This work was supported by the National Institutes of Health (grant no. R21-NS106434), the Citizens United for Research in Epilepsy Taking Flight Award, the Mirowski Family Foundation and Neil and Barbara Smit (F.V.); the National Science Foundation Graduate Research Fellowship Program (grant no. DGE-1845298 to N.D. and B.M.); the Army Research Office (Cooperative Agreement Number W911NF-18-2-0026 to K.M.); and by the U.S. Army via the Surface Science Initiative Program at the Edgewood Chemical Biological Center (PE 0601102A Project VR9 to Y.G. and K.M.). This work was carried out in part at the Singh Center for Nanotechnology, which is supported by the National Science Foundation National Nanotechnology Coordinated Infrastructure Program (NNCI-1542153).

All in vivo procedures conformed to the National Institutes of Health (NIH) Guide for the Care and Use of Laboratory Animals and were approved by the Institutional Animal Care and Use Committee (IACUC) of the University of Pennsylvania.
1. Synthesis of Ti3C2 MXene
NOTE: The reaction procedures described in this section are intended for use inside a chemical fume hood. Washing steps included in this procedure are intended to be used with balanced centrifuge tubes. All waste produced is considered hazardous waste and should be discarded appropriately following University guidelines.
CAUTION: Hydrofluoric acid (HF) is an extremely dangerous, highly corrosive acid. Consult the materials safety data sheets (MSDS) for the chemicals used to synthesize MXenes before use and implement and follow appropriate safety measures. Appropriate personal protective equipment (PPE) for handling HF includes a laboratory coat, acid resistant apron, close-toed shoes, long pants, goggles, full face shield, nitrile gloves, and HF resistant gloves made of butyl rubber or neoprene rubber.
<ol>
	<li>MAX phase synthesis
	<ol>
		<li>Synthesize Ti3AlC2 by ball milling TiC (2 &#181;m), Ti (44 &#181;m), and Al (44 &#181;m) powders at a molar ratio (TiC:Ti:Al) of 2:1:1 for 18 h using zirconia balls. Place the powders in an alumina crucible, heat to 1,380 &#176;C (5 &#176;C heating rate) and hold for 2 h under argon. After the powders have been cooled, mill the MAX block and sieve through a 200 mesh sieve (&#60;74 &#181;m particle size). 
		NOTE: The Ti3AlC2 MAX phase precursor used to synthesize MXenes has been shown to have direct implications on the resulting Ti3C2 MXene properties38. The Ti3C2 used to fabricate neural electrodes was selectively etched from MAX prepared following a previous procedure26.</li>
	</ol>
	</li>
	<li>Etching: Removal of the Al layer in Ti3AlC2 in an acidic etchant solution (Figure 1A)
	<ol>
		<li>Prepare the selective etching solution in a 125 mL plastic container by first adding 12 mL of deionized water (DI H2O) followed by the addition of 24 mL of hydrochloric acid (HCl). Wearing all appropriate HF etching PPE, add 4 mL of HF to the etchant container. Perform selective etching by slowly adding 2 g of Ti3AlC2 MAX phase to the reaction container and stirring with a Teflon magnetic bar for 24 h at 35 &#176;C at 400 rpm.</li>
	</ol>
	</li>
	<li>Washing: Bringing the material to neutral pH.
	<ol>
		<li>Fill two 175 mL centrifuge tubes with 100 mL of DI H2O. Split the etching reaction mixture into 175 mL centrifuge tubes and wash the material by repeated centrifugation at 3,500 rpm (2,550 x g) for 5 min. Decant the acidic supernatant into a plastic hazardous waste container. Repeat until the pH reaches 6.</li>
	</ol>
	</li>
	<li>Intercalation: Insertion of molecules between multilayer MXene particle to waken out-of-plane interactions (Figure 1B)
	<ol>
		<li>Add 2 g of lithium chloride (LiCl) to 100 mL of DI H2O and stir at 200 rpm until dissolved. Mix 100 mL of LiCl/H2O with the Ti3C2/Ti3AlC2 sediment and stir the reaction for 12 h at 25 &#176;C.</li>
	</ol>
	</li>
	<li>Delamination: Exfoliation from bulk multilayer particle into single- to few- layer Ti3C2 MXene (Figure 1C)
	<ol>
		<li>Wash the intercalation reaction in 175 mL centrifuge tubes by centrifugation at 2,550 x g for 5 min. Decant the clear supernatant. Repeat until a dark supernatant is found.</li>
		<li>Continue to centrifuge for 1 h at 2,550 x g. Decant the dilute-green supernatant.</li>
		<li>Re-disperse the swollen sediment with 150 mL of DI H2O. Transfer supernatant to 50 mL centrifuge tubes and centrifuge at 2,550 x g for 10 min to separate remaining MAX (sediment) from MXene (supernatant). 
		NOTE: Re-dispersion of the sediment will become difficult and will require agitation or manual shaking.</li>
		<li>Collect supernatant as Ti3C2 MXene. Perform further size selection and optimization of the solution to isolate single- to few-layer flakes by collecting the supernatant following a centrifugation step at 2,550 x g for 1 h.</li>
	</ol>
	</li>
	<li>Solution storage: Packaging the MXene ink for long-term storage (Figure 1D)
	<ol>
		<li>Argon bubble the solutions for 30 min prior to packaging in an Argon sealed headspace vial (transfer via a syringe). Store solutions at high concentrations (&#62;5 mg/mL), away from sunlight, and at low temperatures (&#8804;5 &#176;C) to ensure longevity.</li>
	</ol>
	</li>
</ol>
2. Fabrication of Ti3C2 MXene Microelectrode Arrays
NOTE: The procedure described in this section is intended for use inside a standard university clean room facility, such as the Singh Center for Nanotechnology at the University of Pennsylvania. This facility, as well as similar facilities, are accessible to outside users as part of the National Nanotechnology Infrastructure Network (NNIN) supported by the National Science Foundation (NSF). In these facilities, many of the tools, equipment, and materials described in this section are provided along with access to the clean room facility and would not require separate purchase.
CAUTION: Many of the chemicals used in the fabrication of MXene electrodes are hazardous, including photoresists, RD6 developer, remover PG, aluminum etching solution, and buffered oxide etchant. Consult MSDS for these chemicals before use and implement and follow appropriate safety measures at all times. All chemicals should be handled in a fume hood.
<ol>
	<li>Deposit a 4 &#956;m thick bottom layer of parylene-C onto a clean Si wafer (see Figure 2A).</li>
	<li>Use the first photomask (mask-1) to define the metal interconnects of the devices, as well as a metal ring around the edge of the wafer to aid in later lift-off steps (Figure 2B).
	<ol>
		<li>Spin coat NR71-3000p onto the wafer at 3,000 rpm for 40 s. Soft bake the wafer on a hot plate for 14.5 min at 95 &#176;C.</li>
		<li>Load the wafer and mask-1 into a mask aligner. Position the wafer so that the ring on the photomask overlaps with all edges of the wafer.</li>
		<li>Expose with i-line (365 nm wavelength) at a dose of 90 mJ/cm2. Hard bake the wafer on a hot plate for 1 min at 115 &#176;C.</li>
		<li>Immerse the wafer in the RD6 developer for 2 min, continuously agitating the solution. Rinse thoroughly with DI H2O and blow dry with an N2 gun.</li>
		<li>Use an electron beam evaporator to deposit 10 nm Ti, followed by 100 nm Au onto the wafer. 
		NOTE: Typical deposition parameters are a base pressure of 5 x 10-7 Torr and a rate of 2 &#197;/s.</li>
		<li>Immerse the wafer in remover PG for ~10 min until the photoresist has dissolved and the excess metal has fully lifted off, leaving Ti/Au only in the desired interconnect traces and the ring around the edge of the wafer. Once lift-off appears complete, sonicate for 30 s to remove any remaining traces of unwanted metal. Rinse wafer first in clean remover PG solution, then thoroughly rinse in DI H2O and dry the wafer with an N2 gun.</li>
	</ol>
	</li>
	<li>Deposit the sacrificial parylene-C layer (Figure 2C).
	<ol>
		<li>Expose the wafer to O2 plasma for 30 s to render the underlying parylene-C layer hydrophilic. Spin coat 2% cleaning solution (e.g., Micro-90) in DI H2O onto the wafer at 1,000 rpm for 30 s. Allow wafer to air dry for at least 5 min. 
		NOTE: The dilute soap solution acts as an anti-adhesive, allowing the sacrificial parylene-C layer to be peeled up later in the process.</li>
		<li>Deposit 3 &#956;m of parylene-C onto the wafer.</li>
	</ol>
	</li>
