作者没有致谢。

本试验所用牙齿的收集是按照区域医学伦理委员会的指导方针进行的。
1. 标本采集和样品制备
<ol><li>收集24声音提取的人 (前) 臼齿从牙科实践, 并刷与浮石在低速手机到一个干净的 (无碎片, 没有牙龈残余) 和光滑的牙齿表面, 最后冲洗十五年代下自来水。</li>
	<li>嵌入的样品, 使他们适合的凹槽 (12 毫米 x 15 mm x 27.5 毫米) 的气缸的设备。<ol>
<li>在板 (50 ° c) 上熔化印模化合物 (一根113克), 大约10分钟, 在熔融物质中浸出臼齿的咬合部分, 覆盖咬合表面。将臼齿倒置放在显微镜下的幻灯片上, 然后按下直到所有杯子的提示触摸玻璃和等待±三十年代, 直到印象化合物已冷却和设置, 固定的牙齿。</li>
		<li>使用注射器将10毫升的酯 (pmma) 混合物倒入硅胶模具中, 内部尺寸为 12 mm x 15 mm x 27.5 mm. 混合 PMMA 在油烟罩 (比13克聚合物:10 毫升单体) 大约二十五年代使用刮刀。离开到十五年代, 这样任何气泡都可以在使用前逃脱。</li>
		<li>将显微镜滑轨倒置, 并在填充有 PMMA 的硅模中暂停磨牙。按下幻灯片, 直到它触及模具。浇注相在室温下持续约1.5 分钟。</li>
		<li>在室温下设置 PMMA 和 1000 hPa 20 分钟后, 取下显微镜滑轨, 从硅模具中取出嵌入的牙齿。</li>
		<li>测量嵌入摩尔的总高度, 并通过用 16 mm 的铣刀, 从底部增量去除固化的 PMMA, 将高度调整到刚好 27.3 mm。</li>
	</ol>
</li>
</ol>2. 脱矿溶液的制备
<ol><li>添加0.1 米乳酸 (50 克), 1.5 mm CaCl2 (1.103 g), 0.9 mm,2PO4 (0.612 g), 10 毫升1% 氯, 0.5 ppm F (2.5 毫升 1000 ppm 氟化物标准溶液) 到4900毫升的去离子水搅拌板上。</li>
	<li>滴定与10米 KOH (±50毫升), 以 ph 4.8 与校准 ph 玻璃电极。</li>
</ol>3. 摩擦 & 轧辊的安装和机器设置 (图 1)
<ol><li>从容器中取出钢瓶, 将24试样放在摩擦 & 辊筒的凹槽中。</li>
	<li>为了调整加载力, 通过在试样下方的凹槽中放置一个垫片来调整试样的突起。对于没有负载 (0 n) 的8标本, 使用无垫片, 并为 30 n (8 标本) 和 50 n (8 标本), 使用一个垫片的1毫米和1.5 毫米, 分别。</li>
	<li>安装气缸的2部分, 用 M6 螺栓固定, 并将钢瓶放在容器中。</li>
	<li>用500毫升脱矿溶液填充容器。</li>
	<li>放置装货杆: PVC 管 (硬度73岸 a), 外径为14毫米, 内径为 10 mm, 插入不锈钢316杆 (硬度 130-150 HB), 直径为9毫米。</li>
	<li>将转速设置为 20 rpm, 模拟临床咀嚼频率, 并让设备不间断运行。</li>
	<li>在实验中, 更换除盐溶液和 PVC 管, 并检查 pH 与校准玻璃电极每周两次。</li>
	<li>在3月后 (对应于大约150万个周期) 断开钢瓶与容器的连接, 拆下样品, 拆卸2部分的气缸, 并将标本存放在去离子水中。 注: 所有试样都在摩擦 & 辊的前后进行扫描, 使用非接触仪。</li>
</ol>4. 测量扫描、分析和减法
<ol><li>使用仪生成样品的地形测量。</li>
	<li>开关设备: 计算机、电源模块和传感器控制器。放置适当的传感器, 并与螺钉安全。然后, 小心地将光纤插入传感器控制器。</li>
	<li>在传感器控制器上选择正确的传感器。传感器控制器将显示4选项 (F1-F4)。按 F4 两次, 并显示共焦传感器菜单。<ol>
<li>按 F3 (传感器选择), 滚动到 2-1万µm. 选择 (10 mm) 并按 F4。按 F1 并选择 F4 (是) 将设置保存到 EEPROM。选择 LED 强度, 并转到位置 "±9点", 并按 F4-F2-F4 采取了 "暗参考" 的传感器。</li>
	</ol>
</li>
	<li>打开软件并选择 "连接" 到设备的选项。注意, 测量表将自动移动到 "主页位置" 搜索。显示屏上会显示主屏幕。按下菜单栏中的工具, 然后选择传感器 S29 |10-1万µm。<ol>
<li>按下菜单栏中的工具, 然后选择300赫兹. 在菜单栏中的按下工具, 然后是速度传感器, 然后选择 0-100%。</li>
	</ol>
</li>
	<li>在菜单栏中选择 "扫描"。然后选择关键移动阶段。按屏幕中间的黄色区域, 将测量表移动到中心。</li>
	<li>将试样放置在测量表的中心, 然后在传感器的范围内设置正确的高度。将传感器置于样本感兴趣的区域之上, 并调整传感器的距离, 使扫描的完整采样区域位于传感器的焦点范围内。传感器控制器指示高度是否在显示活动数据高度中的绿色区域的传感器范围内。</li>
	<li>选择设置。将平均值设置为 2, 以确保每个记录的数据点都是平均2测量值。这会减慢扫描速度, 但会提高扫描质量。完成设置后, 按 OK 返回主扫描设置。</li>
	<li>将传感器光束放置在试样的左上角。将总扫描区域设置为 15 mm x 12 mm, 在 x 和 y 方向的步长为40µm (0.04 mm), 步骤数 x = 375 和 y = 300。再次, 较小的步骤将增加扫描分辨率, 但也扫描时间。现在按扫描开始扫描。</li>
	<li>当扫描完成约10分钟后, 在菜单栏中选择 "文件", 随后选择 "另存为"。扫描被规范化, 在这种方式下, 天平总是在相同的水平。</li>
	<li>选择菜单栏中的文件, 然后选取 "打开文件"。在菜单栏中选择翘曲。使用1的翘曲滤镜来消除扫描台和传感器的噪音。选择菜单栏中的最高点, 然后在磨牙上找到最高点。</li>
	<li>在菜单栏中选择工具, 然后在扫描配置中选择选项缩放。在扫描配置中, 按 Z 值最高点 (在4.10 中测量)-3500 计算 mm 的偏移量。手动设置范围, 从0到 3.6 mm, 然后按 "确定"。</li>
	<li>选择菜单栏中的 "加载区域" 以重置缩放比例。选择菜单栏中的文件, 接着选择 "另存为"。</li>
	<li>减去扫描在两个不同的时刻, 在时间。<ol>
<li>在软件的菜单栏中选择 "打开"。在目录中找到原始扫描和修改后的扫描文件, 选择 "文件", 然后按 "确定"。将显示 "选项" 屏幕, 在 "调配" 选项中选择: 手动调配选项;并在补偿抵消的选项分别, 适用于原件和适用于修改。</li>
		<li>在菜单栏中选择 "窗口", 后跟选项创建视图, 最后是选项横截面视图。</li>
	</ol>
</li>
	<li>选取已修改的曲面, 并在水平、垂直和 Z 方向 (高度) 上, 通过按住控制键并按下左右箭头键以水平方向移动经过修改的曲面;按住控制键并按向上和向下箭头键进行垂直方向;按住 shift 键并按 Z 方向向上和向下键, 这样, 差异视图中显示的减去的音量和高度就尽可能低。</li>
	<li>选择菜单栏中的文件, 然后选择 "另存为". 输出被读为平均体积损失和平均高度损失。</li>
</ol>

