JPH03218769A - Implant member - Google Patents
Implant memberInfo
- Publication number
- JPH03218769A JPH03218769A JP2015652A JP1565290A JPH03218769A JP H03218769 A JPH03218769 A JP H03218769A JP 2015652 A JP2015652 A JP 2015652A JP 1565290 A JP1565290 A JP 1565290A JP H03218769 A JPH03218769 A JP H03218769A
- Authority
- JP
- Japan
- Prior art keywords
- titanium alloy
- base material
- bioactive
- titanium
- implant member
- 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.)
- Granted
Links
- 239000007943 implant Substances 0.000 title claims abstract description 27
- 239000000463 material Substances 0.000 claims abstract description 50
- 229910001069 Ti alloy Inorganic materials 0.000 claims abstract description 28
- 230000000975 bioactive effect Effects 0.000 claims abstract description 19
- 239000002344 surface layer Substances 0.000 claims abstract description 17
- 239000010936 titanium Substances 0.000 claims abstract description 13
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 claims abstract description 10
- 229910052719 titanium Inorganic materials 0.000 claims abstract description 10
- 239000010410 layer Substances 0.000 claims abstract description 9
- 229910052715 tantalum Inorganic materials 0.000 claims abstract description 6
- 229910052758 niobium Inorganic materials 0.000 claims abstract description 5
- 239000000843 powder Substances 0.000 claims description 10
- 239000005313 bioactive glass Substances 0.000 claims description 6
- 229910052586 apatite Inorganic materials 0.000 claims description 5
- VSIIXMUUUJUKCM-UHFFFAOYSA-D pentacalcium;fluoride;triphosphate Chemical compound [F-].[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 VSIIXMUUUJUKCM-UHFFFAOYSA-D 0.000 claims description 5
- 210000000988 bone and bone Anatomy 0.000 abstract description 14
- 238000011282 treatment Methods 0.000 abstract description 13
- 239000011248 coating agent Substances 0.000 abstract description 5
- 238000000576 coating method Methods 0.000 abstract description 5
- 230000015572 biosynthetic process Effects 0.000 abstract description 2
- 238000001354 calcination Methods 0.000 abstract 1
- 230000021615 conjugation Effects 0.000 abstract 1
- 238000007788 roughening Methods 0.000 abstract 1
- 239000000956 alloy Substances 0.000 description 10
- 229910045601 alloy Inorganic materials 0.000 description 9
- 230000000694 effects Effects 0.000 description 8
- 238000010304 firing Methods 0.000 description 5
- 238000000137 annealing Methods 0.000 description 4
- 238000005260 corrosion Methods 0.000 description 4
- 230000007797 corrosion Effects 0.000 description 4
- 239000000654 additive Substances 0.000 description 3
- 230000000996 additive effect Effects 0.000 description 3
- 239000012620 biological material Substances 0.000 description 3
- 239000008187 granular material Substances 0.000 description 3
- 230000005484 gravity Effects 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 210000001519 tissue Anatomy 0.000 description 3
- 239000010839 body fluid Substances 0.000 description 2
- 229910010293 ceramic material Inorganic materials 0.000 description 2
- 238000005238 degreasing Methods 0.000 description 2
- 229910052588 hydroxylapatite Inorganic materials 0.000 description 2
- 239000012535 impurity Substances 0.000 description 2
- 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 description 2
- 239000011148 porous material Substances 0.000 description 2
- 238000001556 precipitation Methods 0.000 description 2
- 239000000758 substrate Substances 0.000 description 2
- 230000009466 transformation Effects 0.000 description 2
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 2
- 229910000883 Ti6Al4V Inorganic materials 0.000 description 1
- 238000005275 alloying Methods 0.000 description 1
- 239000005312 bioglass Substances 0.000 description 1
- 210000001124 body fluid Anatomy 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 230000010354 integration Effects 0.000 description 1
- 238000003754 machining Methods 0.000 description 1
- 238000010309 melting process Methods 0.000 description 1
- 229910052751 metal Inorganic materials 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 239000007769 metal material Substances 0.000 description 1
- 239000002245 particle Substances 0.000 description 1
- 230000001737 promoting effect Effects 0.000 description 1
- 238000010791 quenching Methods 0.000 description 1
- 230000000171 quenching effect Effects 0.000 description 1
- 229910052814 silicon oxide Inorganic materials 0.000 description 1
- 239000012890 simulated body fluid Substances 0.000 description 1
- 238000005245 sintering Methods 0.000 description 1
- 238000009864 tensile test Methods 0.000 description 1
- 238000007751 thermal spraying Methods 0.000 description 1
- 231100000331 toxic Toxicity 0.000 description 1
- 230000002588 toxic effect Effects 0.000 description 1
- 231100000701 toxic element Toxicity 0.000 description 1
Landscapes
- Materials For Medical Uses (AREA)
Abstract
Description
【発明の詳細な説明】
（産業上の利用分野）
本発明は、人工関節、接骨板、人工歯根等のインプラン
ト部材に関し、詳しくは生体骨組織との結合性を改善し
たインプラント部材に関するものである。DETAILED DESCRIPTION OF THE INVENTION (Field of Industrial Application) The present invention relates to implant members such as artificial joints, bone plates, and artificial tooth roots, and more specifically to implant members that have improved bonding properties with living bone tissue. .
