62285462A Pending JPH01126977A (en) | 1987-11-13 | 1987-11-13 | Filler for crack or opening of bone |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH01126977A (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6350462B1 (en) | 1990-12-26 | 2002-02-26 | Olympus Optical Co., Ltd. | Hollow porous ceramic carrier for embedding in patient for sustained medicament release and method of preparation thereof |
| US10286102B2 (en) | 2010-05-11 | 2019-05-14 | Howmedica Osteonics Corp | Organophosphorous, multivalent metal compounds, and polymer adhesive interpenetrating network compositions and methods |
-
1987
- 1987-11-13 JP JP62285462A patent/JPH01126977A/en active Pending
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6350462B1 (en) | 1990-12-26 | 2002-02-26 | Olympus Optical Co., Ltd. | Hollow porous ceramic carrier for embedding in patient for sustained medicament release and method of preparation thereof |
| US10286102B2 (en) | 2010-05-11 | 2019-05-14 | Howmedica Osteonics Corp | Organophosphorous, multivalent metal compounds, and polymer adhesive interpenetrating network compositions and methods |
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