The authors would like to acknowledge the BPI PIAVE AUTONOTEX grant for the financial support.

1.图案纺织导电聚合物<ol><li>在此过程中固定在易于处理的平面表面在10cm×10cm的织物片。用于纺织，使用100％的双罗纹针织聚酯织物的厚度为300微米，针织方向拉伸能力达50％。 </li><li>为了使包含图形设计的面具，使用125微米厚的聚酰亚胺薄膜;的图案的例子在图1中示出。 <ol><li>使用激光切割器（ 例如，Protolaser S，LPKF），以图案的聚酰亚胺掩模10;电极的图案设计在图1中示出。 </li><li>涂布的PDMS制剂（10:1基固化剂的比例），使用自动带铸造工具（K控制印刷涂布机，刮刀）为200微米，在一个的湿膜厚度上的掩模（聚酰亚胺膜）的顶6米/分钟的涂布速度。使用约0.5毫升为3厘米×5厘米的掩模。执行日是通风柜下处理。 </li></ol></li><li>轻轻织物转移到涂覆PDMS-掩模。离开10分钟，在此之后，PDMS应当在织物结构被充分吸收。 </li><li>固化样品在空气烘箱中在100℃下10分钟。 </li><li>制备导电性聚合物:PEDOT:PSS分散液（80毫升），乙二醇（20毫升），4-十二烷基苯磺酸（40微升），并在通风橱3-甲基丙烯酰（1毫升）。 </li><li>刷涂布PEDOT:对纺织的游离PDMS区域的PSS溶液，直至溶液的均匀渗透被获得。重复此步骤，实现了统一的图案颜色。应用约1毫升/厘米2。 </li><li>固化在110℃的织物1小时以干燥PEDOT:PSS溶液。降低温度至60℃为将高温处理敏感，如尼龙的纺织品。 </li></ol> 2.有机器件制造注:第1节describ协议ES进行纺织品材料的选择性沉积。下面的章节将描述制造有机器件，如拉伸传感器，OECT晶体管，皮肤电极，电容式传感器所需要的额外的步骤。 <ol><li>为了制造对纺织拉伸传感器， 如图3a所示，图案的电极线，如在第1节中所述，步骤1.1-1.5。 注:图案设计的一个例子示于图3a。这种传感器的制造不需要任何额外的步骤。 </li><li>为了制造在图3b中所示的晶体管设计，图案按照第1中描述的步骤的尼龙机织色带晶体管阵列稍微修改的PDMS退火和PEDOT:PSS的固化步骤，通过在60℃固化，以避免尼龙的热降解下一个较长的时间。 </li><li>用于皮肤的电极的制造中， 如图3c所示，沉积一个PSS纺织品:在图案化PEDOT离子凝胶。 <ol><li>制备含有离子液体的离子液体的凝胶混合物，1-乙基-3-甲基咪唑乙基硫酸盐;的交联剂，聚（乙二醇）二丙烯酸酯;和光引发剂，2-羟基-2-甲基苯丙酮在0.6 / 0.35 / 0.05，分别（体积/体积）的比例。 </li><li>涂层在PEDOT:与离子液体（20微升/厘米2）的PSS电极和由滴铸步骤2.3.1（25微升/厘米2）添加离子液体的凝胶混合物。 </li><li>暴露于UV光（365纳米）以引发交联反应10-15分钟，直至凝胶固化。执行在通风柜此步骤。 UV曝光时使用紫外线防护笼。 </li></ol></li><li>用于电容传感器的制造，使用PEDOT:用绝缘材料（ 图3d）绝缘的PSS纺织品电极。 <ol><li>隔离键盘般的PEDOT:使用PDMS PSS电极;键盘设计可以在图2b &lt;可见/ STRONG&gt;。分配在织物顶部的PDMS制剂并用刮板除去多余的。 </li><li>放置织物的烘箱中在100℃下进行10分钟。执行在通风柜此步骤。 </li></ol></li></ol>

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The authors have nothing to disclose.

