WO2009147819A1 - 骨修復材料及びその製造方法 - Google Patents
骨修復材料及びその製造方法 Download PDFInfo
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- WO2009147819A1 WO2009147819A1 PCT/JP2009/002426 JP2009002426W WO2009147819A1 WO 2009147819 A1 WO2009147819 A1 WO 2009147819A1 JP 2009002426 W JP2009002426 W JP 2009002426W WO 2009147819 A1 WO2009147819 A1 WO 2009147819A1
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- aqueous solution
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/02—Inorganic materials
- A61L27/04—Metals or alloys
- A61L27/06—Titanium or titanium alloys
-
- 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
- A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/30—Inorganic materials
-
- 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
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00023—Titanium or titanium-based alloys, e.g. Ti-Ni alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/02—Materials or treatment for tissue regeneration for reconstruction of bones; weight-bearing implants
Definitions
- the present invention relates to a bone repair material and a manufacturing method thereof.
- This bone repair material can be suitably used for bone repair in a portion to which a large load is applied such as a femur, a hip joint, a spine, and a tooth root.
- Titanium or its alloy with an apatite layer formed on its surface has great fracture toughness and is bonded to living bone through apatite in vivo, so it is expected as a bone repair material in areas where large loads are applied. Yes. Therefore, various methods for forming an apatite layer on the surface of a substrate made of titanium or an alloy thereof have been studied. Among these, those obtained by immersing an alkali-treated base material in an aqueous solution having a saturated concentration of apatite or more to precipitate apatite are likely to crack in the apatite during drying.
- Patent Document 1 and Non-Patent Document 1 lose their apatite forming ability when exposed to high temperature and high humidity for a long time as an accelerated test assuming long-term storage. Therefore, it is not possible to store inventory in preparation for repair surgery.
- the materials obtained by the methods described in Patent Documents 2-4 and 6-7 and Non-Patent Document 2-3 have low scratch resistance, and the titanate layer easily peels off when embedded in the body.
- the materials obtained by the methods described in Patent Documents 5 and 8 and Non-Patent Document 5 are inferior in apatite-forming ability, and it takes 10 days to form apatite on the entire surface.
- an object of the present invention is to provide a bone repair material having excellent apatite forming ability and storage stability and having high scratch resistance.
- the bone repair material is A substrate made of titanium or a titanium alloy; A titanate layer formed on a substrate and containing calcium, the concentration of which decreases as it goes from the surface toward the inside,
- a stylus with a spring constant of 200 g / mm is given an amplitude of 100 ⁇ m and a load of 100 mN / min is applied, when the stylus is moved at a speed of 10 mm / sec, it exhibits a scratch resistance of 20 mN or more, and is in vivo or simulated. It has the ability to form apatite on the entire surface within 3 days in body fluid.
- the calcium concentration in the titanate layer decreases as it goes inward. Accordingly, the titanium concentration increases as it goes inward, and the titanate layer is strongly bonded to the base material and exhibits the above-mentioned high scratch resistance. Further, since the portion close to the surface is rich in calcium and activated, it has excellent apatite forming ability.
- Suitable methods for producing the bone repair material of this invention include: A step of immersing a base material made of titanium or a titanium alloy in an alkaline first aqueous solution containing at least one cation of sodium ions and potassium ions without containing calcium ions; Immersing in a second aqueous solution containing calcium ions without containing phosphate ions; Heating in a dry atmosphere; And a step of treating with warm water or steam at 60 ° C. or higher.
- the base material and the aqueous solution react to easily form a sodium hydrogen titanate or potassium hydrogen titanate layer on the surface of the base material.
- This surface layer is known to have a gradient structure in which sodium concentration or potassium concentration decreases from the surface toward the inside (Kim et al., J. Biomed. Mater. Res., Vol. 45, p100-109, (1999)).
- sodium ions or potassium ions in the surface layer are exchanged with calcium ions in the aqueous solution.
- the said titanate layer which has the gradient composition which contains calcium in high concentration is formed on a base material by immersing a base material in two different types of aqueous solution in steps. By heating this in a dry atmosphere, it is dehydrated to form a mechanically and chemically stable anhydrous titanate layer, and the scratch resistance is remarkably improved. Thereafter, the surface is activated to such a degree that the surface exhibits predetermined apatite-forming ability by treatment with warm water or steam of 60 ° C. or higher. Its ability to form is as high as 3 days to form apatite on the entire surface, and it is maintained even after long-term storage.