	<li>Use the second photomask (mask-2) to define the MXene patterns and a ring around the edge of the wafer (Figure 2D).
	<ol>
		<li>Repeat steps 2.2.1&#8722;2.2.4, this time using mask-2 and carefully aligning the alignment marks between the wafer and photomask before exposure.</li>
		<li>Use O2 plasma reactive ion etching (RIE) to etch through the sacrificial parylene-C layer in the areas not covered by the photoresist to define the MXene electrodes and traces, which should partially overlap with the Ti/Au interconnects, as well as the ring around the edges of the wafer. Confirm complete etching of the sacrificial parylene-C layer by using a profilometer to measure the profile between the exposed Ti/Au interconnects and the bottom parylene-C layer. 
		NOTE: When etching is complete, the profile across the exposed metal surface will be smooth, while the bottom parylene-C layer will be rough and partially etched. This etch step should be completed in a planar etch RIE system, not a barrel asher, and etch times and parameters will be highly dependent on the RIE system.</li>
	</ol>
	</li>
	<li>Spin-coat the MXene solution onto the wafer (Figure 2E).
	<ol>
		<li>Pipette MXene solution onto each of the desired MXene patterns, then spin the wafer at 1,000 rpm for 40 s. Dry the wafer on a 120 &#176;C hot plate for 10 min to remove any residual water from the MXene film.</li>
	</ol>
	</li>
	<li>Use an electron beam evaporator to deposit 50 nm SiO2 onto the wafer, to act as a protective layer over the MXene patterns for subsequent processing steps. 
	NOTE: Typical deposition parameters are a base pressure of 5 x 10-7 Torr and a rate of 2 &#197;/s.</li>
	<li>Remove the sacrificial parylene-C layer to pattern the MXene and SiO2 layers (Figure 2F).
	<ol>
		<li>Apply a small drop of DI H2O to the edge of the wafer and use tweezers to peel up the sacrificial parylene-C layer, beginning where its edges are defined in the ring around the outside of the wafer. 
		NOTE: The water will combine with the soap residue beneath the sacrificial parylene-C layer to enable this lift-off.</li>
		<li>Rinse the wafer thoroughly in DI H2O to remove any remaining cleaning solution residue. Dry the wafer with an N2 gun, then place on a 120 &#176;C hot plate for 1 h to remove any residual water from the patterned MXene films.</li>
	</ol>
	</li>
	<li>Deposit the 4 &#956;m thick top layer of parylene-C (Figure 2G).</li>
	<li>Use the third photomask (mask-3) to define device outline and openings over electrodes and Au bonding pads (VIAs) (Figure 2H).
	<ol>
		<li>Repeat steps 2.2.1&#8722;2.2.4, this time using mask-3 and carefully aligning the alignment marks between the wafer and photomask before exposure.</li>
		<li>Use an electron beam evaporator to deposit 100 nm Al onto the wafer. 
		NOTE: Typical deposition parameters are a base pressure of 5 x 10-7 Torr and a rate of 2 &#197;/s.</li>
		<li>Immerse the wafer in remover PG for ~10 min until the metal has fully lifted off, leaving Al covering the devices with openings for the electrodes and bonding pads. When lift-off is complete, sonicate for 30 s to remove any remaining traces of unwanted metal. Rinse wafer first in clean remover PG solution, then thoroughly rinse in DI H2O and dry the wafer with an N2 gun.</li>
	</ol>
	</li>
	<li>Etch the parylene-C to pattern the device outline and openings over electrodes and Au bonding pads (VIAs) (Figure 2I). Use O2 plasma RIE to etch through the parylene-C layers surrounding the devices, and through the top parylene-C layer covering both the MXene electrode contacts and the Au bonding pads. 
	NOTE: Etching is complete when no parylene-C residue remains on the wafer between devices. The SiO2 layer covering the MXene will act as an etch-stop layer, preventing the O2 plasma from etching into or damaging the MXene electrode contacts.</li>
	<li>Etch the Al layer covering the devices using a wet chemical etch in Al etchant type A at 50 &#176;C either for 10 min, or for 1 min past when all visual traces of Al have disappeared, whichever comes first. Etch the SiO2 covering the MXene electrodes using a wet chemical etch in 6:1 buffered oxide etchant (BOE) for 30 s (Figure 2J). 
	NOTE: The MXene microelectrode arrays are now complete.</li>
	<li>Release the devices from the Si substrate wafer by placing a small drop of DI H2O at the edge of a device, and gently peeling up the device as water is wicked underneath it by capillary action (Figure 2K and Figure 3).</li>
</ol>
3. Adapter Construction and Interfacing
NOTE: At this point, the thin film microelectrode arrays must be interfaced with an adapter to connect to the electrophysiology recording system. The 128ch stimulation/recording controller with the RHS2000 16-ch stim/record headstage (Table of Materials) used in this protocol requires input via a connector compatible with the 18-pin connector A79039-001. This section uses a printed circuit board (PCB, Figure 4A) with a zero-insertion force (ZIF) connector for interfacing with the Au bonding pads on the microelectrode array and the connector A79040-001 for interfacing with the head-stage of the recording system. Depending on the data acquisition system, different connectors can be used on the PCB to enable interfacing with the electrophysiology headstage.
<ol>
	<li>Solder the Omnetics and ZIF connectors to the PCB by applying a thin film of solder paste to each of the contact pads on the PCB, placing the parts in their appropriate locations, and heating on a hot plate until the solder reflows to form connections (Figure 4B). 
	NOTE: Reflow soldering can be done very easily on a hot plate or in a toaster oven and does not require the use of a costly reflow oven.</li>
	<li>Apply two layers of polyimide tape (Table of Materials) to the back side of the Au bonding pad region of the MXene microelectrode array to give the device sufficient thickness to be secured in the ZIF connector. After applying the tape, trim any excess beyond the edges of the parylene-C device using a razor blade or precision scissors (Figure 4C).</li>
	<li>Either under an inspection scope or using magnifying glasses, align the MXene microelectrode array in the ZIF connector so that the Au bonding pads align with the pins inside the ZIF connector, then close the ZIF to form a secure connection (Figure 4D,E). 
	NOTE: The ZIF connector used here is an 18-channel connector, while the device used here has 16 channels. The extra uncontacted channels are easily identified as an open circuit by means of impedance testing during recording sessions.</li>
	<li>Test the electrochemical impedance of the MXene electrodes using a potentiostat to ensure successful fabrication and connection to the PCB adapter. 
	NOTE: Reasonable impedance values are given in the discussion section to aid in troubleshooting.</li>
</ol>
4. Acute Implantation and Neural Recording
NOTE: Surgeries on adult male Sprague Dawley rats are performed using sterile instruments and with aseptic technique. Respiratory rate, palpebral reflex, and pedal pinch reflex are checked every 10 min to monitor depth of anesthesia. Body temperature is maintained with a heating pad.
<ol>
	<li>Administer preemptive analgesia (subcutaneous injection of buprenorphine sustained release [SR], 1.2 mg/kg).</li>
	<li>Administer anesthesia (intraperitoneal injection of a mixture of 60 mg/kg ketamine and 0.25 mg/kg dexmedetomidine).</li>
	<li>Confirm proper level of anesthesia every 10 min throughout the experiment by checking for absence of palpebral and pedal pinch reflexes.</li>
	<li>Secure rat in stereotaxic frame, apply ocular lubricant to the eyes, and clean shaved scalp with 10% povidone-iodine.</li>
	<li>Expose the calvaria with single midline scalp incision and blunt dissection of underlying tissue.</li>
	<li>Place a 00-90 screw into the skull to serve as the ground for recordings.</li>
	<li>Using a dental drill with a small burr, make a craniotomy at the desired cortical recording site.</li>
	<li>Secure the array connector to a stereotaxic manipulator and position the device over the craniotomy. Gently lower until the entire array is in contact with the exposed cortex.</li>
	<li>Wrap the ground wire around the skull screw.</li>
	<li>Connect the recording system headstage to the array and begin recording spontaneous activity.</li>
</ol>