导电材料的图案化是在功能的电子器件的制造中的第一个步骤。这可以成为具有挑战性的，因为在制造过程中需要考虑到这样的材料的化学和物理性质，并且处理流程需要考虑的制造步骤之间的材料的交叉兼容性。在有机电子器件的微细加工，这两个方面是更加显著由于有机物的反应性高的性质。然而，今天，有机材料是可穿戴和柔性电子为其电弹性性能14,15极具吸引力。这些技术的纺织品以获得完全集成电子穿戴式的传送由它们的三维结构的限制。在微细加工中使用的常规技术被限制为只在薄SUBSTR导电油墨的喷墨或丝网印刷的阿泰和纺织品16，17，18。传统刺绣技术，其中单纤维缝入织物，仍然缺乏工业生产的可扩展性。 在有机材料的图案化的最重要的方面是，而不会干扰电性能沉积。在图1中所描述的图案化技术依赖于有机物的直接沉积，而无需满足淀积技术或工具的参数。的有机材料被配制成最好其表演，然后可以直接沉积在所选择的织物结构体。 PDMS的效用是关键，从解决方案模式上的材料纺织品。从低粘度溶液的导电材料，而不是使用膏状油墨中的应用，使得在织物结构的保形和深涂层。然而，它限制了selectivË沉积并导致图案分辨率的损失。我们已经通过创建从PDMS负图案以限制非受控导电溶液渗透入纺织克服此限制。与PDMS的战略选择是基于其粘弹性性能，这保持纺织伸缩性和灵活性。将PDMS也是疏水性的，允许在PEDOT的扩散的控制:在图案化期间的基于水的PSS溶液。我们观察到，使用该协议所制造的导电性图案中机械变形表现出良好的导电性和稳定性。这种方法允许与具有电子功能的智能组件现有服装的未来定制。然而，临界和，在某些情况下，限制了该方法的要点之一是仍在穿戴条件的有机材料的耐用性。一些方面中，例如在洗涤一后的机械应力性和行为有机纺织品进行烘干次，还是一个未知数。 绝大多数可佩戴电子设备的依赖于伸缩器件，其中创建类似弹簧的结构，以保持设备变形期间的电连接。根据纺织类型，在针织织物的纤维被组装在一个马蹄形的设计，提供了结构的机械伸缩性。用导电材料涂覆这些纺织品允许单独的纤维来充当智能服装应变和运动传感器， 如图3a所示 。此外，更复杂的设备的几何形状可以容易地图案化，不仅对针织物，而且对织造织物。在图3b中 ，我们提出了具有可变几何OECTs的阵列。在传统的光刻，大和小的特点同时制造几乎是不可能实现的，而不需要多个步骤。我们证明，我们的图案化技术是能够全国生产Ë模式与从0.5mm变化到约一百倍的分辨率。这种晶体管可直接使用在穿戴汗水传感具有可调节时间响应和检测分辨率19。 我们已经证明，PDMS还允许附加的功能层的连续沉积以选择性方式， 如图2。那么设备可以集成在纺织品，成为完全集成在可穿戴式系统。在图2a中的处理示出了皮肤的纺织品电极，其中在电极和皮肤之间的接触与离子性液体凝胶增强的制造。在皮肤电可穿戴电极从引起记录在穿用者和电极之间的电接触退化运动伪影苦。在纺织电极离子凝胶整合的可能性将打开一个包含一个有效的沟通渠道人体，这是所希望的在可穿戴的医疗设备。这种装置的一个例子可在图3c中看到。 的其它活性物质的连续沉积可导致使用堆叠几何如有机电池，电容器，太阳能电池，晶体管，或传感器设备。 图2b示出的绝缘或介电材料的沉积路径。一种可佩戴有机键盘（ 图3d）可使用该方法，其中该PDMS用于创建在电极顶部的介电层来制造。这样的装置能够电容变化的电极和手指，其可具有在可穿戴计算和人机接口可能有趣的应用之间感测的。

可穿戴电子领域是一个快速增长的市场预计将价值50十亿欧元的2025年，在目前市场的三倍。当前面临的穿戴式设备的主要挑战是，侵入式固体电子附件限制在可穿戴式系统建立了设备的使用。使用已经存在于日常生活的纺织品是避免这种限制一个非常有吸引力的，直接的方法。由于它的弹性性能，我们穿着服装的某些部分是自然与皮肤紧密接触。目前市场上可用的智能衣服的许多例子都基于轻薄，塑料显示器，键盘和嵌入纺织品的光源设备，连接与人类电子在一个时尚的方式1。在体育实践中，卫生监测依赖于纺织电极，它提供常用的胶粘剂电极和金属腕带舒适的替代品。这里，导电性纤维是有弹性的面料直接集成，以防止皮肤刺激和长期佩戴过程中其他不适。此外，纺织品提供了许多机会来整合曲率传感器捕捉运动2，剪切传感器整合为功能性机器人致动器3的发展，当然到生物传感器通过检测分析物的汗水4集成。 现代可穿戴技术依赖于具有独特性质提供电子设备基于碳的半导体材料。有机物的"软"性与人体接口比传统的固态电子提供更好的机械性能。这种机械相容性，与机械柔性基板成对的，使能在设备中使用的非平面外形如纺织品。利用有机物也是生命科学相关，由于其混合ELEctronic和离子电导率5。此外，有机半导体和光电子材料赋予了大量的各种带显示，晶体管，逻辑和电源功能6，7，8，9功能器件。在这样的有机器件的制造的主要困难是纺织品的非平面表面上的功能材料的受控沉积。传统的微细加工技术由以纺织基材的结构维度沉积过程的不相容主要限制。 在这里，我们描述一个简单且可扩展的制造协议，允许对结构化织物导电聚合物的选择性沉积。所提出的方法使得可穿戴和保形电子器件的制造。该方法是基于C的图案形成ommercially可用导电聚合物聚（3,4-乙撑）:聚（苯乙烯磺酸酯）（PEDOT:PSS）和纺织品的弹性体蜡纸材料聚二甲基硅氧烷（PDMS）。这种组合允许用于含水PEDOT的有效约束:PSS溶液，以及用于纺织品的柔软和可拉伸的特性的保留。这个简单的和可靠的制造方法铺平了道路的上直接以成本有效和工业上可伸缩的方式纺织各种电子设备的制造中的方法。

