本研究では、生体材料（BMM）研究所の研究プログラムで実施した。 BMMは、経済情勢、農業イノベーションのオランダの省cofundedされています。 NederlandseのHartstichtingの財政的貢献は感謝して承諾されます。

1。ヒト伏在静脈細胞の培養<ol><li> 9。シュネルらのプロトコールに従って、二次利用の材料のためのガイドラインに従ったドナーから取得した伏在静脈マグナから細胞を分離し、液体窒素中で、これらを保存する。 6ウェルプレートでの培養に2×2mmの1ドナー切断片から伏在静脈マグナの一部から。ウェルあたり2枚を使用してください。一般に十分な細胞を液体窒素中で0.25×10 6細胞を約3バイアルを充填するために得ることができる。 HVSCsはビメンチン、デスミンの発現およびα平滑筋アクチン10を表現する集団の発現を示すことによって、筋線維芽細胞として特徴付けられる。次に進む細胞数を増加させる液体窒素から細胞を解凍するためのプロトコルを開始する。 </li><li> T75組織培養フラスコに1バイアルからの細胞を配置し、アドバンストDMEM 50mlのウシ胎児血清（FBS）、5 mlのペニシリン/からなる増殖培地（GM）を加えるストレプトマイシン5mlのL-グルタマックス。 2〜3日ごとに培地を変更します。 </li><li>細胞は約14日後にコンフルエントに成長。継代1と呼ばれる液体窒素で1バイアルに保管0.5×10 6細胞、。 </li></ol> 注：細胞の凍結がHVSCsを収穫するときには必要ありませんが、もっぱら貯蔵のために使用されます。 <ol start="4"><li> T175組織培養フラスコに1バイアルからHVSCsを置き、GMを追加します。 2〜3日ごとに培地を変更します。細胞は約7日後にコンフルエントに成長。液体窒素で1バイアルに保管3×10 6個の細胞、通路2と呼ばれる。 </li><li> rollerbottleに1バイアルから細胞を配置し、GMを追加します。 2〜3日ごとに培地を変更します。細胞が約8日後にコンフルエントに成長。 One rollerbottleは約20〜30×10 6個の細胞が含まれています。通路6に培養細胞まで。細胞表現型が変化するかもしれないので、通路9よりも高く、通路のセルを使用しないでください。 </li></oL&gt; 2。フィブリンベースの組織構築のエンジニアリング<ol><li>硬化剤（10:1）とエラストマーとを混合することにより、シリコーン接着剤を準備します。ベルクロの7×3mmの長方形のセグメントをカットします。クロスを形成する、とベルクロストリップ間3mmの二乗のスペースを残して柔軟性のある膜を有する6ウェル培養プレートに接着剤はベルクロ、。 </li></ol> 注：のみベルクロのソフト面を使用し、この面を上に直面しています。とき接着ベルクロは、唯一のシリコーン接着剤でベルクロをカバー、うまく全体にのりを広げません。培養プレートは、シリコーン膜底を持っているので、プレートに簡単に接着を確保するために、柔軟性のある膜を補強するためのウェルプレートの下に何かを使用しています。 <ol start="2"><li>接着剤の硬化を保証するために60°Cのオーブンで一晩シリコーン接着剤を乾燥させる。 30分間インキュベートし、ウェルに70％エタノールを加えることによって滅菌する。 PBSで3回すすぎ、WELからすべてのPBSを削除lsコマンドとベルクロ。 30分間UV下に置き、使用するまで無菌に保つ。 </li><li>ティッシュエンジニアリングのGMから成る培地（TM）、およびL-アスコルビン酸2 - リン酸の130mgのを準備します。 </li><li> TMに1 mg / mlのε-アミノカプロン酸（ACA）を追加します。 ACAは、分解11からフィブリンを防止するために、培養の最初の7日間に使用される。あるいは、アプロチニンを使用することができる。 </li><li>塊の形成を防ぐために、フィブリノゲン、開口前に室温に到達させる。塊のフィブリノゲンことなく、より簡単に溶解します。 ACAを補っ10mgを実際タンパク質/ mlのTM 7の濃度にフィブリノゲンを溶かす。無菌フィルターフィブリノゲン溶液、複数のフィルタが必要になることがあります。使用するまで氷上に保管してください。 </li></ol> 注：あまりにも多くの泡の形成を防止するために優しくフィブリノゲン混合物を溶解する。 <ol start="6"><li> ACAを補った10 IU / mlのTM 7の濃度にトロンビンを溶かす。使用するまで氷上に保管してください。 </li> &lt;/ OL&gt; 注：氷上のストレージがトロンビンとフィブリノゲンの早期ゲル化を防ぐために必要とされる。 <ol start="7"><li> GMとカウントに再懸濁した細胞を、トリプシン処理。 </li><li>フィブリンベースの組織構造（組織工学心臓弁7のための方法に基づいて濃度）を播種するための15×10 6細胞/ mlを使用してください。シングルゲルは100μlのGOFエル、したがって1.5×10 6個の細胞で構成されています。説明するゲルの数と同数の遠心管をもたらす、ある遠心管に1.5×10 6細胞を入れた。 </li><li> 7分間350 xgで細胞を遠心し、上清を捨てる。 50μlのトロンビンで細胞を再懸濁します。この懸濁液に青色蛍光ポリスチレン微小球の4μLを加える。バイアルにフィブリノゲン液50μlを入れて。細胞を50μlのトロンビンを取るためにピペットを使用してください。 100μlにピペットの容積を大きくします。トロンビン50μlの溶液とをピペットトロンビンおよびフィブリノゲンを混ぜ、そして100μlの混合物を取るためにフィブリノゲンとバイアルへの細胞。 </li></ol> 注 ：蛍光ポリスチレン微小球は、画像解析のための内部基準マーカとして使用される。トロンビンおよびフィブリノゲンを混合する際に、注意深く混合物をピペットで気泡の形成を防止する。気泡がフィブリンゲルの穴になります。 <ol start="10"><li>へとベルクロストリップ間にゲル混合物をピペット。フィブリンゲルの典型的なゲル化時間は、一度成分が混合され、20秒程度である。 </li></ol> 注 ：混合物をウェルプレートにピペットれる前にゲル化を防ぐために、できるだけ早くこれを行います。細胞やビーズを使用する前に練習。 <ol start="11"><li> ACAで培養TMを追加する前にゲル化を可能にするために加湿95％空気/ 5％CO 2インキュベーター内で37℃で30分間懸濁液をインキュベート。 </li><li>最初の7日ごとに2〜3日は、ACAとTMを交換してください。ゲルはACAずに培養することが、一週間後には十分安定している。最初の週の後2〜3日ごとにTMを交換してください。ウェルあたりTM 6mlのを追加します。当日12細胞が可視化のために十分なコラーゲンを作り出した。 </li></ol> 3。ひずみと制約のひずみと誘導の変更の適用<ol><li>静的株は、細胞トラクションとコンパクション12により直接細胞によって適用される。コラーゲン再編を誘導するために、組織が一つの方向に2つのベルクロストリップから緩い構築カット。一方向の制約この結果（ 図1A）。構文はその後安定した十分で、コラーゲンが堆積されているので、12日目でこれを実行します。 </li><li>のFlexCell FX4000Tシステムを用いて、可撓膜と培養プレートの底部に真空を適用することにより、環状歪みを適用する。番目の一部であるローディングポスト（の上に、ベースプレートにプレートを置きます電子環状ローディング装置）。ポンプは膜に真空を適用することにより、下に横たわっている長方形のポストを介して膜を引っ張る。メンブレン（ベルクロを介して）組織構造の十字形添付ファイルや長方形のポストのために、適用された環状株は（ 図1B）一軸です。 </li><li>当初、巡回ひずみの適用は6日目に開始する前に、初期の機械的完全性を達成するために5日間静置培養を使用しています。真空ポンプ用のコントローラにプログラムは、環状染色プロトコル。例えば一軸方向13で、以前に確立された断続的な巡回ひずみプロトコルを使用します。これは3時間休憩期間と交互に3時間の期間の0〜5％の株からいきみ1Hzの正弦波、、、の断続的な歪みから構成されています。整列コラーゲン組織を誘導、7日間この巡回ひずみプロトコルを実行します。 </li><li>一般的に12日後にHVSCs、整列コラーゲンorganizatioを作り出したN。整列コラーゲン組織に到達した後、元の歪みの方向に対して垂直になるように、一軸環状歪み方向を変える。 90°長方形のポストを回してこれを行います。 </li></ol> 4。可視セルとコラーゲン<ol><li>細胞生存率またはコラーゲン形成を妨害しないプローブでアクティブなリアルタイムコラーゲンリモデリング、ラベルサンプルを可視化する。蛍光細胞質とコラーゲンを染色するためのプローブを使用します。 </li><li>共焦点レーザー走査顕微鏡を用いて或いは第二高調波発生は、780 nmおよび500〜550 nmの検出で励起し自家蛍光14を用いて、コラーゲン構造を可視化するために使用することができる。 </li><li> 3時間の休息期間中に周期的に緊張したサンプルについては、セットアップとインキュベーターから培養プレートを外し、細胞やコラーゲンを可視化するために共焦点レーザー走査顕微鏡にそれらを転送します。 </li></ol>

