この研究は、米国立衛生研究所、国立癌研究所、癌研究センターの学内研究プログラムによってサポートされていました。

注：以下のプロトコルは、NIR-PITを使用して、特定の細胞を排除するために必要な手順を説明します。コントロールとNIR-PITと細胞生存率に関するその他の詳細は、別の場所で18見つけることができます。 モノクローナル抗体にIR700の1コンジュゲートモノクローナル抗体（mAb） <ol><li> 0.1 MのNa 2 HPO 4（pHは8.6）溶液中の2-5 mg / mlとに関心のmAbを準備します。 </li><li>マイクロ遠心チューブ中の0.1MのNa 2 HPO 4溶液（pHは8.6）中の10mM IR700の30.8ナノモルとmAbの6.8ナノモルを混合し、アルミ箔で覆われて1時間、室温でインキュベートします。 </li><li>二回、15ミリリットルのPBSでPD-10カラム（材料/機器の表を参照）を洗浄します。ステップ1.2からサンプルをロードします。 </li><li>製造業者の指示に従ってPBS溶出により、PD-10カラムを介して混合物を精製します。 注：ここでは、溶出はIR700のバンド色に沿っていました。 300μlのサンプルについて、PBS溶出画分4.4 mlを典型的には2.5〜mlです。 </li><li>決定します分光光度計9で595nmの吸収を測定することによりクマシー染色でタンパク質濃度。各mAb分子9にコンジュゲート蛍光体分子の数を確認するために、689 nmでの吸収がIR700の濃度を決定します。 注：分光光度計で1モノクローナル抗体でIR700分子の最適なコンジュゲーション数を決定することが重要です。一般的に、1抗体分子中の3 IR700分子の周りには、両方のin vitroおよびin vivoの仕事に最適です。 HPLCおよびSDS-PAGE法は、mAbおよびIR700が結合しているか否かを確認するために使用することができます。 </li><li>タンパク質濃度を決定した後、4℃で保管してください。 </li></ol>混合3D細胞培養（混合スフェロイド）の調製<ol><li>ドロッププレートをぶら下げのプレート貯留部に無菌水（約1 ml）を適用します。 </li><li> A431-LUC-GFP細胞および3T3-RFP細胞 - 様々な目的の細胞タイプの比率を準備 -各サンプルは合計5,000個の細胞を含有する培養培地50μlに懸濁しました。 注：培地中の目的の細胞タイプの割合は、細胞型に応じてその他 100、100、10：100、25：100、50 1を準備します。 </li><li> 37℃、5％二酸化炭素の加湿インキュベーター内で96ウェル懸滴プレートにおいて5~7日間ミックスをインキュベートします。 2日ごとに培地を変更します。注：正確な3Dスフェロイドを作る静かにプレートを処理するために、細胞を含有する液滴は、3D形状を形成する前に、簡単に落ちるように。 </li><li> 40X倍率 - 10Xで反転明視野顕微鏡を用いてスフェロイドの形態と大きさを観察します。注：それは細胞の種類やハンギングドロップの大きさに依存するが、回転楕円体の直径は96ウェル懸滴プレート中でのインキュベーションの7日後の周りの400から600ミクロンであることを確認してください。 </li></ol>混合3D細胞培養のためのインビトロ NIR-PIT 3. <ol><li>ヘクタールのメディアを変更10μg/ mlの抗体光吸収複合体（APC）を含む培地にドロッププレートnging、37℃、5％二酸化炭素の加湿インキュベーター内で6時間インキュベートします。 </li><li> 6時間のインキュベーション後、新鮮な培地（フェノールレッドを含まない）で2回回転楕円体を洗浄します。先端がカットオフで優しく滅菌200μlのピペットチップを使用して、100μlの新鮮なフェノールレッドを含まない培地でガラス底の50ミリメートル皿にスフェロイドを転送します。各皿に1回転楕円体を配置します。 </li><li>形態の変化を検出するために倒立明視野顕微鏡でスフェロイドを守ってください。光学レポーター（ 例えば、GFPおよびRFP）を観察するには、以下のフィルタ設定で蛍光顕微鏡を使用する：GFP - 469 nmの励起フィルター、および525 nmの発光フィルター; RFP - 559 nmの励起フィルター、および630nmの発光フィルター。 </li><li>照射用ガラスボトムディッシュの上に発光ダイオード（LED）を配置します。 注：スフェロイドは、NIRに露出させることができます顕微鏡上または層流フード内のいずれかの光。 <ol><li>光パワーメータ9でNIR光のパワー密度を測定します。この測定によれば、2 J / cm 2で670〜710ナノメートルの波長で光を放射する発光ダイオード（LED）を介して近赤外光を照射します。 注：LEDの光は、約5インチの最大の深さに浸透することができます。 NIR-PITの細胞傷害性効果は関係なく、電力密度と暴露23の期間だけ与えられたエネルギーに依存しています。 </li></ol></li><li>照射後、新鮮な培地の50μlの新た懸滴プレートに回転楕円体を移し、37℃、5％二酸化炭素の加湿インキュベーター中で1日間インキュベートします。 </li><li>優しくカットオフチップで滅菌200μlのピペットチップを使用して、新鮮な培地（フェノールレッドを含まない）の100μlでガラス底の皿にスフェロイドを転送します。 NIR-PIT fiを使って後の蛍光顕微鏡1日でスフェロイドを守ってLTERの設定は、ステップ3.3に記載します。 <ol><li> 、または蛍光顕微鏡（ 図2B）14,18,22 を用いて、細胞質GFP蛍光の消失によって2μg/ mlの最終濃度で培地にヨウ化プロピジウムを添加することによって、死細胞を検出します。 </li></ol></li><li>標的細胞が完全に除去されていない場合、繰り返し3.1~3.6手順。 </li></ol>

