This work was supported by the Belgian National Foundation for Scientific Research (F.R.S.-FNRS) through &#8220;MIS Confocal Microscopy&#8221;, &#8220;Cr&#233;dit aux Chercheurs&#8221; grants and the &#8220;Nanomotility FRFC project&#8221; (no. 2.4622.11). T.G. doctoral fellowship is supported by the Foundation for Training in Industrial and Agricultural Research (FRIA). The authors gratefully acknowledge Sylvain Desprez for mechanical characterization and G&#233;raldine Circelli for confocal imaging.

1ガラスカバースリップの表面を活性化<ol><li>ペトリ皿とスミア（推奨化学ヒュームフード）で5分間、その上に、0.1MのNaOH溶液中でガラスの円形カバースリップ（直径25mm）。 </li><li> NaOH溶液を外し、静かに無菌培養フード内で揺動板に揺動しながら、完全に20分間、無菌のddH 2 Oでカバースリップを浸す。 </li><li>無菌のddH 2 Oを排出し、ステップ1.2を繰り返します。 </li><li>無菌ピンセットでカバーガラスを取り外して、活性化した顔を上にして新しいペトリ皿に配置します。 </li><li>高純度窒素ガスの定常流の下で乾燥したカバースリップ。 </li><li>無菌培養フードでは、1時間カバースリップの活性化された側の3-（トリメトキシシリル）プロピルアクリレート（92％）の薄層を汚す。 </li><li>広範囲に無菌のddH 2 Oを3回洗浄したカバーガラスを洗浄し、新しいシャーレに無菌のddH 2 Oでそれらを浸す。 </li><li>ペトリ皿をタップそしてパラフィルムで10分間穏やかに攪拌しながらロッカープレートの上に置きます。 </li><li>細かいヒントを、滅菌ピンセットでのddH 2 Oからのカバーガラスを取り外して、活性化した顔を上にして新しいペトリ皿に配置します。 </li><li>カバーガラスに付着するほこりを避けるために、アルミホイルで乾燥した場所に、室温で保管してください。 </li></ol>ヒドロキシのPAAmハイドロゲルの調製<ol><li> 1.5mlのエッペンドルフチュー​​ブ中のN-ヒドロキシエチルアクリルアミド（HEA）65mgの重量を準備します。それは、新鮮なHEA溶液を調製することが重要です。 </li><li> HEAに50mMのHEPES緩衝液1mlを加え、完全に溶解するまでのHEAボルテックスを使って混ぜる。 </li><li>希望ヒドロゲルの剛性に到達するために（ 表1参照）のHEPESアクリルアミド溶液およびHEPESビスアクリルアミド溶液中のw / wの2％の必要な数量のw / wの40％の400を添加する。最終容量5mlに50 mMのHEPESで調整する。 </li><li>ボルテックスと脱ガスを使用して溶液を混ぜるヒドロキシ-PAAmを重合を防止し、溶液内の酸素濃度を減少させるために20分間真空チャンバー内。 </li><li>無菌フード下では、それを滅菌するために、0.2μmの孔径のフィルターと脱気溶液を濾過。 </li><li> 7分間のUV /オゾンクリーナー円形カバーガラス（直径22mm）をアクティブにします。 </li><li> 10％硫酸アンモニウム（APS）溶液100μlを準備し、それを100μlのddH 2 O中に10mgのAPSですこれは、新鮮なAPS溶液を調製することが重要である。 </li><li>重合を開始し滅菌ヒドロキシのPAAm溶液（ステップ2.5）にテトラメチレンジアミン2.5μlの（TEMED）とAPS溶液25μlを追加します。無菌条件下で、気泡を導入せずに3連続したピペッティングにより溶液を混ぜる。 </li><li>無菌フード下では、（ステップ1.9から入手可能）25mmのカバースリップ上のヒドロキシのPAAm溶液25μl滴を配置し、すぐに22ミリメートルGLを置くヒドロキシ-PAAmをソリューションを絞る液滴の上に（ステップ2.5に調製した）お尻のカバースリップ。無菌ピンセットで22ミリメートルのガラス製カバースリップを中央にして気泡を滑らかに。 </li><li>ヒドロキシのPAAmハイドロゲルは、室温で15分間重合させた。重合プロセスの完了を追跡する手動エッペンドルフチュー​​ブ内の残りのヒドロキシのPAAm水溶液を反転させる。 </li><li>完全無菌のddH 2 Oでカバーガラスを浸すと、慎重に22ミリメートルのガラス製カバースリップおよびヒドロキシのPAAmハイドロゲル層との間にカミソリの刃のエッジを導入することにより、22ミリメートルのカバーガラスを分離する。 </li><li>滅菌PBS（PBSの3取引所）とヒドロキシのPAAmハイドロゲルを洗浄し、ゲルが完全に水分補給を維持するために、無菌PBS中に浸漬してみましょう。 </li><li>最大3日間4℃で滅菌PBS中のヒドロキシ-PAAmをヒドロゲルに保管してください。 </li></ol> 3ポリジメチルシロキサン（PDMS）Microstamp製作注：シリコンマスターの製造は、駅の前に必要とされるPDMSのmicrostamp製造を室温。