Abstract:There is a critical need to transition research level flexible polymer bioelectronics toward the clinic by demonstrating both reliability in fabrication and stable device performance. Conductive elastomers (CEs) are composites of conductive polymers in elastomeric matrices that provide both flexibility and enhanced electrochemical properties compared to conventional metallic electrodes. This work focuses on the development of nerve cuff devices and the assessment of the device functionality at each development… Show more
“…As the geometric size of metallic electrodes is reduced, their suitability for neural recordings may be significantly hindered due to their low charge injection capability and charge storage capacitance. A few soft organic polymers (PDMS ( Figure 1 e) [ 27 , 28 ], PI [ 29 ], parylene C [ 30 ], PU [ 31 ]) have been used to fabricate neural electrodes in order to mitigate the mechanical mismatch in the tissue–electrode interface. Compared to metals and carbon materials, polymeric materials are less efficient for the transfer of the electrical signals due to their low electrical conductivity [ 32 ].…”
Neural electrodes are essential for nerve signal recording, neurostimulation, neuroprosthetics and neuroregeneration, which are critical for the advancement of brain science and the establishment of the next-generation brain–electronic interface, central nerve system therapeutics and artificial intelligence. However, the existing neural electrodes suffer from drawbacks such as foreign body responses, low sensitivity and limited functionalities. In order to overcome the drawbacks, efforts have been made to create new constructions and configurations of neural electrodes from soft materials, but it is also more practical and economic to improve the functionalities of the existing neural electrodes via surface coatings. In this article, recently reported surface coatings for neural electrodes are carefully categorized and analyzed. The coatings are classified into different categories based on their chemical compositions, i.e., metals, metal oxides, carbons, conducting polymers and hydrogels. The characteristic microstructures, electrochemical properties and fabrication methods of the coatings are comprehensively presented, and their structure–property correlations are discussed. Special focus is given to the biocompatibilities of the coatings, including their foreign-body response, cell affinity, and long-term stability during implantation. This review article can provide useful and sophisticated insights into the functional design, material selection and structural configuration for the next-generation multifunctional coatings of neural electrodes.
“…As the geometric size of metallic electrodes is reduced, their suitability for neural recordings may be significantly hindered due to their low charge injection capability and charge storage capacitance. A few soft organic polymers (PDMS ( Figure 1 e) [ 27 , 28 ], PI [ 29 ], parylene C [ 30 ], PU [ 31 ]) have been used to fabricate neural electrodes in order to mitigate the mechanical mismatch in the tissue–electrode interface. Compared to metals and carbon materials, polymeric materials are less efficient for the transfer of the electrical signals due to their low electrical conductivity [ 32 ].…”
Neural electrodes are essential for nerve signal recording, neurostimulation, neuroprosthetics and neuroregeneration, which are critical for the advancement of brain science and the establishment of the next-generation brain–electronic interface, central nerve system therapeutics and artificial intelligence. However, the existing neural electrodes suffer from drawbacks such as foreign body responses, low sensitivity and limited functionalities. In order to overcome the drawbacks, efforts have been made to create new constructions and configurations of neural electrodes from soft materials, but it is also more practical and economic to improve the functionalities of the existing neural electrodes via surface coatings. In this article, recently reported surface coatings for neural electrodes are carefully categorized and analyzed. The coatings are classified into different categories based on their chemical compositions, i.e., metals, metal oxides, carbons, conducting polymers and hydrogels. The characteristic microstructures, electrochemical properties and fabrication methods of the coatings are comprehensively presented, and their structure–property correlations are discussed. Special focus is given to the biocompatibilities of the coatings, including their foreign-body response, cell affinity, and long-term stability during implantation. This review article can provide useful and sophisticated insights into the functional design, material selection and structural configuration for the next-generation multifunctional coatings of neural electrodes.
“…Unfortunately, 1 ms was the minimum pulse width that could be applied to distinguish the voltage related to the ohmic resistance of the system, also known as access voltage (Va). This fact is significant as the maximum polarization potentials are calculated by subtracting Va from the total voltage response [121], [122]. In any case, the pulse width was the same in platinum and PEDOT:PSS VTs, and therefore, the experiments are consistent.…”
Section: Voltage Transient Measurementsmentioning
confidence: 89%
“…These PEDOT:PSS films are biocompatible [118], transparent in the visible light spectrum, present high conductivity (> 200 S cm −1 [119]), outstanding flexibility [120], and proper thermal stability [117]. These features also favor an optimal implanttissue interface, decreasing inflammatory responses and device rejection [121], [122]. Furthermore, the work function of these films (around 5.0-5.2 eV) benefits high charge injection limits [117].…”
Section: Pedot:pss Optimal Materialsmentioning
confidence: 99%
“…For that, the current injected into the electrodes is increased until the limits of water window match with the maximum polarization voltages (Emc and/or Ema). As the CIC might vary depending on the pulse width [122], pulse widths comparable to the ones employed CI stimulation (i.e., 25 s [77], [136]) should be ideally used for this experiment. Unfortunately, 1 ms was the minimum pulse width that could be applied to distinguish the voltage related to the ohmic resistance of the system, also known as access voltage (Va).…”
Cochlear implants (CIs) are the most effective solution to treat severe-to-profound hearing loss. These medical devices mimic and replace the function of the damaged structures of the cochlea. To this date, more than 700,000 individuals worldwide have benefited from CIs. However, state-of-the-art CIs do not provide a natural and high-quality sound perception to their recipients, who poorly appreciate music and hardly understand speech in crowded or noisy atmospheres. Furthermore, CIs are expensive and unaffordable for poorer portions of society. The CI electrode array is the component that presents the most margin of improvement as it is still composed of classic materials and is fabricated via a tailored manual manufacturing process that does not maximize the potential of the system. Concretely, commercial CI electrode arrays contain from 12 to 24 individual stimulating channels that cannot optimally substitute the role of the 3000 neural stimulation sites of a normal-functioning cochlea. Moreover, most of the commercial CI electrode arrays cannot fit in the narrow deep areas of the cochlea to completely cover the low-frequency audible spectrum. Hence, to overcome these limitations, novel strategies and materials to optimize CI electrode arrays ought to be investigated.Chapter 1 of this work starts with an introduction to the auditory system and the different types of hearing loss. Chapter 2 goes through the history and research that led to the development of cochlear implants and presents their main components and current limitations. Chapter 3 discusses in detail the state-of-the-art of CI electrode arrays and Chapter 4 reviews novel materials to enhance them. In Chapter 5, PEDOT:PSS is suggested for the development of all-polymeric cochlear implant micro-electrode arrays. Initial experiments provide a proof-of-concept that demonstrates that by patterning the PEDOT:PSS layers with conductive and non-conductive areas, it is possible to create an electric circuit with superior electrodes and leads that give rise to all-polymeric CI microelectrode arrays. Future work will be directed towards developing an actual prototype using this strategy. Furthermore, a study of the long-term stability of the material will be necessary.
“…13h). Simultaneously, an all-polymer cuff electrode made of the CE was successfully developed, 227 which demonstrated good stability during manufacture, disinfection, cyclic tensile test, model wearing in vitro and so on. These studies demonstrate that a CE significantly improves the CIL performance of neural electrodes compared with commercial Pt ones.…”
Section: Current Developing Status Of Neural Electrodesmentioning
Neural electrodes, as a bridge for bidirectional communication between the body and external devices, are crucial means for detecting and controlling nerve activity. The electrodes play a vital role in...
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