这项工作得到了中国国家自然科学基金委员会（81601608）和NUPTSF（NY216024）的支持。

所有动物实验都是按照OG药物指南批准的动物护理和实验室动物使用指南进行的。这些议定书遵循了OG制药公司实验室动物伦理委员会的准则。
1. 纳米粒子壳微泡 （NSM） 合成
<ol><li>将磁性纳米粒子（Fe3O4，氧化铁）分散在电离水中，形成10毫克/mL的库存溶液。</li>
	<li>将含有离子溶液的管子放入超声波清洁机中 20 分钟。使用前获取均匀分散的 IONP 解决方案。</li>
	<li>添加 150 μL 的去离子水、150 μL 的 10 mM 钠硫酸钠 （SDS） 和 400 μL 的离子体库存溶液，从第 1.1 步开始。在 1.5 mL 离心机管中。</li>
	<li>在冰浴中用脚手架修复同质化器。</li>
	<li>将混合物的管子放在冰浴中，并将同质化器探针精确定位，以浸入混合物溶液中。</li>
	<li>将同质化器速度调整到 20，000 rpm，并打开同质化器 3 分钟。</li>
	<li>关闭同质化物，将管子从冰浴中取出。</li>
	<li>将管子放在管架上，在室温下稳定12小时。</li>
	<li>用磁铁将产生的 NSM 吸附到管壁上，并取出超高分子。然后补充1兆L的新鲜去离子水。</li>
	<li>重复洗涤过程三次，并在 1 mL 的新鲜蒸馏水中重新悬挂 NSM。</li>
	<li>轻微摇晃后，将 10 μL 的 NSM 悬架转移到干净的玻璃滑梯上。</li>
	<li>使用 20 倍放大倍率的荧光显微镜可视化 NSM 形态。确保在随机区域拍照。</li>
	<li>使用开放式纳米测量器 1.2 软件从照片中测量 NSM 的直径。至少计算200个微泡。<ol>
<li>单击"文件"和"打开"以选择要处理的图像文件。图像导入后，按"尺子"。绘制一条与标尺长度相同的红线。</li>
		<li>然后按"设置"|"统治者"，并进入统治者的长度。绘制与图像中单个微泡直径相同的长度的线条。完成所有测量，然后单击"报告"| 查看报告"。</li>
	</ol>
</li>
</ol>2. NSM 的声学响应
<ol><li>用 800 μL 去离子水稀释 200 μL 的 NSM，然后转移到 1.5 mL 离心机管中形成库存溶液。</li>
	<li>连接功能发生器、放大器、阻抗匹配和自制聚焦传感器。将传感器放在人工凹陷底部的中心，并将水听器与示波器连接起来，以监测输出超声波强度（图1）。将电离水加入水槽中，让传感器浸入水中。</li>
	<li>将功能发生器调整到扫描模式，调整频率范围从 10 kHz 到 900 kHz，并将振幅设置为 20 Vpp（电压峰值峰值）。通过放大器将超声波功率调整到 0.1%。每个周期的持续时间为 4s，时间间隔为 1s。</li>
	<li>在管子中准备 1 mL NSM 库存溶液样品，并在自制聚焦传感器顶部用脚手架固定管子。将磁铁连接到管子底部并吸引 NSM。</li>
	<li>打开功能发生器和放大器的电源。应用 5 个周期（25 s） 超声波后关闭功能发生器。取下磁铁并收集包含释放的 IONP 的溶液的 1 mL。在离心机管中加入 1 mL 的去离子水。</li>
	<li>重复步骤 2.5。直到管子里的 Nsm 完全崩溃</li>
	<li>通过电感耦合等离子光学发射光谱 （ICP-OES） 对所有已释放的 ION 进行量化，如前13所述。</li>
</ol>3. NSM 的光学响应
注：在这项工作中，使用了一个激光系统，包含808纳米激光功率和红外热像仪之前描述的徐等人。
<ol><li>激光系统制备<ol>
<li>打开激光的电源，让它加热几分钟。将光纤耦合 808 nm 激光二极管固定在反驳支架上。</li>
		<li>通过光纤将激光束引导到样品阶段，并聚焦在样品阶段，通过凸透镜实现 6 mm 光点（直径）。</li>
		<li>使用激光功率计测量功率输出，并将功率调整到 1 W/cm2。</li>
		<li>修复三脚架上的红外热像仪。打开相机并检查是否工作（例如，监控重点感兴趣的区域 （ROI） 温度）。关闭电源和红外热像仪。</li>
	</ol></li>
	<li>在溶液中进行光热测量<ol>
<li>在 1.5 mL 离心机管中，以不同的 IONP 浓度（1.05 毫克/毫升、1.35 毫克/mL、3.65 毫克/兆升、5 毫克/兆升）准备 1 mL 样品。</li>
		<li>将感兴趣的管子放在激光束的聚焦区域，并记录样品的基线温度。</li>
		<li>打开激光电源和红外热像仪，连续照射样品 10 分钟。同时，实时记录温度。</li>
		<li>经过 10 分钟的辐照后，关闭激光电源和红外热像仪。等待区域温度返回基线。</li>
		<li>重复 3.2.2 到 3.2.4 用于测量其他样品。 注：在 20 °C 下使用电离水作为光热测量的控制。</li>
	</ol></li>
	<li>培养细胞中的光热测量 注：Murine乳腺癌细胞（4T1）被选为研究光热治疗的抑制作用的模型。<ol>
<li>用罗斯韦尔公园纪念研究所-1640（RPMI-1640）中等补充10%的胎儿牛血清（FBS）和1%青霉素喂养细胞。将栽培环境设置为 37 °C 和 5% CO2。</li>
		<li>在T25烧瓶中培养4T1细胞，当达到90%的汇合时，以1：2的比例通过细胞。 注：亚栽培比例可根据不同实验室的特定细胞条件进行调整。</li>
		<li>删除并丢弃培养介质。用1x PBS溶液冲洗细胞层，去除含有试丁酶抑制剂的残留血清。</li>