シリコンマスターのこの微細加工は、特殊な装置や訓練を必要リソグラフィ技術によって行うことができる。ナノ加工施設とのコラボレーションは、シリコンマスターを製作することをお勧めします。代わりに、オンデマンドでカスタムメイドの微細構造のシリコンマスターを製作する会社に連絡してください。これは、シリコンマスターの製造は一度だけ実行される必要があることに留意することが重要である。実際に、微細構造のシリコンマスターが、エラストマースタンプを生成するために無期限に使用することができる。 <ol><li> 10にPDMSと硬化剤を混合する：プラスチックビーカー中に1の比率で10分間、ピペットを用いて完全に混合する。 </li><li>ステップ3.1の間に形成された気泡を除去するために真空下でPDMS混合物を脱気。 </li><li>シャーレ内の微細構造のシリコンマスターを配置し、気泡を形成することなく、その上に脱気したPDMS混合物の10 mmの厚さの層をキャスト。 </li><li>で、60℃で2時間、PDMSを治すLETオーブン。 </li><li>ほこりのない環境では、剥離PDMS層と物品税メスで1cm 2の microstamps。 </li><li>鉗子を使用して、場所PDMSをペトリ皿にパターンアップmicrostamps。 </li></ol> 4。マイクロパターニングヒドロキシ - のPAAmハイドロゲル<ol><li> 15分間のエタノール/水（50:50）溶液中超音波処理中に置きのPDMS microstampsを。 </li><li>窒素流流でスタンプを乾燥させ、それらを7分間UV /オゾンクリーナーパターンアップ（λ&lt;200 nm）を配置します。 </li><li>無菌フード下で、1cmの2 PDMSスタンプの微細構造表面上に所望のタンパク質溶液（ 例えば 、100μg/ mlのラミニンPBS中または25 / mlのフィブロネクチンPBS中）の150μlのドロップを置きます。 </li><li>オプション：細胞 - リガンド密度を調節するために、タンパク質溶液の濃度を変更します。 </li><li>の各コーナーに向かってピペットの先端を無菌でそれを移動させることによって、スタンプ表面を横切るタンパク質溶液を広げるスタンプ。 </li><li>無菌フード下で60分間PDMSスタンプに吸着するタンパク質溶液のままにしておきます。タンパク質損傷を避けるため、ランプをオフにします。 </li><li>無菌フード下では、ペトリ皿に（ステップ2.13から入手可能）、ヒドロキシPAAmをコーティングしたカバースリップを転送します。 </li><li>無菌条件下での低窒素流でヒドロキシ-PAAmを基材の表面から過剰のPBSを削除します。とすぐにゲル表面に水を立っての証拠が観察されないように手続きを停止します。ゲルは、この段階で完全に乾燥してはならない。 </li><li>乾燥は、慎重にPDMSの構造化表面は、高純度窒素ガスの定常流でスタンプ。 </li><li>ドレッシング組織鉗子を用いたタンパク質でコーティングされたスタンプをつかみ、乾燥したハイドロゲル表面に接触して構造化した表面に置きます。スタンプマイクロ構造およびヒドロゲル表面との間の良好な接触を確保するためにPDMSスタンプの上にピンセットの先端で簡単な圧力ポイントを適用します。 </li><li>目の上のPDMSスタンプのままに室温で1時間の電子化ヒドロゲル表面。 </li><li>静かにドレッシング組織鉗子でヒドロキシ - のPAAmハイドロゲルからPDMSスタンプを削除して、スタンプをきれいにするステップ4.1に従ってください。 </li><li>為替当たり10分間、無菌状態でのPBS 3の交換液（pH = 7.4）によって広く刻印ヒドロキシPAAmをハイドロゲルを洗ってください。 </li><li>オプション：他のECMタンパク質のさらなる微細パターンは、ステップ4.11〜4.5に従うことによってヒドロキシPAAmを表面に添加することができる。 </li><li>ロッキングプレート上穏やかな撹拌下、4℃で1夜の間に、PBS中5mg / mlのBSAの無菌溶液で不動態化非印刷ゾーン。 </li><li>交換につき10分間滅菌条件下でのPBS 3の交換液（pH = 7.4）で広く洗浄します。この段階では、スタンプさヒドロキシ-PAAmをヒドロゲルは、一週間まで4℃で保存することができる。 </li></ol>マイクロパターンヒドロキシPAAmをヒドロゲル上の5の細胞沈着<ol><li>めっき前cに30〜45分間、細胞培地中でカバースリップをインキュベートのエル。 </li><li> 37℃で滅菌したPBSで75cm 2の培養フラスコで培養接着細胞を洗浄し、トリプシン-EDTAまたは10分間ACCUTASE 3mlで、それを取り外してください。 </li><li> 650のx gで3分間、細胞懸濁液を遠心分離した細胞を含むフラスコにあなたの細胞株についての予め温めた完全増殖培地に適切な所望の量を転送する。 </li><li>マイクロピペットで上清を除去し、15-20,000細胞/ mlで完全培地中で細胞を懸濁します。 </li><li> （ステップ5.1から得られた）マイクロパターン化カバースリップに細胞溶液4mlを加え、37℃で培養インキュベーター中で細胞に覆われたカバースリップを置き、1〜2時間、5％の湿度。 </li><li>吸引し優しく付着していない細胞と培養液を交換してください。インキュベーターに付着した細胞を戻し、それらを（細胞型に応じて、3〜6時間）完全に広げてみましょう。 </li></ol>

