JPH0592019A - Artificial joint - Google Patents
Artificial jointInfo
- Publication number
- JPH0592019A JPH0592019A JP27847191A JP27847191A JPH0592019A JP H0592019 A JPH0592019 A JP H0592019A JP 27847191 A JP27847191 A JP 27847191A JP 27847191 A JP27847191 A JP 27847191A JP H0592019 A JPH0592019 A JP H0592019A
- Authority
- JP
- Japan
- Prior art keywords
- stem
- artificial joint
- strength support
- strength
- direction strength
- 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
- 229920005989 resin Polymers 0.000 claims abstract description 38
- 239000011347 resin Substances 0.000 claims abstract description 38
- 239000000463 material Substances 0.000 claims abstract description 32
- 239000012783 reinforcing fiber Substances 0.000 claims abstract description 31
- 239000011247 coating layer Substances 0.000 claims abstract description 23
- 239000000835 fiber Substances 0.000 claims abstract description 18
- 229920000049 Carbon (fiber) Polymers 0.000 claims abstract description 7
- 239000004917 carbon fiber Substances 0.000 claims abstract description 7
- 239000003365 glass fiber Substances 0.000 claims abstract description 7
- 229910052751 metal Inorganic materials 0.000 claims description 15
- 239000002184 metal Substances 0.000 claims description 15
- 239000004696 Poly ether ether ketone Substances 0.000 claims description 9
- 229920002530 polyetherether ketone Polymers 0.000 claims description 9
- 229920006231 aramid fiber Polymers 0.000 claims description 6
- 239000004734 Polyphenylene sulfide Substances 0.000 claims description 5
- 229920000069 polyphenylene sulfide Polymers 0.000 claims description 5
- 239000011800 void material Substances 0.000 claims description 5
- VNWKTOKETHGBQD-UHFFFAOYSA-N methane Chemical compound C VNWKTOKETHGBQD-UHFFFAOYSA-N 0.000 claims description 4
- 229920001643 poly(ether ketone) Polymers 0.000 claims description 4
- 229920002492 poly(sulfone) Polymers 0.000 claims description 4
- -1 polyallyletherketone Polymers 0.000 claims description 3
- 238000005452 bending Methods 0.000 abstract description 26
- 229920006351 engineering plastic Polymers 0.000 abstract description 4
- 239000000543 intermediate Substances 0.000 abstract 2
- 229920000914 Metallic fiber Polymers 0.000 abstract 1
- 210000000988 bone and bone Anatomy 0.000 description 31
- 239000000126 substance Substances 0.000 description 17
- 210000001185 bone marrow Anatomy 0.000 description 10
- 238000000034 method Methods 0.000 description 9
- 230000002093 peripheral effect Effects 0.000 description 9
- 210000001503 joint Anatomy 0.000 description 8
- 230000000052 comparative effect Effects 0.000 description 7
- 238000000465 moulding Methods 0.000 description 5
- PXHVJJICTQNCMI-UHFFFAOYSA-N Nickel Chemical compound [Ni] PXHVJJICTQNCMI-UHFFFAOYSA-N 0.000 description 4
- PNEYBMLMFCGWSK-UHFFFAOYSA-N aluminium oxide Inorganic materials [O-2].[O-2].[O-2].[Al+3].[Al+3] PNEYBMLMFCGWSK-UHFFFAOYSA-N 0.000 description 4
- 239000004918 carbon fiber reinforced polymer Substances 0.000 description 4
- 239000000470 constituent Substances 0.000 description 4
- 238000002513 implantation Methods 0.000 description 4
- 231100000614 poison Toxicity 0.000 description 4
- 239000010935 stainless steel Substances 0.000 description 4
- 229910001220 stainless steel Inorganic materials 0.000 description 4
- 238000005728 strengthening Methods 0.000 description 4
- 239000003440 toxic substance Substances 0.000 description 4
- 238000004804 winding Methods 0.000 description 4
- 229910000990 Ni alloy Inorganic materials 0.000 description 3
- 229910001069 Ti alloy Inorganic materials 0.000 description 3
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 description 3
- WAIPAZQMEIHHTJ-UHFFFAOYSA-N [Cr].[Co] Chemical class [Cr].[Co] WAIPAZQMEIHHTJ-UHFFFAOYSA-N 0.000 description 3
- 238000007664 blowing Methods 0.000 description 3
- 239000000919 ceramic Substances 0.000 description 3
- 230000006835 compression Effects 0.000 description 3
- 238000007906 compression Methods 0.000 description 3
- 230000007797 corrosion Effects 0.000 description 3
- 238000005260 corrosion Methods 0.000 description 3
- 238000006073 displacement reaction Methods 0.000 description 3
- 229910052602 gypsum Inorganic materials 0.000 description 3
- 239000010440 gypsum Substances 0.000 description 3
- 238000004519 manufacturing process Methods 0.000 description 3
- 238000002844 melting Methods 0.000 description 3
- 230000008018 melting Effects 0.000 description 3
- 229910052759 nickel Inorganic materials 0.000 description 3
- 239000007787 solid Substances 0.000 description 3
- 239000010936 titanium Substances 0.000 description 3
- 229910052719 titanium Inorganic materials 0.000 description 3
- 229910052720 vanadium Inorganic materials 0.000 description 3
- VEXZGXHMUGYJMC-UHFFFAOYSA-N Hydrochloric acid Chemical compound Cl VEXZGXHMUGYJMC-UHFFFAOYSA-N 0.000 description 2
- MCMNRKCIXSYSNV-UHFFFAOYSA-N Zirconium dioxide Chemical compound O=[Zr]=O MCMNRKCIXSYSNV-UHFFFAOYSA-N 0.000 description 2
- 229910045601 alloy Inorganic materials 0.000 description 2
- 239000000956 alloy Substances 0.000 description 2
- 210000001124 body fluid Anatomy 0.000 description 2
- 239000010839 body fluid Substances 0.000 description 2
- SZMZREIADCOWQA-UHFFFAOYSA-N chromium cobalt nickel Chemical compound [Cr].[Co].[Ni] SZMZREIADCOWQA-UHFFFAOYSA-N 0.000 description 2
- 230000006378 damage Effects 0.000 description 2
- 238000010828 elution Methods 0.000 description 2
- 238000002474 experimental method Methods 0.000 description 2
- 238000009730 filament winding Methods 0.000 description 2
- 210000004394 hip joint Anatomy 0.000 description 2
- 238000001746 injection moulding Methods 0.000 description 2
- 230000002787 reinforcement Effects 0.000 description 2
- 229910001285 shape-memory alloy Inorganic materials 0.000 description 2
- 210000000689 upper leg Anatomy 0.000 description 2
- 238000005406 washing Methods 0.000 description 2
- ZOXJGFHDIHLPTG-UHFFFAOYSA-N Boron Chemical compound [B] ZOXJGFHDIHLPTG-UHFFFAOYSA-N 0.000 description 1
- 206010007269 Carcinogenicity Diseases 0.000 description 1
- 229910000756 V alloy Inorganic materials 0.000 description 1
- 238000010521 absorption reaction Methods 0.000 description 1
- 239000000654 additive Substances 0.000 description 1
- 239000004760 aramid Substances 0.000 description 1
- 230000001580 bacterial effect Effects 0.000 description 1
- 239000012620 biological material Substances 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 230000000740 bleeding effect Effects 0.000 description 1
- 239000008280 blood Substances 0.000 description 1
- 210000004369 blood Anatomy 0.000 description 1
- 229910052796 boron Inorganic materials 0.000 description 1
- 231100000260 carcinogenicity Toxicity 0.000 description 1
- 230000007670 carcinogenicity Effects 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 239000011651 chromium Substances 0.000 description 1
- 239000011248 coating agent Substances 0.000 description 1
- 238000000576 coating method Methods 0.000 description 1
- 239000002131 composite material Substances 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 230000001054 cortical effect Effects 0.000 description 1
- 230000006866 deterioration Effects 0.000 description 1
- 238000007598 dipping method Methods 0.000 description 1
- 238000007599 discharging Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 210000002310 elbow joint Anatomy 0.000 description 1
- 230000002708 enhancing effect Effects 0.000 description 1
- 239000000945 filler Substances 0.000 description 1
- 230000006870 function Effects 0.000 description 1
- 230000035876 healing Effects 0.000 description 1
- 210000001981 hip bone Anatomy 0.000 description 1
- 238000001727 in vivo Methods 0.000 description 1
- 208000015181 infectious disease Diseases 0.000 description 1
- 230000001788 irregular Effects 0.000 description 1
- 230000007794 irritation Effects 0.000 description 1
- 238000005304 joining Methods 0.000 description 1
- 230000008407 joint function Effects 0.000 description 1
- 150000002576 ketones Chemical class 0.000 description 1
- 210000000629 knee joint Anatomy 0.000 description 1
- 239000010410 layer Substances 0.000 description 1
- 210000000528 lesser trochanter Anatomy 0.000 description 1
- 230000007774 longterm Effects 0.000 description 1
- 229920001684 low density polyethylene Polymers 0.000 description 1
- 239000004702 low-density polyethylene Substances 0.000 description 1
- 150000002739 metals Chemical class 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000017074 necrotic cell death Effects 0.000 description 1
- 230000001338 necrotic effect Effects 0.000 description 1
- 231100000956 nontoxicity Toxicity 0.000 description 1
- 230000000399 orthopedic effect Effects 0.000 description 1
- 230000011164 ossification Effects 0.000 description 1
- 230000001737 promoting effect Effects 0.000 description 1
- 230000003014 reinforcing effect Effects 0.000 description 1
- 239000012779 reinforcing material Substances 0.000 description 1
- 210000000323 shoulder joint Anatomy 0.000 description 1
- 229920002379 silicone rubber Polymers 0.000 description 1
- 239000004945 silicone rubber Substances 0.000 description 1
- 239000003381 stabilizer Substances 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 230000002195 synergetic effect Effects 0.000 description 1
- 229920005992 thermoplastic resin Polymers 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
- 231100000331 toxic Toxicity 0.000 description 1
- 230000002588 toxic effect Effects 0.000 description 1
- LEONUFNNVUYDNQ-UHFFFAOYSA-N vanadium atom Chemical compound [V] LEONUFNNVUYDNQ-UHFFFAOYSA-N 0.000 description 1
- 239000002759 woven fabric Substances 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
Landscapes
- Prostheses (AREA)
Abstract
Description
【０００１】[0001]
【産業上の利用分野】本発明は、生体の骨関節を代替す
る人工関節に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an artificial joint which replaces a bone joint of a living body.