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<li>Alhabeb, M., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Guidelines+for+Synthesis+and+Processing+of+Two-Dimensional+Titanium+Carbide+%28Ti3C2Tx+MXene%29%5BTitle%5D)+AND+%22Chemistry+of+Materials%22%5BJournal%5D)">Guidelines for Synthesis and Processing of Two-Dimensional Titanium Carbide (Ti3C2Tx MXene).</a> Chemistry of Materials. 29 (18), 7633-7644 (2017).</li>
<li>Ghidiu, M., Lukatskaya, M. R., Zhao, M. Q., Gogotsi, Y., Barsoum, M. W. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Conductive+two-dimensional+titanium+carbide+%E2%80%98clay%E2%80%99+with+high+volumetric+capacitance%5BTitle%5D)+AND+%22Nature%22%5BJournal%5D)">Conductive two-dimensional titanium carbide ‘clay’ with high volumetric capacitance.</a> Nature. 516 (7529), 78-81 (2014).</li>
<li>Lukatskaya, M. R., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Ultra-high-rate+pseudocapacitive+energy+storage+in+two-dimensional+transition+metal+carbides%5BTitle%5D)+AND+%22Nature+Energy%22%5BJournal%5D)">Ultra-high-rate pseudocapacitive energy storage in two-dimensional transition metal carbides.</a> Nature Energy. 2, 17105(2017).</li>
<li>Zhu, Y., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Carbon-Based+Supercapacitors+Produced+by+Activation+of+Graphene%5BTitle%5D)+AND+%22Science%22%5BJournal%5D)">Carbon-Based Supercapacitors Produced by Activation of Graphene.</a> Science. 332 (6037), 1537-1541 (2011).</li>
<li>Heon, M., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Continuous+carbide-derived+carbon+films+with+high+volumetric+capacitance%5BTitle%5D)+AND+%22Energy+%26+Environmental+Science%22%5BJournal%5D)">Continuous carbide-derived carbon films with high volumetric capacitance.</a> Energy & Environmental Science. 4 (1), 135-138 (2011).</li>
<li>Yang, X., Cheng, C., Wang, Y., Qiu, L., Li, D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Liquid-mediated+dense+integration+of+graphene+materials+for+compact+capacitive+energy+storage%5BTitle%5D)+AND+%22Science%22%5BJournal%5D)">Liquid-mediated dense integration of graphene materials for compact capacitive energy storage.</a> Science. 341 (6145), 534-537 (2013).</li>
<li>Zhang, C. J., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Transparent%2C+Flexible%2C+and+Conductive+2D+Titanium+Carbide+%28MXene%29+Films+with+High+Volumetric+Capacitance%5BTitle%5D)+AND+%22Advanced+Materials%22%5BJournal%5D)">Transparent, Flexible, and Conductive 2D Titanium Carbide (MXene) Films with High Volumetric Capacitance.</a> Advanced Materials. 29 (36), 1702678(2017).</li>
<li>Han, X., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((2D+Ultrathin+MXene-Based+Drug-Delivery+Nanoplatform+for+Synergistic+Photothermal+Ablation+and+Chemotherapy+of+Cancer%5BTitle%5D)+AND+%22Advanced+Healthcare+Materials%22%5BJournal%5D)">2D Ultrathin MXene-Based Drug-Delivery Nanoplatform for Synergistic Photothermal Ablation and Chemotherapy of Cancer.</a> Advanced Healthcare Materials. 7 (9), 1701394(2018).</li>
<li>Dai, C., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Biocompatible+2D+Titanium+Carbide+%28MXenes%29+Composite+Nanosheets+for+pH-Responsive+MRI-Guided+Tumor+Hyperthermia%5BTitle%5D)+AND+%22Chemistry+of+Materials%22%5BJournal%5D)">Biocompatible 2D Titanium Carbide (MXenes) Composite Nanosheets for pH-Responsive MRI-Guided Tumor Hyperthermia.</a> Chemistry of Materials. 29 (20), 8637-8652 (2017).</li>
<li>Xu, B., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Ultrathin+MXene-Micropattern-Based+Field-Effect+Transistor+for+Probing+Neural+Activity%5BTitle%5D)+AND+%22Advanced+Materials%22%5BJournal%5D)">Ultrathin MXene-Micropattern-Based Field-Effect Transistor for Probing Neural Activity.</a> Advanced Materials. 28 (17), 3333-3339 (2016).</li>
<li>Driscoll, N., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Two-Dimensional+Ti3C2+MXene+for+High-Resolution+Neural+Interfaces%5BTitle%5D)+AND+%22ACS+Nano%22%5BJournal%5D)">Two-Dimensional Ti3C2 MXene for High-Resolution Neural Interfaces.</a> ACS Nano. 12 (10), 10419-10429 (2018).</li>
<li>Sessolo, M., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Easy-to-Fabricate+Conducting+Polymer+Microelectrode+Arrays%5BTitle%5D)+AND+%22Advanced+Materials%22%5BJournal%5D)">Easy-to-Fabricate Conducting Polymer Microelectrode Arrays.</a> Advanced Materials. 25 (15), 2135-2139 (2013).</li>
<li>Shuck, C. E., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Effect+of+Ti3AlC2+MAX+Phase+on+Structure+and+Properties+of+Resultant+Ti3C2Tx+MXene%5BTitle%5D)+AND+%22ACS+Applied+Nano+Materials%22%5BJournal%5D)">Effect of Ti3AlC2 MAX Phase on Structure and Properties of Resultant Ti3C2Tx MXene.</a> ACS Applied Nano Materials. 2 (6), 3368-3376 (2019).</li>
<li>Hantanasirisakul, K., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Fabrication+of+Ti3C2Tx+MXene+Transparent+Thin+Films+with+Tunable+Optoelectronic+Properties%5BTitle%5D)+AND+%22Advanced+Electronic+Materials%22%5BJournal%5D)">Fabrication of Ti3C2Tx MXene Transparent Thin Films with Tunable Optoelectronic Properties.</a> Advanced Electronic Materials. 2 (6), 1600050(2016).</li>
<li>Xu, B., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Ultrathin+MXene-Micropattern-Based+Field-Effect+Transistor+for+Probing+Neural+Activity%5BTitle%5D)+AND+%22Advanced+Materials%22%5BJournal%5D)">Ultrathin MXene-Micropattern-Based Field-Effect Transistor for Probing Neural Activity.</a> Advanced Materials. 28 (17), 3333-3339 (2016).</li>
<li>Zhang, C., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Additive-free+MXene+inks+and+direct+printing+of+micro-supercapacitors%5BTitle%5D)+AND+%22Nature+Communications%22%5BJournal%5D)">Additive-free MXene inks and direct printing of micro-supercapacitors.</a> Nature Communications. 10 (1), 1795(2019).</li>
<li>Quain, E., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Direct+Writing+of+Additive-Free+MXene-in-Water+Ink+for+Electronics+and+Energy+Storage%5BTitle%5D)+AND+%22Advanced+Materials+Technologies%22%5BJournal%5D)">Direct Writing of Additive-Free MXene-in-Water Ink for Electronics and Energy Storage.</a> Advanced Materials Technologies. 4 (1), 1800256(2019).</li>
<li>Salles, P., Quain, E., Kurra, N., Sarycheva, A., Gogotsi, Y. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Automated+Scalpel+Patterning+of+Solution+Processed+Thin+Films+for+Fabrication+of+Transparent+MXene+Microsupercapacitors%5BTitle%5D)+AND+%22Small%22%5BJournal%5D)">Automated Scalpel Patterning of Solution Processed Thin Films for Fabrication of Transparent MXene Microsupercapacitors.</a> Small. 14 (44), 1802864(2018).</li>
</ol>