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			<td height="42" style="height:42px;width:304px;">SYLGARD 184, Silicone elastomer kit (Base and Curing agent)</td>
			<td style="width:159px;">Dow Corning</td>
			<td style="width:119px;"></td>
			<td style="width:167px;">PDMS elastomer</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;"></td>
			<td style="width:159px;"></td>
			<td style="width:119px;"></td>
			<td></td>
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			<td colspan="4" height="21" style="height:21px;width:748px;">The conducting polymer formulation</td>
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			<td height="21" style="height:21px;width:304px;">CleviosTM PH 1000 PEDOT:PSS</td>
			<td style="width:159px;">Heraeus</td>
			<td style="width:119px;"></td>
			<td>Conductive polymer</td>
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		<tr height="42">
			<td height="42" style="height:42px;width:304px;">Ethylene glycol</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">03750-250ML</td>
			<td>Solvent (EG), CAS: 107-21-1</td>
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			<td height="42" style="height:42px;width:304px;">3-methacryloxypropyltrimethoxysilane</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td>M6514</td>
			<td>Cros linker (GOPs), CAS: 2530-85-0</td>
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			<td height="42" style="height:42px;width:304px;">4-dodecylbenzenesulfonic acid</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">44198</td>
			<td>(DBSA), CAS: 121-65-3</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;"></td>
			<td style="width:159px;"></td>
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		</tr>
		<tr height="21">
			<td colspan="4" height="21" style="height:21px;width:748px;">The ionic liquid gel</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">UV lamp DFE 2340</td>
			<td style="width:159px;">C.I.F/ ATHELEC</td>
			<td style="width:119px;">DP134</td>
			<td>UV-365nm</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">1-Ethyl-3-methylimidazolium ethyl sulfate</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">51682-100G-F</td>
			<td>Ionic Liquid (IL), CAS: 342573-75-5</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">Poly(ethylene glycol) diacrylate</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">455008-100ML</td>
			<td>Mn 700, CAS: 26570-48-9</td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">2-Hydroxy-2-methylpropiophenon</td>
			<td style="width:159px;">Sigma-Aldrich</td>
			<td style="width:119px;">405655-50ML</td>
			<td>Phot Initiator (PI), CAS: 7473-98-5</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;"></td>
			<td style="width:159px;"></td>
			<td style="width:119px;"></td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;"></td>
			<td style="width:159px;"></td>
			<td style="width:119px;"></td>
			<td></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;width:304px;">The textile fabric</td>
			<td style="width:159px;">VWR</td>
			<td style="width:119px;">Spec-Wipe 7 Wipers</td>
			<td>100% interlock knit polyester fabric</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:304px;">The polyimide film</td>
			<td style="width:159px;">DuPont</td>
			<td style="width:119px;">HN100</td>
			<td>Polyimide film with 125 &#181;m thickness</td>
		</tr>
	</tbody>
</table>

a simple and scalable fabrication method for organic electronic devices on textiles

Today, wearable electronics devices combine a large variety of functional, stretchable, and flexible technologies. However, in many cases, these devices cannot be worn under everyday conditions. Therefore, textiles are commonly considered the best substrate to accommodate electronic devices in wearable use. In this paper, we describe how to selectively pattern organic electroactive materials on textiles from a solution in an easy and scalable manner. This versatile deposition technique enables the fabrication of wearable organic electronic devices on clothes.