【０００２】[0002]
【従来の技術】人体内の骨関節の変形や欠損を人工関節
を用いて代替えする治療は、整形外科等で広く行なわれ
ている。例えば、大腿骨骨頭壊死に対し、壊死した骨頭
を除去した後、人工関節を補綴し、関節機能を回復させ
ることが頻繁に行なわれている。2. Description of the Related Art Treatment for replacing the deformation or loss of bone joints in the human body with artificial joints is widely performed in orthopedics and the like. For example, with respect to femoral head necrosis, it is often practiced to remove the necrotic head and then restore the joint function by prosthesis of an artificial joint.
【０００３】すなわち、この治療では、骨頭およびステ
ム部を有する人工関節のステム部を大腿骨の骨髄腔に埋
入して固定すると共に、カップ（ソケット）を腰骨に固
定し、該カップの凹部に骨頭を嵌合してこれらを回動自
在に連結する。That is, in this treatment, the stem part of an artificial joint having a femoral head and a stem part is embedded and fixed in the medullary cavity of the femur, and a cup (socket) is fixed to the lumbar bone and the concave part of the cup is fixed. The bone heads are fitted and these are rotatably connected.
【０００４】このような人工関節には、機械的強度、弾
性（靱性）、耐久性、生体内での安定性（体液に対する
腐食、劣化等がないこと）、生体親和性（造骨促進作用
等の周辺組織との適合性）、安全性（毒性、分解性等が
ないこと）、加工性等の特性が要求されている。Such an artificial joint has mechanical strength, elasticity (toughness), durability, in-vivo stability (no corrosion or deterioration with respect to body fluid), and biocompatibility (bone formation promoting action, etc.). Properties such as compatibility with surrounding tissues), safety (no toxicity, degradability, etc.) and processability are required.
【０００５】しかしながら、これら全ての特性を満足す
る材料は未だ発見されておらず、現在では、人工関節の
構成材料として、主に、ステンレス鋼、コバルト−クロ
ム合金、チタン、チタン合金等の金属、またはアルミナ
等のセラミックスが用いられている。However, a material satisfying all of these characteristics has not been found yet, and at present, as a constituent material of an artificial joint, mainly a metal such as stainless steel, cobalt-chromium alloy, titanium, titanium alloy, or the like, Alternatively, ceramics such as alumina are used.
【０００６】ところで、金属製の人工関節は、生体骨に
比べ曲げ弾性率が著しく大きい。すなわち、ヒト皮質骨
の曲げ弾性率は、約１６GPa であり、人工関節に用いら
れているステンレス鋼（ＳＵＳ３１６Ｌ）、Ｃｏ−Ｃｒ
合金、Ｔｉ−６％Ａｌ−４％Ｖ合金の曲げ弾性率は、そ
れぞれ、２００、２１３、１２４GPa であり、骨の８〜
１３倍である。By the way, the bending modulus of elasticity of the artificial joint made of metal is significantly larger than that of the living bone. That is, the bending elastic modulus of human cortical bone is about 16 GPa, and stainless steel (SUS316L) and Co-Cr used for artificial joints are used.
Alloys and Ti-6% Al-4% V alloys have bending elastic moduli of 200, 213 and 124 GPa, respectively, which are 8 to 10% of that of bone.
13 times.
【０００７】また、金属製の人工関節は、重量が重く、
患者の負担（または負担感）が大きいという欠点があ
る。[0007] Further, the artificial joint made of metal is heavy,
There is a drawback that the burden (or feeling of burden) on the patient is large.
【０００８】さらに、ニッケルやバナジウムは、生体に
とって有毒であり、発癌性があることも報告されている
が、上記金属製の人工関節では、このような有毒物質の
溶出がわずかながら生じることがある。Furthermore, nickel and vanadium have been reported to be toxic to the living body and have carcinogenicity, but in the above-mentioned metallic artificial joints, such toxic substances may slightly elute. ..
【０００９】人工関節とこれを埋入する生体骨との間に
は、例えば体重や歩行等の運動により荷重、特に繰り返
し荷重が加わるが、金属製の人工関節では、上述のよう
に、曲げ弾性率が高いため、前記荷重により曲げ、ねじ
れ、たわみが生じると、局所的に応力が集中し、この集
中部分において骨が破壊されることがある。A load, especially a repeated load is applied between the artificial joint and the living bone into which the artificial joint is embedded due to, for example, a motion such as weight or walking, but in the case of a metal artificial joint, as described above, the bending elasticity is increased. Because of the high rate, when the load causes bending, twisting, or bending, stress is locally concentrated, and bone may be broken at this concentrated portion.
【００１０】また、前記荷重が人工関節のステム部から
生体骨に伝達される部分では骨の増勢（造骨作用）が見
られるが、前記応力集中部以外の荷重が加わらない部分
では、骨への刺激がなくなるため、逆に骨組織の吸収が
起こり、骨量が減少して人工関節の生体骨への固定に緩
みが生じることが報告されている。In the portion where the load is transmitted from the stem portion of the artificial joint to the living bone, the bone is strengthened (bone-forming effect), but in the portion other than the stress concentration portion where the load is not applied, the bone is applied to the bone. It has been reported that the bone tissue is resorbed and the bone mass is reduced to loosen the fixation of the artificial joint to the living bone because the irritation is eliminated.
【００１１】このような状況下で、上記有毒物質の溶出
がなく、しかも、人工関節の曲げ弾性率を生体骨のそれ
に適合させうる方法として、エンジニアリングプラスチ
ックスを用いて人工関節のステム部を作製することが提
案されている（米国特許第４９０２２９７号）。Under such circumstances, the stem portion of the artificial joint is manufactured by using engineering plastics as a method for adjusting the bending elastic modulus of the artificial joint to that of the living bone without elution of the above-mentioned toxic substances. Has been proposed (US Pat. No. 4,902,297).
【００１２】しかしながら、エンジニアリングプラスチ
ックスは、それ自体、強度、特に引張り応力、圧縮応力
に対する強度が不足するため、単独で用いるには適さ
ず、炭素繊維、ガラス繊維、アラミド繊維等の強化繊維
を埋入した繊維強化樹脂として使用することが試みられ
ている。However, since engineering plastics themselves lack strength, particularly strength against tensile stress and compressive stress, they are not suitable for use alone and are reinforced with reinforcing fibers such as carbon fibers, glass fibers and aramid fibers. Attempts have been made to use it as an incorporated fiber reinforced resin.
【００１３】この場合、繊維強化樹脂は、繊維の方向
（強化方向）がステム部長手方向となるように用いら
れ、プレス成形や引抜き成形により製造されることか
ら、その横断面における繊維の配設状態は、ステム部の
長手方向に沿って一様である。従って、不規則でしかも
個々の症例に応じて形状が異なる骨髄腔への形状合わせ
を行なうためには、棒状の繊維強化樹脂をステム部の中
心部に置き、その周囲に同様の樹脂にて肉付けをして形
状を調整する方法を採らざるをえない。In this case, the fiber-reinforced resin is used so that the direction of the fibers (strengthening direction) is the longitudinal direction of the stem portion and is manufactured by press molding or pultrusion molding, so that the fibers are arranged in the cross section thereof. The state is uniform along the longitudinal direction of the stem portion. Therefore, in order to match the shape of the bone marrow cavity, which is irregular and has a different shape depending on the individual case, place a rod-shaped fiber-reinforced resin in the center of the stem and add a similar resin around it. There is no choice but to adopt a method of adjusting the shape by doing.
【００１４】ところで、人工関節のステム部には、引っ
張り応力や圧縮応力の他に、曲げやねじれの応力が加わ
るが、これらの曲げやねじれに対する強度は、ステム部
の中心部よりはむしろ外周部付近の材料強度に大きく左
右される。この場合、ステム部の外周部付近は、上記の
ごとく、肉付けがなされた樹脂で構成されているため、
その材料自体の強度は弱く、よって、ステム部は、曲げ
やねじれに対する強度が弱いものとなっていた。By the way, in addition to tensile stress and compressive stress, bending and twisting stresses are applied to the stem portion of the artificial joint, and the strength against these bending and twisting is not the central portion of the stem portion but the outer peripheral portion thereof. It is greatly affected by the material strength in the vicinity. In this case, since the vicinity of the outer peripheral portion of the stem portion is made of the resin that has been fleshed out as described above,
The strength of the material itself is weak, so that the stem portion is weak in strength against bending and twisting.
【００１５】また、この欠点を改善すべく、前記棒状の
繊維強化樹脂の周囲に、同様の強化繊維をステム部の外
周方向に沿って配設し、さらにその外周に樹脂にて肉付
けをして形状を調整する方法も提案されているが、この
場合でも、やはりステム部の外周部付近は、肉付けがな
された樹脂で構成されることとなるため、曲げやねじれ
に対する強度を十分に改善するには至っていない。In order to remedy this drawback, similar reinforcing fibers are arranged around the rod-shaped fiber reinforced resin along the outer peripheral direction of the stem portion, and the outer periphery thereof is fleshed with resin. A method of adjusting the shape has also been proposed, but even in this case, since the vicinity of the outer peripheral portion of the stem portion will be composed of a resin that has been fleshed out, it is possible to sufficiently improve the strength against bending and twisting. Has not arrived.
