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. 2024 Jun 18;57(12):1684-1695.
doi: 10.1021/acs.accounts.4c00160. Epub 2024 May 30.

Improving the Biocompatibility and Functionality of Neural Interface Devices with Silica Nanoparticles

Affiliations

Improving the Biocompatibility and Functionality of Neural Interface Devices with Silica Nanoparticles

Delin Shi et al. Acc Chem Res. .

Abstract

ConspectusNeural interface technologies enable bidirectional communication between the nervous system and external instrumentation. Advancements in neural interface devices not only open new frontiers for neuroscience research, but also hold great promise for clinical diagnosis, therapy, and rehabilitation for various neurological disorders. However, the performance of current neural electrode devices, often termed neural probes, is far from satisfactory. Glial scarring, neuronal degeneration, and electrode degradation eventually cause the devices to lose their connection with the brain. To improve the chronic performance of neural probes, efforts need to be made on two fronts: enhancing the physiochemical properties of the electrode materials and mitigating the undesired host tissue response.In this Account, we discuss our efforts in developing silica-nanoparticle-based (SiNP) coatings aimed at enhancing neural probe electrochemical properties and promoting device-tissue integration. Our work focuses on three approaches:(1) SiNPs' surface texturization to enhance biomimetic protein coatings for promoting neural integration. Through covalent immobilization, SiNP introduces biologically relevant nanotopography to neural probe surfaces, enhancing neuronal cell attachments and inhibiting microglia. The SiNP base coating further increases the binding density and stability of bioactive molecules such as L1CAM and facilitates the widespread dissemination of biomimetic coatings. (2) Doping SiNPs into conductive polymer electrode coatings improves the electrochemical properties and stability. As neural interface devices are moving to subcellular sizes to escape the immune response and high electrode site density to increase spatial resolution, the electrode sites need to be very small. The smaller electrode size comes at the cost of a high electrode impedance, elevated thermal noise, and insufficient charge injection capacity. Electrochemically deposited conductive polymer films reduce electrode impedance but do not endure prolonged electrical cycling. When incorporated into conductive polymer coatings as a dopant, the SiNP provides structural support for the polymer thin films, significantly increasing their stability and durability. Low interfacial impedance maintained by the conducting polymer/SiNP composite is critical for extended electrode longevity and effective charge injection in chronic neural stimulation applications. (3) Porous nanoparticles are used as drug carriers in conductive polymer coatings for local drug/neurochemical delivery. When triggered by external electrical stimuli, drug molecules and neurochemicals can be released in a controlled manner. Such precise focal manipulation of cellular and vascular behavior enables us to probe brain circuitry and develop therapeutic applications.We foresee tremendous opportunities for further advancing the functionality of SiNP coatings by incorporating new nanoscale components and integrating the coating with other design strategies. With an enriched nanoscale toolbox and optimized design strategies, we can create customizable multifunctional and multimodal neural interfaces that can operate at multiple spatial levels and seamlessly integrate with the host tissue for extended applications.

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Conflict of interest statement

The authors declare no competing financial interest.

