Name: development of a low-cost epimysial electromyography electrode: a simplified workflow for fabrication and testing
Uploaded: 2024-04-12T14:50:00.000+00:00
Duration: 4 min 48 s
Description: Read this Scientific Article Protocol about Author Spotlight: Epimysial Electrode Fabrication and Testing in ACL Injury Studies at JoVE.com

<meta charset="utf8"></head><body> 为临床前啮齿动物模型制造肌外肌电图电极

<ol>
	<li>Grandjean, P. A., Mortimer, J. T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Recruitment+properties+of+monopolar+and+bipolar+epimysial+electrodes.">Recruitment properties of monopolar and bipolar epimysial electrodes.</a> Ann. Biomed. Eng. 14 (1), 53-66 (1986).</li><li>Memberg, W. D., Stage, T. G., Kirsch, R. F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+fully+implanted+intramuscular+bipolar+myoelectric+signal+recording+electrode.">A fully implanted intramuscular bipolar myoelectric signal recording electrode.</a> Neuromodulation J. Int. Neuromodulation Soc. 17 (8), 794-799 (2014).</li><li>Loeb, G. E., Gans, C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=.">.</a> Electromyography for Experimentalists. , (1986).</li><li>Boehler, C., Carli, S., Fadiga, L., Stieglitz, T., Asplund, M. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Tutorial:+guidelines+for+standardized+performance+tests+for+electrodes+intended+for+neural+interfaces+and+bioelectronics.">Tutorial: guidelines for standardized performance tests for electrodes intended for neural interfaces and bioelectronics.</a> Nat. Protoc. 15 (11), 3557-3578 (2020).</li><li>Patel, P. 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=Insertion+of+linear+8.4+&#181;m+diameter+16+channel+carbon+fiber+electrode+arrays+for+single+unit+recordings.">Insertion of linear 8.4 &#181;m diameter 16 channel carbon fiber electrode arrays for single unit recordings.</a> J. Neural Eng. 12 (4), 046009 (2015).</li><li>Richie, J. M., 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=Open-source+toolkit:+benchtop+carbon+fiber+microelectrode+array+for+nerve+recording.">Open-source toolkit: benchtop carbon fiber microelectrode array for nerve recording.</a> J. Vis. Exp. (176), e63099 (2021).</li><li>Sarolic, A., Skalic, I., Deftu, A., Sapunar, D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Impedance+measurement+of+bipolar+stimulation+electrodes+immersed+in+medium.">Impedance measurement of bipolar stimulation electrodes immersed in medium.</a> , 1-2 (2018).</li><li>Pritchett-Corning, K. R., Mulder, G. B., Luo, Y., White, W. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Principles+of+rodent+surgery+for+the+New+Surgeon.">Principles of rodent surgery for the New Surgeon.</a> J. Vis. Exp.: JoVE. (47), e2586 (2011).</li><li>Zealear, D., Li, Y., Huang, S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=An+implantable+system+for+chronic+in+vivo+electromyography.">An implantable system for chronic in vivo electromyography.</a> J. Vis. Exp. JoVE. (158), e60345 (2020).</li><li>Butterfield, T. A., Leonard, T. R., Herzog, W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Differential+serial+sarcomere+number+adaptations+in+knee+extensor+muscles+of+rats+is+contraction+type+dependent.">Differential serial sarcomere number adaptations in knee extensor muscles of rats is contraction type dependent.</a> J. Appl. Physiol. Bethesda Md 1985. 99 (4), 1352-1358 (2005).</li><li>Farago, E., MacIsaac, D., Suk, M., Chan, A. D. C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=A+review+of+techniques+for+surface+electromyography+signal+quality+analysis.">A review of techniques for surface electromyography signal quality analysis.</a> IEEE Rev. Biomed. Eng. 16, 472-486 (2023).</li><li>Raez, M. B. I., Hussain, M. S., Mohd-Yasin, F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Techniques+of+EMG+signal+analysis:+detection,+processing,+classification+and+applications.">Techniques of EMG signal analysis: detection, processing, classification and applications.</a> Biol. Proced. Online. 8, 11-35 (2006).</li><li>Tankisi, 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=Standards+of+instrumentation+of+EMG.">Standards of instrumentation of EMG.