（従来の技術）
チタンおよびチタン合金は表面が強間で縁密な不動態被
膜に覆われているため、生体内においても耐蝕性を示す
ことはよく知られている。また、比重は４．４〜４．８
ｇ／ｃ＋ｗ３と小さいため、生体材料として有用である
。そのうちでも、Ｔｉ−６ＡＩ−４ＶやＴ４５Ａｌ−２
．５Ｆｅ合金は機械的性質、耐蝕性、生体適合性などに
優れており、人工関節、接骨板、人工歯根などの素材と
して広く用いられている。(Prior Art) It is well known that titanium and titanium alloys exhibit corrosion resistance even in living organisms because the surfaces of titanium and titanium alloys are covered with a strong and dense passive film. Also, the specific gravity is 4.4 to 4.8
Since it has a small value of g/c+w3, it is useful as a biomaterial. Among them, Ti-6AI-4V and T45Al-2
．． 5Fe alloy has excellent mechanical properties, corrosion resistance, biocompatibility, etc., and is widely used as a material for artificial joints, bone plates, artificial tooth roots, etc.
これら材料の表面は、生体骨組織との強い固着性を確保
するために、金属材料やセラミックス材料をコーティン
グして粗面化されている。第２図（ａ）、（ｂ）は粗面
化したインプラント部材の表面を拡大して示す断面説明
図であり、（ａｌ図は基材層工上に粉粒体２を、Ｑ：１
）図は線状体３をそれぞれコーティングして粗而を構成
したものである。これらの表面構造においては、例えば
第２図（ａ）に基づいて説明すると、基材層１と粉粒体
２の間および粉粒体２同士の間等に孔部４が形成され、
インプラント部材の表面に粗而を形成する。その結果、
孔部４内には新しい生体骨組織が侵入、成長し易くなり
両者が強い固着状態を形成する。The surfaces of these materials are roughened by coating with metal or ceramic materials to ensure strong adhesion to living bone tissue. FIGS. 2(a) and 2(b) are cross-sectional explanatory diagrams showing an enlarged view of the roughened surface of the implant member.
) The figure shows a structure in which the linear bodies 3 are each coated. In these surface structures, for example, referring to FIG. 2(a), holes 4 are formed between the base material layer 1 and the granular material 2 and between the granular materials 2,
Roughness is formed on the surface of the implant member. the result,
New living bone tissue easily invades and grows into the hole 4, and the two form a strong bond.
一方、粗面化した基材の表面にハイオガラスやハイドロ
キシアパタイトなどの生体活性材料を被覆し、生体骨組
織との結合性をさらに改善する試みが行われている。On the other hand, attempts have been made to coat the surface of a roughened base material with a bioactive material such as hyoglas or hydroxyapatite to further improve the bonding properties with living bone tissue.