- the bone repair material obtained by the manufacturing method of the present invention has excellent apatite forming ability and high scratch resistance, when it is embedded in a portion where a large load is applied in vivo, The bone defect can be repaired by bonding. Moreover, since it is excellent in preservability, stock can be used in the case of surgery.
- the titanate layer preferably has a calcium concentration of 0.1 to 20 atomic% in the range of a depth of at least 1 ⁇ m from the surface.
- the titanate layer preferably has a thickness of 0.1 to 10 ⁇ m. When the thickness is less than 0.1 ⁇ m, the calcium component which is the core of the apatite is too scarce on the surface and it is difficult to form apatite. When it exceeds 10 ⁇ m, the titanate layer is easily peeled off from the substrate.
- the preferred alkali concentration of the first aqueous solution is 0.1 to 20M
- the preferred calcium ion concentration of the second aqueous solution is 0.1 to 1,000 mM.
- the preferred soaking temperature and time are 5 to 99 ° C., 0 .5 to 48 hours. This is because if any of these is less than the lower limit, a titanate layer having the preferred thickness or gradient composition is difficult to form, and if the upper limit is exceeded, the titanate layer becomes too thick and easily peels from the substrate. .
- the second aqueous solution is preferably prepared by dissolving one or more salts selected from calcium chloride, calcium nitrate, calcium acetate, and calcium hydroxide in water.
- the heating temperature after the aqueous solution treatment is preferably 400 to 800 ° C. When the temperature is lower than 400 ° C., it is difficult to improve the mechanical strength and chemical stability of the titanate layer.
- the preferred temperature for the hot water treatment or the steam treatment is 60 to 99 ° C. or 100 to 180 ° C., respectively, and the preferred treatment time is 0.1 to 48 hours.
- the titanium metal plate was heated from normal temperature to 600 ° C. at a rate of 5 ° C./min in an electric furnace, held at 600 ° C. for 1 hour, and allowed to cool in the furnace (hereinafter referred to as “heat treatment”). ). Thereafter, the titanium metal plate was immersed in 10 ml of ultrapure water at 60 ° C. for 24 hours (hereinafter referred to as “warm water treatment”) and washed with ultrapure water for 30 seconds to produce a sample.
- heat treatment 10 ml of ultrapure water at 60 ° C. for 24 hours
- Example 1 a sample was produced under the same conditions as in Example 1 except that the temperature of the hot water in the hot water treatment was 80 ° C. -Example 3- In Example 1, a sample was produced under the same conditions as in Example 1 except that the temperature of the hot water in the hot water treatment was 95 ° C. -Example 4- In Example 1, a sample was produced under the same conditions as in Example 1 except that instead of the hot water treatment, the titanium metal plate was treated with water vapor at 121 ° C. for 20 minutes in an autoclave.
- Example 1 a sample was produced under the same conditions as in Example 1 except that a calcium nitrate aqueous solution was used instead of the calcium chloride aqueous solution and that the temperature of the hot water in the hot water treatment was 80 ° C.
- Example 6- In Example 1, a sample was produced under the same conditions as in Example 1 except that a calcium acetate aqueous solution was used instead of the calcium chloride aqueous solution, and that the temperature of the hot water in the hot water treatment was 80 ° C.
- Example 7- a sample was produced under the same conditions as in Example 1 except that the holding temperature in the electric furnace was 800 ° C. and the temperature of the hot water in the hot water treatment was 80 ° C.
- Example 8- a sample was produced under the same conditions as in Example 1 except that a Ti-6Al-4V alloy plate was used instead of the titanium metal plate and that the temperature of the hot water in the hot water treatment was 80 ° C. did.
- Example 9- the sample was used under the same conditions as in Example 1 except that a Ti-15Mo-5Zr-3Al alloy plate was used instead of the titanium metal plate and that the temperature of the hot water in the hot water treatment was 80 ° C. Manufactured.
- Example 10 the sample was used under the same conditions as in Example 1 except that a Ti-6Al-2Nb-1Ta alloy plate was used instead of the titanium metal plate and that the temperature of the hot water in the hot water treatment was 80 ° C. Manufactured.
- Example 11 the sample was used under the same conditions as in Example 1 except that a Ti-15Zr-4Nb-4Ta alloy plate was used instead of the titanium metal plate and that the temperature of the hot water in the hot water treatment was 80 ° C. Manufactured.
- Example 12 In Example 1, a Ti-29Nb-13Ta-4.6Zr alloy plate was used instead of the titanium metal plate, a 1M sodium hydroxide aqueous solution was used instead of the 5M sodium hydroxide aqueous solution, and the holding temperature of the electric furnace was 600. A sample was produced under the same conditions as in Example 1 except that the temperature was changed to 700 ° C instead of 0 ° C, and the temperature of the hot water in the hot water treatment was changed to 80 ° C instead of 60 ° C.
