JP2004305748A - 哺乳動物細胞接種済み複合スカフォルド - Google Patents
哺乳動物細胞接種済み複合スカフォルド Download PDFInfo
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Abstract
【解決手段】 植込み可能な生体適合性スカフォルドにおいて、生体適合性多孔質ポリマーマトリックスと、前記ポリマーマトリックスによって被包されており、且つ、該ポリマーマトリックス内部に配置されている生体適合性多孔質の繊維マットと、前記組織スカフォルド内部に接種されている多数の哺乳動物細胞とを有している上記スカフォルド。本発明は、本発明のスカフォルドを利用する、哺乳動物の疾患又は構造的欠陥を治療する方法にも向けられている。
【選択図】 図1
Description
本発明は、軟組織又は硬組織における疾患又は構造的欠陥を治療するための、哺乳動物細胞接種済み複合組織スカフォルド(scaffolds; 足場的構体)に関する。
多くの個体を苦しめる3種類の疾患を処置するための臨床治療の必要性が存在する。第1種の疾患は、病的/損傷した筋骨格組織(例えば、軟骨、硬骨、半月又は筋肉)に関する。一般的に、損傷筋骨格組織又は病的筋骨格組織(例えば、硬骨、軟骨若しくは筋肉)を修復するための臨床的アプローチによって、該組織の元の機能は実質的に元に戻らない。そのような欠陥を治療するために、人工の関節/デバイスがしばしば使用されてきたが、弛み(loosening);限られた耐久性;及び、該欠陥を取り囲んでいる機能的組織の破壊;に起因する複雑な結果を招いていた。
第2種の疾患は、糖尿病(DM)等の器官機能の低下に関する。糖尿病は、膵臓中のβ細胞の破壊によるか、又はインスリンに対する筋肉若しくは脂肪組織の無感応(insensitivity)によって引き起こされる。糖尿病に関する現行療法は、主な健康合併症(例えば、失明、腎不全及び潰瘍)を回避するには不十分である。
従って、従来の諸材料の限界を解決することのできる細胞接種済みスカフォルドの必要性が存在している。
本発明は、植込み可能な生体適合性スカフォルドにおいて、生体適合性多孔質ポリマーマトリックス(matrix; 基質)と;前記ポリマーマトリックスによって被包されており、且つ、該ポリマーマトリックス内部に配置されている生体適合性多孔質の繊維マットと;哺乳動物の欠陥部位又は異所性部位の中に前記スカフォルドを植え込む前に前記組織スカフォルド内部に接種されている多数の哺乳動物細胞と;を有している上記スカフォルドに向けられている。本発明はまた、本発明のスカフォルドを用いて、哺乳動物の疾患を治療する方法にも向けられている。繊維マットは好ましくは、不織布マットである。繊維マットを被包している生体適合性多孔質マトリックスは好ましくは、多孔質ポリマーフォームであって、好ましくは凍結乾燥法を用いて形成されるものである。
加えて、細胞が接種された複合スカフォルドは、細胞分泌の生物学的因子(cell-secreted biological factors)を放出する媒体の機能を果たすことができる。そのような生物学的因子は、他の諸成長因子;タンパク質;サイトカイン;又は、他の細胞種の増殖;の上昇調整(up-regulation)又は下降調整(down-regulation)を誘発することがある。そのような複合スカフォルドを欠陥部位若しくは患部組織の部位の中に植え込む前又は植え込んだ後、多数の細胞は、該スカフォルドの表面に接種することができる。
本発明は、生体適合性の複合組織スカフォルドにおいて、生体適合性多孔質ポリマーマトリックスによって被包されており、且つ、該ポリマーマトリックス内部に配置されている生体適合性多孔質の繊維マットを備えている上記スカフォルドに向けられている。好ましくは、哺乳動物の欠陥部位又は異所性部位の中に前記複合スカフォルドを植え込む前、該複合スカフォルドの中に、哺乳動物の細胞を投与する(即ち、接種する)。
