Funding was provided in part by BU and the NIH R01CA149561. The authors wish to thank the electrospinning/electrospraying team including Stefan Yohe, Eric Falde, Joseph Hersey, and Julia Wang for their helpful discussions and contributions to the preparation and characterization of superhydrophobic biomaterials.

1.合成官能化聚（1,3-甘油碳酸盐共己内酯）29和聚（1,3-甘油碳酸盐共 -丙交酯）27,28。 <ol><li>单体合成。 <ol><li>溶解顺 -2-苯基-1,3-二恶烷-5-醇（50克，0.28摩尔，1当量）在500毫升无水四氢呋喃（THF）中并在氮气下搅拌在冰上。添加氢氧化钾（33.5克，0.84摩尔，3当量），细粉碎用研钵和研杵。将烧瓶在冰浴。 </li><li>添加49.6 ml的苄基溴（71.32克，0.42摩尔，1.5当量）逐滴搅拌在冰上。使反应温热至室温，搅拌24小时，在氮气氛下。 </li><li>增加150个ml的蒸馏水以溶解氢氧化钾和通过旋转蒸发除去THF。 </li><li>提取用200ml二氯甲烷（DCM）的其余材料的1-L分液漏斗中。重复萃取两次。 </li><li>干上硫酸钠有机相。 </li><li>结晶产物通过加入600毫升无水乙醇的溶液中，充分混合，并存储过夜，在-20℃下。该产品可以储存在-20℃下数天在进行后续步骤之前。 </li><li>通过一个布氏漏斗分离产物通过真空过滤和干燥的高真空。该产品可在执行后续步骤之前可存放数天。一个典型的产量这一步〜80％。 </li><li>在1升圆底烧瓶中，在暂停步骤1.1.7获得的产物。在甲醇（300毫升）中。加加入150ml 2N盐酸。回流下，在80℃进行2小时。 </li><li>蒸发溶剂并高真空下放置24小时。收率此步骤通常是&gt; 98％。 </li><li>溶解的1.1.9在THF产品（650毫升）中，并转移到一个2升圆底烧瓶中。将烧瓶在冰浴并在氮气中搅拌。添加22.4毫升氯甲酸乙酯（25.6克，0.29摩尔，2当量）在氮气下烧瓶中。 </li><li>添加32.8 ml的三乙胺（0.29摩尔，2当量）吨Ø滴液漏斗。混合用THF等体积。放置加料漏斗上的圆底烧瓶中，并保持在氮气下。 </li><li>在剧烈搅拌下，小心地分配三乙胺/ THF混合物逐滴向圆底烧瓶在冰上。注意:这是一个放热反应。为了防止温度急剧上升，加入三乙胺/ THF溶液不会高于每秒1滴。添加全卷后，搅拌4小时，反应，升温至室温，或24小时。 </li><li>滤除用布氏漏斗的三乙胺盐酸盐。蒸发溶剂在旋转蒸发器。 </li><li>添加二氯甲烷（200毫升）到该烧瓶中并加热，直到轻轻将残余物溶解。加入乙醚120ml的同时旋涡。储存在-20℃下过夜，以使产物结晶。 </li><li>筛选的单体晶体和聚合前再结晶。单体产品可以存储密封在室温下2周或在-206的温度下去。确认产品由1 H NMR，质谱和元素分析。一个典型的产率在单体合成最后一步是40-60％之间。 </li></ol></li><li>的D共聚，L-丙交酯/ε己内酯与5-苄氧基-1,3-二恶烷-2-酮。 <ol><li>热硅油浴中以140℃。 </li><li>测量2.1克5-苄基-1,3-二恶烷-2-酮（1.1制备）和将其添加到干燥的100毫升圆底烧瓶中。如果共聚D，L-丙交酯，测算出5.7克，并加入到烧瓶现在。添加磁性搅拌棒和密封用橡胶塞烧瓶中。 <ol><li>也测量的锡（II）乙基己酸240毫克（过量）在一个小的梨形烧瓶中。该聚合将导致20％摩尔甘油碳酸酯单体组合物。调整单体的质量来实现不同的单体组成。 </li></ol></li><li>冲洗两个烧瓶用氮上的Schlenk歧管5分钟，并添加4.24 ml的ε-caprolac在氮气基调。通过施加高真空（300毫乇）15分钟以除去痕量水抽空烧瓶&#39;气氛。 </li><li>充电瓶"的氛围，氮;重复这个循环两次。 </li><li>混合500μl的无水甲苯在氮气的锡催化剂。 </li><li>放置在140℃油浴中的烧瓶中单体和添加催化剂一旦所有固体都熔化。催化剂混合物递送的总体积应为〜100微升。保持在140℃不超过24小时，然后冷却该熔融聚合物至室温。立即或至少24小时后进行随后的步骤。 </li><li>溶解在二氯甲烷中的聚合物（50毫升）和沉淀到冷的甲醇（200ml）。弃去上清液，干燥的高真空下。后续的步骤可以立即或在任何点来执行。商店聚合物在冷冻直至进一步使用。典型的聚合收/转换之间80-95％。 </li><li>执行1H-NMR分析来确定共聚单体摩尔比。溶解聚合物在氘代氯仿（CDCL 3）中，在4.58-4.68 ppm的整合碳酸酯单体的苄基质子移;与在2.3 PPM（PCL）和次甲基峰亚甲基峰在5.2 PPM（PLGA）的比较该峰值区域。 </li></ol></li><li>聚合物改性:脱保护和嫁接。 <ol><li>在高压加氢容器溶解聚合物（〜7克）在120毫升四氢呋喃（THF）。称重并加入钯 - 碳催化剂（〜2克）。 </li><li>添加氢以使用氢化装置的容器中。氢化在50psi 4小时。注意:氢气极易燃烧。寻求熟悉此过程的人提供援助，并在执行此实验之前，请务必检查是否存在泄漏电源线。 </li><li>使用硅藻土填充床过滤掉钯炭催化剂。浓缩该聚合物至〜下旋转蒸发和PRECI50毫升pitate到冷甲醇。注意:干钯微粒能自燃。保持湿毛巾附近的激化为窒息火焰事件。加水至钯/碳的滤饼，以保持它成群并防止其点火。寻求熟悉这个程序的人提供援助。 </li><li>滗高真空下上清，干燥。通过注意峰值消失在4.65 ppm的（1 HNMR 在 CDCl 3中）确认总转化到游离的羟基。这些聚合物可立即使用或保存以备后用。产量的这一步骤是&gt; 90％。 </li><li>溶解在500ml无水二氯甲烷（DCM）中的聚合物和硬脂酸（1.5当量）。添加N，N&#39;-二环己基（DCC，2.0当量）和4-二甲氨基吡啶3薄片。在氮气下在室温搅拌24小时。 </li><li>通过一系列的重复的过滤和浓度的除去不溶N，N&#39;- dicyclohexylcarbourea。最后，集中溶液至50ml。 </li><li>沉淀聚合物成冷甲醇（〜175毫升），倒出上清液。干下高真空过夜的聚合物。随后使用这些聚合物的可在任何时间进行，但保留聚合物在冷冻长期储存。产量为这最后的修饰步骤一般在85％-90％。 </li></ol></li></ol> 2.定性合成共聚物<ol><li>称取〜10毫克聚合物（记录的实际质量），并添加铝样品盘中，然后密封密封。装载样品盘和卸载（参考）出锅倒入差示扫描量热。 </li><li>程序的升温和冷却（"热/冷/热"）循环:以10℃/分钟1）热从20℃至225℃，2）冷却至-75℃，在5℃/分钟， 3）热至225℃以10℃/分钟。 </li><li>确定熔点（T M），结晶（&lt;的EM&gt; T c）和玻璃化转变温度（T g）和融合（ΔH˚F热）从热迹线（如果适用）。 </li><li>溶解在THF中合成的各共聚物（1毫克/毫升），并通过一个0.02微米的PTFE过滤器进行过滤。注入溶液成凝胶渗透色谱系统和比较​​保留时间相对于一个范围的聚苯乙烯标准。 </li></ol>对于静电/电喷雾27,31 3.制备聚合物解决方案<ol><li>溶解聚合物（S）在10-40％（重量）在适当的溶剂中，例如氯仿/甲醇（5:1）为PCL或四氢呋喃/ N，N-二甲基甲酰胺（7:3）为PLGA，过夜。聚合物的该步骤所需的质量将取决于所期望的目的尺寸。 注意:例如，以产生大约300微米的厚度10厘米×10厘米网眼1克，通常需要。值得一提的是，材料的损耗西文，可能会发生在后续步骤中这个协议，如​​溶液转移到注射器（特别是粘性溶液）中，并从存在于可选连接管和针头壳体本身死体积，这将减少电纺丝过程的产量。这些减少产量可能导致高达20％的材料损失，并建议，以扩大1.5倍来预测这些损失，也包括那些与尝试此过程的第一次时优化静电参数相关联的损失。 <ol><li>通过改变总的聚合物浓度，以从更浓的溶液预期较大纤维控制纤维尺寸。为适度增强疏水性的，可以使用10％（以聚合物总质量计）的超疏水掺杂剂。对于极疏水性/超疏水材料，使用30-50％的掺杂剂和/或减少总的聚合物浓度（即，减小的纤维尺寸）。这些解决方案的后续工作可能会PERFORmed指第二天或之后一周内。 </li><li>对于电喷雾，准备在较低浓度（即，2-10％）在适当的溶剂如氯仿溶液。像静电纺丝，调节粒径通过改变聚合物浓度。 </li></ol></li><li>涡聚合物溶液充分混合。允许大气泡平息（5分钟）。 </li><li>负载溶液到玻璃注射器。取决于溶液的粘度，它可能是最容易取出柱塞和直接将溶液倒入注射器。一块惰性，软管可能静电纺丝设置中帮助操作性。倒置注射器通过软管/针组件取代空气。 </li></ol> 4.静电/电喷雾聚合物解决方案<ol><li>负载注射器到注射器泵中，设置总体积（例如，4.5毫升），在其中分配该溶液的速率（例如，5毫升/小时）。 </li><li>覆盖集电板与luminum箔缓解后续的拆卸和运输。固定箔沿外边缘遮蔽胶带​​。 </li><li>装上高压直流（HVDC）电源线到针尖。此针尖到收集器的距离是考虑，因为它1）影响的电场在给定电压的一个重要变量，和2）其收集期间影响纤维的溶剂和随后干燥的蒸发。 <ol><li>作为第一次尝试中，使用一个尖 - 集电极间距15厘米。注意:有高压和易燃溶剂参与静电/电喷雾。提供足够的通风外排，从不触碰注射器/针或打开机壳，直到完全确定高压直流电源是关闭的。 </li></ol></li><li>如果静电/电喷雾的大面积覆盖，打开旋转和平移收集桶。否则，继续下一步。 </li><li>启动注射泵。 </li><li>打开和调整高电压年龄源获得可接受的泰勒锥。如果该溶液在针尖下垂，提高电压。如果多个射流形成，降低电压。除了这些调整，可能有必要调整尖端 - 集电极距离如果纤维/颗粒出现湿或者如果调整电压并不能充分解决的拖动液滴在针尖。 注:有关详细的故障排除，请参阅里奇和他的同事47综合电纺丝优化过程。电喷一般会涉及到较高的电压和较低的溶液浓度比静电。 </li><li>关闭高电压源，然后注射泵和电动鼓（如果适用）。允许电纺丝外壳继续通气30分钟。 </li><li>从收集器删除网/涂料。允许痕量溶剂在通风橱中蒸发过夜。材料可在室温下保存为至少两周（PLGA）或两个个月（PCL）。步骤4.5-4.8可以以任何顺序来执行。 </li></ol> 5.表征纤维和颗粒尺寸光学显微镜和扫描电子显微镜<ol><li>光镜<ol><li>如果产生静电网，切割和安装它的薄部分在载玻片上。 </li><li>观察纤维直径，节点特性（斑点或分立），以及纤维形状（ 即 ，串珠，平，直/波状）。理想的静电纤维网眼均匀，直线或波浪，和珠免费的。 </li></ol></li><li>扫描电子显微镜（SEM） <ol><li>剪切和安装在使用导电铜带铝SEM存根网格或涂层表面。电纺纤维和电喷雾涂层也可以通过SEM观察通过预先纤维/颗粒在磁带上直接沉积。 </li><li>大衣网/涂层薄（〜4 nm）的金/钯通过溅射涂层。 </li><li>加载存根到SEM室，观察1-2千电子伏。一个250X放大倍率化提供了物质的一般地形评估，而较高的放大倍数显示其他纤维和颗粒的功能，如层次图案的极其超疏水性纤维和互联的颗粒涂层。 </li></ol></li></ol> 6.确定非润湿性能的<ol><li>推进和使用量变化的方法后退水接触角测量<ol><li>切上的接触角测角器的阶段目或涂覆的材料（如果可能的话），并代替薄（0.5厘米×5厘米）的条。 </li><li>捕捉水滴轮廓在分配它（从24 AWG注射器针头）在材料表面。 <ol><li>要做到这一点，开始用一种近似5微升下降，并与材料表面接触。继续缓慢添加量（20-25微升）和捕获液滴的图像，它表示水前进接触角。相比液滴针尖要小，和ThË毛细管长度应大于液滴，以尽量减少小滴形状的失真。 </li></ol></li><li>退出同样下降的同时，捕捉它的下降曲线。重复上几个样品的分立表面位置来报告的平均值 - 通常，10次测量都前进和后退接触角是足够这些材料来表征。 </li></ol></li><li>通过修改探测液体确定材料的临界表面张力。 <ol><li>制备在乙醇，丙二醇，或乙二醇含量不同的解决方案，因为这些混合物都已知表面张力的99-101。 <ol><li>或者，使用的溶剂具有不同表面张力，例如，水（72达因/厘米），丙三醇（64达因/厘米），二甲基亚砜（44达因/厘米），苄醇（39达因/厘米），1,4-二恶烷（33达因/厘米），1-辛醇（28达因/厘米），和丙酮（25达因/厘米）。重要的是要使用溶剂不会溶解聚合物，因为这些将混淆的结果。此外，要注意的是，除了表面张力，这些液体具有不同的粘度，这可能会影响接触角测量，是该技术的限制是重要的。 </li><li>测量这些溶液探测在材料表面的接触角。积接触角为表面张力的函数。 </li></ol></li></ol></li></ol> 7.检测网格31的散装润湿<ol><li>观察水渗透到3D网格采用微型计算机断层扫描（μCT）。 <ol><li>准备一个80毫克/毫升的溶液Ioxaglate的（一种碘造影剂）的水。 </li><li>淹没在这些解决方案网格和孵化，在37℃;使用70 KVP管电压，114微安的电流周期性地测量造影剂（水）渗透通过μCT（18微米3体素分辨率），以及一个300毫秒的积分时间。 </li><li>使用图像处理软件，测量像素INTENS性在整个网格，在那里明亮的像素代表水渗入的厚度。选择一个像素阈值（〜1500），这些高强度代表水的渗透。 </li></ol></li></ol> 8.测试网格的力学性能<ol><li>切啮合到1厘米×7厘米及地点的拉​​伸试验装置的夹具之间。测量精确的宽度，长度和厚度。 </li><li>三个样品进行延伸的斜坡测试。绘制使用这些数据来确定弹性模量，极限抗拉强度和延伸率，在断的应力 - 应变曲线。 </li></ol>