<ol>
	<li>Beamish, J. A., He, P., Kottke-Marchant, K., Marchant, R. E. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Molecular+regulation+of+contractile+smooth+muscle+cell+phenotype:+implications+for+vascular+tissue+engineering.">Molecular regulation of contractile smooth muscle cell phenotype: implications for vascular tissue engineering.</a> Tissue Eng. Part B Rev. 16, 467-491 (2010).</li><li>Isenberg, B. C., Tranquillo, R. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Long-term+cyclic+distention+enhances+the+mechanical+properties+of+collagen-based+media-equivalents.">Long-term cyclic distention enhances the mechanical properties of collagen-based media-equivalents.</a> Ann. Biomed. Eng. 31, 937-949 (2003).</li><li>Nichol, J. W., Khan, A. R., Birbach, M., Gaynor, J. W., Gooch, K. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Hemodynamics+and+axial+strain+additively+increase+matrix+remodeling+and+MMP-9,+but+not+MMP-2,+expression+in+arteries+engineered+by+directed+remodeling.">Hemodynamics and axial strain additively increase matrix remodeling and MMP-9, but not MMP-2, expression in arteries engineered by directed remodeling.</a> Tissue Eng. Part A. 15, 1281-1290 (2009).</li><li>Sander, E. A., Stylianopoulos, T., Tranquillo, R. T., Barocas, V. H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Image-based+multiscale+modeling+predicts+tissue-level+and+network-level+fiber+reorganization+in+stretched+cell-compacted+collagen+gels.">Image-based multiscale modeling predicts tissue-level and network-level fiber reorganization in stretched cell-compacted collagen gels.</a> Proc. Natl. Acad. Sci. U.S.A. 106, 17675-17680 (2009).</li><li>Hu, J. J., Humphrey, J. D., Yeh, A. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Characterization+of+engineered+tissue+development+under+biaxial+stretch+using+nonlinear+optical+microscopy.">Characterization of engineered tissue development under biaxial stretch using nonlinear optical microscopy.</a> Tissue Eng. Part A. 15, 1553-1564 (2009).</li><li>Lee, E. J., Holmes, J. W., Costa, K. D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Remodeling+of+engineered+tissue+anisotropy+in+response+to+altered+loading+conditions.">Remodeling of engineered tissue anisotropy in response to altered loading conditions.</a> Ann. Biomed. Eng. 36, 1322-1334 (2008).</li><li>Mol, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Fibrin+as+a+cell+carrier+in+cardiovascular+tissue+engineering+applications.">Fibrin as a cell carrier in cardiovascular tissue engineering applications.</a> Biomaterials. 26, 3113-3121 (2005).</li><li>de Jonge, N., Kanters, F. M., Baaijens, F. P., Bouten, C. V. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Strain-induced+Collagen+Organization+at+the+Micro-level+in+Fibrin-based+Engineered+Tissue+Constructs.">Strain-induced Collagen Organization at the Micro-level in Fibrin-based Engineered Tissue Constructs.</a> Ann. Biomed. Eng. 41 (4), 763-774 (2012).</li><li>Schnell, A. M., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Optimal+cell+source+for+cardiovascular+tissue+engineering:+venous+vs.+aortic+human+myofibroblasts.">Optimal cell source for cardiovascular tissue engineering: venous vs. aortic human myofibroblasts.</a> Thorac. Cardiovasc. Surg. 49, 221-225 (2001).</li><li>Mol, A., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Autologous+human+tissue-engineered+heart+valves:+prospects+for+systemic+application.">Autologous human tissue-engineered heart valves: prospects for systemic application.</a> Circulation. , I152-I158 (2006).</li><li>Ahmann, K. A., Weinbaum, J. S., Johnson, S. L., Tranquillo, R. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Fibrin+degradation+enhances+vascular+smooth+muscle+cell+proliferation+and+matrix+deposition+in+fibrin-based+tissue+constructs+fabricated+in+vitro.">Fibrin degradation enhances vascular smooth muscle cell proliferation and matrix deposition in fibrin-based tissue constructs fabricated in vitro.</a> Tissue Eng. Part A. 16, 3261-3270 (2010).</li><li>John, J., Quinlan, A. T., Silvestri, C., Billiar, K. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Boundary+stiffness+regulates+fibroblast+behavior+in+collagen+gels.">Boundary stiffness regulates fibroblast behavior in collagen gels.</a> Ann. Biomed. Eng. 38, 658-673 (2010).</li><li>Rubbens, M. P., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Intermittent+straining+accelerates+the+development+of+tissue+properties+in+engineered+heart+valve+tissue.">Intermittent straining accelerates the development of tissue properties in engineered heart valve tissue.</a> Tissue Eng. Part A. 15, 999-1008 (2009).</li><li>Chen, W. L., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Multiphoton+imaging+and+quantitative+analysis+of+collagen+production+by+chondrogenic+human+mesenchymal+stem+cells+cultured+in+chitosan+scaffold.">Multiphoton imaging and quantitative analysis of collagen production by chondrogenic human mesenchymal stem cells cultured in chitosan scaffold.</a> Tissue Eng. Part C Methods. 16, 913-920 (2010).</li><li>de Jonge, N., Kanters, F. M., Baaijens, F. P., Bouten, C. V. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Strain-induced+Collagen+Organization+at+the+Micro-level+in+Fibrin-based+Engineered+Tissue+Constructs.">Strain-induced Collagen Organization at the Micro-level in Fibrin-based Engineered Tissue Constructs.</a> Ann. Biomed. Eng. 41, 763-774 (2013).</li><li>Merryman, W. D., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Correlation+between+heart+valve+interstitial+cell+stiffness+and+transvalvular+pressure:+implications+for+collagen+synthesis.">Correlation between heart valve interstitial cell stiffness and transvalvular pressure: implications for collagen synthesis.</a> Am. J. Physiol. 290, (2006).</li><li>Ingber, D. E. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=From+cellular+mechanotransduction+to+biologically+inspired+engineering:+2009+Pritzker+Award+Lecture,+BMES+Annual+Meeting+October+10,+2009.">From cellular mechanotransduction to biologically inspired engineering: 2009 Pritzker Award Lecture, BMES Annual Meeting October 10, 2009.</a> Ann. Biomed. Eng. 38, 1148-1161 (2009).</li><li>Sander, E. A., Barocas, V. H., Tranquillo, R. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Initial+fiber+alignment+pattern+alters+extracellular+matrix+synthesis+in+fibroblast-populated+fibrin+gel+cruciforms+and+correlates+with+predicted+tension.">Initial fiber alignment pattern alters extracellular matrix synthesis in fibroblast-populated fibrin gel cruciforms and correlates with predicted tension.</a> Ann. Biomed. Eng. 39, 714-729 (2010).</li><li>van der Schaft, D. W., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Engineering+Skeletal+Muscle+Tissues+from+Murine+Myoblast+Progenitor+Cells+and+Application+of+Electrical+Stimulation.">Engineering Skeletal Muscle Tissues from Murine Myoblast Progenitor Cells and Application of Electrical Stimulation.</a> J. Vis. Exp. (73), e4267 (2013).</li></ol>