</a> Clin. Neurophysiol. 131 (1), 243-258 (2020).</li><li>Kumar, A., Accorsi, A., Younghwa, R., Mahasweta, G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Do's+and+don'ts+in+the+preparation+of+muscle+cryosections+for+histological+analysis.">Do's and don'ts in the preparation of muscle cryosections for histological analysis.</a> J. Vis. Exp. JoVE. (99), e52793 (2015).</li><li>Wang, C., Yue, F., Kuang, S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Muscle+histology+characterization+using+H&amp;E+staining+and+muscle+fiber+type+classification+using+immunofluorescence+staining.">Muscle histology characterization using H&amp;E staining and muscle fiber type classification using immunofluorescence staining.</a> Bio-Protoc. 7 (10), e2279 (2017).</li><li>Kreifeldt, J. G. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Signal+versus+noise+characteristics+of+filtered+EMG+used+as+a+control+source.">Signal versus noise characteristics of filtered EMG used as a control source.</a> IEEE Trans. Biomed. Eng. BME-18 (1), 16-22 (1971).</li><li>Farina, D., Yoshida, K., Stieglitz, T., Koch, K. P. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Multichannel+thin-film+electrode+for+intramuscular+electromyographic+recordings.">Multichannel thin-film electrode for intramuscular electromyographic recordings.</a> J. Appl. Physiol. 104 (3), 821-827 (2008).</li><li>Muceli, 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=Decoding+motor+neuron+activity+from+epimysial+thin-film+electrode+recordings+following+targeted+muscle+reinnervation.">Decoding motor neuron activity from epimysial thin-film electrode recordings following targeted muscle reinnervation.</a> J. Neural Eng. 16 (1), 016010 (2018).</li><li>Guo, L., Guvanasen, G., Tuthill, C., Nichols, T., Deweerth, S. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=.">.</a> Characterization of a Stretchable Multielectrode Array for Epimysial Recording. , 694 (2011).</li><li>Zwarts, M. J., Stegeman, D. F. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Multichannel+surface+EMG:+basic+aspects+and+clinical+utility.">Multichannel surface EMG: basic aspects and clinical utility.</a> Muscle Nerve. 28 (1), 1-17 (2003).</li><li>Koch, K. P., Leinenbach, C., Stieglitz, T. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Fabrication+and+test+of+robust+spherical+epimysial+electrodes+for+lower+limb+stimulation.">Fabrication and test of robust spherical epimysial electrodes for lower limb stimulation.</a> Aalb. Den. , (2000).</li><li>Uhlir, J. P., Triolo, R. J., Davis, J. A., Bieri, C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Performance+of+epimysial+stimulating+electrodes+in+the+lower+extremities+of+individuals+with+spinal+cord+injury.">Performance of epimysial stimulating electrodes in the lower extremities of individuals with spinal cord injury.</a> IEEE Trans. Neural Syst. Rehabil. Eng. 12 (2), 279-287 (2004).</li><li>Deer, T. 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=The+appropriate+use+of+neurostimulation:+new+and+evolving+neurostimulation+therapies+and+applicable+treatment+for+chronic+pain+and+selected+disease+states.">The appropriate use of neurostimulation: new and evolving neurostimulation therapies and applicable treatment for chronic pain and selected disease states.</a> Neuromodulation Technol. Neural Interface. 17 (6), 599-615 (2014).</li><li>Ortiz-Catalan, M., Br&#229;nemark, R., H&#229;kansson, B., Delbeke, J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=On+the+viability+of+implantable+electrodes+for+the+natural+control+of+artificial+limbs:+Review+and+discussion.">On the viability of implantable electrodes for the natural control of artificial limbs: Review and discussion.</a> Biomed. Eng. OnLine. 11, 33 (2012).</li><li>Sando, I. 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=Regenerative+peripheral+nerve+interface+for+prostheses+control:+electrode+comparison.">Regenerative peripheral nerve interface for prostheses control: electrode comparison.</a> J. Reconstr. Microsurg. 32 (3), 194-199 (2016).</li></ol>