		<li>在烧瓶中加入 2 mL 的 Trypsin-EDTA 溶液 （0.25%），用于分离。然后加入3 mL的1640中等和吸气细胞轻轻地管道。</li>
		<li>以 500 x g 收集 5 mL 的电池悬架和离心机，3 分钟。</li>
		<li>取出超高纳坦，加入1 mL的新鲜1640介质，形成细胞悬浮。</li>
		<li>将 100 μL 的电池悬架添加到包含 1 mL 培养介质的共聚焦盘中。确保细胞悬浮浓度为 9 x 105/mL，细胞培养共焦盘中的最终细胞浓度为 8.1 x 104/mL。</li>
		<li>将接种的细胞培养共聚焦盘放入孵化器中24小时。</li>
		<li>稀释不同浓度（1.05 毫克/mL，1.35 毫克/mL，3.65 毫克/mL，5 毫克/mL）的离子体样品，使 1 mL 溶液与无血清 1640 介质。</li>
		<li>从焦盘中吸气培养介质，并添加准备好的样品溶液。</li>
		<li>打开激光电源。将激光束聚焦在盘的中心，并将输出功率调整到 1 W/cm2。打开红外热像仪，连续照射焦盘中的细胞 10 分钟。实时记录重点区域的温度。</li>
		<li>关闭激光和红外热像仪。将辐照盘转移到孵化器再持续 24 小时。</li>
		<li>去除并丢弃培养介质，在共焦盘中加入 1 mL 的新鲜培养介质。在菜中加入 5 μL 的钙素-AM 溶液 （1 毫克/兆升）。</li>
		<li>在 37 °C 和 5% CO2 下孵育焦盘 15 分钟。用 1x PBS 溶液冲洗细胞层两次。</li>
		<li>通过共聚焦荧光显微镜观察和成像细胞，激发波长为488纳米，发射波长为500-540纳米。</li>
		<li>随机选择共聚焦图像中的 5 个区域，手动计算每个区域的活 4T1 细胞数量。通过比较所有实验组的活细胞数量与对照组，量化 4T1 细胞的生存能力。 注意：在 20 °C 下使用无血清 1640 介质作为光热测量的控制。使用无激光照射的样品作为细胞生存控制组。</li>
	</ol></li>
	<li>体内光热测量<ol>
<li>准备3只8周大的ICR雄性小鼠，平均体重为25±2克。</li>
		<li>在 20 mL 的去离子水中加入 2 克明胶粉末。将溶液加热到 40 - 50 °C，完全溶解明胶凝胶，形成透明清晰的溶液。</li>
		<li>从 3.4.2 中向解决方案添加 100 毫克离子。</li>
		<li>将凝胶加热到 40 ~ 50 °C，立即将 500 μL 的明胶溶液注入鼠标的右胸垫。</li>
		<li>打开激光电源，将激光束聚焦在兴趣区（小鼠的右胸垫）。将输出功率调整到 1 W/cm2。 打开红外热像仪，连续照射兴趣区 10 分钟。实时记录感兴趣的区域的温度。</li>
		<li>关闭激光和红外热像仪。</li>
		<li>通过CO2 窒息和颈椎脱位或经研究所动物研究委员会批准的任何方法对小鼠实施安乐死。</li>
	</ol></li>
</ol>4. 磁性体温过高测量
注：这里利用了吴等人以前描述的磁性高温系统（21）。
<ol><li>准备磁性高温系统包括交替磁场 （AFM） 发生器和红外热成像摄像机。<ol>
<li>打开冷水机组 10 分钟，然后在中等射频加热机上（即 AFM 发电机）上供电。</li>
		<li>将机器的参数设置为：频率 （f） = 415 kHz，磁场强度 = 1.8 kA/m。</li>
	</ol>
</li>
	<li>在溶液中的磁性体温过高测量<ol>
<li>在 1.5 mL 离心机管中，以不同的离子浓度（1.05 毫克/mL、1.35 毫克/mL、3.65 毫克/mL、5 毫克/兆升）准备 1 mL 的样品。</li>
		<li>将管子放在水冷磁感应铜线圈的中心。</li>
		<li>打开交替磁场 （AFM） 和红外热像仪。连续诱导样品10分钟，实时记录温度。 注：摄像机位于样品顶部，提供样品的横截面视图。</li>
		<li>关闭自动对焦和红外热像仪。等待铜线圈的温度回到基线 10 分钟。 注意：注意高温，避免直接接触手部，等待冷却后再取出样品。</li>
		<li>重复 4.2.2 到 4.2.4 用于测量其他样品。</li>
		<li>关闭中等射频加热机 （AFM） 和冷水机组。 注：在 20 °C 下使用去离子化水作为磁性体温过高测量的控制。</li>
	</ol>
</li>
	<li>体内磁性体温过高测量<ol>
<li>准备3只8周大的ICR雄性小鼠，平均体重为25±2克。</li>
		<li>准备 20 mL 的 10% 明胶凝胶，其中含有 5 毫克/mL IONP 溶液。</li>
		<li>将明胶凝胶加热到 40 - 50 °C，立即将 500 μL 的明胶溶液注入动物的右胸垫。 注：磁诱导体温过高实验使用与体外测试相同的参数在加热机上进行。</li>
		<li>打开交替磁场 （AFM） 和红外热像仪。将小鼠的右胸垫放在水冷磁感应铜线圈的中心。</li>
		<li>打开红外热像仪，连续拍摄 10 分钟的兴趣区域（小鼠的右乳房垫），实时记录兴趣区域的温度。</li>
		<li>感应 10 分钟后关闭机器的电源开关和红外热像仪。等待铜线圈的温度返回基线 10 分钟。</li>
		<li>重复 4.3.4 到 4.3.6 用于测量其他样品。</li>
		<li>关闭中等射频加热机 （AFM） 和冷水机组。 注意：注意高温，避免直接接触手部，等待冷却后再取出样品。</li>
		<li>通过CO2 窒息和颈椎脱位或经研究所动物研究委员会批准的任何方法对小鼠实施安乐死。</li>
	</ol>
</li>
</ol>