著者は、彼らが競合する経済的利益を持っていないことを宣言します。

細胞移入フィブリン構築物の記載モデル系は、細胞およびコラーゲンの研究のための大きな可能性を秘めている（再）組織（デ·ヨンゲら 15）、組織工学の目的で使用されるなど 。最初の細胞担体としてフィブリンを用いて、フィブリン分解した後、組織、細胞および内因性マトリックスのみを使用して作成される。この方法では、細胞は、境界剛性12、又は表?...

心血管組織が目立つ耐荷重機能を持っています。細胞外マトリックス中のコラーゲン線維の特定のコンテンツと、組織内の耐荷重特性に寄与し、全体的な組織強度1を支配する。組織工学において、構築物の機械的調整が使用されている-典型的には（環状）緊張レジメンから成る-組織組織と機械的性質2,3を向上させることができる。事前定義されたコラーゲンのアーキテクチャを持つ組織を作成するために複雑な組織ジオメトリのひずみ誘起コラーゲン組織の完全な理解は、まだ達成されていません。これは、開発組織におけるコラーゲンリモデリングの我々の限られた知識によるものである。既存のモデルは、主に静的なひずみ4-6の使用とコラーゲンリモデリングの最終的な正味の結果に関する情報を与える。ここでは、影響を受けて、3Dで、リアルタイムの方法でコラーゲン（再）組織の研究を可能にする高度にチューニングモデルシステムを提供静的または環状株の。組織構造は、構造内のすべてのコラーゲンが内因性であることを保証する、フィブリンベースです。コンストラクトの細胞とコラーゲン組織が可視化され、内部リファレンス·システムは、私たちが時間経過解析のための細胞とコラーゲン構造を再配置することができます。これらの細胞は基づいて強化された細胞外マトリックス産生およびエンジニアリング心血管組織7マトリックス、当社設立の使用を改造する能力で知られていますので、このプロトコルでは、人間の伏在静脈細胞（HVSCs）のためのモデルシステムの使用を説明します8デヨングらの作業に

<table border="1">
	<tbody>
		<tr>
			<td>Name</td>
			<td>Company</td>
			<td>Catalog number</td>
			<td>Comments</td>
		</tr>
		<tr>
			<td>Culture plastic</td>
			<td>Greiner</td>
			<td></td>
			<td>Includes culture flasks and pipettes</td>
		</tr>
		<tr>
			<td>Advanced DMEM</td>
			<td>Gibco</td>
			<td>12491</td>
			<td></td>
		</tr>
		<tr>
			<td>Fetal bovine serum</td>
			<td>Greiner</td>
			<td>758075</td>
			<td></td>
		</tr>
		<tr>
			<td>Penicillin/streptomycin</td>
			<td>Gibco</td>
			<td>10378016</td>
			<td></td>
		</tr>
		<tr>
			<td>GlutaMax</td>
			<td>Gibco</td>
			<td>35050-079</td>
			<td></td>
		</tr>
		<tr>
			<td>Elastomer and curing agent</td>
			<td>Dow Corning Corporation</td>
			<td>3097358-1004</td>
			<td>Silastic MDX 4-4210#</td>
		</tr>
		<tr>
			<td>Velcro</td>
			<td>Regular store</td>
			<td></td>
			<td>You can buy this at a regular store, only use the soft side</td>
		</tr>
		<tr>
			<td>Bioflex culture plates</td>
			<td>Flexcell Int</td>
			<td>BF-3001U</td>
			<td>Untreated</td>
		</tr>
		<tr>
			<td>L-Ascorbic Acid 2-phosphatase</td>
			<td>Sigma</td>
			<td>A8960</td>
			<td></td>
		</tr>
		<tr>
			<td>&#949;-Amino Caproic Acid</td>
			<td>Sigma-Aldrich</td>
			<td>D7754</td>
			<td></td>
		</tr>
		<tr>
			<td>Bovine thrombin</td>
			<td>Sigma</td>
			<td>T4648</td>
			<td></td>
		</tr>
		<tr>
			<td>Bovine fibrinogen</td>
			<td>Sigma</td>
			<td>F8630</td>
			<td></td>
		</tr>
		<tr>
			<td>0.45 syringe filter</td>
			<td>Whatmann (Schleicher and Scheul)</td>
			<td>10462100</td>
			<td></td>
		</tr>
		<tr>
			<td>Polystyrene microspheres</td>
			<td>Invitrogen</td>
			<td>F-8829</td>
			<td>Blue fluorescent, 10 &#956;m diameter</td>
		</tr>
		<tr>
			<td>Flexcell FX-4000T</td>
			<td>Flexcell Int</td>
			<td></td>
			<td>Includes rectangular loading posts</td>
		</tr>
		<tr>
			<td>Cell Tracker Orange</td>
			<td>Invitrogen Molecular Probes</td>
			<td>C2927</td>
			<td></td>
		</tr>
		<tr>
			<td>CNA35-OG488</td>
			<td></td>
			<td></td>
			<td>Cordially provided by the Laboratory for Macromolecular and Organic Chemistry, Department of Biomedical Engineering, Eindhoven University of Technology</td>
		</tr>
		<tr>
			<td>Confocal laser scanning microscope</td>
			<td>Carl Zeiss</td>
			<td></td>
			<td>LSM 510 Meta laser scanning microscope and Two-Photon-LSM mode</td>
		</tr>
		<tr>
			<td>Amphotericin</td>
			<td>Gibco</td>
			<td>15290-018</td>
			<td>Needed for cell isolation</td>
		</tr>
	</tbody>
</table>

engineering fibrin-based tissue constructs from myofibroblasts and application of constraints and strain to induce cell and collagen reorganization