<table><tbody><tr><td>&lt;strong&gt;Electrode Materials&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>&amp;nbsp; &amp;nbsp;</td><td>&amp;nbsp; &amp;nbsp;</td><td>&amp;nbsp; &amp;nbsp;</td><td>&lt;strong&gt;Quantity &amp;amp; price per electrode&lt;/strong&gt;</td></tr><tr><td>Contact surface</td><td>Prince and Izant PT90/IR10 1.25 mm x 5 mm foil</td><td>Catalog #1040055&amp;nbsp;</td><td>2 per electrode&lt;br/&gt; $7.50 per foil&lt;br/&gt; $15.00 per electrode</td></tr><tr><td>PFA coated stainless-steel electrode lead wire&amp;nbsp;</td><td>A-M Systems Multi-Stranded PFA-Coated Stainless Steel Wire 50.8 &amp;micro;m strand diameter&amp;nbsp;</td><td>Catalog #793500</td><td>Dependent on desired lead length (e.g., 9 inch lead wires x2)&lt;br/&gt; $128 per 25 ft spool&lt;br/&gt; $5.12 per foot&lt;br/&gt; $0.42 per inch (x18)&lt;br/&gt; $7.68 per electrode</td></tr><tr><td>Folding jig&amp;nbsp;</td><td>3D printed&lt;br/&gt; (see .gcode file)</td><td>NA</td><td>NA</td></tr><tr><td>Sealant for electrode body</td><td>Nusil Med-1137 liquid silicone</td><td>Catalog #MED-1137</td><td>1 gram&lt;br/&gt; $344.66 per 2 oz. (59.15 mL)&lt;br/&gt; $5.83 per electrode</td></tr><tr><td>Silicone base</td><td>Implantech Alliedsil Silicone Sheeting-Reinforced, Long Term Implantable (8&amp;rdquo; x 6&amp;rdquo;) .007 thick</td><td>Catalog #701-07&amp;nbsp;</td><td>10mm x 5mm sheet&lt;br/&gt; $225.00 per 8 x 6 inch&lt;br/&gt; $0.36 per electrode (10 mm x 5 mm)</td></tr><tr><td>&amp;nbsp;Thinner for sealant mixture</td><td>Toluene 99.5% ACS Reagent 500mL or Xylene ACS 99.5%</td><td>Catalog #179418-500 ML</td><td>0.75 mL&lt;br/&gt; $25.53 per 500 mL&lt;br/&gt; $0.38 per electrode</td></tr><tr><td>Template for perforating silicone base</td><td>Cutting jig &amp;ndash; 3D printed&lt;br/&gt; (see CAD file)</td><td>NA</td><td>NA</td></tr><tr><td>Custom-fabricated electrode: &lt;strong&gt;$29.25&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>Industry standard electrode (EP105 EMG Patch Electrode, 2 contacts, single-sided, 7mm x 4mm, MicroProbe for Life Science): $305.00</td><td></td><td></td><td></td></tr><tr><td>&lt;strong&gt;Additional Fabrication Materials&amp;nbsp;&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>&amp;nbsp; &amp;nbsp;&amp;nbsp;</td><td>&amp;nbsp; &amp;nbsp;&amp;nbsp;</td><td>&amp;nbsp; &amp;nbsp;&amp;nbsp;</td><td>&lt;strong&gt;Quantity &amp;amp; price per electrode&lt;/strong&gt;</td></tr><tr><td>3D printing software&amp;nbsp;</td><td>Solidworks (Solidworks, 2022)</td><td></td><td></td></tr><tr><td>Micro-Tig welder&amp;nbsp;</td><td>Micro-Tig Welder (CD1000SPM, Single Pulse Research and Light Production Resistance Spot Welder, Sunstone)</td><td>SKU&amp;nbsp;301010</td><td>$3,500</td></tr><tr><td>Ultrasonic bath</td><td>Ultrasonic bath (CPX Series Ultrasonic Bath, Fisherbrand).&amp;nbsp;</td><td>15-337-403</td><td>NA</td></tr><tr><td>&lt;strong&gt;Ex Vivo Testing Materials&amp;nbsp;&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>&amp;nbsp; &amp;nbsp;</td><td>&amp;nbsp; &amp;nbsp;</td><td>&amp;nbsp; &amp;nbsp;</td><td>&lt;strong&gt;Quantity &amp;amp; price per electrode&lt;/strong&gt;</td></tr><tr><td>Data acquisition platform and software</td><td>DigitalLynx 4sX Base Cheetah version 6.0 (Neuralynx Inc.)&amp;nbsp;</td><td>NA</td><td>EMG acquisition hardware and software</td></tr><tr><td>Electrode interface board (EIB)</td><td>EIB, EIB16-QC, Neuralynx Inc.</td><td>31-0603-0007</td><td>NA</td></tr><tr><td>Signal generator</td><td>5 MHz Function Generator, B&amp;amp;K Precision&amp;nbsp;</td><td>&amp;nbsp;4005DDS220V</td><td>$387.46</td></tr><tr><td>Potentiostat</td><td>PGSTAT1 potentiostat (EcoChemie, Utrecht, Netherlands)</td><td>NA</td><td>NA</td></tr><tr><td>Stainless steel screw</td><td>Fine Science Tools</td><td>19010-00</td><td>$98</td></tr><tr><td>&lt;strong&gt;Ex Vivo Testing Materials&amp;nbsp;&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>&amp;nbsp; &amp;nbsp;</td><td>&amp;nbsp; &amp;nbsp;</td><td>&amp;nbsp; &amp;nbsp;</td><td>&lt;strong&gt;Quantity &amp;amp; price per electrode&lt;/strong&gt;</td></tr><tr><td>Rodent treadmill&amp;nbsp;</td><td>Exer 3/6 Open Treadmill, Columbus Instruments</td><td>NA</td><td>NA</td></tr><tr><td>Dental cement</td><td>Excel Formula&amp;reg; Pourable Dental Material, St. George Technology Inc.</td><td>#24211</td><td>$125.60</td></tr><tr><td>Light microscope</td><td>Keyence BZ-X800, Keyence Corporation, Osaka, Japan&amp;nbsp;</td><td>NA</td><td>NA</td></tr><tr><td>Motion capture system</td><td>Optitrack Color Camera, Optitrack, NaturalPoint Inc.</td><td>NA</td><td>NA</td></tr><tr><td>Peak detection algorithm</td><td>&amp;ldquo;SciPy.signal.find_peaks - SciPy v1.8.1 Manual&amp;rdquo;, 2022</td><td>NA</td><td>NA</td></tr><tr><td>Python software</td><td>Python Software Foundation. Python Language Reference, version 3.9. Available at http://www.python.org</td><td>NA</td><td>NA</td></tr><tr><td>Rat</td><td>HsdBlu: LE, Envigo</td><td>140</td><td>NA</td></tr><tr><td>Statistical sotware</td><td>GraphPad Prism version 10.0.0 (GraphPad Software, Boston, Massachusetts USA)</td><td>NA</td><td>NA</td></tr></tbody></table>