<ol>
	<li>Kievit, F. M., Zhang, M. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Cancer+nanotheranostics:+improving+imaging+and+therapy+by+targeted+delivery+across+biological+barriers.">Cancer nanotheranostics: improving imaging and therapy by targeted delivery across biological barriers.</a> Advanced Materials. 23 (36), 217-247 (2011).</li><li>Wu, H., 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=Fe3O4-Based+Multifunctional+Nanospheres+for+Amplified+Magnetic+Targeting+Photothermal+Therapy+and+Fenton+Reaction.">Fe3O4-Based Multifunctional Nanospheres for Amplified Magnetic Targeting Photothermal Therapy and Fenton Reaction.</a> ACS Biomaterials Science &amp; Engineering. 5 (2), 1045-1056 (2018).</li><li>Thorat, N. D., 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=Physically+stimulated+nanotheranostics+for+next+generation+cancer+therapy:+Focus+on+magnetic+and+light+stimulations.">Physically stimulated nanotheranostics for next generation cancer therapy: Focus on magnetic and light stimulations.</a> Applied Physics Reviews. 6 (4), 041306 (2019).</li><li>Sun, Q., Zhou, Z., Qiu, N., Shen, Y. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Design+of+Cancer+Nanomedicine:+Nanoproperty+Integration+and+Synchronization.">Design of Cancer Nanomedicine: Nanoproperty Integration and Synchronization.</a> Advanced Materials. 29 (14), 1606628 (2017).</li><li>Minchinton, A. I., Tannock, I. F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Drug+penetration+in+solid+tumours.">Drug penetration in solid tumours.</a> Nature Reviews Cancer. 6 (8), 583-592 (2006).</li><li>Anchordoquy, T. J., 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=Mechanisms+and+Barriers+in+Cancer+Nanomedicine:+Addressing+Challenges,+Looking+for+Solutions.">Mechanisms and Barriers in Cancer Nanomedicine: Addressing Challenges, Looking for Solutions.</a> ACS Nano. 11 (1), 12-18 (2017).</li><li>Cazares-Cortes, E., 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=Recent+insights+in+magnetic+hyperthermia:+From+the+"hot-spot"+effect+for+local+delivery+to+combined+magneto-photo-thermia+using+magneto-plasmonic+hybrids.">Recent insights in magnetic hyperthermia: From the "hot-spot" effect for local delivery to combined magneto-photo-thermia using magneto-plasmonic hybrids.</a> Advanced Drug Delivery Reviews. 138, 233-246 (2019).</li><li>Espinosa, A., 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=of+Iron+Oxide+Nanoparticles+in+Cancer+Therapy:+Amplification+of+Heating+Efficiency+by+Magnetic+Hyperthermia+and+Photothermal+Bimodal+Treatment.">of Iron Oxide Nanoparticles in Cancer Therapy: Amplification of Heating Efficiency by Magnetic Hyperthermia and Photothermal Bimodal Treatment.</a> ACS Nano. 10 (2), 2436-2446 (2016).</li><li>Rastinehad, A. R., 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=Gold+nanoshell-localized+photothermal+ablation+of+prostate+tumors+in+a+clinical+pilot+device+study.">Gold nanoshell-localized photothermal ablation of prostate tumors in a clinical pilot device study.</a> Proceedings of the National Academy of Sciences of the United States of America. 116 (37), 18590-18596 (2019).</li><li>Sharma, S. K., Shrivastava, N., Rossi, F., Tung, L. D., Thanh, N. T. K. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Nanoparticles-based+magnetic+and+photo+induced+hyperthermia+for+cancer+treatment.">Nanoparticles-based magnetic and photo induced hyperthermia for cancer treatment.</a> Nano Today. 29, 100795 (2019).</li><li>Das, R., Rinaldi-Montes, N. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Boosted+Hyperthermia+Therapy+by+Combined+AC+Magnetic+and+Photothermal+Exposures+in+Ag/Fe3O4+Nanoflowers.">Boosted Hyperthermia Therapy by Combined AC Magnetic and Photothermal Exposures in Ag/Fe3O4 Nanoflowers.</a> ACS Applied Materials &amp; Interfaces. 8 (38), 25162-25169 (2016).</li><li>Yang, Y., 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=1D+Coordination+Polymer+Nanofibers+for+Low-Temperature+Photothermal+Therapy.">1D Coordination Polymer Nanofibers for Low-Temperature Photothermal Therapy.</a> Advanced Materials. 29 (40), 1703588 (2017).</li><li>Curcio, A., 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=Iron+Oxide+Nanoflowers+CuS+Hybrids+for+Cancer+Tri-Therapy:+Interplay+of+Photothermal+Therapy,+Magnetic+Hyperthermia+and+Photodynamic+Therapy.">Iron Oxide Nanoflowers CuS Hybrids for Cancer Tri-Therapy: Interplay of Photothermal Therapy, Magnetic Hyperthermia and Photodynamic Therapy.</a> Theranostics. 9 (5), 1288-1302 (2019).</li><li>Espinosa, A., 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=Hyper)Thermia+or+Photothermia?+Progressive+Comparison+of+Iron+Oxide+and+Gold+Nanoparticles+Heating+in+Water,+in+Cells,+and+In+Vivo.">Hyper)Thermia or Photothermia? Progressive Comparison of Iron Oxide and Gold Nanoparticles Heating in Water, in Cells, and In Vivo.</a> Advanced Functional Materials. 28 (37), 1803660 (2018).</li><li>Xu, 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=Magnetic+Hyperthermia+Ablation+of+Tumors+Using+Injectable+Fe(3)O(4)/Calcium+Phosphate+Cement.">Magnetic Hyperthermia Ablation of Tumors Using Injectable Fe(3)O(4)/Calcium Phosphate Cement.</a> ACS Applied Materials &amp; Interfaces. 7 (3), 13866-13875 (2015).</li><li>Wilhelm, S., 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=Analysis+of+nanoparticle+delivery+to+tumours.">Analysis of nanoparticle delivery to tumours.</a> Nature Reviews Materials. 1, 16014 (2016).</li><li>Chen, H., Zhang, W., Zhu, G., Xie, J., Chen, X. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Rethinking+cancer+nanotheranostics.">Rethinking cancer nanotheranostics.</a> Nature Reviews Materials. 2, (2017).</li><li>Rapoport, N. Y., Kennedy, A. M., Shea, J. E., Scaife, C. L., Nam, K. H. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Controlled+and+targeted+tumor+chemotherapy+by+ultrasound-activated+nanoemulsions/microbubbles.">Controlled and targeted tumor chemotherapy by ultrasound-activated nanoemulsions/microbubbles.</a> Journal of Controlled Release : The Official Journal of the Controlled Release Society. 138 (3), 268-276 (2009).</li><li>Gao, Y., 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=Controlled+nanoparticle+release+from+stable+magnetic+microbubble+oscillations.">Controlled nanoparticle release from stable magnetic microbubble oscillations.</a> NPG Asia Materials. 8 (4), 260 (2016).</li><li>Bao, B., 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=Mussel-inspired+functionalization+of+semiconducting+polymer+nanoparticles+for+amplified+photoacoustic+imaging+and+photothermal+therapy.">Mussel-inspired functionalization of semiconducting polymer nanoparticles for amplified photoacoustic imaging and photothermal therapy.</a> Nanoscale. 11 (31), 14727-14733 (2019).</li><li>Wu, H., 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=Enhanced+Tumor+Synergistic+Therapy+by+Injectable+Magnetic+Hydrogel+Mediated+Generation+of+Hyperthermia+and+Highly+Toxic+Reactive+Oxygen+Species.">Enhanced Tumor Synergistic Therapy by Injectable Magnetic Hydrogel Mediated Generation of Hyperthermia and Highly Toxic Reactive Oxygen Species.</a> ACS Nano. 13 (12), 14013-14023 (2019).</li><li>Alzaraa, A., 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=Targeted+microbubbles+in+the+experimental+and+clinical+setting.">Targeted microbubbles in the experimental and clinical setting.</a> American Journal of Surgery. 204 (3), 355-366 (2012).</li></ol>