【００１６】特に、ステム部のうちのステム基部（ステ
ム部のネック部側）は、人工関節を生体骨に埋入、固定
する上での主要部分であり、あらゆる応力が集中し易い
ため、十分な強度を必要とするが、このステム基部は、
埋入時に骨髄腔が拡大した部分に位置するため、他所よ
り太くなっており、そのため、肉付けされる樹脂の厚さ
も厚くなる。従って、このステム基部では、前記ステム
部外周方向に沿って配設した強化繊維の曲げやねじれに
対する補強効果はほとんど得られていない。Particularly, the stem base portion (neck portion side of the stem portion) of the stem portion is a main portion for embedding and fixing the artificial joint in the living bone, and since any stress is likely to be concentrated, it is sufficient. However, this stem base is
Since the bone marrow cavity is located in the enlarged portion at the time of implantation, it is thicker than other places, and therefore the thickness of the resin to be fleshed is also thick. Therefore, in this stem base portion, almost no reinforcing effect against bending and twisting of the reinforcing fibers arranged along the outer peripheral direction of the stem portion is obtained.
【００１７】[0017]
【発明が解決しようとする課題】本発明の目的は、エン
ジニアリングプラスチックスの特性を生かしつつ、引っ
張り、圧縮に対する強度のみならず、曲げ、ねじれに対
する強度をも高めることができる人工関節を提供するこ
とにある。SUMMARY OF THE INVENTION An object of the present invention is to provide an artificial joint capable of enhancing not only the strength against pulling and compression but also the strength against bending and twisting while making the most of the characteristics of engineering plastics. It is in.
【００１８】[0018]
【課題を解決するための手段】このような目的は、下記
（１）〜（５）の本発明により達成される。These objects are achieved by the present invention described in (1) to (5) below.
【００１９】（１）頭部と、これに続くネック部と、こ
れに続くステム部とで構成された人工関節において、前
記ステム部は、ステム基部とステム先端部とで構成さ
れ、少なくとも前記ステム基部においては、中間部を介
して一対の一次方向強度支持部が対向配置され、かつ両
一次方向強度支持部の外周に二次方向強度支持部が配置
されており、前記一次方向強度支持部は、生体用樹脂材
料に強化繊維が埋入され、該強化繊維により、前記ステ
ム部の長手方向に強化されたものであり、前記二次方向
強度支持部は、生体用樹脂材料に強化繊維が埋入され、
該強化繊維により、前記ステム部の長手方向に対し４５
〜１３５°の方向に強化されたものであることを特徴と
する人工関節。(1) In an artificial joint comprising a head portion, a neck portion following the head portion, and a stem portion following the head portion, the stem portion includes a stem base portion and a stem tip portion, and at least the stem. In the base portion, the pair of primary direction strength support portions are arranged to face each other via the intermediate portion, and the secondary direction strength support portions are arranged on the outer periphery of both primary direction strength support portions, and the primary direction strength support portion is The reinforcing fiber is embedded in the biomedical resin material, and is reinforced in the longitudinal direction of the stem portion by the reinforced fiber. Entered,
With the reinforcing fiber, 45
An artificial joint characterized by being reinforced in the direction of ~ 135 °.
【００２０】（２）前記中間部が空隙である上記（１）
に記載の人工関節。(2) The above (1) wherein the intermediate portion is a void.
The artificial joint described in.
【００２１】（３）前記一次方向強度支持部および／ま
たは前記二次方向強度支持部における強化繊維は、炭素
繊維、ガラス繊維、アラミド繊維、金属繊維よりなる群
から選ばれた少なくとも一種である上記（１）または
（２）に記載の人工関節。(3) The reinforcing fiber in the primary direction strength supporting portion and / or the secondary direction strength supporting portion is at least one selected from the group consisting of carbon fiber, glass fiber, aramid fiber and metal fiber. The artificial joint according to (1) or (2).
【００２２】（４）前記一次方向強度支持部および／ま
たは前記二次方向強度支持部における生体用樹脂材料
は、ポリエーテルケトン、ポリエーテルエーテルケト
ン、ポリアリルエーテルケトン、ポリフェニレンサルフ
ィド、ポリサルフォンよりなる群から選ばれた少なくと
も一種である上記（１）ないし（３）のいずれかに記載
の人工関節。(4) The biomedical resin material in the primary direction strength support portion and / or the secondary direction strength support portion is composed of polyetherketone, polyetheretherketone, polyallyletherketone, polyphenylene sulfide, polysulfone. The artificial joint according to any one of (1) to (3) above, which is at least one selected from the group.
【００２３】（５）前記二次方向強度支持部の外周に被
覆層を有する上記（１）ないし（４）のいずれかに記載
の人工関節。(5) The artificial joint as described in any one of (1) to (4) above, which has a coating layer on the outer periphery of the secondary strength support portion.
【００２４】[0024]
【発明の構成】以下、本発明の人工関節を添付図面に示
す好適実施例に基づいて詳細に説明する。DETAILED DESCRIPTION OF THE INVENTION The artificial joint of the present invention will now be described in detail with reference to the preferred embodiments shown in the accompanying drawings.
【００２５】図１は、本発明の人工関節の構成例を示す
正面図、図２は、図１中のＡ−Ａ線での断面図、図３
は、図１中のＢ−Ｂ線での断面図、図４は、図１中のＣ
−Ｃ線での断面図である。図１に示すように、人工関節
（人工骨頭）１は、頭部２と、これに続くネック部３
と、これに続く金属製のステム部４とで構成されてい
る。FIG. 1 is a front view showing a constitutional example of an artificial joint of the present invention, FIG. 2 is a sectional view taken along line AA in FIG. 1, and FIG.
Is a cross-sectional view taken along line BB in FIG. 1, and FIG. 4 is C in FIG.
It is sectional drawing in the -C line. As shown in FIG. 1, an artificial joint (artificial head) 1 includes a head 2 and a neck portion 3 following the head 2.
And a stem part 4 made of metal following this.
【００２６】頭部２は、例えば球状のような湾曲面を有
する部材であり、この頭部２は、図示しないカップ（ソ
ケット）の凹部に嵌合してこれらが回動自在に連結され
る。The head 2 is a member having a curved surface such as a sphere, and the head 2 is fitted in a recess of a cup (socket) (not shown) so that they are rotatably connected.
【００２７】頭部２の構成材料としては、耐摩耗性、動
特性向上の理由から、好ましくは硬質材料が用いられ
る。具体的には、例えば、ステンレス鋼（例えば、ＳＵ
Ｓ３１６、ＳＵＳ３１６Ｌ）、コバルト−クロム合金、
コバルト−クロム−ニッケル合金、チタン、チタン合金
（例えばＴｉ−６％Ａｌ−４％Ｖ）または、それらの表
面硬化処理物等の耐食性に優れる金属、合金、または、
例えばアルミナ、ジルコニア等のセラミックスを用いる
ことができる。As a constituent material of the head portion 2, a hard material is preferably used in order to improve wear resistance and dynamic characteristics. Specifically, for example, stainless steel (for example, SU
S316, SUS316L), cobalt-chromium alloy,
Cobalt-chromium-nickel alloy, titanium, titanium alloy (for example, Ti-6% Al-4% V), or metal, alloy, or the like having excellent corrosion resistance such as a surface-hardened product thereof, or
For example, ceramics such as alumina and zirconia can be used.
【００２８】また、頭部２は、中空でも中実でもよい。
ネック部３は、前記頭部２と例えばネジ止め、テーパ
嵌合、接着等により連結されている。The head 2 may be hollow or solid.
The neck portion 3 is connected to the head portion 2 by, for example, screwing, taper fitting, bonding or the like.
【００２９】ステム部４は、骨髄腔に埋入されて固定さ
れる部分であり、好ましくは前記ネック部３と連続して
一体的に形成されている。このステム部４は、ネック部
３側のステム基部５とステム先端部６とで構成されてい
る。The stem portion 4 is a portion that is embedded and fixed in the bone marrow cavity, and is preferably formed continuously and integrally with the neck portion 3. The stem portion 4 includes a stem base portion 5 on the neck portion 3 side and a stem tip portion 6.
【００３０】主に、ステム基部５の外周と骨髄腔（特
に、リーミングにより拡大されて骨髄腔）とが密着する
ため、ステム基部５はネック部３やステム先端部６より
太くなっており、その形状は、埋入する骨髄腔の形状と
一致するように成形されている。また、ステム先端部６
は、骨髄腔の奥部まで挿入されるため、先細りの形状を
なしている。Since the outer periphery of the stem base 5 and the bone marrow cavity (in particular, the bone marrow cavity enlarged by reaming) are in close contact with each other, the stem base 5 is thicker than the neck portion 3 and the stem tip portion 6. The shape is shaped to match the shape of the bone marrow cavity to be implanted. Also, the stem tip 6
Has a tapered shape because it is inserted deep into the bone marrow cavity.
【００３１】図示のように、ステム先端部６の軸線は、
ネック部３の軸線に対し、例えば１５〜３５度程度傾斜
している。As shown, the axis of the stem tip 6 is
It is inclined, for example, by about 15 to 35 degrees with respect to the axis of the neck portion 3.
【００３２】このようなネック部３およびステム部４
は、図２、図３および図４に示すように、芯材として一
対の一次方向強度支持部７ａ、７ｂが対向配置され、こ
れらのの外周に二次方向強度支持部９が配置されてお
り、さらに、その外周を被覆層１１で被覆したものであ
る。Such a neck portion 3 and a stem portion 4
As shown in FIGS. 2, 3 and 4, a pair of primary direction strength support portions 7a and 7b are arranged as a core member so as to face each other, and a secondary direction strength support portion 9 is arranged on the outer periphery thereof. Further, the outer periphery thereof is coated with the coating layer 11.
【００３３】一次方向強度支持部７ａ、７ｂは、後述す
る生体用樹脂材料（以下、単に樹脂ともいう）に強化繊
維１０が埋入された繊維強化樹脂で構成されている。こ
の場合、強化繊維１０の方向は、ステム部４の長手方向
であり、従って、一次方向強度支持部７ａ、７ｂは、ス
テム部の長手方向に強化されたものである。これによ
り、ネック部３およびステム部４は、その長手方向に負
荷される引っ張り応力および圧縮応力に対し、十分な強
度が得られる。The primary-direction strength support portions 7a and 7b are made of a fiber-reinforced resin in which a reinforcing fiber 10 is embedded in a biomedical resin material (hereinafter, also simply referred to as a resin) described later. In this case, the direction of the reinforcing fibers 10 is the longitudinal direction of the stem portion 4, and therefore the primary strength support portions 7a, 7b are reinforced in the longitudinal direction of the stem portion. As a result, the neck portion 3 and the stem portion 4 have sufficient strength against tensile stress and compressive stress applied in the longitudinal direction thereof.