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No conflicts of interest declared.

現代の細胞生物学のin vitroでの観察の多くは、多くの場合、ECMタンパク質またはRGD配列を含む合成ペプチドの薄層で被覆された硬質ガラス製カバースリップ上で行われている。しかし、そのような基本的な培養基質は、細胞のメカノプロセスを研究するための正確なモデルを提供しないので、ECMの全体の物理化学の複雑さを再現していません。この問題に取り組むために、任意の所望?...

局所的な細胞微小環境（ 例えば 、剛性、細孔径、タンパク質の性質、または細胞リガンド密度）の多くの局面は、運動性、細胞増殖、分化、および遺伝子発現のような細胞プロセスを制御する調節手がかりの座標セットを提供する。細胞外環境の物理化学的特性の改変は、細胞によって認識されると細胞の分極の変形、移動、および分化を含む、異なる生理学的結果を引き起こすことができる。これは、細胞が細胞の生化学的シグナルにECMの変更を変換する方法が、依然として不明である。したがって、主要な重要性メカノ経路を研究するための細胞とそれらの微小環境との間の相互作用を再現できるin vitroでの微小環境を制御操作することである。この問題に対処するために、容易に二ダイムを生成するために、ヒドロキシ-PAAmをヒドロゲルと呼ばれる新規な方法1を 、最近導入されている独立して重要なメカノキューを制御することが可能とnsionalソフト行列：行列のこわばり、セルの形状と閉じ込め、タンパク質の性質および細胞リガンド密度。 ECMはモルフォゲン（走化性）における勾配、接着性タンパク質（走触性）、および剛性（durotaxis）を介して細胞プロセスを指示します。過去数十年にわたり、in vitroでのプラットフォームの高度は、細胞が生理学的プロセス2-5に生化学的および生物物理学的特徴を翻訳することができますどのように引き出すために、これらの細胞外の合図を分離するために開発されてきた。電子ビーム6、フォトリソグラフィー7、光化学固定化8、またはプラズマ支援技法9は、マイクロパターン化基体上の生きている細胞の増殖を導くために開発されてきた。これらの技術は重要な結果が得られているが、それらのほとんどが細胞挙動に対する異なる手がかりの個別の影響の間の識別を許可しない彼らはいくつかの研究室は余裕ができるという技術的設備を必要とします。これらの技術の中でも、マイクロコンタクトプリント（μCP）は、細胞接着性ミクロの島10を作成するために、堅牢でアクセス可能な方法として浮上している。より最近では、多大な努力11-14は、生体組織において観察された剛性の広い範囲を再現するために調整可能な剛性を有するヒドロゲルでμCPの開発がなされてきた。これらの作品の中では、ポリアクリルアミド（PAAmを） を15普及し、すでに細胞バイオメカニクスアッセイのための最も一般的に使用されるポリマーベースのマトリックスの1つになっています。 PAAmを表面は一般的にN-スルホスクシンイミジル-6 - [4&#39;-アジド-2&#39;-nitrophenylamido]（スルホ-SANPAH）およびECMタンパク質は、スルホ-SANPAHニトロフェニルのUV活性化により表面に結合されているヘテロ二官能性架橋剤で官能化されアジド基16。別の技術は深刻な酸化されたタンパク質に結合ヒドラジンから成るヨウ素酸17。ハインドらはアクロイル-ストレプトアビジンモノマー18の存在下での光重合を必要とするタンパク質およびペプチドと生体模倣ハイドロゲルの表面をパターン化するための技術を導入した。より最近では、ツェンらは、1 -エチル-3 - [3 -ジメチルアミノプロピル]カルボジイミド塩酸塩（EDC）で活性化PAゲルをインキュベートするために必要な光学石英マスクを通してのPAAmのディープUV露光に基づいて新しい微細方法19を報告しているタンパク質を追加する前とN-ヒドロキシスクシンイミド（NHS）水溶液。長い合成方法（ 例えば 、透析、凍結乾燥など）、高価な化学化合物（ 例えば 、ヒアルロン酸、スルホ-SANPAH）または深UV：均質で再現性のあるタンパク質の微細パターンを作成するためにこれらの技術の能力にもかかわらず、それらのほとんどは、主要な制限を被る照射。また、これらの技術は、基板の剛性の独立した変調、微細パターンを許可しないジオメトリ、ECMタンパク質の性質、および細胞 - リガンド密度。 考慮にこれらの制限を考えると、私たちはソフトハイドロゲル上のタンパク質および生体分子の多様性の固定化を可能にし、細胞機能に及ぼす役割を解読するために、メカノキューとは独立してチューニングを可能にする新規かつシンプルなアクリルアミドベースのアプローチを開発しました。代わりに過酷な化学的化合物とのPAAmヒドロゲルの治療は、PAAmを重合中のヒドロキシル基を有する市販のアクリルアミドモノマーを導入する。この単純な操作は、他の技術的な要件なしのPAAmハイドロゲルの固有抗接着性を克服する。 水酸基の存在は水素結合相互作用を形成するタンパク質および生体分子のためのヒドロキシ-PAAmをヒドロゲルの高い親和性をもたらす。 μCPと組み合わせて、ヒドロキシ-PAAmをヒドロゲルは、独立した制御を備え​​た二次元培養プラットフォームの迅速な生成を可能にするメカノを研究するための強力なプラットフォームであると想定されているマトリックスの剛性、ECMタンパク質の種類、細胞リガンド密度と閉じ込められた接着性、オン。 このプロトコルの目的は、容易に材料科学の専門知識を持たない任意のヒドロキシPAAmをヒドロゲルを作製するために必要な情報を提供することにある。研究者は病態生理学的メカニズムに関与してメカノ経路のより良い理解につながる可能性が細胞および組織レベルでの生理学的に関連する質問をするための究極の目標は、手段を提供することである。