スカフォルド10を造った後、植え込みを行なう前又は植え込みを行なう時、哺乳動物細胞をスカフォルド内部に投与する(即ち、接種する)。それら哺乳動物細胞は、脈管又は脈管組織から分離することができ、このことは、予想される用途又は治療されている疾患によって決まる。それら細胞は、細胞の数を増やすためか、又は所望の表現型への分化を誘導するために、当業者に知られている標準条件下で培養することができる。代替的に、分離済み哺乳動物細胞は、スカフォルド10の中に直接注入し;次いで、植え込みを行なう前、適切な生物学的マトリックスの増殖と堆積とを促進する条件の下、生体外で培養することができる。この開示内容に関し利益を有する当業者は、そのような条件を容易に認識するであろう。好ましい具体例において、それら分離済み細胞は、体内への植え込みを行なう前、体外での更なる培養を行うことなく、スカフォルド10の中に直接注入する。
該多孔質ポリマーマトリックス又は該繊維マットは、[ポリエチレン、ポリビニルアルコール(PVA)、ポリメチルメタクリレート(PMMA)、シリコーン、ポリエチレンオキシド(PEO)、ポリエチレングリコール(PEG)、及びポリウレタンを包含するが、それらに限定されない]非生分解性ポリマーを含有することがある。
もう1つの具体例において、複合スカフォルドの不織布繊維マットを形成する繊維は、生分解性ガラスで造る。生体ガラス;ケイ酸塩含有リン酸カルシウムガラス;又は、分解時間を制御するために変動量の鉄粒子が添加されているリン酸カルシウムガラス;は、紡いでガラス繊維にし、繊維マットを造るのに使用することができた材料の諸例である。
1つの具体例において、不織布マットを形成するフィラメントは、同時押出し成形を行なって、シース(sheath; 被覆)/コア構造を有するフィラメントを造ることができる。そのようなフィラメントは、もう1種の生分解性ポリマーを含有する1つ以上のコアを取り囲む生分解性ポリマーのシースを有している。一層遅く分解するコアを取り囲んでいる一層速く分解するシースを有するフィラメントは、拡張された支持体が組織の内方成長のために必要である場合、望ましいことがある。
利用することのできる、適用可能なポリマー濃度又は溶媒の量は、各々の系によって変わる。該溶液中のポリマーの量は通常、約0.01重量%から約90重量%まで変化することがあり、好ましくは、約0.1重量%から約30重量%まで変化する。これは、所定の溶媒に入っているポリマーの溶解度と、フォームスカフォルドにおいて望ましい最終特性とによって決まる。
適切な生体物質には、小腸粘膜下組織(SIS)、ヒアルロン酸、コラーゲン、アルギン酸塩、コンドロイチン硫酸、キトサン、及びそれらの混合物の固形粒子が包含される。それら固形物は、無傷構造(intact structure)内に見出だされる生体物質又は生体活性フラグメントの完全な構造を含有することがある。
もう1つの方法として、糖尿病等の疾患を治療するためには、細胞接種済み複合スカフォルドは、臨床的に好都合な部位[例えば、皮下空間、腸間膜、又は網(omentum)]に配置することができる。この特殊な場合において、複合スカフォルドは、異所性部位に生体内移植を行なった後、投与済み島を適切に捕らえるための担体(vehicle)としての役目を果たす。
島を、門脈循環に注入することによって直接移植する以前の試みは、長期間に渡って糖尿病を治療するためには不十分であることが実証された。更に、生分解性又は非分解性のマイクロスフェア(microspheres; 微小球体)を用いて、同種又は異種の島を被包する多くの方法は、血糖値を長期間に渡って制御するのを維持することはできなかった。これらの失敗は、脈管構造が不充分であったこと及び/又は移植された島の免疫拒絶(immune rejection)に起因すると考えられた。
