A high strength chitin composite material and method of making
Abstract
The present invention relates to a composite laminated material having high mechanical strength and a method for producing the material. The present invention also provides a method of attaching a medical implant device to tissue.

Term
4.9 yearsto projected expiry
Projected expiry 30 August 2031, counted from filing; an application has no term until it is granted.
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101 claims: 28 independent, 73 dependent
- 1炭水化物ベースの基材とタンパク質とを含む、複合積層材料。
- 2前記炭水化物ベースの基材が、フィルム、繊維、スポンジ、メッシュ、発泡体、またはナノスケール構造物を含む、請求項1記載の複合積層材料。
- 3炭水化物対タンパク質の比が10:1~1:10の範囲内にある、請求項1または2記載の複合積層材料。
- 4炭水化物ベースの基材が、キチン、フルクトオリゴ糖、ガラクトオリゴ糖、マンナンオリゴ糖、グリコーゲン、デンプン(アミラーゼ、アミロペクチン)、グリコサミノグリカン(例えば、ヒアルロン酸、コンドロイチン-4-硫酸、コンドロイチン-6-硫酸、デルマタン硫酸、ケラチン硫酸、ヘパリン、および同様のもの)、セルロース、βグルカン(ザイモサン、レンチナン、シゾフィラン)、マルトデキストリン、イヌリンまたはレバンβ(2→6)ベースの基材である、請求項1~3のいずれか一項記載の複合積層材料。
- 5前記炭水化物ベースの基材が、キトサンベースの基材である、請求項1~4のいずれか一項記載の複合積層材料。
- 6前記タンパク質が、絹フィブロイン、パークリン(perculin)、アブダクチン、エラスチン、レシリン、フィブロネクチン、フィブリノゲン、ケラチン、チチン、コラーゲン、アクチン、Arp2/3、コロニン、ジストロフィン、FtsZ、ミオシン、スペクトリン、タウ(タンパク質)、チューブリン、F-スポンジン、ピカチュリン、それらの断片および類似体および誘導体、ならびにそれらの任意の組み合わせからなる群より選択される、請求項1~5のいずれか一項記載の複合積層材料。
- 7前記炭水化物がキトサンであり、かつ前記タンパク質が絹フィブロインを含み、かつキトサン対絹フィブロインの比が1:1.5~1:2の範囲内にある、請求項1記載の複合積層材料。
- 8前記炭水化物ベースの基材が、予め規定されたマイクロトポグラフィーを有する少なくとも1つの表面を含み、かつ前記タンパク質が該表面に適用されている、請求項1~7のいずれか一項記載の複合積層材料。
- 9前記予め規定されたマイクロトポグラフィーが、前記炭水化物ベースの基材に成形されている、請求項8記載の複合積層材料。
- 10前記タンパク質が、予め規定されたマイクロトポグラフィーを有する少なくとも1つの表面を含む、請求項1~9のいずれか一項記載の複合積層材料。
- 11前記予め規定されたマイクロトポグラフィーが、前記タンパク質に成形されている、請求項10記載の複合積層材料。
- 12第2の炭水化物ベースの基材をさらに含む、請求項1~11のいずれか一項記載の複合積層材料。
- 13前記第2の炭水化物ベースの基材がキチンベースの基材である、請求項12記載の複合積層材料。
- 14カーボンファイバー、カーボンナノチューブ、ガラスファイバー、低分子、ポリマー、タンパク質、ペプチド、ペプチド模倣体、核酸、有機化合物、無機化合物、結晶性化合物、生物学的化合物、生物活性化合物、生物活性を有する化合物、および生物学的、薬学的または治療的な作用物質、ならびにそれらの任意の組み合わせからなる群より選択される分子を、炭水化物層またはタンパク質層の少なくとも一方の層中に含む、請求項1~13のいずれか一項記載の複合積層材料。
- 15前記分子が前記炭水化物層中に存在する、請求項14記載の方法。
- 16前記分子が、前記炭水化物層に共有結合により連結されている、請求項15記載の方法。
- 17前記分子が前記タンパク質層中に存在する、請求項14記載の方法。
- 18前記分子が、前記タンパク質層に共有結合により連結されている、請求項17記載の方法。
- 19前記結晶性物質が炭酸カルシウムである、請求項14~18のいずれか一項記載の複合積層材料。
- 20前記複合材料の少なくとも一部に対する撥水性コーティングをさらに含む、請求項1~19のいずれか一項記載の複合積層材料。
- 21パリレンで構成される、請求項20記載の複合積層材料。
- 22水性環境に曝露された場合に、前記複合材料の一部に対する撥水性コーティングの位置に応じて変化する機械的特性を示す、請求項20~21のいずれか一項記載の複合積層材料。
- 23複合積層材料を形成する方法であって、 炭水化物ベースの基材を供給する工程、および 該炭水化物ベースの基材をタンパク質溶液と接触させる工程を含む、方法。
- 24前記炭水化物ベースの基材が、キチン、フルクトオリゴ糖、ガラクトオリゴ糖、マンナンオリゴ糖、グリコーゲン、デンプン(アミラーゼ、アミロペクチン)、グリコサミノグリカン(例えば、ヒアルロン酸、コンドロイチン-4-硫酸、コンドロイチン-6-硫酸、デルマタン硫酸、ケラチン硫酸、ヘパリン、および同様のもの)、セルロース、βグルカン(ザイモサン、レンチナン、シゾフィラン)、マルトデキストリン、イヌリンまたはレバンβ(2→6)ベースの基材である、請求項23記載の方法。
- 25前記炭水化物ベースの基材が、キトサンベースの基材である、請求項23~24のいずれか一項記載の方法。
- 26前記タンパク質が、絹フィブロイン、パークリン、アブダクチン、エラスチン、レシリン、フィブロネクチン、フィブリノゲン、ケラチン、チチン、コラーゲン、アクチン、Arp2/3、コロニン、ジストロフィン、FtsZ、ミオシン、スペクトリン、タウ(タンパク質)、チューブリン、F-スポンジン、ピカチュリン、それらの断片および類似体および誘導体、ならびにそれらの任意の組み合わせからなる群より選択される、請求項23~25のいずれか一項記載の方法。
- 27炭水化物対タンパク質の比が10:1~約1:10の範囲内にある、請求項23~26のいずれか一項記載の方法。
- 28炭水化物ベースの材料の溶液を脱水することによって、前記炭水化物ベースの基材を形成する、請求項23~27のいずれか一項記載の方法。
- 29炭水化物ベースの材料の前記溶液が酸を含む、請求項28記載の方法。
- 30前記酸が、イタコン酸、ポリイタコン(polyitaconic)酸、アコニット酸、尿酸、グルクロン酸、ギ酸、酢酸、トリクロロ酢酸、プロピオン酸、ブタン酸、4-クロロブタン酸、3-クロロブタン酸、2-ブロモブタン酸、2-クロロブタン酸、亜塩素酸、次亜塩素酸、クエン酸、グルコン酸、乳酸、シュウ酸、酒石酸、アスコルビン酸、メルドラム酸、フッ化水素酸、シアン化水素酸、硫化水素、オルトリン酸、亜硫酸、炭酸、弱塩基の共役酸、およびそれらの任意の組み合わせからなる群より選択される、請求項29記載の方法。
- 31塩基性溶液を適用することによって、前記炭水化物ベースの材料を中和する工程をさらに含む、請求項29~30のいずれか一項記載の方法。
- 32前記塩基性溶液が、水酸化ナトリウム、水酸化アンモニウム、水酸化カリウム、水酸化カルシウム、水酸化マグネシウム、水酸化バリウム、水酸化ストロンチウム、水酸化リチウム、水酸化ルビジウム、炭酸ナトリウムおよびアンモニアからなる群より選択される塩基を含むか、または該塩基性溶液が高pH緩衝液である、請求項30記載の方法。
- 33前記高pH緩衝液が炭酸緩衝液である、請求項32記載の方法。
- 34炭水化物ベースの材料の溶液を凍結乾燥することによって、前記炭水化物ベースの基材を形成する、請求項23~33のいずれか一項記載の方法。
- 35炭水化物ベースの材料の溶液に気泡を注入することによって、前記炭水化物ベースの基材を形成する、請求項23~33のいずれか一項記載の方法。
- 36炭水化物ベースの溶液をスピニングして繊維を形成することによって、前記炭水化物ベースの基材を形成する、請求項23~33のいずれか一項記載の方法。
- 37キチンベースの溶液をエレクトロスピニングして繊維を形成することによって、前記炭水化物ベースの基材を形成する、請求項23~33または35のいずれか一項記載の方法。
- 38炭水化物ベースの溶液をロータリースピニングして繊維を形成することによって、前記炭水化物ベースの基材を形成する、請求項22~32または35のいずれか一項記載の方法。
- 39前記タンパク質のβ転移を誘導する工程をさらに含む、請求項23~38のいずれか一項記載の方法。
- 40アルコール、有機溶媒、水溶液、または応力の印加、圧力の印加もしくは熱の印加を含む因子のうちの1つまたは複数で前記タンパク質を処理することによって、前記β転移を誘導する、請求項39記載の方法。
- 41カーボンナノチューブ、ガラスファイバー、低分子、ポリマー、タンパク質、ペプチド、ペプチド模倣体、核酸、有機化合物、無機化合物、結晶性物質、生物学的化合物、生物活性化合物、生物活性を有する化合物、および生物学的、薬学的または治療的な作用物質、ならびにそれらの任意の組み合わせからなる群より選択される保有材料を前記複合材料に導入する工程をさらに含む、請求項23~40のいずれか一項記載の方法。
- 42前記保有材料が、前記複合材料に共有結合により連結されている、請求項40記載の方法。
- 43請求項23~42のいずれか一項記載の方法により形成される物質の組成物。
- 44請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含む、補綴デバイス。
- 45請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含む、組織工学用スキャホールド。
- 46請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含む、薬物送達デバイス。
- 47請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含む、移植可能材料。
- 48請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含み、該組成物が鉱物または結晶性物質を含む、材料。
- 49請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含む、薄い透明フィルム。
- 50請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含む、多層材料。
- 51請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含み、該組成物が、目的に合った機械的特性を提供するために追加の成分を含む、多層材料。
- 52請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含み、該組成物が撥水性コーティング材料を含む、材料。
- 53請求項23~42のいずれか一項記載の方法により形成される物質の組成物を含み、該組成物が、可変の柔軟性を有する領域を提供するために、撥水性コーティング材料の可変領域を含む、材料。
- 54複合積層材料を形成する方法であって、 キチンベースの材料を酸性溶液に溶解する工程、 溶媒を蒸発させることによって、該キチンベースの材料のキチンベースの構造物を形成する工程、 該キチンベースの構造物を塩基性溶液で処理して、プロトン化されたアミノ基を中和する工程、 該キチンベースの構造物を洗浄する工程、 任意で、該キチンベースの構造物を脱水する工程、 該キチンベースの構造物にタンパク質溶液を適用して、少なくとも1つのタンパク質層を該キチンベースの構造物表面に有する複合材料を生成する工程、 該キチンベースの構造物表面の該タンパク質層を乾燥させる工程、および 該複合材料をアルコールベースの溶液で処理して、該タンパク質のβ転移を誘導する工程を含む、方法。
- 55キチンベースの材料対タンパク質の比が10:1~1:10の範囲内にある、請求項54記載の方法。
- 56前記キチンベースの材料がキトサンである、請求項54~55のいずれか一項記載の方法。
- 57前記タンパク質がフィブロインである、請求項54~56のいずれか一項記載の方法。
- 58前記酸性溶液が酢酸を含む、請求項54~57のいずれか一項記載の方法。
- 59前記塩基性溶液がNaOHを含む、請求項54~58のいずれか一項記載の方法。
- 60前記アルコールベースの溶液がメタノールを含む、請求項54~59のいずれか一項記載の方法。
- 61請求項54~60のいずれか一項記載の方法により形成される物質の組成物。
- 62医学的移植デバイスを組織または臓器に接着させる方法であって、 有効量のトランスグルタミナーゼを該組織または該臓器の表面に適用する工程、および 該医学的移植デバイスを該組織の表面に接触させる工程を含む、方法。
- 63前記医学的移植デバイスがトランスグルタミナーゼを含む、請求項62記載の方法。
- 64医学的移植デバイスを組織または臓器に接着させる方法であって、 有効量のトランスグルタミナーゼを含む該医学的移植デバイスを、該臓器と接触させる工程を含む、方法。
- 65前記有効量のトランスグルタミナーゼを前記組織の表面に適用する工程をさらに含む、請求項64記載の方法。
- 66前記トランスグルタミナーゼが哺乳動物トランスグルタミナーゼである、請求項62~65のいずれか一項記載の方法。
- 67前記トランスグルタミナーゼが微生物トランスグルタミナーゼ(mTgase)である、請求項62~65のいずれか一項記載の方法。
- 68前記トランスグルタミナーゼがカルシウム非依存性トランスグルタミナーゼである、請求項62~67のいずれか一項記載の方法。
- 69前記トランスグルタミナーゼが、第XIII因子A(フィブリン安定化因子)、1型トランスグルタミナーゼ(ケラチノサイトトランスグルタミナーゼ)、2型トランスグルタミナーゼ(組織トランスグルタミナーゼ、tTgase)、3型トランスグルタミナーゼ(上皮トランスグルタミナーゼ)、4型トランスグルタミナーゼ(前立腺トランスグルタミナーゼ)、5型トランスグルタミナーゼ(トランスグルタミナーゼX)、6型トランスグルタミナーゼ(トランスグルタミナーゼY)、7型トランスグルタミナーゼ(トランスグルタミナーゼZ)、およびそれらの任意の組み合わせからなる群より選択される、請求項62~68のいずれか一項記載の方法。
- 70前記トランスグルタミナーゼが、溶液、エマルジョン、エアロゾル、発泡体、軟膏、ペースト、ローション、粉末、ゲル、ヒドロゲル、親水コロイド、マイクロ粒子、ナノ粒子、またはクリームとして製剤化される、請求項62~69のいずれか一項記載の方法。
- 71前記医学的移植デバイスが、人工組織、人工臓器、補綴デバイス、薬物送達デバイス、創傷被覆材、フィルム、発泡体、スポンジ、止血材、およびそれらの任意の組み合わせからなる群より選択される、請求項62~70のいずれか一項記載の方法。
- 72前記医学的移植デバイスが、包帯、ガーゼ、テープ、メッシュ、ネット、ばんそうこう、フィルム、メンブレン、パッチ、マイクロ粒子、ナノ粒子、およびそれらの任意の組み合わせからなる群より選択される創傷被覆材である、請求項71記載の方法。
- 73前記医学的移植デバイスが発泡体である、請求項71記載の方法。
- 74前記医学的移植デバイスがタンパク質を含み、かつ該タンパク質がトランスグルタミナーゼにより架橋可能である、請求項62~73のいずれか一項記載の方法。
- 75前記医学的移植デバイスが前記タンパク質でコーティングされている、請求項74記載の方法。
- 76前記タンパク質が絹フィブロインである、請求項74~75のいずれか一項記載の方法。
- 77前記トランスグルタミナーゼが、前記医学的移植デバイスの表面にコーティングされている、請求項62~76のいずれか一項記載の方法。
- 78前記トランスグルタミナーゼが、前記医学的移植デバイスに非共有結合により連結されている、請求項62~77のいずれか一項記載の方法。
- 79トランスグルタミナーゼの前記有効量が、前記組織または前記臓器と前記医学的移植デバイスの間の接触表面積1cm 2 あたり約1μg~約100mgである、請求項62~78のいずれか一項記載の方法。
- 80創傷治癒物質を投与する工程をさらに含む、請求項62~79のいずれか一項記載の方法。
- 81前記創傷治癒物質が、デクスパンテノール;成長因子;酵素、ホルモン;ポビドンヨード;脂肪酸;抗炎症剤;抗生物質;抗菌剤;消毒剤;サイトカイン;トロンビン;鎮痛剤;オピオイド;アミノキシル;フロキサン;ニトロソチオール;ナイトレートおよびアントシアニン;ヌクレオシド、例えばアデノシン;ならびにヌクレオチド、例えばアデノシン二リン酸(ADP)およびアデノシン三リン酸(ATP);神経伝達物質/神経修飾物質、例えばアセチルコリンおよび5-ヒドロキシトリプタミン(セロトニン/5-HT);ヒスタミンおよびカテコールアミン、例えばアドレナリンおよびノルアドレナリン;脂質分子、例えばスフィンゴシン-1-リン酸およびリゾホスファチジン酸;アミノ酸、例えばアルギニンおよびリジン;ペプチド、例えばブラジキニン、サブスタンスPおよびカルシウム遺伝子関連ペプチド(CGRP);一酸化窒素;ならびにそれらの任意の組み合わせからなる群より選択される、請求項80記載の方法。
- 82前記医学的移植デバイスが、生体適合性で生分解性の材料から製造される、請求項62~81のいずれか一項記載の方法。
- 83前記医学的移植デバイスが、請求項1~21のいずれか一項記載の複合材料から製造される、請求項62~82のいずれか一項記載の方法。
- 84前記適用する工程が、宿主トランスグルタミナーゼの発現または活性を増加させることを含む、請求項62~83のいずれか一項記載の方法。
- 85それを必要とする対象において創傷治癒を促進する方法であって、 有効量のトランスグルタミナーゼを創傷表面に適用する工程、および 請求項1~21のいずれか一項記載の複合材料を含む創傷被覆材を、該創傷に接触させる工程を含む、方法。
- 86請求項1~21のいずれか一項記載の複合材料を含む発泡体を、前記創傷に適用する工程をさらに含む、請求項85記載の方法。
- 87前記創傷が、切傷および裂創、外科的切開、穿刺創、かすり傷、引っ掻き傷、圧迫傷、擦傷、摩擦創傷、慢性創傷、潰瘍、熱作用による創傷、化学的創傷、病原体感染に起因する創傷、皮膚移植片/移植ドナーおよびレシピエント部位、免疫反応状態、口腔創傷、胃または腸の創傷、損傷軟骨または損傷骨、切断部位、ならびに角膜病変からなる群より選択される、請求項85~86のいずれか一項記載の方法。
- 88前記トランスグルタミナーゼが哺乳動物トランスグルタミナーゼである、請求項85~87のいずれか一項記載の方法。
- 89前記トランスグルタミナーゼが微生物トランスグルタミナーゼ(mTgase)である、請求項85~87のいずれか一項記載の方法。
- 90前記トランスグルタミナーゼがカルシウム非依存性トランスグルタミナーゼである、請求項85~89のいずれか一項記載の方法。
- 91前記トランスグルタミナーゼが、第XIII因子A(フィブリン安定化因子)、1型トランスグルタミナーゼ(ケラチノサイトトランスグルタミナーゼ)、2型トランスグルタミナーゼ(組織トランスグルタミナーゼ)、3型トランスグルタミナーゼ(上皮トランスグルタミナーゼ)、4型トランスグルタミナーゼ(前立腺トランスグルタミナーゼ)、5型トランスグルタミナーゼ(トランスグルタミナーゼX)、6型トランスグルタミナーゼ(トランスグルタミナーゼY)、7型トランスグルタミナーゼ(トランスグルタミナーゼZ)、およびそれらの任意の組み合わせからなる群より選択される、請求項85~90のいずれか一項記載の方法。
- 92前記トランスグルタミナーゼが、溶液、エマルジョン、エアロゾル、発泡体、軟膏、ペースト、ローション、粉末、ゲル、ヒドロゲル、親水コロイド、マイクロ粒子、ナノ粒子、またはクリームとして製剤化される、請求項85~91のいずれか一項記載の方法。
- 93前記創傷被覆材が、包帯、ガーゼ、テープ、メッシュ、ネット、ばんそうこう、フィルム、メンブレン、パッチ、およびそれらの任意の組み合わせからなる群より選択される、請求項85~92のいずれか一項記載の方法。
- 94前記トランスグルタミナーゼが前記創傷被覆材に結合されている、請求項85~93のいずれか一項記載の方法。
- 95前記トランスグルタミナーゼが、前記創傷被覆材の表面にコーティングされている、請求項94記載の方法。
- 96前記トランスグルタミナーゼが、前記創傷被覆材に非共有結合により連結されている、請求項94~95のいずれか一項記載の方法。
- 97トランスグルタミナーゼの前記有効量が、創傷面積1cm 2 あたり約1μg~約100mgである、請求項85~96のいずれか一項記載の方法。
- 98創傷治癒物質を前記対象に投与する工程をさらに含む、請求項85~97のいずれか一項記載の方法。
- 99前記創傷治癒物質が、デクスパンテノール;成長因子;酵素、ホルモン;ポビドンヨード;脂肪酸;抗炎症剤;抗生物質;抗菌剤;消毒剤;サイトカイン;トロンビン;鎮痛剤;オピオイド;アミノキシル;フロキサン;ニトロソチオール;ナイトレートおよびアントシアニン;ヌクレオシド;ヌクレオチド;神経伝達物質/神経修飾物質、例えばアセチルコリンおよび5-ヒドロキシトリプタミン(セロトニン/5-HT);ヒスタミンおよびカテコールアミン、例えばアドレナリンおよびノルアドレナリン;脂質分子、例えばスフィンゴシン-1-リン酸およびリゾホスファチジン酸;アミノ酸、例えばアルギニンおよびリジン;ペプチド、例えばブラジキニン、サブスタンスPおよびカルシウム遺伝子関連ペプチド(CGRP);一酸化窒素;ならびにそれらの任意の組み合わせからなる群より選択される、請求項98記載の方法。
- 100前記適用する工程が、宿主トランスグルタミナーゼの発現または活性を増加させることを含む、請求項85~99のいずれか一項記載の方法。
- 101前記適用する工程が、前記医学的移植デバイスまたは前記創傷被覆材の接触前、接触後または接触中に行われる、請求項85~99のいずれか一項記載の方法。
Independent claims101
218 paragraphs, as filed
Related application The present application claims the benefits of 35 USC § 119 (e), US Patent Provisional Application No. 61 / 378,056, filed August 30, 2010, the entire contents of which are incorporated herein by reference in its entirety.