<table border="0" cellpadding="0" cellspacing="0" width="573">
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	<tbody>
		<tr height="64">
			<td height="64" style="height:64px;width:216px;">UV/Ozone Photoreactor</td>
			<td style="width:71px;">Ultra-Violet Products</td>
			<td style="width:119px;">Model PR-100</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Rocking plate</td>
			<td style="width:71px;">IKAcWerke</td>
			<td style="width:119px;">Model KS 130 Basic</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Vortexer</td>
			<td style="width:71px;">Scientific Industries</td>
			<td style="width:119px;">Model Vortex Genie2</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="85">
			<td height="85" style="height:85px;width:216px;">Vacuum degassing chamber</td>
			<td style="width:71px;">Applied Vacuum Engineering</td>
			<td style="width:119px;">DP- 8-KIT</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Parafilm</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">P7793-1EA</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Stainless steel forceps with fine tip</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">Z225304-1EA</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Dressing tissue forceps</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">F4392-1EA</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Petri dishes in polystyrene</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">P5731-500EA</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Aluminium foil, thickness 0.5&#160;mm</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">266574-3.4G</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Isopore membrane filter (0,2 &#181;m pore size)</td>
			<td style="width:71px;">Millipore</td>
			<td style="width:119px;">GTTP Filter code</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Round glass coverslip (22 mm diameter)</td>
			<td style="width:71px;">Neuvitro</td>
			<td style="width:119px;">GG-22</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Round glass coverslip (25 mm diameter)</td>
			<td style="width:71px;">Neuvitro</td>
			<td style="width:119px;">GG-25</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Variable volume micropipette</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">Z114820</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Protein microcentrifuge tubes</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">Z666505-100EA</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Scalpel handles</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">S2896-1EA</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Scalpel blades</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">S2771-100EA</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Cell culture flasks (75 cm2)</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">CLS430641</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Ultrasonic bath tray, solid (stainless steel)</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">Z613983-1EA</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="22">
			<td height="22" style="height:22px;width:216px;"></td>
			<td style="width:71px;"></td>
			<td style="width:119px;"></td>
			<td></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Name of the Reagent</td>
			<td style="width:71px;">Company</td>
			<td style="width:119px;">Catalogue Number</td>
			<td style="width:167px;">Comments</td>
		</tr>
		<tr height="64">
			<td height="64" style="height:64px;width:216px;">Polydimethylsiloxane&#160;</td>
			<td style="width:71px;">Dow Corning</td>
			<td style="width:119px;">Sylgard 184 silicone elastomer kit</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Acrylamide (powder)</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">A3553</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">N,N&#8217;-Methylenebis(acrylamide)</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">146072</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">N-Hydroxyethylacrylamide</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">697931</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">N,N,N&#8217;,N&#8217;-Tetramethylethylenediamine</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">T9281</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Amonium PerSulfate (APS)</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">A3678</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">3-(Trimetoxysilyl)propyle acrylate</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">1805</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="22">
			<td height="22" style="height:22px;width:216px;">Human Plasma Fibronectin</td>
			<td style="width:71px;">Millipore</td>
			<td style="width:119px;">FC010</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Laminin from EHS</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">L2020</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Sodium hydroxyde</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">221465-25G</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="26">
			<td height="26" style="height:26px;width:216px;">Double-distilled water (ddH2O)</td>
			<td style="width:71px;"></td>
			<td style="width:119px;"></td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="64">
			<td height="64" style="height:64px;width:216px;">Endothelial cell growth medium</td>
			<td style="width:71px;">Cells Applications</td>
			<td style="width:119px;">211K-500</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Human Umbilical Vein Endothelial Cells (HUVEC)</td>
			<td style="width:71px;">Invitrogen</td>
			<td style="width:119px;">C-003-5C</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="64">
			<td height="64" style="height:64px;width:216px;">Accutase</td>
			<td style="width:71px;">PAA laboratories</td>
			<td style="width:119px;">L11-007</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="47">
			<td height="47" style="height:47px;width:216px;">HEPES buffer solution 1M in H20</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">83264-500ML-F</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="64">
			<td height="64" style="height:64px;width:216px;">Antibiotics-antimycotics</td>
			<td style="width:71px;">PAA laboratories</td>
			<td style="width:119px;">P11-002</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="64">
			<td height="64" style="height:64px;width:216px;">Phosphate Buffer Saline solution</td>
			<td style="width:71px;">PAA laboratories</td>
			<td style="width:119px;">H15-002</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Alexa Fluor 488 Phaloidin</td>
			<td style="width:71px;">Molecular Probes</td>
			<td style="width:119px;">A12379</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Anti-vinculin antibody produced in mouse</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">V9131</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Goat anti-mouse antibody-tetramethylrhodamine</td>
			<td style="width:71px;">Molecular Probes</td>
			<td style="width:119px;">T-2762</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:216px;">Anti-Fibronectin</td>
			<td rowspan="2" style="width:71px;">Sigma-Aldrich</td>
			<td rowspan="2" style="width:119px;">F3648</td>
			<td rowspan="2" style="width:167px;"></td>
		</tr>
		<tr height="22">
			<td height="22" style="height:22px;width:216px;">(rabbit)</td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Streptavidin&#160;</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">41469</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:216px;">Anti-Laminin antibody</td>
			<td rowspan="2" style="width:71px;">Sigma-Aldrich</td>
			<td rowspan="2" style="width:119px;">L9393</td>
			<td rowspan="2" style="width:167px;"></td>
		</tr>
		<tr height="22">
			<td height="22" style="height:22px;width:216px;">(rabbit)</td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Anti-rabbit IgG-FITC</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">F7512</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Trypsin-EDTA solution</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">T3924-100ML</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="43">
			<td height="43" style="height:43px;width:216px;">Absolute ethanol</td>
			<td style="width:71px;">Sigma-Aldrich</td>
			<td style="width:119px;">459844-2.5L</td>
			<td style="width:167px;"></td>
		</tr>
	</tbody>
</table>

preparation of hydroxy-paam hydrogels for decoupling the effects of mechanotransduction cues

現在では、多くの細胞機能は、それらの細胞外マトリックス（ECM）環境の物理化学的および機械的な手がかりを用いた細胞の相互作用によって調節されることが確立されている。真核細胞は、常に、遺伝子発現の特定の変化を達成するために、生化学的シグナルにECMの物理的変化を形質導入し、これらの信号を統合するために、表面mechanosensorsを通じて局所微小環境を感知する。興味深いことに、互いにECM缶のカップルの物理化学的及び機械的パラメータは、細胞の運命を調節する。そのため、メカノを理解する鍵は、細胞機能上のECM手がかりの相対的な寄与を分離することです。 ここでは、迅速かつ容易にin vitroでのメカノ手がかりから独立チューニングのための生物学的に関連するヒドロゲルを生成するために、詳細な実験プロトコルを提示します。私たちは化学的に修飾されたポリアクリルアミドハイドロゲル（PAAmを）は、それらの本質的に非adhesを克服するために重合中にヒドロキシル官能アクリルアミドモノマーを組み込むことによって特性をアイブ。私たちは、ECMタンパク質の任意の所望の性質の固定化を可能にするヒドロキシPAAmを呼ばれる小説のPAAmハイドロゲルを、取得した。マイクロコンタクトプリンティング、ヒドロキシ-PAAmをヒドロゲルの組み合わせは、独立して、単一細胞の形態、マトリックス剛性、性質およびECMタンパク質の濃度を制御することを可能にする。私たちは、in vitro細胞メカノ過程で勉強するすべての生物学の実験室で設定することができ、簡単で迅速な方法を提供する。今後は、ECMの剛性と核との間の機械的結合を実証する内皮細胞上の実験を行うことにより、この新規二次元のプラットフォームを検証します。

