我们感谢科学暑期大学生研究奖学金（SURF）学院为这个项目的财政支持。作者还感谢葛伦·尼伯，圣母大学教授，提供在本研究中使用骨样品（上面详述）。

所有人类计算机断层摄影数据集是根据批准SJRMC协议匿名。 1. CT数据采集临床前和临床样品<ol><li>进行微X射线计算机断层摄影，以产生临床前数据集。在当前情况下，使用显微CT图像骨芯样品使用以下设置:45千伏，0.4毫安，和1000周的突起。 五 </li><li>以高分辨率（125微米各向同性体素）重建原始数据。为了进一步提高分辨率，识别和重建1cm的立方体与该卷的原点（10微米各向同性体素）的中心。 </li><li>导出重构后的数据以DICOM格式进行额外的处理设置。 </li><li>可替代地，获得重建的CT数据集，如那些断腕和足在本研究中使用的，从临床的协作者（这里示出从圣约瑟地区医疗中心获取的数据）或开放源码DICO中号档案（http://www.osirix-viewer.com/datasets/）。 </li><li>将文件导入的DICOM图像处理软件和出口为解压缩DICOM文件，如果必要的。 </li></ol> 2.数据处理<ol><li>打开使用"加载DICOM"在图像处理软件的"查看"设置每个DICOM数据集（包括所有图像切片的）。 </li><li>保存每个数据集作为一个NIfTI分析，进行科学的分析建立映像格式。导入NIfTI文件转换成一个程序，在医学成像中计算已确立的使用和自动分割为表面图的生成（ 例如 ，3DSlicer）。 </li><li>上传给定NIfTI文件到表面地图生成器程序使用"添加数据"工具。 </li><li>选择与规范"创建和重命名新模式"的"灰度模型制作"工具。设置下限阈值，以约300 HU为骨的分割。 </li><li>保存灰度模式作为用于进一步的数据处理STL文件。 </li><li>导入每个表面地图到3D数据准备软件（ 例如 ，Netfabb工作室基本），并选择"修复"模式。 </li><li>使用"选择零件"和"删除"工具来删除不代表的利益结构中的所有表面。 </li><li>使用"添加三角"工具部分覆盖在表面的孔和"自动修复"脚本完全关闭剩余的差距。 </li><li>选择操作菜单中的"修复退化面孔"脚本来解决，而不表面积和"应用修复"脚本的边缘，退出与修改后的部分"修复"模式。 </li><li>使用"剪切"工具删除不需要的功能或减少模型的大小。的"X"内指定的每个切口的位置，"Y"，或"Z"平面中的上下文区域的"剪切"菜单。 </li><li>使用"执行剪切"工具，然后选择";三角测量剪切"中的设置自动关闭所有得到的孔。 </li><li>使用"选择零件"和"删除"工具，同时以删除不表示感兴趣结构的切割产生的所有表面。 注:如果表面地图要带刻度酒吧邻接，跳过下面的步骤。他们是在一个单一的STL统一后的解剖特征和比例尺将同时缩放。 </li><li>选择"缩放"选项来修改每个表面地图的尺寸​​。模型可以被扩张（骨芯）或尺寸（脚）降低，或保持在原尺寸（手腕），以适应一个8厘米的立方体或5厘米×5厘米×8厘米的长方形棱柱内。需要注意的是，在这个阶段，文件可能用于SSLE如果没有标签或比例尺期望发送。 </li></ol> 3.解剖标签<ol><li>选择CAD程序的菜单中的"新建"选项（ 例如 ，Autodesk Inventor的专业）笔o创建使用用于度量模板"标准（毫米）的.ipt"一部分的新的工作簿。 </li><li>选择"创建二维草图"选项，并选择任何平面。在工具栏的"绘图"菜单中的"文本"工具，所需的字体和大小（宋体和2.0毫米），生产类型化解剖标签。 </li><li>完成后，选择"完成绘制"工具栏的"退出​​"菜单选项。 </li><li>从选择的选项"2D文本"工具栏上的"创建"菜单中的"挤出"工具。指定一个挤出深度（2.0毫米）对称设置。 </li><li>导出文本格式的CAD标签与"保存类型" STL设置。 </li><li>打开一个新的工作簿用于生产圆柱形标签生产线。选择"文件"选项来创建一个"标准（毫米）的.ipt"部分的新度量标准模板。 </li><li>选择"创建二维草图"工具，选择任何平面。使用"中心点画圆工具栏的绘图‘菜单"中的工具’来产生一个圆，在原点的中心。 </li><li>在"约束"菜单使用"尺寸"工具设置圆（1.0毫摩尔）的直径。 </li><li>完成后，选择"完成绘制"工具栏的"退出​​"菜单选项。 </li><li>从选择的选项"2D文本"工具栏上的"创建"菜单中选择"拉伸"工具。选择挤压深度（10.00毫米）对称设置。 </li><li>导出文本标签和汽缸CAD格式与"保存类型"设置·STL。 </li></ol> 4.附件标签<ol><li>进口车型，文本标签，并且标签的圆柱形线到3D数据准备软件。 </li><li>翻译文本标签使用"移动部分"工具相关的解剖学的左侧或右侧。使用"旋转部件"工具来确定标签，使得他们面临的第ë相同的方向。 </li><li>平移和旋转使用"移动部分"和"旋转部件"工具模型中的标签，相关结构连接圆柱形标线。 </li><li>必要时，输入"修复"模式，并使用"选择三角形"和"删除所选三角"到汽缸的大小缩小到合适的长度。 </li><li>如果使用基本版本，选择所有部件，并保存为一个项目。然后重新打开在专业版这个项目。 </li><li>在专业版中，选择所有零部件和出口作为一个单一的STL。 </li></ol> 5.比例尺设计注:两种类型的比例尺都设计在CAD程序。首先是存在于图1中 ，涉及三个独立的比例尺，与刻度标记在不同的测量，躺在每个平面。第二，包括在图2， 图URE 3，＆ 图4中 ，由垂直线躺在三个轴和在角部会聚。按照步骤5.1-5.2开始设计每个比例尺。 <ol><li>通过选择"新"和"标准（毫米）的.ipt"部分创建在CAD程序中的新的工作簿。 </li><li>选择"创建二维草图"，并选择任意三个平面，开始工作。 注:与步骤5.3-5.16继续生产第一种类型的标尺。所提供的尺寸，在25个mm递增的创建与刻度标记1厘米比例尺被实现。 </li><li>使用"矩形"和"尺寸"工具来与对应于所述刻度杆（10毫米），任何合理的值（0.25mm）的长度的所需长度的宽度绘制一个矩形（10毫米×0.25毫米）。放置左下顶点上的原点所以x坐标可用于刻度线的间距。 </li><li>要创建刻度线，利用ŧ他"矩形"工具绘制一个矩形，直接比例尺以上。用"尺寸"工具约束尺寸（0.025毫米×0.432毫米）。 </li><li>使用X坐标，所以其位于在距边缘所需的距离平移新形成的矩形。这是刻度线的顶部。 </li><li>为了创建刻度标记的底部，绘制另一个矩形，具有相同的尺寸与上半部分，正下方的比例尺。使用"对齐"工具对准刻度标记的两半。 </li><li>选择在"修改"菜单中的"裁剪"工具，并选择其中的比例尺和刻度线重叠的区域。这将除去过量的线，并允许挤出时的部分被解释为单个特征。 </li><li>为刻度线的其余部分重复步骤5.4-5.7。 </li><li>完成后，选择"完成绘制"工具栏的"退出​​"菜单选项。 </li><li>选择"挤压"下的"创建"男人u和选择的比例尺。确定挤压距离和方向（0.25毫米到屏幕）。 </li><li>要为刻度线设计标签，选择"创建二维草图"，然后选择比例尺为工作平面。 </li><li>根据"绘图"菜单，选择"文本"工具，具有一定的字体和大小（宋体和0.25mm）的创建文本。翻译的文本到所需位置比例尺旁边。 </li><li>完成后，选择"完成绘制"工具栏的"退出​​"菜单选项。 </li><li>从选择的选项"2D文本"工具栏上的"创建"菜单中的"挤出"工具。指定一个挤出深度（0.25mm）的和方向（到屏幕）。 </li><li>重复步骤5.12-5.14创建的其他标签。 </li><li>在导出CAD格式完成的比例尺与"保存类型"设置·STL。 注:整理步骤5.1-5.16后，继续步骤5.17-5.31创建第二类型的比例尺。所提供的测量是用于创建一个比例尺其为2cm每个轴上和2mm厚。 </li><li>选择"矩形"工具来创建一个正方形和约束与"尺寸"工具的长度和宽度（2毫米×2mm）的。在这个步骤中选择的尺寸将确定部分的厚度。 </li><li>选择"完成绘制"返回到3D模式设置。 </li><li>在"创建"，选择"拉伸"，然后选择2D草图模式下绘制的正方形。选择所需的挤出深度和方向（20毫米到屏幕）。 </li><li>选择"创建二维草图"，并继续在同一平面上工作作为以前的草图。 </li><li>使用"矩形"和"尺寸"工具来绘制一个矩形（2毫米×18毫米）直接平方上方。匹配矩形的平方（2毫米）的长度的长度和宽度应比例尺减去WID的所需尺寸（ - 2毫米=18毫米20mm）的平方的位。按"完成绘制"完成时。 </li><li>在"创建"，选择"拉伸"，然后选择矩形。进入挤出深度，这应该是正方形（2mm）的长度，和选择的方向（到屏幕）。 </li><li>旋转部分，使它看起来像字母"L"。创建一个新的2D草图，然后选择"L"为工作平面的前面。 </li><li>在使用"矩形"工具的两个矩形的角落绘制一个正方形。约束的尺寸（2毫米×2mm）的，以便它完全适合在角落里。退出与"完成绘制"工具的草图。 </li><li>在"创建"，选择"拉伸"，并选择新创建的平方。进入挤压距离，这应该是比例尺的所需尺寸减去平方的宽度（20毫米 - 2毫米= 18毫米）。选择一个方向（从屏幕），并应用了挤压。 </li><li>要添加文本indicatin克中的标尺的尺寸，创建一个新的2D草图掉任何平面。 </li><li>在工具栏的"绘图"菜单中的"文本"工具生成的标签与所需的字体和大小（宋体和2.5毫米）。 </li><li>翻译的文本到所需位置比例尺旁边。通过选择"完成草图"退出草图模式。 </li><li>利用"挤压"工具并输入该对准与比例尺（到屏幕）标签的比例尺条（2毫米），方向的厚度相匹配的挤压距离。 </li><li>使用其他飞机为所有三个轴的标签，重复步骤5.26-5.30。 </li><li>完成后，与导出CAD格式的比例尺和与之配套的标签"保存类型"设置·STL。 </li></ol> 6.加法比例尺来解剖学模型<ol><li>打开在3D数据准备软件的解剖模型，并导入比例尺。 </li><li>使用 &#39;;将部分"和‘旋转部件’工具定位旁边的解剖模型的比例尺。 </li><li>如果比例尺的第一种类型的创建，两次输入的部分。平移和旋转各比例尺这样一个位于每个轴。 </li><li>如果使用基本版本，选择所有部件，并保存为一个项目。 </li><li>打开在专业版本的文件。选择所有零部件和出口作为一个单一的STL。 注:当表面地图和比例尺被导入到基本或专业版尺寸保持不变。之前雕刻，表面图，具有相关联的标签和比例尺一起被缩放以适合晶体内部。由于比例尺以相同的速度模型缩放，在比例尺大小的变化代表了在解剖结构尺寸的变化。 </li></ol> 7.减少的面孔<ol><li>利用"导入网格"工具来添加一个.STL文件中的3D网格处理亲公克。调整将被应用到所述表面模型和所有组件，包括文本和比例尺，因为该软件解释网格作为一个部件。 </li><li>下"过滤器"和"网格再划分，简化和重建，"选择"二次边折叠抽取"工具，以减少网格内的本脸的数目。 </li><li>下的"面的目标编号"进入面的期望数目（100,000），并选择"应用"。此操作完成以创建SSLE软件可管理的文件大小，并防止过度雕刻倍。 </li><li>出口成品产物，使用以下的STL"导出网为..."设置。 </li></ol> 8.模型雕刻在水晶注:完成STL文件被转发到一个工业合作者，其中玻璃晶体激光刻以产生所述解剖数据的物理模型。如欲查询进一步的援助，PL以便于联系这个手稿的作者产业。 <ol><li>打开STL文件转换成激光雕刻软件程序，并转换为SCAX文件。 </li><li>导入SCAX文件中的一个软件包连接到3D激光雕刻机。 </li><li>限定适合于与SCAX文件接口的晶体尺寸。 </li><li>设置激光的功率和输入电压和密度。而典型地被选择为电压和密度8.5 V和0.2，其他测量可以通过降低电压，提高密度，确保晶体不破裂或断裂来确定。 </li><li>将该文件发送到3D激光雕刻为晶体的生产。 </li></ol>