- Example 13 In Example 1, a Ti-36Nb-2Ta-3Zr-0.3O alloy plate was used instead of the titanium metal plate, a 1M sodium hydroxide aqueous solution was used instead of the 5M sodium hydroxide aqueous solution, and the holding temperature of the electric furnace was set to 700 ° C. instead of 600 ° C., and a sample was produced under the same conditions as in Example 1 except that the temperature of the hot water in the hot water treatment was changed to 80 ° C. instead of 60 ° C.
- -Comparative Example 1- A pure titanium metal plate having a size of 10 mm ⁇ 10 mm ⁇ 1 mm was polished with a # 400 diamond pad, ultrasonically cleaned with acetone, 2-propanol, and ultrapure water for 30 minutes each, and then the same conditions as in Example 1 The sample was manufactured by treating with alkali and washing with ultrapure water for 30 seconds.
- -Comparative Example 2- The comparative substrate obtained in Comparative Example 1 was heat-treated under the same conditions as in Example 1.
- -Comparative Example 3- The comparative substrate obtained in Comparative Example 1 was treated with calcium under the same conditions as in Example 1.
- -Comparative Example 5- The comparative substrate obtained in Comparative Example 1 was heat-treated under the same conditions as in Example 1, and then subjected to calcium treatment under the same conditions as in Example 1.
- strength did not fall even if it gave warm water processing or steam processing (Example 2, Example 4).
- the heat treatment was performed at 800 ° C. (Example 7)
- the scratch strength of the surface layer was reduced to about half compared to the case where the heat treatment was performed at 600 ° C.
- Example 2 and Comparative Example 2 were subjected to a moisture resistance test in which the sample was exposed to an atmosphere at a temperature of 80 ° C. and a relative humidity of 95% for 1 week, and then immersed in a simulated body fluid.
- the sample of Example 2 was covered with apatite on the entire surface within 72 hours of immersion in the simulated body fluid as before the moisture resistance test, and the sample was kept for a long time under high temperature and high humidity. It was confirmed that high apatite forming ability was not lost.
- the sample of Comparative Example 2 formed apatite only on a part of the surface of the sample, and it was found that the apatite-forming ability was remarkably lowered when placed under high temperature and high humidity.
- composition analysis When the composition of the sample surface was analyzed by an energy dispersive X-ray analysis method with an acceleration voltage of 9 kV, as shown in Table 2, 5.2 atomic% sodium was detected in the sample after the alkali treatment (Comparative Example 1). Thereafter, sodium disappeared in the calcium-treated sample (Comparative Example 3), and about 4 atomic% of calcium was newly detected instead. Even when these were further subjected to heat treatment (Comparative Example 4) and hot water treatment (Example 2), the values thereof hardly changed.