図1Aは、ランダムラジカル重合によって埋め込 ​​まヒドロキシル基（水酸基のPAAm）、ポリアクリルアミドの親水性ネットワークを形成された一次ヒドロキシル基を含むN-ヒドロキシエチル（HEA）モノマーとアクリルアミドの共重合（AAM）を提示し、ビスアクリルアミド（ビス-AAmと） 。このプロトコルでは、HEAの重量65 mgのHEPESの1ミリリットルの容量で希釈しなければならない...

Watch this Scientific Journal Video about Preparation of Hydroxy-PAAm Hydrogels for Decoupling the Effects of Mechanotransduction Cues at JoVE.com

Preparation of Hydroxy-PAAm Hydrogels for Decoupling the Effects of Mechanotransduction Cues

私たちは、最小限のコストや専門知識を持つECMタンパク質の直接結合を可能にするヒドロキシPAAmを呼ばれる新しいポリアクリルアミドハイドロゲルを、提示します。マイクロコンタクトプリント法でヒドロキシ - のPAAmハイドロゲルの組み合わせは、細胞のmechanostransductionを研究するための天然の細胞の微小環境の多くの手がかりを独立して制御を容易にします。

メカノキューの影響をデカップリングするためのヒドロキシのPAAmハイドロゲルの調製

It is now well established that many cellular functions are regulated by interactions of cells with physicochemical and mechanical cues of their ...

preparation-hydroxy-paam-hydrogels-for-decoupling-effects

Research

JoVE Journal

Bioengineering

13.2K ビュー.  Université de Mons. 私たちは、最小限のコストや専門知識を持つECMタンパク質の直接結合を可能にするヒドロキシPAAmを呼ばれる新しいポリアクリルアミドハイドロゲルを、提示します。マイクロコンタクトプリント法でヒドロキシ - のPAAmハイドロゲルの組み合わせは、細胞のmechanostransductionを研究するための天然の細胞の微小環境の多くの手がかりを独立して制御を容易に?...

ビデオ: Preparation of Hydroxy-PAAm Hydrogels for Decoupling the Effects of Mechanotransduction Cues

Axon Stretch Growth: The Mechanotransduction of Neuronal Growth

During pre-synaptic embryonic development, neuronal processes traverse short distances to reach their targets via growth cone. Over time, neuronal somata are separated from their axon terminals due to skeletal growth of the enlarging organism (Weiss 1941; Gray, Hukkanen et al. 1992). This mechanotransduction induces a secondary mode of neuronal growth capable of accommodating continual elongation of the axon (Bray 1984; Heidemann and Buxbaum 1994; Heidemann, Lamoureux et al. 1995; Pfister, Iwata et al. 2004).
Axon Stretch Growth (ASG) is conceivably a central factor in the maturation of short embryonic processes into the long nerves and white matter tracts characteristic of the adult nervous system. To study ASG in vitro, we engineered bioreactors to apply tension to the short axonal processes of neuronal cultures (Loverde, Ozoka et al. 2011). Here, we detail the methods we use to prepare bioreactors and conduct ASG. First, within each stretching lane of the bioreactor, neurons are plated upon a micro-manipulated towing substrate. Next, neurons regenerate their axonal processes, via growth cone extension, onto a stationary substrate. Finally, stretch growth is performed by towing the plated cell bodies away from the axon terminals adhered to the stationary substrate; recapitulating skeletal growth after growth cone extension.
Previous work has shown that ASG of embryonic rat dorsal root ganglia neurons are capable of unprecedented growth rates up to 10mm/day, reaching lengths of up to 10cm; while concurrently resulting in increased axonal diameters (Smith, Wolf et al. 2001; Pfister, Iwata et al. 2004; Pfister, Bonislawski et al. 2006; Pfister, Iwata et al. 2006; Smith 2009). This is in dramatic contrast to regenerative growth cone extension (in absence of mechanical stimuli) where growth rates average 1mm/day with successful regeneration limited to lengths of less than 3cm (Fu and Gordon 1997; Pfister, Gordon et al. 2011). Accordingly, further study of ASG may help to reveal dysregulated growth mechanisms that limit regeneration in the absence of mechanical stimuli.

A unique tissue engineering method was developed to elongate numerous nerve fibers in culture by recapitulating axon stretch growth; a form of nervous system growth whereby nerves elongate in conjunction with growth of the enlarging body.

軸索のストレッチの成長：神経成長のメカノトランスダ

During pre-synaptic embryonic development, neuronal processes traverse short distances to reach their targets via growth cone. Over time, neuronal somata ...