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作者没有什么可透露的。

在这里提出的应用给了一个良好的印象的临床相关性的揉 & 辊。在实验中产生的咬合形态学在最高的负载水平是非常相似的临床表现糜烂牙齿磨损 (图 5)11,12。
设置的多才多艺首先说谎与使用的解答。在最简单的模型中, 可以使用水。在水介质中加载样品可用于样品老化, 例如复合树脂修复胶粘接, 在粘结强度测试之前13。在一个更具临床相关性的模型中, 水可以被人工唾液取代。研磨性成分, 如纤维可以添加到模拟咀嚼的磨料食品。即使是整个食品, 也可以在咀嚼磨损是调查结果的情况下使用。对于纯腐蚀磨损, 可以制定出模拟软饮料或果汁的解决方案。
其次, 如本例所示, 可以通过改变样品的位置来调整载荷。装载被限制到大约 75 N, 但这在正常嚼力量的范围之内很好14。通过选择生理负荷水平, 衰老过程的速度与临床相关。由于旋转单元中的连续曝光, 以及在同一时间可以暴露的大量试样, 实验总时间仍在减少。
可以设想对设备进行更多的修改。通过添加热控单元, 可以引入冷热的方面, 这是口腔老化的另一个重要方面。通过改变培养基周期, 可以引入 pH 循环, 用于模拟釉质的龋齿过程 (de 和再)。可以对杆面进行修改, 以模拟不同的拮抗剂情况, 如瓷或复合修复体。通过在样品下方放置粘弹性材料, 可以模拟牙周韧带的作用。该设备是相对简单的, 可以很容易地定制的用户, 根据需要。
在操作设备时必须考虑一些细节。当使用不均匀接触面时, 样品定位是复杂的, 因为在表面上的杆的运动可能会受到凸出形状的阻碍。这可能会导致滑杆和不必要的振动。在每一个实验的开始, 因此, 有必要密切监测设备的运行。大约8小时后, 它通常会顺利运行。建议在这段时间后更换杆, 并从该点起, 每周更换两次。
在牙被嵌入为咬合装载之前, 应该仔细地考虑定位, 以便杆运动的方向模拟发音或咀嚼运动尽可能接近。咬合面上的力可能会导致磨损, 这反过来会降低载荷。建议定期监测样品的突起, 以便在预定范围内保持装货。在使用酸性介质进行的实验中, 对于侵蚀或龋齿的建模, pH 值也应进行监测。由于搪瓷的溶解, 它可能会在更长的实验过程中发生变化。