用于施加颜色或图案，以纺织传统方法依赖于可移动的掩模层，以允许染料的选择性沉积。在图1中 ，我们表明这种办法的PEDOT的图案化的适配:对纺织品的PSS电极。作为掩蔽层中，我们使用的疏水性聚二甲基硅氧烷，其可以抑制水性PEDOT的非可控扩散:PSS溶液。而且，柔软性和针织和机织织物的伸缩性可以保存得益于PDMS的弹性和机械性能。 在图1中 ，该过程开始于从聚酰亚胺膜（步骤1）制备的图案化的主的。图案轮廓的设计是由一个激光雕刻到薄膜上。使用磁带铸造工具，与PDMS施加在此主站（步骤2），和纺织被放置在它的上面（步骤3）。 ŧ<html>他PDMS然后逐步扩散到纺织品（步骤4）。为了制止这种转移，需要一个短暂的热退火工艺来固化PDMS。与PDMS的粘度和厚度可通过使用不同量的固化剂和涂料的参数，分别控制扩散并保证主设计的完美的复制进行调整。最后，导电溶液是刷子涂在无保护纺织品和烘烤干燥（步骤5）。聚酰亚胺主然后从织物表面剥离。的制造流程的结果在图1中所示，在右侧。在这种情况下，成功地形成图案置于针织聚酯。这样的纺织图案形成分辨率是大于1毫米。但是，也可以在紧密的或编织的纺织品中获得较低的分辨率。使用这种沉积技术，导电织物的估计薄层电阻是接近230Ω/□。 _content"FO:保持-together.within页="1"&gt;上针织和机织织物的功能的电子设备的例子示于图3a和b，包括成功制备的PEDOT:上编织纺织品的PSS电极上的天然马蹄形的排列在针织纺织纤维提供可调节伸缩性到织物上。这种弹簧状针织结构的能力可导致高度敏感的应变传感器11。在纺织结构的简单变形是通过在电阻率的变化，由于导电扭转反射纤维中的螺纹。此外，通过取纺织品的吸湿容量的优点，在图3b的电极的阵列图案的纺织品以与矩形通道和不同的栅极宽度，其可以在可穿戴汗水传感被用于平面晶体管。这样的几何结构在有机电化学transisto用于该通道和栅极被分析物12的样品联用于检测RS（OECT）。 所呈现的图形化技术可以扩展到对纺织品制造复杂的有机电子器件。作为PDMS模版保持在图案形成处理后的纺织，附加层可以在PEDOT被图案:PSS涂覆的导电纺织品。在图2中，我们提出在其中离子液体凝胶溶液（ 图2a）和PDMS制剂（ 图2b）被应用于官能或隔离PEDOT的表面上的过程:PSS电极。离子凝胶在皮肤电极主要用于。在进行纺织品的离子凝胶的掺入用于制造可穿戴纺织品电极，用于电生理监测10和图3c中示出。电容式传感器作了bŸ绝缘纺织电极表面PDMS。当电极被感动了检测的电容的变化。这样的触敏装置被用来制造有机电子织物键盘13， 如图3d的值 。 <img alt="图1" src="/files/ftp_upload/55439/55439fig1.jpg" /> 图1.工艺流程说明导电聚合物纺织品上的图案。示出导电聚合物上的纺织品的图案化处理流程。第1步:面膜准备;步骤2:在聚酰亚胺图案形成掩模定义期望设计的轮廓的PDMS沉积;步骤3:通过在涂布的PDMS掩模纺织的位置转移掩模层;步骤4:转移的PDMS到大量的纺织的，步骤5:导电性聚合物溶液到未受保护纺织品的沉积。右边的图片显示的地区环境部门一道的处理流程的关键步骤LTS。 <a href="https://ecsource-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55439/55439fig1large.jpg" target="_blank">请点击此处查看该图的放大版本。</a> <img alt="图2" src="/files/ftp_upload/55439/55439fig2.jpg" /> 图2.两个制造有机器件的例子。制造有机器件的两个例子。在PEDOT 一 ）离子液体凝胶涂层:用于皮肤敏感PSS纺织电极。 PSS纺织电极触摸传感器:b）关于PEDOT绝缘层沉积。 <a href="https://ecsource-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55439/55439fig2large.jpg" target="_blank">请点击此处查看该图的放大版本。</a> <img alt="图3" src="/files/ftp_upload/55439/55439fig3.jpg" /> 图3.有机电子文本的照片ILE设备。一个）PEDOT:PSS电极的拉伸感测。 B）OECT晶体管可穿戴生物传感阵列。 三 ）圆形PEDOT:涂覆有离子液体的凝胶用于皮肤电PSS电极。 d）对于可穿戴键盘有机触摸传感器。 <a href="https://ecsource-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55439/55439fig3large.jpg" target="_blank">请点击此处查看该图的放大版本。</a>

Watch this Scientific Journal Video about A Simple and Scalable Fabrication Method for Organic Electronic Devices on Textiles at JoVE.com

A Simple and Scalable Fabrication Method for Organic Electronic Devices on Textiles

在本文中，我们提出了一个协议，以选择性地沉积在纺织品上的有机材料，允许直接集成与身打扮有机电子器件。在制造的器件可以完全集成在纺织品，尊重他们的机械外观，使感应功能。

关于纺织品有机电子设备的简单和可扩展的制作方法

Today, wearable electronics devices combine a large variety of functional, stretchable, and flexible technologies. However, in many cases, these devices ...

a-simple-scalable-fabrication-method-for-organic-electronic-devices

Nanyang Technological University

Research

JoVE Journal

Bioengineering

10.3K 次观看.  Ecole Nationale Supérieure des Mines de Saint-Étienne, CMP-EMSE, MOC. 在本文中，我们提出了一个协议，以选择性地沉积在纺织品上的有机材料，允许直接集成与身打扮有机电子器件。在制造的器件可以完全集成在纺织品，尊重他们的机械外观，使感应功能。 