生物工学

Alginate Hydrogels for Three-Dimensional Organ Culture of Ovaries and Oviducts

Ovarian cancer is the fifth leading cause of cancer deaths in women and has a 63% mortality rate in the United States1. The cell type of origin for ovarian cancers is still in question and might be either the ovarian surface epithelium (OSE) or the distal epithelium of the fallopian tube fimbriae2,3. Culturing the normal cells as a primary culture in vitro will enable scientists to model specific changes that might lead to ovarian cancer in the distinct epithelium, thereby definitively determining the cell type of origin. This will allow development of more accurate biomarkers, animal models with tissue-specific gene changes, and better prevention strategies targeted to this disease.
Maintaining normal cells in alginate hydrogels promotes short term in vitro culture of cells in their three-dimensional context and permits introduction of plasmid DNA, siRNA, and small molecules. By culturing organs in pieces that are derived from strategic cuts using a scalpel, several cultures from a single organ can be generated, increasing the number of experiments from a single animal. These cuts model aspects of ovulation leading to proliferation of the OSE, which is associated with ovarian cancer formation. Cell types such as the OSE that do not grow well on plastic surfaces can be cultured using this method and facilitate investigation into normal cellular processes or the earliest events in cancer formation4.
Alginate hydrogels can be used to support the growth of many types of tissues5. Alginate is a linear polysaccharide composed of repeating units of &beta;-D-mannuronic acid and &alpha;-L-guluronic acid that can be crosslinked with calcium ions, resulting in a gentle gelling action that does not damage tissues6,7. Like other three-dimensional cell culture matrices such as Matrigel, alginate provides mechanical support for tissues; however, proteins are not reactive with the alginate matrix, and therefore alginate functions as a synthetic extracellular matrix that does not initiate cell signaling5. The alginate hydrogel floats in standard cell culture medium and supports the architecture of the tissue growth in vitro.
A method is presented for the preparation, separation, and embedding of ovarian and oviductal organ pieces into alginate hydrogels, which can be maintained in culture for up to two weeks. The enzymatic release of cells for analysis of proteins and RNA samples from the organ culture is also described. Finally, the growth of primary cell types is possible without genetic immortalization from mice and permits investigators to use knockout and transgenic mice.

Culture of normal cells in their three-dimensional context represents an alternative method to study early events required for cellular transformation and tumorigenesis. This method is used to grow normal ovarian and oviductal cells to study early events in ovarian cancer formation.

卵巣と卵管の三次元器官培養用アルギン酸ゲル

Ovarian cancer is the fifth leading cause of cancer deaths in women and has a 63% mortality rate in the United States1. The cell type of origin for ...

Low Molecular Weight Protein Enrichment on Mesoporous Silica Thin Films for Biomarker Discovery

The identification of circulating biomarkers holds great potential for non invasive approaches in early diagnosis and prognosis, as well as for the monitoring of therapeutic efficiency.1-3 The circulating low molecular weight proteome (LMWP) composed of small proteins shed from tissues and cells or peptide fragments derived from the proteolytic degradation of larger proteins, has been associated with the pathological condition in patients and likely reflects the state of disease.4,5 Despite these potential clinical applications, the use of Mass Spectrometry (MS) to profile the LMWP from biological fluids has proven to be very challenging due to the large dynamic range of protein and peptide concentrations in serum.6 Without sample pre-treatment, some of the more highly abundant proteins obscure the detection of low-abundance species in serum/plasma. Current proteomic-based approaches, such as two-dimensional polyacrylamide gel-electrophoresis (2D-PAGE) and shotgun proteomics methods are labor-intensive, low throughput and offer limited suitability for clinical applications.7-9 Therefore, a more effective strategy is needed to isolate LMWP from blood and allow the high throughput screening of clinical samples. 
Here, we present a fast, efficient and reliable multi-fractionation system based on mesoporous silica chips to specifically target and enrich LMWP.10,11 Mesoporous silica (MPS) thin films with tunable features at the nanoscale were fabricated using the triblock copolymer template pathway. Using different polymer templates and polymer concentrations in the precursor solution, various pore size distributions, pore structures, connectivity and surface properties were determined and applied for selective recovery of low mass proteins. The selective parsing of the enriched peptides into different subclasses according to their physicochemical properties will enhance the efficiency of recovery and detection of low abundance species. In combination with mass spectrometry and statistic analysis, we demonstrated the correlation between the nanophase characteristics of the mesoporous silica thin films and the specificity and efficacy of low mass proteome harvesting. The results presented herein reveal the potential of the nanotechnology-based technology to provide a powerful alternative to conventional methods for LMWP harvesting from complex biological fluids. Because of the ability to tune the material properties, the capability for low-cost production, the simplicity and rapidity of sample collection, and the greatly reduced sample requirements for analysis, this novel nanotechnology will substantially impact the field of proteomic biomarker research and clinical proteomic assessment.

We developed a technology based on mesoporous silica thin film for the selective recovery of low molecular weight proteins and peptides from human serum. The physico-chemical properties of our mesoporous chips were finely tuned to provide substantial control in peptide enrichment and consequently profile the serum proteome for diagnostic purposes.

バイオマーカー探索のためのメソポーラスシリカ薄膜の低分子量蛋白質の濃縮

The identification of circulating biomarkers holds great potential for non invasive approaches in early diagnosis and prognosis, as well as for the ...

The Synthesis of RGD-functionalized Hydrogels as a Tool for Therapeutic Applications

The use of polymers as biomaterials has provided significant advantages in therapeutic applications. In particular, the possibility to modify and functionalize polymer chains with compounds that are able to improve biocompatibility, mechanical properties, or cell viability allows the design of novel materials to meet new challenges in the biomedical field. With the polymer functionalization strategies, click chemistry is a powerful tool to improve cell-compatibility and drug delivery properties of polymeric devices. Similarly, the fundamental need of biomedicine to use sterile tools to avoid potential adverse-side effects, such as toxicity or contamination of the biological environment, gives rise to increasing interest in the microwave-assisted strategy.
The combination of click chemistry and the microwave-assisted method is suitable to produce biocompatible hydrogels with desired functionalities and improved performances in biomedical applications. This work aims to synthesize RGD-functionalized hydrogels. RGD (arginylglycylaspartic acid) is a tripeptide that can mimic cell adhesion proteins and bind to cell-surface receptors, creating a hospitable microenvironment for cells within the 3D polymeric network of the hydrogels. RGD functionalization occurs through Huisgen 1,3-dipolar cycloaddition. Some PAA carboxyl groups are modified with an alkyne moiety, whereas RGD is functionalized with azido acid as the terminal residue of the peptide sequence. Finally, both products are used in a copper catalyzed click reaction to permanently link the peptide to PAA. This modified polymer is used with carbomer, agarose and polyethylene glycol (PEG) to synthesize a hydrogel matrix. The 3D structure is formed due to an esterification reaction involving carboxyl groups from PAA and carbomer and hydroxyl groups from agarose and PEG through microwave-assisted polycondensation. The efficiency of the gelation mechanism ensures a high degree of RGD functionalization. In addition, the procedure to load therapeutic compounds or biological tools within this functionalized network is very simple and reproducible.