口腔可以被认为是一个严酷的环境: 湿度, 温度的变化, 由于热和冷的食物摄入, 和机械负荷与一些最强的肌肉在人体。然而, 牙齿有能力抵御这些挑战。搪瓷是非常坚硬的, 并且牙本质在之下防止相对地易碎的搪瓷从破裂。这两种材料的矿物成分, 羟基磷灰石是非常低的溶解度和平衡与饱和唾液。咀嚼, 饮酒, 偶尔磨牙会导致生理牙齿磨损在一生中1,2,3。极端的挑战, 如磨牙或习惯性咀嚼异物, 可能导致过度磨损。近年来, 侵蚀在加速机械齿磨损中的作用得到了认可。牙齿侵蚀已被广泛研究的体外, 但所使用的模型一般是简单的, 和机械因素很大程度上被忽视。因此, 化学和机械磨损过程之间的临床相互作用是不完全理解的4。
许多体外侵蚀和糜烂磨损研究使用简单的酸浸泡平坦抛光珐琅或牙本质样品, 使用硬度损失或轮廓术作为测量方法5。磨料成分的引入通常涉及刷牙动作, 或有时舌或珐琅尖滑动接触点6。这些研究表明, 釉质侵蚀导致软化表面层, 这是容易磨损。平面通常是需要的, 因为机械加载装置不能处理凹凸不平的表面, 而且测量不均匀的表面的技术也更加复杂。然而, 在咬合尖, 大多数的青少年糜烂牙齿磨损, 咀嚼食物的磨损预计是最相关的机械因素咬合侵蚀磨损。理想的口腔磨损机, 模仿口腔环境的所有细节不存在, 大多数体外模型将不允许天然咬合表面的牙齿是暴露或测量7,8。
我们的实验室最近推出了一种新颖的设备, 它符合许多 Heintze 的7规范和口腔磨损模拟模型的公差, 并使用户能够单独或同时在侵蚀和/或研磨环境。新设备 (搓 & 卷) 由搅拌机器和容器 (图 1a) 组成.在容器中, 可以安装带有试样的圆柱体。在圆筒和容器的内壁之间一个更多标尺被安置 (图 1b)。通过启动搅拌马达, 杆在气缸中的试样上旋转 (图 1c)。使用垫片, 不同的力量可以应用于标本。有关设备的设计、构造、运行机制和功能的全面描述, 请参阅介绍和讨论设备9的文章。该装置坚固耐用, 技术要求不高, 可同时将载荷应用于32试样。拮抗力在试样表面上移动, 同时保持平滑连续的接触, 这与正常咀嚼的10相当。本文介绍了天然牙咬合面磨损模型的应用, 并说明了该方法的临床意义和通用性。

<table><tbody><tr><td>Low speed handpiece</td><td>KAVO, Leutkirch imm Allgau, Germany</td><td></td><td>Dental equipment</td></tr><tr><td>Brush for handpiece</td><td>KAVO, Leutkirch imm Allgau, Germany</td><td></td><td>Dental equipment</td></tr><tr><td>Pumish</td><td></td><td></td><td>Dental equipment</td></tr><tr><td>Human third molars</td><td></td><td></td><td></td></tr><tr><td>Impression compound green</td><td>Kerr, Bioggio, Switzerland</td><td>Art.nr. 00444</td><td></td></tr><tr><td>Microscope slide</td><td>Menzel, Braunschweig, Germany</td><td></td><td>76 x 26 mm</td></tr><tr><td>Autoplast Cold curing denture base material</td><td>Candulor, Wangen, Switzerland</td><td></td><td></td></tr><tr><td>Silicone mold with inside dimensions of 12 x 15 x 27.5</td><td>3M Espe Neuss, Germany</td><td>Express STD</td><td></td></tr><tr><td>Pressure vessel</td><td>Al Dente, Meckenbeuren, Germany</td><td>581-009-024/25</td><td></td></tr><tr><td>Milling cutter &amp;oslash;16mm</td><td>Format, Germany</td><td>HSSCo8 nr. 21691600</td><td></td></tr><tr><td>Milling machine</td><td>Weiss Machine Tools</td><td>WMD 20 LV</td><td></td></tr><tr><td>Rub&amp;amp;Roll</td><td>UMCN , Nijmegen The Netherlands</td><td></td><td>Technical workshop</td></tr><tr><td>Rub&amp;amp;Roll container</td><td>UMCN , Nijmegen The Netherlands</td><td></td><td>Technical workshop</td></tr><tr><td>Rub&amp;amp;Roll cylinder sample holder</td><td>UMCN , Nijmegen The Netherlands</td><td></td><td>Technical workshop</td></tr><tr><td>Rub&amp;amp;Roll motor</td><td>UMCN , Nijmegen The Netherlands</td><td></td><td>Technical workshop</td></tr><tr><td>Shim: Silicone plate massive 1 mm/ 1,5mm, 60 &amp;plusmn; 5&amp;deg; Shore A, red</td><td>Peter van den Berg afdichtingstechniek, Barendrecht</td><td></td><td></td></tr><tr><td>Lactid acid extra pure 88%</td><td>Boom, The Netherlands</td><td>CAS nummer: 79-33-4</td><td></td></tr><tr><td>Calcium Chloride dihydrate CaCL&lt;sub&gt;2&lt;/sub&gt; .2H&lt;sub&gt;2&lt;/sub&gt;O</td><td>Merck, Darmstadt, Germany</td><td>CAS nummer: 10043-52-4</td><td></td></tr><tr><td>Pottassium dihydrogen Phosphate KH&lt;sub&gt;2&lt;/sub&gt;PO&lt;sub&gt;4&lt;/sub&gt;</td><td>Merck, Darmstadt, Germany</td><td>CAS nummer: 7778-77-0</td><td></td></tr><tr><td>Chloramine T (sodium salt) trihydrate for synthesis CH&lt;sub&gt;3&lt;/sub&gt;C&lt;sub&gt;6&lt;/sub&gt;H&lt;sub&gt;4&lt;/sub&gt;SO&lt;sub&gt;2&lt;/sub&gt;NClNa&amp;middot;3H&lt;sub&gt;2&lt;/sub&gt;O</td><td>Merck, Darmstadt, Germany</td><td>CAS nummer: 7080-50-4</td><td></td></tr><tr><td>Natriumfluoride standard solution 1000mg/L F Certipur</td><td>Merck, Darmstadt, Germany</td><td>CAS nummer: 7681-49-4</td><td></td></tr><tr><td>Deionized water</td><td></td><td></td><td></td></tr><tr><td>Kaliumhydroxide, pellets EMSURE analytical reagent KOH</td><td>Merck, Darmstadt, Germany</td><td>CAS nummer: 1310-58-3</td><td></td></tr><tr><td>PVC tube(Hardness73 Shore A)outer diameter 14mm inner diameter 10mm</td><td>DEUTSCH &amp;amp; NEUMANN, Germany</td><td>Art.nr. 3501014</td><td></td></tr><tr><td>Insert of a stainless steel 316 (Hardness 130&amp;ndash;150 HB) diameter 9mm</td><td>UMCN , Nijmegen The Netherlands</td><td></td><td>Technical workshop</td></tr><tr><td>pH glass electrode</td><td>WTW, Weilheim, Germany</td><td>Sentix 61 103640</td><td></td></tr><tr><td>Non contact Profilometer Proscan 2100</td><td>Scantron Industrial Products Ltd, Taunton, UK</td><td></td><td>http://www.scantronltd.co.uk</td></tr><tr><td>Software version Proscan 2100 2.1.1.15A+ Sensor S29 / 10-10000 microns</td><td>Scantron Industrial Products Ltd, Taunton, UK</td><td></td><td></td></tr><tr><td>Software version Proform</td><td>Scantron Industrial Products Ltd, Taunton, UK</td><td></td><td></td></tr><tr><td>Stereomicroscope Leica</td><td>www.leica-microsystems.com</td><td>M50</td><td></td></tr><tr><td>Photocamera Canon</td><td>Canon Japan</td><td>EOS 50D</td><td></td></tr><tr><td>Syringe</td><td>BD Plastipak, Spain</td><td>20 ml.</td><td></td></tr><tr><td>Hotplate</td><td>Schott instruments Mainz</td><td>SLK1</td><td></td></tr><tr><td>Silone impression material (Vinyl Polysiloxane Expres)</td><td>3M Espe , USA</td><td>Regular</td><td></td></tr><tr><td>Stirring Plate</td><td>IKA Werke, Germany</td><td>KMO2 Basic</td><td></td></tr></tbody></table>

