JP5837996B2 - 水和ゲル及び水和ゲルメンブレイン並びにそれらの製造方法 - Google Patents
水和ゲル及び水和ゲルメンブレイン並びにそれらの製造方法 Download PDFInfo
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- JP5837996B2 JP5837996B2 JP2014548646A JP2014548646A JP5837996B2 JP 5837996 B2 JP5837996 B2 JP 5837996B2 JP 2014548646 A JP2014548646 A JP 2014548646A JP 2014548646 A JP2014548646 A JP 2014548646A JP 5837996 B2 JP5837996 B2 JP 5837996B2
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- peg
- polymer network
- hydrated gel
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- membrane
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Description
すなわち、歯科用メンブレインの場合、骨再生が完成される時点まではメンブレイン強度が維持され、骨再生が完成された以後には速く分解されて、最終的に硬組織と軟組織の融合にメンブレインが妨害物でとして作用してはならないが、光重合を利用した水和ゲルタイプのメンブレインは、強い物理的強度を有する半面、適切な時点で分解されにくいという問題点がある。
本発明の他の目的は、従来のシートタイプのメンブレインの使用上の不便さを克服するために骨欠損部の形状に関係なく自由に適用することができる水和ゲルメンブレイン及びその製造方法を提供することにある。
また、光重合が可能な官能基は、アクリレート、メタクリレート、クマリン、チミン及びシンナマートのいずれか一つ以上を使用することができる。
また、光重合開始剤は、400〜750nm波長の可視光線に反応してラジカルを生成することができる。
本発明の水和ゲルは、光重合が可能な官能基を有するPEGと、光重合されたPEGとともに相互侵入高分子網目(IPN)を形成し、PEGより高い粘度と速い生体分解速度を有する天然高分子添加剤と、PEGの光重合を開始するためのラジカルを生成する光重合開始剤と、を含んで構成され、光重合されたPEGと天然高分子添加剤が混合されて形成された相互侵入高分子網目(IPN)形態を有することを特徴とする。
しかし、本発明の水和ゲルを適用したメンブレインの場合、図1に示したとおり、相互侵入高分子網目を構成する天然高分子添加剤が適切な分解時点(target point)で先に分解されながら水和ゲルの内部ネットワーク構造が緩んで、緩んだネットワーク内部に兔疫細胞が容易に浸透して、結果的にメンブレインの速い体内分解が進行される。
すなわち、PEGより速い生体分解速度を有する天然高分子添加剤が体内分解性を主導することにより、水和ゲルの体内分解速度の加速が可能になり、天然高分子の添加を通じて水和ゲル−組職相互間の親和性を増加させて、窮極的には、これを歯科用メンブレインで使用する場合、硬組織と軟組織の融合を促進させることができる。
一方、高分子網目の骨組みを形成するPEGは、〔(−CH2CH2O−)n(ここで nは10〜1,000の自然数)〕の化学式を有する高分子として、好ましくは、分子量範囲内で直鎖状(2−arm)以外にも分枝状(4または8−arm)、星状(multi−arm)のPEGを単独または混合して使用することができる。
また、光重合開始剤は、PEGの光重合を開始するためのラジカルを生成する役目をし、好ましくは、400〜750nm波長の可視光線に反応してラジカルを生成する。
また、水和ゲルを使用したメンブレインは、I)PEGを含む第1の液型及び、天然高分子添加剤と光重合開始剤を含む第2の液型と、を準備する段階と、II)準備された第1の液型と第2の液型を空洞部の中で混合する段階と、III)混合溶液をメンブレイン形態で形象化する段階と、IV)メンブレインに可視光線を加える段階と、を通じて製造することができ、または、I)PEGを含む第1の液型及び、天然高分子添加剤と光重合開始剤を含む第2の液型を準備する段階と、II)準備された第1の液型と第2の液型を空洞部内で混合する段階と、III)混合溶液に可視光線を照射して相互侵入高分子網目(IPN)形態の水和ゲルを形成する段階と、IV)水和ゲルをメンブレイン形態で形象化する段階と、を通じて製造することができる。