development of a low-cost epimysial electromyography electrode: a simplified workflow for fabrication and testing

Read this Scientific Article Protocol about Author Spotlight: Epimysial Electrode Fabrication and Testing in ACL Injury Studies at JoVE.com

<meta charset="utf8"></head><body>作者聚焦:ACL 损伤研究中的肌外膜电极制造和测试

低成本肌外肌电图电极的开发:简化的制造和测试工作流程

Electromyography (EMG) is a valuable diagnostic tool for detecting neuromuscular abnormalities. Implantable epimysial electrodes are commonly used to ...

development-low-cost-epimysial-electromyography-electrode-simplified

Research

JoVE Journal

Neuroscience

Development of a Low-cost Epimysial Electromyography Electrode: A Simplified Workflow for Fabrication and Testing

372 次观看.  University of Michigan, Ann Arbor. 我们试图使用临床前啮齿动物模型了解 ACL 损伤的神经肌肉和电生理后果。我们目前的实验使用植入式肌外肌电图电极来研究非侵入性 ACL 损伤如何改变股四头肌激活。尽管存在详细介绍电极制造和测试注意事项的基本资源，但我们旨在为现代电生理学实验室提供更新的、易于遵循的附加电极制造和测试指南。我们的目标是简化肌外肌电图的制?...