The authors declare that they have no competing financial interests.

我们的方法从生物医用高分子构建超疏水材料结合合成高分子化学与静电和电喷雾的聚合物加工技术。这些技术提供任一纤维或颗粒，分别。具体地，基于聚己内酯和聚（丙交酯共 -glycolide）超疏水性材料使用的是这种策略制备。通过改变疏水性共聚物组合物，在最终的聚合物共混物百分之共聚物，纤维/颗粒尺寸，总聚合物的重量百分比，和制造条件，所得到的静电/电喷雾材料的润湿性受...

超疏水表面通常被分类为显示出明显的水接触角大于150°的低接触角滞后。这些表面通过引入对低表面能材料的高表面粗糙度建立所得空气-液体-固体界面抵抗润湿1-6制造。根据不同的制造方法，薄或多层超疏水表面，多层超疏水基底涂层，或甚至散装超疏水结构可以制备。此永久或半永久性的防水性]是用于制备自清洁面 7，微流体装置8，防污细胞/蛋白质表面9,10，减阻表面11，和药物递送装置一个有用的性质-12- 15。最近，刺激响应超疏水性材料被描述其中非润湿湿润状态是通过化学引发，物理或环境因素（例如，光，pH，温度，超声，和施加的电势/电流）14,16-20，和这些材料都发现使用其他应用程序21-25。 第一个合成超疏水表面被处理材料的表面与methyldihalogenosilanes 26制备，并且是用于生物医学应用价值有限，所用的材料是不适合在体内使用 。在此，我们描述了从生物相容性的聚合物制备表面和体超疏水材料。我们的方法需要电纺丝或电喷雾含有可生物降解的，生物相容的脂族聚酯作为主要组分，掺杂有所述聚酯和硬脂酸改性的聚（甘油碳酸酯）27-30组成的疏水性共聚物的聚合物混合物。的制造技术提供增强的表面粗糙度和孔隙度上和fibe内RS或颗粒，分别，而采用的共聚物掺杂剂提供了一种低表面能聚合物，融合与聚酯，并且可以稳定地静电纺丝或电喷雾27,31,32。 脂族可生物降解的聚酯如聚（乳酸）（PLA），聚（乙醇酸）（PGA），聚（乳酸- 共 -glycolic乙酸）（PLGA），和聚己内酯（PCL）是在临床上批准的设备中使用的聚合物和在由于它们的非毒性，生物降解性，并且易于合成33的生物医学材料研究突出。 PGA和PLGA开张的诊所在1960年的生物可吸收缝合线和70年代初期，分别为34-37。从那时起，这些聚（羟基酸）已被加工成各种其它应用程序特定的形状因子，例如微38,39和纳米颗粒40,41，晶片/光盘42，啮合27,43，泡沫44和电影45 </sup&gt;。 脂族聚酯，以及生物医学兴趣的其它聚合物，可以静电纺丝来生产纳米或微纤维网状结构具有高的表面积和孔隙率以及拉伸强度。 表1列出了合成聚合物静电关于各种生物医学应用和它们的相应参考。静电和电喷雾的快速商用的可扩展技术。这两种类似的技术依赖于施加高电压（静电斥力）克服的聚合物溶液的表面张力/融化在注射器泵的设置，因为它是针对一种接地目标46,47。当这种技术用于与低表面能的聚合物结合（疏水性聚合物如聚（caprolactone- 共 -甘油单硬脂酸酯）），将得到的材料表现超疏水性。 为了说明这一点一般合成和材料加工方法从生物医学聚合物构建超疏水材料中，我们描述超疏水polycaprolactone-和聚（丙交酯共 -glycolide）基材料作为代表性实例的合成。各共聚物的掺杂剂的聚（caprolactone- 共 -甘油单硬脂酸酯）和聚（丙交酯共 -甘油单硬脂酸酯）被首先合成，然后混合以聚己内酯和聚（丙交酯共 -glycolide），分别和最后电纺丝或电喷雾。所得到的材料的特征在于通过SEM成像和接触角测角器，并测试其在体外和体内的生物相容性。最后，散湿通过三维超疏水网格使用造影剂增强microcomputed断层扫描进行检查。