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Abstract
Description
それ故、この発明の課題は、アパタイト形成能及び保存性に優れ、高い引っかき抵抗を有する骨修復材料を提供することにある。
チタン又はチタン合金からなる基材と、
基材上に形成され、カルシウムを含み,その濃度が表面から内部に向かうにつれ減少するチタン酸塩層とを備え、そのチタン酸塩層が、
バネ定数200g/mmのスタイラスに100μmの振幅を与え、100mN/minの荷重を印加しながら、スタイラスを10mm/secの速度で移動させたとき、20mN以上のひっかき抵抗を示し、且つ生体内あるいは擬似体液中で3日以内に全面にアパタイトが形成される能力を有することを特徴とする。
カルシウムイオンを含まずナトリウムイオン及びカリウムイオンのうち1種以上のカチオンを含みアルカリ性の第1の水溶液にチタン又はチタン合金からなる基材を浸漬する工程と、
リン酸イオンを含まずカルシウムイオンを含む第2の水溶液に浸漬する工程と、
乾燥雰囲気中で加熱する工程と、
60℃以上の温水又は水蒸気で処理する工程と
を備えることを特徴とする。
前記チタン酸塩層が、0.1~10μmの厚さを有するのが好ましい。厚さが0.1μmに満たない場合は、アパタイトの核となるカルシウム成分が表面に乏しすぎてアパタイトを形成しにくい。10μmを超えると、チタン酸塩層が基材から剥離しやすくなる。
水溶液処理後の加熱温度は、400~800℃が好ましい。温度が400℃未満の場合には、チタン酸塩層の機械的強度も化学的安定性も向上しにくい。
温水処理または水蒸気処理の好ましい温度は、それぞれ60~99℃又は100~180℃であり、その好ましい処理時間は0.1~48時間である。
-実施例1-
10mm×10mm×1mmの大きさの純チタン金属板を#400のダイヤモンドパッドを用いて研磨し、アセトン、2-プロパノール、超純水で順に各30分間超音波洗浄した後、5Mの水酸化ナトリウム水溶液5mlに60℃で24時間浸漬し(以下、「アルカリ処理」という。)、超純水で30秒間洗浄した。このチタン金属板を100mMの塩化カルシウム水溶液10mlに40℃で24時間浸漬し(以下、「カルシウム処理」という。)、超純水で30秒洗浄した。次いで、チタン金属板を電気炉中で常温から600℃まで5℃/minの速度で昇温し、600℃で1時間保持して、炉内で放冷した(以下、「加熱処理」という。)。その後、チタン金属板を10mlの超純水に60℃で24時間浸漬し(以下、「温水処理」という。)、超純水で30秒洗浄することにより、試料を製造した。
実施例1において、温水処理における温水の温度を80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
-実施例3-
実施例1において、温水処理における温水の温度を95℃としたことを除く他は実施例1と同じ条件で試料を製造した。
-実施例4-
実施例1において、温水処理に代えてチタン金属板をオートクレーブ中121℃の水蒸気で20分間処理したことを除く他は実施例1と同じ条件で試料を製造した。
実施例1において、塩化カルシウム水溶液に代えて硝酸カルシウム水溶液を用いたことと、温水処理における温水の温度を80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
-実施例6-
実施例1において、塩化カルシウム水溶液に代えて酢酸カルシウム水溶液を用いたことと、温水処理における温水の温度を80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
-実施例7-
実施例1において、電気炉中の保持温度を800℃としたことと、温水処理における温水の温度を80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
実施例1において、チタン金属板に代えてTi-6Al-4V合金板を用いたことと、温水処理における温水の温度を80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
-実施例9-
実施例1において、チタン金属板に代えてTi-15Mo-5Zr-3Al合金板を用いたことと、温水処理における温水の温度を80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
実施例1において、チタン金属板に代えてTi-6Al-2Nb-1Ta合金板を用いたことと、温水処理における温水の温度を80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
-実施例11-
実施例1において、チタン金属板に代えてTi-15Zr-4Nb-4Ta合金板を用いたことと、温水処理における温水の温度を80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
実施例1において、チタン金属板に代えてTi-29Nb-13Ta-4.6Zr合金板を用い、5Mの水酸化ナトリウム水溶液に代えて1Mの水酸化ナトリウム水溶液を用い、電気炉の保持温度を600℃に代えて700℃とし、温水処理における温水の温度を60℃に代えて80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
実施例1において、チタン金属板に代えてTi-36Nb-2Ta-3Zr-0.3O合金板を用い、5Mの水酸化ナトリウム水溶液に代えて1Mの水酸化ナトリウム水溶液を用い、電気炉の保持温度を600℃に代えて700℃とし、温水処理における温水の温度を60℃に代えて80℃としたことを除く他は実施例1と同じ条件で試料を製造した。
10mm×10mm×1mmの大きさの純チタン金属板を#400のダイヤモンドパッドを用いて研磨し、アセトン、2-プロパノール、超純水で各30分間超音波洗浄した後、実施例1と同一条件でアルカリ処理し、超純水で30秒間洗浄することにより、試料を製造した。