【００３４】図２および図４に示すように、ネック部３
およびステム先端部６においては、一次方向強度支持部
７ａおよび７ｂは密着して接合され、中実の棒状をなし
ているが、図３に示すように、ステム基部５において
は、一次方向強度支持部７ａおよび７ｂが中間部８を介
して対向配置されている。この中間部８は、図示の例で
は、空隙（空間）である。As shown in FIGS. 2 and 4, the neck portion 3
Also, at the stem tip portion 6, the primary direction strength support portions 7a and 7b are intimately bonded and joined to each other to form a solid rod shape. However, as shown in FIG. The portions 7a and 7b are arranged to face each other with the intermediate portion 8 interposed therebetween. The intermediate portion 8 is a void (space) in the illustrated example.
【００３５】ネック部３およびステム部４の強度は、そ
の中心部よりはむしろ外周部付近の材料の強度に大きく
左右されるが、この中間部８を設けることにより、一次
方向強度支持部７ａ、７ｂおよび後述する二次方向強度
支持部９をより外周部付近に位置させることができ、ネ
ック部３およびステム部４の強度を確保する上で有利で
ある。The strengths of the neck portion 3 and the stem portion 4 are largely influenced by the strength of the material in the vicinity of the outer peripheral portion, rather than the central portion thereof. By providing the intermediate portion 8, the primary direction strength supporting portion 7a, 7b and the secondary direction strength support portion 9 described later can be located closer to the outer peripheral portion, which is advantageous in securing the strength of the neck portion 3 and the stem portion 4.
【００３６】また、中間部８を空隙とすることにより、
人工関節１の軽量化を図ることができ、患者の負担を軽
減することができると共に、繊維強化樹脂材料の節減に
もなる。Further, by making the intermediate portion 8 a void,
The weight of the artificial joint 1 can be reduced, the burden on the patient can be reduced, and the fiber-reinforced resin material can be saved.
【００３７】なお、本発明では、中間部８に、例えば、
シリコーンゴム、低密度ポリエチレン、生体用樹脂材料
のような充填物が充填されていてもよい。In the present invention, the intermediate portion 8 may be, for example,
Fillers such as silicone rubber, low density polyethylene, and biomedical resin materials may be filled.
【００３８】このような中間部８は、少なくともステム
基部５に設けられる。その理由は、次の通りである。Such an intermediate portion 8 is provided at least in the stem base portion 5. The reason is as follows.
【００３９】人工関節１を例えば大腿骨に埋入、固定す
る場合、ステム先端部６は緻密質の部分（コンパクトボ
ーン）まで挿入され、その上部のステム基部５は海綿骨
の部分に位置することとなるが、海綿骨ではリーミング
により骨髄腔が拡大しているため、ステム基部５の外周
との接触面積が大きくなり、ステム基部５への応力の集
中も生じ易く、よって、生体骨との曲げ弾性率や強度の
バランスが重要となる。金属製のステム部に見られるよ
うな曲げ弾性率の過多による骨の破壊や吸収（特にカル
カー部の骨の吸収）を防止し、かつ十分な強度および耐
久性を得るためには、人工関節埋入時の小転子より上部
であるステム基部５の曲げ弾性率および強度を改善する
ことが特に有効となる。When implanting and fixing the artificial joint 1 in, for example, the femur, the stem tip 6 is inserted up to the compact part (compact bone), and the stem base 5 above it is located in the cancellous bone part. However, in the cancellous bone, since the bone marrow cavity is enlarged due to reaming, the contact area with the outer circumference of the stem base 5 is large, and stress is likely to be concentrated on the stem base 5, so that bending with the living bone is performed. The balance of elastic modulus and strength is important. In order to prevent bone destruction and resorption (especially resorption of bone in the calcar part) due to excessive bending elasticity as seen in the metal stem part, and to obtain sufficient strength and durability, artificial joint implantation is required. It is particularly effective to improve the flexural modulus and strength of the stem base 5 which is above the lesser trochanter when it is inserted.
【００４０】ネック部３およびステム先端部６は、ステ
ム基部５に比べて細いため、中間部８を設ける必要性は
比較的少ないが、本発明では、ネック部３やステム先端
部６の全域または一部に中間部８を設けてもよい。Since the neck portion 3 and the stem tip portion 6 are thinner than the stem base portion 5, it is relatively unnecessary to provide the intermediate portion 8. However, in the present invention, the neck portion 3 and the stem tip portion 6 are entirely or You may provide the intermediate part 8 in a part.
【００４１】中間部８の全長（ステム部４の長手方向）
は、１０〜１００mm程度、特に、２０〜６０mm程度とす
るのが好ましい。Total length of the intermediate portion 8 (longitudinal direction of the stem portion 4)
Is preferably about 10 to 100 mm, and more preferably about 20 to 60 mm.
【００４２】また、空隙による中間部８は、人工関節１
の外部に連通しない閉空間であるのが好ましい。その理
由は、骨髄腔に死腔が少なく、例えば手術時に出血した
血液やその他の体液が閉空間である中間部８に貯留する
ことがないので、治癒反応の遅延や細菌の繁殖による感
染を防止することができる。Also, the intermediate portion 8 formed by the void is the artificial joint 1
It is preferable that the closed space does not communicate with the outside of the. The reason is that there are few dead spaces in the bone marrow cavity and, for example, blood and other body fluids bleeding during surgery are not stored in the intermediate part 8 which is a closed space, so that the delay of the healing reaction and the infection due to bacterial propagation are prevented. can do.
【００４３】なお、ステム基部５の横段面積に対する中
間部８の横段面積の比率（以下、面積比という）は、特
に限定されないが、通常は、１０〜６０％程度、特に、
２０〜４０％程度とするのが好ましい。この値は、ステ
ム基部長手方向の最大長径での値を示す。The ratio of the horizontal area of the intermediate portion 8 to the horizontal area of the stem base 5 (hereinafter referred to as area ratio) is not particularly limited, but is usually about 10 to 60%, and particularly,
It is preferably about 20 to 40%. This value shows the value at the maximum major axis in the longitudinal direction of the stem base.
【００４４】二次方向強度支持部９は、生体用樹脂材料
に強化繊維１０が埋入された繊維強化樹脂で構成されて
いる。この場合、強化繊維１０の方向は、前記ステム部
の長手方向に対し４５〜１３５°の方向であり、従っ
て、二次方向強度支持部９は、ステム部の長手方向に対
し４５〜１３５°の方向に強化されたものである。これ
により、ネック部３およびステム部４は、その長手方向
に負荷される曲げおよびねじれの応力に対し、十分な強
度が得られる。The secondary strength support portion 9 is made of a fiber-reinforced resin in which a reinforcing fiber 10 is embedded in a biomedical resin material. In this case, the direction of the reinforcing fibers 10 is 45 to 135 ° with respect to the longitudinal direction of the stem portion, and therefore, the secondary direction strength support portion 9 is 45 to 135 ° with respect to the longitudinal direction of the stem portion. It has been strengthened in the direction. As a result, the neck portion 3 and the stem portion 4 have sufficient strength against bending and twisting stresses applied in the longitudinal direction thereof.
【００４５】二次方向強度支持部９の強化方向は、ステ
ム部の長手方向に対し４５〜１３５°の方向であり、好
ましくは、６０〜１２０°の方向である。二次方向強度
支持部９の強化方向がステム部の長手方向に対し４５°
未満または１３５°超であると、一次方向強度支持部７
ａ、７ｂの強化方向に近づきすぎ、曲げおよびねじれに
対する強度が不足する傾向となるからである。The strengthening direction of the secondary direction strength support portion 9 is 45 to 135 ° with respect to the longitudinal direction of the stem portion, and preferably 60 to 120 °. Secondary direction strength Strengthening direction of the supporting portion 9 is 45 ° with respect to the longitudinal direction of the stem portion.
If it is less than or more than 135 °, the primary direction strength support portion 7
This is because the strengths of a and 7b are too close to each other, and the strength against bending and twisting tends to be insufficient.
【００４６】二次方向強度支持部９の厚さ、特に、ステ
ム基部５における厚さは、平均０．３〜２．５mm程度が
好ましく、平均０．５〜１．５mm程度がより好ましい。
この厚さが０．３mm未満では、二次方向強度支持部９の
強化方向によっては、曲げおよびねじれに対する強度が
不足することがあり、また、２．５mmを超えると、ステ
ム基部全体の太さが限定されている関係上、不都合とな
る。The thickness of the secondary direction strength support portion 9, particularly the thickness of the stem base portion 5, is preferably about 0.3 to 2.5 mm on average, and more preferably about 0.5 to 1.5 mm on average.
If the thickness is less than 0.3 mm, the strength against bending and twisting may be insufficient depending on the strengthening direction of the secondary strength support portion 9, and if it exceeds 2.5 mm, the thickness of the entire stem base portion may be insufficient. It is inconvenient because of the limitation.
【００４７】このような二次方向強度支持部９は、例え
ばフィラメントワインディング法またはその改良法によ
り製造することができる。The secondary strength support portion 9 can be manufactured, for example, by the filament winding method or an improved method thereof.
【００４８】このような製造方法により製造された二次
方向強度支持部９の構成例を図５に示す。同図に示すよ
うに、二次方向強度支持部９は、接合された一次方向強
度支持部７ａおよび７ｂの外周に、溶融した生体用樹脂
材料に浸漬された強化繊維１０を、その方向がステム部
の長手方向に対し４５〜１３５°となるように巻き付
け、その後、溶融した生体用樹脂材料を固化してなるも
のである。この場合、強化繊維１０を巻き付ける際また
は巻き付けた後、熱風を吹き付けること等により生体用
樹脂材料を再度溶融し、さらには、熱風吹き付け後、必
要に応じローラーにて圧着し、二次方向強度支持部９の
表面を平滑化するのが好ましい。FIG. 5 shows an example of the structure of the secondary strength support portion 9 manufactured by such a manufacturing method. As shown in the figure, the secondary-direction strength support portion 9 has a structure in which the reinforced fiber 10 dipped in the molten biomedical resin material is provided on the outer periphery of the joined primary-direction strength support portions 7a and 7b in a stem direction. It is formed by winding at 45 to 135 ° with respect to the longitudinal direction of the part, and then solidifying the molten biomedical resin material. In this case, when or after winding the reinforcing fiber 10, the biomedical resin material is melted again by blowing hot air or the like, and further, after blowing hot air, pressure bonding with a roller is performed to support the secondary strength. It is preferable to smooth the surface of the portion 9.