<table border="0" cellpadding="0" cellspacing="0">
	<tbody>
		<tr>
			<td>Silicone oil</td>
			<td>Sigma-Aldrich</td>
			<td>85409</td>
			<td></td>
		</tr>
		<tr>
			<td>Cis-2-Phenyl-1,3-dioxan-5-ol</td>
			<td>Sigma-Aldrich</td>
			<td align="right">13468</td>
			<td></td>
		</tr>
		<tr>
			<td>Benzyl bromide</td>
			<td>Sigma-Aldrich</td>
			<td>B17905</td>
			<td>Toxic, lacrymator/eye irritant, use in chemical fume hood</td>
		</tr>
		<tr>
			<td>Potassium hydroxide</td>
			<td>Sigma-Aldrich</td>
			<td align="right">221473</td>
			<td>Corrosive</td>
		</tr>
		<tr>
			<td>Rotary evaporator</td>
			<td>Buchi</td>
			<td>R-124</td>
			<td></td>
		</tr>
		<tr>
			<td>High-vacuum pump</td>
			<td>Welch</td>
			<td align="right">8907</td>
			<td></td>
		</tr>
		<tr>
			<td>Nitrogen, ultra high purity</td>
			<td>Airgas</td>
			<td>NI UHP300</td>
			<td>Compressed gas</td>
		</tr>
		<tr>
			<td>Tetrahydrofuran, stabilized with BHT</td>
			<td>Pharmaco-Aaper</td>
			<td align="right">346000</td>
			<td>Flammable. Dried through column of XXX</td>
		</tr>
		<tr>
			<td>Dichloromethane</td>
			<td>Pharmaco-Aaper</td>
			<td align="right">313000</td>
			<td>Flammable, toxic.</td>
		</tr>
		<tr>
			<td>Separatory funnel (1 L)</td>
			<td>Fisher Scientific</td>
			<td>13-678-606</td>
			<td></td>
		</tr>
		<tr>
			<td>Sodium sulfate</td>
			<td>Sigma-Aldrich</td>
			<td align="right">239313</td>
			<td></td>
		</tr>
		<tr>
			<td>Ethanol, absolute</td>
			<td>Pharmaco-Aaper</td>
			<td>111USP200</td>
			<td>Flammable, toxic.</td>
		</tr>
		<tr>
			<td>Buchner funnel</td>
			<td>Fisher Scientific</td>
			<td>FB-966-F</td>
			<td></td>
		</tr>
		<tr>
			<td>Methanol</td>
			<td>Pharmaco-Aaper</td>
			<td>339000ACS</td>
			<td>Flammable, toxic.</td>
		</tr>
		<tr>
			<td>Hydrochloric acid</td>
			<td>Sigma-Aldrich</td>
			<td align="right">320331</td>
			<td>Corrosive. Diluted to 2N in distilled water.</td>
		</tr>
		<tr>
			<td>Ethyl chloroformate, 97%</td>
			<td>Sigma-Aldrich</td>
			<td align="right">185892</td>
			<td>Toxic, flammable, harmful to environment</td>
		</tr>
		<tr>
			<td>Triethylamine (anhydrous)</td>
			<td>Sigma-Aldrich</td>
			<td align="right">471283</td>
			<td>Toxic, flammable, harmful to environment</td>
		</tr>
		<tr>
			<td>Diethyl ether</td>
			<td>Pharmaco-Aaper</td>
			<td>373ANHACS</td>
			<td>Highly flammable. Purified through XXX column.</td>
		</tr>
		<tr>
			<td>3,6-Dimethyl-1,4-dioxane-2,5-dione (D,L-lactide)</td>
			<td>Sigma-Aldrich</td>
			<td align="right">303143</td>
			<td></td>
		</tr>
		<tr>
			<td>Tin (II) ethylhexanoate</td>
			<td>Sigma-Aldrich</td>
			<td>S3252</td>
			<td>Toxic.</td>
		</tr>
		<tr>
			<td>&#949;-caprolactone (97%)</td>
			<td>Sigma-Aldrich</td>
			<td align="right">704067</td>
			<td></td>
		</tr>
		<tr>
			<td>Toluene, anhydrous</td>
			<td>Sigma-Aldrich</td>
			<td align="right">244511</td>
			<td>Flammable, toxic.</td>
		</tr>
		<tr>
			<td>Glass syringe</td>
			<td>Hamilton Company</td>
			<td>1700-series</td>
			<td></td>
		</tr>
		<tr>
			<td>Deuterated chloroform</td>
			<td>Cambridge Isotopes Laboratories, Inc.</td>
			<td>DLM-29-10</td>
			<td>Toxic</td>
		</tr>
		<tr>
			<td>Nuclear magnetic resonance instrument</td>
			<td>Varian</td>
			<td>V400</td>
			<td></td>
		</tr>
		<tr>
			<td>Palladium on carbon catalyst</td>
			<td>Strem Chemicals, Inc.</td>
			<td>46-1707</td>
			<td></td>
		</tr>
		<tr>
			<td>Hydrogenator unit</td>
			<td>Parr</td>
			<td align="right">3911</td>
			<td></td>
		</tr>
		<tr>
			<td>Hydrogenator shaker vessel</td>
			<td>Parr</td>
			<td>66CA</td>
			<td></td>
		</tr>
		<tr>
			<td>Hydrogen</td>
			<td>Airgas</td>
			<td>HY HP300</td>
			<td>Highly flammable.</td>
		</tr>
		<tr>
			<td>Diatomaceous earth</td>
			<td>Sigma-Aldrich</td>
			<td align="right">22140</td>
			<td></td>
		</tr>
		<tr>
			<td>2H,2H,3H,3H-perflurononanoic acid</td>
			<td>Oakwood Products, Inc.</td>
			<td align="right">10519</td>
			<td>Toxic.</td>
		</tr>
		<tr>