Field of invention The present invention relates to organic composites formed from carbohydrates and proteins. More specifically, the present invention relates to composite biocompatible materials formed from layers of chitosan and proteins such as fibroin, which have excellent strength and energy dissipation properties.
Background of the invention Chitin is the second most abundant polymer on the planet after cellulose, is a common waste in marine factories, and is biodegradable (as a natural polymer). However, attempts to manufacture it in the laboratory yield only hydrogel materials with poor mechanical properties.
Chitin is a polymer that is widely used in nature. It is found in the cell wall of fungi, the shell of mollusks and the exoskeleton of arthropods. It offers many structural applications due to its mechanical properties. Although many attempts have been made to use this polymer as an alternative to current synthetic plastics; it has not been possible to reproduce its special natural properties in the laboratory. The reason for unsuccessfulness is the lack of understanding of the important structural role played by chitin-related proteins present within natural structures and of the laminated microstructures of natural products produced by living organisms.
The main protein, present in both mollusc shells and arthropod exoskeletons and playing a fundamental role in the structural integrity of shells, has an amino acid sequence similar to silk fibroin.
The blend of chitin and protein (eg, silk fibroin) in the prior art is produced by mere mixing of both materials in solution. These processes focus on producing a homogeneous mixture of chitin / chitosan and silk fibroin by mixing both polymers in solution and casting the mixture. The approach does not improve the mechanical properties of the mixture over its constituents, and typically even produces fragile materials due to the interaction of both polymers that interfere with each other's molecular and crystal structures.
Silk fibroin is a well-known polymeric material. Silk offers important material choices in biomaterials and tissue engineering due to its impressive mechanical properties, biocompatibility and biodegradability. Silk polymers and silk fibroin include silk moth fibroin and insect or spider silk proteins (Lucas et al., Adv. Protein Chem 13: 107-242 (1958) (Non-Patent Document 1)). Preferably, fibroin is obtained from a solution containing dissolved silk moth silk or spider silk. In general, silk-derived fibroin polymers (or proteins) are treated to substantially remove sericin. The silk moth silk protein is obtained, for example, from Bombyx mori, and the spider silk thread is obtained, for example, from Nephila clavipes. Alternatively, silk proteins suitable for use in the present invention can be obtained from solutions containing genetically engineered silk, such as those derived from bacteria, yeast, mammalian cells, transgenic animals or transgenic plants. See, for example, WIPO Publication No. WO 1997/108315 (Patent Document 1) and US Pat. No. 5,245,012 (Patent Document 2), which are incorporated herein by reference.
Silk fibroin has excellent film-forming ability and is also compatible for use in the human body. Silk fibroin film dissolves in water without further manipulation or treatment due to the predominance of random coil protein structures. The structural features of this protein can be converted from random coils to β-sheet structures by a variety of treatments, including mechanical stretching, immersion in polar organic solvents or curing in water vapor. Without wishing to be bound by theory, it is also known that the use of high-concentration silk solutions facilitates the conversion of random coils to β-sheets. This structural transformation makes it insoluble in water, thereby providing the option of using this material in a range of biomedical and other applications. Some pure silk fibroin films tend to become stiff and brittle over time in the dry state, but exhibit impressive tensile strength, albeit with low ductility. In addition, the dissolved silk fibroin can be mixed with the particles to produce a homogeneous mixture capable of forming implantable structures. The silk polymer structure and the method for producing silk fibroin film are both described herein in WIPO No. WO 2009/0100280 (Patent Document 3) and WO 2010/0042798 (Patent Document 4), both incorporated herein by reference. ing.
<p><patcit num="1"><text>WO 1997/108315</text></patcit><patcit num="2"><text>U.S. Pat. No. 5,245,012</text></patcit><patcit num="3"><text>WO 2009/0100280</text></patcit><patcit num="4"><text>WO 2010/0042798</text></patcit></p>
<p><nplcit num="1"><text>Lucas et al., Adv. Protein Chem 13: 107-242 (1958)</text></nplcit></p>
The present invention relates to methods for the formation of complex 3D structures containing carbohydrate polymers such as oligosaccharides and polysaccharides, which have highly controlled shapes, topography and physical characteristics, as well as the resulting composites. Also, to improve certain characteristics by using silk fibroin and by coating different areas of the material with a water resistant coating for adjusting the hydration, eg, of the mechanical properties of the material. Concerning the continuous modification of those structures, including proteins, for restriction. The resulting composite has enhanced mechanical strength properties that are significantly higher than any of the constituent materials and unpredictable from them.
By practicing the present invention, one or more of the following capabilities may be provided.
One object of the present invention is to provide a method for producing composite materials formed from layers of carbohydrate-based polymers and proteins. For example, composites are formed from layers of chitin-based materials and proteins.
Another object of the present invention is to provide a method of making a composite material formed from a layer of carbohydrate-based polymer and fibroin. For example, a method of producing a composite material formed from a chitin-based material and a layer of fibroin.
Another object of the present invention is to provide a composite material formed from a carbohydrate-based polymer and protein and having excellent mechanical properties as compared with the material of its constituents. For example, composites are formed from chitin-based materials and proteins and have excellent mechanical properties compared to their constituent materials.
Another object of the present invention is to provide a composite material formed from chitosan and fibroin, which has excellent mechanical properties as compared with the material of its constituents.
Another object of the present invention is to provide composite materials with adjustable mechanical properties formed from carbohydrate-based polymers and proteins. For example, composites are formed from chitin-based materials and proteins and have adjustable flexibility properties.
Another object of the present invention is to provide a composite material with adjustable mechanical properties formed from chitosan and protein.
Another object of the present invention is to provide a biocompatible and biodegradable composite material formed from chitosan and protein that is stable in the presence of moisture.
These and other capabilities of the invention as well as the invention itself will be further understood by browsing the drawings, detailed description and claims below.
<figref num="1">FIG. 1A shows a diagram of a composite material according to the invention that mimics the natural laminated structure of insect cuticles and crustacean exoskeletons. Chitosan film (blue) is merged with a separate fibroin phase (yellow). FIG. 1B shows an image of a chitosan fibroin film named "Shrilk" according to the present invention (bar is 2.3 cm). Figure 1C shows typical stress-strain curves for Schrilk composite laminates (blue line, chitosan: fibroin weight ratio 1: 2), chitosan elemental (red line) and chitosan: fibroin 1: 2 blend (mixture). Shown. Figure 1D shows a graph of the toughness coefficient (gray, vertical axis on the left) and fracture strength (black, vertical axis on the right) of the Schrilk composite, chitosan, fibroin and fibroin-chitosan blends (with SD error bars).</figref><figref num="2">FIG. 2A shows the breaking strength of Schrilk composites with different chitosan: fibroin ratios manufactured according to the present invention. The dotted line represents the breaking strength of the chitosan film in the absence of protein. FIG. 2B shows a scanning electron microscope (SEM) image of the chitosan-fibroin contact surface in the Schrilk laminate. The darker material (top) corresponds to the chitosan layer and the lighter (bottom) is the fibroin layer (bar is 20 μm). Figure 2C shows a plot of hydrated sample weight against fibroin: chitosan content. The linear fitting presumes that the absorption of each phase is independent, indicating the absence of interaction effects between the polymer layers. The gradient of the linear fitting is 8.20 mg and the y-intercept is 18.89 mg. FIG. 2D shows a graph of mechanical strain at break points in dry (red) and water-saturated (blue) Schrilk composites manufactured according to the present invention (with SD error bars).</figref><figref num="3">FIG. 3A shows the topography of a Schrilk composite produced by depositing a protein layer on a microstructured chitosan film according to the present invention (bar = 100 μm). FIG. 3B shows a composite tube with a partially microstructured surface. One area of the protein layer is scratched, forming an open area (white arrow), so the chitosan layer beneath it is visible (bar = 1 mm). Figure 3C shows microtopography of the surface of Schrilk, showing the formation of structures in the fibroin protein layer (bar = 50 μm). Figure 3D shows the structured surface manufactured according to the present invention in higher magnification and in more detail (bar = 5 μm). FIG. 3E shows a multilayer material containing multiple repeating layers of chitosan and fibroin produced according to the present invention (1, 2 and 3 show three consecutive layers of chitosan fibroin laminate). ).</figref><figref num="4">FIG. 4A shows the FTIR spectra of chitosan (black) and protonated chitosan (gray). The molecule at the top represents a typical chitosan / chitin structure, in which the acetylglucosamine (left) and glucosamine (right) monomers represent chitin and chitosan, respectively. FIG. 4B shows the FTIR spectrum of the composite laminated material manufactured according to the present invention. Chitosan's strong polysaccharide structure (950 ~ 1850cm)<sup>-1</sup>) And fibroin-derived amides I and II (1640 and 1536 cm, respectively)<sup>-1</sup>) Are both clearly observable. FIG. 4C shows the FTIR spectra of fibroin (black) and fibroin (gray) in a composite laminate manufactured according to the present invention.</figref><figref num="5">An image of a comparison between a Schrilk composite produced as a foam or sponge structure in the form of a cylinder and chitosan alone is shown.</figref><figref num="6">FIG. 6A shows a mineralized foam composite structure manufactured according to the present invention. FIG. 6B shows an enlarged image of the porous material in the inset of FIG. 6A.</figref><figref num="7">Shown are pieces of tissue that have been subjected to different wound healing approaches. The tissues are bound by the use of foam, film or a combination of both.</figref><figref num="8">Shows a piece of tissue with an incision.</figref><figref num="9">The chitosan-based film (Schrilk) used to bond the separated tissue pieces is shown.</figref><figref num="10">It shows the deposition of transglutaminase (ie, white powder) on the tissue.</figref><figref num="11">Tissue closure using the chitosan-based film of FIG. 9 against transglutaminase-treated tissue is shown.</figref><figref num="12">The sample of FIG. 11 after 3 days is shown.</figref><figref num="13">The sample subjected to the same procedure as in FIGS. 10 to 12 except that a high concentration of fat was added to the sample is shown.</figref><figref num="14">The sample of FIG. 13 is cut in the lateral direction, and the film can be clearly confirmed in the figure.</figref><figref num="15">Shows a piece of tissue with a hole.</figref><figref num="16">The sample of FIG. 15 which was treated with transglutaminase and covered with a chitosan-based foam from above is shown.</figref><figref num="17">The insertion of a chitosan-based foam piece into the treated cavity is shown.</figref><figref num="18">A sample of FIG. 17 covered with a chitosan-based film (similar to FIG. 9) is shown. The region under the chitosan film was also treated with transglutaminase to promote cross-linking.</figref><figref num="19">The same sample as in FIG. 18, but after 3 days is shown. Samples were cut along the diameter of the cavity to observe foam / tissue binding.</figref><figref num="20">The same sample as in FIG. 19, but viewed from a different angle.</figref><figref num="21">A close-up image of the contact surface between the foam and the tissue is shown. It is also clearly observed that the film sticks to the foam.</figref><figref num="22">A close-up image of the contact surface between the foam and the tissue is shown. It is also clearly observed that the film sticks to the foam.</figref><figref num="23">An analysis of the adhesive strength of the film to biological tissue is shown. The tissue is the lumbar tissue of post-mortem domestic pigs (Sus domesticus). FIG. 23A shows an image of a piece of tissue covered with a chitosan fibroin film enzymatically attached to the tissue (as shown in the inset). Trench in the tissue piece was created to show that the film can easily follow complex geometry. FIG. 23B shows the removal of the film by pulling (T-peel test). The film is removed from right to left. The inset diagram shows the principle of the T-shaped peeling test. FIG. 23C shows the measured values obtained from the T-shaped peeling test. Figure 23D shows a 1 cm wide film (Shr + tTG) attached to the tissue by enzymatic adhesion, the average force required to peel off the film (Shr) just placed on the tissue without using a promoter, and by enzymatic adhesion. It is a bar graph showing the adhesive strength (tTg) of two tissue pieces glued together and the adhesive strength (Cyn) of a film by a cyanoacrylate-based glue (aka "super glue"). As you can see, enzyme bonding (Shr) + tTG) not only clearly exceeds the adhesive strength of natural tissues, but is also very close to the adhesive strength of cyanoacrylates, and both methods and materials are fully compatible and bioabsorbable.</figref><figref num="24">It is a bar graph showing that the parylene coating is an effective moisture barrier even under extreme conditions. The dry sample corresponds to a plain-coated Schrilk (standard condition) and "hydration" is in equilibrium with the aqueous environment (24-hour immersion). In that environment and in the presence of a coating as thick as only 1 micrometer, the strength of the sample is about 80% (84 MPa) of the strength under standard conditions.</figref><figref num="25">It is a bar graph which shows the adhesion to the dermis tissue (porcine). The final layer of epithelium is produced by keratinization, which involves intense (natural) treatment of this layer with transglutaminase. Therefore, this layer may be the only tissue in the subject that has no groups that can be used for binding by transglutaminase treatment. This was confirmed by the result that no binding by transglutaminase was observed. However, when the final layer was slightly damaged and the second layer was exposed, transglutaminase binding was successful, as demonstrated in experiments in which Schrilk bound to the dermis rather than the epithelium. In FIG. 25, Tg-1 to Tg-5: transglutaminase-treated sample; non-Tg-2: transglutaminase-untreated sample; and dermis + Tg: adhesion to the dermis in the presence of transglutaminase. This indicates that Schrilk can be used as a "patch" (eg, bandage) in the treatment of the skin.</figref>
Detailed description of the invention The present invention relates to composite materials formed from carbohydrate polymers and one or more proteins, and methods for producing useful structures from these composite materials. The present invention relates to composite materials that include layers of constituent materials. According to the present invention, complex 3D structures with highly controlled shapes, topography and physical characteristics can be produced from the resulting composites.
In some embodiments, the composite is [(protein layer).<sub>x</sub>: [(Carbohydrate layer)<sub>y</sub>: (Protein layer)<sub>z</sub>]<sub>m</sub>]<sub>n</sub>M, n, y and z are independently integers greater than 1 or 1; and x is 0 or greater than 1 or 1.
In general, n, m, y and z are 1-10 independently.<sup>6</sup>Is an integer of. For example, m, n, y and z are independently 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, respectively, It can be 18, 19 or 20. Similarly, x is 0 or 1-10<sup>6</sup>Can be an integer of. For example, x can be 0, 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19 or 20.
In some embodiments, the composite comprises one or more layers of carbohydrate layer: protein layer, eg, m is 1 and n is 1-10.<sup>6</sup>, X is 0, y is 1 and z is 1, and the composite is [Carbohydrate layer: Protein layer]<sub>n</sub>Has the structure of. In some embodiments, m is 1; n is 1, 2, 3, 4, 5, 6, 7, 8 or 9; x is 0; y is 1; and z is 1. Is.
In some embodiments, the composite comprises one carbohydrate layer and one protein layer, eg, m, n, y and z are 1, x is 0, and the composite is carbohydrate layer: protein. It has a layered structure.
In some embodiments, the composite comprises three carbohydrate layers and three protein layers, eg, m, y and z are 1, x is 0; n is 3 and the composite is. [Carbohydrate layer: Protein layer]<sub>3</sub>Has the structure of.
In some embodiments, the outermost layer of the composite is a protein layer, eg, m is 1-10.<sup>6</sup>N, x, y and z are all 1, and the composite is protein layer: (carbohydrate layer: protein layer)<sub>m</sub>Has the structure of.
In some embodiments, the composite comprises one carbohydrate layer and two protein layers, eg m, n, x, y and z are all 1, and the composite is protein layer: carbohydrate layer: protein. It has a layered structure.
In some embodiments, the composite comprises one carbohydrate layer and two or more protein layers, eg, m is 1 and n is 1-10.<sup>6</sup>, X is 0, y is 1, and z is 2 ~ 10.<sup>6</sup>And the composite material is [Carbohydrate layer: (Protein layer)<sub>z</sub>]<sub>n</sub>Has the structure of. In some embodiments, n is 1, x is 0, y is 1, and z is 2-10.<sup>6</sup>And the composite material is carbohydrate layer: (protein layer)<sub>z</sub>Has the structure of. In some embodiments, z is 2, 3, 4, 5, 6, 7, 8, 9 or 10.
In some embodiments, the composite is [(carbohydrate layer)<sub>p</sub>: [(Protein layer)<sub>q</sub>: (Carbohydrate layer)<sub>r</sub>]<sub>t</sub>]<sub>u</sub>P, q, r, t and u are independently integers greater than 1 or 1.
In general, p, q, r, t and u are independently 1-10.<sup>6</sup>Is an integer of. In some embodiments, p, q, r, t and u are independently 1, 2, 3, 4, 5, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13 , 14, 15, 16, 17, 18, 19 or 20.
In some embodiments, the outermost layer of the composite is a carbohydrate layer, eg p, q, r and u are 1 and t is 1-10.<sup>6</sup>And the composite material is carbohydrate layer: [protein layer: carbohydrate layer]<sub>t</sub>Has the structure of. In some embodiments, the composite comprises two carbohydrate layers and one protein layer, eg, p, q, r, t and u are all 1, and the composite is carbohydrate layer: protein layer: It has a carbohydrate layer structure.
The carbohydrate layer and the protein layer can have the same spread as each other or do not have the same spread. In other words, the entire surface of the carbohydrate layer can be coated with the protein layer, or only part of the surface of the carbohydrate layer can be coated with the protein layer.
According to one aspect of the invention, the continuous modification of the constituent carbohydrate-based materials and the production of composite structures with proteins can provide improvements in certain characteristics. In some embodiments, the resulting composite has significantly higher mechanical strength properties than any of its constituents. In some embodiments, the mechanical strength of the composite of the present invention is at least 2 times, at least 3 times, at least 4 times, at least 5 times, at least 10 times higher than the mechanical strength of any one of the constituent materials. , At least 15 times, at least 20 times, at least 25 times, at least 30 times, at least 40 times, at least 50 times, at least 100 times, at least 200 times, at least higher.