【００４９】このようにして得られた二次方向強度支持
部９の形状（輪郭）は、得ようとするネック部３および
ステム部４の形状にほぼ等しく、このような二次方向強
度支持部９を用いれば、曲げおよびねじれに対する強度
が極めて高い人工関節が得られる。The shape (contour) of the secondary direction strength supporting portion 9 thus obtained is substantially the same as the shape of the neck portion 3 and the stem portion 4 to be obtained, and such a secondary direction strength supporting portion 9 is formed. When 9 is used, an artificial joint having extremely high strength against bending and twisting can be obtained.
【００５０】なお、上記方法において、溶融樹脂付着強
化繊維１０の巻き付けに代わり、リボン状（薄板状）に
成形された繊維強化樹脂を巻き付けてもよい。In the above method, instead of winding the molten resin-adhered reinforcing fiber 10, a ribbon-shaped (thin plate-shaped) fiber-reinforced resin may be wound.
【００５１】以上のごとく、一次方向強度支持部７ａ、
７ｂは、主に、ネック部３およびステム部４の長手方向
に負荷される荷重に対する強度を担い、二次方向強度支
持部９は、主に、ネック部３およびステム部４の曲げ、
ねじれに対する強度を担うこととなり、これらを組み合
せたことによる相乗作用により、引っ張り、圧縮、曲
げ、ねじれ等の応力に対する十分な強度および適度な弾
性率を有し、前記応力が繰り返し、頻繁に負荷された場
合でも、追従性が良く、優れた耐久性を有する。As described above, the primary strength support 7a,
7b mainly bears the strength against the load applied in the longitudinal direction of the neck portion 3 and the stem portion 4, and the secondary direction strength support portion 9 mainly bends the neck portion 3 and the stem portion 4,
It bears the strength against twisting, and due to the synergistic effect of combining these, it has sufficient strength against stress such as tension, compression, bending, twisting, etc. and an appropriate elastic modulus, and the stress is repeatedly and frequently applied. Even if it does, it has good followability and has excellent durability.
【００５２】また、本発明の人工関節は、ネック部３お
よびステム部４の外表面に、生体にとって有害な金属が
存在しないため、そのような毒性物質の溶出が生じず、
安全である。Further, in the artificial joint of the present invention, since no metal harmful to the living body exists on the outer surfaces of the neck portion 3 and the stem portion 4, such toxic substances are not eluted,
It's safe.
【００５３】なお、本発明では、二次方向強度支持部９
が２層以上あってもよい。この場合、各二次方向強度支
持部９における繊維強化方向は、それぞれ異なっている
（特に、一次方向強度支持部に対し、９０°以上と９０
°未満）のが好ましく、これにより強度がより一層増
す。In the present invention, the secondary strength support portion 9
There may be two or more layers. In this case, the fiber reinforcement directions in the respective secondary direction strength supporting portions 9 are different from each other (in particular, 90 ° or more and 90 ° or more relative to the primary direction strength supporting portion).
(Less than 0 °), which further increases the strength.
【００５４】一次方向強度支持部７ａ、７ｂおよび二次
方向強度支持部９における強化繊維１０は、織物、編物
または網状物（メッシュ）等のような加工された形態で
埋入されていてもよい。The reinforcing fibers 10 in the primary strength support parts 7a, 7b and the secondary strength support part 9 may be embedded in a processed form such as a woven fabric, a knitted material or a mesh. ..
【００５５】このような強化繊維１０の素材としては、
例えば、炭素繊維、ガラス繊維、アラミド繊維、ボロン
繊維または金属繊維等が挙げられるが、その中でも特
に、強度が高く、また樹脂との複合性がよいという点
で、炭素繊維、ガラス繊維、アラミド繊維、金属繊維の
うちの１種または２種以上を組み合せて用いるのが好ま
しい。As a material for such a reinforcing fiber 10,
Examples thereof include carbon fiber, glass fiber, aramid fiber, boron fiber, metal fiber, and the like. Among them, carbon fiber, glass fiber, and aramid fiber are particularly preferable because of their high strength and good composite with resin. It is preferable to use one kind or a combination of two or more kinds of metal fibers.
【００５６】なお、金属繊維の構成材料としては、例え
ば、ステンレス鋼（例えば、ＳＵＳ３１６、ＳＵＳ３１
６Ｌ）、コバルト−クロム合金、コバルト−クロム−ニ
ッケル合金、チタン、チタン合金（例えばＴｉ−６％Ａ
ｌ−４％Ｖ、Ｔｉ−４９〜５１％Ｎｉ）等の耐食性に優
れる金属を用いることができる。その中でも特に、形状
記憶合金（Ｔｉ−４９〜５１％Ｎｉ）を用いるのが好ま
しい。この形状記憶合金は、繰り返し荷重に対する追従
性、復元性、疲労特性が優れるため、長期の埋入におい
て安定性、耐久性が向上する。The constituent material of the metal fiber is, for example, stainless steel (for example, SUS316, SUS31).
6L), cobalt-chromium alloy, cobalt-chromium-nickel alloy, titanium, titanium alloy (for example, Ti-6% A).
1-4% V, Ti-49 to 51% Ni) and other metals having excellent corrosion resistance can be used. Among them, it is particularly preferable to use the shape memory alloy (Ti-49 to 51% Ni). Since this shape memory alloy has excellent followability with respect to repeated loads, resilience, and fatigue characteristics, stability and durability are improved during long-term implantation.
【００５７】強化繊維１０の直径の好適な範囲は、その
構成材料にもよるが、好ましくは０．３〜１．５mm、よ
り好ましくは０．６〜１．２mm、さらに好ましくは０．
８〜１．０mmである。強化繊維１０の直径が０．３mm未
満では、耐荷重性が不足し、１．５mmを超えると、その
剛性のために生体骨に対しダメージを与えることがあ
る。The preferred range of the diameter of the reinforcing fiber 10 depends on its constituent material, but is preferably 0.3 to 1.5 mm, more preferably 0.6 to 1.2 mm, and further preferably 0.
It is 8 to 1.0 mm. If the diameter of the reinforcing fiber 10 is less than 0.3 mm, the load bearing capacity is insufficient, and if it exceeds 1.5 mm, the bone may be damaged due to its rigidity.
【００５８】一次方向強度支持部７ａ、７ｂおよび二次
方向強度支持部９における強化繊維１０の配設密度は特
に限定されないが、３０〜７０ vol％程度、特に、４５
〜６０ vol％程度とするのが好ましい。The arrangement density of the reinforcing fibers 10 in the primary-direction strength support portions 7a and 7b and the secondary-direction strength support portion 9 is not particularly limited, but is about 30 to 70 vol%, and particularly 45.
It is preferably about 60 to 60 vol%.
【００５９】なお、一次方向強度支持部７ａ、７ｂおよ
び二次方向強度支持部９における強化繊維１０の形状、
素材、直径、配設密度等は、それぞれ同一でも、異なっ
ていてもよい。The shape of the reinforcing fibers 10 in the primary strength support parts 7a, 7b and the secondary strength support part 9
The material, diameter, arrangement density, etc. may be the same or different.
【００６０】一次方向強度支持部７ａ、７ｂおよび二次
方向強度支持部９における生体用樹脂材料８とは、生体
内において安定であり、すなわち分解、変質、劣化等を
生じず、かつ生体にとって有害な溶出物を生じることが
ない樹脂材料であり、例えば、ポリエーテルケトン、ポ
リエーテルエーテルケトン、ポリアリルエーテルケトン
のようなケトン系樹脂や、ポリフェニレンサルフィド、
ポリサルフォン等の熱可塑性樹脂が挙げられる。本発明
では、これらのうちの１種または２種以上を任意に組み
合せて用いることができる。The biomaterial 8 in the primary strength support portions 7a and 7b and the secondary strength support portion 9 is stable in the living body, that is, it does not decompose, deteriorate, or deteriorate and is harmful to the living body. It is a resin material that does not generate various eluates, for example, a ketone resin such as polyetherketone, polyetheretherketone, polyallyletherketone, polyphenylene sulfide,
A thermoplastic resin such as polysulfone may be used. In the present invention, one kind or two kinds or more of these can be arbitrarily combined and used.
【００６１】ポリエーテルケトンとしては、例えば、下
記化１に示すようなものが挙げられる。Examples of the polyether ketone include those represented by the following chemical formula 1.
【００６２】[0062]
【化１】 [Chemical 1]
【００６３】ポリエーテルエーテルケトンとしては、例
えば、下記化２、化３に示すようなものが挙げられる。Examples of the polyether ether ketone include those represented by the following chemical formulas 2 and 3.
【００６４】[0064]
【化２】 [Chemical 2]
【００６５】[0065]
【化３】 [Chemical 3]
【００６６】ポリフェニレンサルフィドとしては、例え
ば、下記化４に示すようなものが挙げられる。Examples of the polyphenylene sulfide include those shown in the following chemical formula 4.
【００６７】[0067]
【化４】 [Chemical 4]
【００６８】ポリサルフォンとしては、例えば、下記化
５に示すようなものが挙げられる。Examples of polysulfones include those represented by the following chemical formula 5.
【００６９】[0069]
【化５】 [Chemical 5]
【００７０】このような生体用樹脂材料８中には、例え
ば、安定剤、強化材のような各種添加剤が添加されてい
てもよい。Various additives such as stabilizers and reinforcing materials may be added to the biomedical resin material 8.
【００７１】なお、一次方向強度支持部７ａ、７ｂおよ
び二次方向強度支持部９における生体用樹脂材料の組成
は、それぞれ同一でも、異なっていてもよい。The composition of the biomedical resin material in the primary strength support parts 7a and 7b and the secondary strength support part 9 may be the same or different.