The authors have nothing to disclose.

The MXene synthesis and delamination procedure described in this protocol (HF/HCl/LiCl) was built from the MILD etching approach which employed a LiF/HCl (in situ HF) etchant medium26. The MILD approach allows for large Ti3C2 flakes (several &#181;m in lateral size) to be spontaneously delaminated during washing once pH ~5&#8722;6 has been attained. Compared to etching with HF alone, this results in material with higher quality and improved material properties, such as electr...

Understanding the fundamental mechanisms underlying neural circuits, and how their dynamics are altered in disease or injury, is a critical goal for developing effective therapeutics for a broad range of neurological and neuromuscular disorders. Microelectrode technologies have been widely used to elucidate neural dynamics on fine spatial and temporal scales. However, obtaining stable recordings with high signal-to-noise ratio (SNR) from microscale electrodes has proven to be particularly challenging. As the dimensions of the electrodes are reduced to approach cellular scale, a corresponding rise in electrode impedance degrades signal quality1. Additionally, numerous studies have shown that rigid electrodes comprised of conventional silicon and metal electronic materials produce significant damage and inflammation in the neural tissue, which limits their usefulness for long-term recording2,3,4,5. Given these facts, there has been significant interest in developing microelectrodes with new materials which can reduce the electrode-tissue interface impedance and can be incorporated into soft and flexible form factors.
One commonly used method for reducing the electrode-tissue interface impedance is increasing the area over which ionic species in the extracellular fluid can interact with the electrode, or the &#34;effective surface area&#34; of the electrode. This can be achieved through nanopatterning6, surface roughening7, or electroplating with porous additives8,9. Nanomaterials have gained significant attention in this field because they offer intrinsically high specific surface areas and unique combinations of favorable electrical and mechanical properties10. For example, carbon nanotubes have been used as a coating to significantly reduce electrode impedance11,12,13, graphene oxide has been processed into soft, flexible free-standing probe electrodes14, and laser-pyrolyzed porous graphene has been utilized for flexible, low-impedance micro-electrocorticography (micro-ECoG) electrodes15. Despite their promise, a lack of scalable assembly methods has limited the widespread adoption of nanomaterials for neural interfacing electrodes. Carbon-based nanomaterials in particular are typically hydrophobic, and thus require the use of surfactants16, superacids17, or surface functionalization18 to form aqueous dispersions for solution-processing fabrication methods, while alternative methods of fabrication, such as chemical vapor deposition (CVD), typically require high temperatures which are incompatible with many polymeric substrates19,20,21,22.
Recently, a class of two-dimensional (2D) nanomaterials, known as MXenes, has been described which offers an exceptional combination of high conductivity, flexibility, volumetric capacitance, and inherent hydrophilicity, making them a promising class of nanomaterials for neural interfacing electrodes23. MXenes are a family of 2D transition metal carbides and nitrides which are most commonly produced by selectively etching the A element from layered precursors. These are typically MAX phases with the general formula Mn+1AXn, where M is an early transition metal, A is a group 12&#8722;16 element of the periodic table, X is carbon and/or nitrogen, and n = 1, 2, or 324. Two-dimensional MXene flakes have surface-terminating functional groups that can include hydroxyl (&#8722;OH), oxygen (&#8722;O) or fluorine (&#8722;F). These functional groups make MXenes inherently hydrophilic and enable flexible surface modification or functionalization. Of the large class of MXenes, Ti3C2 has been the most extensively studied and characterized25,26,27. Ti3C2 shows remarkably higher volumetric capacitance (1,500 F/cm3)28 than activated graphene (~60&#8722;100 F/cm3)29, carbide-derived carbons (180 F/cm3)30, and graphene gel films (~260 F/cm3)31. Furthermore, Ti3C2 shows extremely high electronic conductivity (~10,000 S/cm)32, and its biocompatibility has been demonstrated in several studies33,34,35,36. The high volumetric capacitance of Ti3C2 films is advantageous for biological sensing and stimulation applications, because electrodes that exhibit capacitive charge transfer can avoid potentially harmful hydrolysis reactions.
Our group has recently demonstrated flexible, thin-film Ti3C2 microelectrode arrays, prepared using solution processing methods, which are capable of recording both micro-electrocorticography (micro-ECoG) and intracortical neuronal spiking activity in vivo with high SNR36. These MXene electrodes showed significantly reduced impedance compared to size-matched gold (Au) electrodes, which can be attributed to the high conductivity of MXene and the high surface area of the electrodes. In this protocol, we describe the key steps for fabricating planar microelectrode arrays of Ti3C2 MXene on flexible parylene-C substrates and utilizing them in vivo for intraoperative micro-ECoG recording. This method takes advantage of the hydrophilic nature of MXene, which makes possible the use of solution processing methods that are simple and scalable while not requiring the use of surfactants or superacids to achieve stable aqueous suspensions. This ease of processability may enable cost-effective production of MXene biosensors at industrial scales, which has been a major limitation to the widespread adoption of devices based on other carbon nanomaterials. The key innovation in the electrode fabrication lies in the use of a sacrificial polymeric layer to micropattern the MXene after spin-coating, a method adapted from literature on solution-processed poly(3,4-ethylenedioxythiophene):poly(styrene sulfonate) (PEDOT:PSS) microelectrodes37, but which had not previously been described for patterning MXene. The exceptional electrical properties of Ti3C2, coupled with its processability and 2D morphology make it a very promising material for neural interfaces. In particular, Ti3C2 offers a route towards overcoming the fundamental trade-off between electrode geometric area and electrochemical interface impedance, a primary limiting factor for micro-scale electrode performance. Additionally, the fabrication procedure described in this protocol can be adapted to produce MXene electrode arrays of varying sizes and geometries for different recording paradigms, and can also easily be adapted to incorporate other conductive inks besides MXene.