このように混合された溶液は、周辺部に流れない程度の粘度を有するので、混合溶液を骨欠損部形態の枠に注射型容器などを利用して塗布するか哺乳類の骨欠損部の部分に直接塗布して適切なメンブレイン形態で自由に形象化することができ、このように形象化されたメンブレインに可視光線を照射して重合させることにより、最終的に相互侵入高分子網目(IPN)形態の水和ゲルメンブレインを製造することができる。
本発明の水和ゲルを歯科用材料で使用する際、上述の注射型容器を利用する方法の外にもペースト容器を利用する方法、直接形象化する方法、鋳型を利用する方法など、本発明の要旨を脱しない限り多様な方法で使用が可能である。
一方、本発明のまた他の実施例では、第1の液型と第2の液型との混合溶液にすぐ可視光線を照射して水和ゲル形態で先に硬化させた後、水和ゲルに適切な圧力を加えて塗布することにより水和ゲルメンブレインを製造するができる。
Claims (7)
- 重合が可能な官能基を有するポリエチレングリコール(polyethylene glycol:以下、PEGと略す)と、
光重合されたPEGとともに相互侵入高分子網目(interpenetrating polymer network:IPNと略す)を形成し、前記PEGより高い粘度と速い生体分解速度を有することにより前記PEGより先に分解されて前記高分子網目の体内分解を促進させる天然高分子添加剤と、
前記PEGの光重合を開始するためのラジカルを生成する光重合開始剤と、を含み、
前記天然高分子添加剤は、ヒアルロン酸とコラーゲンの組み合わせが用いられ、分子量が100,000〜10,000,000であり、
前記PEGは、〔(−CH2CH2O−)n(ここでnは10〜1,000の自然数)〕の化学式を有し、前記分子量範囲内で直鎖状(2−arm)、分枝状(4または8−arm)、星状(multi−arm)のPEGが単独または混合して使用され、
前記光重合が可能な官能基は、アクリレート、メタクリレート、クマリン、チミン及びシンナマートのいずれか一つ以上を含み、
骨再生が完成された後、前記天然高分子添加剤が相互侵入高分子網目内で前記PEGより先に分解されて前記高分子網目の体内分解を促進させ、
骨欠損部に適用されることを特徴とする水和ゲル。 - I)光重合が可能な官能基を有するポリエチレングリコール(polyethylene glycol:以下、PEGと略す。)を含む第1の液型及び、前記PEGより高い粘度と速い生体分解速度を有することにより前記PEGより先に分解されて前記高分子網目の体内分解を促進させる天然高分子添加剤と前記PEGの光重合を開始するためのラジカルを生成する光重合開始剤とを含む第2の液型を準備する段階と、
II)前記準備された第1の液型と第2の液型を空洞部内で混合する段階と、
III)前記混合溶液に可視光線を照射して相互侵入高分子網目(IPN)形態の水和ゲルを形成する段階と、を含み、
前記天然高分子添加剤は、ヒアルロン酸とコラーゲンの組み合わせが用いられ、分子量が100,000〜10,000,000であり、
前記PEGは、〔(−CH2CH2O−)n(ここでnは10〜1,000の自然数)〕の化学式を有し、前記分子量範囲内で直鎖状(2−arm)、分枝状(4または8−arm)、星状(multi−arm)のPEGが単独または混合して使用され、
前記光重合が可能な官能基は、アクリレート、メタクリレート、クマリン、チミン及びシンナマートのいずれか一つ以上を含み、
骨再生が完成された後、前記天然高分子添加剤が相互侵入高分子網目内で前記PEGより先に分解されて前記高分子網目の体内分解を促進させ、
骨欠損部に適用されることを特徴とする水和ゲルの製造方法。 - 前記光重合開始剤は、400〜750nm波長の可視光線に反応してラジカルを生成することを特徴とする請求項2に記載の水和ゲルの製造方法。
- 光重合が可能な官能基を有するポリエチレングリコール(polyethylene glycol:以下、PEGと略す)と、