<ol>
	<li>Edelman, R., Warach, S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Magnetic+Resonance+Imaging.">Magnetic Resonance Imaging.</a> N. Engl. J. Med. 328 (10), 708-716 (1993).</li><li>Momose, A., Takeda, T., Itai, Y., Hirano, K. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Phase-contrast+X-ray+computed+tomography+for+observing+biological+soft+tissues.">Phase-contrast X-ray computed tomography for observing biological soft tissues.</a> Nat. Med. 2 (4), 473-475 (1996).</li><li>Paulus, M., Gleason, S., Kennel, S., Hunsicker, P., Johnson, D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=High+Resolution+X-ray+Computed+Tomography:+An+Emerging+Tool+for+Small+Animal+Cancer+Research.">High Resolution X-ray Computed Tomography: An Emerging Tool for Small Animal Cancer Research.</a> Neoplasia. 2 (1), 62-70 (2000).</li><li>Robb, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=3D+visualization+in+biomedical+applications.">3D visualization in biomedical applications.</a> Annu. Rev. Biomed. Eng. 1 (1), 377-399 (1999).</li><li>Hsieh, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Chapter+12,+Section+1,+Advanced+CT+Applications.">Chapter 12, Section 1, Advanced CT Applications.</a> Computed Tomography: Principles, Design, Artifacts, and Recent Advances. , (2009).</li><li>Robb, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+biomedical+imaging+resource+at+Mayo+Clinic.">The biomedical imaging resource at Mayo Clinic.</a> IEEE Trans. Med. Imaging. 20 (9), 854-867 (2001).</li><li>Davison, C., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Multimodal+Optical,+X-Ray+CT,+and+SPECT+Imaging+of+a+Mouse+Model+of+Breast+Cancer+Lung+Metastasis.">Multimodal Optical, X-Ray CT, and SPECT Imaging of a Mouse Model of Breast Cancer Lung Metastasis.</a> Curr. Mol. Med. 13 (3), 368-376 (2013).</li><li>Preece, D., Williams, S., Lam, R., Weller, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=&amp;#34;Let's+Get+Physical&amp;#34;:+Advantages+of+a+physical+model+over+3D+computer+models+and+textbooks+in+learning+imaging+anatomy.">&amp;#34;Let's Get Physical&amp;#34;: Advantages of a physical model over 3D computer models and textbooks in learning imaging anatomy.</a> Anat. Sci. Educ. 6 (4), 216-224 (2013).</li><li>Torres, K., Staskiewicz, G., Sniezynski, M., Drop, A., Maciejewski, R. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Application+of+rapid+prototyping+techniques+for+modelling+of+anatomical+structures+in+medical+training+and+education.">Application of rapid prototyping techniques for modelling of anatomical structures in medical training and education.</a> Folia Morphol. 70 (1), 1-4 (2011).</li><li>Camaros, E., Sanchez-Hernandez, C., Rivals, F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Make+it+clear:+molds,+transparent+casts+and+lightning+techniques+for+stereomicroscopic+analysis+of+taphonomic+modifications+on+bone+surfaces.">Make it clear: molds, transparent casts and lightning techniques for stereomicroscopic analysis of taphonomic modifications on bone surfaces.</a> J. Anthropol. Sci. 94, 223-230 (2016).</li><li>Rengier, F., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=3D+Printing+based+on+imaging+data:+review+of+medical+applications.">3D Printing based on imaging data: review of medical applications.</a> Int. J. Comput. Assist. Radiol. Surg. 5 (4), 335-341 (2010).</li><li>Esses, S., Berman, P., Bloom, A., Sosna, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Clinical+Applications+of+Physical+3D+Models+Derived+From+MDCT+Data+and+Created+by+Rapid+Prototyping.">Clinical Applications of Physical 3D Models Derived From MDCT Data and Created by Rapid Prototyping.</a> AJR Am. J. Roentgenol. 196 (6), W683-W688 (2011).</li><li>Canessa, E., Fonda, C., Zennaro, M. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Low-cost+3D+Printing+for+Science,+Education+and+Sustainable+Development.">Low-cost 3D Printing for Science, Education and Sustainable Development.</a> Low-Cost 3D Printing. , (2013).</li><li>Schelly, C., Anzalone, G., Wijnen, B., Pearce, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Open-source+3-D+printing+technologies+for+education:+Bringing+additive+manufacturing+to+the+classroom.">Open-source 3-D printing technologies for education: Bringing additive manufacturing to the classroom.</a> J. Vis. Lang. Comput. 28, 226-237 (2015).</li><li>Bourke, P. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Scientific+Data+Visualization+Using+Techniques+Normally+Reserved+for+more+Frivolous+Activities.">Scientific Data Visualization Using Techniques Normally Reserved for more Frivolous Activities.</a> GTSF Int. J. Comput. 4 (3), 35-41 (2015).</li><li>Evans, B. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+World+of+3D+Printers.">A World of 3D Printers.</a> Practical 3D Printers: The Science and Art of 3D Printing. , (2012).</li><li>Berman, B. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=3-D+printing:+The+new+industrial+revolution.">3-D printing: The new industrial revolution.</a> Bus. Horizons. 55, 155-162 (2012).</li><li>Macken, J., Palanos, P. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Image+Transfer+Laser+Engraving.">Image Transfer Laser Engraving.</a> United States Patent. , (1979).</li><li>. National Biomedical Imaging Archive Available from: <a target="_blank" href="https://imaging.nci.nih.gov/ncia/login.jsf">https://imaging.nci.nih.gov/ncia/login.jsf</a> (2016)</li></ol>