作者没有什么可透露的。

在这里，我们提出了一个协议，通过自组装，协同磁性，声学和光学响应性在一个纳米治疗平台制造氧化铁纳米粒子壳微泡（NSM）。IONP 被密集地包装在空气核心周围，形成磁壳，磁壳可以由外部磁场控制以进行瞄准。一旦交付，通过超声波触发器可以实现离子点的释放。释放的 IONP 可以通过 PTT 和 MHT 的 NIR 光和 AFM 激活，也可以同时激活两者的组合。
在整个协议中，NSM的合?...

癌症是最致命的疾病之一，每年在全世界造成数百万人死亡和巨大的经济损失。在诊所，传统的抗癌疗法，如手术切除，放疗和化疗仍然不能提供令人满意的治疗效果2。这些疗法的局限性是高毒副作用，高复发率和高转移率3。例如，化疗是遭受化疗药物的低交付效率正是肿瘤部位4。药物无法深入肿瘤组织跨越生物屏障，包括细胞外基质和高肿瘤间质液压，也是导致疗效低的原因。此外，肿瘤耐药性通常发生在接受单次化疗治疗的患者中。因此，发生肿瘤热消融的技术，如光热疗法（PTT）和磁性高温治疗（MHT），已经显示出了降低肿瘤抵抗力的可喜结果，并已在临床试验7，8，9中出现。
PTT通过光热转换剂在激光能量照射下的作用触发癌细胞的热消融。产生的高温（高于50°C）诱导完整的细胞坏死10。最近，氧化铁纳米粒子（IONPs）被证明是一种光热转换剂，可以通过近红外（NIR）光11激活。 尽管近红外区域的摩尔吸收系数较低，但IONP是低温（43°C）光热疗法的候选者，这是一种经过改良的疗法，旨在减少热暴露对正常组织造成的损害，并启动肿瘤转移的抗肿瘤免疫力。PTT的局限性之一是激光的低穿透深度。对于深座肿瘤，交替磁场（AFM）诱导加热的氧化铁纳米粒子，也被称为磁性高温，是PTT13，14的替代疗法。MHT的主要优点是磁场15的高渗透率。然而，需要相对较高的IONP浓度仍然是其临床应用的主要劣势。由于循环、积累和渗透等一系列障碍，纳米医学（或纳米粒子）对动物实体肿瘤的输送效率一直为1-10%。因此，具有高组织渗透能力的受控和有针对性的IONP输送策略对癌症治疗非常感兴趣。
超声介质纳米粒子的输送已经显示出它的能力，以促进纳米粒子深入肿瘤组织，由于现象称为微泡腔18，19。在本研究中，我们通过在一个纳米治疗平台中自组装、协同磁性、声学和光学响应性来制造离子体壳化微气泡（NSM）。NSM 包含空气核心和氧化铁纳米粒子壳，直径约为 5.4 μm。NSM 可以磁引导到肿瘤位点。然后，IONP 的释放由超声波触发，并伴有微泡空腔和微流。从微流获得的势头有助于离子体渗透到肿瘤组织中。PTT 和 MHT 可以通过 NIR 激光照射或 AFM 应用或两者的组合实现。