视频: 作者聚焦:ACL 损伤研究中的肌外膜电极制造和测试

Spinal Cord Electrophysiology II: Extracellular Suction Electrode Fabrication

Development of neural circuitries and locomotion can be studied using neonatal rodent spinal cord central pattern generator (CPG) behavior. We demonstrate a method to fabricate suction electrodes that are used to examine CPG activity, or fictive locomotion, in dissected rodent spinal cords. The rodent spinal cords are placed in artificial cerebrospinal fluid and the ventral roots are drawn into the suction electrode. The electrode is constructed by modifying a commercially available suction electrode. A heavier silver wire is used instead of the standard wire given by the commercially available electrode. The glass tip on the commercial electrode is replaced with a plastic tip for increased durability. We prepare hand drawn electrodes and electrodes made from specific sizes of tubing, allowing consistency and reproducibility. Data is collected using an amplifier and neurogram acquisition software. Recordings are performed on an air table within a Faraday cage to prevent mechanical and electrical interference, respectively.

A demonstration of the fabrication and use of an extracellular suction electrode used to measure electrophysiological recordings of neonatal rodent spinal cords in vitro

脊髓电二：外吸电极的制作

Development of neural circuitries and locomotion can be studied using neonatal rodent spinal cord central pattern generator (CPG) behavior. We demonstrate ...

科研

神经科学

Hollow Microneedle-based Sensor for Multiplexed Transdermal Electrochemical Sensing

The development of a minimally invasive multiplexed monitoring system for rapid analysis of biologically-relevant molecules could offer individuals suffering from chronic medical conditions facile assessment of their immediate physiological state. Furthermore, it could serve as a research tool for analysis of complex, multifactorial medical conditions. In order for such a multianalyte sensor to be realized, it must be minimally invasive, sampling of interstitial fluid must occur without pain or harm to the user, and analysis must be rapid as well as selective.
Initially developed for pain-free drug delivery, microneedles have been used to deliver vaccines and pharmacologic agents (e.g., insulin) through the skin.1-2 Since these devices access the interstitial space, microneedles that are integrated with microelectrodes can be used as transdermal electrochemical sensors. Selective detection of glucose, glutamate, lactate, hydrogen peroxide, and ascorbic acid has been demonstrated using integrated microneedle-electrode devices with carbon fibers, modified carbon pastes, and platinum-coated polymer microneedles serving as transducing elements.3-7,8
This microneedle sensor technology has enabled a novel and sophisticated analytical approach for in situ and simultaneous detection of multiple analytes. Multiplexing offers the possibility of monitoring complex microenvironments, which are otherwise difficult to characterize in a rapid and minimally invasive manner. For example, this technology could be utilized for simultaneous monitoring of extracellular levels of, glucose, lactate and pH,9 which are important metabolic indicators of disease states7,10-14 (e.g., cancer proliferation) and exercise-induced acidosis.15

This article details the construction of a multiplexed microneedle-based sensor. The device is being developed for in situ sampling and electrochemical analysis of multiple analytes in a rapid and selective manner. We envision clinical medicine and biomedical research uses for these microneedle-based sensors.

复透皮电化学传感的空心微针为基础的传感器

The development of a minimally invasive multiplexed monitoring system for rapid analysis of biologically-relevant molecules could offer individuals ...

生物工程

Scalable Solution-processed Fabrication Strategy for High-performance, Flexible, Transparent Electrodes with Embedded Metal Mesh

Here, the authors report the embedded metal-mesh transparent electrode (EMTE), a new transparent electrode (TE) with a metal mesh completely embedded in a polymer film. This paper also presents a low-cost, vacuum-free fabrication method for this novel TE; the approach combines lithography, electroplating, and imprint transfer (LEIT) processing. The embedded nature of the EMTEs offers many advantages, such as high surface smoothness, which is essential for organic electronic device production; superior mechanical stability during bending; favorable resistance to chemicals and moisture; and strong adhesion with plastic film. LEIT fabrication features an electroplating process for vacuum-free metal deposition and is favorable for industrial mass production. Furthermore, LEIT allows for the fabrication of metal mesh with a high aspect ratio (i.e., thickness to linewidth), significantly enhancing its electrical conductance without adversely losing optical transmittance. We demonstrate several prototypes of flexible EMTEs, with sheet resistances lower than 1 &#937;/sq and transmittances greater than 90%, resulting in very high figures of merit (FoM) &#8211; up to 1.5 x 104 &#8211; which are amongst the best values in the published literature.