作者什么都没有透露。

通过生物医学成像方式获得的临床前和临床数据集已经在现代的研究和医学进步的工具。生物医学数据可视化的现有方法包括在计算机显示器和从传统的铸造或现代3D打印方法产生的物理模型。在这里，我们描述了作为替代装置，用于可视化断层生物医学数据，因为它以简单的方式产生良好限定的，标记的模型三维晶体雕刻方法。这些相对低廉的机型可广泛用作教育工具。晶体雕刻的利用率，精确地表示解剖数据使得它在临床和教育设置高电位。在一个物理的，三维格式可视化数据的能力，克服了使用平面图像或虚拟渲染9教育传统形式的限制。雕刻结构的高分辨率和附件标签具体可见的功能，方便病人或学生教育中使用这些模型。此外，这种模式提供了一个样本中识别和观察的原因和疾病状态方面的能力。例如，骨折的分类和位置，如手腕骨折在图2中所指出的，提供疾病状态和其它物理表观体征和/或症状的患者的关系的更全面的了解。 通过三维晶体雕刻，临床前和临床的CT数据集被表示为晶体内切物理结构。临床前CT数据使用一个微CT扫描仪来获取，而临床CT图像是从临床放射来源收集。在进一步处理前，临床成像数据经由成像软件转换成解压缩的DICOM文件。随后的软件程序变换重建的DICOM文件到面的地图。这些表面图和生成的解剖学标记和比例尺的修改与数据准备软件和计算机辅助设计（CAD）来完成的。完成STL文件被还原并转化为SCAX文件。晶体尺寸和激光功率被设定之后，文件被创建在晶体中的自由形式的解剖结构三维激光雕刻机读取。 上述方法可以应用于各种临床和临床前的数据集。虽然CT数据集被在这个项目中实现的，它有可能从其他成像模态获得的数据可以在晶体被可视化，包括3D超声（US），磁共振成像（MRI）和正电子发射断层扫描（PET）。此外，其他人的解剖结构和生物标本可以被成像和在该介质中表示。然而，进来预定大小和结构晶体将需要被切割或相应地缩放。明智的做法是符合日与晶体的尺寸的解剖部分电子几何形状。例如，腿部最好在装配有5厘米×5厘米×8厘米的长方形固体（ 图4），而脚适合于一个8厘米的立方体（ 图3）。变化的大小，字体，以及文本的厚度可以在CAD软件中进行。此外，最好是将标签上的一个或两个平面，以不旋转的晶体其他面时阻碍解剖结构的视图清楚地读标签。 表面图中的面的数目，这是激光雕刻到晶体的每个点的尺寸:两个附加的因素必须在执行解剖数据的SSLE时加以考虑。这些因素影响，将吸收入射光，从而潜在地增强或从给定SSLE可视化减损的点的数量和大小。首先，脸的数量，这是成正比的点在三维空间的数量，将同时影响整体的分辨率和显示模式的"亮度/对比度"。在每一个的本文所提出的实施例中，完成的STL文件减少到100000面而不将所得晶体产物的明显的降解，无论大小或放大率。整体亮度/对比度也是可以接受的使用这种方法。 100000值是安全范围使用不负担过重的软件和硬件的雕刻。然而，在某些情况下，可能需要额外的面以正确地显示给定数据集，这些文件可以被认为是实验，直到顺利完成。此外，也就是"烧"在晶体的每个点的尺寸可以经由电压进行调谐和雕刻的"密度"的输入值，以提高输出亮度对比度。在本情况下，电压的缺省值:选择0.2:8.5和密度。虽然这些值代表一个起点，他们可以在改变试验和错误的方式根据需要，以提高数据可视化。 有许多的利用3D晶体雕刻用于临床前和临床成像数据的显示的优点。晶体通常产生在30分钟内，而3D印刷结构可能需要几个小时，这取决于它们的尺寸和复杂性16，图 20，22。激光雕刻可以用于表示悬浮结构无需使用支撑，便于制造的解剖结构的复杂的或悬挂的特征，而不会降低与附加材料16的精度。与800-1,200 DPI的分辨率和小于10μm的精确度，这些模型非常类似于医疗数据24。虽然专业级3D打印机有大约600 DPI在XY一个类似的决议和1600 DPI的Z，他们是AC一般较少牧师（20-200微米）17，19，20（ 表1）。 3D水晶内雕具有很强的潜力，但在几个方面都受到限制。由于数据是刻水晶里面，用户不能与解剖部位的触觉体验。按比例的表示是难以生产作为数据通常放大或缩小，以适应晶体。此外，激光只能雕刻用最少的对比度灰度。该结构的密度也由激光的处理数据能力的限制。晶体的整体稳定性是有利的，以在数年内的潜在用途，但固体玻璃可能不承受跌落在硬表面（ 表1）。 尽管有这些限制，3D晶体雕刻保持显著值作为用于生物医学数据可视化的介质。虽然开始材料和支持需要考虑到与3D打印机，这些方面并不需要考虑激光雕刻。更复杂的部件，如人的脚，可以被表示为的结果。虽然稍微更复杂的结构的生产时间增加，不需要额外的材料和所述模型的成本保持不变。激光器的烧玻璃以点通过点的方式的能力产生高度定义了显示生物医学数据的细节，如在图2中的打破半径指出的结构。此外，内部晶体这些结构的位置使它们在户外耐损伤。不像许多三维打印平台利用固体塑料，透光性玻璃表面允许以简单的方式被可视化内部结构。一个三维水晶内雕的最有力的工具是其标注各个部分，也可以增加大小的参考比例尺能力。这个技术增加了大量的教育价值的晶体作为各级学生可以学习解剖和临床资料，生物学和医学教育两个有价值的成分相互作用，在一个模型。与各种角度以保持他们在一只手和视图结构的手掌的功能相结合，标签极大地增强了这些模型的教育价值。其结果是，3D雕刻晶体在解剖课程使用适用性广，临床实践，教育和普通教育。