<table><tbody><tr><td>00-90 screw</td><td>McMaster-Carr</td><td>90910A630</td><td>Skull screw around which ground wire is wrapped</td></tr><tr><td>128ch stimulation/recording controller</td><td>Intan Technologies</td><td></td><td>A component of the neural recording system.</td></tr><tr><td>175 mL polypropylene (PP) conical centrifuge tubes</td><td>Falcon</td><td>REF: 352076</td><td>Used for washing</td></tr><tr><td>18 position 0.5 mm pitch ZIF connector</td><td>Molex</td><td>505110-1892</td><td>Used to interface the flexible Parylene microelectrode array with the PCB adapter board.</td></tr><tr><td>18 position dual row male nano-miniature (.025&quot;/.64mm) connector</td><td>Omnetics Connector Corporation</td><td>A79008-001</td><td>Used to interface the PCB adapter board to the recording headstage.</td></tr><tr><td>3ML Disposable Plastic Set Transfer Graduated Pipettes</td><td>Rienar</td><td>Rienar-3ML-20PCS</td><td>Used for transferring etchant or MXene solutions</td></tr><tr><td>50 mL polyproylene (PP) concial centrifuge tube</td><td>Falcon</td><td>REF: 352070</td><td>Used for washing and size selection</td></tr><tr><td>Al etchant Type A</td><td>Transene</td><td>060-0026000-QT</td><td>For removing Al etch mask layer after final Parylene-C etch.</td></tr><tr><td>Aluminum Powder, -325 Mesh, 99.5% (metals basis), particle size &amp;lt; 44 &amp;micro;m</td><td>Alfa Aesar</td><td>CAS: 7429-90-5</td><td>Used for MAX synthesis</td></tr><tr><td>AutoCAD software</td><td>Autodesk Inc.</td><td></td><td>Design software for drawing photomasks. Free alternatives include DraftSight and LayoutEditor.</td></tr><tr><td>Buffered Oxide Etchant 6:1</td><td>JT Baker</td><td>1178-03</td><td>For removing SiO2 layer to expose MXene electrode contacts at the end of the fabrication procedure.</td></tr><tr><td>Buprenorphine SR</td><td>Wildlife Pharmaceuticals</td><td></td><td>Analgesia for rat surgery</td></tr><tr><td>Centrifuge</td><td>Hermle</td><td>Benchmark Z 446</td><td>Used for washing and size selection</td></tr><tr><td>Dexdomitor</td><td>Midwest Veterinary Supply</td><td>193.13250.3</td><td>Anesthesia for rat surgery</td></tr><tr><td>Drill burr</td><td>Fine Science Tools</td><td>19007-07</td><td>Burrs for drill</td></tr><tr><td>Electric drill</td><td>Foredom</td><td>K.1070</td><td>Micromotor drill for craniotomies</td></tr><tr><td>Electron beam evaporator</td><td>Kurt J. Lesker Company</td><td></td><td>Used to evaporate Ti, Au, and SiO2 during fabrication. Most university clean rooms have this or a similar tool.</td></tr><tr><td>Ground wire</td><td>A-M Systems</td><td>781500</td><td>Bare silver wire</td></tr><tr><td>Headspace Vial, glass</td><td>Supelco</td><td>REF: 27298</td><td>Used for storing MXene solutions</td></tr><tr><td>Hydrochloric acid (12.1N)</td><td>Fisher Scientific</td><td>CAS: 7647-01-0</td><td>Corrosive; etchant material</td></tr><tr><td>Hydrofluoric Acid, (48-51% solution in H2O)</td><td>Acros</td><td>CAS: 7664-39-3</td><td>Etchant material</td></tr><tr><td>Jupiter II RIE system</td><td>March Plasma Systems Inc.</td><td></td><td>Planar RIE etching system used to etch the Parylene-C using O&lt;sub&gt;2&lt;/sub&gt; plasma. Most university clean rooms have a comparable planar RIE etching system.</td></tr><tr><td>Kapton standard polyimide tape, 1/4&quot;</td><td>DuPont</td><td></td><td>Used to add thickness to the Au bonding pad region of the flexible Parylene microelectrode array for insertion into the ZIF connector.</td></tr><tr><td>Ketamine</td><td>Hospital of the Univ. of Penn.</td><td></td><td>Anesthesia for rat surgery</td></tr><tr><td>KLA P-7 Stylus Profilometer</td><td>KLA Corporation</td><td></td><td>Used the measure 2D profiles to confirm complete etching through the sacrificial parylene-C layer in step 2.4.2. Most university clean rooms have this or a comparable stylus profilometer tool.</td></tr><tr><td>Lithium chloride, 99% for analysis, anhydrous</td><td>Acros</td><td>CAS: 7447-41-8</td><td>Hygroscopic; delamination material</td></tr><tr><td>MA6 mask aligner</td><td>Karl Suss Microtec AG</td><td></td><td>Used to align each photomask to the pattern on the wafer and expose the wafer to UV light. Most university clean rooms have this or a similar tool.</td></tr><tr><td>Micro-90 cleaning solution</td><td>International Products Corporation</td><td>M-9050-12</td><td>Used as the anti-adhesive layer to enable removal of the sacrificial Parylene-C layer to pattern the MXene</td></tr><tr><td>NR71-3000p photoresist</td><td>Futurrex Inc.</td><td>NR71-3000p</td><td>Negative photoresist used to define Ti/Au traces and MXene patterns in the devices.</td></tr><tr><td>Ophthalmic ointment</td><td>Midwest Veterinary Supply</td><td>193.63200.3</td><td>To prevent corneal drying during surgery</td></tr><tr><td>Parylene deposition system</td><td>Specialty Coating Systems</td><td></td><td>Used to evaporate thin conformal films of Parylene-C</td></tr><tr><td>Parylene-C dimer</td><td>Specialty Coating Systems</td><td>980130-c-01lbe</td><td>Flexible polymer used as bottom and top passivating layers for the flexible MXene devices</td></tr><tr><td>Photomasks (chrome on soda lime glass)</td><td>University of Pennsylvania</td><td></td><td>Our photomasks were produced in the University clean room using a Heidelberg DWL66+ laser writer system, however several vendors manufacture photomasks from provided design files.</td></tr><tr><td>Povidone-iodine solution</td><td>Medline</td><td>MDS093901</td><td>To help prevent infection around scalp incision</td></tr><tr><td>Printed Circuit Board (PCB)</td><td>Advanced Circuits</td><td></td><td>Used to interface between the MXene electrode array and the measurement electronics such as the potentiostat and the Intan recording system. Advanced Circuits and other vendors manufacture and assemble PCBs based on the provided design files.</td></tr><tr><td>RD6 Developer</td><td>Futurrex Inc.</td><td>RD6 Developer</td><td>Used to develop NR71-3000p negative photoresist following UV exposure</td></tr><tr><td>Reference 600 potentiostat</td><td>Gamry Instruments</td><td></td><td>Used to measure the electrodes&#039; impedance to assess quality of the devices</td></tr><tr><td>Remover PG</td><td>MicroChem Corp.</td><td>G050200</td><td>Used to remove NR71-3000p following metal deposition to perform lift-off patterning</td></tr><tr><td>RHS2000 Stim SPI interface cable</td><td>Intan Technologies</td><td></td><td>A component of the neural recording system.</td></tr><tr><td>RHS2116 amplifier board</td><td>Intan Technologies</td><td></td><td>A component of the neural recording system.</td></tr><tr><td>Si wafers</td><td>Wafer World</td><td>2885</td><td>Substrate for fabrication</td></tr><tr><td>Spin Coater</td><td>Cost Effective Equipment</td><td></td><td>For coating wafers with resists and applying the Micro-90 and MXene layers. Most university clean rooms have spin coaters.</td></tr><tr><td>Stereotaxic frame</td><td>Kopf Instruments</td><td>Model 902</td><td>For positioning the rat for neurosurgery</td></tr><tr><td>Teflon-coated magnetic stir bar</td><td>Corning</td><td>REF: 1233W95</td><td>Used to stir during etching and intercalation</td></tr><tr><td>Titanium carbide, 99.5% (metals basis), particle size ~2 &amp;micro;m</td><td>Alfa Aesar</td><td>CAS: 12070-08-5</td><td>Used for MAX synthesis</td></tr><tr><td>Titanium powder, -325 mesh, 99% (metals basis), particle size &amp;lt; 44&amp;micro;m</td><td>Alfa Aesar</td><td>CAS: 7440-32-6</td><td>Used for MAX synthesis</td></tr><tr><td>Ultrasonic bath sonicator</td><td>Reynolds Tech</td><td></td><td>For removing metal and photoresist particles during lift-off processes to pattern metals.</td></tr><tr><td>UV vis spectrophotometer</td><td>ThermoScientific</td><td>Evolution 201</td><td>Used to determine concentration and observe absorption peak</td></tr><tr><td>Zetasizer, Particle Size Analysis</td><td>Malvern Panalytical</td><td>Nano ZS</td><td>Used to determine particle lateral size distibution</td></tr></tbody></table>