In some embodiments, the mechanical strength of the composite of the present invention is at least 1.2 times, at least 1.5 times, at least 10.75 times, at least 2 times, at least 3 times, at least the total mechanical strength of the constituent materials. 4x, at least 5x, at least 10x, at least 15x, at least 20x, at least 25x, at least 30x, at least 40x, at least 50x, at least 100x, at least 200x, at least higher.
Moreover, the composites of the present invention have a very low density. In some embodiments, the density of the composite is 2 g / cm.<sup>3</sup>Less than 1.9 g / cm<sup>3</sup>Less than 1.8 g / cm<sup>3</sup>Less than 1.7 g / cm<sup>3</sup>Less than 1.6 g / cm<sup>3</sup>Less than 1.5 g / cm<sup>3</sup>Less than 1.4 g / cm<sup>3</sup>Less than 1.3 g / cm<sup>3</sup>Less than 1.2 g / cm<sup>3</sup>Less than 1.1 g / cm<sup>3</sup>Less than 1 g / cm<sup>3</sup>Less than 0.9 g / cm<sup>3</sup>Less than 0.8 g / cm<sup>3</sup>Less than 0.7 g / cm<sup>3</sup>Less than 0.6 g / cm<sup>3</sup>Less than 0.5 g / cm<sup>3</sup>Less than 0.4 g / cm<sup>3</sup>Less than 0.3 g / cm<sup>3</sup>Less than 0.2 g / cm<sup>3</sup>Less than 0.1 g / cm<sup>3</sup>Less than or 0.05 g / cm<sup>3</sup>Is less than.
The density of the composite material can be calculated as described in ASTM Standard D792-00. Composite material g / cm according to ASTM standard D792-00<sup>3</sup>Density (ρ) is<img file="JP2013536734A_D0001.tif" />And in the ceremony, W<sub>a</sub>Is the weight of the specimen when suspended in the air; W<sub>w</sub>Is the weight of the partially immersed specimen holding wire; W<sub>b b</sub>Is the weight of the specimen when fully immersed in distilled water, in addition to the partially immersed specimen holding wire; and ρ<sub>water</sub>Is g / cm of distilled water under test temperature<sup>3</sup>Density (eg 0.9975 g / cm at 23 ° C)<sup>3</sup>). Although the above is related to water, other liquids can be used instead of water. Instead of or in addition to the above, density gradient techniques for measuring the density of plastics can also be used, as described in ASTM Standard D1505.
The density of the composite can be measured under any suitable temperature and pressure. In some embodiments, the density of the composite is measured at temperatures in the range 0 ° C to 25 ° C. For example, the density can be measured at 0 ° C, 5 ° C, 10 ° C, 15 ° C, 20 ° C or 25 ° C. In some embodiments, the density of the composite is measured under a pressure of 100 kPa or 101.325 kPa.
In some embodiments, the density of the composite is under standard conditions of temperature and pressure. Standard conditions for temperature and pressure, without limitation, may be those defined by the International Union of Pure and Applied Chemistry (IUPAC) or the National Institute of Standards and Technology (NIST). The current version of the IUPAC standard has a temperature of 0 ° C and an absolute pressure of 100 kPa, and the NIST version has a temperature of 20 ° C and an absolute pressure of 101.325 kPa.
In some embodiments, the density is 25 at 0 ° C and 100 kPa, at 0 ° C and 101.325 kPa, at 15 ° C and 101.325 kPa, at 20 ° C and 101.325 kPa, at 25 ° C and 101.325 kPa. Measured at ° C and 100 kPa, at 20 ° C and 100 kPa, at 15 ° C and 100 kPa, or at 20 ° C and 101.3 kPa.
In some embodiments, the composite material comprises an exterior waterproof coating. As used herein, the term "waterproof" refers to a barrier against both liquid and gaseous water (ie, against both liquid water and water vapor). Waterproof coatings typically have a permeability of less than 1 as measured by the Water Vapor Transmission Test ASTM E96. Exemplary water repellent materials include parylene, polydimethylsiloxane, polyethylene, polyvinyl, polypropylene, polyester, latex, oil, organic solvents, waxes, lipids, fatty acid esters, sterol esters, long chain alcohols, myricyl palmitate, Includes, but is not limited to, cetyl palmitate, lanolin, candelilla wax, olicury wax, sugar cane wax, estero wax, jojoba oil, paraffin, and any combination thereof.
The composite material is made by immersing the composite material in an organic solution (eg, a solution of a water repellent material) and / or protecting some areas from hydration (eg, a pattern of water repellent wax material). It can be coated with a waterproof layer by allowing hydration otherwise (by microcontact printing on the surface of the). Organic solutions usually have an affinity for carbohydrate and / or protein layers. In some embodiments, the organic solution comprises a wax or wax and protein. Alternatively, the composite can be waterproofed by depositing a layer of waterproof material on at least one surface of the composite. In some embodiments, the composite is coated by vapor deposition of a waterproof material. Waterproof materials are sensitive to water contact next to areas that are insensitive to water contact in order to form composite materials that vary in mechanical properties and degradability on the surface of the composite material. It can also be patterned to form a region of.
In some embodiments, at least one surface of the composite comprises an outer coating of parylene (eg, one or more layers). Parylene is the trade name for various chemically vapor deposition poly (p-xylylene) polymers, which are USP Class VI biocompatible polymers. Exemplary parylenes include, but are not limited to, parylenes A, AF-4, AM, C, D, E, HT, N, SF and X. Of the three most common types of parylene (C, D and N), parylene C is the most widely used in the industry. The advantages of using parylene are its proven biocompatibility, its strength and flexibility (eg Young's modulus = 4 GPa), its adaptable and pinhole-free room temperature deposition, its low dielectric constant (= 3). ) And high volume resistivity (> 1016) Q-cm), its transparency, and its ease of operation with standard microfabrication techniques. Therefore, parylene coatings can be used to form biocompatible and waterproof coatings on composites. The parylene coating can be patterned to form a hydrophobic or biocompatible region next to the non-hydrophilic or non-biocompatible region. Without wishing to be bound by theory, this allows the formation of composites that vary in biocompatibility, mechanical properties or degradability on the surface of the composite.
<u style="single">Carbohydrate polymer</u> As used herein, the term "carbohydrate-based polymer" is C.<sub>m</sub>(H<sub>2</sub>O)<sub>n</sub>Including, but not limited to, oligomers or polymers comprising monomers in which m and n are 3 and m and n may be the same or different. Preferably, m and n are independently 3, 4, 5, 6 or 7. Carbohydrate-based polymers include, but are not limited to, oligosaccharides, polysaccharides, glycoproteins, glycolipids, and similar compounds.
In some aspects of this and other aspects of the invention, the carbohydrate polymer comprises at least 5, at least 6, at least 7, at least 8, at least 9 or at least 10 sugar monomers.
Carbohydrate polymers include, but are not limited to, erythrose, treose, ribose, arabinose, xylose, lyxose, ribulose, xylulose, allose, altrose, glucose, mannose, growth, idose, galactose, galactosamine, N-acetylgalactose. , Glucosamine, N-acetylglucosamine, sialic acid, talose, psicose, fructose, sorbose, tagatos, fucose, fuclaus, ramnorth, sedhepturose, octose, sulfoquinobos, and nonose (neuramic acid). These sugars may be optionally substituted. Each sugar, but not limited to, can independently have an L or D conformation.
The linkage between the two sugar monomers can independently have an α or β structure. In addition, the linkage between the two sugars can be 1 3, 1 4, 1 5 or 1 6.
In some embodiments, the hydroxyl of at least one (eg, 1, 2, 3 or 4) of the sugar monomer is substituted with an amino group. In some embodiments, the hydroxyl at the 2-position of the sugar monomer is replaced with an amino group. Amino group is optional, C<sub>1</sub>~ C<sub>6</sub>It can be substituted with an alkyl or acyl group. Preferred C<sub>1</sub>~ C<sub>6</sub>Alkyl groups include methyl, ethyl, propyl, butyl and t-butyl. One preferred acyl group is acetyl.
In some aspects of this and other aspects of the invention, the carbohydrate polymers are sucrose, lactulose, lactose, maltose, trehalose, cellobiose, kojibiose, nigerose, isomaltose, β, β-trehalose, α, β-trehalose, Sophorose, laminaribiose, gentibiose, trehalose, maltulose, palatinose, gentibiulose, mannobiose, melibiose, rutinose, rutinulose, xylobiose, raffinose, meregitos, carbose and staquiose Includes one or more (eg, 1, 2, 3, 4, 5, 6, 7, 8, 9 or 10 or more) disaccharide monomers, trisaccharide monomers or sucrose monomers.
As used herein, the term "oligosaccharide" refers, but is not limited to, several (eg, 5-10) monosaccharide units linked by covalent bonds. As used herein, the term "polysaccharide" refers, but is not limited to, a large number (eg, 11 or more) of covalently linked sugar units. Polysaccharides can have molecular weights ranging from millions of daltons. Exemplary oligosaccharides and polysaccharides include fructo-oligosaccharides, galactooligosaccharides, mannan oligosaccharides, glycogens, starches (amylase, amylopectin), glycosaminoglycans (eg, hyaluronic acid, chondroitin-4-sulfate, chondroitin-6-sulfate). , Dermatin sulphate, keratin sulphate, heparin and the like), cellulose, β-glucan (zymosan, lentinan, cizophyllan), maltodextrin, inulin, levan β (2 6), chitin and chitosan, but limited to these Not done.
In some aspects of this and other aspects of the invention, the carbohydrate polymer is chitin or a derivative thereof. One preferred chitin derivative is chitosan (α- (1-4) 2-amino-2-deoxy-β-D-glucan) and its derivatives. Exemplary chitosan derivatives include N- (aminoalkyl) chitosan, succinyl chitosan, quaternary aminoated chitosan, N-acylated chitosan (eg, caproyl chitosan, octanoyl chitosan, myristyl chitosan and palmitoyl chitosan), N. -Methylenephosphonate chitosan, N-lauryl-N-methylenephosphonate chitosan, N-lauryl-carboxymethyl chitosan, N-alkyl-O-sulfated chitosan, thiolated chitosan (eg chitosan-2-iminothiorane, chitosan-4) -Thiobutylamidine and chitosan-thioglycolic acid), as well as but not limited to phosphorylated chitosan.
Synthetic methods that can be used to synthesize carbohydrate polymers are well known to those of skill in the art. For example, Stick, RV, Carbohydrates: The Sweet Molecules of Life .; Academic Press, pp 113-177 (2002); Crich, D. and Dudkin V., J., the entire contents of which are incorporated herein by reference. Am. Chem. Soc., 123: 6819-6825 (2001); Garegg, PJ, Chemtracts-Org. Chem., 5: 389 (1992); Mayer, TG, Kratzer, B. and Schmidt, RR Synthesis of a GPI anchor of the yeast Saccharomyces cerevisiae. Angew. Chem. Int. Ed. Engl. 33, 2177-2181 (1994); Seifert, J., Lergenmuller, M. and Ito, Y. Synthesis of an α- (2,3) -sialylated complex-type undecasaccharide. Angew. Chem. Int. Ed. 39, 531-534 (2000); Wang, Z.-G. Et al. Toward fully synthetic homogeneous glycoproteins: a high mannose core containing glycopeptide containing carrying full H-type 2 human blood group specifity. Angew. Chem. Int. Ed. 40, 1728-1732 (2001); Caruthers, MH Gene synthesis machines: DNA chemistry and its uses. Science 230 , 281-285 (1985); Sears, P. and Wong, C.-H. Toward automated synthesis of oligosaccharides and glycoproteins. Science 291, 2344-2350 (2001); Zhang, Z. et al. Programmable one-pot oligosaccharide synthesis. J. Am. Chem. Soc. 121, 734-753 (1999; Nishimura, S. Automated glycosynthesizer'Golgi' by mimicking biosynthetic process. Tanpakushitsu Kakusan Koso 48, 1220-1225 (2003); Plante, OJ, Palmacci, ER and Seeberger, PH Automated solid-phase synthesis & oligosaccharides. Science 291, 1523-1527 (2001); Andrade, RB, Plante, OJ, Melean, LG and Seeberger, PH Solid-phase oligosaccharide synthesis: preparation of complex structures using a novel linker and different glycosylating agents. Org. Lett. 1, 1811-1814 (1999); Love, KR and Seeberger, PH Automated solid-phase synthesis of protected tumor-associated antigen and blood group determinant oligosaccharides. Angew. Chem. Int. Ed. 43, 602-605 (2004); and Seeberger , PH and Werz, DB See Synthesis and medical applications of oligosaccharides. Nature 446, 1046-1051 (2007).
<u style="single">protein</u> Almost any protein that can be induced to form an ordered structure, eg, from a random coil and / or helical structure to a β-sheet, can be used in the production of the composites of the present invention. Proteins can be converted from random coils to β-sheet form by heating, mechanical stretching, immersion in organic solvents such as ethanol, methanol and curing in steam. For example, Hu et al., 41 Macromolecules 3939-48 (2008); Jin and Kaplan, 424 Nature 1057-61 (2003); Canetti et al., 28 Biopolymers-, the entire contents of which are incorporated herein by reference. Peptide Sci. § 1613-24 (1989); and Jin et al., 15 Adv. Funct. Mat. See 1241-47 (2005). In some cases, the use of high-concentration protein solutions can also promote the transition from random coils to β-sheets. Without wishing to be bound by theory, this transfer of structure imparts water insolubility, thereby providing the option of using such materials within the scope of biomedical and other applications, such as sensor platforms. To do. See, for example, Zhang, 16 Biotechnol. Adv. 961-71 (1998), the contents of which are incorporated herein by reference.
In some embodiments, the protein is a silk protein or an analog or derivative thereof. In some embodiments, the silk protein is fibroin. The silk protein can be a naturally occurring silk protein, such as silk extracted from silk moth cocoons, or a silky protein or polymer. Many silky proteins and polymers are known in the art and they fit the present invention. For example, Asakura et al., Production and characterization of a silk-like hybrid protein, based on the polyalanine region of Samia cynthia ricini silk fibroin and a cell adhesion region derived from fibronectin, the entire contents of which are incorporated herein by reference. , Biomaterials, 25 (4): 617-624 (2004); Yang, M. and Kawamura, J. Development of silk-like materials based on Bombyx mori and Nephila clavipes dragline silk fibroins, Polymer, 50 (1): 117-124 (2009); Barr, LA, Fahnestock SR, and Yang, J. Production and purification of recombinant DP1B silk -like protein in plants, Molecular Breeding, 13 (4): 345-356 (2004); Anderson, JP, Cappello, J., and Martin, DC Morphology and primary crystal structure of a silk-like protein polymer synthesized by genetically engineered Escherichia coli bacteria, Biopolymers, 34 (8): 1049-1058 (2004); Huang, J. Foo, CWP, and Kaplan, DL Biosynthesis and Applications of Silk-like and Collagen-like Proteins, Polymer Reviews, 47 (1) 29-62 (2007); Yao, J. and Asakura, T. Synthesis and Structural TEXT of Silk-Like Materials Incorporated with an Elastic Motif, J. Biochem .. 133 (1): 1147-1154 (2003); Yang et al., Silklike materials constructed from sequences of Bombyx mori silk fibroin, fibronectin, and elastin, J. Biomed. Mater. Res. Part A, 84A (2): 353 -363 (2007); and Werten et al., Biosynthesis of an Amphiphilic Silk-Like Polymer, Biomacromolecules, 9 (7): 1705-1711 (2008). Hardy and Scheible are a review of silk-inspired polymers and proteins in Hardy, JG and Scheibel, TR Biochem. Soc. Trans. 36: 677-681 (2009), the contents of which are incorporated herein by reference. Is provided.
Without wishing to be bound by theory, silk fibroin has excellent film-forming ability, is biocompatible, and is acceptable for use in the human body. Altman et al., 24 Biomats. 401-16 (2003); Vepari and Kaplan, 32 Prog. Polym. Sci. 991-1007 (2007). Silk fibroin films, like human skin, have good dissolved oxygen permeability in wet conditions, suggesting potential uses for these films in wound dressings and artificial skin systems. Minoura et al., 11 Biomats., 430-34 (1990); Minoura et al., 31 Polymer, 265-69 (1990a). However, films formed from silk fibroin are soluble in water without further manipulation due to the predominance of random coil protein structures.
In addition, the structural features of silk fibroin can be converted from random coils to β-sheet morphology by heating, mechanical stretching, immersion in organic solvents such as methanol, ethanol and curing in steam. Silk fibroin can also be induced to form β-sheets by using a high concentration fibroin solution.
In some aspects of the aspects described herein, the protein is perculin, abductin, fibron, fibronectin, elastin, recillin, fibronectin, fibrinogen, keratin, titin, collagen, actin, Arp2 /. 3. Consists of coronin, dystrophin, FtsZ, myosin, spectroline, tau (protein), tuberin, F-spondin, picaturin, their protein fragments, synthetic peptides, gene expression moieties of proteins, fragments and any combination thereof. Selected from the group.
The characteristics of the composite can be adjusted, eg, enhanced, by using a non-silk protein or non-silk protein protein, a mixture of proteins, and / or by incorporating a non-protein molecule into the protein layer. .. For example, elastin or resilin can be used in the protein layer or added to the carbohydrate and / or protein layer to increase elasticity. Similarly, pericin can be used in the protein layer or added to the carbohydrate and / or protein layer to improve mineralization.
In some aspects of the aspects described herein, the composite material is a carbon fiber, carbon nanotube, glass fiber, small molecule, polymer, protein in at least one layer of the carbohydrate layer or protein layer of the composite material. , Peptides, peptide mimetics, nucleic acids, organic compounds, inorganic compounds, crystalline compounds, biological compounds, bioactive compounds, bioactive compounds, and biological, pharmaceutical or therapeutic agents, and them. Includes molecules selected from the group consisting of any combination of.
<u style="single">Composite material synthesis</u> The composite material of the present invention can be prepared by alternately preparing a carbohydrate layer and a protein layer on a suitable surface. Carbohydrate-based substrates, such as films, can first be prepared by drying a carbohydrate solution (eg, a carbohydrate polymer solution). In some embodiments, the carbohydrate-based substrate is contained in an acidic solution. Some exemplary acids include itaconic acid, polyitaconic acid, aconitic acid, uric acid, glucuronic acid, formic acid, acetic acid, trichloroacetic acid, propionic acid, butanoic acid, 4-chlorobutanoic acid, 3-chlorobutanoic acid, 2-Bromobutanoic acid, 2-Chlorobutanoic acid, chloric acid, hypochlorous acid, citric acid, gluconic acid, lactic acid, oxalic acid, tartaric acid, ascorbic acid, merdrum acid, hydrofluoric acid, hydrocyanos, hydrogen sulfide, orthrin Includes, but is not limited to, acids, sulfites, carbonates, and weakly base conjugated acids. The acid concentration in solution can be in the range of about 0.1% w / v to about 10% w / v, without limitation. In some embodiments, the solution comprises from about 1% w / v to about 2% w / v of acid. In some embodiments, the acid is 10 at 25 ° C.<sup>-2</sup>It is a weak acid having an acid dissociation constant (Ka) of less than. In some embodiments, the acid is acetic acid.
The prepared carbohydrate substrate can be washed, further modified and / or neutralized. Depending on the specifications of the substrate prepared, an acidic or basic solution can be used to modify and / or neutralize the substrate. Exemplary bases include sodium hydroxide, ammonium hydroxide, potassium hydroxide, calcium hydroxide, magnesium hydroxide, barium hydroxide, strontium hydroxide, lithium hydroxide, rubidium hydroxide, sodium carbonate and ammonia. However, it is not limited to these. The base concentration in the neutralizing solution can be in the range of about 0.1% w / v to about 10% w / v, without limitation. In some embodiments, the solution contains about 4% w / v to about 6% w / v of base. In some embodiments, the neutralizing solution is a pH buffer, such as a high pH carbonate buffer. High pH buffer means a buffer having a pH of 7, 8, 9, 10, 11 or 12 or higher.