像计算机断层摄影（CT）或磁共振成像（MRI）的生物医学成像模态是常规使用的具有医学，研究，和学术界非侵入性检查人体或生物对象1，2，3的内部结构。在现代医学中，这种技术能够更明智的诊断，因此，改善患者的治疗4。特别地，CT提供了用于3-D重建一个极好的机会，由于其高分辨率和各向同性体素性质（每个立方体边缘的相同长度）。 5此外，软件包可以在三维（3D），用于高阶函数等计算机辅助外科手术和虚拟内窥镜6，其使生物医学成像数据。在临床前研究，非破坏性成像提供了一个平移平台在其研究小鼠和大鼠7疾病模型。数字库，如生物数据库数字形态（http://digimorph.org），已被填充有来自不同样品或临床疾病状态导出由更广泛的科学和医学界8随时获得CT数据。 目前，生物医学成像数据已经显现在虚拟空间在计算机屏幕上，或者在手持模式的物理空间。虽然计算机软件允许用户剖析和操纵数据，物理副本是一个很好的补充与优秀的教育效益9，10。传统模型已经使用低成本铸造方法，其中基本的模具中填充树脂变硬后成为所期望的结构11产生的。铸造模型适合于廉价的大规模生产，但仅限于基本不是从患者的数据集导出的结构。在过去的五年中，人体解剖学的3D打印复制品由于高复杂性已经变得越来越普遍，很多时候患者特异性，可以生成并显示对象。这些模型是由存款液体或添加剂层熔化的塑料，并协助医生提供诊断，复杂的手术，治疗的疾病，假体的设计，和患者沟通12,13机创建。此外，内小学，中学和大学学校设置的消费级3D打印机的普及起到推动共同解剖模型的教育效果文件14，15。 总体来说，3D打印大大推进医药内的解剖模型的开发，但它也有局限性。首先，创建多由于额外的工作，往往需要以数字方式结合单独的拼在一起，其可以以其他方式散架16 -part解剖模型可能是有挑战性的。此外，许多3D印刷材料，特别是对于消费级机器的不透明度，防止了提供关于样本的骨和软组织的附加洞察内部子结构的可视化。此外，液体或熔融的塑料挤出机约束三维打印的分辨率。专业打印机挤出机的直径为大约50微米，并允许为14μm的层厚度，具有高达600点每英寸（DPI）在X的分辨率和Y轴和1600 DPI在Z轴17，18 。相比较而言，消费级3D打印机具有在直径大约为400微米，得到100μm的层厚度和分辨率大致相当于42 DPI 19的挤出机， <s向上类= "外部参照"&gt; 20。价格也从消费级的变化很大，以专业的打印机20，21。此外，材料成本高防止工业批量生产从实现规模22效益。 子表面激光雕刻（SSLE），或三维晶体雕刻，利用激光束，以形成在成千上万的X，Y小"气泡"或点以高精度，Z的刚性，高纯度内的坐标，立方体，玻璃基质23上 。每个点为20-40微米，其产生800-1,200 DPI 24之间的分辨率。此外每个点是半透明的，从而使内部子结构的可视化。多个，断开部件在相同的晶体来表示，并且不需要大的，复杂结构的附加材料。由于基质是固体，解剖标签和大小比例尺可加入，以提高内显示的成像数据的教育潜力。这里，我们提出，其中X射线计算机断层摄影（CT）数据被格式化为晶体SSLE的处理。首先，数据可以从商业临床前微型电脑系统，从放射科/清华紫光，或如国家生物医学影像存档在线储存库（来源https://imaging.nci.nih.gov/ncia/login.jsf临床扫描仪收集）25这里，我们证明用绵羊骨芯，手腕骨折，标记的脚，并标记腿晶体这种方法来说明纳入临床前和临床数据，调整解剖结构的规模和坐标的结构与晶体大小的几何形状的能力。鉴于SSLE的随和的个性，并已广泛使用的STL文件在3D打印，标记解剖晶体的制造提供了学术和教育社区内使用一个令人兴奋的，手手持可视化工具。

<table border="0" cellpadding="0" cellspacing="0" width="1388">
	<tbody>
		<tr height="21">
			<td height="21" style="height:21px;width:249px;">3D Laser Engraving Machine</td>
			<td style="width:473px;">Wuhan Synpny Laser Co., Ltd.</td>
			<td style="width:235px;">STNP-801AB4</td>
			<td style="width:431px;">3D Laser Engraver</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;width:249px;">3D Slicer</td>
			<td style="width:473px;">Slicer</td>
			<td style="width:235px;">Version 4.3.1</td>
			<td style="width:431px;">Surface Map Generator Program</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Albira micro CT</td>
			<td>Bruker Corporation</td>
			<td></td>
			<td>Alternatively, a PET/SPECT/CT scanner can be utilized</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Autodesk Inventor Professional 2013</td>
			<td>Autodesk, Inc.</td>
			<td>64bit edition, 2013 RTM, Build 138</td>
			<td>CAD program</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Clinical CT data sets</td>
			<td>Saint Joseph Regional Medical Center</td>
			<td></td>
			<td></td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">MeshLab</td>
			<td>Institute of the National Research Council of Italy (ISTI-CNR)</td>
			<td>Volume 1.3.4 BETA</td>
			<td>3D Mesh Processing Program</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Netfabb Studio Basic</td>
			<td>netfabb GmbH</td>
			<td>Version 4.9.0</td>
			<td>3D Data Prepartion Software</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">Netfabb Studio Professional</td>
			<td>netfabb GmbH</td>
			<td>Version 5.2.1 64bit</td>
			<td>3D Data Prepartion Software-Professional</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">OsiriX Lite Imaging Software</td>
			<td>Pixmeo</td>
			<td>Version 7.0.3</td>
			<td>DICOM Imaging Software</td>
		</tr>
		<tr height="21">
			<td height="21" style="height:21px;">PMOD</td>
			<td>PMOD Technologies LLC</td>
			<td>Version 3.306</td>
			<td>Image Processing Software</td>
		</tr>
	</tbody>
</table>

scaled anatomical model creation of biomedical tomographic imaging data and associated labels for subsequent sub-surface laser engraving (ssle) of glass crystals

像计算机断层摄影（CT）和磁共振生物医学成像模态（MR），用于收集患者的三维数据集提供优异的平台或在临床或临床前设置样本的解剖结构。然而，使用一个虚拟的，在屏幕上显示的限制了这些断层图像来充分传达嵌入内的解剖信息的能力。一种解决方案是对接的生物医学成像数据的3D印刷技术设置为生成物理复制品。在这里，我们详细的互补方法与手持式模型可视化断层摄影成像数据:水晶玻璃的子表面激光雕刻（SSLE）。 SSLE提供了一些独特的优势，包括:包括解剖标签，以及比例尺轻便能力;在一个介质的复杂结构的流线型多组件;在X，Y和Z平面高分辨率;和半透明壳内部解剖子结构的可视化。这里w ^Ë表明SSLE的过程与来自临床前和临床来源的CT数据集。该协议将作为一个强大的和廉价的新工具，使用它以可视化的科学家和学生复杂的解剖结构在许多教育和研究环境。