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著者らは、開示することは何もありません。

我々は、NIR-PITを用いて、非標的細胞に損傷を与えることなく、混合三次元細胞培養物から特定の細胞除去の方法を示します。これまでのところ、実用的な細胞除去の方法組織が確立されるか、移植後はありません。したがって、NIR-PITは、これを達成するための有望な方法です。 APCはモノクローナル抗体自体と同様の薬物動態を示すので、この技術は、 インビボ 18,22 に利用することができます。標的細胞型は、種々のAPCで適合させることができます。 21 -抗EGFR、抗PSMA抗メソテリン、および抗CEAを含む様々な抗体または抗体フラグメントは、既にAPCを15としました。また、NIR照射領域を変更すると、処理された領域を最小限に抑えることができます。ここでは、標的細胞のルシフェラーゼ活性の定量化と蛍光と、特定の細胞の完全な消失を確認しました。 NIR-PITは、このように臨界点がtである、光ベースの治療法であります光エネルギーと逆二乗法則に従って、したがって細胞壊死の減少（ステップ3.4）以降、NIR光源とターゲットの間、彼は距離、。正確な3Dスフェロイドを作るために、プレートはできるだけ穏やかに処理し、インキュベートする必要があります。細胞を含有する液滴は容易に破壊または3D形状を形成する前に少しの衝撃によって脱落しています。 NIR-PITは、いくつかのユニークな利点を持っています。まず、NIR-PIT APCは原因細胞と最小の非標的の蓄積を標的とするために高度に特異的な結合につながるIR700の親水性特性に対する親の非標識抗体と類似の静脈内薬物動態を、実証します。したがって、でも組織の移植後、NIR-PITは、NIRへの関心領域の暴露に続いてAPCの静脈内注射を介して標的細胞を治療することができます。第二に、NIR光は、UVまたは可視光よりも組織へより深く浸透することができ、したがって、NIR-PITは表面だけでなく、entiないだけを扱うことができ表面でのNIRへの曝露による移植された組織の厚み再。最後に、NIR-PITは、繰り返し制限なく標的細胞を除去するために使用することができます。標的細胞は、細胞表面18上の標的分子の十分なコピーを発現する場合に、この方法は有用です。 しかし、この手法にはいくつかの制限があります。それは大きな分子であるため、まず、APCの透過性が限られています。この問題を克服するために、NIR-PITの治療または抗体断片は18,19,22を利用することができる繰り返します。別の制限は、光の浸透です。 NIR光が適切に体外培養に浸透することができますが、in vivoでの治療への変換は、消化器内視鏡検査、気管支鏡検査、または標的領域に近い光源を移動するための光ファイバーとの直接胸腔などの適応的なアプローチが必要となります。 NIR-PITのさらなる適応は、ローカルおよび仕様の両方におけるこの方法の使用を可能にします26 -このような免疫調節または腫瘍微小環境24のような多くの分野でIFIC細胞の除去。