If necessary, any residual water molecule can be removed from the carbohydrate substrate using methods known to those of skill in the art for that purpose. For example, the film can be washed with an organic solvent such as alcohol, such as methanol, ethanol and the like. In addition, methods of preparing carbohydrate films are well known in the art and can be used to prepare such films. For example, Ito, R. and Matsuo, Y. Eds. Handbook of Carbohydrate Polymers: Development, Properties and Applications, Nova Science Pub. Inc. (2010); and Richert et al, the contents of which are incorporated herein by reference. ., Langmuir, 20 (2): See 448-58 (2004).
The carbohydrate substrate can then be coated with a layer of protein by immersing it in a protein solution. Alternatively, the carbohydrate substrate can be coated with a layer of protein by depositing a layer of protein solution on it. Generally, any protein-to-carbohydrate ratio, such as weight or molar ratio, can be used to adjust the overall composition of the composite. In some embodiments, the carbohydrate to protein ratio is 10: 1 to 1:10. In some embodiments, the carbohydrate to protein ratios are 5: 1 to 1: 5, 2.5: 1 to 1: 2.5, 1.15: 1 to 1: 1.15. In some embodiments, the ratio is 1: 1.5 to 1: 2.5. In some embodiments, the ratio is 1: 2. The ratio can be based on the dry weight or molar amount of carbohydrates and proteins added to the solution for the formation of each layer.
In general, carbohydrate solutions contain from about 1% w / v to about 50% w / v of carbohydrate polymers. In some embodiments, the carbohydrate solution comprises from about 1% w / v to about 25% w / v of carbohydrates. In some embodiments, the carbohydrate solution comprises from about 2% w / v to about 6% w / v of carbohydrates. Although not bound by theory, in some embodiments a high concentration carbohydrate solution is used. For example, in some embodiments, the carbohydrate solution comprises from about 50% w / v to about 95% w / v of carbohydrates. In some embodiments, the carbohydrate solution comprises from about 75% w / v to about 85% w / v of carbohydrates.
Like carbohydrate solutions, protein solutions contain about 1% w / v to about 50% w / v of protein. In some embodiments, the protein solution comprises from about 1% w / v to about 25% w / v of protein. In some embodiments, the protein solution comprises from about 2% w / v to about 6% w / v of protein.
The protein layer can optionally be treated to induce changes in its protein structure, such as from fibrous to crystalline, from α-helical to β-sheets and vice versa. For example, the protein layer can be treated to induce the formation of crystal structures. In some embodiments, the protein layer can be treated to induce the formation of β-sheets or similar structures. In some embodiments, the protein layer is treated to induce β-transition. Illustrative methods of inducing changes in protein structure include the use of high-concentration protein solutions, heating, freezing, mechanical stretching, pressure, immersion or washing with organic solvents such as ethanol, methanol, and curing in steam. Includes, but is not limited to.
The protein layer itself can be constructed on a layer-by-layer basis. For example, the carbohydrate substrate can be coated with a first protein layer. The carbohydrates so coated can then be coated with a second layer of the same or different proteins. This process can be repeated until the overall protein layer reaches the appropriate thickness. After coating each protein, the protein layer can optionally be treated to induce changes in protein structure, as described above.
Generally, the composite has a thickness of about 1 to about 500 μm. In some embodiments, the composite material is about 1 to about 250 μm, about 1 to about 150 μm, about 1 to about 100 μm, about 1 to about 75, about 1 to about 50 μm, about 1 to about 25 μm, about 1 to about 1 to about. It has a thickness of 20 μm, about 1 to about 15 μm, about 1 to about 10 μm, or about 1 to about 5 μm.
The thickness of each of the carbohydrate and protein layers in the composite can independently range from a few angstroms to a few millimeters, eg, about 1 Å to about 5 mm. In some embodiments, the thickness of each carbohydrate layer can independently range from about 1 to about 250 μm. In some embodiments, the thickness of each carbohydrate layer is independently about 1 to about 100 μm, about 1 to about 75 μm, about 1 to about 50 μm, about 1 to about 40 μm, about 1 to about 30 μm, about 1 to about 1 to. It is selected from the group consisting of about 25 μm, about 1 to about 20 μm, about 1 to about 15 μm, about 1 to about 10 μm and about 1 to about 5 μm. In some embodiments, all carbohydrate layers have the same thickness. In some embodiments, at least two carbohydrate layers have different thicknesses.
Similarly, the thickness of the protein layer in the composite can also independently range from a few angstroms to a few millimeters, eg, about 1 Å to about 5 mm. In some embodiments, the thickness of each protein layer is independently from about 1 to about 250 μm. In some embodiments, the thickness of each protein layer is independently about 1 to about 100 μm, about 1 to about 75 μm, about 1 to about 50 μm, about 1 to about 40 μm, about 1 to about 30 μm, about 1 to about 1 to. It is selected from the group consisting of about 25 μm, about 1 to about 20 μm, about 1 to about 15 μm, about 1 to about 10 μm and about 1 to about 5 μm. In some embodiments, all protein layers have the same thickness. In some embodiments, at least two protein layers have different thicknesses.
In some embodiments, the thickness of the protein layer is about 0.1 × to about 5 × of the thickness of the carbohydrate layer. In some embodiments, the thickness of the protein layer is about 0.25x, about 0.5x, about 0.75x, about 1x, about 1.25x, about 1.5x, about 1.75x, about 2 of the thickness of the composite carbohydrate layer. ×, about 2.5 × or about 5 ×.
In some embodiments, all layers of the composite have the same thickness. In some embodiments, at least two layers of the composite have different thicknesses. At least two layers with different thicknesses can be layers of the same constituents (eg, carbohydrate or protein layers) or at least one carbohydrate layer and at least one protein layer.
In one non-limiting example, the composite material is formed by preparing a chitosan film. Chitosan films can be prepared by drying a chitosan solution in an acid, eg acetic acid, and neutralizing the film with, for example, NaOH. The chitosan film is optionally dehydrated with, for example, methanol, which promotes the liberation of intermolecular water molecules. The resulting dried chitosan film may have low hydration and high brittleness. However, the combination of a chitosan film and a coating of a protein, such as fibroin, by immersing the chitosan film in an aqueous solution of fibroin, for example, by drying the resulting composite material produces a composite laminated film with significantly improved strength properties. Will be done. According to one aspect of the invention, the chitosan film is combined with fibroin in a fibroin: chitosan ratio in the range of approximately 1: 1 to 4: 1 (preferably 2: 1.5 to 2: 1) (w / w). If so, the resulting composite exhibits significantly higher strength properties than chitosan alone.
According to an alternative embodiment of the present invention, the composite material can be made from intermediate molecular weight chitosan. Chitosan material (Sigma Aldrich) with medium molecular weight and high degree of deacetylation can be dissolved in 1% v / v acetic acid at 2% w / v. 6 ml of the resulting solution can be poured into a 9 cm diameter Petri dish and the solvent evaporated at 37 ° C. To neutralize the protonated amino groups and avoid further dissolution, the resulting film can be immersed in NaOH 4% (w / v) for a time of 5-15 minutes, eg 10 minutes. To remove residual NaOH, the resulting chitosan film can be thoroughly washed in deionized (DI) water and then optionally dried at 37 ° C. The final thickness of chitosan can be in the range of 7-13 μm, eg 10 μm.
<u style="single">Manufacture of chitosan fibroin laminated composites:</u> According to one aspect of the invention, already sericin-depleted Bombix moly-derived silk available from Mielke's Fiber Arts (USA) is used to form the protein layer. After washing the silk several times in DI water, it can be dissolved in 80% (w / v) LiBr at 60 ° C for 6 hours to 10% w / v. The melted silk can be dialyzed against water in a dialysis tube (VWR Scientific, USA) with a molecular weight cutoff of 12-14 kDa. Dialysis can be performed for 3, 4 or 5 days, changing water at regular intervals. The final concentration of fibroin is weighed (XS205, Mettler Toledo, It can be measured by USA). The resulting fibroin concentration can be in the range of 2-6%, eg about 4% (w / v). An alternative method of making an aqueous silk fibroin solution is described in detail in WIPO Publication No. WO 2005/012606 entitled "Concentrated Aqueous Silk Fibroin Solution and Use There of", which is incorporated herein by reference.
The fibroin solution can be deposited on a chitosan film fixed to the bottom of a 9 cm diameter Petri dish and dried at 37 ° C. The resulting composite film can be immersed in methanol for 25-35 minutes, eg 30 minutes, for β-transfer of the protein (and to prevent further lysis), and it can be washed with DI water. it can. In other embodiments, β-transition can also be induced by other inducing factors, including alcohol, organic solvents, aqueous solutions, pressure application and / or heat application.
Figures 1A and 1B show samples of composites according to the present invention. FIG. 1A shows a diagram of a composite material according to one aspect of the invention, in which a chitosan film (blue) is bonded to a fibroin layer (green), mimicking a natural laminated structure and insects. Cuticles and crustacean exoskeletons are provided along with their new mechanical properties. FIG. 1B shows an image of the composite laminate, which in this example is a thin (15 μm) transparent film (bar 2.3 cm).
<u style="single">Microtopography</u> According to aspects of the invention, a pre-defined microtopography of the resulting composite film is a polydimethoxysilane (PDMS) template of the protein solution (produced by casting the polymer on a structured silicon surface). And can be formed by casting between a flat carbohydrate layer or film. The composite is then processed to induce changes in protein structure, such as from fibrous to crystalline, from α-helical to β-sheets and vice versa. For example, the protein layer can be treated to induce the formation of crystal structures. In some embodiments, the protein layer can be treated to induce the formation of β-sheets or similar structures. In some embodiments, the protein layer, it induces β transition is processed cormorants. The composite can be dried and removed from the mold.
In a non-limiting example, the pre-defined microtopography of the resulting composite film is a polydimethoxysilane (PDMS) template of the fibroin solution (produced by casting the polymer on a structured silicon surface). It can be formed by casting between and a flat chitosan film. Moisture can be evaporated at 37 ° C for several hours and the composite can be removed from the mold. As with the unstructured composites, the samples were treated with methanol for β conversion and washed with DI water.
According to aspects of the invention, the resulting composite film microtopography can be produced by depositing proteins on a structured carbohydrate film. Carbohydrate films can be structured by known methods, for example, by drying a solution of carbohydrates on a PDMS template. The structured carbohydrate film can then be further processed as described herein to produce a structured composite material according to the present invention.
In one non-limiting example, microtopography of the resulting composite film can be produced by depositing a fibroin protein on a structured chitosan film. Chitosan films can be structured by known methods, for example, by drying chitosan in solution on a PDMS template. Structured chitosan can be further processed as described herein to produce a structured composite material according to the present invention.
FIG. 3 shows casting according to an aspect of the present invention. FIG. 3A shows the topography of a composite material formed according to the present invention by depositing a protein phase on a structured chitosan film (bar = 100 μm). FIG. 3B shows a tube of composite material according to the invention, with a portion of the surface structured and a portion of the surface unstructured. The white arrow points to the opening on the protein layer, through which the chitosan layer below is visible (bar = 1 mm). FIG. 3C shows a topography of a composite material formed according to aspects of the invention with a structured surface formed on fibroin (bar = 50 μm). Figure 3D shows in more detail the structured surface of Figure 3C. The horizontal band on the wall is a replica of the deep reactive ion etching marks on the mold (bar = 5 μm). FIG. 3E shows SEM images of multiple layers of a multilayer composite chitosan fibroin material formed according to aspects of the invention. The numbers between the lines represent three different chitosan layers (bar = 50 μm).
<u style="single">Stress / strain measurement</u> A dried composite sample was cut into 1.5 cm wide and 8 cm long strips and tested using Instron 3342 (500N, Instron, USA). The thickness of the sample was measured using a microscope (Axio Observer, Zeiss, Germany) as the average of five different points on the film. Thickness measurements were also backed up in the samples submitted for SEM analysis.
FIG. 1C shows a stress-strain curve comparing the composite material and the individual constituents according to the present invention. As shown, the strength of the 1: 2 ratio composite chitosan-fibroin laminate, referred to herein as "Schrilk", is produced by mixing chitosan or both chitosan and fibroin in the liquid phase. Much higher than the non-laminated chitosan fibroin blend. Fibroin film is very brittle (data not shown in Figure 1C) and has a low fracture strength of 3.14 MPa (shown in Figure 1C). Figure 1D shows the toughness coefficients and break points of the composite Schrilk material and its constituent materials. As shown, both the toughness coefficient and the breaking point of the composite laminated Schrilk material are much higher than either chitosan, fibroin or unstructured chitosan fibroin blends.
FIG. 2A shows the strength characteristics with respect to the chitosan to fibroin ratio in the composite laminate. FIG. 2A shows that the fracture strength of the composite material is significantly higher than the fracture strength of chitosan alone when the chitosan to fibroin ratio is 1: 2. FIG. 2B shows an SEM image of the chitosan-fibroin contact surface in the laminated composite.
As mentioned above, composites manufactured according to the present invention have the same constituents and amounts as the blend, but composites that mimic the natural structure (eg, those in insect cuticles) are nearly 10 times higher. The strength of. Moreover, surprisingly, the combination of chitosan and fibroin in a particular composition of "Schrilk" composite laminates is almost twice as strong as the strongest constituent (ie, chitosan). The energy per unit volume that each material can absorb before breaking (ie, toughness factor, Figure 1D) further illustrates the unexpected properties of chitin / protein composites according to the present invention. Although it may be predictable that the addition of extremely brittle materials to chitosan, such as fibroin, will result in materials that are weaker than chitosan but stronger than fibroin (eg, blends), the resulting "Schrilk" composite laminates are pre-breakable. It absorbs 1.5 times more energy than chitosan.
Therefore, before breaking, the composite material is at least 1.2 times, at least 1.3 times, at least 1.4 times, at least 1.5 times, at least 2 times, at least 3 times, at least 4 times, at least 5 times, than the film of the constituent carbohydrates. It can absorb at least 10 times, at least 50 times, and at least 100 times more energy.
Compared to common materials, the ultimate strength of 120MPa for composite materials is twice that of nylon and comparable to aluminum. However, since the density of this composite is approximately 1.46 g / cm3, the chitosan-fibroin composite "Schrilk" material exhibits the same mechanical properties as aluminum alloys and their equivalents, but by half the weight. In addition, Schrilk is biocompatible and biodegradable; in certain configurations, it is also optically transparent.
Thus, composites are at least 1.2 times, at least 1.3 times, at least 1.4 times, at least 1.5 times, at least 2 times, at least 3 times, at least 4 times more than materials formed from elemental carbohydrates or proteins alone or blends thereof. Can have at least 5 times, at least 10 times, at least 50 times, at least 100 times or more strength. In some embodiments, the composite material is at least 5 MPa, at least 10 MPa, at least 20 MPa, at least 30 MPa, at least 40 MPa, at least 50 MPa, at least 60 MPa, at least 70 MPa, at least 80 MPa, at least 90 MPa, It has a strength of at least 100 MPa or more.
In Schrilk, the maximum strength of the composite is achieved when the chitosan: fibroin weight ratio is approximately 1: 2 (Fig. 2A). Increasing the amount of protein beyond a certain limit is unlikely to enhance its binding effect; further, increasing protein above a 1: 2 ratio negates the effect of the design and mechanically It was observed that a material close to fibroin was produced.
In the SEM image of the fibroin / chitosan contact surface (Fig. 2B), the boundaries are clearly demarcated by the different electrical properties of those materials, but there is no other evidence to distinguish between them. High chemical affinity is confirmed.
Composites have been discussed for carbohydrate films coated with a protein layer, but carbohydrate layers can also be in forms other than film. Thus, in some embodiments, the carbohydrate layer can be in the form of foam, sponge, fiber, mesh or nanoscale structures.
Composites according to aspects of the invention use exudative substances (eg, salt crystals) that can be dissolved by injecting air bubbles into the carbohydrate solution as it dries, or after the formation of foam or sponge. Thereby, it can be produced as a foam-like or sponge-like material. Alternatively, the foam or sponge structure can be formed by lyophilizing the carbohydrate solution. The sublimation of the solvent becomes the core of the bubbles that form the porous structure of the foam or sponge. There are many ways to control the size of the holes. For example, the size of the pores can be controlled by controlling the temperature during freeze-drying, changing the solvent concentration, and the like. The formed carbohydrate foam or sponge can then be dipped in a solution of protein or otherwise coated with a solution of protein to create a foam-like or sponge-like structure complex. Only or all of, but not limited to, carbohydrate-based foams or sponges can be coated with protein.
Further information on the formation of porous carbohydrate materials can be found, for example, in Madihally, SV and Matthew, HWT Porous Chitosan scaffolds for tissue engineering. Biomaterials, 20 (12): 1133-1142 (1999); and Xu, HHK and Simon, CG. Fast setting calcium phosphate-Chitosan scaffold: mechanical properties and biocompatibility. Biomaterials, 26 (12): 1337-1348 (2005), the contents of both documents are incorporated herein by reference. Another interesting option for foam formation is high pressure CO for solid materials.<sub>2</sub>(That is, supercritical CO<sub>2</sub>) Is used. This almost always increases the pressure, usually in the range of 20 Bar, and CO in the molecular structure.<sub>2</sub>This is due to the introduction of. If that pressure is reached, CO<sub>2</sub>Causes material cavitation. This method is gaining popularity and is considered "green".
The resulting foam or sponge introduces the crystalline material by immersing the composite material of the foam or sponge structure in a supersaturated solution of a crystalline material, such as calcium carbonate, and forming crystals on its surface and in cavities. By doing so, it can be mineralized.
In a non-limiting example, composites according to aspects of the invention are exudative substances (eg, exudatives) that can be dissolved by injecting air bubbles into the chitosan solution as it dries, or after the formation of foam or sponge. By using salt crystals), it can be produced as a foam-like or sponge-like material. According to aspects of the invention, the chitosan foam sponge can be dipped in a fibroin solution or otherwise coated with a fibroin solution to create a composite material with a foam-like structure. The obtained foam is made of calcium carbonate by introducing a crystalline substance, for example, by immersing a composite material having a foam structure in a supersaturated aqueous solution of calcium carbonate and forming crystals on the surface and in the cavity of the foam. Can be mineralized by introducing. In one aspect of the invention, any large amount of CaCO<sub>3</sub>Dissolve in water and dissolve this in 20 psi CO for 1-3 days<sub>2</sub>To serve. Undissolved CaCO after relieving pressure<sub>3</sub>The resulting liquid is filtered to remove. CaCO the chitosan foam or sponge (or film) after the solution has returned to room temperature<sub>3</sub>It can be immersed in a solution.
In another non-limiting example, the foam or sponge structure can be formed by lyophilizing chitosan dissolved in solution. The sublimation of the solvent becomes the core of the bubbles that form the porous structure of the foam or sponge. There are many ways to control the size of the holes. For example, the size of the pores can be controlled by controlling the temperature during lyophilization. Alternatively, the pore size can be controlled by varying the concentration of solvent. In the structures shown in FIGS. 5 and 6, chitosan was dissolved in a 1% acetic acid solution, whereas a 2% acetic acid solution was used to prepare the chitosan film. For more information on the formation of porous substrate materials, see Madihally, SV and HWT Matthew, Porous Chitosan scaffolds for tissue engineering. Biomaterials, 1999, 20 (12): p.1133-1142; and Xu, HHK and CG. Simon, Fast setting calcium phosphate-Chitosan scaffold: mechanical properties and biocompatibility. Biomaterials, 2005, 26 (12): p.1337-1348, both references incorporated herein by reference.
FIG. 5 shows a sample of a composite material produced as a foam according to the present invention side by side with a chitosan-based foam structure in cylindrical form. Figures 6A and 6B show mineralized foam composite structures. FIG. 6B shows an enlarged image of the inset view of FIG. 6A, and the opening of the structure can be clearly confirmed.