（発明が解決しようとする課題）
しかし、上述のチタン合金を基材として疲労強度の高い
状態で使用するには、例えばＴｉ−６ＡＩ−４Ｖでは、
β変態点以下すなわち９７０〜９８０゜Ｃの温度以下で
溶体化処理することが必須条件であって、生体活性材料
を被覆するときの必要焼成温度が１０００゜Ｃ以上であ
ることから、実用上は基材のチタン合金材料あるいは被
覆生体活性材料のいずれかの機能を犠牲にして使用せざ
るを得なかった．また、粗面化した多孔表面層において
、生体骨組織との強い固着性を確保するために、気孔率
を高めようとすると、基材と異なる金属材料あるいはセ
ラミソクス材料を用いて多孔表面層を構成する場合、基
材層と粉粒体間あるいは線状体間の結合力が低下し、基
材層から多孔表面層が剥離し易くなるという問題がある
。(Problems to be Solved by the Invention) However, in order to use the above-mentioned titanium alloy as a base material in a state with high fatigue strength, for example, Ti-6AI-4V,
Solution treatment at a temperature below the β-transformation point, that is, 970-980°C, is an essential condition, and the required firing temperature when coating bioactive materials is 1000°C or higher, so it is not practical in practice. The use of either the base titanium alloy material or the coating bioactive material had to be sacrificed. In addition, when trying to increase the porosity of a roughened porous surface layer to ensure strong adhesion with living bone tissue, the porous surface layer is constructed using a metal material or a ceramic material different from the base material. In this case, there is a problem that the bonding force between the base material layer and the powder or granular material or the linear material decreases, and the porous surface layer easily peels off from the base material layer.
粗面化した基材の表面にバイオガラスやハイドロキシア
パタイトなどの生体活性材料を被覆し、生体骨組織との
結合性を改善する試みが行われているが、実際臨床の場
においては、インプラント部材との結合は、通常４〜８
週間という長期間を必要とし、しかも生体骨との到達結
合固着強度は、人体重量や日常生活上負荷される荷重の
支持等において十分満足し得るまでには至っていない．
（ＩＩを解決するための手段）
本発明は上記の問題点を、１０００゜Ｃ以上の温度に加
熱しても常温強度の低下しないチタン合金を基材に用い
、基材表面の多孔表面層の形成にチタンまたはチタン合
金を用い、この多孔表面層に生体組織との親和性が高い
生体活性材料を被覆することによって解決するもので、
その第１発明は粗面化されたチタン合金製基材の表面に
生体組織との親和性が高い生体活性材料層を形成してな
るインプラント部材において、チタン合金がＡＩ：５．
５〜６．５ｗｔ％、Ｎｂ：１．５〜２．５ｗｔ％、Ｔａ
：０．５〜１．５ｗｔ％、Ｍｏ：０．５〜１．Ｏｗｔ％
を含有し、残部がＴｉから成るＴｉＡｌ−Ｎｂ−Ｔａ−
Ｍｏ系チタン合金であるインプラント部材である。Attempts have been made to coat the surface of the roughened base material with bioactive materials such as bioglass and hydroxyapatite to improve the bonding with living bone tissue, but in actual clinical practice, implant components The bond with is usually 4 to 8
It requires a long period of time (weeks), and the bonding strength achieved with living bone has not yet reached a level that is sufficient to support human weight and the loads that are applied in daily life.
(Means for Solving II) The present invention solves the above problem by using a titanium alloy as a base material, which does not lose its strength at room temperature even when heated to a temperature of 1000°C or more, and by forming a porous surface layer on the surface of the base material. This is solved by using titanium or titanium alloy for formation and coating this porous surface layer with a bioactive material that has high affinity with living tissue.
The first invention is an implant member in which a bioactive material layer having high affinity with living tissue is formed on the surface of a roughened titanium alloy base material, wherein the titanium alloy has an AI: 5.
5 to 6.5 wt%, Nb: 1.5 to 2.5 wt%, Ta
:0.5-1.5wt%, Mo:0.5-1. Owt%
TiAl-Nb-Ta- with the remainder consisting of Ti
This is an implant member made of a Mo-based titanium alloy.
第２発明は基材表面の粗而化がチタンまたはチタン合金
の粉粒体または線状体を付着させて多孔表面層を形成さ
れてなる請求項（１）記載のインプラント部材である。A second aspect of the invention is the implant member according to claim 1, wherein the roughened surface of the base material is formed by adhering a powder or linear body of titanium or a titanium alloy to form a porous surface layer.
第３発明は生体活性材料がＮａ２Ｏ−ＣａＯ−Ｓｉ０２
−Ｐｚ０ＢあるいはＭｇＯ−ＣａＯ−Ｓｔｏｗ−Ｐ２Ｏ
ｓを主成分とする生体活性ガラスあるいはアパタイトで
ある請求項（１）または請求項（２）記載のインプラン
ト部材である。In the third invention, the bioactive material is Na2O-CaO-Si02
-Pz0B or MgO-CaO-Stow-P2O
The implant member according to claim (1) or claim (2), which is bioactive glass or apatite containing s as a main component.