更に、細胞接種済み複合スカフォルドを構成している諸ポリマー及び混合物は、治療薬又は薬剤の放出貯留槽(release depot)として使用することができる。本発明と併せて使用することのできる種々の異なる治療薬は、非常に広い。本発明の諸組成物を媒介として投与することのできる治療薬には通常、拒絶反応抑制剤;鎮痛剤;酸化防止剤;抗アポトーシス剤(例えば、エリスロポエチン);抗炎症薬(例えば、抗がん壊死因子α);抗−CD44;抗−CD3;抗−CD154;p38キナーゼ抑制剤;JAK−STAT抑制剤;抗−CD28;アセトアミノフェン;トラニラスト(Tranilast);細胞成長抑止剤(例えば、ラパマイシン);抗−IL2剤;及びそれらの組み合わせ;が包含されるが、それらに制限されない。
次の諸実施例は、本発明の原理と実施とを説明するが、本発明の範囲を限定しない。本発明の適用範囲内及び趣旨の範囲内での多くの更なる具体例は、当業者には容易に分かるであろう。
それらポリマー及びコポリマーのインヘレント粘度(I.V.,dl/g)は、溶媒としてクロロホルム又はヘキサフルオロイソプロパノール(HFIP)を利用し、0.1g/dlの濃度で、サーモスタット制御の30℃の水浴の中に浸漬された「50ボーア・キャノン−ウッベローデ希釈粘度計(50 bore Cannon-Ubbelhode dilution viscometer)」を用いて測定した。
以下に記述するように、90/10のPGA/PLA繊維で構成されるニードルパンチ不織布マット(厚さ2mm)を作った。PGA/PLA(90/10)のコポリマーは、ヤーンを造る従来法によって溶融押し出しを行い、連続マルチフィラメントヤーンにし;次いで、破壊に必要なエネルギー、強度、及び伸び率を増大させるために、配向させた。それらヤーンは、直径が約20μmのフィラメントから成った。これらヤーンは次いで、切断して、縮みしわをつけ、2インチの均一な長さにして、2インチのステープルファイバー(staple fiber; 短繊維)を形成した。
該マットは、酢酸エチルを用いて60分間洗い流し、次いで、真空乾燥を行った。
次いで、該モールド集成体(mold assembly)は、凍結乾燥機の棚の上に置き、凍結乾燥のシーケンス(sequence; 順序)を開始した。この実施例で使用した凍結乾燥のシーケンスは、(1)−17℃で60分間、(2)100mTの真空下、−5℃で60分間、(3)20mTの真空下、5℃で60分間、(4)20mTの真空下、20℃で60分間、であった。
結果として得られたスカフォルドは、ポリマーフォームマトリックスによって被包されており、且つ、該マトリックス内部に配置されている不織布繊維マットを有した。該スカフォルドの厚さは、約1.5mmであった。
凍結乾燥を行ってフォームにしたポリマーが、バーミンガム・ポリマーズ社(アラバマ州バーミンガム)からの、1.45dl/gのインヘレント粘度を有する60/40のPLA/PCLコポリマーであったことを除き、実施例1の手順に従って、生分解性複合スカフォルドを造った。この複合スカフォルドの孔径は、水銀圧入多孔率分析(Mercury Porosimetry analysis)を用いて決定した。孔径の範囲は、1〜300μmであり、メジアン孔径は45μmであった。図1は、該複合スカフォルドの横断面の走査電子顕微鏡写真(SEM)である。SEMは、不織布繊維を取り囲んで被包している、凍結乾燥済みフォームスカフォルドを明瞭に示している。
凍結乾燥を行ってフォームにしたポリマーが、バーミンガム・ポリマーズ社(アラバマ州バーミンガム)からの、1.50dl/gのインヘレント粘度を有する60/40のPLA/PCLコポリマーと、1.45dl/gのインヘレント粘度を有する35/65のPCL/PGAコポリマーの50:50混合物であったことを除き、実施例1の手順に従って、生分解性複合スカフォルドを造った。