视频: A Simple and Scalable Fabrication Method for Organic Electronic Devices on Textiles

Simple Microfluidic Devices for in vivo Imaging of C. elegans, Drosophila and Zebrafish

Micro fabricated fluidic devices provide an accessible micro-environment for in vivo studies on small organisms. Simple fabrication processes are available for microfluidic devices using soft lithography techniques 1-3. Microfluidic devices have been used for sub-cellular imaging 4,5, in vivo laser microsurgery 2,6 and cellular imaging 4,7. In vivo imaging requires immobilization of organisms. This has been achieved using suction 5,8, tapered channels 6,7,9, deformable membranes 2-4,10, suction with additional cooling 5, anesthetic gas 11, temperature sensitive gels 12, cyanoacrylate glue 13 and anesthetics such as levamisole 14,15. Commonly used anesthetics influence synaptic transmission 16,17 and are known to have detrimental effects on sub-cellular neuronal transport 4. In this study we demonstrate a membrane based poly-dimethyl-siloxane (PDMS) device that allows anesthetic free immobilization of intact genetic model organisms such as Caenorhabditis elegans (C. elegans), Drosophila larvae and zebrafish larvae. These model organisms are suitable for in vivo studies in microfluidic devices because of their small diameters and optically transparent or translucent bodies. Body diameters range from ~10 &mu;m to ~800 &mu;m for early larval stages of C. elegans and zebrafish larvae and require microfluidic devices of different sizes to achieve complete immobilization for high resolution time-lapse imaging. These organisms are immobilized using pressure applied by compressed nitrogen gas through a liquid column and imaged using an inverted microscope. Animals released from the trap return to normal locomotion within 10 min.
We demonstrate four applications of time-lapse imaging in C. elegans namely, imaging mitochondrial transport in neurons, pre-synaptic vesicle transport in a transport-defective mutant, glutamate receptor transport and Q neuroblast cell division. Data obtained from such movies show that microfluidic immobilization is a useful and accurate means of acquiring in vivo data of cellular and sub-cellular events when compared to anesthetized animals (Figure 1J and 3C-F 4).
Device dimensions were altered to allow time-lapse imaging of different stages of C. elegans, first instar Drosophila larvae and zebrafish larvae. Transport of vesicles marked with synaptotagmin tagged with GFP (syt.eGFP) in sensory neurons shows directed motion of synaptic vesicle markers expressed in cholinergic sensory neurons in intact first instar Drosophila larvae. A similar device has been used to carry out time-lapse imaging of heartbeat in ~30 hr post fertilization (hpf) zebrafish larvae. These data show that the simple devices we have developed can be applied to a variety of model systems to study several cell biological and developmental phenomena in vivo.

Simple Microfluidic Devices for in vivo Imaging of C. elegans, Drosophila and Zebrafish

A simple microfluidic device has been developed to perform anesthetic free in vivo imaging of C. elegans, intact Drosophila larvae and zebrafish larvae. The device utilizes a deformable PDMS membrane to immobilize these model organisms in order to perform time lapse imaging of numerous processes such as heart beat, cell division and sub-cellular neuronal transport. We demonstrate the use of this device and show examples of different types of data collected from different model systems.

简单的微流控芯片的<em在体内</em&gt;成像<em&gt; C.线虫</em&gt;<em&gt;果蝇</em&gt;和斑马鱼

Micro fabricated fluidic devices provide an accessible micro-environment for in vivo studies on small organisms. Simple fabrication processes are ...

科研

生物工程

Microfluidic Chip Fabrication and Method to Detect Influenza

Fast and effective diagnostics play an important role in controlling infectious disease by enabling effective patient management and treatment. Here, we present an integrated microfluidic thermoplastic chip with the ability to amplify influenza A virus in patient nasopharyngeal (NP) swabs and aspirates. Upon loading the patient sample, the microfluidic device sequentially carries out on-chip cell lysis, RNA purification and concentration steps within the solid phase extraction (SPE), reverse transcription (RT) and polymerase chain reaction (PCR) in RT-PCR chambers, respectively. End-point detection is performed using an off-chip Bioanalyzer (Agilent Technologies, Santa Clara, CA). For peripherals, we used a single syringe pump to drive reagent and samples, while two thin film heaters were used as the heat sources for the RT and PCR chambers. The chip is designed to be single layer and suitable for high throughput manufacturing to reduce the fabrication time and cost. The microfluidic chip provides a platform to analyze a wide variety of virus and bacteria, limited only by changes in reagent design needed to detect new pathogens of interest.

An integrated microfluidic thermoplastic chip has been developed for use as a molecular diagnostic. The chip performs nucleic acid extraction, reverse transcriptase, and PCR. Methods for fabricating and running the chip are described.

微流控芯片的制备及方法检测甲型流感

Fast  and effective diagnostics play an important role in controlling infectious  disease by enabling effective patient management and treatment. Here, we ...