（作用） 以下、本発明の作用について説明する。(effect) Hereinafter, the effects of the present invention will be explained.
チタンおよびその合金は軽量で強靭で耐蝕性に優れ、か
つ生体適合性にも優れているため生体材料として広く使
用されている。しかし、生体材料として使用する場合に
は種々の制約がある。すなわち、■適度な疲労強度を有
し、使用に耐えること、■生体に無害であること、■イ
ンプラント部材に加工することが容易であること、など
である。これらの制約を満足するためには、■に関して
は生体活性材料の必要焼成温度とチタン合金の溶体化処
理温度（β変態点以上）とが同一温度域であることが必
要である。■に関しては，．毒性を有する元素を含まな
いことが望ましいが、合金化することで、たとえ単体で
は毒性を示す元素を含んでいても、溶出しなければ使用
に耐えることになる。■に関しては、インプラント部材
に加工する際に熱間塑性加工、冷間塑性加工、機械加工
を施すので、いずれの施工も容易であることが要求され
る．
そこで、本発明者らは、種々のチタン合金について、上
記制約条件に関して検討を行った．第１表にその検討結
果を示す．
第１表にチタン合金種類、β変態点、焼成温度からの適
否、
素材加工性の良否、
その他を示す．
（以下余白）
第
１
表
（以下余白）
？タン合金には第１表に示すように種々の成分系のもの
があるが、強度を確保するための熱処理温度は大部分の
ものがｌ０００゜Ｃ以下であって、従来Ｔｉ−６ＡＩ−
４Ｖ合金を用いる場合に生じていた問題点と同様の問題
を含んでいる。また、疲労強度の点からはＴｉ−６ＡＩ
−４Ｖ合金のインプラント部材としての実績が示すよう
に、Ｔｉ−６ＡＩ−４Ｖ合金以上の強度を有することが
必要である．
また、Ｖは人体に有害であるという説もあり、本発明で
は安全を考慮して、Ｖを含む合金系を除くことにした。Titanium and its alloys are widely used as biomaterials because they are lightweight, strong, have excellent corrosion resistance, and are also biocompatible. However, there are various restrictions when using it as a biomaterial. That is, (1) it has appropriate fatigue strength and can withstand use, (2) it is harmless to living organisms, and (2) it is easy to process into implant members. In order to satisfy these constraints, regarding (1), it is necessary that the required firing temperature of the bioactive material and the solution treatment temperature (beta transformation point or higher) of the titanium alloy are in the same temperature range. Regarding ■. Although it is desirable that the material does not contain toxic elements, by alloying it, even if it contains elements that are toxic alone, it can withstand use as long as it does not elute. Regarding (2), hot plastic working, cold plastic working, and machining are performed when processing the implant components, so all of these processes must be easy. Therefore, the present inventors investigated various titanium alloys regarding the above-mentioned constraint conditions. Table 1 shows the results of the study. Table 1 shows the type of titanium alloy, β transformation point, suitability of firing temperature, material processability, and other information. (The following is the margin) Table 1 (The following is the margin) ? There are various types of tan alloys as shown in Table 1, but the heat treatment temperature for most of them to ensure strength is 1000°C or less, and conventional Ti-6AI-
This includes problems similar to those encountered when using 4V alloy. In addition, from the point of view of fatigue strength, Ti-6AI
As shown by the experience of -4V alloy as an implant member, it is necessary to have a strength greater than that of Ti-6AI-4V alloy. Furthermore, there is a theory that V is harmful to the human body, so in the present invention, we have decided to exclude alloys containing V in consideration of safety.
したがって、第１表から明らかなように、上記■、■、
■の制約条件を満足するものはＴｉ−６ＡＩ−２Ｎｂ−
ＩＴａ−０．８Ｍｏを主成分とするものが最も好ましい
。本Ｔｉ合金の主要成分範囲と限定理由は以下の通りで
ある。Therefore, as is clear from Table 1, the above ■, ■,
The one that satisfies the constraint condition is Ti-6AI-2Nb-
The one containing ITa-0.8Mo as the main component is most preferred. The range of the main components of this Ti alloy and the reasons for the limitations are as follows.