凍結乾燥を行ってフォームにしたポリマーが、バーミンガム・ポリマーズ社(アラバマ州バーミンガム)からの、1.50dl/gのインヘレント粘度を有する60/40のPLA/PCLと、1.78dl/gのインヘレント粘度を有する85/15のPLA/PGA[イリノイ州リンコルシン(Lincolshine)、プラック(Purac)]の70:30混合物であったことを除き、実施例1の手順に従って、生分解性複合スカフォルドを造った。
凍結乾燥を行ってフォームにしたポリマーが、バーミンガム・ポリマーズ社(アラバマ州バーミンガム)からの、1.50dl/gのインヘレント粘度を有する60/40のPLA/PCLと、1.78dl/gのインヘレント粘度を有する85/15のPLA/PGA(イリノイ州リンコルシン、プラック)の30:70混合物であったことを除き、実施例1の手順に従って、生分解性複合スカフォルドを造った。
凍結乾燥を行ってフォームにしたポリマーが、バーミンガム・ポリマーズ社(アラバマ州バーミンガム)からの、1.50dl/gのインヘレント粘度を有する60/40のPLA/PCLと、1.78dl/gのインヘレント粘度を有する85/15のPLA/PGA(イリノイ州リンコルシン、プラック)の50:50混合物であったことを除き、実施例1の手順に従って、生分解性複合スカフォルドを造った。
乾燥レイ・ニードルパンチ不織布のマットをPDO繊維で作ったことを除き、実施例1の手順に従って、生分解性複合スカフォルドを造った。
乾燥レイ・ニードルパンチ不織布のマットをPGA繊維で作ったことを除き、実施例1の手順に従って、生分解性複合スカフォルドを造った。
乾燥レイ・ニードルパンチ不織布のマットをPGA繊維で作ったことを除き、実施例4の手順に従って、生分解性複合スカフォルドを造った。
この実施例は、複合スカフォルド内のポリマーフォーム又は乾燥レイ・ニードルパンチ不織布マットが、軟骨細胞の生体外反応に悪影響を与えたことを例示する。
J.Orthop.Res.,10,745(1992)の中で、ブッシュマン(Buschmann)等によって記述されている通りに、ウシ肩から一次軟骨細胞を分離した。ウシ軟骨細胞は、10%ウシ胎仔血清(FCS)、10mMのHEPES、0.1mMの非必須アミノ酸、20μg/mlのL−プロリン、50μg/mlのアスコルビン酸、100U/mlのペニシリン、100μg/mlのストレプトマイシン、及び0.25μg/mlのアンフォテリシンBを補足したダルベッコ変性ワシ培地(DMEM−高グルコース)(増殖培地)の中で培養した。該培地の半分は、一日置きに補充した。
実施例1、4、8及び9に記述する通りに、諸複合スカフォルドを造った。それらスカフォルドは、直径が5mm、厚さが1.5mmであり、70%エタノールで、20分間殺菌し、次いで、リン酸緩衝食塩水(PBS)で5回洗浄した。
要約すれば、不織布繊維マットを被包しているフォームスカフォルドの構造によって、細胞の移動と、硫酸化プロテオグリカンマトリックスの堆積とが支持された。
この実施例は、複合スカフォルド内のポリマーフォーム又は乾燥レイ・ニードルパンチ不織布マットが、セルトーリ細胞の生体外反応に悪影響を与えたことを例示する。
セルトーリ細胞は、9〜12日齢のBalb/c雄マウスの諸精巣から採取した。諸精巣は、ハンクス液(Hank’s balanced salt solution)(HBSS)中で収集し、1mmの断片に切断し、ハンクス液中で、コラゲナーゼ(2.5mg/ml;シグマタイプV)を用いて37℃で10分間消化させた。その消化産物は、1ミリモル/lのEDTAと、0.5%ウシ血清アルビミン(BSA)とを含有するCa+2/Mg2+を含有していないハンクス液を用いて3回洗浄し;ハンクス液に入れたデオキシリボヌクレアーゼ (Dnace)[4μg/ml、ベーリンガー・マンハイム社(Boehringer Mannheim)]とトリプシン(25μg/ml、ベーリンガー・マンハイム社)とを用いて37℃で10分間消化させ;次いで、ハンクス液で4回洗浄した。最終の細胞植込み剤(cell pellet)は、10%加熱不活性化済みウマ血清を補足したM199培地[ギブコ・ライフ・テクノロジーズ社(Gibco Life Technologies)、メリーランド州ロックビル]に再懸濁させ;500μm濾過器を通過させ;次いで、超浅クラスターディッシュ[コーニング社(Corning Inc.)、ニューヨーク州コーニング]中で2日間培養して、セルトーリ細胞を凝集させた。