mimicking and measuring occlusal erosive tooth wear with the "rub&amp;roll" and non-contact profilometry

咀嚼、饮酒和偶尔磨牙会导致生理上的牙齿磨损。极端的挑战, 如磨牙或习惯性咀嚼异物, 可能导致过度磨损。近年来, 腐蚀在加速机械齿磨损中的作用已经得到了认可, 但化学和机械磨损过程之间的相互影响还没有得到广泛的研究。我们的实验室最近引入了一种新型的口腔磨损模拟装置, 即摩擦 & 轧辊, 使用户能够单独或同时在侵蚀和/或研磨环境中进行磨损和加载研究。这份手稿描述了该装置的一个应用: 在模拟咀嚼运动中, 被提取的人 (前) 磨牙的复合机械和腐蚀载荷, 具有受力、速度、流体和时间的控制应用,非接触式轮廓术在可视化和测量所产生的磨损模式。在最高负荷水平实验中产生的咬合形态学与糜烂磨损的临床表现非常相似。

我们暴露了人磨牙 (n = 8 每组) 到酸性水溶液在 pH 4.8 在摩擦 & 轧辊, 3 月。这对应于一个临床运作时间大约6年。施加的机械载荷为: 无负载 (0 n)、30 n 或 50 n。
平均咬合面高度损失为三组为:76 ±20µm 为 0 N;161±40µm 30 N;和266±101µm 50 N (图 2)。磨损与机械加载造成的咬合尖齿状病变的牙颌尖端尖端类似的临床现象与侵蚀牙齿磨损称为 "拔火罐" (图 3和图 4)。
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/56400/56400fig1.jpg"> 图1。摩擦 & 轧辊示意图.(a) 设备概述: 1. 搅拌电机, 2. 容器。(b) 容器的内部视图: 3. 杆, 4 缸。(c) 与试样和容器外部接触的连杆: 3. 杆, 5. 垫片, 6. 嵌入的摩尔。<a href="//cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/56400/56400fig1large.jpg" target="_blank">请单击此处查看此图的较大版本.</a>
<img alt="Figure 2" class="xfigimg" src="/files/ftp_upload/56400/56400fig2.jpg"> 图 2.条形图显示的平均咬合表面高度损失的人磨牙牙齿加载 0, 30, 或 50 N 在一个脱矿溶液 pH 4.8 使用的摩擦 & 辊装置。误差线指示 SD.<a href="//cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/56400/56400fig2large.jpg" target="_blank">请单击此处查看此图的较大版本.</a>
<img alt="Figure 3" class="xfigimg" src="/files/ftp_upload/56400/56400fig3.jpg"> 图 3.典型的磨牙牙后3月的摩擦 & 辊在一个脱盐溶液与 pH 值4.8。从左到右, 牙齿机械地加载 0 n, 30 n, 或 50 n 首行显示 stereomicroscopic 光照片 (放大 10X), 和底部行显示相应的减法图像。减法图像中的颜色表示从无损耗 (红色) 到1500µm 损耗 (蓝色) 的高度损失。<a href="//cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/56400/56400fig3large.jpg" target="_blank">请单击此处查看此图的较大版本.</a>
<img alt="Figure 4" class="xfigimg" src="/files/ftp_upload/56400/56400fig4.jpg"> 图 4.示例测量扫描选定的样本, 前 (上一行) 和后3月曝光 (中间行)。底部的行显示两个叠加扫描的行剖面 (在曝光后为红色和黑色)。<a href="//cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/56400/56400fig4large.jpg" target="_blank">请单击此处查看此图的较大版本.</a>
<img alt="Figure 5" class="xfigimg" src="/files/ftp_upload/56400/56400fig5.jpg"> 图 5.咬合侵蚀牙磨耗的临床应用实例。注意尖的拔火罐 (Dr. r 高路易)。<a href="//cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/56400/56400fig5large.jpg" target="_blank">请单击此处查看此图的较大版本.</a>