Ａｌ：５．５〜６．５ｗｔ％
八１は強度向上のための主要添加元素であり、５．５ｗ
ｔ％未満ではＴｉ−６Ａｌ−４Ｖ合金以上の強度が得ら
れず、逆に、６．５ｗｔ％を越えるとα■相（ＴｉＪ１
）が生じ脆化し易くなる．
Ｎｂ：１．５〜２．５圓ｔ％
Ｔａ：０．５〜１．５ｗｔ％
Ｎｂ， Ｔａは共にＴｉ母材のα相にβ相を導入して強
度を向上させる添加元素であり、本発明では前記したＶ
の代替となるものである。Al: 5.5-6.5wt% 81 is the main additive element for improving strength, and 5.5w
If it is less than t%, it will not be possible to obtain a strength higher than that of the Ti-6Al-4V alloy, and conversely, if it exceeds 6.5wt%, the α■ phase (TiJ1
) occurs, making it more likely to become brittle. Nb: 1.5 to 2.5 wt% Ta: 0.5 to 1.5 wt% Both Nb and Ta are additive elements that improve strength by introducing a β phase into the α phase of the Ti base material. In the invention, the above-mentioned V
It is an alternative to
各々、下限値未満ではその効果が発揮できないとともに
、上限値を越えて加えても効果の向上は期待できず、併
せてこれらの元素は比重がＮｂ：８．５７ 、Ｔａ：１
６．６と大きく、全体の重量が数百グラムで軽量化が必
要なインプラント部材の重量を不要に増加させることに
なる。If each element is added below the lower limit, the effect cannot be exhibited, and if added above the upper limit, no improvement in effect can be expected.In addition, these elements have specific gravity of Nb: 8.57 and Ta: 1
6.6, and the total weight is several hundred grams, which unnecessarily increases the weight of the implant member, which should be lightweight.
Ｍｏ：０．５〜１．０ｉｉｔ％
Ｍｏは耐蝕性を向上させる添加元素であり、０．５ｗｔ
％未満ではその効果が薄く、１．Ｏｗｔ％を越えて加え
てもやはり効果の向上が期待できず、Ｎｂ， Ｔａと同
様に比重が１０．２２と重いＭｏの添加がインプラント
部材の重量を不要に増加させることになる．不純物につ
いては、Ｔｉ合金の溶製上不可避的に混入する不純物元
素は本発明でも通常の規格通り許容される。Mo: 0.5 to 1.0iit% Mo is an additive element that improves corrosion resistance, and 0.5wt%
If it is less than %, the effect will be weak.1. Even if more than Owt% is added, no improvement in the effect can be expected, and the addition of Mo, which has a heavy specific gravity of 10.22 like Nb and Ta, will unnecessarily increase the weight of the implant member. Regarding impurities, impurity elements that are unavoidably mixed during the melting process of the Ti alloy are allowed in the present invention as well according to normal standards.
ここで、Ｔｉ−６ＡＩ−２Ｎｂ−ＩＴａ−０．８一〇を
主成分とするチタン合金について、各種溶体化処理後の
室温強度について調査した。なお、参考のためにＡｎｎ
（焼鈍）後の室温強度についても調査した。その結果
を第１図に示す。Here, the room temperature strength of a titanium alloy whose main component is Ti-6AI-2Nb-ITa-0.810 after various solution treatments was investigated. For reference, Ann
The room temperature strength after (annealing) was also investigated. The results are shown in FIG.
第１図はインプラント部材の引張特性に及ぼす溶体化処
理条件とＡｎｎ （焼鈍）条件の影響を示すグラフであ
る。溶体化処理条件と＾ｎｎ（焼鈍）条件はつぎの通り
である。FIG. 1 is a graph showing the influence of solution treatment conditions and Ann (annealing) conditions on the tensile properties of implant members. The solution treatment conditions and ^nn (annealing) conditions are as follows.
溶体化処理：溶体化処理温度Ｘ１ｈｒＷＱ＋５９０゜Ｃ
Ｘ８ｈｒＡＣ
Ａｎｎ （焼鈍） ： ７００゜Ｃ×２ｈｒＡＣこ
こで、ＷＱは水焼入れ、ＡＣは空冷を示す．第１図から
明らかなように、溶体化処理温度が１０００〜１０５０
゜Ｃの範囲において引張特性が安定していることがわか
る。また、＾ｎｎでは引張強度が低下している。これら
の結果と、上記第１表における検討結果とから、？＋−
６ＡＩ−２Ｎｂ−ＩＴａ−０．８Ｍｏを主成分とするチ
タン合金が本発明の目的に適合することが明らかである
。Solution treatment: Solution treatment temperature X1hrWQ+590°C
X8hrAC Ann (annealing): 700°C x 2hrAC where WQ indicates water quenching and AC indicates air cooling. As is clear from Figure 1, the solution treatment temperature is 1000-1050.