-比較例2-
比較例1で得られた比較用基板を実施例1と同一条件で加熱処理した。
-比較例3-
比較例1で得られた比較用基板を実施例1と同一条件でカルシウム処理した。
-比較例4-
比較例1で得られた比較用基板を実施例1と同一条件でカルシウム処理し、更に加熱処理した。
-比較例5-
比較例1で得られた比較用基板を実施例1と同一条件で加熱処理した後、実施例1と同一条件でカルシウム処理した。
実施例および比較例の試料を36.5℃に保たれたISO規格23317の擬似体液(SBF)に浸漬したところ、表1に示すように、比較例4を除くすべての試料において擬似体液浸漬72時間以内にアパタイトが形成された。しかもすべての実施例および比較例2の試料では、試料の表面全体にアパタイトが形成され、これらの試料は生体内で高いアパタイト形成能を示すことが確かめられた。
株式会社レスカ製のスクラッチ試験機CSR-2000を用いて、バネ定数200g/mmのスタイラスに試料上で100μmの振幅を与え、100mN/minの荷重を印加しながら、スタイラスを10mm/secの速度で移動させた。このときの臨界ひっかき強度を測定した。その結果、図1に示すように、その強度は加熱処理前(比較例1、比較例3)においては5mN以下であったのが、600℃の加熱処理後(比較例2、比較例4)には約50mNまで飛躍的に上昇した。また、その強度は温水処理または水蒸気処理を施しても低下しなかった(実施例2、実施例4)。一方、800℃の加熱処理を施した場合(実施例7)においては、600℃で加熱処理した場合に比べて、表面層の引っかき強度が半分程度まで低下した。
実施例2及び比較例2の試料を温度80℃、相対湿度95%の雰囲気下に1週間さらす耐湿試験を行った後、擬似体液に浸漬した。その結果、図2に示すように実施例2の試料は耐湿試験前と同様に擬似体液浸漬72時間以内に表面全体がアパタイトで覆われ、同試料は高温高湿下に長時間おかれても高いアパタイト形成能を失わないことが確かめられた。一方、比較例2の試料は、試料の表面の一部にしかアパタイトを形成せず、高温高湿下におかれるとアパタイト形成能が著しく低下することが判った。
試料表面の組成を加速電圧9kVでエネルギー分散X線分析法で分析すると、表2に示すようにアルカリ処理後の試料(比較例1)には、5.2原子%のナトリウムが検出された。その後カルシウム処理した試料(比較例3)ではナトリウムが消失し、代わりに約4原子%のカルシウムが新たに検出された。これらを更に加熱処理(比較例4)および温水処理(実施例2)してもその値がほとんど変化しなかった。
Claims (7)
- カルシウムイオンを含まずナトリウムイオン及びカリウムイオンのうち1種以上のカチオンを含みアルカリ性の第1の水溶液にチタン又はチタン合金からなる基材を浸漬する工程と、
リン酸イオンを含まずカルシウムイオンを含む第2の水溶液に浸漬する工程と、
乾燥雰囲気中で加熱する工程と、
60℃以上の温水又は水蒸気で処理する工程と
を備えることを特徴とする骨修復材料の製造方法。 - 第1の水溶液のアルカリイオン濃度が0.1~20Mの範囲にあり、浸漬温度が5~99℃の範囲にあり、浸漬時間が0.5~48時間の範囲にある請求項1に記載の製造方法。
- 第2の水溶液に含まれるアニオンが、塩化物イオン、酢酸イオン、硝酸イオン及び水酸化物イオンから選択される1種以上である請求項1に記載の製造方法。
- 第2の水溶液のカルシウムイオン濃度が0.1~1,000mMの範囲にあり、浸漬温度が5~99℃の範囲にあり、浸漬時間が0.5~48時間の範囲にある請求項1に記載の製造方法。
- 前記加熱の温度が400~800℃で、その時間が0.5~24時間である請求項1に記載の製造方法。
- 前記温水処理または水蒸気処理の時間が0.1~48時間である請求項1に記載の製造方法。
- チタン又はチタン合金からなる基材と、
基材上に形成され、カルシウムを含み,その濃度が表面から内部に向かうにつれ減少するチタン酸塩層とを備え、そのチタン酸塩層が、
バネ定数200g/mmのスタイラスに100μmの振幅を与え、100mN/minの荷重を印加しながら、スタイラスを10mm/secの速度で移動させたとき、20mN以上のひっかき抵抗を示し、且つ生体内あるいは擬似体液中で3日以内に全面にアパタイトが形成される能力を有することを特徴とする骨修復材料。
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US12/995,850 US8470387B2 (en) | 2008-06-03 | 2009-06-01 | Bone repair material and method for producing the same |
JP2010515759A JP5499347B2 (ja) | 2008-06-03 | 2009-06-01 | 骨修復材料及びその製造方法 |
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EP09758086.4A EP2301590B1 (en) | 2008-06-03 | 2009-06-01 | Method for producing a bone-repairing material |
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JP2013236700A (ja) * | 2012-05-14 | 2013-11-28 | Chube Univ | 抗菌性骨修復材料及びその製造方法 |
WO2014027612A1 (ja) * | 2012-08-16 | 2014-02-20 | 学校法人中部大学 | 骨修復材料及びその製造方法 |
JP2015171520A (ja) * | 2014-03-11 | 2015-10-01 | 国立大学法人三重大学 | 骨接合スクリューおよびその製造方法 |
WO2022097670A1 (ja) | 2020-11-05 | 2022-05-12 | 株式会社丸ヱム製作所 | 生体適合性材料及びその製造方法 |
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JP6746117B2 (ja) * | 2016-06-15 | 2020-08-26 | 株式会社小糸製作所 | アパタイト結晶の製造方法 |
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