Watch this Scientific Journal Video about Mimicking and Measuring Occlusal Erosive Tooth Wear with the "Rub&Roll" and Non-contact Profilometry at JoVE.com

Mimicking and Measuring Occlusal Erosive Tooth Wear with the "Rub&Roll" and Non-contact Profilometry

摩擦 & 辊可以模仿咀嚼周期, 允许变化的咀嚼力, 滑动距离, 咀嚼速度, 周期数, 和频率, 并与侵蚀和磨料的挑战, 可能导致复杂的模拟口腔老化。

用 "搓 &amp; 辊" 和非接触式轮廓术模拟和测量咬合侵蚀齿磨损

Chewing, drinking, and occasional tooth grinding will result in physiological tooth wear during a lifetime. Extreme challenges, such as bruxism or ...

mimicking-measuring-occlusal-erosive-tooth-wear-with-rub-roll-non

Nanyang Technological University

Research

JoVE Journal

Bioengineering

Mimicking and Measuring Occlusal Erosive Tooth Wear with the "Rub&amp;Roll" and Non-contact Profilometry

12.1K 次观看.  Radboud University Medical Center. 摩擦 & 辊可以模仿咀嚼周期, 允许变化的咀嚼力, 滑动距离, 咀嚼速度, 周期数, 和频率, 并与侵蚀和磨料的挑战, 可能导致复杂的模拟口腔老化。

视频: Mimicking and Measuring Occlusal Erosive Tooth Wear with the "Rub&Roll" and Non-contact Profilometry

Gold Nanostar Synthesis with a Silver Seed Mediated Growth Method

The physical, chemical and optical properties of nano-scale colloids depend on their material composition, size and shape 1-5. There is a great interest in using nano-colloids for photo-thermal ablation, drug delivery and many other biomedical applications 6. Gold is particularly used because of its low toxicity 7-9. A property of metal nano-colloids is that they can have a strong surface plasmon resonance 10. The peak of the surface plasmon resonance mode depends on the structure and composition of the metal nano-colloids. Since the surface plasmon resonance mode is stimulated with light there is a need to have the peak absorbance in the near infrared where biological tissue transmissivity is maximal 11, 12.
We present a method to synthesize star shaped colloidal gold, also known as star shaped nanoparticles 13-15 or nanostars 16. This method is based on a solution containing silver seeds that are used as the nucleating agent for anisotropic growth of gold colloids 17-22. Scanning electron microscopy (SEM) analysis of the resulting gold colloid showed that 70 % of the nanostructures were nanostars. The other 30 % of the particles were amorphous clusters of decahedra and rhomboids. The absorbance peak of the nanostars was detected to be in the near infrared (840 nm). Thus, our method produces gold nanostars suitable for biomedical applications, particularly for photo-thermal ablation.

We synthesized star shaped gold nanostars using a silver seed mediated growth method. The diameter of the nanostars ranges from 200 to 300 nm and the number of tips vary from 7 to 10. The nanoparticles have a broad surface plasmon resonance mode centered in the near infrared.

黄金Nanostar合成银种子介导的生长方法

The physical, chemical and optical properties of nano-scale colloids depend on their material composition, size and shape 1-5. There is a great interest ...

科研

生物工程

Non-contact, Label-free Monitoring of Cells and Extracellular Matrix using Raman Spectroscopy

Non-destructive, non-contact and label-free technologies to monitor cell and tissue cultures are needed in the field of biomedical research.1-5 However, currently available routine methods require processing steps and alter sample integrity. Raman spectroscopy is a fast method that enables the measurement of biological samples without the need for further processing steps. This laser-based technology detects the inelastic scattering of monochromatic light.6 As every chemical vibration is assigned to a specific Raman band (wavenumber in cm-1), each biological sample features a typical spectral pattern due to their inherent biochemical composition.7-9 Within Raman spectra, the peak intensities correlate with the amount of the present molecular bonds.1 Similarities and differences of the spectral data sets can be detected by employing a multivariate analysis (e.g. principal component analysis (PCA)).10
Here, we perform Raman spectroscopy of living cells and native tissues. Cells are either seeded on glass bottom dishes or kept in suspension under normal cell culture conditions (37 &deg;C, 5% CO2) before measurement. Native tissues are dissected and stored in phosphate buffered saline (PBS) at 4 &deg;C prior measurements. Depending on our experimental set up, we then either focused on the cell nucleus or extracellular matrix (ECM) proteins such as elastin and collagen. For all studies, a minimum of 30 cells or 30 random points of interest within the ECM are measured. Data processing steps included background subtraction and normalization.

Raman spectroscopy is a suitable technique for the non-contact, label-free analysis of living cells, tissue-engineered constructs and native tissues. Source-specific spectral fingerprints can be generated and analyzed using multivariate analysis.

非接触，无标签使用拉曼光谱研究细胞和细胞外基质的监测

Non-destructive, non-contact and label-free technologies to monitor cell and tissue cultures are needed in the field of biomedical research.1-5 However, ...