玻璃结晶的分型面的激光雕刻是形象化许多类型的生物医学断层摄影成像数据的一个深刻的装置。 图1包括临床前的CT数据，而图2， 图3，及图4说明了如何临床CT扫描也可以使用。由于尺寸之前雕刻改性，不同尺寸的结构可通过激光雕刻来表示。虽然图2举例说明了解剖结构如何被打印成比例的，大多数结构需要被放大或缩小。两种类型的比例尺可以实现测量尺寸的变化:一个跨越结构的两侧，另设有三个轴在一个角落汇聚。第一种类型是理想的扩张结构，例如骨核心，而所述第二类型是最适合于进制或降低的结构。此外，该晶体的尺寸是搭配的解剖结构的形状。其结果是，脚放置在立方体，而腿悬浮于矩形棱柱。 子表面雕刻的一个主要特点是将文本标签附加到解剖特征的能力。该技术可以应用于各种类型的成像数据的，具有取决于结构的几何形状最佳标签位置。在图2中，文本放在两个平面空间标签并避免妨碍解剖结构的图。对于图3及图4中 ，骨可以清楚地从一侧观察，以便将标签放置在一个平面上。 <img alt="图1" class="xfigimg" src="/files/ftp_upload/55340/55340fig1.jpg" /> 图1。绵羊骨芯组的临床前的CT数据，显示几乎并悬浮在3D刻晶体。成像软件被用来生成和连接比例尺到1厘米的同位素绵羊骨（左）的表面地图。结构进行了沿每个轴在尺寸的增加五倍，由比例尺所示，并且都被激光雕刻在一个8厘米见方的晶体（右）。 <a href="http://ecsource.jove.com/files/ftp_upload/55340/55340fig1large.jpg" target="_blank">请点击此处查看该图的放大版本。</a> <img alt="图2" class="xfigimg" src="/files/ftp_upload/55340/55340fig2.jpg" /> 图2.断腕解剖标记的临床CT数据，显示几乎与刻在晶体。附有虚半径的人的手腕的临床CT数据集被转换成通过计算机软件的表面地图。解剖标签和2厘米比例尺瓦特<html>使用计算机辅助设计（CAD）中产生并附着到模型（左）ERE。三维雕刻机刻在一个8厘米的立方体晶体（右）的结构。比例尺保留了它的尺寸，展示了手腕产生按比例的。 <a href="http://ecsource.jove.com/files/ftp_upload/55340/55340fig2large.jpg" target="_blank">请点击此处查看该图的放大版本。</a> <img alt="图3" class="xfigimg" src="/files/ftp_upload/55340/55340fig3.jpg" /> 图3.在解剖学标记的人脚解剖标记，虚拟显示和刻在晶体。一个人的脚的CT数据集被转换成与成像软件的灰度模式。文本和4厘米比例尺使用CAD创建并与所述表面图（左）并入。该模型是减少到一半大小和激光雕刻在一个8厘米晶体立方体（右）。<html> 55340 / 55340fig3large.jpg"目标=‘_空白’&gt;点击此处查看该图的放大版本。 <img alt="图4" class="xfigimg" src="/files/ftp_upload/55340/55340fig4.jpg" /> 图4.临床CT数据集人腿的使用计算机软件在解剖学标记和刻在晶体。软件包被用于从一个完整的人类CT扫描和第腿从所述本体的其余部分制备表面地图。解剖标签和2.5cm的比例尺设计有CAD附着（左）和结构刻在5厘米×5厘米×8cm的晶体（右）。晶体中的比例尺示出了腿在5被按比例缩小:3的比率。 <a href="http://ecsource.jove.com/files/ftp_upload/55340/55340fig4large.jpg" target="_blank">请点击此处查看该图的放大版本。</a> YS"&gt; <tbody><tr><td fo:width="1in" style="width:100px"></td><td> 3D打印 </td><td> 子表面激光雕刻（SSLE）晶体 </td></tr><tr><td rowspan="10"> 优点 </td><td>触觉体验</td><td>在自由空间结构的创建</td></tr><tr><td>全彩色模式</td><td>多部分车型的代</td></tr><tr><td>到尺度表示可能与较大的多种结构</td><td>解剖标签的附件</td></tr><tr><td>固体塑料材料耐滴</td><td>比例尺暂停模型中</td></tr><tr><td>获得的廉价消费级打印机</td><td>高分辨率和精度</td></tr><tr><td>专业级打印机高分辨率</td><td>较短的生产时间</td></tr><tr><td></td><td>易于分离解剖亚基在三维空间链接在一起</td></tr><tr><td></td><td>晶体内的结构不容易受到外界损伤</td></tr><tr><td></td><td>材料成本低</td></tr><tr><td></td><td>激光雕刻机价格适中</td></tr><tr><td rowspan="8"> 缺点 </td><td>很难在3D空间链接分离的解剖亚基</td><td>没有触觉体验</td></tr><tr><td>成本和生产时间，复杂程度而异</td><td>灰度</td></tr><tr><td>更容易产生错误</td><td>大小由晶体限于</td></tr><tr><td>后期制作洗可能是必要的</td><td>为了尺度表达困难</td></tr><tr><td>分辨率通过塑料挤出机的限制</td><td>密度激光约束</td></tr><tr><td>部分可以削掉模型的</td><td>晶体可能碎裂或下降时，打破</td></tr><tr><td>昂贵的专业级打印机</td><td></td></tr><tr><td>的材料价格相差很大</td><td></td></tr></tbody></table> 表1.优点和3D打印和SSLE生产解剖模型的优缺点。三维打印和SSLE是用于可视化的生物医学断层摄影成像数据的两个装置，并且每个具有在问候在创建数据的物理模型的数目的优势和劣势的。

Watch this Scientific Journal Video about Scaled Anatomical Model Creation of Biomedical Tomographic Imaging Data and Associated Labels for Subsequent Sub-surface Laser Engraving SSLE of Glass Crystal

Scaled Anatomical Model Creation of Biomedical Tomographic Imaging Data and Associated Labels for Subsequent Sub-surface Laser Engraving SSLE of Glass Crystals

甲方法是对晶体内表示解剖学成像数据在此描述。我们创建缩放的生物医学成像数据的三维模型水晶玻璃的在次表面激光雕刻（SSLE）使用。该工具提供了计算显示或在临床或教育环境中使用三维打印模式的有益补充。

缩放生物医学层析成像数据的解剖模型的创建和相关联的标签玻璃晶体的随后的子表面激光雕刻（SSLE）

Biomedical imaging modalities like computed tomography (CT) and magnetic resonance (MR) provide excellent platforms for collecting three-dimensional data ...

scaled-anatomical-model-creation-biomedical-tomographic-imaging-data

Research

JoVE Journal

Bioengineering

Scaled Anatomical Model Creation of Biomedical Tomographic Imaging Data and Associated Labels for Subsequent Sub-surface Laser Engraving (SSLE) of Glass Crystals