It can be seen that the tensile properties are stable within the °C range. In addition, the tensile strength is decreased in ^nn. Based on these results and the examination results in Table 1 above,? +-
It is clear that a titanium alloy based on 6AI-2Nb-ITa-0.8Mo is suitable for the purpose of the present invention.
基材表面に多孔表面層を形成する場合、基材表面と多孔
表面層が完全に一体化することが必須条件である．これ
を達成するために、基材の主成分と同じであるチタンま
たはチタン合金の粉粒体または線状体を用いる．このよ
うに同一主成分の粉粒体または線状体を用いることによ
って、溶射、焼結などの方法によって基材表面と多孔表
面層が完全に一体化した多孔表面層を形成することがで
きる。この結果、多孔表面層の気孔率を高めることがで
き、生体骨組織との強い固着性を確保することができる
．
早期にインプラント部材に生体骨組織を親和させインプ
ラント部材と新生体骨を結合させ、人体重量や日常生活
の負荷に十分耐え得るようにするために生体活性材料を
用いる。この目的のために、本発明では、生体活性材料
にＮａ２Ｏ−ＣａＯ−ＳｉＯｚ−ＰｇＯ，あるいはＭｇ
Ｏ−ＣａＯ−ＳｉＯｚ−Ｐ２Ｏｓを主成分とする生体活
性ガラスあるいはアパタイトを用いる．（実施例）
以下に本発明の実施例について説明する。When forming a porous surface layer on the surface of a substrate, it is essential that the surface of the substrate and the porous surface layer are completely integrated. To achieve this, we use powder or linear bodies of titanium or titanium alloy, which is the same as the main component of the base material. By using powder particles or linear bodies having the same main component in this way, it is possible to form a porous surface layer in which the base material surface and the porous surface layer are completely integrated by a method such as thermal spraying or sintering. As a result, the porosity of the porous surface layer can be increased and strong adhesion with living bone tissue can be ensured. Bioactive materials are used in order to make the implant member compatible with the living bone tissue and bond the implant member to the new living bone, so that the implant member can sufficiently withstand the weight of the human body and the loads of daily life. For this purpose, in the present invention, Na2O-CaO-SiOz-PgO or Mg
Bioactive glass or apatite whose main component is O-CaO-SiOz-P2Os is used. (Example) Examples of the present invention will be described below.
実施例ｌ
成分Ｔｉ−６八ｌ−２Ｎｂ−ＩＴａ−０．８Ｍｏからな
るチタン合金の丸棒を用い、脱脂等を行い表面を清浄に
した後、表面に、０．５１厚さにＭｇＯ−ＣａＯ−Ｓｉ
Ｏｚ−Ｐ２Ｏｓ系生体活性ガラス粉末をプラズマ溶射し
、生体活性材料層を形成した。次いで、これらに１００
０゜Ｃ、１０２０゜Ｃ、１０４０゜Ｃで各２時間の溶体
化処理を施した後、引張試験および疑領体液中に浸漬し
表面の状態観察を行った。その結果、引張強度は、９３
〜９６ｋｇｆ／Ｎｌ１” ＋７１範囲であり、従来（７
）Ｔｉ−６ＡＩ−４Ｖ合金の強度に遜色ないものであっ
た。一方、疑領体液中に浸漬したものは、２日目に生体
活性材料層表面にアパタイトの析出を認めた。Example 1 A titanium alloy round bar consisting of Ti-68l-2Nb-ITa-0.8Mo was used, the surface was cleaned by degreasing, and then MgO-CaO was applied to the surface to a thickness of 0.51. -Si
Oz-P2Os bioactive glass powder was plasma sprayed to form a bioactive material layer. Then add 100 to these
After solution treatment at 0°C, 1020°C, and 1040°C for 2 hours each, a tensile test was performed and the surface condition was observed by immersing it in a pseudo-body fluid. As a result, the tensile strength was 93
~96 kgf/Nl1” +71 range, compared to conventional (7
) The strength was comparable to that of Ti-6AI-4V alloy. On the other hand, for those immersed in the suspected body fluid, precipitation of apatite was observed on the surface of the bioactive material layer on the second day.