Experiments on Ultrasonic Lubrication Using a Piezoelectrically-assisted Tribometer and Optical Profilometer

Friction and wear are detrimental to engineered systems. Ultrasonic lubrication is achieved when the interface between two sliding surfaces is vibrated at a frequency above the acoustic range (20 kHz). As a solid-state technology, ultrasonic lubrication can be used where conventional lubricants are unfeasible or undesirable. Further, ultrasonic lubrication allows for electrical modulation of the effective friction coefficient between two sliding surfaces. This property enables adaptive systems that modify their frictional state and associated dynamic response as the operating conditions change. Surface wear can also be reduced through ultrasonic lubrication. We developed a protocol to investigate the dependence of friction force reduction and wear reduction on the linear sliding velocity between ultrasonically lubricated surfaces. A pin-on-disc tribometer was built which differs from commercial units in that a piezoelectric stack is used to vibrate the pin at 22 kHz normal to the rotating disc surface. Friction and wear metrics including effective friction force, volume loss, and surface roughness are measured without and with ultrasonic vibrations at a constant pressure of 1 to 4 MPa and three different sliding velocities: 20.3, 40.6, and 87 mm/sec. An optical profilometer is utilized to characterize the wear surfaces. The effective friction force is reduced by 62% at 20.3 mm/sec. Consistently with existing theories for ultrasonic lubrication, the percent reduction in friction force diminishes with increasing speed, down to 29% friction force reduction at 87 mm/sec. Wear reduction remains essentially constant (49%) at the three speeds considered.

We present a protocol for using a piezoelectrically-assisted tribometer and optical profilometer to investigate the dependence of ultrasonic wear and friction reduction on linear velocity, contact pressure, and surface properties.

使用超声波润滑实验一压电辅助摩擦试验机和光学轮廓

Friction and wear are detrimental to engineered systems. Ultrasonic lubrication is achieved when the interface between two sliding surfaces is vibrated at ...

工程学

Bridging the Bio-Electronic Interface with Biofabrication

Advancements in lab-on-a-chip technology promise to revolutionize both research and medicine through lower costs, better sensitivity, portability, and higher throughput. The incorporation of biological components onto biological microelectromechanical systems (bioMEMS) has shown great potential for achieving these goals. Microfabricated electronic chips allow for micrometer-scale features as well as an electrical connection for sensing and actuation. Functional biological components give the system the capacity for specific detection of analytes, enzymatic functions, and whole-cell capabilities. Standard microfabrication processes and bio-analytical techniques have been successfully utilized for decades in the computer and biological industries, respectively. Their combination and interfacing in a lab-on-a-chip environment, however, brings forth new challenges. There is a call for techniques that can build an interface between the electrode and biological component that is mild and is easy to fabricate and pattern.
Biofabrication, described here, is one such approach that has shown great promise for its easy-to-assemble incorporation of biological components with versatility in the on-chip functions that are enabled. Biofabrication uses biological materials and biological mechanisms (self-assembly, enzymatic assembly) for bottom-up hierarchical assembly. While our labs have demonstrated these concepts in many formats 1,2,3, here we demonstrate the assembly process based on electrodeposition followed by multiple applications of signal-based interactions. The assembly process consists of the electrodeposition of biocompatible stimuli-responsive polymer films on electrodes and their subsequent functionalization with biological components such as DNA, enzymes, or live cells 4,5. Electrodeposition takes advantage of the pH gradient created at the surface of a biased electrode from the electrolysis of water 6,7,. Chitosan and alginate are stimuli-responsive biological polymers that can be triggered to self-assemble into hydrogel films in response to imposed electrical signals 8. The thickness of these hydrogels is determined by the extent to which the pH gradient extends from the electrode. This can be modified using varying current densities and deposition times 6,7. This protocol will describe how chitosan films are deposited and functionalized by covalently attaching biological components to the abundant primary amine groups present on the film through either enzymatic or electrochemical methods 9,10. Alginate films and their entrapment of live cells will also be addressed 11. Finally, the utility of biofabrication is demonstrated through examples of signal-based interaction, including chemical-to-electrical, cell-to-cell, and also enzyme-to-cell signal transmission. 
Both the electrodeposition and functionalization can be performed under near-physiological conditions without the need for reagents and thus spare labile biological components from harsh conditions. Additionally, both chitosan and alginate have long been used for biologically-relevant purposes 12,13. Overall, biofabrication, a rapid technique that can be simply performed on a benchtop, can be used for creating micron scale patterns of functional biological components on electrodes and can be used for a variety of lab-on-a-chip applications.

This article describes a biofabrication approach: deposition of stimuli-responsive polysaccharides in the presence of biased electrodes to create biocompatible films which can be functionalized with cells or proteins. We demonstrate a bench-top strategy for the generation of the films as well as their basic uses for creating interactive biofunctionalized surfaces for lab-on-a-chip applications.

生物电子界面衔接与Biofabrication

Advancements in lab-on-a-chip technology promise to revolutionize both research and medicine through lower costs, better sensitivity, portability, and ...

Creating Adhesive and Soluble Gradients for Imaging Cell Migration with Fluorescence Microscopy

Cells can sense and migrate towards higher concentrations of adhesive cues such as the glycoproteins of the extracellular matrix and soluble cues such as growth factors. Here, we outline a method to create opposing gradients of adhesive and soluble cues in a microfluidic chamber, which is compatible with live cell imaging. A copolymer of poly-L-lysine and polyethylene glycol (PLL-PEG) is employed to passivate glass coverslips and prevent non-specific adsorption of biomolecules and cells. Next, microcontact printing or dip pen lithography are used to create tracks of streptavidin on the passivated surfaces to serve as anchoring points for the biotinylated peptide arginine-glycine-aspartic acid (RGD) as the adhesive cue. A microfluidic device is placed onto the modified surface and used to create the gradient of adhesive cues (100% RGD to 0% RGD) on the streptavidin tracks. Finally, the same microfluidic device is used to create a gradient of a chemoattractant such as fetal bovine serum (FBS), as the soluble cue in the opposite direction of the gradient of adhesive cues.

