采用生物医学工程系佛罗里达国际大学的设施，这项工作进行。

1，静电收集器安装<ol><li>切铝箔成一块长方形。 </li><li>折叠矩形片成长方形条状，且垂直安装到一个平坦的金属板带（ 图1）。注意:该纤维垫的大小取决于带材的长度和宽度。因此，如所需要的带材的尺寸可以调节。 </li></ol> 2，聚合物溶液的制备<ol><li>在一个烧杯1:1的摩尔比混合的甘油和十二烷二酸（DDA），在120℃下进行100小时，得到PGD聚合物。 </li><li>溶解的聚（氧化乙烯）（PEO）和明胶在65％的乙醇与1.5:3:95.5在一个15毫升管的重量比，拧紧盖和加热的炉中，混合物在60℃下进行1小时搅拌直到它变成一种均匀的溶液（溶液基底）。 </li><li>对于静电，混合PGD聚合物和4:6重量比的基础解决方案。注:PGD浓度具有双向对纤维直径克效果。 30％-50％的胚胎植​​入前诊断％是可以接受的，以生产纤维长于5厘米，纤维直径增大。 </li><li>添加0.1％核黄素的聚合物溶液拌匀。 </li></ol> 3，静电<ol><li>喂聚合物溶液倒入5毫升的标准注射器18G的迟钝不锈钢针。 </li><li>将注射器插入注射器泵。 </li><li>附加的高电压电源向所述金属板和带正电的导线连接到针的接地引线。 </li><li>调节机针和铝箔带材至15cm之间的距离。 </li><li>将注射器泵中的与水平面大约15°的角度，以防止纤维聚集在条带的前部。 </li><li>打开注射泵和调节泵的流速0.6毫升/小时。 </li><li>打开高压电源，并设置工作电压14.6千伏。 </li></ol> 4。纤维加工<ol><li>后收集完成后，露出纤维垫在UV光下60分钟进行交联。 </li><li>从铝箔带材传送纤维垫到100 mm培养皿中，并暴露于紫外光下，另一个20分钟的灭菌。 </li><li>在生物安全柜，切纤维垫成圆块相同大小的用手术刀片和放置块放入24孔板中。 </li><li>对电池预播种处理，浸入纤维样品在1ml磷酸盐缓冲盐水（PBS）中，并在37℃保温过夜。 </li><li>翌日，吸PBS小心，加入1 ml的分化培养基（DMEM/F12，N2和FGF2）（见配方中的材料表），以每口井和孵化在37℃3小时。 </li><li>吸分化培养基仔细，加0.2mL的中的每个纤维样品，并在37℃下30分钟。注意:层粘连蛋白，也可用于纤维的涂层。加入0.2 ml的20微克/毫升层粘连蛋白到光纤和在室温下孵育3小时。 </li><li>小心地从每孔中去除多余的基质胶。冲洗用2ml分化培养基一次。注意:该纤维样品准备用于细胞培养。 </li></ol> 5，对纤维细胞种植<ol><li>加入1 ml的Accutase到的mES细胞培养皿中，并孵育10分钟，在37℃下</li><li> 10分钟后，在mES细胞从培养皿中脱落。加入4 mL分化培养基中的板块。收集漂浮ES细胞成15ml试管和吸管细胞向上和向下突破的菌落（约15倍）。 </li><li>离心机在400×g离心5分钟，并重新悬浮的细胞在4毫升的分化培养基。 </li><li>使用血细胞计数器计数细胞。转移200μl的细胞悬浮液到一个15ml试管中，并用分化培养基稀释10倍。转让15微升稀释细胞悬液，以室上有盖，防滑到位的血球。算细胞在1毫米的中心广场和显微镜下血球的四角方块。注:细胞每毫升=每平方米的平均计数x稀释倍数×10 4 </li><li>放置约5×10 4个mES细胞到每个孔中。慢慢地滴细胞悬液到纤维样品的中间，而不是到井的侧面滑出，以防止溶液从排水纤维垫。 </li><li>加入1 ml分化培养基到每个孔中，并保持所述板在培养箱中在37℃和5％CO 2，使细胞附着，生长和分化。 </li><li>从每个吸出旧培养基并用1ml的新鲜分化培养基替换每隔一天。 </li></ol> 6，细胞活力<ol><li>从每孔吸出旧培养基。 </li><li>混合用培养基刃天青荧光试剂的1/10体积并加入1 ml至各孔中。 </li><li> Incub吃了在37℃和5％CO 2 4小时，光线直射保护。 </li><li> 4小时后，从每个孔转移100μl的3倍的试剂到一个96孔板中，然后将样品准备好被使用560EX nm/590EM过滤器设置在荧光分光光度计测定。 </li></ol> 7，实时定量PCR <ol><li>后培养14天，加入裂解缓冲液中的样品和从在纤维样本的细胞中分离总RNA。 </li><li>使用4μl总RNA的反转录合成cDNA在20μl反应体系尺度。 </li><li>准备每个光电管在PCR反应混合物中:10微升主混合物（2×），0.2微升染料，8微升不含核酸酶的水，1微升的cDNA，和1μl引物（在本研究中使用的引物列于表1）。 </li><li>设置PCR程序:a。 95℃2时20分，1个循环B。 95°C 3秒→60℃1分钟，40圈C。 95℃15秒，1比D。 60℃1分钟，1个循环é。 95℃15秒，1个循环。选择比较C T方法来确定相关基因的表达水平。 </li><li> PCR结束后，分析了实时PCR的结果与StepOne软件，并将结果导出到Excel。 </li></ol>