以下に記述するように、90/10のPGA/PLA繊維で構成されるニードルパンチ不織布マット(厚さ2mm)を作った。PGA/PLA(90/10)のコポリマーは、ヤーンを造る従来法によって溶融押し出しを行い、連続マルチフィラメントヤーンにし;次いで、破壊に必要なエネルギー、強度、及び伸び率を増大させるために、配向させた。それらヤーンは、直径が約20μmのフィラメントから成った。これらヤーンは次いで、切断して、縮みしわをつけ、2インチの均一な長さにして、2インチのステープルファイバーを形成した。
次いで、90/10のPGA/PLAコポリマーのステープルファイバーを利用して、乾燥レイ・ニードルパンチ不織布のマットを造った。それらステープルファイバーは、開放して、標準的不織布機械装置でカーディングを行った。結果として得られたマットは、ウェブ状(webbed; クモの巣状)ステープルファイバーの形態であった。これらウェブ状ステープルファイバーは、ニードルパンチを行って、乾燥レイ・ニードルパンチ不織布の繊維マットを形成した。
次いで、凍結乾燥してフォームにすべきポリマーの溶液60mlを調製した。フォーム成分を作るのに使用したポリマーは、バーミンガム・ポリマーズ社(アラバマ州バーミンガム)によって製造された、1.45dl/gのインヘレント粘度(I.V.)を有する35/65のPCL/PGAコポリマーであった。1,4−ジオキサン溶媒に入れた35/65のPCL/PGAの0.25/99.25重量比を量った。該ポリマー及び溶媒は、フラスコの中に入れ、次いで、水浴の中に入れて70℃で5時間の間撹拌し、溶液を形成した。次いで、該溶液は、円筒濾紙[規格外粗め多孔率、ASTM 170−220(EC)タイプ]を用いて濾過し、フラスコ内に蓄えた。
次いで、該モールド集成体は、凍結乾燥機の棚の上に置き、凍結乾燥のシーケンスを開始した。この実施例で使用した凍結乾燥のシーケンスは、(1)−17℃で60分間、(2)100mTの真空下、−5℃で60分間、(3)20mTの真空下、5℃で60分間、(4)20mTの真空下、20℃で60分間、であった。
この実施例は、実施例12に従って造った諸複合スカフォルドの上にマウス島(murine islets)を接種することを例示する。
マウス島は、Balb/cマウスから、コラゲナーゼを用いて膵臓を消化し、フィコール(Ficoll)密度勾配遠心分離を行い、次いで、島を手選すること(hand picking)によって分離した。直径7.75mmの多ウェルを有する特注のテフロン(登録商標)モールドの中に、それら複合スカフォルド(直径8mm×厚さ2mm)を置いた。新たな500個の島は、細胞懸濁液(100μlの容積)として、それらスカフォルドの上に添加した。細胞接種済み諸構造体を含有する該モールドは、300RPMで1分間遠心分離にかけた。それら構造体は、該ウェルから取り去り、標準細胞培養プレート中に置き、ウシ血清アルブミン(0.5%)と、ニコチンアミド(10ミリモル)と、D−グルコース(10ミリモル)と、L−グルタミン(2ミリモル)と、IBMX(3−イソブチル−1−メチルキサンチン、50ミリモル)と、ペニシリン/ストレプトマイシンとで補足した、Hams−F10(ギブコ・ライフ・テクノロジーズ社、メリーランド州ロックビル)を含有する培地で、1日間培養した。それら接種済み構造体は、生存度を求めるために、生/死アッセイキット(Live/Dead assay kit)[モレキュラー・プローブズ社(Molecular Probes)、オレゴン州]を用いて染色した。図6に示すように、それら島の大部分は、生存能力があり、該スカフォルドの全体に渡り均一に分布していた。