【００７２】図１〜図４に示すように、二次方向強度支
持部９の外周面は、被覆層１１により被覆されている。
このような被覆層１１を設けることにより、強化繊維の
離脱を防止すると共に、人工関節１の形状を容易に整え
ることができる。As shown in FIGS. 1 to 4, the outer peripheral surface of the secondary strength support portion 9 is covered with a coating layer 11.
By providing such a coating layer 11, it is possible to prevent the reinforcing fibers from coming off and to easily adjust the shape of the artificial joint 1.
【００７３】この被覆層１１は、前記生体用樹脂材料と
同様の材料で構成されているのが好ましい。また、二次
方向強度支持部９との接着性を良好とするために、二次
方向強度支持部９に用いられる生体用樹脂材料と同一ま
たは類似（同様の性質を有する）のものを用いるのが好
ましい。The coating layer 11 is preferably made of the same material as the biomedical resin material. Further, in order to improve the adhesiveness to the secondary direction strength support portion 9, the same or similar (having similar properties) as the biomedical resin material used for the secondary direction strength support portion 9 is used. Is preferred.
【００７４】被覆層１１の厚さ、特に、ステム基部５に
おける被覆層１１厚さは、平均０．２〜３．０mm程度が
好ましく、平均０．５〜２．０mm程度がより好ましい。
この厚さが０．２mm未満では、上述したような被覆層の
機能が十分に発揮されず、また、被覆層１１が剥離し易
くなり、３．０mmを超えると、曲げおよびねじれに対す
る強度が不足することがあるからである。The thickness of the coating layer 11, particularly the thickness of the coating layer 11 on the stem base 5, is preferably about 0.2 to 3.0 mm on average, and more preferably about 0.5 to 2.0 mm on average.
When the thickness is less than 0.2 mm, the function of the coating layer as described above is not sufficiently exhibited, and the coating layer 11 is easily peeled off, and when it exceeds 3.0 mm, the strength against bending and twisting is insufficient. Because there is something to do.
【００７５】なお、本発明では、このような被覆層１１
は、必ずしも設けなくてもよい。In the present invention, such a coating layer 11
Need not necessarily be provided.
【００７６】以上のような人工関節１は、例えば、次の
ようにして製造される。The artificial joint 1 as described above is manufactured, for example, as follows.
【００７７】まず、リボン状（薄板状）に成形された繊
維強化樹脂を所定数重ね、樹脂の溶融温度以上の温度
（例えば３６０〜４００℃）で加圧成形し、一次方向強
度支持部７ａおよび７ｂをそれぞれ製造する。First, a predetermined number of ribbon-shaped (thin plate-shaped) fiber-reinforced resins are stacked and pressure-molded at a temperature above the melting temperature of the resin (for example, 360 to 400 ° C.), and the primary-direction strength support portions 7a and 7b are manufactured respectively.
【００７８】得ようとする中間部８と同形の中子（石
膏）を作製し、この中子を介して前記一次方向強度支持
部７ａおよび７ｂを接合する。この接合は、例えば、再
度、樹脂の溶融温度以上の温度で加圧成形することによ
り行なう。A core (gypsum) having the same shape as that of the intermediate portion 8 to be obtained is produced, and the primary direction strength support portions 7a and 7b are joined via this core. This joining is performed, for example, by performing pressure molding again at a temperature equal to or higher than the melting temperature of the resin.
【００７９】次に、薬品での洗浄により中子を溶解、除
去する。これにより、一次方向強度支持部７ａ、７ｂ間
に空隙による中間部８が形成される。Next, the core is dissolved and removed by washing with a chemical. As a result, an intermediate portion 8 is formed by a gap between the primary strength support portions 7a and 7b.
【００８０】このようにして得られた一次方向強度支持
部７ａ、７ｂの外周に、例えば前述したフィラメントワ
インディング法またはその改良法により二次方向強度支
持部９を形成する。このとき、吹き付ける熱風の温度
は、例えば４５０〜５００℃とされる。The secondary strength support 9 is formed on the outer periphery of the primary strength support 7a, 7b thus obtained by, for example, the above-mentioned filament winding method or its modification. At this time, the temperature of the hot air blown is, for example, 450 to 500 ° C.
【００８１】なお、二次方向強度支持部９を形成する際
に、前記薬品を中間部８へ注入、排出するための孔は封
止され、中間部８は閉空間となる。When forming the secondary strength support portion 9, the holes for injecting and discharging the chemical into the intermediate portion 8 are sealed, and the intermediate portion 8 becomes a closed space.
【００８２】次に、必要に応じ、被覆層１１を形成す
る。上記のようにして得られた一次方向強度支持部７
ａ、７ｂおよび二次方向強度支持部９を射出成形金型内
に固定し、この金型内に被覆層１１を構成する溶融樹脂
を注入、固化して、インサート成形を行なう。これによ
り、二次方向強度支持部９の外周に被覆層１１が形成さ
れたネック部３およびステム部４が得られる。Next, the coating layer 11 is formed, if necessary. Primary direction strength support portion 7 obtained as described above
The a and 7b and the secondary direction strength support portion 9 are fixed in an injection molding die, and the molten resin forming the coating layer 11 is injected into this die and solidified to perform insert molding. Thereby, the neck portion 3 and the stem portion 4 in which the coating layer 11 is formed on the outer periphery of the secondary strength support portion 9 are obtained.
【００８３】なお、被覆層１１の形成は、コーティング
やディッピングにより行なってもよい。The coating layer 11 may be formed by coating or dipping.
【００８４】このようにして得られたネック部３および
ステム部４のネック部３に、別途製造された金属製また
はセラミックス製の頭部２を連結して本発明の人工関節
１とする。A separately manufactured metal or ceramic head 2 is connected to the neck 3 and the neck 3 of the stem 4 obtained as described above to obtain the artificial joint 1 of the present invention.
【００８５】以上、本発明の人工関節を図示の構成例に
基いて説明したが、本発明はこれらに限定されるもので
はない。Although the artificial joint of the present invention has been described above based on the configuration example shown in the drawings, the present invention is not limited thereto.
【００８６】なお、本発明の人工関節は、上記人工骨頭
に限らず、例えば、人工膝関節、人工肩関節、人工肘関
節、あるいは人工股関節や寛骨に埋入される臼蓋カップ
の一部に適用することもできる。The artificial joint of the present invention is not limited to the above artificial bone head, but may be, for example, an artificial knee joint, an artificial shoulder joint, an artificial elbow joint, or a part of an acetabular cup embedded in an artificial hip joint or hip bone. Can also be applied to.
【００８７】[0087]
【実施例】以下、本発明の具体的実施例について説明す
る。EXAMPLES Specific examples of the present invention will be described below.
【００８８】（実施例１）以下の方法により、股関節用
人工関節（人工骨頭）を製造した。Example 1 An artificial joint for hip joint (artificial head) was manufactured by the following method.
【００８９】［１］ネック部およびステム部の製造 一次方向強度支持部、二次方向強度支持部共に、炭素繊
維を含む上記化３に示すポリエーテルエーテルケトン
（化成ファイバーライト社製、以下、ＣＦＲＰという）
を用いた。[1] Manufacture of Neck Part and Stem Part Both the primary direction strength support part and the secondary direction strength support part contain carbon fibers and are represented by the chemical formula 3 polyetheretherketone (Chemical Fiberlight Co., CFRP, hereinafter. Say)
Was used.
【００９０】まず、ＣＦＲＰのリボンを積み重ね、温度
３８０℃でプレス加工を施して、一対の一次方向強度支
持部を作製した。First, CFRP ribbons were stacked and pressed at a temperature of 380 ° C. to prepare a pair of primary direction strength supporting portions.
【００９１】一方、得ようとする中間部と同形の中子を
石膏により作製し、この中子を介して前記両一次方向強
度支持部を突き合わせ、再び、温度３８０℃でプレス加
工を施して、これらを接合した。一次方向強度支持部の
繊維強化方向は、ネック部およびステム部の長手方向
（軸方向）とした。On the other hand, a core having the same shape as the intermediate part to be obtained is made of gypsum, the both primary direction strength supporting parts are butted against each other through this core, and press working is again performed at a temperature of 380 ° C. These were joined. The fiber reinforcement direction of the primary direction strength support part was the longitudinal direction (axial direction) of the neck part and the stem part.
【００９２】次に、１Ｎの塩酸にて洗浄し、石膏の中子
を溶解、除去して、空隙（中間部）を形成した。Next, the gypsum core was dissolved and removed by washing with 1N hydrochloric acid to form voids (intermediate part).
【００９３】その後、接合された両一次方向強度支持部
の外周に、４８０℃の熱風を吹き付けつつ、ＣＦＲＰの
リボンを、その繊維強化方向が一次方向強度支持部のそ
れに対し９０±１０°となるように巻き付け、冷却して
二次方向強度支持部を作製した。Thereafter, while blowing hot air at 480 ° C. onto the outer circumferences of the joined primary strength supporting portions, the CFRP ribbon has a fiber reinforced direction of 90 ± 10 ° with respect to that of the primary strength supporting portions. Thus, the secondary direction strength support part was produced by winding and cooling.
【００９４】次に、得られた一次方向強度支持部および
二次方向強度支持部を射出成形金型内に固定し、この金
型内に上記化３に示すポリエーテルエーテルケトンのを
注入、固化して、インサート成形を行い、二次方向強度
支持部の外周に被覆層１１が形成されたネック部および
ステム部の一体性形物を得た。Next, the primary direction strength supporting portion and the secondary direction strength supporting portion thus obtained were fixed in an injection molding die, and the polyether ether ketone shown in Chemical formula 3 was injected into the die and solidified. Then, insert molding was performed to obtain an integral shape of the neck portion and the stem portion in which the coating layer 11 was formed on the outer periphery of the secondary strength support portion.
【００９５】［２］頭部の製造 球状アルミナにより、ほぼ球形のアルミナ製頭部（骨
頭）を製造した。なお、この頭部には、テーパ嵌合用の
嵌合孔をも形成した。[2] Manufacture of Head A spherical alumina head (bone head) was manufactured from spherical alumina. A fitting hole for taper fitting was also formed in this head.