fabrication of ti3c2 mxene microelectrode arrays for in vivo neural recording

Implantable microelectrode technologies have been widely used to elucidate neural dynamics at the microscale to gain a deeper understanding of the neural underpinnings of brain disease and injury. As electrodes are miniaturized to the scale of individual cells, a corresponding rise in the interface impedance limits the quality of recorded signals. Additionally, conventional electrode materials are stiff, resulting in a significant mechanical mismatch between the electrode and the surrounding brain tissue, which elicits an inflammatory response that eventually leads to a degradation of the device performance. To address these challenges, we have developed a process to fabricate flexible microelectrodes based on Ti3C2 MXene, a recently discovered nanomaterial that possesses remarkably high volumetric capacitance, electrical conductivity, surface functionality, and processability in aqueous dispersions. Flexible arrays of Ti3C2 MXene microelectrodes have remarkably low impedance due to the high conductivity and high specific surface area of the Ti3C2 MXene films, and they have proven to be exquisitely sensitive for recording neuronal activity. In this protocol, we describe a novel method for micropatterning Ti3C2 MXene into microelectrode arrays on flexible polymeric substrates and outline their use for in vivo micro-electrocorticography recording. This method can easily be extended to create MXene electrode arrays of arbitrary size or geometry for a range of other applications in bioelectronics and it can also be adapted for use with other conductive inks besides Ti3C2 MXene. This protocol enables simple and scalable fabrication of microelectrodes from solution-based conductive inks, and specifically allows harnessing the unique properties of hydrophilic Ti3C2 MXene to overcome many of the barriers that have long hindered the widespread adoption of carbon-based nanomaterials for high-fidelity neural microelectrodes.

Sample micro-ECoG data recorded on a MXene microelectrode array is shown in Figure 5. Following application of the electrode array onto the cortex, clear physiologic signals were immediately apparent on the recording electrodes, with approximately 1 mV amplitude ECoG signals appearing on all MXene electrodes. Power spectra of these signals confirmed the presence of two brain rhythms commonly observed in rats under ketamine-dexmedetomidine anesthesia: 1−2 Hz slow oscillations and γ oscilla...

Watch this Scientific Journal Video about Fabrication of Ti3C2 MXene Microelectrode Arrays for In Vivo Neural Recording at JoVE.com

Fabrication of Ti3C2 MXene Microelectrode Arrays for In Vivo Neural Recording

We describe here a method for fabricating Ti3C2 MXene microelectrode arrays and utilizing them for in vivo neural recording.

Fabrication of Ti3C2 MXene Microelectrode Arrays for In Vivo Neural Recording

Implantable microelectrode technologies have been widely used to elucidate neural dynamics at the microscale to gain a deeper understanding of the neural ...

fabrication-ti3c2-mxene-microelectrode-arrays-for-vivo-neural

Research

JoVE Journal

Bioengineering

13.3K Views.  University of Pennsylvania. Dit syntheseprotocol produceert hoogwaardige MXene-inkt met een metalen geleidbaarheid die boven de 10.000 Siemens per centimeter uitkomt. Het belangrijkste voordeel van deze techniek is dat het de precieze micro-patronen van MXene-films mogelijk maakt zonder de film te beschadigen of schadelijke residuen op de elektroden achter te laten. Om een titanium carbide inkt te bereiden, voeg langzaam twee gram titanium aluminium carbide voorloper aan een 125 milliliter reactie container met selectie...