According to aspects of the invention, carbohydrates can be made into fibers by electrospinning, i.e. using electric charges to produce fibers of the carbohydrate polymer from the carbohydrate solution. For example, carbohydrate fibers can be formed by injecting a solution of carbohydrate into a second solution to coagulate the carbohydrate. The coagulated product can then be extruded through a small diameter opening to control the diameter of the fibers. For example, an acid solution of carbohydrates can be injected into a basic solution and vice versa. Alternatively, coagulation can be induced by chemical and / or mechanical means, such as pressure, heating or cooling, shaking, etc., by adjusting the salt concentration of the solution. Further information on fiber formation can be found, for example, in Duan, B., C. Dong, X. Yuan, et al., Electrospinning of chitosan solutions in acetic acid with poly (ethylene oxide). Journal of Biomaterials Science, Polymer Edition, 15 (6): 797-811 (2004) and Ohkawa, K., D. Cha, H. Kim, et al., Electrospinning of Chitosan. Macromolecular Rapid Communications, 25 (18): Found in 1600-1605 (2004), both references are incorporated herein by reference. In an alternative embodiment of the invention, carbohydrates are incorporated herein by reference, "Nanofiber assembly by rotary jet-spinning," Badrossamay MR, Mcllwee HA, Goss JA, Parker KK, Nano Lett. 2010 Jun 9; 10 ( 6): Can be made into fibers by rotary jet spinning as described in 2257-6.
In a non-limiting example, chitosan can be made into fibers by electrospinning, i.e., by using an electric charge to generate chitosan fibers from a chitosan solution. According to one aspect of the invention, fibrous chitosan can be formed by injecting an acid (eg, acetic acid) solution of chitosan into a basic solution (eg, NaOH). Chitosan coagulates on contact with a basic solution to produce chitosan fibers. The coagulated product can be extruded through a small diameter opening to control the diameter of the fibers. Alternatively, other fiber extrusion methods, such as rotary jet spinning, may be used (eg, Mohammad Reza Badrossamay, Holly Alice Mcllwee, Josue A. Goss, Kevin Kit Parker. Nanofiber Assembly by Rotary Jet-Spinning. Nano Lett., 2010. , 10 (6), pp 2257-2261).
According to the present invention, the carbohydrate layer can be formed to have nanoscale-defined topography. The protein phase can then be applied on this defined nanoscale topography. Although not bound by theory, isotropic deposition and the physical effects introduced by this topography (eg, capillarity) disrupt the structure in the defined region. For example, chitosan can be formed to have nanoscale-defined topography, and the protein phase can be applied on this structured chitosan film. The results (Figure 3A, which is the same topography as B and C) show that isotropic deposition and the physical effects introduced by this topography (eg, capillarity) are at very low fibroin concentrations. Even shows that it disrupts the structure in the defined area.
Proteins can also be used to make microstructures by polymer casting. Therefore, the microstructure can be formed by casting a protein layer on the surface of the preformed microstructure. In addition, the resulting composite can be cast in a secondary shape by drying the composite on a suitable shaped surface. For example, a composite can be cast into a tube by drying the composite on the surface of a circular fixture or tube.
The composite can be softened by exposure to water in either its localized area or in its entirety and then placed on the formwork surface or fixture surface to dry and give a secondary shape. The same composite laminate by protecting some areas from hydration (eg, by microcontact printing a pattern of water repellent wax material on the surface of the composite) and allowing it in other areas. The material can be made to show variable physical properties, eg, higher and lower areas of flexibility based on more and less water absorption, respectively. Without wishing to be bound by theory, this mimics the mechanism by which the exoskeleton of an arthropod acquires its variable mechanical properties.
Fibroin is also a good material for the production of microstructures by polymer casting. According to aspects of the invention, microstructures can be formed by casting protein layers, as shown in Figures 3C and D. In addition, the resulting composite can be cast into a secondary shape, eg, a tube (FIG. 3B), by drying the composite on the surface of a circular fixture or tube. Alternatively, the composite can be softened by exposure to water in either its localized area or in its entirety and then placed on the formwork surface or fixture surface to dry and give a secondary shape. The same composite laminate material by protecting some areas from hydration (eg, by micro-contact printing a pattern of water repellent wax material on the surface of Schrilk) and allowing it in other areas. Can be made to show variable physical properties, eg, higher and lower areas of flexibility based on more and less water absorption, respectively. It mimics the mechanism by which the exoskeleton of an arthropod acquires its variable mechanical properties.
According to the present invention, the affinity between the constituents is used to unite the layers or structured constituents of separate composites by "gluing" them with a protein, such as fibroin. be able to. This process allows the construction of multi-layer composites to produce complex three-dimensional biocompatible structures. In some embodiments, the carbohydrate component is glued together by applying the protein to the dehydrated region (or the entire surface) of the carbohydrate component and then by altering the protein structure, eg, β-conversion. Can be.
Therefore, in aspects of the invention, fibroin can be used to "glue" chitosan structures. In this embodiment, the chitosan component is obtained by applying fibroin to the dehydrated region (or the entire surface) of the chitosan component and optionally β-converting the protein by, for example, application of alcohol, application of pressure or application of heat. Can be glued together into one.
According to aspects of the invention, a first composite layer (having a first protein layer bonded to a first carbohydrate layer) is "glued" using a low concentration protein solution ("glue solution"). By "applying", it can be attached to a second composite layer (having a second protein layer attached to a second carbohydrate layer). In some embodiments, the glue solution provides a carbohydrate to protein ratio of less than 1: 2. In some embodiments, the glue solution comprises <4% w / v protein. Combining the two composite layers by pressing and removing air bubbles, for example using a straight edge or squeegee, can provide a substantially uniform protein layer between the carbohydrate layers. The resulting multilayer composite can be dried, for example, at 37 ° C. Different types of additional materials can be added to the glue layer (eg, carbon fibers, carbon nanotubes or other high-strength materials, particles or fibers) to further improve the physical properties of the laminated material or optimize the desired behavior. it can.
In a non-limiting example, the first composite layer (having a first fibroin layer bonded to a first chitosan layer) has a low concentration (<4) that provides a fibroin to chitosan ratio of less than 2: 1. By "gluing" with a fibroin solution of% w / v), it can be bonded to a second composite layer (having a second fibroin layer bonded to a second chitosan layer). By combining the two composite layers by pressing and removing air bubbles, for example using a straight edge or squeegee, a substantially uniform fibroin layer can be provided between the chitosan layers. The resulting multilayer composite can be dried, for example, at 37C. FIG. 3E shows an SEM cross-sectional image of the multilayer composite. The resulting structure has the mechanical characteristics of a single layer composite film (extreme strength = 116.7 ± 12.3 MPa). As mentioned above, different types of additional materials are added to the glue layer (eg carbon fibers, carbon nanotubes or other high-strength materials, particles or fibers) to further improve the physical properties of the laminated material or optimize the desired behavior. can do.
<u style="single">Schrilk Composition: Chitosan / Protein / Water</u> A 2 cm square chitosan / protein composite sample with a constant chitosan thickness and different amounts of fibroin was weighed and then immersed in DI water at 37 ° C for 24 hours. The linear approximation in Figure 2C shows that both phases are independent and the final weight of the composite sample is Wwet = Wcs Acs + Wfib Afib (i) Given by, in the formula, Wwet is the weight of the hydrated composite, Wcs and Wfib are the dry weights of chitosan and fibroin in the sample, respectively, and Acs and Afib are the water absorptions associated with them. It was done under the assumption that.
We have also found that the flexibility of composites can be adjusted by moisture. In addition, composites can be reversibly changed from very hard materials (when dry) to flexible elastomers by adjusting their water content, independent of other factors such as tanning and composition. Can be done. Figure 2C shows the absorption of water by the chitosan / protein composite, and a graph of the weight of the water-saturated sample is displayed relative to the chitosan / fibroin ratio. Water saturation is volume dependent rather than surface area, and the final weight of the sample is very well consistent with the sum of the individual water uptakes of both material layers (R2 = 0.99); It is shown that the uptake is independent of the interaction between the components on its contact surface. Since the water absorption of the chitosan phase is 2.3 times greater than that of fibroin, chitosan-rich samples contain more water, and the amount of equilibrium is directly related to the concentration of the other two components.
Thus, in some aspects of the aspects described herein, the composite is hydrated. As used herein, the term "hydration" for a composite means that the composite contains water. Thus, in some embodiments, the composite is hydrated and contains from about 5% to about 95% water. The water content of the hydrated composite can be based on the ratio of the weight of water in the composite to the total weight of the hydrated composite. Alternatively, the water content of the hydrated composite can be based on the ratio of the weight of water in the composite to the weight of the composite before hydration. In some embodiments, the water content of the composite refers to the total amount of carbohydrates or proteins in the composite.
Water saturation of a composite compares the ultimate strength of the composite to the ultimate strength of a dry composite at least 10%, at least 20%, at least 30%, at least 40%, at least 50%, at least 60%. , At least 70%, at least 80%, at least 90%, at least 95%, at least one-fifth, at least one-fifth, at least one-tenth, at least one-twentieth, at least one-thirtieth, at least 40 minutes Can be reduced to one, at least one-fiftieth, at least one-hundredth, or less.
We also found that the significant difference between the water-saturated composite and the dried counterpart lies in the homogenization of the former; there is no mechanical significant difference between them. I don't want to be bound by theory, but the changes introduced for moisture cancel out the interactions of other species. Moreover, there are no noticeable differences in the mechanical properties of composite, carbohydrate and protein hydrated films. Again, without wanting to be bound by theory, the outstanding mechanical properties of composites are due to the different mechanical features of their constituents.
In one non-limiting example, water saturation of the chitosan / fibroin composite reduces the ultimate strength to an average of 3.5 Mpa, which is less than one-thirtieth of what is obtained with dry materials. However, the energy absorbed before its surrender is only reduced by half; the remaining energy is its original size compared to 2.7% of the composite material during drying, as shown in Figure 2D. It is conserved as a significant increase in elasticity of up to 23% of the ultimate strain.
<u style="single">IR spectrum</u> IR spectrum, 4000-500 cm<sup>-1</sup>2 cm between<sup>-1</sup>(Vertex 70, Bruker, Germany) and analyzed using Essential FTIR (Operant LLC, USA). The FTIR data of fibroin in the composite material was obtained using the single beam spectrum of chitosan film as a background signal before Fourier transform.
From a molecular point of view, chitin is usually referred to as cellulose in which one hydroxyl group in each monomer is replaced with an acetylamine group. Figure 4 shows an FTIR analysis of chitosan film showing the characteristic absorption of the C = O stretch of the amide (amide I, 1658 cm) showing incomplete deacetylation of chitin.<sup>-1</sup>) Is confirmed. The ratio of acetyl groups per glucosamine residue (ie, degree of acetylation) is the methyl group band (1379 cm).<sup>-1</sup>) Are calculated as the relative intensities of the absorption bands on both sides of the locking, these are 1321 and 1417 cm, as shown in Figure 4.<sup>-1</sup>Located in. In the chitosan analyzed in these experiments, 20.3 ± 0.7% of glucosamine groups were acetylated.
As shown in Figure 4B, the composite Schrilk material (chitosan to fibroin ratio 1: 2) has an IR absorption spectrum very similar to that of chitosan (figure 4A, black) plus fibroin (figure 4C, black). Shown. The amine II band has shifted compared to chitosan (1562 to 1536 cm)<sup>-1</sup>To), this is even seen when the fibroin layer is very thin. This band is associated with a mixture of NH bending and CN stretching modes derived from amides and amines. Therefore, the central interaction between the two phases is thought to be caused by the nitrogen atom at the 2-position of the chitin / chitosan sugar ring.
As shown herein, the interactions between the different constituents in the composite are considered to be confined to the contact surface and the new binding is screened by the signal of the bulk material. To investigate this new molecular bond in detail, the spectrum of fibroin in a composite with the single beam spectrum generated by the chitosan film as the background is shown in gray in Figure 4C. Compared to pure fibroin film, 3454 cm<sup>-1</sup>It was confirmed that there was an apparent loss in the nearby region (stretching of free NH), which supports the hypothesis that new bonds are formed in the initially free NH. In addition, the above (1560 cm<sup>-1</sup>In addition to the change in the amide II band (due to the loss of absorption band in), 1417 cm<sup>-1</sup>There is also a significant decrease in the band. The singularity of all these spectral changes is that they are located in the same band (Fig. 4A, gray) that was changed by the protonation of the amine group in chitosan, which is the case in the composite laminate. It further suggests that the bond between the protein and chitosan is specifically formed through these chemical groups.
This observation can also explain that the mechanical properties of the chitosan: fibroin blend are extremely poor compared to the Schrilk laminate; if the nitrogen atom is chitosan, then the intermolecular hydrogen (at position 6 of glucosamine). It is considered that chitin is directly incorporated into its crystal structure through the bond NH OC and through the hydrogen bond between C = O HN in the case of chitin (there are no free OH and NH groups in the bulk crystal). Be done. Interaction with fibroin is therefore a process that competes with the intermolecular association of chitosan and the formation of crystal structures.
The composite material produced according to the present invention is an organic composite laminated material which is composed of a biodegradable and biocompatible material and has the strength of an aluminum alloy, but at half the density. The strength of this composite is much higher than the original constituents and can be made and adapted for many applications, including both medical and non-medical applications. In addition, it is an excellent model for the study of natural structures and contributes significantly to zoology and materials science. By controlling the amount of water in the composite, the material can be from a very hard composite when dry (Young's coefficient = 5.75 ± 0.48 GPa) to a highly elastic material when saturated with water (Young's coefficient = 0.017 ± 0.004 GPa). Can provide a wide range of mechanical features.
<u style="single">Use of composite materials</u> Due to its biocompatibility, high strength and its ability to adjust its stiffness, composites can be used in many biomedical applications. For example, composites can be used as substitutes for prosthetic devices, tissue engineering scaffolds, wound healing devices and their components, and plastic and other synthetic or inorganic materials. In addition, by controlling the water content in the composite, the stiffness or flexibility of the material allows it to be used as a substitute for a wide range of tissue types and functions, such as scaffolds or other prosthetic components. To do. Moreover, due to the porous nature of the foam and sponge structures, aspects of the invention are delivery of the substance by incorporating a drug delivery and therapeutic agent into the pores during or after the manufacturing process. Can be used for.
Composites can also be used in non-medical applications, such as industrial applications. For example, composites can be used in any situation that requires lightweight, high-strength materials, such as in automobiles (eg, hybrid vehicles, electric vehicles and racing vehicles) and in the aviation industry. Composites can also be used in place of the plastics used in the food industry, for example for containers and bottles. Composite materials can be used to manufacture consumer goods including, but not limited to, storage containers, baggage bags, backpacks, tents, clothing and disposable trash bags. Other exemplary uses of composites include bulletproof windows, shatterproof windows, sails for ships, parachutes, ammunition containment, tires, vehicle bumpers, guardrails and road repair tools (eg, pylon). Obtain, but are not limited to these. In addition, composites can be used in the manufacture of appliances, such as laptop components.
The composites of the invention have many applications, including, for example, drug delivery systems, tissue engineering materials or other biomedical devices. All of the composites described herein can be easily functionalized and retained in function with drugs, antibiotics, cell response molecules, dyes, enzymes and other large and small molecules.
Aspects of the invention are thus composites capable of adapting to tissue engineering constructs that can be used for the purpose of repairing defects and organs, replacing or regenerating organs that may benefit from these modified silk materials. Provide materials. Composite materials of the present invention include, but are limited to, spinal disc, cranial tissue, dural, nervous tissue, liver, pancreas, kidney, bladder, spleen, myocardium, skeletal muscle, tendon, ligament, corneal tissue and breast tissue. It can be used for the purpose of repairing, replacing or regenerating organs that are not. The composites of the present invention can be used in medical applications for repairing defects, such as repairing hernias and closing and repairing wounds. The composite can be used as a complete or partial prosthesis and in plastic surgery applications, for example to assist in reconstruction and to reduce scarring. Musculoskeletal cells, such as cartilage cells, fibroblasts, muscle and bone cells, parenchymal cells, either from donors, from established cell cultures, or before or after molecular genetic manipulation. For example, hepatocytes, pancreatic cells (including pancreatic islet cells), intestinal cells, and other cells such as nerve cells, bone marrow cells, skin cells, pluripotent cells and stem cells (eg embryonic stem cells, adult stem cells and artificial polyplasia). Any type of cell, including capable stem (iPS) cells), as well as combinations thereof, can be added to tissue engineering constructs for culture and future transplantation. Tissue pieces that can provide many different cell types as a single structure can also be used.
The composite can be modified to contain at least one active agent. The agent may be mixed with a carbohydrate and / or protein solution prior to the formation of the composite, or may be filled into the composite or a portion thereof after its formation. The agent can also be covalently linked to a carbohydrate or protein layer. Due to the covalent bond, the agent can be linked with a carbohydrate or protein prior to the formation of the composite. Alternatively, the agent can be covalently linked to the carbohydrate or protein layer after the formation of the composite. Thus, the agent can be linked directly to the carbohydrate or protein layer by binding or through an intermediate linker.
The types of active agents that can be used in combination with the composite materials of the present invention are wide-ranging, including small molecules, polymers, proteins, peptides, peptide mimetics, nucleic acids, organic compounds, inorganic compounds, and biological compounds. Compounds, bioactive compounds, and compounds having bioactivity may be included. For example, active agents are therapeutic or biological agents such as cells (including stem cells), proteins, peptides, nucleic acids (DNA, RNA, plasmids, siRNAs, antisense oligonucleotides, decoy oligonucleotides, microRNAs). , Aptamers and ribozymes), nucleic acid analogs, nucleotides, oligonucleotides or sequences, peptide nucleic acids, antibodies, hormones, hormone antagonists, growth factors or recombinant growth factors and fragments and variants thereof, cytokines, or enzymes, antibiotics, viruses, It can be an antiviral agent, a toxin, a prodrug, a chemotherapeutic agent, a small molecule, a drug or a combination thereof. Some exemplary active agents suitable for modifying the composite materials of the invention include cells (including stem cells), erythropoetin (EPO), YIGSR peptides, glycosaminoglycans (GAG), hyaluronic acid (HA). , Integrins, selectins and cadoherins; painkillers and painkiller combinations; steroids; antibiotics; insulin; interferon α and γ; interleukins; adenosine; chemotherapeutic agents (eg, anticancer agents); tumor necrosis factors α and β; antibodies; Includes cell adhesion mediators such as RGD or integrins, or other naturally occurring or genetically engineered proteins, polysaccharides, glycoproteins, cytotoxins, prodrugs, immune sources or lipoproteins.
Other exemplary therapeutic agents include Harrison's Principles of Internal Medicine, 13<sup>th</sup> Edition, Eds. TR Harrison et al. McGraw-Hill NY, NY; Physicians Desk Reference, 50<sup>th</sup> Edition, 1997, Oradell New Jersey, Medical Economics Co .; Pharmacological Basis of Therapeutics, 8<sup>th</sup> Edition, Goodman and Gilman, 1990; United States Pharmacopeia, The National Formulary, USP XII NF XVII, 1990; Current Edition of Goodman and Oilman's The Pharmacological Basis of Therapeutics; The entire contents of all of these documents, including but not limited to these, are incorporated herein by reference.
Other substances embedded in the composite material include liposomes and related systems for the delivery of genetic material; peptides and proteins that activate the cellular signaling cascade; peptides and proteins that promote mineralization or cell-derived related events. Adhesive peptides and proteins that improve film and tissue contact surfaces; antibacterial peptides; proteins and related compounds; and carbohydrates, including, for example, glycosaminoglycans and proteoglycans.