他の細胞に損傷を与えることなく、特定の細胞を除去することは、特に確立された組織に、非常に困難であり、組織工学の分野における細胞除去方法に対する緊急の必要性があります。 3 -最近再生医療の分野では、胚性幹細胞（ES）、多能性幹細胞（のPSC）、または誘導多能性幹細胞（IPS）を使用して、組織培養、材料1が期待されています。 この組織再生が有望であるが、望ましくない細胞による汚染が主要な関心事です。また、移植4,5後の腫瘍形成能の安全性の懸念があります。多くの研究は、これらの問題に焦点を当ててきたが、特に再生医療6で、特定の細胞を排除するために- 8、実用的な方法が開発されていません。 近赤外photoimmunotherapy（NIR-PIT）は、抗体の光吸収conjugatに基づく治療法ですE（APC）。 APCは、細胞特異的なモノクローナル抗体（mAb）と光吸収、IR700で構成されています。 IR700は、親水性シリカ、フタロシアニン誘導体であり、それ自体9によって光毒性を誘発しません。 IR700は、共有リジン分子の側鎖のアミド残基を介して抗体に結合されます。 APCは、細胞膜上の標的分子に結合し、その後、690 nmの近赤外光への曝露後にほぼ即時の細胞壊死を誘導します。 14 - NIR光への曝露の間に、細胞膜の破裂は、細胞死に9をリード。 21 - NIR-PITは、抗EGFR、抗HER2、抗PSMA、抗CD25、抗メソテリン、抗GPC3、および抗CEA 15を含む複数の抗体または抗体断片と効果的であることが証明されています。したがって、NIR-PITは、標的分子の広範囲に対して使用することができます。また、NIR-PITは、NIR-ガーゼを制限することによって、特定の領域の選択的処理を可能にする十分に制御された治療でありますトン照射18,22。 ここでは、混合3D培養物からNIR-PITを使用して、特定の細胞除去の方法を提示します。

<table border="0" cellpadding="0" cellspacing="0" width="1083">
	<tbody>
		<tr height="21">
			<td height="21" style="height:21px;width:424px;">IRDye 700DX Ester Infrared Dye</td>
			<td style="width:364px;">LI-COR Bioscience (Lincoln, NE, USA)</td>
			<td style="width:191px;">929-70011</td>
			<td style="width:104px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Na2HPO4</td>
			<td>SIGMA-ALDRICH (St. Louis, MO, USA)</td>
			<td>S9763</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Sephadex G25 column (PD-10)&#160;</td>
			<td>GE Healthcare (Piscataway, NJ, USA)</td>
			<td>17-0851-01</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Coomassie (bradford) Plus protein assay</td>
			<td>Thermo Fisher Scientific Inc (Waltham, MA, USA)</td>
			<td>PI-23200</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Perfecta3D 96-Well hanging Drop Plates</td>
			<td>3D Biomatrix Inc (Ann Arbor, MI, USA)</td>
			<td>HDP1096-8</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Optical power meter</td>
			<td>Thorlabs (Newton, NJ, USA)</td>
			<td>PM100</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">LED: L690-66-60</td>
			<td>Marubeni America Co. (Santa Clara, CA, USA)</td>
			<td>L690-66-60</td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Vectibix (panitumumab)</td>
			<td>Amgen (Thousand Oaks, CA, USA)</td>
			<td></td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">35mm glass bottom dish, dish size 35mm, well size 10mm</td>
			<td>Cellvis (Mountain View, CA, USA)</td>
			<td>D35-10-0-N</td>
			<td></td>
		</tr>
	</tbody>
</table>

selective cell elimination from mixed 3d culture using a near infrared photoimmunotherapy technique

Recent developments in tissue engineering offer innovative solutions for many diseases. For example, tissue engineering using induced pluripotent stem cell (iPS) emerged as a new method in regenerative medicine. Although this tissue regeneration is promising, contamination with unwanted cells during tissue cultures is a major concern. Moreover, there is a safety concern regarding tumorigenicity after transplantation. Therefore, there is an urgent need for eliminating specific cells without damaging other cells that need to be protected, especially in established tissue. Here, we present a method for specific cell elimination from a mixed 3D cell culture in vitro with near infrared photoimmunotherapy (NIR-PIT) without damaging non-targeted cells. This technique enables the elimination of specific cells from mixed cell cultures or tissues.