実施例２
成分Ｔｉ−６ＡＩ−２Ｎｂ−ＩＴａ−０．８Ｍｏからな
るチタン合金の丸棒を用い、脱脂等を行い表面を清浄に
した後、表面に純チタン粉粒体をプラズマ溶射にて、厚
み０．７ ａｎの多孔表面層を形成した。その気孔率は
従来の３０〜５０％に対して、５０〜６０％に改善され
、空孔の大きさは１００〜２００μ−のものが適度に分
布していた．次いで、これをＭｇＯ−ＣａＯ−ＳｉＯｚ
−Ｐ ｇｏｓ系生体活性ガラス微粉末を水に分散させた
溶液中に浸漬し、空孔内にガラス微粉末を十分に付着さ
せ乾燥させた後、１０４０゜Ｃで２時間焼成処理を施し
た．焼成処理後、これを疑似体液中に浸漬し、保持した
ところ、２日目゛に多孔表面層の表面にアパタイトの析
出を認めた．
（発明の効果）
以上説明したように、本発明に係わるインプラント部材
は、上記の構成であるから、１０００℃以上の温度で溶
体化処理および被覆生体活性材料の焼成が可能で、この
ため疲労強度に優れ、また、チタンまたはチタン合金の
粉粒体または線状体で多孔表面層を形成するため、気孔
率を高くすることができ、このため、生体活性材料の付
着と新生体骨との結合を強固にすることができ、さらに
、インプラント部材表面に生体活性材料のＮａ，０−Ｃ
ａＯ−Ｓｆｏｇ−ｈｏｓあるいはＭｇＯ−ＣａＯ−Ｓｉ
Ｏｔ−ＰｔＯｓを主成分とする生体活性ガラスあるいは
アバタイトを被覆しているため、早期に生体組織との一
体化を促進することができるという優れた効果を有する
ものである。Example 2 Using a titanium alloy round bar consisting of the components Ti-6AI-2Nb-ITa-0.8Mo, the surface was cleaned by degreasing, etc., and then pure titanium powder was plasma sprayed on the surface to give a thickness A porous surface layer of 0.7 an was formed. The porosity was improved to 50-60% compared to the conventional 30-50%, and the pore sizes were moderately distributed between 100 and 200 μ-. Next, this was converted into MgO-CaO-SiOz
-P Gos-based bioactive glass fine powder was immersed in a solution in which it was dispersed in water, the glass fine powder was sufficiently adhered to the inside of the pores, dried, and then fired at 1040°C for 2 hours. After the firing treatment, this was immersed in a simulated body fluid and held, and on the second day, precipitation of apatite was observed on the surface of the porous surface layer. (Effects of the Invention) As explained above, since the implant member according to the present invention has the above structure, it is possible to perform solution treatment and firing of the coated bioactive material at a temperature of 1000°C or higher, and therefore the fatigue strength is improved. In addition, since a porous surface layer is formed with titanium or titanium alloy powder or linear material, the porosity can be increased, which facilitates the attachment of bioactive materials and the bonding with new bone. Furthermore, the bioactive material Na, 0-C is applied to the surface of the implant member.
aO-Sfog-hos or MgO-CaO-Si
Since it is coated with bioactive glass or abatite whose main component is Ot-PtOs, it has the excellent effect of promoting early integration with living tissue.
第１図はインプラント部材の引張特性に及ぼす溶体化処
理条件とＡｎｎ条件の影響を示すグラフである。
第２図（ａ）、（ｂ）は粗面化したインプラント部材の
表面を拡大して示す断面説明図である．１一基材層
２−・粉粒体
３・一線状体
４・−・孔部FIG. 1 is a graph showing the influence of solution treatment conditions and Ann conditions on the tensile properties of an implant member. FIGS. 2(a) and 2(b) are cross-sectional explanatory views showing an enlarged view of the roughened surface of the implant member. 1 - Base material layer 2 - Powder material 3 - Linear material 4 - - Hole
Claims (3)
との親和性が高い生体活性材料層を形成してなるインプ
ラント部材において、チタン合金がＡｌ：５．５〜６．
５ｗｔ％、Ｎｂ：１．５〜２．５ｗｔ％、Ｔａ：０．５
〜１．５ｗｔ％、Ｍｏ：０．５〜１．０ｗｔ％を含有し
、残部がＴｉから成るＴｉ−Ａｌ−Ｎｂ−Ｔａ−Ｍｏ系
チタン合金であることを特徴とするインプラント部材。(1) In an implant member formed by forming a bioactive material layer having high affinity with living tissues on the surface of a roughened titanium alloy base material, the titanium alloy has an Al content of 5.5 to 6.