We present a protocol for the synthesis of RGD-functionalized hydrogels as devices for cell and drug delivery. The procedure involves copper catalyzed alkyne-azide cycloaddition (CuAAC) between alkyne-modified polyacrylic acid (PAA) and a RGD-azide derivative. The hydrogels are formed using microwave-assisted polycondensation and their physicochemical properties are investigated.

治療用途のためのツールとしてのRGD官能ヒドロゲルの合成

The use of polymers as biomaterials has provided significant advantages in therapeutic applications. In particular, the possibility to modify and ...

Light-mediated Formation and Patterning of Hydrogels for Cell Culture Applications

Click chemistries have been investigated for use in numerous biomaterials applications, including drug delivery, tissue engineering, and cell culture. In particular, light-mediated click reactions, such as photoinitiated thiol&#8722;ene and thiol&#8722;yne reactions, afford spatiotemporal control over material properties and allow the design of systems with a high degree of user-directed property control. Fabrication and modification of hydrogel-based biomaterials using the precision afforded by light and the versatility offered by these thiol&#8722;X photoclick chemistries are of growing interest, particularly for the culture of cells within well-defined, biomimetic microenvironments. Here, we describe methods for the photoencapsulation of cells and subsequent photopatterning of biochemical cues within hydrogel matrices using versatile and modular building blocks polymerized by a thiol&#8722;ene photoclick reaction. Specifically, an approach is presented for constructing hydrogels from allyloxycarbonyl (Alloc)-functionalized peptide crosslinks and pendant peptide moieties and thiol-functionalized poly(ethylene glycol) (PEG) that rapidly polymerize in the presence of lithium acylphosphinate photoinitiator and cytocompatible doses of long wavelength ultraviolet (UV) light. Facile techniques to visualize photopatterning and quantify the concentration of peptides added are described. Additionally, methods are established for encapsulating cells, specifically human mesenchymal stem cells, and determining their viability and activity. While the formation and initial patterning of thiol-alloc hydrogels are shown here, these techniques broadly may be applied to a number of other light and radical-initiated material systems (e.g., thiol-norbornene, thiol-acrylate) to generate patterned substrates.

We describe a sequential process for light-mediated formation and subsequent biochemical patterning of synthetic hydrogel matrices for three-dimensional cell culture applications. The construction and modification of hydrogels with cytocompatible photoclick chemistry is demonstrated. Additionally, facile techniques to quantify and observe patterns and determine cell viability within these hydrogels are presented.

細胞培養アプリケーションのためのヒドロゲルの光媒介形成とパターニング

Click chemistries have been investigated for use in numerous biomaterials applications, including drug delivery, tissue engineering, and cell culture. In ...

Synthesis of Hydrogels with Antifouling Properties As Membranes for Water Purification

Hydrogels have been widely utilized to enhance the surface hydrophilicity of membranes for water purification, increasing the antifouling properties and thus achieving stable water permeability through membranes over time. Here, we report a facile method to prepare hydrogels based on zwitterions for membrane applications. Freestanding films can be prepared from sulfobetaine methacrylate (SBMA) with a crosslinker of poly(ethylene glycol) diacrylate (PEGDA) via photopolymerization. The hydrogels can also be prepared by impregnation into hydrophobic porous supports to enhance the mechanical strength. These films can be characterized by attenuated total reflection Fourier transform infrared spectroscopy (ATR-FTIR) to determine the degree of conversion of the (meth)acrylate groups, using goniometers for hydrophilicity and differential scanning calorimetry (DSC) for polymer chain dynamics. We also report protocols to determine the water permeability in dead-end filtration systems and the effect of foulants (bovine serum albumin, BSA) on membrane performance.

This paper reports practical methods to prepare hydrogels in freestanding films and impregnated membranes and to characterize their physical properties, including water transport properties.

水質浄化のための膜のような防汚特性を持つハイドロゲルの合成

Hydrogels have been widely utilized to enhance the surface hydrophilicity of membranes for water purification, increasing the antifouling properties and ...

Production of Elastin-like Protein Hydrogels for Encapsulation and Immunostaining of Cells in 3D

Two-dimensional (2D) tissue culture techniques have been essential for our understanding of fundamental cell biology. However, traditional 2D tissue culture systems lack a three-dimensional (3D) matrix, resulting in a significant disconnect between results collected in vitro and in vivo. To address this limitation, researchers have engineered 3D hydrogel tissue culture platforms that can mimic the biochemical and biophysical properties of the in vivo cell microenvironment. This research has motivated the need to develop material platforms that support 3D cell encapsulation and downstream biochemical assays. Recombinant protein engineering offers a unique toolset for 3D hydrogel material design and development by allowing for the specific control of protein sequence and therefore, by extension, the potential mechanical and biochemical properties of the resultant matrix. Here, we present a protocol for the expression of recombinantly-derived elastin-like protein (ELP), which can be used to form hydrogels with independently tunable mechanical properties and cell-adhesive ligand concentration. We further present a methodology for cell encapsulation within ELP hydrogels and subsequent immunofluorescent staining of embedded cells for downstream analysis and quantification.

Recombinant protein-engineered hydrogels are advantageous for 3D cell culture as they allow for complete tunability of the polymer backbone and therefore, the cell microenvironment. Here, we describe the process of recombinant elastin-like protein purification and its application in 3D hydrogel cell encapsulation.

カプセル化と 3 D の細胞の免疫染色のエラスチン様タンパク質ゲルの生産

Two-dimensional (2D) tissue culture techniques have been essential for our understanding of fundamental cell biology. However, traditional 2D tissue ...

