Hybrid diamond/ carbon fiber microelectrodes enable multimodal electrical/chemical neural interfacing
Introduction
The cardiac pacemaker, cochlear implant, deep brain stimulator for Parkinson's disease and spinal cord stimulator for pain control are key examples of implantable devices that have progressed from basic research to commercial and clinical success. These examples represent only a small fraction of the possible clinical targets that could be addressed with “electric medicine”. There are many other approaches under development, including electrical stimulation for epilepsy, psychiatric disorders, hypertension, heart failure, gastrointestinal disorders, type II diabetes, and inflammatory disorders [1]. Additionally, recording devices are under investigation for limb prosthetics towards the promise of mobility for amputees and those suffering from paralysis [2,3]. By directly using electrical impulses to modulate the body's neural circuits, electric medicine provides a new paradigm for the treatment of disease. If devices can be miniaturized and their performance improved, electric medicine could be applied to a much broader range of clinical targets.
There is strong interest in implantable neuromodulation technologies that not only treat conditions but also record the efficacy of treatment, i.e. they could remotely inform specialists, measure their own efficacy, self-calibrate and react to the changing needs of the user. In the field, this is referred to as a closed-loop device, as illustrated in Fig. 1. Current neural implants are typically comprised of electrodes that primarily perform one function: either record from or stimulate neurons. Electrodes that perform more than one function are one way that overall device invasiveness can be minimized. Miniaturization of electrodes to microwire geometries, not only enables fabrication of smaller devices but has been shown to lead to less tissue damage and lower electrode failure, particularly when using carbon materials [4,5]. At 7–10 μm in diameter CFs are similar in diameter to the soma of individual neurons.
Therapies that employ neural stimulation hold great promise, but implantable devices face challenges in terms of safety and longevity. These considerations are governed by a range of factors including mechanical compliance, chemical biocompatibility, and electrochemical properties. CFs have been under investigation as promising neural interface electrodes because they exhibit biochemical longevity and are well tolerated in vivo due to their small diameter and flexibility, reducing the risk for infection and formation of glial scars in vivo [[6], [7], [8]]. CFs are also well established as excellent electrodes for neural recording [9] and electrochemical sensing [10,11]. They do not, however, possess sufficient electrochemical capacitance for neural stimulation within safe voltage limits. They also suffer from a relatively small “safe potential window”, the range of safe voltages within which water splitting does not occur. Electrodes that deviate beyond the water splitting water-window during stimulation can cause damage to neural tissue and are considered unsafe. Furthermore, in the case of CFs, etching of the electrode can occur at voltages higher than +1 V resulting in rapid degradation of the electrode.
The stimulation properties of CF electrodes can be improved by the addition of a high capacitance coating, leading to lower interfacial impedance and increased safe charge injection capacity (CIC) [12]. Platinum black or conductive polymers such as PEDOT:PSS have been used as the coating layer for improving the electrochemical properties of CF electrodes but polymer coatings often exhibit degraded performance after repeated stimulation either due to degradation of the coating material or lack of adhesion to the CF surface [9,[13], [14], [15], [16]].
Previously, we demonstrated that nitrogen-included ultrananocrystalline diamond (NUNCD) is an effective neural stimulation material [17]. This is a significant finding that adds an additional dimension to diamond's recognized exceptional properties in terms of chemical stability, wide water-window, and high resistance to surface fouling. Among all diamond forms, NUNCD is the only form of diamond that has been successfully used for both neural stimulation and recording [[18], [19], [20], [21]]. When an appropriate amount of nitrogen is introduced during chemical vapor deposition (CVD) and post-treated with oxygen plasma [[22], [23], [24]], NUNCD has a CIC as high as 1200 μC/cm2 [25]. We have previously demonstrated that this material is well tolerated in vivo [26] and exceptionally stable, even when pushed to the limits of safe operation [17]. It has been also reported that the double-layer capacitance values for the nanostructured CNT/BDD composite electrodes are ~450 times greater than those for the equivalent flat BDD electrodes [27]. The 3D diamond-based electrodes not only used for neuroprostheses but also increase the resolution of stimulation [28].
In this work, we develop a method to grow this material on single CF microfibers and demonstrate that the resultant electrode can be used safely and effectively for neural stimulation whilst retaining excellent properties for neural recording and electrochemical detection of dopamine. The established stability and robustness of UNCD, even under extreme operating conditions, combined with the small size of CFs makes these electrodes ideal for high-resolution, single neuron neural interface electrodes for closed loop medical devices.
Section snippets
Diamond deposition on carbon fibers
Before nanodiamond seeding, PAN-based CFs (Goodfellow) were electrochemically functionalized with aminophenyl groups on the surface. The electrochemistry was performed in a Teflon cell with a three-electrode set-up using a Gamry Potentiostat (Interface 1000E). An Ag/AgCl electrode and a Pt wire were used as the reference and counter electrode, respectively. A cluster of CFs was connected to a copper wire via silver epoxy. The CFs were first subjected to an acetonitrile solution containing 0.1 M
Diamond deposition on carbon fiber
Diamond coatings on CF have been attempted by many researchers before but with limited success [38]. The difficulty is mainly associated with the etching of CF under the CVD environment necessary for diamond deposition [39]. In order to protect the CF during CVD, we developed a new method for pre-seeding CF with covalently bound nanodiamonds before diamond growth (Fig. 2a and b). Covalent bonding of nanodiamonds was achieved by tethering nanodiamonds to the CF surface via a grafted aryl amine
Conclusion
We have demonstrated that diamond-coated CF microelectrodes are capable of performing the three main tasks required for closed-loop electric medicine devices: neural stimulation, neural recording, and chemical biosensing. Our previous work has shown that diamond materials are exceptionally long lasting and electrochemically robust, in vivo. However, the mechanical stiffness of bulk diamond films is likely incompatible with the soft, elastic tissues of the nervous system. By incorporating
Acknowledgments
This research was funded by a Project Grant from The National Health and Medical Research Council of Australia (GNT1101717). JF would like to thank the support from the Australian Research Council (ARC) through the ARC Centre of Excellence for Electromaterials Science (CE140100012). The authors acknowledge the use of the Advanced Microscopy Facility at Bio21 (The University of Melbourne) for SEM imaging and the National Vision Research Institute for use of electrophysiology equipment. The
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2022, CarbonCitation Excerpt :As a comparison, conventional microelectrodes like carbon fiber microelectrode (CFME) usually encounter severe surface fouling for real-time in vivo monitoring of biological fouling molecules(e.g., dopamine, epinephrine, serotonin and 5-hydroxyindoleacetic acid) in the biological environment, limiting its long-term practically biological applications [20,22]. After functionalization of nanodiamonds on the surface of CFME, the ND-CFME microsensor could effectively alleviate electrochemical fouling from electrochemical oxidation of serotonin and 5-hydroxyindoleacetic acid, and also decrease biofouling in brain slice tissue by 50% (see Fig. 7a) [20]. After the 25th injection of serotonin, the ND-CFME maintained 73 ± 1% of the initial signal while the CFME had only 54 ± 2%, and after immersing in 1 μM 5-HIAA solution for 1 h, the ND-CFME maintained 70 ± 3% of the initial signal, significantly higher than that of CFME (39 ± 2%).