Video: Fabrication of Ti3C2 MXene Microelectrode Arrays for In Vivo Neural Recording

Construction of Microdrive Arrays for Chronic Neural Recordings in Awake Behaving Mice

State-of-the-art electrophysiological recordings from the brains of freely behaving animals allow researchers to simultaneously examine local field potentials (LFPs) from populations of neurons and action potentials from individual cells, as the animal engages in experimentally relevant tasks. Chronically implanted microdrives allow for brain recordings to last over periods of several weeks. Miniaturized drives and lightweight components allow for these long-term recordings to occur in small mammals, such as mice. By using tetrodes, which consist of tightly braided bundles of four electrodes in which each wire has a diameter of 12.5 &mu;m, it is possible to isolate physiologically active neurons in superficial brain regions such as the cerebral cortex, dorsal hippocampus, and subiculum, as well as deeper regions such as the striatum and the amygdala. Moreover, this technique insures stable, high-fidelity neural recordings as the animal is challenged with a variety of behavioral tasks. This manuscript describes several techniques that have been optimized to record from the mouse brain. First, we show how to fabricate tetrodes, load them into driveable tubes, and gold-plate their tips in order to reduce their impedance from M&Omega; to K&Omega; range. Second, we show how to construct a custom microdrive assembly for carrying and moving the tetrodes vertically, with the use of inexpensive materials. Third, we show the steps for assembling a commercially available microdrive (Neuralynx VersaDrive) that is designed to carry independently movable tetrodes. Finally, we present representative results of local field potentials and single-unit signals obtained in the dorsal subiculum of mice. These techniques can be easily modified to accommodate different types of electrode arrays and recording schemes in the mouse brain.

The design and assembly of microdrives for in vivo electrophysiological recordings of brain signals from the mouse is described. By attaching microelectrode bundles to sturdy driveable carriers, these techniques allow for long-term and stable neural recordings. The lightweight design allows for unrestricted behavioral performance by the animal following drive implantation.

State-of-the-art electrophysiological recordings from the brains of freely behaving animals allow researchers to simultaneously examine local field ...

Behavior

Micro-drive Array for Chronic in vivo Recording: Drive Fabrication

Chronic recording of large populations of neurons is a valuable technique for studying the function of neuronal circuits in awake behaving rats. Lightweight recording devices carrying a high density array of tetrodes allow for the simultaneous monitoring of the activity of tens to hundreds of individual neurons. Here we describe a protocol for the fabrication of a micro-drive array with twenty one independently movable micro-drives. This device has been used successfully to record from hippocampal and cortical neurons in our lab. We show how to prepare a custom designed, 3-D printed plastic base that will hold the micro-drives. We demonstrate how to construct the individual micro-drives and how to assemble the complete micro-drive array. Further preparation of the drive array for surgical implantation, such as the fabrication of tetrodes, loading of tetrodes into the drive array and gold-plating, is covered in a subsequent video article.

Micro-drive Array for Chronic in vivo Recording: Drive Fabrication

In this protocol we demonstrate how to fabricate a micro-drive array for chronic electrophysiological recordings in rats.

Chronic recording of large populations of neurons is a valuable technique for studying the function of neuronal circuits in awake behaving rats. ...

Biology

Micro-drive Array for Chronic in vivo Recording: Tetrode Assembly

The tetrode, a bundle of four electrodes, has proven to be a valuable tool for the simultaneous recording of multiple neurons in-vivo.  The differential amplitude of action potential signatures over the channels of a tetrode allows for the isolation of single-unit activity from multi-unit signals.  The ability to precisely control the stereotaxic location and depth of the tetrode is critical for studying coordinated neural activity across brain regions.  In combination with a micro-drive array, it is possible to achieve precise placement and stable control of many tetrodes over the course of days to weeks.  In this protocol, we demonstrate how to fabricate and condition tetrodes using basic tools and materials, install the tetrodes into a multi-drive tetrode array for chronic in-vivo recording in the rat, make ground wire connections to the micro-drive array, and attach a protective cone onto the micro-drive array in order to protect the tetrodes from physical contact with the environment.



Micro-drive Array for Chronic in vivo Recording: Tetrode Assembly

In this protocol we demonstrate how to fabricate and condition tetrodes for use with a micro-drive array, which was designed for chronic electrophysiological recordings in rats. In addition, we illustrate the final stages of micro-drive array construction, which includes installing ground wires and a protective cone.

The tetrode, a bundle of four electrodes, has proven to be a valuable tool for the simultaneous recording of multiple neurons in-vivo.  The differential ...

A Method for Systematic Electrochemical and Electrophysiological Evaluation of Neural Recording Electrodes

New materials and designs for neural implants are typically tested separately, with a demonstration of performance but without reference to other implant characteristics.&#160;This precludes a rational selection of a particular implant as optimal for a particular application and the development of new materials based on the most critical performance parameters.&#160;This article develops a protocol for in vitro and in vivo testing of neural recording electrodes.&#160;Recommended parameters for electrochemical and electrophysiological testing are documented with the key steps and potential issues discussed.&#160;This method eliminates or reduces the impact of many systematic errors present in simpler in vivo testing paradigms, especially variations in electrode/neuron distance and between animal models.&#160;The result is a strong correlation between the critical in vitro and in vivo responses, such as impedance and signal-to-noise ratio.&#160;This protocol can easily be adapted to test other electrode materials and designs.&#160;The in vitro techniques can be expanded to any other nondestructive method to determine further important performance indicators.&#160;The principles used for the surgical approach in the auditory pathway can also be modified to other neural regions or tissue.

Different electrode coatings affect neural recording performance through changes to electrochemical, chemical and mechanical properties. Comparison of electrodes in vitro is relatively simple, however comparison of in vivo response is typically complicated by variations in electrode/neuron distance and between animals. This article provides a robust method to compare neural recording electrodes.

New materials and designs for neural implants are typically tested separately, with a demonstration of performance but without reference to other implant ...

Neuroscience

Focused Ion Beam Lithography to Etch Nano-architectures into Microelectrodes

With advances in electronics and fabrication technology, intracortical microelectrodes have undergone substantial improvements enabling the production of sophisticated microelectrodes with greater resolution and expanded capabilities. The progress in fabrication technology has supported the development of biomimetic electrodes, which aim to seamlessly integrate into the brain parenchyma, reduce the neuroinflammatory response observed after electrode insertion and improve the quality and longevity of electrophysiological recordings. Here we describe a protocol to employ a biomimetic approach recently classified as nano-architecture. The use of focused ion beam lithography (FIB) was utilized in this protocol to etch specific nano-architecture features into the surface of non-functional and functional single shank intracortical microelectrodes. Etching nano-architectures into the electrode surface indicated possible improvements of biocompatibility and functionality of the implanted device. One of the benefits of using FIB is the ability to etch on manufactured devices, as opposed to during the fabrication of the device, facilitating boundless possibilities to modify numerous medical devices post-manufacturing. The protocol presented herein can be optimized for various material types, nano-architecture features, and types of devices. Augmenting the surface of implanted medical devices can improve the device performance and integration into the tissue.