<table border="0" cellpadding="0" cellspacing="0" style="width:1331px;" width="1330">
	<colgroup>
		<col />
		<col />
		<col />
		<col />
	</colgroup>
	<tbody>
		<tr height="40">
			<td height="40" style="height:40px;width:337px;">808 nm laser power</td>
			<td style="width:315px;">Changchun New Industries Optoelectronics Tech</td>
			<td style="width:263px;">MDL-F-808-5W-18017023</td>
			<td style="width:416px;"></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Calcein-AM</td>
			<td>Thermo Fisher SCIENTIFIC</td>
			<td>C3099</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Fetal bovine serum</td>
			<td>Invitrogen</td>
			<td>16000-044</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Fluorescence Microscope</td>
			<td>Olympus</td>
			<td>IX71</td>
			<td></td>
		</tr>
		<tr height="42">
			<td height="42" style="height:42px;">Function generator</td>
			<td>Keysight</td>
			<td>33500B series</td>
			<td style="width:416px;">20 MHz, 2 channels with arbitrary waveform generation capability</td>
		</tr>
		<tr height="48">
			<td height="48" style="height:48px;">Gelatin gel</td>
			<td>Sigma</td>
			<td>9000-70-8</td>
			<td style="width:416px;"></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Heating machine</td>
			<td>Shuangping</td>
			<td>SPG-06- II</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Homemade focused transducer</td>
			<td></td>
			<td></td>
			<td>Frequency=855, R-X=36.2W+5.8W, |Z|-&#952;=37W+8&#176;</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Homogenizer</td>
			<td>SCILOGEX</td>
			<td>D-160</td>
			<td>8000-30000 rpm</td>
		</tr>
		<tr height="41">
			<td height="41" style="height:41px;">Hydrophone</td>
			<td>T&#38;C</td>
			<td>NH1000</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">ICR male mice</td>
			<td>OG Pharmaceutical. Co. Ltd</td>
			<td></td>
			<td>8-week-old</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Inductively coupled plasma optical emission spectrometry</td>
			<td>PerkinElmer</td>
			<td></td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Infrared thermal imaging camera.</td>
			<td>FLIR</td>
			<td>E50</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Iron(II,III) oxide</td>
			<td>Alfa Aesar</td>
			<td>1317-61-9</td>
			<td>50-100nm APS Powder</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Laser power meter</td>
			<td colspan="2">Changchun New Industries Optoelectronics Tech</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Oscilloscope</td>
			<td>Keysight</td>
			<td>DSOX3054T</td>
			<td>Bandwidth 500 MHz, Sampling Rate 5 GS/S, 4 channels</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">RF Power Amplifier</td>
			<td>T&#38;C</td>
			<td>AG1020</td>
			<td style="width:416px;">The signal source can also be connected to an external signal source. The gain can be adjusted from 0 to 100%. It has multiple functions such as frequency sweep, pulse, and triangle.</td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Roswell Park Memorial Institute-1640</td>
			<td>KeyGEN BioTECH</td>
			<td>KGM31800</td>
			<td></td>
		</tr>
		<tr height="40">
			<td height="40" style="height:40px;">Sodium dodecyl sulfate</td>
			<td>Sigma</td>
			<td>151-21-3</td>
			<td></td>
		</tr>
	</tbody>
</table>

magnetic-, acoustic-, and optical-triple-responsive microbubbles for magnetic hyperthermia and pothotothermal combination cancer therapy

抗癌剂的精确输送，旨在有针对性和深度渗透的分娩，以及在肿瘤部位的对照释放，已受到挑战。在这里，我们通过自组装、协同磁性、声学和光学响应性，在一个纳米治疗平台上制造氧化铁纳米粒子壳化微泡 （NSM）。氧化铁纳米粒子既可用作磁性剂，又可用作光热剂。静脉注射后，NSM可磁性引导至肿瘤位点。超声波触发氧化铁纳米粒子的释放，由于微泡的腔作用，促进纳米粒子深入肿瘤。此后，磁性高温和光热疗法可以在肿瘤上进行合并癌症治疗，这是治疗肿瘤异质性对癌症的抵抗力的一种解决方案。在本协议中，对NSM进行了合成和定性，包括结构、化学、磁性和声学特性。此外，还利用体外细胞培养物对热疗法的抗癌疗效进行了调查。拟议的分娩策略和联合治疗在癌症治疗方面有很大的希望，以提高分娩和抗癌的疗效。

本研究中使用的三响应纳米粒子壳微泡 （NSM） 是通过搅拌表面活性剂和离子体的混合物而制备的。IONP （50 nm） 在液体和气体核心的接口上自行组装，形成密集的磁壳。NSM 的形态显示在 图 1A 中。结果NSM呈现球形，平均直径为5.41±1.78μm（图1B）。结果表明，NSM的准备工作是成功的。当储存在水中时，微泡保持完好无损超过1年，并在缓冲器和细胞培养介质中稳定至少10天<s...

Watch this Scientific Journal Video about Magnetic-, Acoustic-, and Optical-Triple-Responsive Microbubbles for Magnetic Hyperthermia and Pothotothermal Combination Cancer Therapy at JoVE.com

Magnetic-, Acoustic-, and Optical-Triple-Responsive Microbubbles for Magnetic Hyperthermia and Pothotothermal Combination Cancer Therapy

这里介绍了一个协议，通过自组装，协同磁性，声学和光学响应性在一个纳米治疗平台的磁性高温和光热组合癌症治疗制造氧化铁纳米粒子壳微泡（NSMs）。

磁性、声学和光学三响应性微泡，用于磁性高温和波托托热组合癌症治疗

The precision delivery of anti-cancer agents which aim for targeted and deep-penetrated delivery as well as a controlled release at the tumor site has ...