【００９６】［３］組み立て 前記［１］で得られた一体成形物のネック部を頭部の嵌
合孔にテーパ嵌合し、その後、人工関節の表面を研磨し
て、図１〜図４に示す本発明の人工関節を得た。この人
工関節の寸法等は、次の通りである。[3] Assembly The neck portion of the integrally molded product obtained in the above [1] is taper-fitted into the fitting hole of the head portion, and then the surface of the artificial joint is ground to obtain the structure shown in FIGS. The artificial joint of the present invention shown in FIG. The dimensions and the like of this artificial joint are as follows.
【００９７】頭部直径：３８mm ネック部全長：３５mm ネック部直径：１５mm ステム部全長：１２０mm ステム基部の長径：４０mm ステム基部の短径：２５mm ステム先端部の外径：１２mm 空隙の全長：４０mm 空隙の面積比：３０％ 二次方向強度支持部の厚さ：平均１．０mm 被覆層の厚さ：平均１．０mmHead diameter: 38 mm Neck length: 35 mm Neck diameter: 15 mm Stem length: 120 mm Stem base major diameter: 40 mm Stem base minor diameter: 25 mm Stem tip outer diameter: 12 mm Gap total length: 40 mm Gap Area ratio: 30% Secondary direction strength Thickness of supporting part: 1.0 mm average Thickness of coating layer: 1.0 mm average
【００９８】（実施例２）一次方向強度支持部および二
次方向強度支持部における強化繊維として、ガラス繊維
を用い、化３に示すポリエテールエーテルケトンの溶融
槽より引き抜き成形を行ない、切断することにより一対
の一次方向強度支持部を作製した以外は、実施例１と同
様にして、図１〜図４に示す本発明の人工関節を製造し
た。(Example 2) Glass fiber was used as the reinforcing fiber in the primary direction strength support portion and the secondary direction strength support portion, and the fiber was drawn from the melting tank of the polyether ether ketone shown in Chemical formula 3 and cut. The artificial joint of the present invention shown in FIGS. 1 to 4 was manufactured in the same manner as in Example 1 except that a pair of primary direction strength support parts were manufactured by the above.
【００９９】この人工関節の寸法は、空隙の面積比：４
０％、二次方向強度支持部の厚さ：平均１．０mm、被覆
層の厚さ：平均１．０mmとした以外は、前記実施例１と
同様である。The size of this artificial joint is the area ratio of voids: 4
Same as Example 1 except that 0%, secondary direction strength support portion thickness: average 1.0 mm, coating layer thickness: average 1.0 mm.
【０１００】（実施例３）一次方向強度支持部および二
次方向強度支持部における強化繊維として、アラミド繊
維を用いた以外は、実施例２と同様にして、図１〜図４
に示す本発明の人工関節を製造した。Example 3 FIGS. 1 to 4 were carried out in the same manner as in Example 2 except that aramid fiber was used as the reinforcing fiber in the primary direction strength support portion and the secondary direction strength support portion.
The artificial joint of the present invention shown in FIG.
【０１０１】この人工関節の寸法は、空隙の面積比：２
５％、二次方向強度支持部の厚さ：平均１．５mm、被覆
層の厚さ：平均０．８mmとした以外は、前記実施例１と
同様である。The size of this artificial joint is the area ratio of voids: 2
Same as Example 1 except that the thickness of the secondary strength support portion was 5% on average, and the thickness of the coating layer was 0.8 mm on average.
【０１０２】（実施例４）一次方向強度支持部および二
次方向強度支持部における強化繊維として、Ｔｉ−５０
％Ｎｉ合金繊維（細線）を用いた以外は、実施例１と同
様にして、図１〜図４に示す本発明の人工関節を製造し
た。(Example 4) Ti-50 was used as a reinforcing fiber in the primary direction strength support portion and the secondary direction strength support portion.
An artificial joint of the present invention shown in FIGS. 1 to 4 was manufactured in the same manner as in Example 1 except that% Ni alloy fiber (thin wire) was used.
【０１０３】この人工関節の寸法は、空隙の面積比：４
０％、二次方向強度支持部の厚さ：平均１．０mm、被覆
層の厚さ：平均１．５mmとした以外は、前記実施例１と
同様である。The size of this artificial joint is the area ratio of voids: 4
Same as Example 1 except that 0%, thickness of secondary strength support part: average 1.0 mm, thickness of coating layer: average 1.5 mm.
【０１０４】（実施例５）一次方向強度支持部、二次方
向強度支持部および被覆層における生体用樹脂材料とし
て、上記化４に示すポリフェニレンサルフィド（フィリ
ップス社製）を用い、プレス加工時の温度を２９０〜３
２０℃、吹き付ける熱風の温度を３８０℃とした以外
は、実施例１と同様にして、図１〜図４に示す本発明の
人工関節を製造した。この人工関節の寸法は、前記実施
例１と同様である。Example 5 Polyphenylene sulfide (manufactured by Philips) shown in the chemical formula 4 above was used as a biomedical resin material in the primary strength support, secondary strength support and coating layer, and was used for press working. Temperature 290-3
An artificial joint of the present invention shown in FIGS. 1 to 4 was produced in the same manner as in Example 1 except that the temperature of hot air to be blown was 20 ° C. and the temperature of hot air to be blown was 380 ° C. The dimensions of this artificial joint are the same as those in the first embodiment.
【０１０５】（比較例）上記ＣＦＲＰ製の中実棒状（直
径１０mm）の一次方向強度支持部を作製し、その外周
に、実施例１と同様にして二次方向強度支持部を形成
し、さらにその外周に、インサート成形により上記化３
に示すポリエーテルエーテルケトンによる肉付けを行な
って、実施例１と同様の輪郭形状の人工関節を製造し
た。この人工関節において、肉付けされたポリエーテル
エーテルケトンのステム基部における厚さは、平均５mm
であった。(Comparative Example) A solid rod-shaped (diameter 10 mm) primary strength support portion made of CFRP was prepared, and a secondary strength support portion was formed on the outer periphery thereof in the same manner as in Example 1, and On the outer circumference, the above-mentioned chemical formula 3
By fleshing with the polyether ether ketone shown in, an artificial joint having the same contour shape as in Example 1 was manufactured. In this artificial joint, the thickness of the fleshed polyetheretherketone at the stem base is 5 mm on average.
Met.
【０１０６】［実験１］上記実施例１〜５および比較例
の各人工関節を、頭部を上方にして、頭部の中心とステ
ム部の先端とを結ぶ線（ネック部の軸線と約２５°傾
斜）が鉛直方向となるように固定し、頭部に対し、鉛直
方向下方に５００kgf の荷重を負荷し、荷重負荷による
頭部の変位量を測定した。[Experiment 1] In each of the artificial joints of Examples 1 to 5 and Comparative Example, with the head facing upward, a line connecting the center of the head and the tip of the stem portion (the axis of the neck portion and about 25 mm). It was fixed so that the inclination angle was in the vertical direction, and a load of 500 kgf was applied vertically downward to the head, and the amount of displacement of the head due to the load was measured.
【０１０７】その結果は、比較例の人工関節における変
位量を１としたとき、本発明の実施例１〜５における変
位量は、それぞれ、０．８、０．９、０．８、０．８で
あった。このことから、実施例１〜５の本発明の人工関
節は、比較例に比べ、圧縮および曲げに対する強度が高
く、また曲げ弾性率は生体骨のそれに近く、生体骨への
応力伝達がより広い領域に対し均一に行なわれることが
確認された。As a result, when the displacement amount in the artificial joint of the comparative example is 1, the displacement amounts in Examples 1 to 5 of the present invention are 0.8, 0.9, 0.8, 0. It was 8. From this, the artificial joints of the present invention of Examples 1 to 5 have higher strength against compression and bending than the comparative examples, and the bending elastic modulus is close to that of the living bone, and the stress transmission to the living bone is wider. It was confirmed that the process was performed uniformly on the area.
【０１０８】［実験２］上記実施例１〜５および比較例
の各人工関節を、頭部を上方にして、頭部とステム部の
先端との２箇所で支持し、ステム部の先端を固定した状
態で、頭部に対し、ステム部外周方向に２０kg・cm のト
ルクを与え、このトルクによる頭部の回転角度を測定し
た。[Experiment 2] Each of the artificial joints of Examples 1 to 5 and Comparative Example was supported with the head upward and at two points, the head and the tip of the stem, and the tip of the stem was fixed. In this state, a torque of 20 kg · cm 2 was applied to the head in the outer peripheral direction of the stem, and the rotation angle of the head due to this torque was measured.
【０１０９】その結果は、比較例の人工関節における回
転角度を１としたとき、本発明の実施例１〜５における
回転角度は、それぞれ、０．５、０．６、０．６、０．
７であった。このことから、実施例１〜５の本発明の人
工関節は、比較例に比べ、ねじれに対する強度が高いこ
とが確認された。As a result, when the rotation angle in the artificial joint of the comparative example is 1, the rotation angles in Examples 1 to 5 of the present invention are 0.5, 0.6, 0.6, 0.
It was 7. From this, it was confirmed that the artificial joints of the present invention of Examples 1 to 5 have higher strength against twisting than the comparative examples.
【０１１０】[0110]
【発明の効果】以上述べたように、本発明の人工関節に
よれば、引っ張り、圧縮、曲げ、ねじれに対し、十分な
強度が得られ、耐久性も格段に向上する。As described above, according to the artificial joint of the present invention, sufficient strength can be obtained against pulling, compressing, bending and twisting, and the durability can be remarkably improved.
【０１１１】また、ステム部の弾性率の適正化が図れ、
荷重が広範囲に均等に加わるため、荷重の集中による骨
の破壊や、荷重がかからないことによる骨組織の吸収が
抑制され、骨髄腔への埋入、固定をより強固で確実なも
のとすることができる。Further, the elastic modulus of the stem portion can be optimized,
Since the load is evenly applied over a wide range, bone destruction due to concentration of load and absorption of bone tissue due to no load being applied are suppressed, and implantation and fixation in the bone marrow cavity can be made stronger and more reliable. it can.