(1)スカフォルドが生分解性である、請求項1に記載のスカフォルド。
(2)ポリマーマトリックスが、諸生分解性ポリマーから成る群から選ばれるポリマーを含有しており;しかも、繊維マットが、生分解性ガラスと、リン酸カルシウムを含有するセラミックスと、生分解性ポリマーとから成る群から選ばれる材料を含有する繊維製品を有している;請求項1に記載のスカフォルド。
(3)ポリマーマトリックス及び繊維マットが、生分解性ポリマーを含有している;上記実施態様(2)に記載のスカフォルド。
(4)生分解性ポリマーが、脂肪族ポリエステル、ポリアルキレンオキサレート、ポリアミド、ポリカーボネート、ポリオルトエステル、ポリオキサエステル、ポリアミドエステル、ポリ酸無水物及びポリホスファゼンのホモポリマーとコポリマーとから成る群から選ばれている、上実施態様(3)に記載のスカフォルド。
(5)繊維マットが、ポリグリコリド/ポリラクチドの90/10コポリマーを含有している、上記実施態様(4)に記載のスカフォルド。
ポリマーマトリックスを造るのに用いられるポリマー溶液の重量%:0.1重量%〜10重量%(好ましくは、0.1重量%〜5重量%)に関するクレームを追加する必要性
(7)ポリマーマトリックスが、ポリラクチドとポリグリコリドのコポリマーを、約95/5〜約85/15の範囲のポリラクチド/ポリグリコリドのモル比で含有している、上記実施態様(4)に記載のスカフォルド。
(8)多孔質ポリマーマトリックスが、ポリカプロラクトンとポリグリコリドのコポリマーを、約35/65〜約45/55の範囲のポリカプロラクトン/ポリグリコリドのモル比で含有している、上記実施態様(5)に記載のスカフォルド。
(9)多孔質ポリマーマトリックスがフォームを含有している、上記実施態様(8)に記載のスカフォルド。
(10)多孔質ポリマーマトリックスが、ポリラクチドとポリカプロラクトンのコポリマーを、約35/65〜約65/35の範囲のポリラクチド/ポリカプロラクトンのモル比で含有している、上記実施態様(4)に記載のスカフォルド。
(12)哺乳動物細胞が、骨髄細胞、平滑筋細胞、基質細胞、幹細胞、間葉幹細胞、滑液由来の幹細胞、胚幹細胞、血管細胞、軟骨細胞、骨芽細胞、脂肪組織由来前駆細胞、骨髄由来前駆細胞、腎臓細胞、腸細胞、島(islets)、β細胞、セルトーリ細胞(Sertoli cells)、末梢血液前駆細胞、線維芽細胞、グロムス細胞、ケラチン生成細胞、髄核細胞、線維輪細胞、線維軟骨細胞、成体組織から分離された幹細胞、オーバル細胞(oval cells; 卵形細胞)、ニューロン幹細胞、グリア細胞、マクロファージ、及び遺伝的形質転換細胞から成る群から選ばれている、請求項1に記載のスカフォルド。
(13)哺乳動物細胞が、島及びセルトーリ細胞から成る群から選ばれている、上記実施態様(12)に記載のスカフォルド。
(14)哺乳動物細胞が、成体ニューロン幹細胞、胚幹細胞、及びグリア細胞から成る群から選ばれている、上記実施態様(12)に記載のスカフォルド。
(15)生物学的因子を更に有している、請求項1に記載のスカフォルド。
(17)治療薬を更に含有している、請求項1に記載のスカフォルド。
(18)治療薬が、拒絶反応抑制剤、鎮痛剤、酸化防止剤、抗アポトーシス剤、エリスロポエチン、抗炎症薬、抗がん壊死因子α、抗−CD44、抗−CD3、抗−CD154、p38キナーゼ抑制剤、JAK−STAT抑制剤、抗−CD28、アセトアミノフェン、細胞成長抑止剤、ラパマイシン、及び抗−IL2剤から成る群から選ばれている、上記実施態様(17)に記載のスカフォルド。
(19)スカフォルドは生分解性である、請求項2に記載の方法。