This protocol describes a solution-based fabrication strategy for high-performance, flexible, transparent electrodes with fully-embedded, thick metal mesh. Flexible transparent electrodes fabricated by this process demonstrate among the highest reported performances, including ultra-low sheet resistance, high optical transmittance, mechanical stability under bending, strong substrate adhesion, surface smoothness, and environmental stability.

具有嵌入式金属网的高性能，灵活，透明电极的可扩展解决方案处理制造策略

Here, the authors report the embedded metal-mesh transparent electrode (EMTE), a new transparent electrode (TE) with a metal mesh completely embedded in a ...

工程学

Wireless Intramuscular EMG System for Locomotion Studies in Stroke Model Rats

A Real-Time Wearable Electromyography Measurement System for Small Animals

The intramuscular electromyography (EMG) measurement method for experimental animals has been implemented in various ways. Among these methods, tethering cables to external measurement devices can restrict the movement of experimental animals, while implantable devices may cause unwanted side effects due to the constant presence of a device with considerable size and weight. To address these issues, we propose a low-cost, wireless, detachable EMG measurement system and experimental procedure. This article focuses on the surgical installation of intramuscular wire electrodes with small connectors and the development of the wireless system. Notably, in this system, only the wire electrodes are inserted into the animal's body. Using this system, EMG measurements can be easily performed by attaching the circuit system to a connector installed on the animal's back, with real-time monitoring achievable on a laptop. The proposed method is explained in a detailed, step-by-step manner, followed by a demonstration involving the insertion of intramuscular electrodes into the hindlimbs of a rat. A treadmill experiment is conducted for a locomotion study, and the resulting electrophysiological signals are subsequently obtained and analyzed.

A protocol is presented for the installation and preparation of intramuscular electrodes, along with an animal-mountable, miniaturized measurement device for electromyography (EMG) analysis in locomotion studies. This system enables the wireless transmission of real-time EMG data for investigating locomotion recovery in stroke model rats.

The intramuscular electromyography (EMG) measurement method for experimental animals has been implemented in various ways. Among these methods, tethering ...

Fabrication of High Contact-Density, Flat-Interface Nerve Electrodes for Recording and Stimulation Applications

Many attempts have been made to manufacture multi-contact nerve cuff electrodes that are safe, robust and reliable for long term neuroprosthetic applications. This protocol describes a fabrication technique of a modified cylindrical nerve cuff electrode to meet these criteria. Minimum computer-aided design and manufacturing (CAD and CAM) skills are necessary to consistently produce cuffs with high precision (contact placement 0.51 &#177; 0.04 mm) and various cuff sizes. The precision in spatially distributing the contacts and the ability to retain a predefined geometry accomplished with this design are two criteria essential to optimize the cuff&#39;s interface for selective recording and stimulation. The presented design also maximizes the flexibility in the longitudinal direction while maintaining sufficient rigidity in the transverse direction to reshape the nerve by using materials with different elasticities. The expansion of the cuff&#39;s cross sectional area as a result of increasing the pressure inside the cuff was observed to be 25% at 67 mm Hg. This test demonstrates the flexibility of the cuff and its response to nerve swelling post-implant. The stability of the contacts&#39; interface and recording quality were also examined with contacts&#39; impedance and signal-to-noise ratio metrics from a chronically implanted cuff (7.5 months), and observed to be 2.55 &#177; 0.25 k&#8486; and 5.10 &#177; 0.81 dB respectively.

This article provides a detailed description on the fabrication process of a high contact-density flat interface nerve electrode (FINE). This electrode is optimized for recording and stimulating neural activity selectively within peripheral nerves.

高接触密度的制作，平面接口神经电极用于记录和刺激的应用

Many attempts have been made to manufacture multi-contact nerve cuff electrodes that are safe, robust and reliable for long term neuroprosthetic ...

High-density Electroencephalographic Acquisition in a Rodent Model Using Low-cost and Open-source Resources

Advanced electroencephalographic analysis techniques requiring high spatial resolution, including electrical source imaging and measures of network connectivity, are applicable to an expanding variety of questions in neuroscience. Performing these kinds of analyses in a rodent model requires higher electrode density than traditional screw electrodes can accomplish. While higher-density electroencephalographic montages for rodents exist, they are of limited availability to most researchers, are not robust enough for repeated experiments over an extended period of time, or are limited to use in anesthetized rodents.1-3 A proposed low-cost method for constructing a durable, high-count, transcranial electrode array, consisting of bilaterally implantable headpieces is investigated as a means to perform advanced electroencephalogram analyses in mice or rats.