As mentioned above, one or more active agents can be used to modify the composite. Therefore, when the composite material of the present invention is used as a platform for supporting a biological substance such as a cell, the active material is released from the composite material in order to promote the growth of the active material. Other substances may be added to promote the functionalization of the agent or to improve the viability of the agent or the ability of the agent to maintain its efficacy during the process. It may be desirable. Exemplary substances known to promote cell growth include cell growth media such as Dalveco modified eagle medium (DMEM), bovine fetal serum (FBS), non-essential amino acids and antibiotics, and growth factors and morphogenesis. Factors such as fibroblast growth factor (eg, FGF 1-9), transforming growth factor (TGF), vascular endothelial growth factor (VEGF), epithelial growth factor (EGF), platelet-derived growth factor (PDGF), insulin Transforming growth factors (IGF-I and IGF-II), bone morphogenesis growth factors (eg, BMP) 1-7), bone morphogenesis-like proteins (eg, GFD-5, GFD-7 and GFD-8), transforming growth factors (eg, TGF-α, TGF-β I-III), nerve growth factors, and Includes, but is not limited to, related factors. Growth factors are known in the art, see, for example, Rosen and Thies, Cellular & Mol. Basis Bone Formation & Repair (RG Landes Co.).
<u style="single">Enzymatic binding to extracellular matrix</u> In another aspect, the invention provides a method of attaching a medical implant device to a tissue or organ. The method comprises applying an effective amount of transglutaminase to the surface of a tissue or organ to which the medical transplant device needs to be attached, and bringing the medical transplant device into contact with the surface of the tissue. Alternatively or additionally, transglutaminase can be applied to the surface of a medical implant device and the medical implant device can be brought into contact with the surface of the tissue. In yet another embodiment, the medical implant device can be brought into contact with the surface of the tissue followed by the application of transglutaminase.
As used herein, the term "application" with respect to the application of transglutaminase refers to increasing the amount or activity of transglutaminase at the desired site. Thus, the term "application" includes topical application of transglutaminase to a surface, increased expression of host transglutaminase at the site of attachment and / or increased activity of transglutaminase at the site of attachment. Without wishing to be bound by theory, the expression or activity of the host transglutaminase can be increased by applying a composition that increases the expression and / or activity of the transglutaminase. For example, Davies et al. (J. Biol. Chem. (1985) 260: 5166-5174) describes the induction of transglutaminase expression using retinoic acid. Exemplary transglutaminase activators include, but are not limited to, thrombin, TIG3 protein, calcium chloride, and sphingosylphosphorylcholine. In addition, Sigma-Aldrich sells the Transglutaminase Assay Kit, which can be used to screen transglutaminase activators.
As used herein, "transglutaminase" means a member of an enzyme group identified by Enzyme Commission System of Classification No. 2.3.2.13 (EC 2.3.2.13). Those skilled in the art are well aware that transglutaminase is an enzyme that catalyzes the acyl transfer reaction of the γ-carboxamide group of glutamine residues in the peptide chain. Transglutaminase forms ε- (γ-Glu) -Lys crosslinks within and between protein molecules when the ε-amino group of the lysine residue in the protein acts as an acyl receptor. Transglutaminase can also deaminate glutamine residues to glutamate residues if water acts as an acyl receptor.
Such transglutaminases include calcium-independent transglutaminase and calcium-dependent transglutaminase. The former includes enzymes derived from microorganisms (see, eg, JP-A-1-27471, the entire contents of which are incorporated herein by reference), and the latter includes enzymes derived from the liver of guinea pigs (see, eg, JP-A-1-27471, the entire contents of which are incorporated herein by reference). JP-B-150382, the entire contents of which are incorporated herein by reference), fish-derived enzymes (eg, Seki Nobuo et al. Nihon Suisan Gakkaishi, vol. See .56, No.1, p.125 (1990)), and the like. In addition, genetically modified enzymes (see JP-A-1-300889, JP-A-5-199883, JP-A-6-225775, the entire contents of which are incorporated herein by reference). Is also included.
The transglutaminase used in the methods of the invention can be from natural or synthetic sources, such as recombinants. Thus, mammalian transglutaminase prepared (ie, extracted) from mammalian tissue samples and mammalian transglutaminase expressed by recombinant means are included in the present invention. In addition, variants of naturally occurring mammalian transglutaminase are also included.
In some embodiments, the transglutaminase is a mammalian transglutaminase. Mammalian transglutaminase can be obtained from animal cells and tissues as well as cell products.
In some embodiments, the transglutaminase is tissue transglutaminase (tTgase).
In some embodiments, the transglutaminase is a microbial transglutaminase. Microbial transglutaminase is a strain of Streptomyces hygroscopicus, Streptomyces hygroscopicus, Streptomyces hygroscopicus, Streptomyces hygroscopicus, Streptomyces hygroscopicus, or Escherichia Coli. Alternatively, it can be isolated from a plurality. See, for example, Cui L et al., Bioresource Technology (2008) 99 (9): 3794-3800, the entire contents of which are incorporated herein by reference.
In some embodiments, the transglutaminase is a human transglutaminase. Human transglutaminase can be prepared from human tissue or cells. For example, human transglutaminase can be extracted from human tissue sources such as lung, liver, spleen, kidney, myocardium, skeletal muscle, ocular lens, endothelial cells, erythrocytes, smooth muscle cells, bones and macrophages.
Alternatively, human transglutaminase can be obtained from a culture of human cells expressing mammalian transglutaminase using cell culture methods well known in the art. Preferred cell line sources for such transglutaminase include, but are not limited to, human endothelial cell line ECV304 (for tissue transglutaminase) and human osteosarcoma cell line MG63.
In some embodiments, the transglutaminase is a calcium-independent transglutaminase. In some other embodiments, the transglutaminase is a calcium-dependent transglutaminase.
Some exemplary transglutaminases include factor XIII (fibrin stabilizer), type 1 transglutaminase (keratinocyte transglutaminase), type 2 transglutaminase (tissue transglutaminase), and type 3 transglutaminase (epithelial transglutaminase). ), Type 4 transglutaminase (prostatic transglutaminase), type 5 transglutaminase (transglutaminase X), type 6 transglutaminase (transglutaminase Y), and type 7 transglutaminase (transglutaminase Z), but limited to these Not done.
It will be appreciated by those skilled in the art that the source of transglutaminase can be selected depending on the individual use of the medical implant material (eg, the site of implantation). For example, if a medical implant material is used as an artificial bone, it may be beneficial for the material to contain bone-derived transglutaminase. Therefore, in the method of the present invention, any transglutaminase can be used, and its origin and production process are not limited.
Transglutaminase can be of mammalian or microbial origin. In addition, humanized recombinant transglutaminase can also be used.
Several commercially available mammalian-derived transglutaminase, such as guinea pig liver-derived transglutaminase, goat-derived transglutaminase and rabbit-derived transglutaminase, are available from Oriental Yeast Co., Ltd., Upstate USA Inc. and Biodesign International. it can. Non-limiting examples of other commercially available transglutaminase products include those manufactured by Ajinomoto Co. (Kawasaki, Japan), such as Activa TG-TI, Activa TG-FP, Activa TG-GS, Activa TG-RM and Activa. MP; as well as those manufactured by Yiming Biological Products Co. (Jiangsu, China), such as TG-B and TG-A.
Transglutaminase includes solutions, emulsions (oil in water, water in oil), aerosols, foams, ointments, pastes, lotions, powders, gels, hydrogels, hydrophilic colloids, creams, and any combination thereof. It can be applied in any suitable form without limitation. In one embodiment, the transglutaminase is applied in powder form.
The transglutaminase can optionally be present in a pharmaceutically acceptable composition. A pharmaceutically acceptable composition comprises a transglutaminase formulated with one or more pharmaceutically acceptable carriers (additives) and / or diluents. As used herein, the term "pharmaceutically acceptable" is suitable and overkill for use in contact with human and animal tissues to the extent of established medical judgment. Represents a compound, substance, composition and / or dosage form that is free of toxicity, irritation, allergic reactions or other problems or complications and maintains a reasonable benefit / risk ratio.
In general, the activity of transglutaminase increases at high temperatures. Therefore, the bond can be carried out at any temperature. In some embodiments, the bond is at high temperatures, eg, above 30 ° C or above 30 ° C, above 35 ° C or above 35 ° C, above 40 ° C or above 40 ° C, above 45 ° C or above 45 ° C, Performed at over 50 ° C or above 50 ° C, above 55 ° C or above 55 ° C, or above 60 ° C or above 60 ° C. In some embodiments, the binding is carried out at room temperature, eg, about 15 ° C to about 25 ° C. In some embodiments, the binding is carried out at a temperature of about 20 ° C to about 30 ° C.
As used herein, the term "pharmaceutically acceptable carrier" is used to transport or transport a compound of interest from one organ or part of the body to another. Involved, pharmaceutically acceptable substances, compositions or vehicles surrounding the substance, such as liquid or solid bulking agents, diluents, excipients, production aids (eg, lubricants, talcmagnesium, calcium or stearic acid). Zinc acid or stearic acid), or solvent. Each carrier must be "acceptable" in the sense that it is compatible with the other ingredients of the formulation and is not harmful to the patient. Some examples of substances that can act as pharmaceutically acceptable carriers are: (1) sugars such as lactose, glucose and sucrose; (2) starches such as corn starch and potato starch; (3) cellulose and Derivatives thereof, such as sodium carboxymethyl cellulose, methyl cellulose, ethyl cellulose, microcrystalline cellulose and cellulose acetate; (4) tragacant powder; (5) starch; (6) gelatin; (7) lubricants such as magnesium stearate, sodium lauryl sulfate. And talc; (8) excipients such as cocoa butter and suppository wax; (9) oils such as peanut oil, cottonseed oil, saflower oil, sesame oil, olive oil, corn oil and soybean oil; (10) glycols such as Propylene glycol; (11) polyols such as glycerin, sorbitol, mannitol and polyethylene glycol (PEG); (12) esters such as ethyl oleate and ethyl laurate; (13) agar; (14) buffers such as magnesium hydroxide And aluminum hydroxide; (15) excipients; (16) excipient-free water; (17) isotonic saline; (18) ringer solution; (19) ethyl alcohol; (20) pH buffered solution; (21) polyester , Polycarbonate and / or polyanhydrous;<sub>2</sub>~ C<sub>12</sub>Alcohols such as ethanol; and (23) other non-toxic compatible substances used in pharmaceutical formulations are included. Wetting agents, colorants, mold release agents, coating agents, sweeteners, flavoring agents, fragrances, preservatives and antioxidants may also be present in the formulation. Terms such as "excipient", "carrier", "pharmaceutically acceptable carrier", or the like are used interchangeably herein.
The pharmaceutically acceptable composition can also include any cofactor for transglutaminase, such as a salt.
In some embodiments, the transglutaminase can be attached to the medical transplant device prior to attachment to the tissue or organ. When used in the context of medical transplant devices and transglutaminase, the term "associated with" means that transglutaminase is coated or otherwise (covalently bound) on the medical transplant device. Or means concatenated (by non-covalent bond). In some embodiments, transglutaminase can be dispersed in the materials used to make medical transplant devices. In some embodiments, the transglutaminase can be covalently linked to the surface of a medical transplant device. In some embodiments, the transglutaminase can be non-covalently linked to the surface of a medical transplant device.
In some embodiments, the transglutaminase can be added to the medical transplant device after manufacture of the medical transplant device. This can be achieved, for example, by immersing the manufactured medical implant device in a solution of transglutaminase.
Adhesion of a medical transplant device containing transglutaminase may or may not require the application of any additional transglutaminase to the surface of the tissue or organ where the attachment occurs.
As used herein, "effective amount of transglutaminase" means the amount of transglutaminase that is effective in connecting a medical transplant device to a tissue or organ. Therefore, in some embodiments, the effective amount of transglutaminase is 1 cm of contact surface area.<sup>2</sup>It is about 1 μg to about 100 mg per. In some embodiments, the effective amount of transglutaminase is 1 cm.<sup>2</sup>About 1mg ~ 50mg, 1cm<sup>2</sup>About 5mg ~ 40mg, 1cm<sup>2</sup>About 10mg ~ 30mg, 1cm<sup>2</sup>Approximately 15 mg to 25 mg or 1 cm per<sup>2</sup>Selected from the group consisting of about 20 mg per. "Contact surface area" means the surface area of tissue that comes into contact with the implant device. In the case of a wound, the contact surface area can mean the size of the wound and / or the total exposed area of the wound.
As used herein, the term "medical transplant device" refers to a device for introduction into a subject's body. Exemplary medical transplant devices include, but are not limited to, artificial tissues, artificial organs, prosthetic devices, drug delivery devices, wound dressings, fibers, nanoparticles, microparticles, foams, and sponges. Medical implantable devices can be in any form, including but not limited to, including, but not limited to, 3-D scaffolds, fibers, foams, sponges, films and any combination thereof. Medical transplant devices can be used as permanent replacements for organs (functions).
In some embodiments, the medical implant device is a foam or sponge.
In some embodiments, the medical implant device comprises nanoparticles or microparticles.
In one embodiment, the medical implant device is a wound dressing. Exemplary wound dressings include, but are not limited to, bandages, gauze, tapes, meshes, nets, scabies, films, membranes, and patches. In some embodiments, the wound dressing may comprise a composite material described herein.
In some embodiments, the medical implant device is not a gel.
In some embodiments, the medical transplant device is bound to a protein that can be crosslinked by transglutaminase. When used in the context of a medical transplant device, the term "bound" refers to a medical transplant device that is coated with or contains a protein that can be linked with transglutaminase. Represent. In some embodiments, the medical transplant device is coated with a transglutaminase-linkable protein. "Coated" means that a transglutaminase-linkable protein is applied to the surface of a medical transplant device. Thus, medical transplant devices can be coated or sprayed with a solution containing a protein that can be ligated with transglutaminase. Alternatively, the medical transplant device can be immersed in a possible protein solution linked with transglutaminase.
Proteins that can be ligated with transglutaminase can be bound to the outer surface of a medical transplant device, such as a medical transplant device, by covalent or non-covalent binding. Once bound to a medical transplant device, transglutaminase-linkable proteins provide a means of attaching the medical transplant device to tissues or organs.
As used herein, the term "crosslinkable by transglutaminase" refers to a protein or polypeptide that acts as a substrate for transglutaminase.
Therefore, a protein that can be crosslinked with transglutaminase is or contains a transglutaminase substrate. As used herein, the term "transglutaminase substrate" refers to a peptide or polypeptide sequence that contains a suitable transglutaminase target for cross-linking. Proteins that can be linked with transglutaminase include, but are not limited to, aldolase A, glyceraldehyde-3-phosphate dehydrogenase, phosphorylase kinase, crystallin, glutathione S-transferase, actin, myosin, troponin, β-tubulin. , Tau, rho, histone, α-oxoglutaminase dehydrogenase, β-lactoglobulin, cytochrome, erythrocyte band III, CD38, acetylcholineresterase, collagen, entactin, fibronectin, fibrin, silk, fibron, fibrinogen, bitronectin, osteopontin, nidgen, laminin , LTBP-1, Osteonectin, Osteopontin, Osteocalcin, Thrombospondin, Substance P, Phosphorlipase A<sub>2</sub>, Midkine, wheat gelatin, milk serum protein, casein, soybean protein, pea uregmin, Candida albicans surface protein, HIV envelope glycoproteins gp120 and gp41, HIV aspartyl proteinase, hepatitis C virus core protein, Fragments thereof capable of binding to transglutaminase, as well as transglutaminase substrates selected from the group consisting of combinations thereof, or those containing it. In some embodiments, the transglutaminase ligable protein is a fragment thereof that can be crosslinked by silk fibroin or transglutaminase.
Peptide and polypeptide sequences containing suitable transglutaminase targets for cross-linking are known in the art. Non-limiting examples of such peptides are described, for example, in US Pat. Nos. 5,428,014; 5,939,385; and 7,208,171; all of which are incorporated herein by reference. US Pat. No. 5,428,014 describes a biocompatible, bioadhesive transglutaminase crosslinkable polypeptide in which transglutaminase is the γ-carboxamide group of the glutaminyl residue bound to the protein and the ε- of the Lys residue. It has been described that it is known to catalyze the acyl transition reaction between amino groups to form ε- (γ-glutaminase) lysine isopeptide bonds. U.S. Pat. No. 5,939,385 describes a biocompatible, bioadhesive transglutaminase crosslinkable polypeptide.
U.S. Pat. No. 7,208,171 describes the rational design of transglutaminase substrate peptides. This design approach was based on maximizing the number of acyl receptor lysine peptide substrates and acyl donor glutaminyl peptide substrates available for transglutaminase cross-linking. Since then, Lys and Glu substrate peptides have been designed to have the basic characteristics of known biopolymer and transglutaminase synthetic peptide substrates. For example, Glu substrate peptides have been found to be better transglutaminase substrates with increasing Glu repeat length, and that proteins containing two or more adjacent Glu residues are good substrates. Based on evidence that it has been, it was assumed to contain 2-5 consecutive Glu residues. The Leu residue was shown to significantly increase Glu specificity and was placed adjacent to Glu near the C-terminus in various peptides. For Lys substrate peptides, it has been shown that the composition and sequence of amino acids flanking lysine residues in peptides and protein substrates can have an effect on amine specificity. Finally, in all peptides, the Gly residue acts as a spacer between the peptide and polymer in the peptide-polymer conjugate, thereby allowing the peptide in the conjugate to be more accessible to the enzyme on the C-terminal side. Was added to.
Medical implantable devices can be made from any biocompatible material. As used herein, the term "biocompatible material" does not deteriorate to a perceptible degree over time and, when implanted in or near the biological tissue of interest, and Represents any polymeric material that does not induce a significant immune or harmful tissue reaction, such as a toxic reaction or significant irritation, or, when it comes into contact with blood, does not induce blood coagulation or aggregation. Suitable biocompatible materials include polyimide, poly (ethylene glycol), polyvinyl alcohol, polyethyleneimine, and polyvinylamine, polyacrylate, polyamide, polyester, polycarbonate, and polystyrene derivatives and copolymers.
In some embodiments, the medical implant device is a carbohydrate polymer, protein, silk fibroin, polydimethylsiloxane, polyimide, polyethylene terephthalate, polymethylmethacrylate, polyurethane, polyvinyl chloride, polystyrene polysulfone, polycarbonate, polymethylpentene, polypropylene, foot. Polyvinylidene, Polysilicone, Polytetrafluoroethylene, Polysulfone, Acrylonitrile-butadiene styrene, Polyacrylonitrile, Polybutadiene, Poly (butylene terephthalate), Poly (ethersulfone), Poly (etheretherketone), Poly (ethyleneglycol), Styrene- Manufactured from materials selected from the group consisting of acrylonitrile resin, poly (trimethylene terephthalate), polyvinyl butyral, polyvinylidene difluoride, poly (vinylpyrrolidone) and any combination thereof.
Medical implantable devices can be made from biodegradable materials such as biodegradable polymers. As used herein, the term "biodegradable" refers to a material that can decompose into degradation products under physiological conditions. Such physiological conditions include, for example, hydrolysis (degradation through hydrolytic cleavage), enzymatic catalysis (enzymatic degradation) and mechanical interactions. As used herein, the term "biodegradable" is also degraded under physiological conditions into degradation products that are bioabsorbed by the host organism, ie, metabolites of the host organism's biochemical system. Includes the term "bioabsorbable" to describe a substance that produces.
The term "biodegradable polymer" as used herein refers to a polymer in which at least a portion thereof degrades under physiological conditions. The polymer can therefore be partially or completely degraded under physiological conditions.
Exemplary biodegradable polymers include polyanylene, polyhydroxybutyrate, polyorthoesters, polysiloxane, polycaprolactone, poly (lactic acid-co-glycolic acid), poly (lactic acid), poly (glycolic acid), and Copolymers prepared from monomers of these polymers include, but are not limited to.
In some embodiments, the medical implant device is made from a biocompatible, biodegradable material.