光重合されたPEGとともに相互侵入高分子網目(interpenetrating polymer network:IPNと略す)を形成し、前記PEGより高い粘度と速い生体分解速度を有することにより前記PEGより先に分解されて前記高分子網目の体内分解を促進させる天然高分子添加剤と、
前記PEGの光重合を開始するためのラジカルを生成する光重合開始剤と、を含み、
前記天然高分子添加剤は、ヒアルロン酸とコラーゲンの組み合わせが用いられ、分子量が100,000〜10,000,000であり、
前記PEGは、〔(−CH2CH2O−)n(ここでnは10〜1,000の自然数)〕の化学式を有し、前記分子量範囲内で直鎖状(2−arm)、分枝状(4または8−arm)、星状(multi−arm)のPEGが単独または混合して使用され、
前記光重合が可能な官能基は、アクリレート、メタクリレート、クマリン、チミン及びシンナマートのいずれか一つ以上を含み、
骨再生が完成された後、前記天然高分子添加剤が相互侵入高分子網目内で前記PEGより先に分解されて前記高分子網目の体内分解を促進させ、
骨欠損部に適用されることを特徴とする水和ゲルメンブレイン。 - I)光重合が可能な官能基を有するポリエチレングリコール(polyethylene glycol:以下、PEGと略す)を含む第1の液型及び、光重合されたPEGと一緒に相互侵入高分子網目 (interpenetrating polymer network:IPN)を形成し、前記PEGより高い粘度と速い生体分解速度を有することにより前記PEGより先に分解されて前記高分子網目の体内分解を促進させる天然高分子添加剤と前記PEGの光重合を開始するためのラジカルを生成する光重合開始剤とを含む第2の液型を準備する段階と、
II)前記準備された第1の液型と第2の液型を空洞部内で混合する段階と、
III)前記混合溶液をメンブレイン形態で形象化する段階と、
IV)前記メンブレインに可視光線を照射して相互侵入高分子網目(IPN)形態の水和ゲルを形成する段階と、を含み、
前記天然高分子添加剤は、ヒアルロン酸とコラーゲンの組み合わせが用いられ、分子量が100,000〜10,000,000であり、
前記PEGは、〔(−CH2CH2O−)n(ここでnは10〜1,000の自然数)〕の化学式を有し、前記分子量範囲内で直鎖状(2−arm)、分枝鎖状(4または8−arm)、星状(multi−arm)のPEGが単独または混合して使用され、
前記光重合が可能な官能基は、アクリレート、メタクリレート、クマリン、チミン及びシンナマートのいずれか一つ以上を含み、
骨再生が完成された後、前記天然高分子添加剤が相互侵入高分子網目内で前記PEGより先に分解されて前記高分子網目の体内分解を促進させ、
骨欠損部に適用されることを特徴とする水和ゲルメンブレインの製造方法。 - I)光重合が可能な官能基を有するポリエチレングリコール(polyethylene glycol:以下、PEGと略す)を含む第1の液型及び、前記PEGより高い粘度と速い生体分解速度を有する天然高分子添加剤と前記PEGの光重合を開始するためのラジカルを生成する光重合開始剤とを含む第2の液型を準備する段階と、
II)前記準備された第1の液型と第2の液型を空洞部内で混合する段階と、
III)前記混合溶液に可視光線を照射して相互侵入高分子網目(IPN)形態の水和ゲルを形成する段階と、
IV)前記水和ゲルをメンブレイン形態で形象化する段階と、を含み、
前記天然高分子添加剤は、ヒアルロン酸とコラーゲンの組み合わせが用いられ、分子量が100,000〜10,000,000であり、
前記PEGは、〔(−CH2CH2O−)n(ここでnは10〜1,000の自然数)〕の化学式を有し、前記分子量範囲内で直鎖状(2−arm)、分枝鎖状(4または8−arm)、星状(multi−arm)のPEGが単独または混合して使用され、
前記光重合が可能な官能基は、アクリレート、メタクリレート、クマリン、チミン及びシンナマートのいずれか一つ以上を含み、
骨再生が完成された後、前記天然高分子添加剤が相互侵入高分子網目内で前記PEGより先に分解されて前記高分子網目の体内分解を促進させ、
骨欠損部に適用されることを特徴とする水和ゲルメンブレインの製造方法。 - 前記光重合開始剤は、400〜750nm波長の可視光線に反応してラジカルを生成することを特徴とする請求項5または請求項6に記載の水和ゲルメンブレインの製造方法。
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