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没有利益冲突的声明。

简单的收集器或旋转了目前用于静电增加获得所需的长度和纤维垫的尺寸对于一些应用的限制集热器的复杂性的限制。此外，传输光纤从地面集电极到培养皿或其它基材是一种挑战5。在这份报告中，全新设计的收集器，只需通过将铝箔带与接地收藏家制成，能够20厘米处一次获得大尺寸纤维毡可达10厘米。 图1和图2说明了原理图设计安装制造长达10厘米长的静电纤维与控制垫宽度。通过针尖和集电极之间的静电场的影响，该静电纺丝纤维进行拉伸的整个区域中的铝箔条带和接地集电极之间形成光滑的纤维垫，它可以很容易地转移到另一个Substrate。电纺纤维提供多孔性纤维结构，这使细胞缩小，并连接到多根纤维在一个真正的三维环境。在这项研究中产生的纤维毡是足够大，以使他们的理想候选者广泛的应用，例如伤口愈合，神经再生​​。 纤维直径可通过控制电纺丝过程中的几个变量进行调整。这些变量包括聚合物浓度，施加电压的大小，聚合物输送速率，距离，从针到收集器等6-8。在这项研究中，测试解决方案，它是由具有50％PGD和50％学士学位，40％PGD和60％的学士学位，30％PGD和70％的学士学位，20％PGD和80％的学士学位，分别制备的使静电纤维。使用SEM来确定纤维的直径和形态（ 图3）的纤维支架进行了研究。正如预期的那样，较高的PGD浓度produced较大的电纺纤维的直径。还有，重要的是根据不同的PGD浓度来调整带材的长度。较低浓度的PGD需要一个较短的剥离长度，以确保纤维的形成。 已经做了许多努力，通过细胞培养9-13的研究，探讨了静电纤维支架的生物相容性。 图4显示的共聚焦显微镜图像的贴壁细胞与强烈的绿色荧光信号显示在胚胎植入前诊断纤维细胞的存活率。另外，细胞密度为3天增加到6天还建议对PGD纤维细胞的增殖。在图5中的细胞生存力试验也证实了这一结果。的神经细胞标记MAP2和DCX的基因表达证明了mES细胞能够分化为神经细胞的支架材料（ 图6）。总之，胚胎植入前诊断纤维支架能够支持细胞表面粘附n和增殖，并因此表现出对神经组织工程应用的潜力。 下面是一些常规的故障排除指南:如果光纤出来的针是不连续的，又温暖了聚合物溶液，并拌匀或者纤维粘在铝箔带没有钢带吸引力的金属板，降低带钢长度或增加PGD浓度。有时候大的聚合物水珠在针尖形成，关闭高压电源，用纸巾擦拭，并降低泵的输送速度。另外，在铝箔条带的上边缘有时纤维集合体尝试调整注射器泵的角度。