Measuring Global Cellular Matrix Metalloproteinase and Metabolic Activity in 3D Hydrogels

Three-dimensional (3D) cell culture systems often more closely recapitulate in vivo cellular responses and functions than traditional two-dimensional (2D) culture systems. However, measurement of cell function in 3D culture is often more challenging. Many biological assays require retrieval of cellular material which can be difficult in 3D cultures. One way to address this challenge is to develop new materials that enable measurement of cell function within the material. Here, a method is presented for measurement of cellular matrix metalloproteinase (MMP) activity in 3D hydrogels in a 96-well format. In this system, a poly(ethylene glycol) (PEG) hydrogel is functionalized with a fluorogenic MMP cleavable sensor. Cellular MMP activity is proportional to fluorescence intensity and can be measured with a standard microplate reader. Miniaturization of this assay to a 96-well format reduced the time required for experimental set up by 50% and reagent usage by 80% per condition as compared to the previous 24-well version of the assay. This assay is also compatible with other measurements of cellular function. For example, a metabolic activity assay is demonstrated here, which can be conducted simultaneously with MMP activity measurements within the same hydrogel. The assay is demonstrated with human melanoma cells encapsulated across a range of cell seeding densities to determine the appropriate encapsulation density for the working range of the assay. After 24 h of cell encapsulation, MMP and metabolic activity readouts were proportional to cell seeding density. While the assay is demonstrated here with one fluorogenic degradable substrate, the assay and methodology could be adapted for a wide variety of hydrogel systems and other fluorescent sensors. Such an assay provides a practical, efficient and easily accessible 3D culturing platform for a wide variety of applications.

Here, a protocol is presented for encapsulating and culturing cells in poly(ethylene glycol) (PEG) hydrogels functionalized with a fluorogenic matrix metalloproteinase (MMP)-degradable peptide. Cellular MMP and metabolic activity are measured directly from the hydrogel cultures using a standard microplate reader.

世界的な細胞のマトリックスメタロプロテアーゼと 3 D ゲルの代謝活性を測定

Three-dimensional (3D) cell culture systems often more closely recapitulate in vivo cellular responses and functions than traditional two-dimensional (2D) ...

A Lab-On-A-Chip Platform for Stimulating Osteocyte Mechanotransduction and Analyzing Functional Outcomes of Bone Remodeling

Bone remodeling is a tightly regulated process that is required for skeletal growth and repair as well as adapting to changes in the mechanical environment. During this process, mechanosensitive osteocytes regulate the opposing responses between the catabolic osteoclasts and anabolic osteoblasts. To better understand the highly intricate signaling pathways that regulate this process, our lab has developed a foundationary lab-on-a-chip (LOC) platform for analyzing functional outcomes (formation and resorption) of bone remodeling within a small scale system. As bone remodeling is a lengthy process that occurs on the order of weeks to months, we developed long-term cell culturing protocols within the system. Osteoblasts and osteoclasts were grown on functional activity substrates within the LOC and maintained for up to seven weeks. Afterward, chips were disassembled to allow for the quantification of bone formation and resorption. Additionally, we have designed a 3D printed mechanical loading device that pairs with the LOC platform and can be used to induce osteocyte mechanotransduction by deforming the cellular matrix. We have optimized cell culturing protocols for osteocytes, osteoblasts, and osteoclasts within the LOC platform and have addressed concerns of sterility and cytotoxicity. Here, we present the protocols for fabricating and sterilizing the LOC, seeding cells on functional substrates, inducing mechanical load, and disassembling the LOC to quantify endpoint results. We believe that these techniques lay the groundwork for developing a true organ-on-a-chip for bone remodeling.

Here, we present protocols for analyzing bone remodeling within a lab-on-a-chip platform. A 3D printed mechanical loading device can be paired with the platform to induce osteocyte mechanostransduction by deforming the cellular matrix. The platform can also be used to quantify bone remodeling functional outcomes from osteoclasts and osteoblasts (resorption/formation).

骨造形メカノダクタ化を刺激し、骨改造の機能的成果を解析するためのラボオンチッププラットフォーム

Bone remodeling is a tightly regulated process that is required for skeletal growth and repair as well as adapting to changes in the mechanical ...

Controlled Strain of 3D Hydrogels under Live Microscopy Imaging

External forces are an important factor in tissue formation, development, and maintenance. The effects of these forces are often studied using specialized in vitro stretching methods. Various available systems use 2D substrate-based stretchers, while the accessibility of 3D techniques to strain soft hydrogels, is more restricted. Here, we describe a method that allows external stretching of soft hydrogels from their circumference, using an elastic silicone strip as the sample carrier. The stretching system utilized in this protocol is constructed from 3D-printed parts and low-cost electronics, making it simple and easy to replicate in other labs. The experimental process begins with polymerizing thick (&#62;100 &#956;m) soft fibrin hydrogels (Elastic Modulus of ~100 Pa) in a cut-out at the center of a silicone strip. Silicone-gel constructs are then attached to the printed-stretching device and placed on the confocal microscope stage. Under live microscopy the stretching device is activated, and the gels are imaged at various stretch magnitudes. Image processing is then used to quantify the resulting gel deformations, demonstrating relatively homogenous strains and fiber alignment throughout the gel&#8217;s 3D thickness (Z-axis). Advantages of this method include the ability to strain extremely soft hydrogels in 3D while executing in situ microscopy, and the freedom to manipulate the geometry and size of the sample according to the user&#8217;s needs. Additionally, with proper adaptation, this method can be used to stretch other types of hydrogels (e.g., collagen, polyacrylamide or polyethylene glycol) and can allow for analysis of cells and tissue response to external forces under more biomimetic 3D conditions.

The presented method involves uniaxial stretching of 3D soft hydrogels embedded in silicone rubber while allowing live confocal microscopy. Characterization of the external and internal hydrogel strains as well as fiber alignment are demonstrated. The device and protocol developed can assess the response of cells to various strain regimes.

ライブ顕微鏡イメージング下での3Dヒドロゲルの制御株

External forces are an important factor in tissue formation, development, and maintenance. The effects of these forces are often studied using specialized ...