コラーゲン組織の開発におけるコラーゲン含有量と組織を局所組織系統および組織制約によって影響され得る。ティッシュエンジニアは、あらかじめ定義されたコラーゲンアーキテクチャと組織を作成するために、これらの原則を使用することを目指します。しかしながら、最終的な組織構造を制御するためのコラーゲンリモデリングの正確な基礎プロセスの完全な理解が欠けている。具体的には、少しは、組織の機械的荷重条件の変化に応じてコラーゲン線維の（再）配向について知られている。私たちは、さらにコラーゲンを解明するために、二軸に制約の筋線維芽細胞シードフィブリン構造から成る、in vitroモデル系で開発された私に反応して（再）配向）一軸静的荷重条件及びiiに軸戻す）二軸に制約の巡回一軸負荷はのFlexCell FX4000Tローディング装置の使用と、方向をロードに変更前と後のコンストラクト。タイムラプス共焦点イメージングは​​viに使用されます非破壊的にコラーゲン（再）配向sualize。 コンストラクトの細胞とコラーゲン組織がリアルタイムで可視化することができ、内部リファレンス·システムは、私たちが時間経過解析のための細胞とコラーゲン構造を再配置することができます。モデル·システムの様々な態様は、細胞源又は健康と病気の細胞の使用のように、調整することができる。添加剤はさらに、例えばMMPの追加やインテグリンを遮断することによって、コラーゲンの再構築のメカニズムを解明するために使用することができる。構築物の形状や大きさを容易に細胞およびコラーゲン（再）組織を研究するための高度に調整可能なモデル系で、その結果、特定のニーズに適合させることができる。

このモデルシステムは、筋線維芽細胞培養シードフィブリンゲルが可能になります。 図1Aは、静的軸制約の下で最初の培養組織を示しています。組織制約は、（ 図1A）、その後、一軸静的な制約を作成するために、2つの制約からフィブリンゲルを切断し、そして組織成形および改造によって解放される。環状株について、組織は同様に静的な二軸制約の下で培養す?...

Watch this Scientific Journal Video about Engineering Fibrin-based Tissue Constructs from Myofibroblasts and Application of Constraints and Strain to Induce Cell and Collagen Reorganization at JoVE.co

Engineering Fibrin-based Tissue Constructs from Myofibroblasts and Application of Constraints and Strain to Induce Cell and Collagen Reorganization

このモデルシステムは、非破壊における内因性コラーゲン（再）組織実時間を研究するために使用することができる筋線維芽細胞にポピュレートフィブリンゲルから始まる。モデル系は、それが別のセルソース、媒体添加剤と共に使用することができるように、非常に可変であり、特定のニーズに容易に適合させることができる。

エンジニアリングフィブリンベースの組織の筋線維芽細胞と制約の適用からの構築と細胞とコラーゲン（再）組織を誘導するためにひずみ

Collagen content and organization in developing collagenous tissues can be influenced by local tissue strains and tissue constraint. Tissue engineers aim ...

engineering-fibrin-based-tissue-constructs-from-myofibroblasts

Research

JoVE Journal

Bioengineering

10.8K ビュー.  Eindhoven University of Technology. このモデルシステムは、非破壊における内因性コラーゲン（再）組織実時間を研究するために使用することができる筋線維芽細胞にポピュレートフィブリンゲルから始まる。モデル系は、それが別のセルソース、媒体添加剤と共に使用することができるように、非常に可変であり、特定のニーズに容易に適合させることができる。 

ビデオ: Engineering Fibrin-based Tissue Constructs from Myofibroblasts and Application of Constraints and Strain to Induce Cell and Collagen Reorganization

Directed Cellular Self-Assembly to Fabricate Cell-Derived Tissue Rings for Biomechanical Analysis and Tissue Engineering

Each year, hundreds of thousands of patients undergo coronary artery bypass surgery in the United States.1 Approximately one third of these patients do not have suitable autologous donor vessels due to disease progression or previous harvest. The aim of vascular tissue engineering is to develop a suitable alternative source for these bypass grafts. In addition, engineered vascular tissue may prove valuable as living vascular models to study cardiovascular diseases. Several promising approaches to engineering blood vessels have been explored, with many recent studies focusing on development and analysis of cell-based methods.2-5 Herein, we present a method to rapidly self-assemble cells into 3D tissue rings that can be used in vitro to model vascular tissues.
To do this, suspensions of smooth muscle cells are seeded into round-bottomed annular agarose wells. The non-adhesive properties of the agarose allow the cells to settle, aggregate and contract around a post at the center of the well to form a cohesive tissue ring.6,7 These rings can be cultured for several days prior to harvesting for mechanical, physiological, biochemical, or histological analysis. We have shown that these cell-derived tissue rings yield at 100-500 kPa ultimate tensile strength8 which exceeds the value reported for other tissue engineered vascular constructs cultured for similar durations (&lt;30 kPa).9,10 Our results demonstrate that robust cell-derived vascular tissue ring generation can be achieved within a short time period, and offers the opportunity for direct and quantitative assessment of the contributions of cells and cell-derived matrix (CDM) to vascular tissue structure and function.

This article outlines a versatile method to create cell-derived tissue rings by cellular self-assembly. Smooth muscle cells seeded into ring-shaped agarose wells aggregate and contract to form robust three-dimensional (3D) tissues within 7 days. Millimeter-scale tissue rings are conducive to mechanical testing and serve as building blocks for tissue assembly.