Fabrication of a Functionalized Magnetic Bacterial Nanocellulose with Iron Oxide Nanoparticles

In this study, bacterial nanocellulose (BNC) produced by the bacteria Gluconacetobacter xylinus is synthesized and impregnated in situ with iron oxide nanoparticles (IONP) (Fe3O4) to yield a magnetic bacterial nanocellulose (MBNC). The synthesis of MBNC is a precise and specifically designed multi-step process. Briefly, bacterial nanocellulose (BNC) pellicles are formed from preserved G. xylinus strain according to our experimental requirements of size and morphology. A solution of iron(III) chloride hexahydrate (FeCl3&#183;6H2O) and iron(II) chloride tetrahydrate (FeCl2&#183;4H2O) with a 2:1 molar ratio is prepared and diluted in deoxygenated high purity water. A BNC pellicle is then introduced in the vessel with the reactants. This mixture is stirred and heated at 80 &#176;C in a silicon oil bath and ammonium hydroxide (14%) is then added by dropping to precipitate the ferrous ions into the BNC mesh. This last step allows forming in situ magnetite nanoparticles (Fe3O4) inside the bacterial nanocellulose mesh to confer magnetic properties to BNC pellicle. A toxicological assay was used to evaluate the biocompatibility of the BNC-IONP pellicle. Polyethylene glycol (PEG) was used to cover the IONPs in order to improve their biocompatibility. Scanning electron microscopy (SEM) images showed that the IONP were located preferentially in the fibril interlacing spaces of the BNC matrix, but some of them were also found along the BNC ribbons. Magnetic force microscope measurements performed on the MBNC detected the presence magnetic domains with high and weak intensity magnetic field, confirming the magnetic nature of the MBNC pellicle. Young&#39;s modulus values obtained in this work are also in a reasonable agreement with those reported for several blood vessels in previous studies.

Here, we present a protocol to make a bacterial nanocellulose (BNC) magnetic for applications in damaged blood vessel reconstruction. The BNC was synthesized by G. xylinus strain. On the other hand, magnetization of the BNC was realized through in situ precipitation of Fe2+ and Fe3+ ferrous ions inside the BNC mesh.

一机能磁性纳米纤维素的细菌与氧化铁纳米粒子的制备

In this study, bacterial nanocellulose (BNC) produced by the bacteria Gluconacetobacter xylinus is synthesized and impregnated in situ with iron oxide ...

Fabrication and Characterization of a Conformal Skin-like Electronic System for Quantitative, Cutaneous Wound Management

Recent advances in the development of electronic technologies and biomedical devices offer opportunities for non-invasive, quantitative assessment of cutaneous wound healing on the skin. Existing methods, however, still rely on visual inspections through various microscopic tools and devices that normally include high-cost, sophisticated systems and require well trained personnel for operation and data analysis. Here, we describe methods and protocols to fabricate a conformal, skin-like electronics system that enables conformal lamination to the skin surface near the wound tissues, which provides recording of high fidelity electrical signals such as skin temperature and thermal conductivity. The methods of device fabrication provide details of step-by-step preparation of the microelectronic system that is completely enclosed with elastomeric silicone materials to offer electrical isolation. The experimental study presents multifunctional, biocompatible, waterproof, reusable, and flexible/stretchable characteristics of the device for clinical applications. Protocols of clinical testing provide an overview and sequential process of cleaning, testing setup, system operation, and data acquisition with the skin-like electronics, gently mounted on hypersensitive, cutaneous wound and contralateral tissues on patients.

This article presents methods to fabricate and characterize a conformal, skin-like electronic system and protocols for the use in clinical applications, particularly on cutaneous wound management.

制作定量，皮肤伤口管理一个形皮肤般的电子系统与表征

Recent advances in the development of electronic technologies and biomedical devices offer opportunities for non-invasive, quantitative assessment of ...

Biomembrane Fabrication by the Solvent-assisted Lipid Bilayer (SALB) Method

In order to mimic cell membranes, the supported lipid bilayer (SLB) is an attractive platform which enables in vitro investigation of membrane-related processes while conferring biocompatibility and biofunctionality to solid substrates. The spontaneous adsorption and rupture of phospholipid vesicles is the most commonly used method to form SLBs. However, under physiological conditions, vesicle fusion (VF) is limited to only a subset of lipid compositions and solid supports. Here, we describe a one-step general procedure called the solvent-assisted lipid bilayer (SALB) formation method in order to form SLBs which does not require vesicles. The SALB method involves the deposition of lipid molecules onto a solid surface in the presence of water-miscible organic solvents (e.g., isopropanol) and subsequent solvent-exchange with aqueous buffer solution in order to trigger SLB formation. The continuous solvent exchange step enables application of the method in a flow-through configuration suitable for monitoring bilayer formation and subsequent alterations using a wide range of surface-sensitive biosensors. The SALB method can be used to fabricate SLBs on a wide range of hydrophilic solid surfaces, including those which are intractable to vesicle fusion. In addition, it enables fabrication of SLBs composed of lipid compositions which cannot be prepared using the vesicle fusion method. Herein, we compare results obtained with the SALB and conventional vesicle fusion methods on two illustrative hydrophilic surfaces, silicon dioxide and gold. To optimize the experimental conditions for preparation of high quality bilayers prepared via the SALB method, the effect of various parameters, including the type of organic solvent in the deposition step, the rate of solvent exchange, and the lipid concentration is discussed along with troubleshooting tips. Formation of supported membranes containing high fractions of cholesterol is also demonstrated with the SALB method, highlighting the technical capabilities of the SALB technique for a wide range of membrane configurations.