光学NIR-PITの効果を監視するには、EGFRを過剰発現するA431細胞株は、遺伝的にもGFPおよびルシフェラーゼ（A431-LUC-GFP）を発現するように変更されました。 NIR-PITの非標的として、のBalb / 3T3細胞株を光学的にRFP（3T3-RFP）を発現するように改変しました。 APC、パニツムマブ-IR700（パン-IR700）を合成しました。細胞（A431-LUC-GFPおよび3T3-RFP）の種々の比率で構成された混合スフェロイドは、このプロトコル（ 図1）に従って作製しました。繰り返しNIR-PITがpan-IR700（ 図2A中のレジメンを参照）のインキュベーションを行いました。この混合3D培養からの標的細胞の除去を達成し、蛍光およびルシフェラーゼ活性（ 図2B、C）でモニターしました。一方、非標的細胞は、成長し続けました。 <img alt="図1" src="/files/ftp_upload/53633/53633fig1.jpg" /> <strオング&gt;混合スフェロイドの種々の比率の図1.代表的な画像。混合スフェロイドの代表的な画像は、A431-LUC-GFP細胞と7日目の3T3-RFP細胞の種々の割合が示されています。スケールバー=200μmです。この図は、16から変更されている。 <a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53633/53633fig1large.jpg" target="_blank">この図の拡大版をご覧になるにはこちらをクリックしてください。</a> <img alt="図2" src="/files/ftp_upload/53633/53633fig2.jpg" /> 3Dスフェロイド（混合A431-LUC-GFPのスフェロイドおよび3T3-RFP細胞）における図2の標的細胞除去（A）NIR-PIT（2 J / cm 2）を計画が示されています。 （B）を混合し、3Dスフェロイドにおける非標的細胞（3T3-RFP）への害、とNIR-PIT完全に排除した標的細胞（A431-LUC-GFP）を繰り返し。バー=200μmです。ルシフェラーゼ活性の（C）定量（RLU比）標的細胞（各群のn = 10のスフェロイド）の完全な消失を示しました。この図は、18から変更されています。データは±をSEMとして表している<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/53633/53633fig2large.jpg" target="_blank">。この図の拡大版をご覧になるにはこちらをクリックしてください。</a>

Watch this Scientific Journal Video about Selective Cell Elimination from Mixed 3D Culture Using a Near Infrared Photoimmunotherapy Technique at JoVE.com

Selective Cell Elimination from Mixed 3D Culture Using a Near Infrared Photoimmunotherapy Technique

Eliminating specific cells without damaging other cells is extremely difficult, especially in established tissue, yet there is an urgent need for a cell elimination method in the tissue engineering field. Here, we present a method for specific cell elimination from a mixed 3D cell culture using near infrared photoimmunotherapy (NIR-PIT).

近赤外Photoimmunotherapy法を用いた混合3D文化からの選択的な細胞除去

Recent developments in tissue engineering offer innovative solutions for many diseases. For example, tissue engineering using induced pluripotent stem ...

selective-cell-elimination-from-mixed-3d-culture-using-near-infrared

Nanyang Technological University

Research

JoVE Journal

Bioengineering

7.8K ビュー.  National Cancer Institute. Eliminating specific cells without damaging other cells is extremely difficult, especially in established tissue, yet there is an urgent need for a cell elimination method in the tissue engineering field. Here, we present a method for specific cell elimination from a mixed 3D cell culture using near infrared photoimmunotherapy (NIR-PIT). 

ビデオ: Selective Cell Elimination from Mixed 3D Culture Using a Near Infrared Photoimmunotherapy Technique

A Simple Hanging Drop Cell Culture Protocol for Generation of 3D Spheroids

Studies of cell-cell cohesion and cell-substratum adhesion have historically been performed on monolayer cultures adherent to rigid substrates. Cells within a tissue, however, are typically encased within a closely packed tissue mass in which cells establish intimate connections with many near-neighbors and with extracellular matrix components. Accordingly, the chemical milieu and physical forces experienced by cells within a 3D tissue are fundamentally different than those experienced by cells grown in monolayer culture. This has been shown to markedly impact cellular morphology and signaling. Several methods have been devised to generate 3D cell cultures including encapsulation of cells in collagen gels1or in biomaterial scaffolds2. Such methods, while useful, do not recapitulate the intimate direct cell-cell adhesion architecture found in normal tissues. Rather, they more closely approximate culture systems in which single cells are loosely dispersed within a 3D meshwork of ECM products. Here, we describe a simple method in which cells are placed in hanging drop culture and incubated under physiological conditions until they form true 3D spheroids in which cells are in direct contact with each other and with extracellular matrix components. The method requires no specialized equipment and can be adapted to include addition of any biological agent in very small quantities that may be of interest in elucidating effects on cell-cell or cell-ECM interaction. The method can also be used to co-culture two (or more) different cell populations so as to elucidate the role of cell-cell or cell-ECM interactions in specifying spatial relationships between cells. Cell-cell cohesion and cell-ECM adhesion are the cornerstones of studies of embryonic development, tumor-stromal cell interaction in malignant invasion, wound healing, and for applications to tissue engineering. This simple method will provide a means of generating tissue-like cellular aggregates for measurement of biomechanical properties or for molecular and biochemical analysis in a physiologically relevant model.