			<td>Stearic acid</td>
			<td>Sigma-Aldrich</td>
			<td>S4751</td>
			<td></td>
		</tr>
		<tr>
			<td>N,N&#8217;-dicyclohexylcarbodiimide</td>
			<td>Sigma-Aldrich</td>
			<td>D80002</td>
			<td>Toxic, irritant.</td>
		</tr>
		<tr>
			<td>4-(dimethylamino) pyridine</td>
			<td>Sigma-Aldrich</td>
			<td align="right">107700</td>
			<td>Toxic.</td>
		</tr>
		<tr>
			<td>Hexanes</td>
			<td>Pharmaco-Aaper</td>
			<td>359000ACS</td>
			<td>Toxic, flammable.</td>
		</tr>
		<tr>
			<td>Gel permeation chromatography (GPC) system</td>
			<td>Rainin</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>GPC column</td>
			<td>Waters</td>
			<td>WAT044228</td>
			<td></td>
		</tr>
		<tr>
			<td>Differential scanning calorimeter</td>
			<td>TA Instruments</td>
			<td>Q100</td>
			<td></td>
		</tr>
		<tr>
			<td>Chloroform</td>
			<td>Pharmaco-Aaper</td>
			<td>309000ACS</td>
			<td>Toxic.</td>
		</tr>
		<tr>
			<td>N,N-dimethylformamide</td>
			<td>Sigma-Aldrich</td>
			<td align="right">227056</td>
			<td>Toxic, flammable.</td>
		</tr>
		<tr>
			<td>Polycaprolactone, MW 70-90 kg/mol</td>
			<td>Sigma-Aldrich</td>
			<td align="right">440744</td>
			<td></td>
		</tr>
		<tr>
			<td>Poly(lactide-co-glycolide), MW 136 kg/mol</td>
			<td>Evonik Industries</td>
			<td>LP-712</td>
			<td></td>
		</tr>
		<tr>
			<td>10-mL glass syringe</td>
			<td>Hamilton Company</td>
			<td align="right">81620</td>
			<td></td>
		</tr>
		<tr>
			<td>18 AWG blunt needle</td>
			<td>BRICO Medical Supplies</td>
			<td>BN1815</td>
			<td></td>
		</tr>
		<tr>
			<td>Electrospinner enclosure box</td>
			<td>Custom-built</td>
			<td>N/A</td>
			<td>Made of acrylic panels</td>
		</tr>
		<tr>
			<td>High voltage DC supply</td>
			<td>Glassman High Voltage, Inc.</td>
			<td>PS/EL30R01.5</td>
			<td>High voltages, electrocution hazard</td>
		</tr>
		<tr>
			<td>Linear (translating) stage</td>
			<td>Servo Systems Co.</td>
			<td>LPS-12-20-0.2</td>
			<td>Optional</td>
		</tr>
		<tr>
			<td>Programmable motor &#38; power supply</td>
			<td>Intelligent Motion Systems, Inc.</td>
			<td>MDrive23 Plus</td>
			<td>Optional</td>
		</tr>
		<tr>
			<td>24V DC motor &#38; power supply</td>
			<td>McMaster-Carr</td>
			<td>6331K32</td>
			<td>Optional</td>
		</tr>
		<tr>
			<td>Aluminum collector drum</td>
			<td>Custom-built</td>
			<td></td>
			<td>Optional</td>
		</tr>
		<tr>
			<td>Syringe pump</td>
			<td>Fisher Scientific</td>
			<td>78-0100I</td>
			<td></td>
		</tr>
		<tr>
			<td>Inverted optical microscope</td>
			<td>Olympus</td>
			<td>IX70</td>
			<td></td>
		</tr>
		<tr>
			<td>Scanning electron microscope</td>
			<td>Carl Zeiss</td>
			<td>Supra V55</td>
			<td></td>
		</tr>
		<tr>
			<td>Conductive copper tape</td>
			<td>3M</td>
			<td align="right">16072</td>
			<td></td>
		</tr>
		<tr>
			<td>Aluminum SEM stubs</td>
			<td>Electron Microscopy Sciences</td>
			<td align="right">75200</td>
			<td></td>
		</tr>
		<tr>
			<td>Contact angle goniometer</td>
			<td>Kruss</td>
			<td>DSA100</td>
			<td></td>
		</tr>
		<tr>
			<td>Propylene glycol</td>
			<td>Sigma-Aldrich</td>
			<td>W294004</td>
			<td>Toxic.</td>
		</tr>
		<tr>
			<td>Ethylene glycol</td>
			<td>Sigma-Aldrich</td>
			<td align="right">324558</td>
			<td>Toxic.</td>
		</tr>
		<tr>
			<td>Ioxaglate</td>
			<td>Guerbet</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>Fetal bovine serum</td>
			<td>American Type Culture Collection</td>
			<td>30-2020</td>
			<td></td>
		</tr>
		<tr>
			<td>Micro-computed tomography instrument</td>
			<td>Scanco</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>Image analysis software (Analyze)</td>
			<td>Mayo Clinic</td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>Tensile tester</td>
			<td>Instron</td>
			<td align="right">5848</td>
			<td></td>
		</tr>
		<tr>
			<td>Micrometer</td>
			<td>Multitoyo</td>
			<td>293-340</td>
			<td></td>
		</tr>
		<tr>
			<td>Calipers</td>
			<td>Fisher Scientific</td>
			<td>14-648-17</td>
			<td></td>
		</tr>
	</tbody>
</table>