magnetic-acoustic-optical-triple-responsive-microbubbles-for-magnetic

Research

JoVE Journal

Bioengineering

3.0K 次观看.  Nanjing University of Posts & Telecommunications. 这里介绍了一个协议，通过自组装，协同磁性，声学和光学响应性在一个纳米治疗平台的磁性高温和光热组合癌症治疗制造氧化铁纳米粒子壳微泡（NSMs）。

视频: Magnetic-, Acoustic-, and Optical-Triple-Responsive Microbubbles for Magnetic Hyperthermia and Pothotothermal Combination Cancer Therapy

Magnetic Tweezers for the Measurement of Twist and Torque

Single-molecule techniques make it possible to investigate the behavior of individual biological molecules in solution in real time. These techniques include so-called force spectroscopy approaches such as atomic force microscopy, optical tweezers, flow stretching, and magnetic tweezers. Amongst these approaches, magnetic tweezers have distinguished themselves by their ability to apply torque while maintaining a constant stretching force. Here, it is illustrated how such a &#8220;conventional&#8221; magnetic tweezers experimental configuration can, through a straightforward modification of its field configuration to minimize the magnitude of the transverse field, be adapted to measure the degree of twist in a biological molecule. The resulting configuration is termed the freely-orbiting magnetic tweezers. Additionally, it is shown how further modification of the field configuration can yield a transverse field with a magnitude intermediate between that of the &#8220;conventional&#8221; magnetic tweezers and the freely-orbiting magnetic tweezers, which makes it possible to directly measure the torque stored in a biological molecule. This configuration is termed the magnetic torque tweezers. The accompanying video explains in detail how the conversion of conventional magnetic tweezers into freely-orbiting magnetic tweezers and magnetic torque tweezers can be accomplished, and demonstrates the use of these techniques. These adaptations maintain all the strengths of conventional magnetic tweezers while greatly expanding the versatility of this powerful instrument.

Magnetic tweezers, a powerful single-molecule manipulation technique, can be adapted for the direct measurements of the twist (using a configuration called freely-orbiting magnetic tweezers) and torque (using a configuration termed magnetic torque tweezers) in biological macromolecules. Guidelines for performing such measurements are given, including applications to the study of DNA and associated nucleo-protein filaments.

磁性镊子的扭曲和扭矩的测量

Single-molecule techniques make it possible to investigate the behavior of individual biological molecules in solution in real time. These techniques ...

科研

生物工程

Fabrication of a Functionalized Magnetic Bacterial Nanocellulose with Iron Oxide Nanoparticles

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

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

一机能磁性纳米纤维素的细菌与氧化铁纳米粒子的制备

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

Custom-designed Laser-based Heating Apparatus for Triggered Release of Cisplatin from Thermosensitive Liposomes with Magnetic Resonance Image Guidance

Liposomes have been employed as drug delivery systems to target solid tumors through exploitation of the enhanced permeability and retention (EPR) effect resulting in significant reductions in systemic toxicity. Nonetheless, insufficient release of encapsulated drug from liposomes has limited their clinical efficacy. Temperature-sensitive liposomes have been engineered to provide site-specific release of drug in order to overcome the problem of limited tumor drug bioavailability. Our lab has designed and developed a heat-activated thermosensitive liposome formulation of cisplatin (CDDP), known as HTLC, to provide triggered release of CDDP at solid tumors. Heat-activated delivery in vivo was achieved in murine models using a custom-built laser-based heating apparatus that provides a conformal heating pattern at the tumor site as confirmed by MR thermometry (MRT). A fiber optic temperature monitoring device was used to measure the temperature in real-time during the entire heating period with online adjustment of heat delivery by alternating the laser power. Drug delivery was optimized under magnetic resonance (MR) image guidance by co-encapsulation of an MR contrast agent (i.e.,&#160;gadoteridol) along with CDDP into the thermosensitive liposomes as a means to validate the heating protocol and to assess tumor accumulation. The heating protocol consisted of a preheating period of 5 min prior to administration of HTLC and 20 min heating post-injection. This heating protocol resulted in effective release of the encapsulated agents with the highest MR signal change observed in the heated tumor in comparison to the unheated tumor and muscle. This study demonstrated the successful application of the laser-based heating apparatus for preclinical thermosensitive liposome development and the importance of MR-guided validation of the heating protocol for optimization of drug delivery.

AN MRI-compatible&#160;custom-designed laser-based heating apparatus has been developed to provide local heating of subcutaneous tumors in order to activate release of agents from thermosensitive liposomes specifically at the tumor region.

定制设计的基于激光的加热装置顺铂触发释放的热敏脂质体与磁共振成像制导

Liposomes have been employed as drug delivery systems to target solid tumors through exploitation of the enhanced permeability and retention (EPR) effect ...

Rapid Scan Electron Paramagnetic Resonance Opens New Avenues for Imaging Physiologically Important Parameters In Vivo

We demonstrate a superior method of 2D spectral-spatial imaging of stable radical reporter molecules at 250 MHz using rapid-scan electron-paramagnetic-resonance (RS-EPR), which can provide quantitative information under in vivo conditions on oxygen concentration, pH, redox status and concentration of signaling molecules (i.e., OH&#8226;, NO&#8226;). The RS-EPR technique has a higher sensitivity, improved spatial resolution (1 mm), and shorter acquisition time in comparison to the standard continuous wave (CW) technique. A variety of phantom configurations have been tested, with spatial resolution varying from 1 to 6 mm, and spectral width of the reporter molecules ranging from 16 &#181;T (160 mG) to 5 mT (50 G). A cross-loop bimodal resonator decouples excitation and detection, reducing the noise, while the rapid scan effect allows more power to be input to the spin system before saturation, increasing the EPR signal. This leads to a substantially higher signal-to-noise ratio than in conventional CW EPR experiments.