8.3K 次观看.  University of Notre Dame. 甲方法是对晶体内表示解剖学成像数据在此描述。我们创建缩放的生物医学成像数据的三维模型水晶玻璃的在次表面激光雕刻（SSLE）使用。该工具提供了计算显示或在临床或教育环境中使用三维打印模式的有益补充。 

视频: Scaled Anatomical Model Creation of Biomedical Tomographic Imaging Data and Associated Labels for Subsequent Sub-surface Laser Engraving SSLE of Glass Crystals

Plasma Lithography Surface Patterning for Creation of Cell Networks

Systematic manipulation of a cell microenvironment with micro- and nanoscale resolution is often required for deciphering various cellular and molecular phenomena. To address this requirement, we have developed a plasma lithography technique to manipulate the cellular microenvironment by creating a patterned surface with feature sizes ranging from 100 nm to millimeters. The goal of this technique is to be able to study, in a controlled way, the behaviors of individual cells as well as groups of cells and their interactions.
This plasma lithography method is based on selective modification of the surface chemistry on a substrate by means of shielding the contact of low-temperature plasma with a physical mold. This selective shielding leaves a chemical pattern which can guide cell attachment and movement. This pattern, or surface template, can then be used to create networks of cells whose structure can mimic that found in nature and produces a controllable environment for experimental investigations. The technique is well suited to studying biological phenomenon as it produces stable surface patterns on transparent polymeric substrates in a biocompatible manner. The surface patterns last for weeks to months and can thus guide interaction with cells for long time periods which facilitates the study of long-term cellular processes, such as differentiation and adaption. The modification to the surface is primarily chemical in nature and thus does not introduce topographical or physical interference for interpretation of results. It also does not involve any harsh or toxic substances to achieve patterning and is compatible for tissue culture. Furthermore, it can be applied to modify various types of polymeric substrates, which due to the ability to tune their properties are ideal for and are widely used in biological applications. The resolution achievable is also beneficial, as isolation of specific processes such as migration, adhesion, or binding allows for discrete, clear observations at the single to multicell level.
This method has been employed to form diverse networks of different cell types for investigations involving migration, signaling, tissue formation, and the behavior and interactions of neurons arraigned in a network.

A versatile plasma lithography technique has been developed to generate stable surface patterns for guiding cellular attachment. This technique can be applied to create cell networks including those that mimic natural tissues and has been used for studying several, distinct cell types.

等离子体表面图案光刻技术的蜂窝网络创作

Systematic manipulation of a cell microenvironment with micro- and nanoscale resolution is often required for deciphering various cellular and molecular ...

科研

生物工程

Anatomical Reconstructions of the Human Cardiac Venous System using Contrast-computed Tomography of Perfusion-fixed Specimens

A detailed understanding of the complexity and relative variability within the human cardiac venous system is crucial for the development of cardiac devices that require access to these vessels. For example, cardiac venous anatomy is known to be one of the key limitations for the proper delivery of cardiac resynchronization therapy (CRT)1 Therefore, the development of a database of anatomical parameters for human cardiac venous systems can aid in the design of CRT delivery devices to overcome such a limitation. In this research project, the anatomical parameters were obtained from 3D reconstructions of the venous system using contrast-computed tomography (CT) imaging and modeling software (Materialise, Leuven, Belgium). The following parameters were assessed for each vein: arc length, tortuousity, branching angle, distance to the coronary sinus ostium, and vessel diameter.
	CRT is a potential treatment for patients with electromechanical dyssynchrony. Approximately 10-20% of heart failure patients may benefit from CRT2. Electromechanical dyssynchrony implies that parts of the myocardium activate and contract earlier or later than the normal conduction pathway of the heart. In CRT, dyssynchronous areas of the myocardium are treated with electrical stimulation. CRT pacing typically involves pacing leads that stimulate the right atrium (RA), right ventricle (RV), and left ventricle (LV) to produce more resynchronized rhythms. The LV lead is typically implanted within a cardiac vein, with the aim to overlay it within the site of latest myocardial activation. 
	We believe that the models obtained and the analyses thereof will promote the anatomical education for patients, students, clinicians, and medical device designers. The methodologies employed here can also be utilized to study other anatomical features of our human heart specimens, such as the coronary arteries. To further encourage the educational value of this research, we have shared the venous models on our free access website: <a href="http://www.vhlab.umn.edu/atlas" target="_blank">www.vhlab.umn.edu/atlas</a>.

The objective of this research is to recreate and then access the anatomy of the human cardiac venous system using 3D reconstructions generated from contrast-computed tomography scans.

人类心脏静脉系统使用对比计算机断层扫描灌注固定的标本解剖重建

A detailed  understanding of the complexity and relative variability within the human  cardiac venous system is crucial for the development of cardiac ...

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 ...

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, ...

Fabricating Superhydrophobic Polymeric Materials for Biomedical Applications

Superhydrophobic materials, with surfaces possessing permanent or metastable non-wetted states, are of interest for a number of biomedical and industrial applications. Here we describe how electrospinning or electrospraying a polymer mixture containing a biodegradable, biocompatible aliphatic polyester (e.g., polycaprolactone and poly(lactide-co-glycolide)), as the major component, doped with a hydrophobic copolymer composed of the polyester and a stearate-modified poly(glycerol carbonate) affords a superhydrophobic biomaterial. The fabrication techniques of electrospinning or electrospraying provide the enhanced surface roughness and porosity on and within the fibers or the particles, respectively. The use of a low surface energy copolymer dopant that blends with the polyester and can be stably electrospun or electrosprayed affords these superhydrophobic materials. Important parameters such as fiber size, copolymer dopant composition and/or concentration, and their effects on wettability are discussed. This combination of polymer chemistry and process engineering affords a versatile approach to develop application-specific materials using scalable techniques, which are likely generalizable to a wider class of polymers for a variety of 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 ...

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 ...

Synthesis of Keratin-based Nanofiber for Biomedical Engineering

Electrospinning, due to its versatility and potential for applications in various fields, is being frequently used to fabricate nanofibers. Production of these porous nanofibers is of great interest due to their unique physiochemical properties. Here we elaborate on the fabrication of keratin containing poly (&#949;-caprolactone) (PCL) nanofibers (i.e., PCL/keratin composite fiber). Water soluble keratin was first extracted from human hair and mixed with PCL in different ratios. The blended solution of PCL/keratin was transformed into nanofibrous membranes using a laboratory designed electrospinning set up. Fiber morphology and mechanical properties of the obtained nanofiber were observed and measured using scanning electron microscopy and tensile tester. Furthermore, degradability and chemical properties of the nanofiber were studied by FTIR. SEM images showed uniform surface morphology for PCL/keratin fibers of different compositions. These PCL/keratin fibers also showed excellent mechanical properties such as Young&#39;s modulus and failure point. Fibroblast cells were able to attach and proliferate thus proving good cell viability. Based on the characteristics discussed above, we can strongly argue that the blended nanofibers of natural and synthetic polymers can represent an excellent development of composite materials that can be used for different biomedical applications.