生体力学的解析と組織工学のための細胞由来の組織のリングを製作する監督セルラーセルフアセンブリ

Each year, hundreds of thousands of patients undergo coronary artery bypass surgery in the United States.1 Approximately one third of these patients do ...

生物工学

Non-contact, Label-free Monitoring of Cells and Extracellular Matrix using Raman Spectroscopy

Non-destructive, non-contact and label-free technologies to monitor cell and tissue cultures are needed in the field of biomedical research.1-5 However, currently available routine methods require processing steps and alter sample integrity. Raman spectroscopy is a fast method that enables the measurement of biological samples without the need for further processing steps. This laser-based technology detects the inelastic scattering of monochromatic light.6 As every chemical vibration is assigned to a specific Raman band (wavenumber in cm-1), each biological sample features a typical spectral pattern due to their inherent biochemical composition.7-9 Within Raman spectra, the peak intensities correlate with the amount of the present molecular bonds.1 Similarities and differences of the spectral data sets can be detected by employing a multivariate analysis (e.g. principal component analysis (PCA)).10
Here, we perform Raman spectroscopy of living cells and native tissues. Cells are either seeded on glass bottom dishes or kept in suspension under normal cell culture conditions (37 &deg;C, 5% CO2) before measurement. Native tissues are dissected and stored in phosphate buffered saline (PBS) at 4 &deg;C prior measurements. Depending on our experimental set up, we then either focused on the cell nucleus or extracellular matrix (ECM) proteins such as elastin and collagen. For all studies, a minimum of 30 cells or 30 random points of interest within the ECM are measured. Data processing steps included background subtraction and normalization.

Raman spectroscopy is a suitable technique for the non-contact, label-free analysis of living cells, tissue-engineered constructs and native tissues. Source-specific spectral fingerprints can be generated and analyzed using multivariate analysis.

ラマン分光法を用いた細胞と細胞外マトリックスの非接触、ラベルフリーの監視

Non-destructive, non-contact and label-free technologies to monitor cell and tissue cultures are needed in the field of biomedical research.1-5 However, ...

Engineering Skeletal Muscle Tissues from Murine Myoblast Progenitor Cells and Application of Electrical Stimulation

Engineered muscle tissues can be used for several different purposes, which include the production of tissues for use as a disease model in vitro, e.g. to study pressure ulcers, for regenerative medicine and as a meat alternative 1. The first reported 3D muscle constructs have been made many years ago and pioneers in the field are Vandenburgh and colleagues 2,3. Advances made in muscle tissue engineering are not only the result from the vast gain in knowledge of biochemical factors, stem cells and progenitor cells, but are in particular based on insights gained by researchers that physical factors play essential roles in the control of cell behavior and tissue development. State-of-the-art engineered muscle constructs currently consist of cell-populated hydrogel constructs. In our lab these generally consist of murine myoblast progenitor cells, isolated from murine hind limb muscles or a murine myoblast cell line C2C12, mixed with a mixture of collagen/Matrigel and plated between two anchoring points, mimicking the muscle ligaments. Other cells may be considered as well, e.g. alternative cell lines such as L6 rat myoblasts 4, neonatal muscle derived progenitor cells 5, cells derived from adult muscle tissues from other species such as human 6 or even induced pluripotent stem cells (iPS cells) 7. Cell contractility causes alignment of the cells along the long axis of the construct 8,9 and differentiation of the muscle progenitor cells after approximately one week of culture. Moreover, the application of electrical stimulation can enhance the process of differentiation to some extent 8. Because of its limited size (8 x 2 x 0.5 mm) the complete tissue can be analyzed using confocal microscopy to monitor e.g. viability, differentiation and cell alignment. Depending on the specific application the requirements for the engineered muscle tissue will vary; e.g. use for regenerative medicine requires the up scaling of tissue size and vascularization, while to serve as a meat alternative translation to other species is necessary.

Engineered muscle tissue has great potential in regenerative medicine, as disease model and also as an alternative source for meat. Here we describe the engineering of a muscle construct, in this case from mouse myoblast progenitor cells, and the stimulation by electrical pulses.

電気刺激のマウス筋芽細胞前駆細胞およびアプリケーションからの工学骨格筋組織

Engineered muscle tissues can be used for several different purposes, which include the production of tissues for use as a disease model in vitro, e.g. to ...

Tissue Engineering of Tumor Stromal Microenvironment with Application to Cancer Cell Invasion

3D organotypic cultures of epithelial cells on a matrix embedded with mesenchymal cells are widely used to study epithelial cell differentiation and invasion. Rat tail type I collagen and/or matrix derived from Engelbreth-Holm-Swarm mouse sarcoma cells have been traditionally employed as the substrates to model the matrix or stromal microenvironment into which mesenchymal cells (usually fibroblasts) are populated. Although experiments using such matrices are very informative, it can be argued that due to an overriding presence of a single protein (such as in type I Collagen) or a high content of basement membrane components and growth factors (such as in matrix derived from mouse sarcoma cells), these substrates do not best reflect the contribution to matrix composition made by the stromal cells themselves. To study native matrices produced by primary dermal fibroblasts isolated from patients with a tumor prone, genetic blistering disorder (recessive dystrophic epidermolysis bullosa), we have adapted an existing native matrix protocol to study tumor cell invasion. Fibroblasts are induced to produce their own matrix over a prolonged period in culture. This native matrix is then detached from the culture dish and epithelial cells are seeded onto it before the entire coculture is raised to the air-liquid interface. Cellular differentiation and/or invasion can then be assessed over time. This technique provides the ability to assess epithelial-mesenchymal cell interactions in a 3D setting without the need for a synthetic or foreign matrix with the only disadvantage being the prolonged period of time required to produce the native matrix. Here we describe the application of this technique to assess the ability of a single molecule expressed by fibroblasts, type VII collagen, to inhibit tumor cell invasion.