Figures

Figure 1
Figure 1
Approaches to utilizing SiNP for enhancing neural probes’ electrochemical properties and promoting device–tissue integration. (Left) The performance of traditional neural probes without any coating is usually unsatisfactory because of their limited electrochemical properties and adverse tissue reactions. (Right) SiNP of different functionalities. (Top to bottom inset) Biomimetic molecules coupled with SiNP can promote neurointegration. When doped into the conductive polymer thin film, the SiNP can provide structural support and protect the polymer from fragmentation and delamination. Mesoporous SiNP can carry drugs/neurochemicals for local electrically controlled chemical delivery and cell manipulation. This figure uses icons from Biorender.com.
Figure 2
Figure 2
Synthesis, characterization, and immobilization of silica nanoparticles. (A) Synthesis chemistry of nonporous and porous SiNP with thiol functional groups on the surface. (B) Dynamic light scattering measured particle diameter distribution. Transmission electron microscopy imaging of (C) porous particles and (D) nonporous particles. Adapted with permission from ref (3). Copyright 2019 Wiley. (E) Chemistry route to immobilize thiolated nanoparticles to silicon/silicon dioxide substrate. The aminosilane (APTES) reacts with the hydroxyl groups introduced by the oxygen plasma to form a strong silanol bond with the surface. TNP can be covalently linked to the amines via the GMBS linker. (F) Step-by-step surface characterization (left y axis, roughness measured by ellipsometry; right y axis, water contact angle) during the particle immobilization procedure. Adapted with permission from ref (1). Copyright 2021 Wiley. (G, H) Scanning electron microscopy (SEM) imaging of nonporous particles immobilized on a silicon substrate. Adapted with permission from ref (11). Copyright 2018 Royal Society of Chemistry. Scale bar: (C, D) 100 nm, (G) 100 μm, and (H) 50 nm.
Figure 3
Figure 3
Silica nanoparticles work synergistically with L1 cell adhesion molecules to improve tissue integration. (A) Chemical route using the GMBS linker to covalently bind L1CAM to TNP already immobilized on the substrate. (B–J) Dry-aged TNP+L1 can still improve chronic electrophysiology performance and tissue integration. Adapted with permission from ref (2). Copyright 2023 Elsevier. (B) The number of average single units recorded per channel and mixed model for repeated measurements with Sidak’s multiple comparison tests (p < 0.001). (C–E) Representative histology and quantification of NeuN marked neuronal density. (G–I) Representative histology and quantification of GFAP-marked astrocytes. (E, I) Two-way ANOVA with Tukey’s post hoc. (F, J) SEM of attached tissue from explanted uncoated control and TNP+L1-coated probes. (K) Multiscale topography analysis revealed that the roughness increase is biologically relevant, especially for proteins and peptides. Adapted with permission from ref (13). Copyright 2022 American Chemical Society. (L–N) Two-photon imaging reveals decreased microglial coverage of neural electrodes following L1 immobilization. Adapted with permission from ref (12). Copyright 2022 Elsevier. (L) Coverage within 6 h after implanting. (M) Coverage monitored over 8 weeks. (N) Images of coverage after 8 weeks. Scale bars: (C, D, G, H) 100 μm, (F, J) 5 μm, (K) 2 μm to 2 nm, and (N) 50 μm. *p < 0.05, **p < 0.01, ***p < 0.001, and ****p < 0.0001.
Figure 4
Figure 4
Silica nanoparticles as dopants can improve the stability and durability of the conductive polymer thin film. (A) Thiol groups on the nanoparticle (both nonporous and porous) can be converted to sulfonate groups by oxidation. Then sulfonated nanoparticles can work as dopants to form the PEDOT/SNP composite. The SEM inset is PEDOT/porous SNP. Scale bar 1 μm. (B) Stimulation waveform for charge injection and corresponding voltage transients collected from bare gold or PEDOT/SNP sites. Va is the access voltage and Ve is the electrode voltage for the bare gold electrode and is used to determine the charge injection limit. (C–E) EIS for PEDOT/PSS and PEDOT/SNP polymerized for different times on 2 mm gold electrodes at 10 μA. With longer polymerization times, PEDOT/SNP produces substantially lower impedances, especially in the lower frequency range. (E) 1 Hz impedance of 556 Ω for PEDOT/SNP vs 1203 Ω for PEDOT/PSS after 800 s. Electrochemical characterization: (F) EIS, (G) charge storage capacity, and (H) charge injection limit for PEDOT/SNP (nonporous) films before and after stimulation for 30 min, 8 h, and 24 h at 50 Hz. (A–H) Adapted with permission from ref (3). Copyright 2019 Wiley. *p < 0.05, **p < 0.01, ***p < 0.001, and ****p < 0.0001. Significance in (G, H) is relative to prestim samples.
Figure 5
Figure 5
Silica nanoparticles used as cargo carriers for the controlled delivery of drugs and neurochemicals. (A) Drug loading and release. Drugs are loaded into porous nanoparticles via sonication. Loaded particles are polymerized with EDOT to produce a composite thin film. The release can be triggered with a triangular cyclic voltage sweep with sufficient reducing voltage. (B, E) Comparison of total drug release of fluorescein and rhodamine from active release from PEDOT/SNP, active release of the drug without SNP, and passive diffusion from PEDOT/SNP. Adapted with permission from ref (3). Copyright 2019 Wiley. (C, D, F, G) Fluorescent calcium imaging of neuron activities upon electrically triggered neurochemical release from a PEDOT/SNP-coated microwire carrying (C, D) GLU or (F, G) GABA. Adapted with permission from ref (26). Copyright 2021 by the authors. (H–K) Quantification of GCaMP activity before and during stimulation through (H) a DNQX-loaded electrode or (J) an unloaded electrode. (I, K) Pixel standard deviations for prestimulation and during-stimulation frames for a DNQX-loaded electrode, respectively. Image contrast is enhanced for easier visualization. Adapted with permission from ref (3). Copyright 2019 Wiley. (L–N) Two-photon imaging of the effect of electrically released vasodilator NaNP. (L) Percent diameter change of large vessels (diameters greater than 65 μm, n = 6 for control and n = 9 for NaNP). (M, N) Overlays of cortical vessels before (yellow) and after (magenta) stimulation for the control and NaNP group. Adapted with permission from ref (4). Copyright 2023 Wiley. Scale bars: (I, K) 100 μm and (M, N) 50 μm. *p < 0.05, **p < 0.01, ***p < 0.001, and ****p < 0.0001.
Figure 6
Figure 6
Future directions of SiNP applications. SiNPs can be used to carry or deliver a wide range of biofunctional molecules including drugs, neurochemicals, proteins (receptors, enzymes, antibodies, etc.), and genetic molecules (DNA, RNA, plasmids, aptamers, viruses, etc.). SNPs can also be made more complex (i.e., vesicle shell, metallic core, etc.) and can be integrated with other functional materials such as carbon nanotubes and other electronic parts such as nanoFET. Engineered SiNPs can be activated with versatile remote-control modalities. They can be deployed locally from the surface of neural implants with precise spatial control or injected locally or systemically to interface with regional tissue or the full body. SiNPs will accelerate the development of next-generation neural interfaces that are customizable, multifunctional, and multimodal and can operate at multiple spatial levels for extended time. This figure uses icons from Biorender.com.

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