静电是有效的处理方法之一，以生产微型到纳米尺寸​​纤维支架。电纺丝的基本原理涉及的溶液泰勒锥，是在针的孔的针的前端与接地收集器之间施加高电压保持。当在溶液中的静电斥力克服表面张力，带电荷的液束喷射出来的针尖，穿过空气与溶剂蒸发，并最终沉积在接地的集电极。注射泵提供的解决方案出现从喷丝板连续流动和电纺丝纤维的这样的多个副本可以很短的时间周期内进行制造。在离开喷丝板，以在收集器到达的过程中，带电射流将进行根据多个参数，包括所述聚合物溶液的粘度和表面张力，该electrostati拉伸和搅打在溶液C中的力，以及外部电场的相互作用等，2。 在电纺丝过程中，一个收集器用作导电衬底，其中微至纳米纤维可沉积。在这项研究中，一种新型的纤维收集器被设计成获得的纤维毡具有所需尺寸（长×宽）。传统上，使用铝箔作为集电体，但它是很难从平坦的表面转移的纤维到另一衬底。从传统的收藏家收获一个完整的纤维毡的困难，主要是由于这一事实，即在静电纤维强力附着在收藏家的表面。因此，我们通过折叠一片铝箔的成矩形条和连接它垂直于金属平板改性的集电极。该电纺纤维被拉伸跨过区域的带材的前端部与金属板，它可以很容易地转移到另一substrat之间Ë。 在热交联弹性体聚合物的兴趣正在迅速增长，因为罗伯特·兰格的小组，谁介绍聚（丙三醇酯）（PGS），聚酯它类似于硫化橡胶在2002年3类似PGS的开创性工作，我们已成功开发聚（甘油-十二烷酸）（PGD）由甘油和十二烷二酸热冷凝并显示出其独特的形状记忆性能1。不像硬的合成材料聚（羟基丁酸酯）或聚（L-丙交酯）（杨氏模量分别为250兆帕和660兆帕），PGD表现出弹性性质类似橡胶，具有杨氏模量为1.08兆帕，当温度高于37℃ C，这是一场势均力敌的比赛到现场周围神经（0.45兆帕）。此外，PGD是可生物降解和降解时间可微调，通过改变甘油和十二双酸的比率。十二双酸是一种12 - 碳亚姿态具有两个末端羧酸基团，HOOC（CH 2）10 COOH。偶数编号的二羧酸类似癸二酸和十二双酸可被代谢为乙酰-CoA和进入三羧酸（TCA）/（柠檬酸）周期。二羧酸的代谢产物，琥珀酰-CoA，是一种gluconeogenetic前体和中间体TCA循环4。因此，一些研究表明，它们可以被用作用于肠内和肠外营养的替代燃料底物，特别是在病理条件。此外，PGD表现出独特的形状记忆体，因为其玻璃化转变温度为31℃，因此它示出了不同的机械性能在室温和体温。总之，PGD是可生物降解，​​生物相容性，表现出独特的弹性性质类似于神经组织的机械性能;因此，它是一种合适的材料为神经组织工程应用。在这个协议中，静电长纤维跨越大面积的存款从通过PGD全新设计的收集器是捏造的。纤维支架可以支持鼠标的多能干细胞的生长和分化。

<table border="0" cellpadding="0" cellspacing="0" width="729">
	<tbody>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Glycerol</td>
			<td style="width:175px;">Sigma-Aldrich</td>
			<td style="width:119px;">G7757</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Dodecanedioic acid</td>
			<td style="width:175px;">Sigma-Aldrich</td>
			<td style="width:119px;">D1009</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Gelatin</td>
			<td style="width:175px;">Sigma-Aldrich</td>
			<td style="width:119px;">D1890</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Poly (ehtylene oxide) (PEO)</td>
			<td style="width:175px;">Sigma-Aldrich</td>
			<td style="width:119px;">182028</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Riboflavin</td>
			<td style="width:175px;">Sigma-Aldrich</td>
			<td style="width:119px;">132350250</td>
			<td style="width:167px;">0.10%</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Mouse embryonic stem cells</td>
			<td style="width:175px;">GlobalStem</td>
			<td style="width:119px;">GSC-5002</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Matrigel</td>
			<td style="width:175px;">Becton Dickinson</td>
			<td style="width:119px;">356234</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">DMEM/F12</td>
			<td style="width:175px;">Thermo Scientific</td>
			<td style="width:119px;">SH30272.02</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">N2 supplement&#160;</td>
			<td style="width:175px;">Invitrogen</td>
			<td style="width:119px;">17502048</td>
			<td style="width:167px;">1%</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">FGF2</td>
			<td style="width:175px;">Stemgent</td>
			<td style="width:119px;">03-0002</td>
			<td style="width:167px;">10ng/ml</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Accutase</td>
			<td style="width:175px;">Invitrogen</td>
			<td style="width:119px;">A11105-01</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Phosphate buffered saline (PBS)</td>
			<td style="width:175px;">Invitrogen</td>
			<td style="width:119px;">10010-031&#160;</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Resazurin fluorescence dye&#160;</td>
			<td style="width:175px;">Sigma-Aldrich</td>
			<td style="width:119px;">62758-13-8&#160;</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">SV Total RNA Isolation System</td>
			<td style="width:175px;">Promega</td>
			<td style="width:119px;">Z3100</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">GoScript Reverse Transcription System</td>
			<td style="width:175px;">Promega</td>
			<td style="width:119px;">A5000</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">GoTaq&#129; qPCR Master Mix</td>
			<td style="width:175px;">Promega</td>
			<td style="width:119px;">A6001</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Syringe pump&#160;</td>
			<td style="width:175px;">Fisher scientific</td>
			<td style="width:119px;">14-831-200</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="33">
			<td height="33" style="height:33px;width:268px;">High voltage power source&#160;</td>
			<td style="width:175px;">Spellman High Voltage Electronics Corporation</td>
			<td style="width:119px;"></td>
			<td style="width:167px;">SL30</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">UV light</td>
			<td style="width:175px;">Philips</td>
			<td style="width:119px;">308643</td>
			<td style="width:167px;">15W/G15T8</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Synergy HT Multi-Mode Microplate Reader</td>
			<td style="width:175px;">BioTek</td>
			<td style="width:119px;"></td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">Perkin Elmer GeneAmp PCR System 9600</td>
			<td style="width:175px;">Perkin Elmer</td>
			<td style="width:119px;">8488</td>
			<td style="width:167px;"></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:268px;">StepOne Real-time PCR System</td>
			<td style="width:175px;">Applied Biosystems</td>
			<td style="width:119px;">4376357</td>
			<td style="width:167px;"></td>
		</tr>
	</tbody>
</table>