Biomembrane Fabrication by the Solvent-assisted Lipid Bilayer SALB Method

We present an experimental protocol to form a supported lipid bilayer on solid substrates without using lipid vesicles. We demonstrate a one-step method to form a lipid bilayer on silicon dioxide and gold as well as supported membranes with cholesterol-enriched domain for various biological applications.

生物膜制作的溶剂辅助脂质双分子层（SALB）方法

In order to mimic cell membranes, the supported lipid bilayer (SLB) is an attractive platform which enables in vitro investigation of membrane-related ...

Rod-based Fabrication of Customizable Soft Robotic Pneumatic Gripper Devices for Delicate Tissue Manipulation

Soft compliant gripping is essential in delicate surgical manipulation for minimizing the risk of tissue grip damage caused by high stress concentrations at the point of contact. It can be achieved by complementing traditional rigid grippers with soft robotic pneumatic gripper devices. This manuscript describes a rod-based approach that combined both 3D-printing and a modified soft lithography technique to fabricate the soft pneumatic gripper. In brief, the pneumatic featureless mold with chamber component is 3D-printed and the rods were used to create the pneumatic channels that connect to the chamber. This protocol eliminates the risk of channels occluding during the sealing process and the need for external air source or related control circuit. The soft gripper consists of a chamber filled with air, and one or more gripper arms with a pneumatic channel in each arm connected to the chamber. The pneumatic channel is positioned close to the outer wall to create different stiffness in the gripper arm. Upon compression of the chamber which generates pressure on the pneumatic channel, the gripper arm will bend inward to form a close grip posture because the outer wall area is more compliant. The soft gripper can be inserted into a 3D-printed handling tool with two different control modes for chamber compression: manual gripper mode with a movable piston, and robotic gripper mode with a linear actuator. The double-arm gripper with two actuatable arms was able to pick up objects of sizes up to 2 mm and yet generate lower compressive forces as compared to elastomer-coated and non-coated rigid grippers. The feasibility of having other designs, such as single-arm or hook gripper, was also demonstrated, which further highlighted the customizability of the soft gripper device, and it's potential to be used in delicate surgical manipulation to reduce the risk of tissue grip damage.

This protocol describes a rod-based approach, combining 3D-printing and soft lithography techniques for fabricating the soft gripper devices. This approach eliminates the need for an external air source by incorporating a chamber component and reduces the chance of occlusion during the sealing process, particularly for miniaturized pneumatic channels.

娇嫩的组织操纵定制的软机器人气动设备手爪基于杆制造

Soft compliant gripping is essential in delicate surgical manipulation for minimizing the risk of tissue grip damage caused by high stress concentrations ...

Wet Chemistry and Peptide Immobilization on Polytetrafluoroethylene for Improved Cell-adhesion

Endowing materials surface with cell-adhesive properties is a common strategy in biomaterial research and tissue engineering. This is particularly interesting for already approved polymers that have a long standing use in medicine because these materials are well characterized and legal issues associated with the introduction of newly synthesized polymers may be avoided. Polytetrafluoroethylene (PTFE) is one of the most frequently employed materials for the manufacturing of vascular grafts but the polymer lacks cell adhesion promoting features. Endothelialization, i.e., complete coverage of the grafts inner surface with a confluent layer of endothelial cells is regarded key to optimal performance, mainly by reducing thrombogenicity of the artificial interface.
This study investigates the growth of endothelial cells on peptide-modified PTFE and compares these results to those obtained on unmodified substrate. Coupling with the endothelial cell adhesive peptide Arg-Glu-Asp-Val (REDV) is performed via activation of the fluorin-containing polymer using the reagent sodium naphthalenide, followed by subsequent conjugation steps. Cell culture is accomplished using Human Umbilical Vein Endothelial Cells (HUVECs) and excellent cellular growth on peptide-immobilized material is demonstrated over a two-week period.

Cell-adhesiveness is key to many approaches in biomaterial research and tissue engineering. A step-by-step technique is presented using wet-chemistry for the surface modification of the important polymer PTFE with peptides.

湿化学和肽固定在聚四氟乙烯为改善细胞粘附

Endowing materials surface with cell-adhesive properties is a common strategy in biomaterial research and tissue engineering. This is particularly ...