A method for the assembly of adhesive and soluble gradients in a microscopy chamber for live cell migration studies is described. The engineered environment combines antifouling surfaces and adhesive tracks with solution gradients and therefore allows one to determine the relative importance of guidance cues.

创建的胶粘剂和可溶性梯度荧光显微镜成像细胞迁移

Cells can sense and migrate towards higher concentrations of adhesive cues such as the glycoproteins of the extracellular matrix and soluble cues such as ...

In situ Compressive Loading and Correlative Noninvasive Imaging of the Bone-periodontal Ligament-tooth Fibrous Joint

This study demonstrates a novel biomechanics testing protocol. The advantage of this protocol includes the use of an in situ loading device coupled to a high resolution X-ray microscope, thus enabling visualization of internal structural elements under simulated physiological loads and wet conditions. Experimental specimens will include intact bone-periodontal ligament (PDL)-tooth fibrous joints. Results will illustrate three important features of the protocol as they can be applied to organ level biomechanics: 1) reactionary force vs. displacement: tooth displacement within the alveolar socket and its reactionary response to loading, 2) three-dimensional (3D) spatial configuration and morphometrics: geometric relationship of the tooth with the alveolar socket, and 3) changes in readouts 1 and 2 due to a change in loading axis, i.e. from concentric to eccentric loads. Efficacy of the proposed protocol will be evaluated by coupling mechanical testing readouts to 3D morphometrics and overall biomechanics of the joint. In addition, this technique will emphasize on the need to equilibrate experimental conditions, specifically reactionary loads prior to acquiring tomograms of fibrous joints. It should be noted that the proposed protocol is limited to testing specimens under ex vivo conditions, and that use of contrast agents to visualize soft tissue mechanical response could lead to erroneous conclusions about tissue and organ-level biomechanics.

In situ Compressive Loading and Correlative Noninvasive Imaging of the Bone-periodontal Ligament-tooth Fibrous Joint

In this study, the use of an in situ loading device coupled with micro-X-ray computed tomography for fibrous joint biomechanics will be discussed. Experimental readouts identifiable with an overall change in joint biomechanics will include: 1) reactionary force vs. displacement, i.e. tooth displacement within the alveolar socket and its reactionary response to loading, 2) three-dimensional (3D) spatial configuration and morphometrics, i.e.&#160;geometric relationship of the tooth with the alveolar socket, and 3) changes in readouts 1 and 2 due to a change in loading axis, i.e. concentric or eccentric loads.

原位压极限和骨牙周韧带齿纤维联合的相关性无创成像

This study demonstrates a novel biomechanics testing protocol. The advantage of this protocol includes the use of an in situ loading device coupled to a ...

Roughness Impact of Piezoelectric Dental Scaler on Two Distinct Flowable Composite Filling Materials

Dental ultrasonic scalers are commonly employed in periodontal treatment; however, their ability to roughen tooth surfaces is a worry since roughness may increase plaque production, a key cause of periodontal disease. This research studied the influence of a piezoelectric ultrasonic scaler on the roughness of two distinct flowable composite filling materials. To do this, 10 disc-shaped samples were generated from each of the two flowable composite materials. After standardized polishing, samples were submerged in water for 24 h before the first surface examination using electron microscopy and profilometry. The ultrasonic scaler was applied to a specified location of each sample for 60 s under water cooling and regulated force. Post-scaler surface parameters were again examined. Following the application of the scaler, both composite materials exhibited a notable increase in surface roughness, as determined by profilometry (p &lt; 0.01). Additionally, the observed surface roughness was also qualitatively visualized with scanning electron microscopy. While initial roughness levels were comparable across the two composites (p = 0.143) after scaler application, no substantial discrepancy in surface texture was noticed between them (p = 0.684). The use of a high-power piezoelectric ultrasonic scaler on routinely used flowable composite restorations might generate considerable surface roughness, possibly leading to increased plaque accumulation. Nevertheless, it might be postulated that nanohybrid flowable composite materials having conventional monomer ingredients may demonstrate comparable surface alterations within the limitations of this experiment.

This methodology allows applying a dental appliance on any specimen at any angle with standardized force and stability. This approach might be extensively used in health sciences to standardize the impacts of dental equipment with hand-holding elements such as micromotors, turbines, and ultrasonic scalers on varied surfaces.

压电洁牙机对两种不同流动性复合填充材料的粗糙度影响

Dental ultrasonic scalers are commonly employed in periodontal treatment; however, their ability to roughen tooth surfaces is a worry since roughness may ...

行为学

Precision of In Vivo Quantitative Tooth Wear Measurement Using Intra-Oral Scans

Quantitative wear measurement is of increasing interest for measuring tooth wear progression. However, most research on quantitative wear measurement has focused on simulated wear or scanned gypsum casts. A 3D Wear Analysis (3DWA) protocol has been developed that analyzes tooth wear in vivo through intra-oral scanners available to dental clinicians. This study investigated the precision of the 3DWA protocol for measuring wear through maximum height loss (mm) and volume change (mm3). Observational prospective wear data from 55 patients were analyzed after 0-1-, 0-3-, and 0-5-year intervals to determine rates of wear, and convenience samples were chosen to test the protocol&#39;s precision on dentitions scanned twice in one sitting and its intra- and inter-rater precision on scans with 0-3- and 0-5-year intervals. Scans were made using intra-oral scanners (IOS) and superimposed using 3D measurement software. T-tests were performed to determine the structural and random error, and trimmed ranges were calculated to interpret the error. For protocol precision, the mean difference was 0.015 mm (-0.002; 0.032, p = 0.076) for height and -0.111 mm3 (-0.250; 0.023, p = 0.101) for volume. The duplicate measurement error was 0.062 mm for height and 0.268 mm3 for volume. The height measurements were precise enough to measure wear after intervals of 0-3 or 0-5 years; however, volume measurements were susceptible to procedural error and operator sensitivity. The 3DWA protocol is precise enough to adequately measure tooth height loss after intervals of a minimum of 3 years or in patients with severe wear progression, but it is not suited to measuring volumetric changes.