electrospun fibrous scaffolds of poly(glycerol-dodecanedioate) for engineering neural tissues from mouse embryonic stem cells

组织工程的应用，生物降解性和生物相容性支架的准备是最可取的，但具有挑战性的任务。在各种不同的制造方法，静电是由于它的简单性和通用性的最有吸引力的。此外，静电纺丝纳米纤维模仿天然的细胞外基质确保对细胞的存活和生长的额外支持的大小。这项研究表明长纤维通过使用新设计的收集器，用于电纺丝跨越较大的沉积区名为聚（甘油-十二烷酸），一种新型的可生物降解和生物相容的聚合物（PGD）1的制造中的可行性。 PGD​​具有独特弹性性能相似的机械性能，以神经组织，因此，它适合于神经组织工程应用。合成和制造建立用于制造纤维支架材料很简单，高重现性，而且价格便宜。在生物相容性测试，从小鼠胚胎干细胞来源的细胞可粘附和生长在静电PGD纤维。综上所述，该协议与PGD静电纤维，以支持小鼠胚胎干细胞源性神经系细胞的生长提供了一个通用的制造方法。

电纺丝的主要部件示于图1，一种大尺寸的纤维垫被典型地通过垂直附铝箔带材和平坦的金属板而获得。 图2示出了集电极设计和电纺丝纤维垫。的宽度和长度可以为不同的应用进行调整。与PGD聚合物和基底溶液混合而制成的纤维的长度可达10厘米。电纺纤维的形态示于图3中 。从40％PGD浓度制得的纤维的直径在微米范围内。从mES细胞对纤维3天和6天培养的分化细胞的共聚焦显微镜图像被描绘在图4的绿色荧光信号来自于细胞中的过表达绿色荧光蛋白（GFP）的。在图5中刃天青荧光试剂的结果表明，mES细胞生长氮对胚胎植入前诊断纤维涂层与基质胶和层粘连蛋白有相当于细胞活力，具有相对较高的增殖较未涂层组。的多能性和神经细胞的标记基因的表达进行定量实时PCR（ 图6）。大多数mES细胞的纤维上培养表达的多潜能标志物OCT4，Nanog和Sox2的，而细胞的少数表达的神经干细胞标记PAX6和巢蛋白。经过2周的培养，生长在纤维的mES显示神经细胞的标志，如MAP2和DCX的增加表达水平，以及少突胶质细胞标记Oligo1和星形胶质细胞标志物GFAP。 <img alt="图1" fo:content-width="5in" src="/files/ftp_upload/51587/51587fig1highres.jpg" width="500" /> 图1。静电成立。的聚合物溶液从钝针喷出。高电压电源理由平坦金属板nd为铝箔条带之间的微至纳米纤维沉积（蓝色）。 <img alt="图2" fo:content-width="4in" src="/files/ftp_upload/51587/51587fig2highres.jpg" width="400" /> 图2。集电极设计和电纺纤维垫。纤维垫的宽度和长度可以通过调整铝箔带材的尺寸来容易地改变。没有限制为垫的宽度，而最长的纤维可以是高达10厘米长。 <img alt="图3" fo:content-width="5in" src="/files/ftp_upload/51587/51587fig3highres.jpg" width="500" /> PGD ​​的静电和基底溶液4:6图3。SEM图像（W / W）。的纤维的平均直径约为2微米。当PGD浓度降低到30％时，纤维的平均直径落入纳米范围内。白标尺为10微米。 <img alt="图4" fo:content-width="4in" src="/files/ftp_upload/51587/51587fig4highres.jpg" width="400" /> 图4。对纤维分化ES细胞的共聚焦显微镜图像。携带绿色荧光蛋白表现出明亮的绿色荧光，当蓝色紫外线范围光线照射的细胞。在第6天的绿色荧光细胞的数量增加表示该纤维支架可以支持细胞粘附和增殖。白色的刻度条为100μm。（3日和6日）。 <img alt="图5" fo:content-width="6in" src="/files/ftp_upload/51587/51587fig5highres.jpg" width="500" /> 图5。mES细胞对PGD纤维在1与基质胶和层粘连蛋白涂覆，3和5天的细胞存活率为通过刃天青fluore确定杨继明试剂，细胞培养于作为对照组（P &lt;0.05）的无涂层纤维。 <img alt="图6" fo:content-width="6in" src="/files/ftp_upload/51587/51587fig6highres.jpg" width="500" /> 图6。在胚胎植入前诊断纤维分化ES细胞基因表达的定量RT-PCR分析。神经细胞标记明显，2周后表明，在支架的ES细胞分化为神经细胞。 <table border="0" cellpadding="0" cellspacing="0" width="261"><tbody><tr><td> mGAPDH-L </td><td> AACTTTGGCATTGTGGAAGG </td></tr><tr><td> mGAPDH-R </td><td> ACACATTGGGGGTAGGAACA </td></tr><tr><td> mOct4-L </td><td> CACGAGTGGAAAGCAACTCA </td></tr><tr><td> mOct4-R </td><td> AGATGGTGGTCTGGCTGAAC </td></tr><tr><td> mNanog-L </td><td> AAGTACCTCAGCCTCCAGCA </td></tr><tr><td> mNanog-R </td><td> GTGCTGAGCCCTTCTGAATC </td><html></tr><tr><td> mSox2-L </td><td> CACAGTTCAGCCCTGAGTGA </td></tr><tr><td> mSox2-R </td><td> AGGCCACAACAACAACAACA </td></tr><tr><td> mPax6-L </td><td> AACAACCTGCCTATGCAACC </td></tr><tr><td> mPax6-R </td><td> ACTTGGACGGGAACTGACAC </td></tr><tr><td> mNestin-L </td><td> CCAGAGCTGGACTGGAACTC </td></tr><tr><td> mNestin-R </td><td> ACCTGCCTCTTTTGGTTCCT </td></tr><tr><td> mMAP2-L </td><td> CTTATGGGAATGTGGGATGG </td></tr><tr><td> mMAP2-R </td><td> AAAAAGTGGGCCTTGGAACT </td></tr><tr><td> MDCX-L </td><td> ATGCAGTTGTCCCTCCATTC </td></tr><tr><td> MDCX-R </td><td> ATGCCACCAAGTTGTCATCA </td></tr><tr><td> mOligo1-L </td><td> CTTGCTCTCTCCAGCCAAAC </td></tr><tr><td> mOligo1-R </td><td> GCGAGCCTGAAAAACAGAAC </td></tr><tr><td> mGFAP-L </td><td> CACGAACGAGTCCCTAGAGC </td></tr><tr><td> mGFAP-R </td><td> ATGGTGATGCGGTTTTCTTC </td></tr></tbody></table>ontent"&gt; 表1 PCR引物列表。

Watch this Scientific Journal Video about Electrospun Fibrous Scaffolds of Polyglycerol-dodecanedioate for Engineering Neural Tissues From Mouse Embryonic Stem Cells at JoVE.com

Electrospun Fibrous Scaffolds of Polyglycerol-dodecanedioate for Engineering Neural Tissues From Mouse Embryonic Stem Cells

静电合成长纤维经过了全新设计的收集器从名为聚（甘油 - 十二烷酸）一种新型的可生物降解聚合物跨越一个较大的矿床区（PGD），并制作报告。该纤维为能够支持从小鼠多能干细胞衍生的细胞的生长。

保利的静电纤维支架（甘油 - 十二双）工程神经组织从小鼠胚胎干细胞

For tissue engineering applications, the preparation of biodegradable and biocompatible scaffolds is the most desirable but challenging task. &#160;Among ...

electrospun-fibrous-scaffolds-poly-glycerol-dodecanedioate-for

Nanyang Technological University

Research

JoVE Journal

Bioengineering

Electrospun Fibrous Scaffolds of Poly(glycerol-dodecanedioate) for Engineering Neural Tissues From Mouse Embryonic Stem Cells

10.8K 次观看.  Florida International University. 静电合成长纤维经过了全新设计的收集器从名为聚（甘油 - 十二烷酸）一种新型的可生物降解聚合物跨越一个较大的矿床区（PGD），并制作报告。该纤维为能够支持从小鼠多能干细胞衍生的细胞的生长。 

视频: Electrospun Fibrous Scaffolds of Polyglycerol-dodecanedioate for Engineering Neural Tissues From Mouse Embryonic Stem Cells