Rapid Scan Electron Paramagnetic Resonance Opens New Avenues for Imaging Physiologically Important Parameters In Vivo

A new electron paramagnetic resonance (EPR) method, rapid scan EPR (RS-EPR), is demonstrated for 2D spectral spatial imaging which is superior to the traditional continuous wave (CW) technique and opens new venues for in vivo imaging. Results are demonstrated at 250 MHz, but the technique is applicable at any frequency.

快速扫描电子顺磁共振打开新的途径成像生理重要参数<em&gt;在体内</em

We demonstrate a superior method of 2D spectral-spatial imaging of stable radical reporter molecules at 250 MHz using rapid-scan ...

Magnetic Levitation Coupled with Portable Imaging and Analysis for Disease Diagnostics

Currently, many clinical diagnostic procedures are complex, costly, inefficient, and inaccessible to a large population in the world. The requirements for specialized equipment and trained personnel require that many diagnostic tests be performed at remote, centralized clinical laboratories. Magnetic levitation is a simple yet powerful technique and can be applied to levitate cells, which are suspended in a paramagnetic solution and placed in a magnetic field, at a position determined by equilibrium between a magnetic force and a buoyancy force. Here, we present a versatile platform technology designed for point-of-care diagnostics which uses magnetic levitation coupled to microscopic imaging and automated analysis to determine the density distribution of a patient's cells as a useful diagnostic indicator. We present two platforms operating on this principle: (i) a smartphone-compatible version of the technology, where the built-in smartphone camera is used to image cells in the magnetic field and a smartphone application processes the images and to measures the density distribution of the cells and (ii) a self-contained version where a camera board is used to capture images and an embedded processing unit with attached thin-film-transistor (TFT) screen measures and displays the results. Demonstrated applications include: (i) measuring the altered distribution of a cell population with a disease phenotype compared to a healthy phenotype, which is applied to sickle cell disease diagnosis, and (ii) separation of different cell types based on their characteristic densities, which is applied to separate white blood cells from red blood cells for white blood cell cytometry. These applications, as well as future extensions of the essential density-based measurements enabled by this portable, user-friendly platform technology, will significantly enhance disease diagnostic capabilities at the point of care.

We present a magnetic levitation technique coupled with automated imaging and analysis in both a smartphone-compatible device and a device with embedded imaging and processing. This is applied to measure the density distribution of cells with two demonstrated biomedical applications: sickle cell disease diagnosis and separating white and red blood cells.

磁悬浮加上便携式成像与分析诊断疾病

Currently, many clinical diagnostic procedures are complex, costly, inefficient, and inaccessible to a large population in the world. The requirements for ...

3D Magnetic Stem Cell Aggregation and Bioreactor Maturation for Cartilage Regeneration

Cartilage engineering remains a challenge due to the difficulties in creating an in vitro functional implant similar to the native tissue. An approach recently explored for the development of autologous replacements involves the differentiation of stem cells into chondrocytes. To initiate this chondrogenesis, a degree of compaction of the stem cells is required; hence, we demonstrated the feasibility of magnetically condensing cells, both within thick scaffolds and scaffold-free, using miniaturized magnetic field sources as cell attractors. This magnetic approach was also used to guide aggregate fusion and to build scaffold-free, organized, three-dimensional (3D) tissues several millimeters in size. In addition to having an enhanced size, the tissue formed by magnetic-driven fusion presented a significant increase in the expression of collagen II, and a similar trend was observed for aggrecan expression. As the native cartilage was subjected to forces that influenced its 3D structure, dynamic maturation was also performed. A bioreactor that provides mechanical stimuli was used to culture the magnetically seeded scaffolds over a 21-day period. Bioreactor maturation largely improved chondrogenesis into the cellularized scaffolds; the extracellular matrix obtained under these conditions was rich in collagen II and aggrecan. This work outlines the innovative potential of magnetic condensation of labeled stem cells and dynamic maturation in a bioreactor for improved chondrogenic differentiation, both scaffold-free and within polysaccharide scaffolds.

Chondrogenesis from stem cells requires fine tuning the culture conditions. Here, we present a magnetic approach for condensing cells, an essential step to initiate chondrogenesis. In addition, we show that dynamic maturation in a bioreactor applies mechanical stimulation to the cellular constructs and enhances cartilaginous extracellular matrix production.

3D磁干细胞聚集和生物反应器为成熟软骨再生

Cartilage engineering remains a challenge due to the difficulties in creating an in vitro functional implant similar to the native tissue. An approach ...

Magnetic and Thermal-sensitive Poly(N-isopropylacrylamide)-based Microgels for Magnetically Triggered Controlled Release

Magnetically and thermally sensitive poly(N-isopropylacrylamide) (PNIPAAm)/Fe3O4-NH2 microgels with the encapsulated anti-cancer drug curcumin (Cur) were designed and fabricated for magnetically triggered release. PNIPAAm-based magnetic microgels with a spherical structure were produced via a temperature-induced emulsion followed with physical-crosslinking by mixing PNIPAAm, polyethylenimine (PEI), and Fe3O4-NH2 magnetic nanoparticles. Because of their dispersity, the Fe3O4-NH2 nanoparticles were embedded inside the polymer matrix. The amine groups exposed on the Fe3O4-NH2 and PEI surface supported the spherical structure by physically crosslinking with the amide groups of the PNIPAAm. The hydrophobic anti-cancer drug curcumin can be dispersed in water after encapsulation into the microgels. The microgels were characterized by transmission electron microscopy (TEM), Fourier transform infrared spectroscopy (FT-IR), and UV-Vis spectral analysis. Furthermore, magnetically triggered release was studied under an external high frequency magnetic field (HFMF). A significant &#34;burst release&#34; of curcumin was observed after applying the HFMF to the microgels due to the magnetic inductive heating (hyperthermia) effect. This manuscript describes the magnetically triggered controlled release of Cur-PNIPAAm/Fe3O4-NH2 encapsulated curcumin, which can be potentially applied for tumor therapy.