We describe a simple, rapid method of generating 3D tissue-like spheroids and their potential application to quantify differences in cell-cell interactions.

3D楕円体の生成のための簡単​​なハンギングドロップ細胞培養プロトコル

Studies of cell-cell cohesion and cell-substratum adhesion have historically been performed on monolayer cultures adherent to rigid substrates. Cells ...

生物工学

Rotating Cell Culture Systems for Human Cell Culture: Human Trophoblast Cells as a Model

The field of human trophoblast research aids in understanding the complex environment established during placentation. Due to the nature of these studies, human in vivo experimentation is impossible. A combination of primary cultures, explant cultures and trophoblast cell lines1 support our understanding of invasion of the uterine wall2 and remodeling of uterine spiral arteries3,4 by extravillous trophoblast cells (EVTs), which is required for successful establishment of pregnancy. Despite the wealth of knowledge gleaned from such models, it is accepted that in vitro cell culture models using EVT-like cell lines display altered cellular properties when compared to their in vivo counterparts5,6. Cells cultured in the rotating cell culture system (RCCS) display morphological, phenotypic, and functional properties of EVT-like cell lines that more closely mimic differentiating in utero EVTs, with increased expression of genes mediating invasion (e.g. matrix metalloproteinases (MMPs)) and trophoblast differentiation7,8,9. The Saint Georges Hospital Placental cell Line-4 (SGHPL-4) (kindly donated by Dr. Guy Whitley and Dr. Judith Cartwright) is an EVT-like cell line that was used for testing in the RCCS.
The design of the RCCS culture vessel is based on the principle that organs and tissues function in a three-dimensional (3-D) environment. Due to the dynamic culture conditions in the vessel, including conditions of physiologically relevant shear, cells grown in three dimensions form aggregates based on natural cellular affinities and differentiate into organotypic tissue-like assemblies10,11,12 . The maintenance of a fluid orbit provides a low-shear, low-turbulence environment similar to conditions found in vivo. Sedimentation of the cultured cells is countered by adjusting the rotation speed of the RCCS to ensure a constant free-fall of cells. Gas exchange occurs through a permeable hydrophobic membrane located on the back of the bioreactor. Like their parental tissue in vivo, RCCS-grown cells are able to respond to chemical and molecular gradients in three dimensions (i.e. at their apical, basal, and lateral surfaces) because they are cultured on the surface of porous microcarrier beads. When grown as two-dimensional monolayers on impermeable surfaces like plastic, cells are deprived of this important communication at their basal surface. Consequently, the spatial constraints imposed by the environment profoundly affect how cells sense and decode signals from the surrounding microenvironment, thus implying an important role for the 3-D milieu13.
We have used the RCCS to engineer biologically meaningful 3-D models of various human epithelial tissues7,14,15,16. Indeed, many previous reports have demonstrated that cells cultured in the RCCS can assume physiologically relevant phenotypes that have not been possible with other models10,17-21. In summary, culture in the RCCS represents an easy, reproducible, high-throughput platform that provides large numbers of differentiated cells that are amenable to a variety of experimental manipulations. 
In the following protocol, using EVTs as an example, we clearly describe the steps required to three-dimensionally culture adherent cells in the RCCS.

Traditional, two dimensional cell culture techniques often result in altered characteristics with respect to differentiation markers, cytokines and growth factors. Three-dimensional cell culture in the rotating cell culture system (RCCS) reestablishes expression of many of these factors as shown here with an extravillous trophoblast cell line.

ヒト細胞培養のための回転細胞培養システム：モデルとしてのヒト栄養膜細胞

The field of human trophoblast research aids in  understanding the complex environment established during placentation. Due to the  nature of these ...