【０１１２】さらに、有毒物質の溶出もなく、生体への
安全性が高い。Further, there is no elution of toxic substances, and the safety to the living body is high.
【０１１３】また、人工関節の軽量化により、患者の負
担を軽減することができる。Further, the weight of the artificial joint can be reduced, so that the burden on the patient can be reduced.
【図１】本発明の人工関節の構成例を示す正面図であ
る。FIG. 1 is a front view showing a configuration example of an artificial joint of the present invention.
【図２】図１中のＡ−Ａ線での断面図である。FIG. 2 is a sectional view taken along the line AA in FIG.
【図３】図１中のＢ−Ｂ線での断面図である。FIG. 3 is a cross-sectional view taken along the line BB in FIG.
【図４】図１中のＣ−Ｃ線での断面図である。FIG. 4 is a cross-sectional view taken along the line CC in FIG.
【図５】二次方向強度支持部の構成例を示す一部切り欠
き正面図である。FIG. 5 is a partially cutaway front view showing a configuration example of a secondary direction strength support portion.
１ 人工関節 ２ 頭部 ３ ネック部 ４ ステム部 ５ ステム基部 ６ ステム先端部 ７ａ、７ｂ 一次方向強度支持部 ８ 中間部 ９ 二次方向強度支持部 １０ 強化繊維 １１ 被覆層 1 Artificial Joint 2 Head 3 Neck 4 Stem 5 Stem Base 6 Stem Tip 7a, 7b Primary Strength Support 8 Intermediate 9 Secondary Strength Support 10 Reinforcing Fiber 11 Coating Layer
───────────────────────────────────────────────────── フロントページの続き (72)発明者 松永 昇 東京都八王子市狭間町1463番地 蛇の目ミ シン工業株式会社内 (72)発明者 畔柳 和好 東京都八王子市狭間町1463番地 蛇の目ミ シン工業株式会社内 (72)発明者 曽我石 一郎 東京都八王子市狭間町1463番地 蛇の目ミ シン工業株式会社内 ─────────────────────────────────────────────────── ─── Continuation of the front page (72) Inventor Noboru Matsunaga 1463 Asama-cho, Hachioji-shi, Tokyo Within Jernome Machine Industry Co., Ltd. In-house (72) Inventor Ichiro Soga 1463, Sakuma-cho, Hachioji, Tokyo
Claims (5)
続くステム部とで構成された人工関節において、 前記ステム部は、ステム基部とステム先端部とで構成さ
れ、少なくとも前記ステム基部においては、中間部を介
して一対の一次方向強度支持部が対向配置され、かつ両
一次方向強度支持部の外周に二次方向強度支持部が配置
されており、 前記一次方向強度支持部は、生体用樹脂材料に強化繊維
が埋入され、該強化繊維により、前記ステム部の長手方
向に強化されたものであり、 前記二次方向強度支持部は、生体用樹脂材料に強化繊維
が埋入され、該強化繊維により、前記ステム部の長手方
向に対し４５〜１３５°の方向に強化されたものである
ことを特徴とする人工関節。1. An artificial joint comprising a head portion, a neck portion following the head portion, and a stem portion following the head portion, wherein the stem portion includes a stem base portion and a stem tip portion, and at least the stem base portion. In, the pair of primary direction strength support portions are arranged to face each other via the intermediate portion, and the secondary direction strength support portions are arranged on the outer periphery of both primary direction strength support portions, and the primary direction strength support portion is, A reinforcing fiber is embedded in a biomedical resin material, and the reinforcing fiber is reinforced in the longitudinal direction of the stem portion, and the secondary direction strength supporting portion is such that the reinforcing fiber is embedded in the biomedical resin material. The artificial joint is reinforced by the reinforcing fibers in a direction of 45 to 135 ° with respect to the longitudinal direction of the stem portion.
の人工関節。2. The artificial joint according to claim 1, wherein the intermediate portion is a void.
前記二次方向強度支持部における強化繊維は、炭素繊
維、ガラス繊維、アラミド繊維、金属繊維よりなる群か
ら選ばれた少なくとも一種である請求項１または２に記
載の人工関節。3. The reinforcing fiber in the primary direction strength support portion and / or the secondary direction strength support portion is at least one selected from the group consisting of carbon fiber, glass fiber, aramid fiber and metal fiber. The artificial joint according to 1 or 2.
前記二次方向強度支持部における生体用樹脂材料は、ポ
リエーテルケトン、ポリエーテルエーテルケトン、ポリ
アリルエーテルケトン、ポリフェニレンサルフィド、ポ
リサルフォンよりなる群から選ばれた少なくとも一種で
ある請求項１ないし３のいずれかに記載の人工関節。4. The biomedical resin material in the primary direction strength support part and / or the secondary direction strength support part comprises a group consisting of polyetherketone, polyetheretherketone, polyallyletherketone, polyphenylene sulfide, and polysulfone. The artificial joint according to any one of claims 1 to 3, which is at least one selected from the group consisting of:
を有する請求項１ないし４のいずれかに記載の人工関
節。5. The artificial joint according to claim 1, further comprising a coating layer on the outer periphery of the secondary strength support portion.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP27847191A JPH0592019A (en) | 1991-09-30 | 1991-09-30 | Artificial joint |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP27847191A JPH0592019A (en) | 1991-09-30 | 1991-09-30 | Artificial joint |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH0592019A true JPH0592019A (en) | 1993-04-16 |
Family
ID=17597798
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP27847191A Pending JPH0592019A (en) | 1991-09-30 | 1991-09-30 | Artificial joint |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0592019A (en) |
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH06327705A (en) * | 1993-05-26 | 1994-11-29 | Kobe Steel Ltd | Artificial joint |
| WO2005034818A1 (en) * | 2003-10-09 | 2005-04-21 | B.I.Tec Ltd. | Cementless artificial joint system using composite material |
| JP2008054788A (en) * | 2006-08-30 | 2008-03-13 | Bi Tec:Kk | Socket made of composite material for artificial hip joint and its manufacturing method |
| JP2012515038A (en) * | 2009-01-16 | 2012-07-05 | カーボフィックス オーソピーディックス リミテッド | Composite bone implant |
| US9370388B2 (en) | 2010-06-07 | 2016-06-21 | Carbofix Orthopedics Ltd. | Composite material bone implant |
| US9526549B2 (en) | 2012-01-16 | 2016-12-27 | Carbofix Orthopedics Ltd. | Bone screw with insert |
| US10154867B2 (en) | 2010-06-07 | 2018-12-18 | Carbofix In Orthopedics Llc | Multi-layer composite material bone screw |
| US10617458B2 (en) | 2015-12-23 | 2020-04-14 | Carbofix In Orthopedics Llc | Multi-layer composite material bone screw |
-
1991
- 1991-09-30 JP JP27847191A patent/JPH0592019A/en active Pending
Cited By (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH06327705A (en) * | 1993-05-26 | 1994-11-29 | Kobe Steel Ltd | Artificial joint |
| WO2005034818A1 (en) * | 2003-10-09 | 2005-04-21 | B.I.Tec Ltd. | Cementless artificial joint system using composite material |
| GB2423025A (en) * | 2003-10-09 | 2006-08-16 | B I Tec Ltd | Cementless artificial joint system using composite material |
| GB2423025B (en) * | 2003-10-09 | 2007-10-24 | B I Tec Ltd | Cement-less type artificial joint stem with the use of composite material |
| JP2008054788A (en) * | 2006-08-30 | 2008-03-13 | Bi Tec:Kk | Socket made of composite material for artificial hip joint and its manufacturing method |
| US10028777B2 (en) | 2009-01-16 | 2018-07-24 | Carbofix Orthopedics Ltd. | Composite material bone implant |
| JP2012515038A (en) * | 2009-01-16 | 2012-07-05 | カーボフィックス オーソピーディックス リミテッド | Composite bone implant |
| US9370388B2 (en) | 2010-06-07 | 2016-06-21 | Carbofix Orthopedics Ltd. | Composite material bone implant |
| US9974586B2 (en) | 2010-06-07 | 2018-05-22 | Carbofix Orthopedics Ltd. | Composite material bone implant |
| US10154867B2 (en) | 2010-06-07 | 2018-12-18 | Carbofix In Orthopedics Llc | Multi-layer composite material bone screw |
| US10849668B2 (en) | 2010-06-07 | 2020-12-01 | Carbofix Orthopedics Ltd. | Composite material bone implant |
| US9526549B2 (en) | 2012-01-16 | 2016-12-27 | Carbofix Orthopedics Ltd. | Bone screw with insert |
| US10617458B2 (en) | 2015-12-23 | 2020-04-14 | Carbofix In Orthopedics Llc | Multi-layer composite material bone screw |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| EP0532585B1 (en) | Metal/composite hybrid orthopedic implants | |
| US4750905A (en) | Beam construction and method | |
| US4892552A (en) | Orthopedic device | |
| US5397365A (en) | Composite orthopedic implant with modulus variations | |
| JP3901717B2 (en) | Cementless artificial joint stem using composite material | |
| EP0337757B1 (en) | Endoprostheses with bone resorption preventing means | |
| US4738681A (en) | Femoral-joint prosthetic device | |
| JP2843676B2 (en) | Orthopedic composite implant | |
| US4986834A (en) | Load sharing femoral hip implant | |
| US4895573A (en) | Femoral-joint prosthetic device | |
| EP0297789A1 (en) | Method of making a prosthetic component and component made according to the method | |
| JPH0592019A (en) | Artificial joint | |
| Shen et al. | Mechanical failure of hydroxyapatite-and polysulfone-coated titanium rods in a weight-bearing canine model | |
| JPH05137739A (en) | Artificial joint | |
| JPH0592020A (en) | Artificial joint | |
| WO1993013733A1 (en) | Composite orthopedic implant with modulus variations | |
| JPH02144055A (en) | Artificial joint | |
| JPH0592018A (en) | Artificial joint | |
| JP2005278875A (en) | Artificial bone and artificial joint | |
| CA2365414C (en) | Metal/composite hybrid orthopaedic implants | |
| CA2485888C (en) | Metal/composite hybrid orthopaedic implants |