Magnetic and Thermal-sensitive PolyN-isopropylacrylamide-based Microgels for Magnetically Triggered Controlled Release

This manuscript describes the preparation of magnetic and thermal-sensitive microgels via a temperature-induced emulsion without chemical reaction. These sensitive microgels were synthesized by mixing poly(N-isopropylacrylamide) (PNIPAAm), polyethylenimine (PEI) and Fe3O4-NH2 nanoparticles for the potential use in magnetically and thermally triggered drug-release.

磁性和热敏性聚（<em&gt;ñ</em基于异丙基丙烯酰胺）的微凝胶用于磁触发控制释放

Magnetically and thermally sensitive poly(N-isopropylacrylamide) (PNIPAAm)/Fe3O4-NH2 microgels with the encapsulated anti-cancer drug curcumin (Cur) were ...

Metabolic Support of Excised, Living Brain Tissues During Magnetic Resonance Microscopy Acquisition

This protocol describes the procedures necessary to support normal metabolic functions of acute brain slice preparations during the collection of magnetic resonance (MR) microscopy data. While it is possible to perform MR collections on living, excised mammalian tissue, such experiments have traditionally been constrained by resolution limits and are thus incapable of visualizing tissue microstructure. Conversely, MR protocols that did achieve microscopic image resolution required the use of fixed samples to accommodate the need for static, unchanging conditions over lengthy scan times. The current protocol describes the first available MR technique that enables imaging of living, mammalian tissue samples at microscopic resolutions. Such data is of great importance to the understanding of how pathology-based contrast changes occurring at the microscopic level influence the content of macroscopic MR scans such as those used in the clinic. Once such an understanding is realized, diagnostic methods with greater sensitivity and accuracy can be developed, which will translate directly to earlier disease treatment, more accurate therapy monitoring and improved patient outcomes.
While the described methodology focuses on brain slice preparations, the protocol is adaptable to any excised tissue slice given that changes are made to the gas and perfusate preparations to accommodate the tissue&#39;s specific metabolic needs. Successful execution of the protocol should result in living, acute slice preparations that exhibit MR diffusion signal stability for periods up to 15.5 h. The primary advantages of the current system over other MR compatible perfusion apparatuses are its compatibility with the MR microscopy hardware required to attain higher resolution images and ability to provide constant, uninterrupted flow with carefully regulated perfusate conditions. Reduced sample throughput is a consideration with this design as only one tissue slice may be imaged at a time.

The current protocol describes a method by which users can maintain viability of acute hippocampal and cortical slice preparations during the collection of magnetic resonance microscopy data.

磁共振显微镜下切除活体脑组织的代谢支持

This protocol describes the procedures necessary to support normal metabolic functions of acute brain slice preparations during the collection of magnetic ...

Optimized Setup and Protocol for Magnetic Domain Imaging with In Situ Hysteresis Measurement

This paper elaborates the sample preparation protocols required to obtain optimal domain patterns using the Bitter method, focusing on the extra steps compared to standard metallographic sample preparation procedures. The paper proposes a novel bespoke rig for dynamic domain imaging with in situ BH (magnetic hysteresis) measurements and elaborates the protocols for the sensor preparation and the use of the rig to ensure accurate BH measurement. The protocols for static and ordinary dynamic domain imaging (without in situ BH measurements) are also presented. The reported method takes advantage of the convenience and high sensitivity of the traditional Bitter method and enables in situ BH measurement without interrupting or interfering with the domain wall movement processes. This facilitates establishing a direct and quantitative link between the domain wall movement processes&#8211;microstructural feature interactions in ferritic steels with their BH loops. This method is anticipated to become a useful tool for the fundamental study of microstructure&#8211;magnetic property relationships in steels and to help interpret the electromagnetic sensor signals for non-destructive evaluation of steel microstructures.

Optimized Setup and Protocol for Magnetic Domain Imaging with In Situ Hysteresis Measurement

This paper elaborates the sample and sensor preparation procedures and the protocols for using the test rig particularly for dynamic domain imaging with in situ BH measurements in order to achieve optimal domain pattern quality and accurate BH measurements.

用原位滞后测量进行磁畴成像的优化设置和协议

This paper elaborates the sample preparation protocols required to obtain optimal domain patterns using the Bitter method, focusing on the extra steps ...

Protocol for MicroRNA Transfer into Adult Bone Marrow-derived Hematopoietic Stem Cells to Enable Cell Engineering Combined with Magnetic Targeting

While CD133+ hematopoietic stem cells (SCs) have been proven to provide high potential in the field of regenerative medicine, their low retention rates after injection into injured tissues as well as the observed massive cell death rates lead to very restricted therapeutic effects. To overcome these limitations, we sought to establish a non-viral based protocol for suitable cell engineering prior to their administration. The modification of human CD133+ expressing SCs using microRNA (miR) loaded magnetic polyplexes was addressed with respect to uptake efficiency and safety as well as the targeting potential of the cells. Relying on our protocol, we can achieve high miR uptake rates of 80&#8211;90% while the CD133+ stem cell properties remain unaffected. Moreover, these modified cells offer the option of magnetic targeting. We describe here a safe and highly efficient procedure for the modification of CD133+ SCs. We expect this approach to provide a standard technology for optimization of therapeutic stem cell effects and for monitoring of the administered cell product via magnetic resonance imaging (MRI).

This protocol illustrates a safe and efficient procedure to modify CD133+ hematopoietic stem cells. The presented non-viral, magnetic polyplex-based approach may provide a basis for the optimization of therapeutic stem cell effects as well as for monitoring the administered cell product via magnetic resonance imaging.

MicroRNA 移植成人骨髓造血干细胞促进细胞工程与磁性靶向结合的协议

While CD133+ hematopoietic stem cells (SCs) have been proven to provide high potential in the field of regenerative medicine, their low retention rates ...