Preparation of 3D Fibrin Scaffolds for Stem Cell Culture Applications

Stem cells are found in naturally occurring 3D microenvironments in vivo, which are often referred to as the stem cell niche 1. Culturing stem cells inside of 3D biomaterial scaffolds provides a way to accurately mimic these microenvironments, providing an advantage over traditional 2D culture methods using polystyrene as well as a method for engineering replacement tissues 2. While 2D tissue culture polystrene has been used for the majority of cell culture experiments, 3D biomaterial scaffolds can more closely replicate the microenvironments found in vivo by enabling more accurate establishment of cell polarity in the environment and possessing biochemical and mechanical properties similar to soft tissue.3 A variety of naturally derived and synthetic biomaterial scaffolds have been investigated as 3D environments for supporting stem cell growth. While synthetic scaffolds can be synthesized to have a greater range of mechanical and chemical properties and often have greater reproducibility, natural biomaterials are often composed of proteins and polysaccharides found in the extracelluar matrix and as a result contain binding sites for cell adhesion and readily support cell culture. Fibrin scaffolds, produced by polymerizing the protein fibrinogen obtained from plasma, have been widely investigated for a variety of tissue engineering applications both in vitro and in vivo 4. Such scaffolds can be modified using a variety of methods to incorporate controlled release systems for delivering therapeutic factors 5. Previous work has shown that such scaffolds can be used to successfully culture embryonic stem cells and this scaffold-based culture system can be used to screen the effects of various growth factors on the differentiation of the stem cells seeded inside 6,7.
 This protocol details the process of polymerizing fibrin scaffolds from fibrinogen solutions using the enzymatic activity of thrombin. The process takes 2 days to complete, including an overnight dialysis step for the fibrinogen solution to remove citrates that inhibit polymerization. These detailed methods rely on fibrinogen concentrations determined to be optimal for embryonic and induced pluripotent stem cell culture. Other groups have further investigated fibrin scaffolds for a wide range of cell types and applications - demonstrating the versatility of this approach 8-12.

This work details the preparation of 3D fibrin scaffolds for culturing and differentiating plutipotent stem cells. Such scaffolds can be used to screen the effects of various biological compounds on stem cell behavior as well as modified to contain drug delivery systems.

幹細胞培養アプリケーションのための3Dフィブリン足場の調製

Stem cells are found in naturally occurring 3D microenvironments in vivo, which are often referred to as the stem cell niche 1. Culturing stem cells ...

A Novel Method for Localizing Reporter Fluorescent Beads Near the Cell Culture Surface for Traction Force Microscopy

PA gels have long been used as a platform to study cell traction forces due to ease of fabrication and the ability to tune their elastic properties. When the substrate is coated with an extracellular matrix protein, cells adhere to the gel and apply forces, causing the gel to deform. The deformation depends on the cell traction and the elastic properties of the gel. If the deformation field of the surface is known, surface traction can be calculated using elasticity theory. Gel deformation is commonly measured by embedding fluorescent marker beads uniformly into the gel. The probes displace as the gel deforms. The probes near the surface of the gel are tracked. The displacements reported by these probes are considered as surface displacements. Their depths from the surface are ignored. This assumption introduces error in traction force evaluations. For precise measurement of cell forces, it is critical for the location of the beads to be known. We have developed a technique that utilizes simple chemistry to confine fluorescent marker beads, 0.1 and 1 &#181;m in diameter, in PA gels, within 1.6 &#956;m of the surface. We coat a coverslip with poly-D-lysine (PDL) and fluorescent beads. PA gel solution is then sandwiched between the coverslip and an adherent surface. The fluorescent beads transfer to the gel solution during curing. After polymerization, the PA gel contains fluorescent beads on a plane close to the gel surface.

Traditional techniques for fabricating polyacrylamide (PA) gels containing fluorescent probes involve sandwiching a gel between an adherent surface and a glass slide. Here, we show that coating this slide with poly-D-lysine (PDL) and fluorescent probes localizes the probes to within 1.6 &#181;m from the gel surface.

トラクション力顕微鏡用の細胞培養表面近くのローカライズレポーター蛍光ビーズのための新しい方法

PA gels have long been used as a platform to study cell traction forces due to ease of fabrication and the ability to tune their elastic properties. When ...

Fluorescence-quenching of a Liposomal-encapsulated Near-infrared Fluorophore as a Tool for In Vivo Optical Imaging

Optical imaging offers a wide range of diagnostic modalities and has attracted a lot of interest as a tool for biomedical imaging. Despite the enormous number of imaging techniques currently available and the progress in instrumentation, there is still a need for highly sensitive probes that are suitable for in vivo imaging. One typical problem of available preclinical fluorescent probes is their rapid clearance in vivo, which reduces their imaging sensitivity. To circumvent rapid clearance, increase number of dye molecules at the target site, and thereby reduce background autofluorescence, encapsulation of the near-infrared fluorescent dye, DY-676-COOH in liposomes and verification of its potential for in vivo imaging of inflammation was done. DY-676 is known for its ability to self-quench at high concentrations. We first determined the concentration suitable for self-quenching, and then encapsulated this quenching concentration into the aqueous interior of PEGylated liposomes. To substantiate the quenching and activation potential of the liposomes we use a harsh freezing method which leads to damage of liposomal membranes without affecting the encapsulated dye. The liposomes characterized by a high level of fluorescence quenching were termed Lip-Q. We show by experiments with different cell lines that uptake of Lip-Q is predominantly by phagocytosis which in turn enabled the characterization of its potential as a tool for in vivo imaging of inflammation in mice models. Furthermore, we use a zymosan-induced edema model in mice to substantiate the potential of Lip-Q in optical imaging of inflammation in vivo. Considering possible uptake due to inflammation-induced enhanced permeability and retention (EPR) effect, an always-on liposome formulation with low, non-quenched concentration of DY-676-COOH (termed Lip-dQ) and the free DY-676-COOH were compared with Lip-Q in animal trials.