Elastomeric PGS Scaffolds in Arterial Tissue Engineering

Cardiovascular disease is one of the leading cause of mortality in the US and especially, coronary artery disease increases with an aging population and increasing obesity1. Currently, bypass surgery using autologous vessels, allografts, and synthetic grafts are known as a commonly used for arterial substitutes2. However, these grafts have limited applications when an inner diameter of arteries is less than 6 mm due to low availability, thrombotic complications, compliance mismatch, and late intimal hyperplasia3,4. To overcome these limitations, tissue engineering has been successfully applied as a promising alternative to develop small-diameter arterial constructs that are nonthrombogenic, robust, and compliant. Several previous studies have developed small-diameter arterial constructs with tri-lamellar structure, excellent mechanical properties and burst pressure comparable to native arteries5,6. While high tensile strength and burst pressure by increasing collagen production from a rigid material or cell sheet scaffold, these constructs still had low elastin production and compliance, which is a major problem to cause graft failure after implantation. Considering these issues, we hypothesized that an elastometric biomaterial combined with mechanical conditioning would provide elasticity and conduct mechanical signals more efficiently to vascular cells, which increase extracellular matrix production and support cellular orientation.
The objective of this report is to introduce a fabrication technique of porous tubular scaffolds and a dynamic mechanical conditioning for applying them to arterial tissue engineering. We used a biodegradable elastomer, poly (glycerol sebacate) (PGS)7 for fabricating porous tubular scaffolds from the salt fusion method. Adult primary baboon smooth muscle cells (SMCs) were seeded on the lumen of scaffolds, which cultured in our designed pulsatile flow bioreactor for 3 weeks. PGS scaffolds had consistent thickness and randomly distributed macro- and micro-pores. Mechanical conditioning from pulsatile flow bioreactor supported SMC orientation and enhanced ECM production in scaffolds. These results suggest that elastomeric scaffolds and mechanical conditioning of bioreactor culture may be a promising method for arterial tissue engineering.

Elastomeric PGS scaffolds with vascular smooth muscle cells cultured in a pulsatile flow bioreactor may lead to promising small-diameter arterial constructs with native ECM production in a relatively short culture period.

弹性PGS的动脉组织工程支架

Cardiovascular disease is one of the leading cause of mortality in the US and especially, coronary artery disease increases with an aging population and ...

科研

生物工程

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.

制备纤维蛋白三维支架干细胞培养应用

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 ...

Postproduction Processing of Electrospun Fibres for Tissue Engineering

Electrospinning is a commonly used and versatile method to produce scaffolds (often biodegradable) for 3D tissue engineering.1, 2, 3 Many tissues in vivo undergo biaxial distension to varying extents such as skin, bladder, pelvic floor and even the hard palate as children grow. In producing scaffolds for these purposes there is a need to develop scaffolds of appropriate biomechanical properties (whether achieved without or with cells) and which are sterile for clinical use. The focus of this paper is not how to establish basic electrospinning parameters (as there is extensive literature on electrospinning) but on how to modify spun scaffolds post production to make them fit for tissue engineering purposes - here thickness, mechanical properties and sterilisation (required for clinical use) are considered and we also describe how cells can be cultured on scaffolds and subjected to biaxial strain to condition them for specific applications.
Electrospinning tends to produce thin sheets; as the electrospinning collector becomes coated with insulating fibres it becomes a poor conductor such that fibres no longer deposit on it. Hence we describe approaches to produce thicker structures by heat or vapour annealing increasing the strength of scaffolds but not necessarily the elasticity. Sequential spinning of scaffolds of different polymers to achieve complex scaffolds is also described. Sterilisation methodologies can adversely affect strength and elasticity of scaffolds. We compare three methods for their effects on the biomechanical properties on electrospun scaffolds of poly lactic-co-glycolic acid (PLGA).
Imaging of cells on scaffolds and assessment of production of extracellular matrix (ECM) proteins by cells on scaffolds is described. Culturing cells on scaffolds in vitro can improve scaffold strength and elasticity but the tissue engineering literature shows that cells often fail to produce appropriate ECM when cultured under static conditions. There are few commercial systems available that allow one to culture cells on scaffolds under dynamic conditioning regimes - one example is the Bose Electroforce 3100 which can be used to exert a conditioning programme on cells in scaffolds held using mechanical grips within a media filled chamber.4 An approach to a budget cell culture bioreactor for controlled distortion in 2 dimensions is described. We show that cells can be induced to produce elastin under these conditions. Finally assessment of the biomechanical properties of processed scaffolds cultured with or without cells is described.

Electrospun scaffolds can be processed post production for tissue engineering applications. Here we describe methods for spinning complex scaffolds (by consecutive spinning), for making thicker scaffolds (by multi-layering using heat or vapour annealing), for achieving sterility (aseptic production or sterilisation post production) and for achieving appropriate biomechanical properties.