Tissue engineered fibroblast-derived native matrix is an emerging tool to generate a stromal substrate which supports epithelial cell proliferation and differentiation. Here a protocol applying this methodology to assess the impact of different stromal cell types on tumor cell biology is presented.

癌細胞浸潤への応用による腫瘍間質微小環境の組織工学

3D organotypic cultures of epithelial cells on a matrix embedded with mesenchymal cells are widely used to study epithelial cell differentiation and ...

Engineering 3D Cellularized Collagen Gels for Vascular Tissue Regeneration

Synthetic materials are known to initiate clinical complications such as inflammation, stenosis, and infections when implanted as vascular substitutes. Collagen has been extensively used for a wide range of biomedical applications and is considered a valid alternative to synthetic materials due to its inherent biocompatibility (i.e., low antigenicity, inflammation, and cytotoxic responses). However, the limited mechanical properties and the related low hand-ability of collagen gels have hampered their use as scaffold materials for vascular tissue engineering. Therefore, the rationale behind this work was first to engineer cellularized collagen gels into a tubular-shaped geometry and second to enhance smooth muscle cells driven reorganization of collagen matrix to obtain tissues stiff enough to be handled.
The strategy described here is based on the direct assembling of collagen and smooth muscle cells (construct) in a 3D cylindrical geometry with the use of a molding technique. This process requires a maturation period, during which the constructs are cultured in a bioreactor under static conditions (without applied external dynamic mechanical constraints) for 1 or 2 weeks. The &#8220;static bioreactor&#8221; provides a monitored and controlled sterile environment (pH, temperature, gas exchange, nutrient supply and waste removal) to the constructs. During culture period, thickness measurements were performed to evaluate the cells-driven remodeling of the collagen matrix, and glucose consumption and lactate production rates were measured to monitor the cells metabolic activity. Finally, mechanical and viscoelastic properties were assessed for the resulting tubular constructs. To this end, specific protocols and a focused know-how (manipulation, gripping, working in hydrated environment, and so on) were developed to characterize the engineered tissues.

In this work, we present a technique for the rapid fabrication of living vascular tissues by direct culturing of collagen, smooth muscle cells and endothelial cells. In addition, a new protocol for the mechanical characterization of engineered vascular tissues is described.

エンジニアリング3D細胞化血管組織再生のためのコラーゲンゲル

Synthetic materials are known to initiate clinical complications such as inflammation, stenosis, and infections when implanted as vascular substitutes. ...

Sandwich-like Microenvironments to Harness Cell/Material Interactions

Cell culture has been traditionally carried out on bi-dimensional (2D) substrates where cells adhere using ventral receptors to the biomaterial surface. However in vivo, most of the cells are completely surrounded by the extracellular matrix (ECM), resulting in a three-dimensional (3D) distribution of receptors. This may trigger differences in the outside-in signaling pathways and thus in cell behavior.
This article shows that stimulating the dorsal receptors of cells already adhered to a 2D substrate by overlaying a film of a new material (a sandwich-like culture) triggers important changes with respect to standard 2D cultures. Furthermore, the simultaneous excitation of ventral and dorsal receptors shifts cell behavior closer to that found in 3D environments. Additionally, due to the nature of the system, a sandwich-like culture is a versatile tool that allows the study of different parameters in cell/material interactions, e.g., topography, stiffness and different protein coatings at both the ventral and dorsal sides. Finally, since sandwich-like cultures are based on 2D substrates, several analysis procedures already developed for standard 2D cultures can be used normally, overcoming more complex procedures needed for 3D systems.

The following protocol describes the procedure to assemble sandwich-like cultures to be used as an intermediate stage between bi-dimensional (2D) and three-dimensional (3D) cellular environments. The engineered systems can have applications in microscopy, biomechanics, biochemistry and cell biology assays.

サンドイッチ状の微小環境は、Cell /材料の相互作用を活用します

Cell culture has been traditionally carried out on bi-dimensional (2D) substrates where cells adhere using ventral receptors to the biomaterial surface. ...

Treatment of Ligament Constructs with Exercise-conditioned Serum: A Translational Tissue Engineering Model

In vitro experiments are essential to understand biological mechanisms; however, the gap between monolayer tissue culture and human physiology is large, and translation of findings is often poor. Thus, there is ample opportunity for alternative experimental approaches. Here we present an approach in which human cells are isolated from human anterior cruciate ligament tissue remnants, expanded in culture, and used to form engineered ligaments. Exercise alters the biochemical milieu in the blood such that the function of many tissues, organs and bodily processes are improved. In this experiment, ligament construct culture media was supplemented with experimental human serum that has been &#39;conditioned&#39; by exercise. Thus the intervention is more biologically relevant since an experimental tissue is exposed to the full endogenous biochemical milieu, including binding proteins and adjunct compounds that may be altered in tandem with the activity of an unknown agent of interest. After treatment, engineered ligaments can be analyzed for mechanical function, collagen content, morphology, and cellular biochemistry. Overall, there are four major advantages versus traditional monolayer culture and animal models, of the physiological model of ligament tissue that is presented here. First, ligament constructs are three-dimensional, allowing for mechanical properties (i.e., function) such as ultimate tensile stress, maximal tensile load, and modulus, to be quantified. Second, the enthesis, the interface between boney and sinew elements, can be examined in detail and within functional context. Third, preparing media with post-exercise serum allows for the effects of the exercise-induced biochemical milieu, which is responsible for the wide range of health benefits of exercise, to be investigated in an unbiased manner. Finally, this experimental model advances scientific research in a humane and ethical manner by replacing the use of animals, a core mandate of the National Institutes of Health, the Center for Disease Control, and the Food and Drug Administration.