Procedures for headpiece fabrication and surgical implantation necessary to produce high signal to noise, low-impedance electroencephalographic and electromyographic signals are presented. While the methodology is useful in both rats and mice, this manuscript focuses on the more challenging implementation for the smaller mouse skull. Freely moving mice are only tethered to cables via a common adapter during recording. One version of this electrode system that includes 26 electroencephalographic channels and 4 electromyographic channels is described below.

Instructions for the low-cost construction and surgical implantation of a chronic transcranial high-density electroencephalographic montage into mice are provided. Signal recording, extraction, and processing techniques are also described.

高密度的脑电图采集在啮齿动物模型使用低成本的开源资源

Advanced electroencephalographic analysis techniques requiring high spatial resolution, including electrical source imaging and measures of network ...

Fabrication of Fine Electrodes on the Tip of Hypodermic Needle Using Photoresist Spray Coating and Flexible Photomask for Biomedical Applications

We have introduced a fabrication method for electrical impedance spectroscopy (EIS)-on-a-needle (EoN: EIS-on-a-needle) to locate target tissues in the body by measuring and analyzing differences in the electrical impedance between dissimilar biotissues. This paper describes the fabrication method of fine interdigitated electrodes (IDEs) at the tip of a hypodermic needle using a photoresist spray coating and flexible film photomask in the photolithography process. A polyethylene terephthalate (PET) heat shrink tube (HST) with a wall thickness of 25 &#181;m is employed as the insulation and passivation layer. The PET HST shows a higher mechanical durability compared with poly(p-xylylene) polymers, which have been widely used as a dielectric coating material. Furthermore, the HST shows good chemical resistance to most acids and bases, which is advantageous for limiting chemical damage to the EoN. The use of the EoN is especially preferred for the characterization of chemicals/biomaterials or fabrication using acidic/basic chemicals. The fabricated gap and width of the IDEs are as small as 20 &#181;m, and the overall width and length of the IDEs are 400 &#181;m and 860 &#181;m, respectively. The fabrication margin from the tip (distance between the tip of hypodermic needle and starting point of the IDEs) of the hypodermic needle is as small as 680 &#181;m, which indicates that unnecessarily excessive invasion into biotissues can be avoided during the electrical impedance measurement. The EoN has a high potential for clinical use, such as for thyroid biopsies and anesthesia drug delivery in a spinal space. Further, even in surgery that involves the partial resection of tumors, the EoN can be employed to preserve as much normal tissue as possible by detecting the surgical margin (normal tissue that is removed with the surgical excision of a tumor) between the normal and lesion tissues.

The fabrication method for fine interdigitated electrodes (gap and width: 20 &#181;m) at the tip of a hypodermic needle (diameter: 720 &#181;m) is demonstrated using a spray coating and flexible film photomask in the photolithography process.

用光刻胶喷涂和柔性掩制备医用注射用针尖上的微细电极

We have introduced a fabrication method for electrical impedance spectroscopy (EIS)-on-a-needle (EoN: EIS-on-a-needle) to locate target tissues in the ...

Open-source Toolkit: Benchtop Carbon Fiber Microelectrode Array for Nerve Recording

Conventional peripheral nerve probes are primarily fabricated in a cleanroom, requiring the use of multiple expensive and highly specialized tools. This paper presents a cleanroom "light" fabrication process of carbon fiber neural electrode arrays that can be learned quickly by an inexperienced cleanroom user. This carbon fiber electrode array fabrication process requires just one cleanroom tool, a Parylene C deposition machine, that can be learned quickly or outsourced to a commercial processing facility at marginal cost. This fabrication process also includes hand-populating printed circuit boards, insulation, and tip optimization. 
The three different tip optimizations explored here (Nd:YAG laser, blowtorch, and UV laser) result in a range of tip geometries and 1 kHz impedances, with blowtorched fibers resulting in the lowest impedance. While previous experiments have proven laser and blowtorch electrode efficacy, this paper also shows that UV laser-cut fibers can record neural signals in vivo. Existing carbon fiber arrays either do not have individuated electrodes in favor of bundles or require cleanroom fabricated guides for population and insulation. The proposed arrays use only tools that can be used at a benchtop for fiber population. This carbon fiber electrode array fabrication process allows for quick customization of bulk array fabrication at a reduced price compared to commercially available probes.