Electrospun nanofibers have a high surface area to weight ratio, excellent mechanical integrity, and support cell growth and proliferation. These nanofibers have a wide range of biomedical applications. Here we fabricate keratin/ PCL nanofibers, using the electrospinning technique, and characterize the fibers for possible applications in tissue engineering.

基于角蛋白纳米纤维生物医学工程合成

Electrospinning, due to its versatility and potential for applications in various fields, is being frequently used to fabricate nanofibers. Production of ...

Construction of Modular Hydrogel Sheets for Micropatterned Macro-scaled 3D Cellular Architecture

Hydrogels can be patterned at the micro-scale using microfluidic or micropatterning technologies to provide an in vivo-like three-dimensional (3D) tissue geometry. The resulting 3D hydrogel-based cellular constructs have been introduced as an alternative to animal experiments for advanced biological studies, pharmacological assays and organ transplant applications. Although hydrogel-based particles and fibers can be easily fabricated, it is difficult to manipulate them for tissue reconstruction. In this video, we describe a fabrication method for micropatterned alginate hydrogel sheets, together with their assembly to form a macro-scale 3D cell culture system with a controlled cellular microenvironment. Using a mist form of the calcium gelling agent, thin hydrogel sheets are easily generated with a thickness in the range of 100 - 200 &#181;m, and with precise micropatterns. Cells can then be cultured with the geometric guidance of the hydrogel sheets in freestanding conditions. Furthermore, the hydrogel sheets can be readily manipulated using a micropipette with an end-cut tip, and can be assembled into multi-layered structures by stacking them using a patterned polydimethylsiloxane (PDMS) frame. These modular hydrogel sheets, which can be fabricated using a facile process, have potential applications of in vitro drug assays and biological studies, including functional studies of micro- and macrostructure and tissue reconstruction.

We describe the fabrication of micropatterned hydrogel sheets using a simple process, which can be assembled and manipulated in a freestanding form. Using these modular hydrogel sheets, a simple macro-scaled 3D cell culture system can be generated with a controlled cellular microenvironment.

构建模块化水凝胶片的微模式化宏观缩放3D细胞结构

Hydrogels can be patterned at the micro-scale using microfluidic or micropatterning technologies to provide an in vivo-like three-dimensional (3D) tissue ...

Multimodal Volumetric Retinal Imaging by Oblique Scanning Laser Ophthalmoscopy (oSLO) and Optical Coherence Tomography (OCT)

While fluorescence imaging is widely used in ophthalmology, a large field of view (FOV) three-dimensional (3D) fluorescence retinal image is still a big challenge with the state-of-the-art retinal imaging modalities because they would require z-stacking to compile a volumetric dataset. Newer optical coherence tomography (OCT) and OCT angiography (OCTA) systems overcome these restrictions to provide three-dimensional (3D) anatomical and vascular images, but the dye-free nature of OCT cannot visualize leakage indicative of vascular dysfunction. This protocol describes a novel oblique scanning laser ophthalmoscopy (oSLO) technique that provides 3D volumetric fluorescence retinal imaging. The setup of the imaging system generates the oblique scanning by a dove tail slider and aligns the final imaging system at an angle to detect fluorescent cross-sectional images. The system uses the laser scanning method, and therefore, allows an easy incorporation of OCT as a complementary volumetric structural imaging modality. In vivo imaging on rat retina is demonstrated here. Fluorescein solution is intravenously injected to produce volumetric fluorescein angiography (vFA).

Multimodal Volumetric Retinal Imaging by Oblique Scanning Laser Ophthalmoscopy oSLO and Optical Coherence Tomography OCT

Here, we present a protocol to get a large field of view (FOV) three-dimensional (3D) fluorescence and OCT retinal image by using a novel imaging multimodal platform. We will introduce the system setup, the method of alignment, and the operational protocols. In vivo imaging will be demonstrated, and representative results will be provided.

斜扫描激光检眼镜 (奥斯陆) 与光学相干层析成像 (OCT) 的多模态视网膜成像

While fluorescence imaging is widely used in ophthalmology, a large field of view (FOV) three-dimensional (3D) fluorescence retinal image is still a big ...

A Zebrafish Embryo Model for In Vivo Visualization and Intravital Analysis of Biomaterial-associated Staphylococcus aureus Infection

Biomaterial-associated infection (BAI) is a major cause of the failure of biomaterials/medical devices. Staphylococcus aureus is one of the major pathogens in BAI. Current experimental BAI mammalian animal models such as mouse models are costly and time-consuming, and therefore not suitable for high throughput analysis. Thus, novel animal models as complementary systems for investigating BAI in vivo are desired. In the present study, we aimed to develop a zebrafish embryo model for in vivo visualization and intravital analysis of bacterial infection in the presence of biomaterials based on fluorescence microscopy. In addition, the provoked macrophage response was studied. To this end, we used fluorescent protein-expressing S. aureus and transgenic zebrafish embryos expressing fluorescent proteins in their macrophages and developed a procedure to inject bacteria alone or together with microspheres into the muscle tissue of embryos. To monitor bacterial infection progression in live embryos over time, we devised a simple but reliable method of microscopic scoring of fluorescent bacteria. The results from microscopic scoring showed that all embryos with more than 20 colony-forming units (CFU) of bacteria yielded a positive fluorescent signal of bacteria. To study the potential effects of biomaterials on infection, we determined the CFU numbers of S. aureus with and without 10 &#181;m polystyrene microspheres (PS10) as model biomaterials in the embryos. Moreover, we used the ObjectJ project file &#34;Zebrafish-Immunotest&#34; operating in ImageJ to quantify the fluorescence intensity of S. aureus infection with and without PS10 over time. Results from both methods showed higher numbers of S. aureus in infected embryos with microspheres than in embryos without microspheres, indicating an increased infection susceptibility in the presence of the biomaterial. Thus, the present study shows the potential of the zebrafish embryo model to study BAI with the methods developed here.