Fluorescence-quenching of a Liposomal-encapsulated Near-infrared Fluorophore as a Tool for In Vivo Optical Imaging

The use of fluorophores for in vivo imaging can be greatly limited by opsonization, rapid clearance, low detection sensitivity and cytotoxic effects on the host. Encapsulation of fluorophores in liposomes by film hydration and extrusion leads to fluorescence quenching and protection which enables in vivo imaging with high detection sensitivity.

のためのツールと​​してのリポソームカプセル化された近赤外蛍光体の蛍光消光<em&gt;インビボ</em&gt;光学イメージング

Optical imaging offers a wide range of diagnostic modalities and has attracted a lot of interest as a tool for biomedical imaging. Despite the enormous ...

Using Adhesive Patterning to Construct 3D Paper Microfluidic Devices

We demonstrate the use of patterned aerosol adhesives to construct both planar and nonplanar 3D paper microfluidic devices. By spraying an aerosol adhesive through a metal stencil, the overall amount of adhesive used in assembling paper microfluidic devices can be significantly reduced. We show on a simple 4-layer planar paper microfluidic device that the optimal adhesive application technique and device construction style depends heavily on desired performance characteristics. By moderately increasing the overall area of a device, it is possible to dramatically decrease the wicking time and increase device success rates while also reducing the amount of adhesive required to keep the device together. Such adhesive application also causes the adhesive to form semi-permanent bonds instead of permanent bonds between paper layers, enabling single-use devices to be non-destructively disassembled after use. Nonplanar 3D origami devices also benefit from the semi-permanent bonds during folding, as it reduces the likelihood that unrelated faces may accidently stick together. Like planar devices, nonplanar structures see reduced wicking times with patterned adhesive application vs uniformly applied adhesive.

We demonstrate the use of patterned aerosol adhesives to construct 3D paper microfluidic devices. This method of adhesive application forms semi-permanent bonds between layers, enabling single-use devices to be non-destructively disassembled after use and to ease folding complex nonplanar structures.

3Dペーパーマイクロ流体デバイスを構築するために接着剤パターニングを使用して、

We demonstrate the use of patterned aerosol adhesives to construct both planar and nonplanar 3D paper microfluidic devices. By spraying an aerosol ...

Micropatterning and Assembly of 3D Microvessels

In vitro platforms to study endothelial cells and vascular biology are largely limited to 2D endothelial cell culture, flow chambers with polymer or glass based substrates, and hydrogel-based tube formation assays. These assays, while informative, do not recapitulate lumen geometry, proper extracellular matrix, and multi-cellular proximity, which play key roles in modulating vascular function. This manuscript describes an injection molding method to generate engineered vessels with diameters on the order of 100 &#181;m. Microvessels are fabricated by seeding endothelial cells in a microfluidic channel embedded within a native type I collagen hydrogel. By incorporating parenchymal cells within the collagen matrix prior to channel formation, specific tissue microenvironments can be modeled and studied. Additional modulations of hydrodynamic properties and media composition allow for control of complex vascular function within the desired microenvironment. This platform allows for the study of perivascular cell recruitment, blood-endothelium interactions, flow response, and tissue-microvascular interactions. Engineered microvessels offer the ability to isolate the influence from individual components of a vascular niche and precisely control its chemical, mechanical, and biological properties to study vascular biology in both health and disease.

This manuscript presents an injection molding method to engineer microvessels that recapitulate physiological properties of endothelium. The microfluidic-based process creates patent 3D vascular networks with tailorable conditions, such as flow, cellular composition, geometry, and biochemical gradients. The fabrication process and examples of potential applications are described.

微細と3D微小血管の組立

In vitro platforms to study endothelial cells and vascular biology are largely limited to 2D endothelial cell culture, flow chambers with polymer or glass ...