We present a model of ligament tissue in which three-dimensional constructs are treated with the human exercise-conditioned serum and analyzed for collagen content, function, and cellular biochemistry.

運動調節血清による靭帯構築物の治療：翻訳組織工学モデル

In vitro experiments are essential to understand biological mechanisms; however, the gap between monolayer tissue culture and human physiology is large, ...

Recombinant Collagen I Peptide Microcarriers for Cell Expansion and Their Potential Use As Cell Delivery System in a Bioreactor Model

Tissue engineering is a promising field, focused on developing solutions for the increasing demand on tissues and organs regarding transplantation purposes. The process to generate such tissues is complex, and includes an appropriate combination of specific cell types, scaffolds, and physical or biochemical stimuli to guide cell growth and differentiation. Microcarriers represent an appealing tool to expand cells in a three-dimensional (3D) microenvironment, since they provide higher surface-to volume ratios and mimic more closely the in vivo situation compared to traditional two-dimensional methods. The vascular system, supplying oxygen and nutrients to the cells and ensuring waste removal, constitutes an important building block when generating engineered tissues. In fact, most constructs fail after being implanted due to lacking vascular support. In this study, we present a protocol for endothelial cell expansion on recombinant collagen-based microcarriers under dynamic conditions in spinner flask and bioreactors, and we explain how to determine in this setting cell viability and functionality. In addition, we propose a method for cell delivery for vascularization purposes without additional detachment steps necessary. Furthermore, we provide a strategy to evaluate the cell vascularization potential in a perfusion bioreactor on a decellularized&#160;biological matrix. We believe that the use of the presented methods could lead to the development of new cell-based therapies for a large range of tissue engineering applications in the clinical practice.

We propose a cell expansion protocol on macroporous microcarriers and their use as delivery system in a perfusion bioreactor to seed a decellularized tissue matrix. We also include different techniques to determine cell proliferation and viability of cells cultured on microcarriers. Furthermore, we demonstrate functionality of cells after bioreactor cultures.

組換えコラーゲン ペプチド Microcarriers 細胞伸長と細胞バイオリアクター配信システムとして潜在的な使用のためのモデルします。

Tissue engineering is a promising field, focused on developing solutions for the increasing demand on tissues and organs regarding transplantation ...

A Novel Tenorrhaphy Suture Technique with Tissue Engineered Collagen Graft to Repair Large Tendon Defects

Surgical management of large tendon defects with tendon grafts is challenging, as there are a finite number of sites where donors can be readily identified and used. Currently, this gap is filled with tendon auto-, allo-, xeno-, or artificial grafts, but clinical methods to secure them are not necessarily translatable to animals because of the scale. In order to evaluate new biomaterials or study a tendon graft made up of collagen type 1, we have developed a modified suture technique to help maintain the engineered tendon in alignment with the tendon ends. Mechanical properties of these grafts are inferior to the native tendon. To incorporate engineered tendon into clinically relevant models of loaded repair, a strategy was adopted to offload the tissue engineered tendon graft and allow for the maturation and integration of the engineered tendon in vivo until a mechanically sound neo-tendon was formed. We describe this technique using incorporation of the collagen type 1 tissue engineered tendon construct.

In this paper, we present an in vitro and in situ protocol to repair a tendon gap of up to 1.5 cm by filling it with engineered collagen graft. This was performed by developing a modified suture technique to take the mechanical load until the graft matures into the host tissue.

大きな腱欠損を修復する組織設計されたコラーゲン移植片を用いた新規テノルラフィー縫合技術

Surgical management of large tendon defects with tendon grafts is challenging, as there are a finite number of sites where donors can be readily ...

Pancreatic Tissue-Derived Extracellular Matrix Bioink for Printing 3D Cell-Laden Pancreatic Tissue Constructs

The transplantation of pancreatic islets is a promising treatment for patients who suffer from type 1 diabetes accompanied by hypoglycemia and secondary complications. However, islet transplantation still has several limitations such as the low viability of transplanted islets due to poor islet engraftment and hostile environments. In addition, the insulin-producing cells differentiated from human pluripotent stem cells have limited ability to secrete sufficient hormones that can regulate the blood glucose level; therefore, improving the maturation by culturing cells with proper microenvironmental cues is strongly required. In this article, we elucidate protocols for preparing a pancreatic tissue-derived decellularized extracellular matrix (pdECM) bioink to provide a beneficial microenvironment that can increase glucose sensitivity of pancreatic islets, followed by describing the processes for generating 3D pancreatic tissue constructs using a microextrusion-based bioprinting technique.

Decellularized extracellular matrix (dECM) can provide suitable microenvironmental cues to recapitulate the inherent functions of target tissues in an engineered construct. This article elucidates the protocols for the decellularization of pancreatic tissue, evaluation of pancreatic tissue-derived dECM bioink, and generation of 3D pancreatic tissue constructs using a bioprinting technique.

3D細胞-細胞-膵組織コンストラクトを印刷するための膵組織由来細胞外マトリックスバイオインク

The transplantation of pancreatic islets is a promising treatment for patients who suffer from type 1 diabetes accompanied by hypoglycemia and secondary ...