fabricating superhydrophobic polymeric materials for biomedical applications

超疏水材料，具有表面具有永久的或亚稳的不可润湿的状态，是对于一些生物医学和工业应用的兴趣。在这里，我们描述了如何静电或电喷射含有可生物降解的，生物相容的脂肪族聚酯（ 例如 ，聚己内酯和聚（丙交酯共 -glycolide））的聚合物混合物中，作为主要组分，掺杂有所述聚酯和stearate-构成的疏水共聚物改性的聚（甘油碳酸酯）得到超疏水性生物材料。电纺丝或电喷雾的制造技术提供增强的表面粗糙度和孔隙度，并在纤维或颗粒内，分别。使用低表面能的共聚物的掺杂物，融合与聚酯，并且可以稳定地静电纺丝或电喷雾，得到这些超疏水材料。重要参数，例如纤维的大小，共聚物组合物的掺杂剂和/或共ncentration，以及它们对润湿性的影响进行了讨论。高分子化学和工艺工程的这种组合提供了一个通用方法使用可扩展的技术，这些都可能推广到用于各种应用更广类聚合物来开发应用程序特定的材料。

通过一系列的化学转化的，官能碳酸酯单体5-苄基-1,3-二恶烷-2-酮合成，为白色结晶固体（ 图1A）。1 H NMR确认结构（图1B）和质谱法和元素分析证实了组合物。此固体然后共聚任一D，L-丙交酯或使用锡催化开环在140℃下反应ε己内酯。经沉淀提纯后，将聚合物组合物是使用1 H NMR分析通过积分苄质子化学位移在4.58-4.68 ppm或己内酯或丙交酯的次?...

Watch this Scientific Journal Video about Fabricating Superhydrophobic Polymeric Materials for Biomedical Applications at JoVE.com

Fabricating Superhydrophobic Polymeric Materials for Biomedical Applications

Two- and three-dimensional superhydrophobic polymeric materials are prepared by electrospinning or electrospraying biodegradable polymers blended with a lower surface energy polymer of similar composition.

制造超疏水高分子材料生物医学应用

Superhydrophobic materials, with surfaces possessing permanent or metastable non-wetted states, are of interest for a number of biomedical and industrial ...

fabricating-superhydrophobic-polymeric-materials-for-biomedical

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Organic Chemistry

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Synthetic Polymers

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19.0K 次观看.  Boston University. Two- and three-dimensional superhydrophobic polymeric materials are prepared by electrospinning or electrospraying biodegradable polymers blended with a lower surface energy polymer of similar composition. 

视频: Fabricating Superhydrophobic Polymeric Materials for Biomedical Applications

Graphene Coatings for Biomedical Implants

Atomically smooth graphene as a surface coating has potential to improve implant properties. This demonstrates a method for coating nitinol alloys with nanometer thick layers of graphene for applications as a stent material. Graphene was grown on copper substrates via chemical vapor deposition and then transferred onto nitinol substrates. In order to understand how the graphene coating could change biological response, cell viability of rat aortic endothelial cells and rat aortic smooth muscle cells was investigated. Moreover, the effect of graphene-coatings on cell adhesion and morphology was examined with fluorescent confocal microscopy. Cells were stained for actin and nuclei, and there were noticeable differences between pristine nitinol samples compared to graphene-coated samples. Total actin expression from rat aortic smooth muscle cells was found using western blot. Protein adsorption characteristics, an indicator for potential thrombogenicity, were determined for serum albumin and fibrinogen with gel electrophoresis. Moreover, the transfer of charge from fibrinogen to substrate was deduced using Raman spectroscopy. It was found that graphene coating on nitinol substrates met the functional requirements for a stent material and improved the biological response compared to uncoated nitinol. Thus, graphene-coated nitinol is a viable candidate for a stent material.

Graphene offers potential as a coating material for biomedical implants. In this study we demonstrate a method for coating nitinol alloys with nanometer thick layers of graphene and determine how graphene may influence implant response.

生物医学植入物的石墨涂料

Atomically smooth graphene as a surface coating has potential to improve implant properties. This demonstrates a method for coating nitinol alloys with ...