Suitable polymers that can be used to make medical implantable devices include carbohydrate polymers; silk; glycosaminoglycans; fibrin; polyethylene glycol (PEG); C2-C4 polyalkylene glycols (eg, propylene glycol). Polyhydroxyethyl methacrylate; Polypolyalcohol; Polyacrylamide; Poly (N-vinylpyrrolidone); Polyglycolic acid (PGA); Polylactic acid-co-glycolic acid (PLGA); Polye-caprolactone (PCL); Polyethylene oxide; Polyethylene Fumarate (PPF); Polyacrylic acid (PAA); Hydrolyzed polyacrylonitrile; Polymethacrylic acid; Polyethylene amine; Polyan anhydride; Polyhydroxybutyrate; Polyorthoester; Polysiloxane; Polycaprolactone; Poly (lactic acid-co-glycol) Acid); Poly (lactic acid); Poly (glycolic acid); Arginic acid; Alginic acid ester; Pectinic acid; Pectinic acid ester; Carboxymethyl cellulose; Hyaluronic acid; Hyaluronic acid ester; Heparin; Heparin sulfate; Chitosan; Gellan; xantane; collagen; carboxymethyl starch; carboxymethyl dextran; chondroitin sulfate; cationic guar; cationic starch, as well as one or a mixture of polymers selected from the group consisting of salts and esters thereof. , Not limited to these.
In some embodiments, the medical transplant device is made from a carbohydrate polymer. In one embodiment, the carbohydrate polymer is chitosan or a derivative thereof.
In some embodiments, the medical transplant device is made from a transglutaminase-linkable protein.
In some embodiments, the medical implant device is made from the composites described herein.
Optionally, a wound healing substance can also be administered to the subject. In some embodiments, the medical implant device comprises a wound healing material. Without wishing to be bound by theory, wound healing material can be released from medical transplant devices over time.
As used herein, a "wound healing substance" is a compound or composition that actively promotes the wound healing process. Exemplary wound healing substances include dexpantenol; growth factors; enzymes, hormones; povidone iodine; fatty acids; anti-inflammatory agents; antibiotics; antibacterial agents; disinfectants; cytokines; thrombins; painkillers; opioids; aminoxyl; floxane; Nitrosothiol; nitrate and anthocyanin; nucleosides such as adenosine; and nucleotides such as adenosine diphosphate (ADP) and adenosine triphosphate (ATP); neurotransmitters / neuromodulators such as acetylcholine and 5-hydroxytryptamine (serotonin) / 5-HT); histamine and catecholamines such as adrenaline and noradrenaline; lipid molecules such as sphingosin-1-phosphate and lysophosphatidic acid; amino acids such as arginine and lysine; peptides such as brazikinin, substance P and calcium gene-related peptides ( CGRP); Nitrogen monoxide; as well as any combination thereof, but not limited to these.
Exemplary growth factors include fibroblast growth factor (FGF), FGF-1, FGF-2, FGF-4, FGF-α, FGF-β, platelet-derived growth factor (PDGF), insulin-binding growth factor. (IGF), IGF-1, IGF-2, heparin-binding growth factor 1, heparin-binding growth factor 2, epithelial growth factor (EGF), transforming growth factor (TGF), TGF-α, TGF-β, cartilage Includes, but is limited to, inducers A and B, bone-inducing factors, osteogenin, vascular endothelial growth factor, bone growth factor, collagen growth factor, insulin-like growth factor, and their biologically active derivatives. Not done.
The method of attaching a medical transplant device to a tissue or organ can also be used for wound healing. Accordingly, the present invention provides a method of promoting wound healing in a subject in need thereof, comprising contacting the transglutaminase with the wound surface and contacting the wound dressing with the wound. .. Wound dressings can be used to cover and close wounds. The methods and compositions described herein can be used for non-suturing occlusion of wounds.
As used herein, the term "wound" refers to a tissue structure caused by physical (eg, mechanical) force, biological (eg, heat or chemical ray force) or chemical means. Represents a physical collapse of continuity or completeness. In particular, the term "wound" includes skin wounds. The term "wound" refers to bruises and wounds caused by cuts, punctures, lacerations, open wounds, puncture wounds, punctures, abrasions, abrasions, burns, frostbite, corrosion, tears, scratches, compressions and bites. Also includes other types of wounds. In particular, the term includes ulceration (ie, ulceration), preferably skin ulceration. The term "wound" also includes surgical wounds.
As used herein, the term "wound healing" refers to the process of regeneration and wound occlusion by inducing an appropriate temporal and spatial healing program, including wound occlusion. The term "wound healing" includes, but is not limited to, the processes of granulation, neovascularization, fibroblast, endothelial and epithelial cell migration, extracellular matrix accumulation, reepithelialization, and remodeling. The term "wound healing" includes the restoration of tissue integrity. It will be understood that this may represent a partial or total restoration of tissue integrity. Wound treatment therefore represents facilitation, improvement, progression, acceleration or other progression of one or more stages or processes associated with the wound healing process.
As used herein, the term "wound occlusion" refers to wound healing that rejoins the sides of the wound to form a continuous barrier (eg, intact skin).
As used herein, the term "granuloma" refers to the process by which small, red-grained ridges appear on the peeled surface (that of a wound) as a healing factor.
As used herein, the term "new angioplasty" refers to the new growth of blood vessels that results in improved oxygen and nutrient supply. Similarly, the term "angiogenesis" refers to the angioplasty process that involves the development of new capillaries.
As used herein, the term "cell migration" refers to the migration of cells (eg, fibroblasts, endothelium, epithelium, etc.) to the wound site.
As used herein, the term "extracellular matrix accumulation" refers to cellular fibrous elements (eg, collagen, elastin, reticulin), link proteins (eg, fibronectin, laminin) and space-filling molecules (eg, eg, fibronectin, laminin). , Glycosaminoglycan).
As used herein, the term "re-epithelialization" refers to epithelial remodeling on an exposed surface (eg, a wound).
As used herein, the term "remodeling" refers to granulation tissue replacement and / or angiogenesis arrest.
Wounds can be acute or chronic. As used herein, the term "chronic wound" refers to a wound that does not heal well even after a long period of time (eg, 2-3 months or more). Chronic wounds, including pressure ulcers, venous leg ulcers and diabetic foot ulcers, can simply be described as unhealed wounds. The exact molecular pathology of chronic wounds is not fully understood, but it is believed to be multifactorial. These wounds impair the normal response of resident and migrating cells during acute injury, resulting in long-term inflammatory response, incomplete wound extracellular matrix (ECM) remodeling and reepithelialization. Characterized by defects.
The wound can be an inner wound, eg, one in which the structural integrity of the outer surface of the skin is maintained, eg, a bruise or an inner ulcer, or an outer wound, especially a skin wound, so that the tissue is any medial or It can be the outer body tissue. In some embodiments, the tissue is skin (eg, human skin), i.e. the wound is a skin wound, eg, a dermis or epithelial wound.
Wounds can be classified into one of two broad categories: partial-thickness wounds and full-thickness wounds. Partial wounds are confined to the epithelium and epidermis and are undamaged dermal vessels. Full-thickness wounds extend to the deeper panniculus with dermal collapse and are accompanied by dermal vessel collapse. Healing of partial layer wounds results from simple regeneration of epithelial tissue. Wound healing in full-thickness wounds is more complex.
In some embodiments, the wound is a cut and laceration, a surgical incision or wound, a puncture wound, a scratch, a scratch, a compression wound, a scratch, a friction wound (eg, a rash, a swelling due to friction), a decubitus ulcer. (For example, pressure sores or floor rubs); heat wounds (burns from cold or hot sources directly or through conduction, convection or radiation, and burns from electrical sources), chemical wounds (eg, acid or alkaline burns) ) Or open or closed wounds, pathogenic infections (eg, viruses, bacteria or fungi), including skin rashes, pimples and acne, ulcers, chronic wounds (diabetes-related wounds, such as lower and foot ulcers, venous lower limbs) (Including ulcers and pressure ulcers), skin implants / donor sites and recipient sites, immune response conditions such as psoriasis and eczema, gastric and intestinal ulcers, oral wounds including mouth ulcers, injured cartilage or bone, excised wounds, It is selected from the group consisting of corneal lesions and any combination thereof.
Medical transplant devices containing transglutaminase can be used to treat hemorrhage and stop internal or external bleeding. Therefore, the present invention is a method of treating, stopping, or reducing major bleeding, internal bleeding, or external bleeding, the step of applying a medical transplant device containing transglutaminase to the major bleeding site or the bleeding site. Provide a method to include.
<u style="single">Scaffold join</u> In another aspect, the invention provides a method of joining or adhering two scaffolds, eg, two different scaffolds or different parts of one large structure, together. The method involves applying an effective amount of transglutaminase to the surface of the first scaffold where the second scaffold needs to be attached, and applying the second scaffold to the surface of the first scaffold. Including the step of contacting. Alternatively or additionally, the first scaffold can be contacted with the second scaffold, after which transglutaminase can be applied. In some embodiments, transglutaminase is applied to both of the first and second scaffolds prior to contacting them into one.
In some embodiments, the transglutaminase can be attached to the first scaffold prior to contact with the second scaffold. When used in the context of scaffolds and transglutaminase, the term "bound" means that the transglutaminase is coated on the scaffold or otherwise (covalently or non-covalently). It means that it is connected with hold. In some embodiments, the transglutaminase can be dispersed in the material used to make the scaffold. In some embodiments, the transglutaminase can be covalently linked to the surface of the scaffold. In some embodiments, the transglutaminase can be linked to the surface of the scaffold by a non-covalent bond. In some embodiments, the transglutaminase can be linked to the first and second scaffolds prior to contacting and uniting them.
In some embodiments, transglutaminase can be added to the scaffold after it has been prepared. This can be achieved, for example, by immersing the manufactured scaffold in a solution of transglutaminase. Adhesion of scaffolds containing transglutaminase may or may not require the application of any additional transglutaminase to the surface of the scaffolds to which it is desired to adhere.
The "effective amount of transglutaminase" in the relationship of attaching two scaffolds into one means the amount of transglutaminase effective for connecting the two scaffolds into one. In this connection, the effective amount is 1 cm of contact surface area.<sup>2</sup>It can be in the range of about 1 μg to about 100 mg per. In some embodiments, the effective amount of transglutaminase is 1 cm.<sup>2</sup>About 1mg ~ 50mg, 1cm<sup>2</sup>About 5mg ~ 40mg, 1cm<sup>2</sup>About 10mg ~ 30mg, 1cm<sup>2</sup>Approximately 15 mg to 25 mg or 1 cm per<sup>2</sup>It is about 20 mg per.
As used herein, the term "scaffold" refers to any three-dimensional object. Exemplary scaffolds include artificial tissues, artificial organs, prostheses, drug delivery devices, wound dressings (eg, bandages, gauze, tapes, meshes, nets, bandages, films, membranes, patches, and the like). , Fibers, films, foams, sponges, nanoparticles, microparticles, and any combination thereof.
In some embodiments, the scaffold is attached to a protein that can be crosslinked by transglutaminase. When used in the context of a scaffold, the term "bound" refers to a scaffold that is coated with a transglutaminase-linkable protein, contains the protein, or comprises the protein. In some embodiments, the scaffold is coated with a transglutaminase ligable protein. "Coated" means that a transglutaminase-linkable protein is applied to the surface of the scaffold. Thus, the scaffold can be coated or sprayed with a solution containing a protein that can be ligated with transglutaminase. Alternatively, the scaffold can be immersed in a protein solution that can be ligated with transglutaminase.
Proteins that can be ligated with transglutaminase can be bound to scaffolds, eg, the outer surface of scaffolds, by covalent or non-covalent binding. Once bound to a scaffold, a transglutaminase-linkable protein provides a means to attach the scaffold to a second scaffold and / or tissue or organ.
Scaffolds can be made from any biocompatible and / or biodegradable material. In some embodiments, the scaffold is made from a carbohydrate polymer. In one embodiment, the scaffold is made from chitosan or a derivative thereof. In some embodiments, the scaffold is made from the composites described herein.
In some embodiments, the scaffold is made from a transglutaminase-linkable protein.
<u style="single">Definition</u> Unless otherwise stated or implied by context, the following terms and phrases embrace the meanings provided below. Unless otherwise explicitly stated or clear from the context, the following terms and phrases do not preclude the meaning they have acquired in the field of technology to which they belong. These definitions are provided to assist in the description of the individual embodiments and are not intended to limit the inventions described in the claims. Only limited. Further, unless the context requires otherwise, the singular term embraces the plural, and the plural term embraces the singular.
As used herein, the term "contains" or "contains" is an essential composition of the invention that allows unspecified elements to be included, whether essential or not. Used with reference to objects, methods and their constituents. The terms "contain" and "contain" include the terms "consisting of" and "consisting of essentially".
As used herein, the term "becomes essential" refers to an element required in a given embodiment. The term allows for the presence of additional elements that do not substantially affect the basic and novel or functional features of aspects of the invention.
The term "consisting of" refers to the compositions, methods and their respective constituents described herein that are exclusive to any element not mentioned in the description of that embodiment.
All numbers representing the amounts of components or reaction conditions used herein are the term "about" in all examples, except in the examples performed, or unless indicated otherwise. It should be understood that it is modified by. The term "about" can mean ± 1% when used in connection with percentages.
The singular terms "one (a)", "one (an)" and "the" include multiple references unless the context explicitly indicates otherwise. Similarly, the word "or" is intended to include "and" unless the context explicitly indicates otherwise.
Methods and materials similar or equivalent to those described herein can be used to carry out or test this disclosure, but suitable methods and materials are described below. The term "include" means "include". The abbreviation "eg (eg)" is derived from the Latin word exempli gratia and is used herein to provide non-limiting examples. Therefore, the abbreviation "for example" is synonymous with the term "for example".
The terms "reduced", "reduced" or "inhibited" are all used herein to mean a statistically significant amount of reduction as a whole. However, to answer the question, "decrease", "decrease" or "inhibition" is a decrease of at least 10% compared to the reference level, eg, at least about 20%, or at least about 30%, or A reduction of at least about 40%, or at least about 50%, or at least about 60%, or at least about 70%, or at least about 80%, or at least about 90%, or a reduction of up to 100%, including 100% (eg,). Absent level compared to the reference sample), or any reduction between 10 and 100% compared to the reference level.
The terms "increase" or "enhancement" or "activation" are all used herein to mean a statistically significant amount of increase; to answer the question, "increase" or The term "enhancement" or "activation" is an increase of at least 10% compared to the reference level, eg, at least about 20%, or at least about 30%, or at least about 40%, or at least about 50%, or Increase of at least about 60%, or at least about 70%, or at least about 80%, or at least about 90%, or up to 100% including 100%, or between 10 and 100% compared to reference level Any increase in, or at least about 2 times, or at least about 3 times, or at least about 4 times, or at least about 5 times, or at least about 10 times, or 2 to 10 times the reference level. Means any increase in between, or more.
The term "statistically significant" or "significantly" refers to statistical significance and means that the overall normal or low marker concentration is 2 standard deviations (2SD) below. This term represents statistical evidence that there is a difference there. This is defined as the probability that a decision to reject the null hypothesis will be made if the null hypothesis is actually true. This determination is often made using the p-value.
As used herein, the terms "effective" and "effectiveness" include both pharmacological efficacy and physiological safety. Pharmacological efficacy represents the ability of the treatment to produce the desired biological effect in the patient. Physiological safety represents the level of toxicity or other adverse physiological effects at the cellular, organ and / or biological level caused by the performance of the procedure (often referred to as side effects). "Low efficacy" means that the treatment results in a therapeutically significantly lower level of pharmacological efficacy and / or a therapeutically higher level of adverse physiological effect.
As used herein, "subject" means human or animal. Usually, the animal is a vertebrate, such as a primate, rodent, livestock or hunting animal. Primates include chimpanzees, cynomolgus monkeys, spider monkeys and macaques, such as rhesus monkeys. Rodents include mice, rats, woodchuck, ferrets, rabbits and hamsters. Livestock and hunting animals include cats, horses, pigs, deer, bison, buffalo, cat species such as domestic cats, dog species such as dogs, foxes, wolves, bird species such as chickens, emu, ostriches, and fish such as fish. Includes trout, cats and salmon. Patients or subjects include any subpopulation within the above, eg, all of the above except one or more groups or species, eg humans, primates or rodents. In certain aspects of the aspects described herein, the subject is a mammal, such as a primate, such as a human. The terms "patient" and "subject" are used interchangeably herein. The terms "patient" and "subject" are used interchangeably herein. The subject can be male or female.
Preferably, the subject is a mammal. Mammals can be humans, non-human primates, mice, rats, dogs, cats, horses or cows, but are not limited to these examples. Mammals other than humans can be beneficial in that they can be used as subjects to represent animal models of disorders associated with autoimmune diseases or inflammation. In addition, the methods and compositions described herein can be used to treat domesticated animals and / or pets.