(20)ポリマーマトリックスは、諸生分解性ポリマーから成る群から選ばれるポリマーを含有し;しかも、繊維マットは、生分解性ガラスと、リン酸カルシウムを含有するセラミックスと、生分解性ポリマーとから成る群から選ばれる材料を含有する繊維製品を有する;請求項2に記載の方法。
(22)生分解性ポリマーは、脂肪族ポリエステル、ポリアルキレンオキサレート、ポリアミド、ポリカーボネート、ポリオルトエステル、ポリオキサエステル、ポリアミドエステル、ポリ酸無水物及びポリホスファゼンのホモポリマーとコポリマーとから成る群から選ぶ、上実施態様(21)に記載の方法。
(23)繊維マットは、ポリグリコリド/ポリラクチドの90/10コポリマーを含有する、上記実施態様(22)に記載の方法。
(24)多孔質ポリマーマトリックスが、ポリカプロラクトンとポリグリコリドのコポリマーを、約35/65〜約45/55の範囲のポリカプロラクトン/ポリグリコリドのモル比で含有する、上記実施態様(23)に記載の方法。
(25)多孔質ポリマーマトリックスがフォームを含有する、上記実施態様(24)に記載の方法。
(27)疾患は糖尿病である、請求項2に記載の方法。
(28)スカフォルドに、セルトーリ細胞及び島を接種する、上記実施態様(27)に記載の方法。
(29)スカフォルドは、生物学的因子を更に有する、上記実施態様(27)に記載の方法。
(30)スカフォルドは生分解性である、請求項3に記載の方法。
(32)構造的欠陥は、関節軟骨、半月、及び硬骨から成る群から選ばれる組織の中に存在する、請求項3に記載の方法。
20 繊維マットの繊維
25 マクロ細孔
30 多孔質ポリマーマトリックス
35 ミクロ細孔
Claims (3)
- 植込み可能な生体適合性スカフォルドにおいて、
生体適合性多孔質ポリマーマトリックスと、
前記ポリマーマトリックスによって被包されており、且つ、該ポリマーマトリックス内部に配置されている生体適合性多孔質の繊維マットと、
前記組織スカフォルド内部に接種されている多数の哺乳動物細胞と
を有している上記スカフォルド。 - 哺乳動物に生体適合性スカフォルドを植え込む段階を包含する、該哺乳動物の疾患を治療する方法において、前記スカフォルドは、
生体適合性多孔質ポリマーマトリックスと、
前記ポリマーマトリックスによって被包されており、且つ、該ポリマーマトリックス内部に配置されている生体適合性多孔質の繊維マットと、
前記組織スカフォルド内部に接種されている多数の哺乳動物細胞と
を有する、上記治療方法。 - 哺乳動物に生体適合性スカフォルドを植え込む段階を包含する、該哺乳動物の構造的欠陥を治療する方法において、前記スカフォルドは、
生体適合性多孔質ポリマーマトリックスと、
前記ポリマーマトリックスによって被包されており、且つ、該ポリマーマトリックス内部に配置されている生体適合性多孔質の繊維マットと、
前記組織スカフォルド内部に接種されている多数の哺乳動物細胞と
を有する、上記治療方法。
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Also Published As
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US20040197367A1 (en) | 2004-10-07 |
TW200505514A (en) | 2005-02-16 |
US20080085292A1 (en) | 2008-04-10 |
CN1568903A (zh) | 2005-01-26 |
AU2004201379A1 (en) | 2004-10-21 |
EP1466633A1 (en) | 2004-10-13 |
CN100563600C (zh) | 2009-12-02 |
CA2463443A1 (en) | 2004-10-02 |
US20040197375A1 (en) | 2004-10-07 |
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