科研

生物工程

Designing Silk-silk Protein Alloy Materials for Biomedical Applications

Fibrous proteins display different sequences and structures that have been used for various applications in biomedical fields such as biosensors, nanomedicine, tissue regeneration, and drug delivery. Designing materials based on the molecular-scale interactions between these proteins will help generate new multifunctional protein alloy biomaterials with tunable properties. Such alloy material systems also provide advantages in comparison to traditional synthetic polymers due to the materials biodegradability, biocompatibility, and tenability in the body. This article used the protein blends of wild tussah silk (Antheraea pernyi) and domestic mulberry silk (Bombyx mori) as an example to provide useful protocols regarding these topics, including how to predict protein-protein interactions by computational methods, how to produce protein alloy solutions, how to verify alloy systems by thermal analysis, and how to fabricate variable alloy materials including optical materials with diffraction gratings, electric materials with circuits coatings, and pharmaceutical materials for drug release and delivery. These methods can provide important information for designing the next generation multifunctional biomaterials based on different protein alloys.

Blending is an efficient approach to generate biomaterials with a broad range of properties and combined features. By predicting the molecular interactions between different natural silk proteins, new silk-silk protein alloy platforms with tunable mechanical resiliency, electrical response, optical transparency, chemical processability, biodegradability, or thermal stability can be designed.

设计丝绸蚕丝蛋白合金生物医用材料

Fibrous proteins display different sequences and structures that have been used for various applications in biomedical fields such as biosensors, ...

Fabrication of Mechanically Tunable and Bioactive Metal Scaffolds for Biomedical Applications

Biometal systems have been widely used for biomedical applications, in particular, as load-bearing materials. However, major challenges are high stiffness and low bioactivity of metals. In this study, we have developed a new method towards fabricating a new type of bioactive and mechanically reliable porous metal scaffolds-densified porous Ti scaffolds. The method consists of two fabrication processes, 1) the fabrication of porous Ti scaffolds by dynamic freeze casting, and 2) coating and densification of the porous scaffolds. The dynamic freeze casting method to fabricate porous Ti scaffolds allowed the densification of porous scaffolds by minimizing the chemical contamination and structural defects. The densification process is distinctive for three reasons. First, the densification process is simple, because it requires a control of only one parameter (degree of densification). Second, it is effective, as it achieves mechanical enhancement and sustainable release of biomolecules from porous scaffolds. Third, it has broad applications, as it is also applicable to the fabrication of functionally graded porous scaffolds by spatially varied strain during densification.

Bioactive and mechanically reliable metal scaffolds have been fabricated through a method which consists of two processes, dynamic freeze casting for the fabrication of porous Ti, and coating and densification of the Ti scaffolds. The densification process is simple, effective and applicable to the fabrication of functionally graded scaffolds.

加工机械可调和生物活性金属支架的生物医学应用

Biometal systems have been widely used for biomedical applications, in particular, as load-bearing materials. However, major challenges are high stiffness ...

Fabricating Cotton Analytical Devices

A robust, low-cost analytical device should be user-friendly, rapid, and affordable. Such devices should also be able to operate with scarce samples and provide information for follow-up treatment. Here, we demonstrate the development of a cotton-based urinalysis (i.e., nitrite, total protein, and urobilinogen assays) analytical device that employs a lateral flow-based format, and is inexpensive, easily fabricated, rapid, and can be used to conduct multiple tests without cross-contamination worries. Cotton is composed of cellulose fibers with natural absorptive properties that can be leveraged for flow-based analysis. The simple but elegant fabrication process of our cotton-based analytical device is described in this study. The arrangement of the cotton structure and test pad takes advantage of the hydrophobicity and absorptive strength of each material. Because of these physical characteristics, colorimetric results can persistently adhere to the test pad. This device enables physicians to receive clinical information in a timely manner and shows great potential as a tool for early intervention.

To investigate simple fabrication approaches for multiple assay needs, we created a fluid-absorbing channel system made of cotton material. This device was used to establish a multiple detection platform, and solve contamination issues that commonly affect lateral flow-based biomedical devices, for clinical urinalysis of nitrite, total protein, and urobilinogen.

制造棉分析仪器

A robust, low-cost analytical device should be user-friendly, rapid, and affordable. Such devices should also be able to operate with scarce samples and ...

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

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

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

RGD功能化水凝胶作为治疗应用的工具合成

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

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

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

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

用于细胞培养应用光介导的形成和构图的水凝胶

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

Extraction of Plant-based Capsules for Microencapsulation Applications

Microcapsules derived from plant-based spores or pollen provide a robust platform for a diverse range of microencapsulation applications. Sporopollenin exine capsules (SECs) are obtained when spores or pollen are processed so as to remove the internal sporoplasmic contents. The resulting hollow microcapsules exhibit a high degree of micromeritic uniformity and retain intricate microstructural features related to the particular plant species. Herein, we demonstrate a streamlined process for the production of SECs from Lycopodium clavatum spores and for the loading of hydrophilic compounds into these SECs. The current SEC isolation procedure has been recently optimized to significantly reduce the processing requirements which are conventionally used in SEC isolation, and to ensure the production of intact microcapsules. Natural L. clavatum spores are defatted with acetone, treated with phosphoric acid, and extensively washed to remove sporoplasmic contents. After acetone defatting, a single processing step using 85% phosphoric acid has been shown to remove all sporoplasmic contents. By limiting the acid processing time to 30 hr, it is possible to isolate clean SECs and avoid SEC fracturing, which has been shown to occur with prolonged processing time. Extensive washing with water, dilute acids, dilute bases, and solvents ensures that all sporoplasmic material and chemical residues are adequately removed. The vacuum loading technique is utilized to load a model protein (Bovine Serum Albumin) as a representative hydrophilic compound. Vacuum loading provides a simple technique to load various compounds without the need for harsh solvents or undesirable chemicals which are often required in other microencapsulation protocols. Based on these isolation and loading protocols, SECs provide a promising material for use in a diverse range of microencapsulation applications, such as, therapeutics, foods, cosmetics, and personal care products.