Tunable Hydrogels from Pulmonary Extracellular Matrix for 3D Cell Culture

Here we present a method for establishing multiple component cell culture hydrogels for in vitro lung cell culture. Beginning with healthy en bloc lung tissue from porcine, rat, or mouse, the tissue is perfused and submerged in subsequent chemical detergents to remove the cellular debris. Histological comparison of the tissue before and after processing confirms removal of over 95% of double stranded DNA and alpha galactosidase staining suggests the majority of cellular debris is removed. After decellularization, the tissue is lyophilized and then cryomilled into a powder. The matrix powder is digested for 48 hr in an acidic pepsin digestion solution and then neutralized to form the pregel solution. Gelation of the pregel solution can be induced by incubation at 37 &#176;C and can be used immediately following neutralization or stored at 4 &#176;C for up to two weeks. Coatings can be formed using the pregel solution on a non-treated plate for cell attachment. Cells can be suspended in the pregel prior to self-assembly to achieve a 3D culture, plated on the surface of a formed gel from which the cells can migrate through the scaffold, or plated on the coatings. Alterations to the strategy presented can impact gelation temperature, strength, or protein fragment sizes. Beyond hydrogel formation, the hydrogel stiffness may be increased using genipin.

This is a method to create a 3-dimensional cell culture scaffold from pulmonary extracellular matrix. Intact lung is processed into hydrogels that can support the growth of cells in three-dimensions.

3D細胞培養のための肺細胞外マトリックスから調整可能なヒドロゲル

Here we present a method for establishing multiple component cell culture hydrogels for in vitro lung cell culture. Beginning with healthy en bloc lung ...

Bioprinting of Cartilage and Skin Tissue Analogs Utilizing a Novel Passive Mixing Unit Technique for Bioink Precellularization

Bioprinting is a powerful technique for the rapid and reproducible fabrication of constructs for tissue engineering applications. In this study, both cartilage and skin analogs were fabricated after bioink pre-cellularization utilizing a novel passive mixing unit technique. This technique was developed with the aim to simplify the steps involved in the mixing of a cell suspension into a highly viscous bioink. The resolution of filaments deposited through bioprinting necessitates the assurance of uniformity in cell distribution prior to printing to avoid the deposition of regions without cells or retention of large cell clumps that can clog the needle. We demonstrate the ability to rapidly blend a cell suspension with a bioink prior to bioprinting of both cartilage and skin analogs. Both tissue analogs could be cultured for up to 4 weeks. Histological analysis demonstrated both cell viability and deposition of tissue specific extracellular matrix (ECM) markers such as glycosaminoglycans (GAGs) and collagen I respectively.

Cartilage and skin analogs were bioprinted using a nanocellulose-alginate based bioink. The bioinks were cellularized prior to printing via a single step passive mixing unit. The constructs were demonstrated to be uniformly cellularized, have high viability, and exhibit favorable markers of differentiation.

軟骨と皮膚組織類縁ミキシング ユニット Bioink Precellularization の小説のパッシブ バイオプリンティング

Bioprinting is a powerful technique for the rapid and reproducible fabrication of constructs for tissue engineering applications. In this study, both ...

Fabrication of Custom Agarose Wells for Cell Seeding and Tissue Ring Self-assembly Using 3D-Printed Molds

Engineered tissues are being used clinically for tissue repair and replacement, and are being developed as tools for drug screening and human disease modeling. Self-assembled tissues offer advantages over scaffold-based tissue engineering, such as enhanced matrix deposition, strength, and function. However, there are few available methods for fabricating 3D tissues without seeding cells on or within a supporting scaffold. Previously, we developed a system for fabricating self-assembled tissue rings by seeding cells into non-adhesive agarose wells. A polydimethylsiloxane (PDMS) negative was first cast in a machined polycarbonate mold, and then agarose was gelled in the PDMS negative to create ring-shaped cell seeding wells. However, the versatility of this approach was limited by the resolution of the tools available for machining the polycarbonate mold. Here, we demonstrate that 3D-printed plastic can be used as an alternative to machined polycarbonate for fabricating PDMS negatives. The 3D-printed mold and revised mold design is simpler to use, inexpensive to produce, and requires significantly less agarose and PDMS per cell seeding well. We have demonstrated that the resulting agarose wells can be used to create self-assembled tissue rings with customized diameters from a variety of different cell types. Rings can then be used for mechanical, functional, and histological analysis, or for fabricating larger and more complex tubular tissues.

This protocol describes a platform for fabricating self-assembled tissue rings in variable sizes using a customized 3D-printed plastic mold. PDMS negatives are cured in the 3D-printed mold; then agarose is cast in the cured PDMS negatives. Cells are seeded into the resulting agarose wells where they aggregate into tissue rings.

細胞播種用カスタム Agarose 井戸とティッシュ リング自己組織型の 3 D プリントを使用しての作製

Engineered tissues are being used clinically for tissue repair and replacement, and are being developed as tools for drug screening and human disease ...