静电纤维组织工程的后期处理

Electrospinning is a commonly used and versatile method to produce  scaffolds (often biodegradable) for 3D tissue engineering.1, 2, 3 Many tissues in vivo ...

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.

工程骨骼肌组织中的小鼠成肌细胞的内皮祖细胞与应用电刺激

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 ...

Electrospinning Growth Factor Releasing Microspheres into Fibrous Scaffolds

This procedure describes a method to fabricate a multifaceted substrate to direct nerve cell growth. This system incorporates mechanical, topographical, adhesive and chemical signals. Mechanical properties are controlled by the type of material used to fabricate the electrospun fibers. In this protocol we use 30% methacrylated Hyaluronic Acid (HA), which has a tensile modulus of ~500 Pa, to produce a soft fibrous scaffold. Electrospinning on to a rotating mandrel produces aligned fibers to create a topographical cue. Adhesion is achieved by coating the scaffold with fibronectin. The primary challenge addressed herein is providing a chemical signal throughout the depth of the scaffold for extended periods. This procedure describes fabricating&#160;poly(lactic-co-glycolic acid) (PLGA) microspheres that contain Nerve Growth Factor (NGF) and directly impregnating the scaffold with these microspheres during the electrospinning process. Due to the harsh production environment, including high sheer forces and electrical charges, protein viability is measured after production. The system provides protein release for over 60 days and has been shown to promote primary nerve cell growth.

This protocol combines electrospinning and microspheres to develop tissue engineered scaffolds to direct neurons. Nerve growth factor was encapsulated within PLGA microspheres and electrospun into Hyaluronic Acid (HA) fibrous scaffolds. The protein bioactivity was tested by seeding the scaffolds with primary chick Dorsal Root Ganglia and culturing for 4-6 days.

静电生长因子释放到微纤维支架

This procedure describes a method to fabricate a multifaceted substrate to direct nerve cell growth.  This system incorporates mechanical, topographical, ...

Electrospun Nanofiber Scaffolds with Gradations in Fiber Organization

The goal of this protocol is to report a simple method for generating nanofiber scaffolds with gradations in fiber organization and test their possible applications in controlling cell morphology/orientation. Nanofiber organization is controlled with a new fabrication apparatus that enables the gradual decrease of fiber organization in a scaffold. Changing the alignment of fibers is achieved through decreasing deposition time of random electrospun fibers on a uniaxially aligned fiber mat. By covering the collector with a moving barrier/mask, along the same axis as fiber deposition, the organizational structure is easily controlled. For tissue engineering purposes, adipose-derived stem cells can be seeded to these scaffolds. Stem cells undergo morphological changes as a result of their position on the varied organizational structure, and can potentially differentiate into different cell types depending on their locations. Additionally, the graded organization of fibers enhances the biomimicry of nanofiber scaffolds so they more closely resemble the natural orientations of collagen nanofibers at tendon-to-bone insertion site compared to traditional scaffolds. Through nanoencapsulation, the gradated fibers also afford the possibility to construct chemical gradients in fiber scaffolds, and thereby further strengthen their potential applications in fast screening of cell-materials interaction and interfacial tissue regeneration. This technique enables the production of continuous gradient scaffolds, but it also can potentially produce fibers in discrete steps by controlling the movement of the moving barrier/mask in a discrete fashion.

Here, we present a protocol to fabricate electrospun nanofiber scaffolds with gradated organization of fibers and explore their applications in regulating cell morphology/orientation. Gradients with regard to physical and chemical properties of the nanofiber scaffolds offer a wide variety of applications in the biomedical field.

静电纳米纤维支架与渐变的纤维组织

The goal of this protocol is to report a simple method for generating nanofiber scaffolds with gradations in fiber organization and test their possible ...

Generation of ESC-derived Mouse Airway Epithelial Cells Using Decellularized Lung Scaffolds

Lung lineage differentiation requires integration of complex environmental cues that include growth factor signaling, cell-cell interactions and cell-matrix interactions. Due to this complexity, recapitulation of lung development in vitro to promote differentiation of stem cells to lung epithelial cells has been challenging. In this protocol, decellularized lung scaffolds are used to mimic the 3-dimensional environment of the lung and generate stem cell-derived airway epithelial cells. Mouse embryonic stem cell are first differentiated to the endoderm lineage using an embryoid body (EB) culture method with activin A. Endoderm cells are then seeded onto decellularized scaffolds and cultured at air-liquid interface for up to 21 days. This technique promotes differentiation of seeded cells to functional airway epithelial cells (ciliated cells, club cells, and basal cells) without additional growth factor supplementation. This culture setup is defined, serum-free, inexpensive, and reproducible. Although there is limited contamination from non-lung endoderm lineages in culture, this protocol only generates airway epithelial populations and does not give rise to alveolar epithelial cells. Airway epithelia generated with this protocol can be used to study cell-matrix interactions during lung organogenesis and for disease modeling or drug-discovery platforms of airway-related pathologies such as cystic fibrosis.