This protocol/manuscript describes a streamlined process for the production of sporopollenin exine capsules (SECs) from Lycopodium clavatum spores and for the loading of hydrophilic compounds into these SECs.

基于植物的提取胶囊微胶囊化应用

Microcapsules derived from plant-based spores or pollen provide a robust platform for a diverse range of microencapsulation applications. Sporopollenin ...

Rapid Mix Preparation of Bioinspired Nanoscale Hydroxyapatite for Biomedical Applications

Hydroxyapatite (HA) has been widely used as a medical ceramic due to its good biocompatibility and osteoconductivity. Recently there has been interest regarding the use of bioinspired nanoscale hydroxyapatite (nHA). However, biological apatite is known to be calcium-deficient and carbonate-substituted with a nanoscale platelet-like morphology. Bioinspired nHA has the potential to stimulate optimal bone tissue regeneration due to its similarity to bone and tooth enamel mineral. Many of the methods currently used to fabricate nHA both in the laboratory and commercially, involve lengthy processes and complex equipment. Therefore, the aim of this study was to develop a rapid and reliable method to prepare high quality bioinspired nHA. The rapid mixing method developed was based upon an acid-base reaction involving calcium hydroxide and phosphoric acid. Briefly, a phosphoric acid solution was poured into a calcium hydroxide solution followed by stirring, washing and drying stages. Part of the batch was sintered at 1,000 &#176;C for 2 h in order to investigate the products&#39; high temperature stability. X-ray diffraction analysis showed the successful formation of HA, which showed thermal decomposition to &#946;-tricalcium phosphate after high temperature processing, which is typical for calcium-deficient HA. Fourier transform infrared spectroscopy showed the presence of carbonate groups in the precipitated product. The nHA particles had a low aspect ratio with approximate dimensions of 50 x 30 nm, close to the dimensions of biological apatite. The material was also calcium deficient with a Ca:P molar ratio of 1.63, which like biological apatite is lower than the stoichiometric HA ratio of 1.67. This new method is therefore a reliable and far more convenient process for the manufacture of bioinspired nHA, overcoming the need for lengthy titrations and complex equipment. The resulting bioinspired HA product is suitable for use in a wide variety of medical and consumer health applications.

This paper describes a novel method for the rapid manufacture of high quality bioinspired nanoscale hydroxyapatite. This biomaterial is of great significance in the manufacture of a wide range of innovative medical devices for clinical applications in orthopedics, craniofacial surgery and dentistry.

仿生纳米羟基磷灰石的快速混合制备生物医学应用

Hydroxyapatite (HA) has been widely used as a medical ceramic due to its good biocompatibility and osteoconductivity. Recently there has been interest ...

Melt Electrospinning Writing of Three-dimensional Poly(&#949;-caprolactone) Scaffolds with Controllable Morphologies for Tissue Engineering Applications

This tutorial reflects on the fundamental principles and guidelines for electrospinning writing with polymer melts, an additive manufacturing technology with great potential for biomedical applications. The technique facilitates the direct deposition of biocompatible polymer fibers to fabricate well-ordered scaffolds in the sub-micron to micro scale range. The establishment of a stable, viscoelastic, polymer jet between a spinneret and a collector is achieved using an applied voltage and can be direct-written. A significant benefit of a typical porous scaffold is a high surface-to-volume ratio which provides increased effective adhesion sites for cell attachment and growth. Controlling the printing process by fine-tuning the system parameters enables high reproducibility in the quality of the printed scaffolds. It also provides a flexible manufacturing platform for users to tailor the morphological structures of the scaffolds to their specific requirements. For this purpose, we present a protocol to obtain different fiber diameters using melt electrospinning writing (MEW) with a guided amendment of the parameters, including flow rate, voltage and collection speed. Furthermore, we demonstrate how to optimize the jet, discuss often experienced technical challenges, explain troubleshooting techniques and showcase a wide range of printable scaffold architectures.

This protocol serves as a comprehensive guideline to fabricate scaffolds via electrospinning with polymer melts in a direct writing mode. We systematically outline the process and define the appropriate parameter settings for achieving targeted scaffold architectures.

用于组织工程应用的三维聚 (ε-内) 支架的熔体静电纺丝

This tutorial reflects on the fundamental principles and guidelines for electrospinning writing with polymer melts, an additive manufacturing technology ...

Three-dimensional Printing of Thermoplastic Materials to Create Automated Syringe Pumps with Feedback Control for Microfluidic Applications

Microfluidics has become a critical tool in research across the biological, chemical, and physical sciences. One important component of microfluidic experimentation is a stable fluid handling system capable of accurately providing an inlet flow rate or inlet pressure. Here, we have developed a syringe pump system capable of controlling and regulating the inlet fluid pressure delivered to a microfluidic device. This system was designed using low-cost materials and additive manufacturing principles, leveraging three-dimensional (3D) printing of thermoplastic materials and off-the-shelf components whenever possible. This system is composed of three main components: a syringe pump, a pressure transducer, and a programmable microcontroller. Within this paper, we detail a set of protocols for fabricating, assembling, and programming this syringe pump system. Furthermore, we have included representative results that demonstrate high-fidelity, feedback control of inlet pressure using this system. We expect this protocol will allow researchers to fabricate low-cost syringe pump systems, lowering the entry barrier for the use of microfluidics in biomedical, chemical, and materials research.

Here we present a protocol to construct a pressure-controlled syringe pump to be used in microfluidic applications. This syringe pump is made from an&#160;additively manufactured body, off-the-shelf hardware, and open-source electronics. The resulting system is low-cost, straightforward to build, and delivers well-regulated fluid flow to enable rapid microfluidic research.

三维热塑性材料的印刷, 以创建自动注射器泵的反馈控制微流控应用

Microfluidics has become a critical tool in research across the biological, chemical, and physical sciences. One important component of microfluidic ...