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The biofunctionalization of the nanofiber tissue electrodes was carried out by activation of the amino groups via incubation in glutaraldehyde vapor.
Therefore, pHi values calculated from tonometry might differ from those directly measured with tissue electrodes [ 14].
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New technology to engineer the tissue-electrode interface, electrode design, and extraction algorithms to transform the recorded signal to movement will help translate exciting laboratory demonstrations to patient practice in the near future.
We have demonstrated the potential of polymeric, neurotrophin-eluting hydrogels to be incorporated into existing neural prosthesis designs, to improve the conditions of surrounding cells and, eventually, of the tissue-electrode interface in case of in vivo applications.
These considerations, combined with the long-term stability of DBS at the tissue-electrode interface, make LFPs very attractive feedback control parameters for responsive DBS.
The results show significantly different temperature of tissue around electrodes for radiofrequency ablation and irreversible electroporation.
The biocompatibility, biodegradability, and existence of several polar functional groups endow Chit the ability of using some important applications such as water treatment, separation membrane, tissue engineering, electrodes, and drug delivery.
In the latter group we can include technologies such as gastric tonometry, tissue oxygen electrodes, sublingual capnometry, and near-infrared spectroscopy (NIRS).
A typical USEA can reach up to 1.5-mm deep into tissue, but electrodes as long as 9 mm have been machined using alternative fabrication methods [ 6].
In this study we evaluate the effects of the tissue and electrode capacitance on the volume of tissue activated (VTA) during deep brain stimulation (DBS).
Metal-polymer hybrids are able to decline the disparity between soft tissues and electrodes in which the polymeric part can regulate the metal modulus.
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