This protocol efficiently directs mouse embryonic stem cell-derived definitive endoderm to mature airway epithelial cells. This differentiation technique uses 3-dimensional decellularized lung scaffolds to direct lung lineage specification, in a defined, serum-free culture setting.

用脱细胞支架龙ESC衍生鼠气道上皮细胞的生成

Lung lineage differentiation requires integration of complex environmental cues that include growth factor signaling, cell-cell interactions and ...

Microfluidic Bioprinting for Engineering Vascularized Tissues and Organoids

Engineering vascularized tissue constructs and organoids has been historically challenging. Here we describe a novel method based on microfluidic bioprinting to generate a scaffold with multilayer interlacing hydrogel microfibers. To achieve smooth bioprinting, a core-sheath microfluidic printhead containing a composite bioink formulation extruded from the core flow and the crosslinking solution carried by the sheath flow, was designed and fitted onto the bioprinter. By blending gelatin methacryloyl (GelMA) with alginate, a polysaccharide that undergoes instantaneous ionic crosslinking in the presence of select divalent ions, followed by a secondary photocrosslinking of the GelMA component to achieve permanent stabilization, a microfibrous scaffold could be obtained using this bioprinting strategy. Importantly, the endothelial cells encapsulated inside the bioprinted microfibers can form the lumen-like structures resembling the vasculature over the course of culture for 16 days. The endothelialized microfibrous scaffold may be further used as a vascular bed to construct a vascularized tissue through subsequent seeding of the secondary cell type into the interstitial space of the microfibers. Microfluidic bioprinting provides a generalized strategy in convenient engineering of vascularized tissues at high fidelity.

We provide a generalized protocol based on a microfluidic bioprinting strategy for engineering a microfibrous vascular bed, where a secondary cell type could be further seeded into the interstitial space of this microfibrous structure to generate vascularized tissues and organoids.

微流控生物工程血管化组织和细胞器解体

Engineering vascularized tissue constructs and organoids has been historically challenging. Here we describe a novel method based on microfluidic ...

Two Methods for Decellularization of Plant Tissues for Tissue Engineering Applications

The autologous, synthetic, and animal-derived grafts currently used as scaffolds for tissue replacement have limitations due to low availability, poor biocompatibility, and cost. Plant tissues have favorable characteristics that make them uniquely suited for use as scaffolds, such as high surface area, excellent water transport and retention, interconnected porosity, preexisting vascular networks, and a wide range of mechanical properties. Two successful methods of plant decellularization for tissue engineering applications are described here. The first method is based on detergent baths to remove cellular matter, which is similar to previously established methods used to clear mammalian tissues. The second is a detergent-free method adapted from a protocol that isolates leaf vasculature and involves the use of a heated bleach and salt bath to clear the leaves and stems. Both methods yield scaffolds with comparable mechanical properties and low cellular metabolic impact, thus allowing the user to select the protocol which better suits their intended application.

Here we present, and contrast two protocols used to decellularize plant tissues: a detergent-based approach and a detergent-free approach. Both methods leave behind the extracellular matrix of the plant tissues used, which can then be utilized as scaffolds for tissue engineering applications.

组织工程应用中植物组织去细胞的两种方法

The autologous, synthetic, and animal-derived grafts currently used as scaffolds for tissue replacement have limitations due to low availability, poor ...

Core/shell Printing Scaffolds For Tissue Engineering Of Tubular Structures

Three-dimensional (3D) printing of core/shell filaments allows direct fabrication of channel structures with a stable shell that is cross-linked at the interface with a liquid core. The latter is removed post-printing, leaving behind a hollow tube. Integrating an additive manufacturing technique (like the one described here with tailor-made [bio]inks, which structurally and biochemically mimic the native extracellular matrix [ECM]) is an important step towards advanced tissue engineering. However, precise fabrication of well-defined structures requires tailored fabrication strategies optimized for the material in use. Therefore, it is sensible to begin with a set-up that is customizable, simple-to-use, and compatible with a broad spectrum of materials and applications. This work presents an easy-to-manufacture core/shell nozzle with luer-compatibility to explore core/shell printing of woodpile structures, tested with a well-defined, alginate-based scaffold material formulation.

Presented here is a simple-to-use, core/shell, three-dimensional bioprinting set-up for one-step fabrication of hollow scaffolds, suitable for tissue engineering of vascular and other tubular structures.

管状结构组织工程的核心/壳印刷支架

Three-dimensional (3D) printing of core/shell filaments allows direct fabrication of channel structures with a stable shell that is cross-linked at the ...