5wt%, Nb: 1.5-2.5wt%, Ta: 0.5
1.5 wt%, Mo: 0.5 to 1.0 wt%, and the remainder is Ti.
粒体または線状体を付着させて多孔表面層を形成されて
なる請求項（１）記載のインプラント部材。(2) The implant member according to claim 1, wherein the surface of the base material is roughened by adhering a powder or linear body of titanium or a titanium alloy to form a porous surface layer.
−Ｐ＿２Ｏ＿５あるいはＭｇＯ−ＣａＯ−ＳｉＯ＿２−
Ｐ＿２Ｏ＿５を主成分とする生体活性ガラスあるいはア
パタイトである請求項（１）または請求項（２）記載の
インプラント部材。(3) Bioactive material is Na_2O-CaO-SiO_2
-P_2O_5 or MgO-CaO-SiO_2-
The implant member according to claim (1) or claim (2), which is bioactive glass or apatite containing P_2O_5 as a main component.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2015652A JP2710849B2 (en) | 1990-01-24 | 1990-01-24 | Implant components |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2015652A JP2710849B2 (en) | 1990-01-24 | 1990-01-24 | Implant components |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH03218769A true JPH03218769A (en) | 1991-09-26 |
| JP2710849B2 JP2710849B2 (en) | 1998-02-10 |
Family
ID=11894652
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2015652A Expired - Fee Related JP2710849B2 (en) | 1990-01-24 | 1990-01-24 | Implant components |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2710849B2 (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| KR100441765B1 (en) * | 2001-11-14 | 2004-07-27 | 한국과학기술연구원 | Ti-BASED ALLOY BIOMATERIALS WITH ULTRA FINE BIOACTIVE POROUS SURFACE AND MANUFACTURING METHOD THEREOF |
| KR100487118B1 (en) * | 2001-03-05 | 2005-05-03 | 주식회사 바이오스마트 | Composition of Porous Element for Biomaterial |
| WO2007069532A1 (en) * | 2005-12-12 | 2007-06-21 | Nakashima Propeller Co., Ltd. | Bone-compatible implant and method of producing the same |
| US20120064290A1 (en) * | 2008-12-01 | 2012-03-15 | The Furlong Research Charitable Foundation | Article and method of surface treatment of an article |
| JP2013022234A (en) * | 2011-07-21 | 2013-02-04 | Ngk Spark Plug Co Ltd | Biological implant and manufacturing method therefor |
-
1990
- 1990-01-24 JP JP2015652A patent/JP2710849B2/en not_active Expired - Fee Related
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| KR100487118B1 (en) * | 2001-03-05 | 2005-05-03 | 주식회사 바이오스마트 | Composition of Porous Element for Biomaterial |
| KR100441765B1 (en) * | 2001-11-14 | 2004-07-27 | 한국과학기술연구원 | Ti-BASED ALLOY BIOMATERIALS WITH ULTRA FINE BIOACTIVE POROUS SURFACE AND MANUFACTURING METHOD THEREOF |
| WO2007069532A1 (en) * | 2005-12-12 | 2007-06-21 | Nakashima Propeller Co., Ltd. | Bone-compatible implant and method of producing the same |
| JP2007159685A (en) * | 2005-12-12 | 2007-06-28 | Okayama Univ | Bone-compatible implant and method for producing the same |
| US8257445B2 (en) | 2005-12-12 | 2012-09-04 | Nakashima Medical Co., Ltd. | Bone-compatible implant and method of producing the same |
| US20120064290A1 (en) * | 2008-12-01 | 2012-03-15 | The Furlong Research Charitable Foundation | Article and method of surface treatment of an article |
| US9044528B2 (en) * | 2008-12-01 | 2015-06-02 | Ucl Business Plc | Article and method of surface treatment of an article |
| JP2013022234A (en) * | 2011-07-21 | 2013-02-04 | Ngk Spark Plug Co Ltd | Biological implant and manufacturing method therefor |
Also Published As
| Publication number | Publication date |
|---|---|
| JP2710849B2 (en) | 1998-02-10 |
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