The present invention can be defined by any of the following numbered terms. 1. A composite laminate containing a carbohydrate-based substrate and protein. 2. The composite laminated material according to paragraph 1, wherein the carbohydrate-based substrate comprises a film, fiber, sponge, mesh, foam, or nanoscale structure. 3. The composite laminated material according to any one of Items 1 and 2, wherein the carbohydrate-to-protein ratio is in the range of 10: 1 to 1:10. 4. Carbohydrate-based substrates are chitin, fructo-oligosaccharides, galactooligosaccharides, mannan oligosaccharides, glycogen, starch (amylopectin), glycosaminoglycans (eg, hyaluronic acid, chondroitin-4-sulfate, chondroitin-6- Sulfuric acid, dermatin sulfate, keratin sulfate, heparin, and similar), cellulose, β-glucan (zymosan, lentinan, cizophyllan), maltodextrin, inulin or levan β (2 6) -based substrate, 1st ~ The composite laminated material according to any one of Section 3. 5. The composite laminated material according to any one of Items 1 to 4, wherein the carbohydrate-based base material is a chitosan-based base material. 6. The proteins are silk fibron, perklin, abductin, elastin, lecillin, fibronectin, fibrinogen, keratin, titin, collagen, actin, Arp2 / 3, coronin, dystrophin, FtsZ, myosin, spectrin, tau (protein), tubulin, The composite laminated material according to any one of Items 1 to 5, selected from the group consisting of F-spondin, picaturin, fragments and analogs thereof and derivatives thereof, and any combination thereof. 7. The composite laminated material according to paragraph 1, wherein the carbohydrate is chitosan, the protein contains silk fibroin, and the ratio of chitosan to silk fibroin is in the range of 1: 1.5 to 1: 2. 8. The composite laminate according to any one of paragraphs 1-7, wherein the carbohydrate-based substrate comprises at least one surface having a pre-defined microtopography and the protein is applied to the surface. material. 9. The composite laminated material according to paragraph 8, wherein the pre-defined microtopography is molded into a carbohydrate-based substrate. Ten. The composite laminated material according to any one of items 1 to 9, wherein the protein comprises at least one surface having a predetermined microtopography. 11. The composite laminated material according to paragraph 10, wherein the pre-defined microtopography is molded into the protein. 12. The composite laminated material according to any one of paragraphs 1 to 11, further comprising a second carbohydrate-based substrate. 13. The composite laminated material according to paragraph 12, wherein the second carbohydrate-based substrate is a chitin-based substrate. 14. Carbon fibers, carbon nanotubes, glass fibers, small molecules, polymers, proteins, peptides, peptide mimetics, nucleic acids, organic compounds, inorganic compounds, crystalline compounds, biological compounds, bioactive compounds, compounds with biological activity , And a molecule selected from the group consisting of biological, pharmaceutical or therapeutic agents, and any combination thereof, in at least one layer of the carbohydrate layer or the protein layer, paragraphs 1-13. The composite laminated material according to any of the above. 15. The method of paragraph 14, wherein the molecule is present in the carbohydrate layer. 16. 15. The method of paragraph 15, wherein the molecule is covalently linked to the carbohydrate layer. 17. The method of paragraph 14, wherein the molecule is present in the protein layer. 18. The method of paragraph 17, wherein the molecule is covalently linked to the protein layer. 19. The composite laminated material according to any one of paragraphs 14 to 18, wherein the crystalline substance is calcium carbonate. 20. The composite laminate according to any of paragraphs 1-19, further comprising a water repellent coating on at least a portion of the composite. 21. The composite laminated material according to paragraph 20, which is composed of parylene. 22. The composite laminated material according to any one of paragraphs 20 to 21, which exhibits mechanical properties that change depending on the position of the water repellent coating on a part of the composite material when exposed to an aqueous environment. 23. A method of forming a composite laminated material The process of supplying carbohydrate-based substrates, and Step of contacting the carbohydrate-based substrate with the protein solution Including methods. twenty four. The carbohydrate-based substrate is chitin, fructo-oligosaccharide, galactooligosaccharide, mannan oligosaccharide, glycogen, starch (amylopectin), glycosaminoglycan (eg, hyaluronic acid, chondroitin-4-sulfate, chondroitin-6-sulfate). , Dermatin sulfate, keratin sulfate, heparin, etc.), cellulose, β-glucan (zymosan, lentinan, cizophyllan), maltodextrin, inulin or levan β (2 6) -based substrate, according to paragraph 23. 25. The method of any of paragraphs 23-24, wherein the carbohydrate-based substrate is a chitosan-based substrate. 26. The proteins are silk fibroin, perklin, abductin, elastin, lecillin, fibronectin, fibrinogen, keratin, titin, collagen, actin, Arp2 / 3, coronin, dystrophin, FtsZ, myosin, spectrin, tau (protein), tube. 28. The method of any of paragraphs 23-25, selected from the group consisting of phosphorus, F-spondin, picaturin, fragments and analogs and derivatives thereof, and any combination thereof. 27. 28. The method of any of paragraphs 23-36, wherein the carbohydrate-to-protein ratio is in the range of 10: 1 to about 1:10. 28. The method of any of paragraphs 23-27, wherein the carbohydrate-based substrate is formed by dehydrating a solution of the carbohydrate-based material. 29. The method of paragraph 28, wherein the solution of the carbohydrate-based material comprises an acid. 30. The acids are itaconic acid, polyitaconic acid, aconitic acid, uric acid, glucuronic acid, formic acid, acetic acid, trichloroacetic acid, propionic acid, butanoic acid, 4-chlorobutanoic acid, 3-chlorobutanoic acid, 2-bromobutanoic acid, 2- Chlorobutanoic acid, chloric acid, hypochlorous acid, citric acid, gluconic acid, lactic acid, oxalic acid, tartaric acid, ascorbic acid, meldrum acid, hydrofluoric acid, hydrochanic acid, hydrogen sulfide, ortholic acid, sulfite, carbonic acid, weak 28. The method of paragraph 29, selected from the group consisting of conjugated acids of bases and any combination thereof. 31. The step of neutralizing the carbohydrate-based material by applying a basic solution The method of any of paragraph 29 or 30, further comprising. 32. From the group consisting of sodium hydroxide, ammonium hydroxide, potassium hydroxide, calcium hydroxide, magnesium hydroxide, barium hydroxide, strontium hydroxide, lithium hydroxide, rubidium hydroxide, sodium carbonate and ammonia. 30. The method of claim 30, wherein the method comprises a base of choice or the basic solution is a high pH buffer. 33. The method of paragraph 32, wherein the high pH buffer is a carbonate buffer. 34. The method of any of paragraphs 23-33, wherein a solution of the carbohydrate-based material is lyophilized to form the carbohydrate-based substrate. 35. The method of any of paragraphs 23-33, wherein the carbohydrate-based substrate is formed by injecting air bubbles into a solution of the carbohydrate-based material. 36. The method of any of paragraphs 23-33, wherein the carbohydrate-based substrate is formed by spinning a carbohydrate-based solution to form fibers. 37. The method of any of paragraphs 23-33 or 35, wherein the carbohydrate-based substrate is formed by electrospinning a chitin-based solution to form fibers. 38. The method of any of paragraphs 22-32 or 35, wherein the carbohydrate-based substrate is formed by rotary spinning a carbohydrate-based solution to form fibers. 39. Step of inducing β-transition of the protein The method according to any of paragraphs 23 to 38, further comprising. 40. Inducing the β-transition by treating the protein with one or more of alcohol, organic solvents, aqueous solutions, or one or more of the factors including the application of stress, the application of pressure or the application of heat, paragraph 39. The method described. 41. Carbon nanotubes, glass fibers, small molecules, polymers, proteins, peptides, peptide mimetics, nucleic acids, organic compounds, inorganic compounds, crystalline substances, biological compounds, bioactive compounds, bioactive compounds, and organisms. The step of introducing a possession material selected from the group consisting of a scientific, pharmaceutical or therapeutic agent, and any combination thereof into the composite material. The method according to any of paragraphs 23-40, further comprising. 42. The method of paragraph 40, wherein the holding material is covalently linked to the composite material. 43. A composition of a substance formed by any of the methods described in paragraphs 23-42. 44. A prosthetic device comprising a composition of substances formed by any of the methods described in paragraphs 23-42. 45. A tissue engineering scaffold containing a composition of substances formed by any of the methods described in paragraphs 23-42. 46. A drug delivery device comprising a composition of substances formed by any of the methods described in paragraphs 23-42. 47. A transplantable material comprising a composition of substances formed by any of the methods described in paragraphs 23-42. 48. A material comprising a composition of a substance formed by any of the methods described in paragraphs 23-42, wherein the composition comprises a mineral or crystalline substance. 49. A thin transparent film containing a composition of substances formed by any of the methods described in paragraphs 23-42. 50. A multilayer material comprising a composition of substances formed by any of the methods described in paragraphs 23-42. 51. A multilayer material comprising a composition of a substance formed by any of the methods described in paragraphs 23-42, wherein the composition comprises additional components to provide the mechanical properties for the purpose. 52. A material comprising a composition of a substance formed by any of the methods of paragraphs 23-42, comprising a water repellent coating material. 53. A variable region of a water repellent coating material, comprising a composition of a substance formed by any of the methods of paragraphs 23-42, wherein the composition provides a region of variable flexibility. Including, material. 54. A method of forming a composite laminated material The process of dissolving a chitin-based material in an acidic solution, The step of forming a chitin-based structure of the chitin-based material by evaporating the solvent, A step of treating the chitin-based structure with a basic solution to neutralize the protonated amino groups. The step of cleaning the chitin-based structure, Optionally, a step of dehydrating the chitin-based structure, A step of applying a protein solution to the chitin-based structure to produce a composite material having at least one protein layer on the surface of the chitin-based structure. The step of drying the protein layer on the surface of the chitin-based structure, and The step of treating the composite with an alcohol-based solution to induce β-transition of the protein. Including methods. 55. 54. The method of paragraph 54, wherein the chitin-based material-to-protein ratio is in the range of 10: 1 to 1:10. 56. The method of any of paragraphs 54-55, wherein the chitin-based material is chitosan. 57. The method of any of paragraphs 54-56, wherein the protein is fibroin. 58. The method of any of paragraphs 54-57, wherein the acidic solution comprises acetic acid. 59. The method of any of paragraphs 534-58, wherein the basic solution comprises NaOH. 60. The method of any of paragraphs 54-59, wherein the alcohol-based solution comprises methanol. 61. A composition of a substance formed by any of the methods described in paragraphs 54-60. 62. A method of adhering a medical implant device to a tissue or organ, in which an effective amount of transglutaminase is applied to the surface of the tissue or organ, and The step of bringing the medical implant device into contact with the surface of the tissue Including methods. 63. The method of paragraph 62, wherein the medical transplant device comprises transglutaminase. 64. A method of adhering a medical transplant device to a tissue or organ, The step of contacting the medical transplant device containing an effective amount of transglutaminase with the organ. Including methods. 65. Step of applying the effective amount of transglutaminase to the surface of the tissue 65. The method of paragraph 65, further comprising. 66. The method according to any of paragraphs 62-65, wherein the transglutaminase is a mammalian transglutaminase. 67. The method according to any of paragraphs 62 to 65, wherein the transglutaminase is a microbial transglutaminase (mTgase). 68. The method of any of paragraphs 62-67, wherein the transglutaminase is a calcium-independent transglutaminase. 69. The transglutaminase is factor XIII (fibrin stabilizing factor), type 1 transglutaminase (keratinocyte transglutaminase), type 2 transglutaminase (tissue transglutaminase, tTgase), type 3 transglutaminase (epithelial transglutaminase), type 4. Selected from the group consisting of transglutaminase (prostatic transglutaminase), type 5 transglutaminase (transglutaminase X), type 6 transglutaminase (transglutaminase Y), type 7 transglutaminase (transglutaminase Z), and any combination thereof. The method according to any one of paragraphs 62 to 68. 70. The transglutaminase is formulated as a solution, emulsion, aerosol, foam, ointment, paste, lotion, powder, gel, hydrogel, hydrophilic colloid, microparticles, nanoparticles, or cream, paragraphs 62-69. Any of the methods described. 71. The medical transplant device is selected from the group consisting of artificial tissues, artificial organs, prosthetic devices, drug delivery devices, wound dressings, films, foams, sponges, hemostatic materials, and any combination thereof, 62nd The method described in any of items ~ 70. 72. The medical implant device is a wound dressing selected from the group consisting of bandages, gauze, tapes, meshes, nets, sardines, films, membranes, patches, microparticles, nanoparticles, and any combination thereof. There is a method according to paragraph 71. 73. The method of paragraph 71, wherein the medical implant device is a foam. 74. The method of any of paragraphs 62-73, wherein the medical transplant device comprises a protein and the protein can be crosslinked by transglutaminase. 75. The method of paragraph 74, wherein the medical transplant device is coated with the protein. 76. The method according to any of paragraphs 74-75, wherein the protein is silk fibroin. 77. 62-76. The method of any of paragraphs 62-76, wherein the transglutaminase is coated on the surface of the medical transplant device. 78. The method of any of paragraphs 62-77, wherein the transglutaminase is non-covalently linked to the medical transplant device. 79. The effective amount of transglutaminase is 1 cm of contact surface area between the tissue or organ and the medical transplant device.<sup>2</sup>The method according to any of paragraphs 62 to 78, wherein the amount is about 1 μg to about 100 mg per unit. 80. The process of administering a wound healing substance The method of any of paragraphs 62-79, further comprising. 81. The wound healing substances are dexpantenol; growth factors; enzymes, hormones; povidone iodine; fatty acids; anti-inflammatory agents; antibiotics; antibacterial agents; disinfectants; cytokines; thrombins; painkillers; opioids; aminoxyl; floxane; nitrosothiol; Nitrate and anthocyanins; nucleosides such as adenosine; and nucleotides such as adenosine diphosphate (ADP) and adenosine triphosphate (ATP); neurotransmitters / neuromodulators such as acetylcholine and 5-hydroxytryptamine (serotonin / 5- HT); histamine and catecholamines such as adrenaline and noradrenaline; lipid molecules such as sphingosine-1-phosphate and lysophosphatidic acid; amino acids such as arginine and lysine; peptides such as bradykinin, substance P and calcium gene-related peptides (CGRP); 80. The method of paragraph 80, selected from the group consisting of nitrogen monoxide; as well as any combination thereof. 82. The method of any of paragraphs 62-81, wherein the medical implant device is made from a biocompatible and biodegradable material. 83. 62-82. The method of any of 62-82, wherein the medical implant device is made from the composite material of any of 1-21. 84. The method of any of paragraphs 62-83, wherein the applied step comprises increasing the expression or activity of the host transglutaminase. 85. A method of promoting wound healing in subjects who need it, The process of applying an effective amount of transglutaminase to the wound surface, and A step of bringing a wound dressing containing the composite material according to any one of paragraphs 1 to 21 into contact with the wound. Including methods. 86. A step of applying a foam containing the composite material according to any one of paragraphs 1 to 21 to the wound. 85. The method of paragraph 85. 87. The wound results from incisions and lacerations, surgical incisions, puncture wounds, scratches, scratches, compression wounds, scratches, friction wounds, chronic wounds, ulcers, thermal wounds, chemical wounds, pathogen infections. 85-86 selected from the group consisting of wounds, skin grafts / graft donors and recipient sites, immune response status, oral wounds, gastric or intestinal wounds, injured cartilage or injured bone, cut sites, and corneal lesions. The method described in any of the sections. 88. 28. The method of any of paragraphs 85-87, wherein the transglutaminase is a mammalian transglutaminase. 89. The method according to any of paragraphs 85-87, wherein the transglutaminase is a microbial transglutaminase (mTgase). 90. The method according to any of paragraphs 85-89, wherein the transglutaminase is a calcium-independent transglutaminase. 91. The transglutaminase is factor XIII (fibrin stabilizing factor), type 1 transglutaminase (keratinocyte transglutaminase), type 2 transglutaminase (tissue transglutaminase), type 3 transglutaminase (epithelial transglutaminase), type 4. Selected from the group consisting of transglutaminase (prostatic transglutaminase), type 5 transglutaminase (transglutaminase X), type 6 transglutaminase (transglutaminase Y), type 7 transglutaminase (transglutaminase Z), and any combination thereof. The method according to any one of paragraphs 85 to 90. 92. 28-91, wherein the transglutaminase is formulated as a solution, emulsion, aerosol, foam, ointment, paste, lotion, powder, gel, hydrogel, hydrophilic colloid, microparticles, nanoparticles, or cream. Or the method described. 93. any of paragraphs 85-92, wherein the wound dressing is selected from the group consisting of bandages, gauze, tapes, meshes, nets, scabies, films, membranes, patches, and any combination thereof. Method. 94. The method of any of paragraphs 85-93, wherein the transglutaminase is bound to the wound dressing. 95. The method of paragraph 94, wherein the transglutaminase is coated on the surface of the wound dressing. 96. The method of any of paragraphs 94-95, wherein the transglutaminase is non-covalently linked to the wound dressing. 97. The effective amount of transglutaminase is 1 cm in wound area.<sup>2</sup>The method according to any of paragraphs 85-96, wherein the amount is about 1 μg to about 100 mg per. 98. The process of administering a wound healing substance to a subject The method of any of paragraphs 85-97, further comprising. 99. The wound healing substances are dexpantenol; growth factors; enzymes, hormones; povidone iodine; fatty acids; anti-inflammatory agents; antibiotics; antibacterial agents; disinfectants; cytokines; thrombins; painkillers; opioids; aminoxyl; floxane; nitroso Thiol; nitrate and anthocyanin; nucleoside; nucleotides; neurotransmitters / neuromodulators such as acetylcholine and 5-hydroxytryptamine (serotonin / 5-HT); histamine and catecholamines such as adrenaline and noradrenaline; lipid molecules such as sphingosine-1 -Selected from the group consisting of phosphates and lysophosphatidic acids; amino acids such as arginine and lysine; peptides such as bradykinin, substance P and calcium gene-related peptides (CGRP); nitrogen monoxide; and any combination thereof. The method described in paragraph 98. 100. 28. The method of any of paragraphs 85-99, wherein the applied step comprises increasing the expression or activity of the host transglutaminase. 101. The method of any of paragraphs 85-99, wherein the applied step is performed before, after, or during contact with the medical implant device or wound dressing.
To the extent not shown so far, any one of the various aspects described and exemplified herein shall incorporate the features exhibited in any of the other aspects disclosed herein. It will be appreciated by those skilled in the art that it can be further modified. Thus, other aspects are within the scope of the invention and within the spirit of the invention. Further, although the above description refers to the present invention, the description may include a plurality of inventions.
<p> GENERAL herein present invention which are substantially shown and described, by may it but be more readily understood by reference to the following examples, however, these examples are certain aspects of the present invention And are included only for the purpose of exemplifying aspects, and are not intended to limit the present invention.</p><p> Approximately 20 mg / cm of transglutaminase in powder form<sup>2</sup>The tissue was applied to the tissue and the tissue was coated with a hydrated film (either Schrilk or chitosan film). After binding for 30 minutes at room temperature, the sample was subjected to a peel test. The result of the peeling test is shown in FIG. We have found that either side of the Schrilk film (carbohydrate layer or protein layer) can be contacted with the tissue for binding.</p><p> Similar experiments were performed to test binding to dermal tissue. Since the final layer of epithelium is produced by keratinization, this layer may be the only tissue in the subject that has no groups available for binding by transglutaminase treatment. This was confirmed by the result that no binding by transglutaminase was observed. However, as demonstrated in the experiment in which Schrilk bound to the dermis rather than the epithelium, as shown in Figure 25, if this final layer is slightly damaged and the second layer is exposed, the binding by transglutaminase is success. This indicates that Schrilk can be used as a "patch" (eg, bandage) for skin treatment.</p><p> All patents and other publications specified herein are expressly incorporated herein by reference for all purposes. These publications are only provided as disclosures prior to the filing date of the present application. It is acknowledged that no circumstances in this context qualify us to claim a date prior to such disclosure, either because it is a prior invention or for any other reason. It should not be interpreted as a thing. All references to dates or indications regarding the content of these documents are based on the information available to the applicant and do not constitute an endorsement of the accuracy of that date or the content of these documents.</p>
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| Event | Code | |
|---|---|---|
| Receipt of annual feesJAPANESE INTERMEDIATE CODE: R250R250 | R250 | |
| Receipt of annual feesJAPANESE INTERMEDIATE CODE: R250R250 | R250 | |
| Receipt of annual feesJAPANESE INTERMEDIATE CODE: R250R250 | R250 | |
| Receipt of annual feesJAPANESE INTERMEDIATE CODE: R250R250 | R250 | |
| Receipt of annual feesJAPANESE INTERMEDIATE CODE: R250R250 | R250 | |
| Receipt of annual feesJAPANESE INTERMEDIATE CODE: R250R250 | R250 | |
| Receipt of annual feesJAPANESE INTERMEDIATE CODE: R250R250 | R250 | |
| Certificate of patent or registration of utility modelJAPANESE INTERMEDIATE CODE: R150R150 | R150 | |
| First payment of annual fees (during grant procedure)JAPANESE INTERMEDIATE CODE: A61A61 | A61 | |
| Written decision to grant a patent or to grant a registration (utility model)JAPANESE INTERMEDIATE CODE: A01A01 | A01 | |
| Decision of grant or rejection writtenTRDD | TRDD | |
| Transfer to examiner for re-examination before appeal (zenchi)AppealJAPANESE INTERMEDIATE CODE: A911A911 | A911 | |
| Request for written amendment filedJAPANESE INTERMEDIATE CODE: A523A521 | A521 | |
| Request for written amendment filedJAPANESE INTERMEDIATE CODE: A523A521 | A521 | |
| Decision of refusalJAPANESE INTERMEDIATE CODE: A02A02 | A02 | |
| Request for written amendment filedJAPANESE INTERMEDIATE CODE: A523A521 | A521 | |
| Notification of reasons for refusalJAPANESE INTERMEDIATE CODE: A131A131 | A131 | |
| Notification of resignation of power of attorneyJAPANESE INTERMEDIATE CODE: A7424RD04 | RD04 | |
| Request for written amendment filedJAPANESE INTERMEDIATE CODE: A523A521 | A521 | |
| Written request for application examinationJAPANESE INTERMEDIATE CODE: A621A621 | A621 |
Numbers
- Publication
- 2013536734
- Publication, DOCDB
- 2013536734
- Publication, EPODOC
- JP2013536734
- Application
- 2013527187
- Application, DOCDB
- 2013527187
- Application, EPODOC
- JP20130527187
Titles2
- Japanese
- 高強度キチン複合材料および製造方法
- English
- High-strength chitin composites and manufacturing methods
Classification
- CPC, 34
- A61L15/38
- A61L27/20
- A61L27/24
- C08L5/08
- A61L27/227
- A61L27/34
- A61L27/48
- A61L27/54
- A61L27/56
- A61L15/425
- A61L15/44
- A61L15/52
- C08L1/02
- C08L3/02
- C08L5/00
- C08L5/10
- C08L89/00
- A61P1/02
- A61P1/04
- A61P17/02
- A61P19/08
- A61P25/04
- A61P27/02
- A61P29/00
- A61P31/00
- A61P31/04
- A61P37/06
- A61P43/00
- A61L27/22
- A61F13/00
- A61L15/225
- B05D3/104
- A61L15/28
- A61L15/325
- IPC, 2
- A61L27 00
- A61L15 16
Designated states5
- Regional, 4
- Zimbabwe
- Turkmenistan
- Türkiye
- Togo
- National, 1
- Zambia