Fabrication of Three-dimensional Paper-based Microfluidic Devices for Immunoassays

Paper wicks fluids autonomously due to capillary action. By patterning paper with hydrophobic barriers, the transport of fluids can be controlled and directed within a layer of paper. Moreover, stacking multiple layers of patterned paper creates sophisticated three-dimensional microfluidic networks that can support the development of analytical and bioanalytical assays. Paper-based microfluidic devices are inexpensive, portable, easy to use, and require no external equipment to operate. As a result, they hold great promise as a platform for point-of-care diagnostics. In order to properly evaluate the utility and analytical performance of paper-based devices, suitable methods must be developed to ensure their manufacture is reproducible and at a scale that is appropriate for laboratory settings. In this manuscript, a method to fabricate a general device architecture that can be used for paper-based immunoassays is described. We use a form of additive manufacturing (multi-layer lamination) to prepare devices that comprise multiple layers of patterned paper and patterned adhesive. In addition to demonstrating the proper use of these three-dimensional paper-based microfluidic devices with an immunoassay for human chorionic gonadotropin (hCG), errors in the manufacturing process that may result in device failures are discussed. We expect this approach to manufacturing paper-based devices will find broad utility in the development of analytical applications designed specifically for limited-resource settings.

We detail a method to fabricate three-dimensional paper-based microfluidic devices for use in the development of immunoassays. Our approach to device assembly is a type of multilayer, additive manufacturing. We demonstrate a sandwich immunoassay to provide representative results for these types of paper-based devices.

三维纸基微流体装置的制造用于免疫分析

Paper wicks fluids autonomously due to capillary action. By patterning paper with hydrophobic barriers, the transport of fluids can be controlled and ...

Microfluidic Platform with Multiplexed Electronic Detection for Spatial Tracking of Particles

Microfluidic processing of biological samples typically involves differential manipulations of suspended particles under various force fields in order to spatially fractionate the sample based on a biological property of interest. For the resultant spatial distribution to be used as the assay readout, microfluidic devices are often subjected to microscopic analysis requiring complex instrumentation with higher cost and reduced portability. To address this limitation, we have developed an integrated electronic sensing technology for multiplexed detection of particles at different locations on a microfluidic chip. Our technology, called Microfluidic CODES, combines Resistive Pulse Sensing with Code Division Multiple Access to compress 2D spatial information into a 1D electrical signal. In this paper, we present a practical demonstration of the Microfluidic CODES technology to detect and size cultured cancer cells distributed over multiple microfluidic channels. As validated by the high-speed microscopy, our technology can accurately analyze dense cell populations all electronically without the need for an external instrument. As such, the Microfluidic CODES can potentially enable low-cost integrated lab-on-a-chip devices that are well suited for the point-of-care testing of biological samples.

We demonstrate a microfluidic platform with an integrated surface electrode network that combines resistive pulse sensing (RPS) with code division multiple access (CDMA), to multiplex detection and sizing of particles in multiple microfluidic channels.

与复用电子检测的粒子的空间跟踪微流体平台

Microfluidic processing of biological samples typically involves differential manipulations of suspended particles under various force fields in order to ...

Fabrication and Validation of an Organ-on-chip System with Integrated Electrodes to Directly Quantify Transendothelial Electrical Resistance

Organs-on-chips, in vitro models involving the culture of (human) tissues inside microfluidic devices, are rapidly emerging and promise to provide useful research tools for studying human health and disease. To characterize the barrier function of cell layers cultured inside organ-on-chip devices, often transendothelial or transepithelial electrical resistance (TEER) is measured. To this end, electrodes are usually integrated into the chip by micromachining methods to provide more stable measurements than is achieved with manual insertion of electrodes into the inlets of the chip. However, these electrodes frequently hamper visual inspection of the studied cell layer or require expensive cleanroom processes for fabrication. To overcome these limitations, the device described here contains four easily integrated electrodes that are placed and fixed outside of the culture area, making visual inspection possible. Using these four electrodes the resistance of six measurement paths can be quantified, from which the TEER can be directly isolated, independent of the resistance of culture medium-filled microchannels. The blood-brain barrier was replicated in this device and its TEER was monitored to show the device applicability. This chip, the integrated electrodes and the TEER determination method are generally applicable in organs-on-chips, both to mimic other organs or to be incorporated into existing organ-on-chip systems.

This publication describes the fabrication of an organ-on-chip device with integrated electrodes for direct quantification of transendothelial electrical resistance (TEER). For validation, the blood-brain barrier was mimicked inside this microfluidic device and its barrier function was monitored. The presented methods for electrode integration and direct TEER quantification are generally applicable.

用集成电极直接量化 Transendothelial 电阻的 Organ-on-chip 系统的制作与验证

Organs-on-chips, in vitro models involving the culture of (human) tissues inside microfluidic devices, are rapidly emerging and promise to provide useful ...