We have shown that the etching of nano-architecture into intracortical microelectrode devices may reduce the inflammatory response and has the potential to improve electrophysiological recordings. The methods described herein outline an approach to etch nano-architectures into the surface of non-functional and functional single shank silicon intracortical microelectrodes.

With advances in electronics and fabrication technology, intracortical microelectrodes have undergone substantial improvements enabling the production of ...

Surgical Training for the Implantation of Neocortical Microelectrode Arrays Using a Formaldehyde-fixed Human Cadaver Model

This protocol describes a procedure to assist surgeons in training for the implantation of microelectrode arrays into the neocortex of the human brain. Recent technological progress has enabled the fabrication of microelectrode arrays that allow recording the activity of multiple individual neurons in the neocortex of the human brain. These arrays have the potential to bring unique insight onto the neuronal correlates of cerebral function in health and disease. Furthermore, the identification and decoding of volitional neuronal activity opens the possibility to establish brain-computer interfaces, and thus might help restore lost neurological functions. The implantation of neocortical microelectrode arrays is an invasive procedure requiring a supra-centimetric craniotomy and the exposure of the cortical surface; thus, the procedure must be performed by an adequately trained neurosurgeon. In order to provide an opportunity for surgical training, we designed a procedure based on a human cadaver model. The use of a formaldehyde-fixed human cadaver bypasses the practical, ethical and financial difficulties of surgical practice on animals (especially non-human primates) while preserving the macroscopic structure of the head, skull, meninges and cerebral surface and allowing realistic, operating room-like positioning and instrumentation. Furthermore, the use of a human cadaver is closer to clinical daily practice than any non-human model. The major drawbacks of the cadaveric simulation are the absence of cerebral pulsation and of blood and cerebrospinal fluid circulation. We suggest that a formaldehyde-fixed human cadaver model is an adequate, practical and cost-effective approach to ensure proper surgical training before implanting microelectrode arrays in the living human neocortex.

We designed a procedure in which a formaldehyde-fixed human cadaver is used to assist neurosurgeons in training for the implantation of microelectrode arrays into the neocortex of the human brain.

This protocol describes a procedure to assist surgeons in training for the implantation of microelectrode arrays into the neocortex of the human brain. ...

Medicine

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.

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

Chronic Implantation of Multiple Flexible Polymer Electrode Arrays

Simultaneous recordings from large populations of individual neurons across distributed brain regions over months to years will enable new avenues of scientific and clinical development. The use of flexible polymer electrode arrays can support long-lasting recording, but the same mechanical properties that allow for longevity of recording make multiple insertions and integration into a chronic implant a challenge. Here is a methodology by which multiple polymer electrode arrays can be targeted to a relatively spatially unconstrained set of brain areas.
The method utilizes thin-film polymer devices, selected for their biocompatibility and capability to achieve long-term and stable&#160;electrophysiologic recording interfaces. The resultant implant allows accurate and flexible targeting of anatomically distant regions, physical stability for months, and robustness to electrical noise. The methodology supports up to sixteen serially inserted devices across eight different anatomic targets. As previously demonstrated, the methodology is capable of recording from 1024 channels. Of these, the 512 channels in this demonstration used for single neuron recording yielded 375 single units distributed across six recording sites. Importantly, this method also can record single units for at least 160 days.
This implantation strategy, including temporarily bracing each device with a retractable silicon insertion shuttle, involves tethering of devices at their target depths to a skull-adhered plastic base piece that is custom-designed for each set of recording targets, and stabilization/protection of the devices within a silicone-filled, custom-designed plastic case. Also covered is the preparation of devices for implantation, and design principles that should guide adaptation to different combinations of brain areas or array designs.

Described below is a method for implantation of multiple polymer electrode arrays across anatomically distant brain regions for chronic electrophysiological recording in freely moving rats. Preparation and surgical implantation are described in detail, with emphasis on design principles to guide adaptation of these methods for use in other species.

Simultaneous recordings from large populations of individual neurons across distributed brain regions over months to years will enable new avenues of ...

Construction and Implementation of Carbon Fiber Microelectrode Arrays for Chronic and Acute In Vivo Recordings

Multichannel electrode arrays offer insight into the working brain and serve to elucidate neural processes at the single-cell and circuit levels. Development of these tools is crucial for understanding complex behaviors and cognition and for advancing clinical applications. However, it remains a challenge to densely record from cell populations stably and continuously over long time periods. Many popular electrodes, such as tetrodes and silicon arrays, feature large cross-diameters that produce damage upon insertion and elicit chronic reactive tissue responses associated with neuronal death, hindering the recording of stable, continuous neural activity. In addition, most wire bundles exhibit broad spacing between channels, precluding simultaneous recording from a large number of cells clustered in a small area. The carbon fiber microelectrode arrays described in this protocol offer an accessible solution to these concerns. The study provides a detailed method for fabricating carbon fiber microelectrode arrays that can be used for both acute and chronic recordings in vivo. The physical properties of these electrodes make them ideal for stable and continuous long-term recordings at high cell densities, enabling the researcher to make robust, unambiguous recordings from single units across months.

Construction and Implementation of Carbon Fiber Microelectrode Arrays for Chronic and Acute In Vivo Recordings

This protocol describes a procedure for constructing carbon fiber microelectrode arrays for chronic and acute in vivo electrophysiological recordings in mouse (Mus musculus) and ferret (Mustela putorius furo) from multiple brain regions. Each step, following the purchase of raw carbon fibers to microelectrode array implantation, is described in detail, with emphasis on microelectrode array construction.

Multichannel electrode arrays offer insight into the working brain and serve to elucidate neural processes at the single-cell and circuit levels. ...

Construction of Local Field Potential Microelectrodes for in vivo Recordings from Multiple Brain Structures Simultaneously

Researchers often need to record local field potentials (LFPs) simultaneously from several brain structures. Recording from multiple desired brain regions requires different microelectrode designs, but commercially available microelectrode arrays often do not offer such flexibility. Here, the present protocol outlines the straightforward design of custom-made microelectrode arrays to record LFPs from multiple brain structures simultaneously at different depths. This work describes the construction of the bilateral cortical, striatal, ventrolateral thalamic, and nigral microelectrodes as an example. The outlined design principle offers flexibility, and the microelectrodes can be modified and customized to record LFPs from any structure by calculating stereotaxic coordinates and quickly changing the construction accordingly to target different brain regions in either freely moving or anesthetized mice. The microelectrode assembly requires standard tools and supplies. These custom microelectrode arrays allow investigators to easily design microelectrode arrays in any configuration to track neuronal activity, providing LFP recordings with millisecond resolution.

Construction of Local Field Potential Microelectrodes for in vivo Recordings from Multiple Brain Structures Simultaneously

The present protocol describes the construction of custom-made microelectrode arrays to record local field potentials in vivo from multiple brain structures simultaneously.

Researchers often need to record local field potentials (LFPs) simultaneously from several brain structures. Recording from multiple desired brain regions ...

Fabrication of Ti₃C₂ MXene Microelectrode Arrays for In Vivo Neural Recording

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