Here, we describe fabrication methodology for customizable carbon fiber electrode arrays for recording in vivo in nerve and brain.

开源工具包:用于神经记录的台式碳纤维微电极阵列

Conventional peripheral nerve probes are primarily fabricated in a cleanroom, requiring the use of multiple expensive and highly specialized tools. This ...

Conformable Wearable Electrodes: From Fabrication to Electrophysiological Assessment

Wearable electronic devices are becoming key players in monitoring the body signals predominantly altered during physical activity tracking. Considering the growing interest in telemedicine and personalized care driven by the rise of the Internet of Things era, wearable sensors have expanded their field of application into healthcare. To ensure the collection of clinically relevant data, these devices need to establish conformable interfaces with the human body to provide high-signal-quality recordings and long-term operation. To this end, this paper presents a method to easily fabricate conformable thin tattoo- and soft textile-based sensors for their application as wearable organic electronic devices in a broad spectrum of surface electrophysiological recordings. 
The sensors are developed through a cost-effective and scalable process of cutaneous electrode patterning using poly(3,4-ethylenedioxythiophene)-poly(styrenesulfonate) (PEDOT:PSS), the most popular conductive polymer in bioelectronics, on off-the-shelf, wearable substrates. This paper presents key steps in electrode characterization through impedance spectroscopy to investigate their performance in signal transduction when coupled with the skin. Comparative studies are required to position the performance of novel sensors with respect to the clinical gold standard. To validate the fabricated sensors' performance, this protocol shows how to perform various biosignal recordings from different configurations through a user-friendly and portable electronic setup in a laboratory environment. This methods paper will allow multiple experimental initiatives to advance the current state of the art in wearable sensors for human body health monitoring.

Two recent technologies-tattoo and textiles-have demonstrated promising results in cutaneous sensing. Here, we present the fabrication and evaluation methods of tattoo and textile electrodes for cutaneous electrophysiological sensing. These electronic interfaces made of conductive polymers outperform the existing standards in terms of comfort and sensitivity.

适形可穿戴电极:从制造到电生理评估

Wearable electronic devices are becoming key players in monitoring the body signals predominantly altered during physical activity tracking. Considering ...

Fabrication of Flat-Interface Nerve Electrodes for Recording Neural Activity

To add a shielding layer, remove the large fixture bar, and remove the transparency piece with tweezers. Then, place the shielding sheet in the center of each face of the electrode and gently press it into the electrode.
Then, deposit some uncured silicone into the through-holes, and partially cure it for 30 minutes at 130 degrees Celsius. Once cooled to room temperature, place adhesive tape over the outer ends of the electrode and over the closing flanges, to keep silicone out of these segments.
Then, repeat the process of adding a layer of silicone to cover the entire electrode body. Follow this by placing silicone and transparency sheets over the electrode, and then, secure them with a large fixture bar and cure the silicone.
After curing, to complete the process, remove the excess silicone and the tape. Then, cut windows through the silicone to expose the spacer segments, and use tweezers to remove the spacer segments.
Next, under a microscope, remove the tape and silicone over the tubes, until it is level with the electrode body. Then, carefully cut around the perimeter of the electrode down to the base plate.
Now, taking caution to not damage the electrode, follow the guide diagram to shape the leads&#39; exit sites. Cut out a triangle between each tube pair that goes completely through the electrode layers, and onto the outer side.
Now, cut windows into the silicone that covers the shielding layer. Then, glide the polypropylene suture between the electrode base and the adjacent transparent layer, and use it to delaminate the nearly finished cuff electrode. Finally, cut windows out of the silicone to expose the center contacts and reference contacts.
The fabricated fine electrode was used to record the activity of the sciatic nerve in a dog over 7.5 months. A customized preamplifier and a super beta input instrumentation amplifier were implemented. The electrode was implanted around the nerve by suturing the two free edges together. The cuff flattens the nerve while retaining flexibility in the longitudinal direction.