Precision of In Vivo Quantitative Tooth Wear Measurement Using Intra-Oral Scans

Quantitative wear measurement is a method of increasing importance in measuring tooth wear progression. We here describe a protocol, its precision, and its intra/inter-rater precision for the acquisition and superimposition of repeated in vivo scanned dentitions in patients with moderate to severe wear, reporting on both height and volume measurements.

使用口腔内扫描进行 体内 定量牙齿磨损测量的精度

Quantitative wear measurement is of increasing interest for measuring tooth wear progression. However, most research on quantitative wear measurement has ...

医学

<meta charset="utf8"></head><body>牙本质类似物上 CAD/CAM 咬合贴面的准静态断裂载荷测试

Quasistatic Mechanical Testing for Computer-Aided Design and Manufacturing Occlusal Veneers Cemented to Milled Dentin Analog Material

Under current minimally invasive treatment regimes, minor tooth preparation and thinner biomimetic ceramic restoration are used to preserve the restored tooth&#39;s vitality, aesthetics, and function. New computer-aided design and computer-aided manufacturing (CAD/CAM) ceramic-like material are&#160;now available. To guarantee longevity, a dental clinician must know these&#160;newly launched product&#39;s mechanical strength compared to the relatively brittle glass-matrix ceramic. Furthermore, a tooth substitute has been promoted for laboratory investigation, especially after the pandemic, and more evidentiary support is required for its application.
This study developed a laboratory protocol for a monotonic load-to-fracture test to determine the fracture strength of 1 mm-thick CAD/CAM occlusal veneers. Master dies were milled from high-pressure fiberglass laminate, which has&#160;similar elastic modulus and bond strength as hydrated dentin. They were mounted into polyvinyl chloride (PVC) end caps with cold-curing epoxy resin. Occlusal veneers, also called tabletop restorations, were milled from lithium disilicate (LD) and resin nanoceramic blocks (RNC) and cemented to prepared master dies using dual-cured adhesive resin cement. They were&#160;allowed to cure fully by storing in distilled water for 48 h at 37 &#176;C.
All samples were then placed in a universal testing machine and loaded via a non-fixed 5.5 mm stainless-steel ball that allows lateral movement as would occur against the antagonist&#160;teeth. Compression was applied at a 1 mm/min rate, and the load-displacement graph was generated. The average maximum load-bearing capacity of restorations in the RNC group (3,212.80 &#177; 558.67 N) was significantly higher than in the LD group (2727.10 &#177; 472.41 N) (p &#60; 0.05). No debonding was found during the test.&#160;Both CAD/CAM materials may have a similar flaw distribution. Hertzian cone crack was found at the loading site, whereas radial cracks propagating from the cementation surface were found close to the margin in both groups.

<meta charset="utf8"></head><body>计算机辅助设计和制造粘合到铣削牙本质模拟材料的咬合贴面的准静态力学测试

A quasistatic load-to-fracture test with a non-fixed stainless steel ball was developed to determine the fracture strength of minimally invasive posterior computer-aided design and manufacturing restorations cemented to dentin analog materials. This test models the typical loading regime responsible for the fracture of dental restorations.

计算机辅助设计和制造粘合到铣削牙本质模拟材料的咬合贴面的准静态力学测试

Under current minimally invasive treatment regimes, minor tooth preparation and thinner biomimetic ceramic restoration are used to preserve the restored ...

用 "搓 & 辊" 和非接触式轮廓术模拟和测量咬合侵蚀齿磨损

摘要

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此视频中的章节

黄金Nanostar合成银种子介导的生长方法

非接触，无标签使用拉曼光谱研究细胞和细胞外基质的监测

使用超声波润滑实验一压电辅助摩擦试验机和光学轮廓

生物电子界面衔接与Biofabrication

创建的胶粘剂和可溶性梯度荧光显微镜成像细胞迁移

原位压极限和骨牙周韧带齿纤维联合的相关性无创成像

压电洁牙机对两种不同流动性复合填充材料的粗糙度影响

使用口腔内扫描进行体内定量牙齿磨损测量的精度

计算机辅助设计和制造粘合到铣削牙本质模拟材料的咬合贴面的准静态力学测试

计算机辅助设计和制造粘合到铣削牙本质模拟材料的咬合贴面的准静态力学测试

用 "搓 & 辊" 和非接触式轮廓术模拟和测量咬合侵蚀齿磨损

摘要

探索更多视频

此视频中的章节

黄金Nanostar合成银种子介导的生长方法

非接触，无标签使用拉曼光谱研究细胞和细胞外基质的监测

使用超声波润滑实验一压电辅助摩擦试验机和光学轮廓

生物电子界面衔接与Biofabrication

创建的胶粘剂和可溶性梯度荧光显微镜成像细胞迁移

原位压极限和骨牙周韧带齿纤维联合的相关性无创成像

压电洁牙机对两种不同流动性复合填充材料的粗糙度影响

使用口腔内扫描进行 体内 定量牙齿磨损测量的精度

计算机辅助设计和制造粘合到铣削牙本质模拟材料的咬合贴面的准静态力学测试

计算机辅助设计和制造粘合到铣削牙本质模拟材料的咬合贴面的准静态力学测试

使用口腔内扫描进行体内定量牙齿磨损测量的精度