Subdural porous and notched mini-grid electrodes for wireless intracranial electroencephalographic recordings
Received 18 March 2014
Accepted for publication 22 April 2014
Published 9 December 2014 Volume 2014:7 Pages 573—586
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 3
Muhammad Tariqus Salam,1 Sébastien Gélinas,1 Sébastien Desgent,2 Sandra Duss,2 Félix Bernier Turmel,1,3 Lionel Carmant,2 Mohamad Sawan,1 Dang Khoa Nguyen3
1Polystim Neurotechnologies Laboratory, Polytechnique Montréal, QC, Canada; 2Research Center, Sainte-Justine University Hospital Center (CHU Sainte-Justine), Université de Montréal, QC, Canada; 3Neurology Service, Department of Medicine, Notre-Dame Hospital, Centre Hospitalier de l'Université de Montréal (CHUM), QC, Canada
Background: Intracranial electroencephalography (EEG) studies are widely used in the presurgical evaluation of drug-refractory patients with partial epilepsy. Because chronic implantation of intracranial electrodes carries a risk of infection, hemorrhage, and edema, it is best to limit the number of electrodes used without compromising the ability to localize the epileptogenic zone (EZ). There is always a risk that an intracranial study may fail to identify the EZ because of suboptimal coverage. We present a new subdural electrode design that will allow better sampling of suspected areas of epileptogenicity with lower risk to patients.
Method: Impedance of the proposed electrodes was characterized in vitro using electrochemical impedance spectroscopy. The appearance of the novel electrodes on magnetic resonance imaging (MRI) was tested by placing the electrodes into a gel solution (0.9% NaCl with 14 g gelatin). In vivo neural recordings were performed in male Sprague Dawley rats. Performance comparisons were made using microelectrode recordings from rat cortex and subdural/depth recordings from epileptic patients. Histological examinations of rat brain after 3-week icEEG intracerebral electroencephalography (icEEG) recordings were performed.
Results: The in vitro results showed minimum impedances for optimum choice of pure gold materials for electrode contacts and wire. Different attributes of the new electrodes were identified on MRI. The results of in vivo recordings demonstrated signal stability, 50% noise reduction, and up to 6 dB signal-to-noise ratio (SNR) improvement as compared to commercial electrodes. The wireless icEEG recording system demonstrated on average a 2% normalized root-mean-square (RMS) deviation. Following the long-term icEEG recording, brain histological results showed no abnormal tissue reaction in the underlying cortex.
Conclusion: The proposed subdural electrode system features attributes that could potentially translate into better icEEG recordings and allow sampling of large of areas of epileptogenicity at lower risk to patients. Further validation for use in humans is required.
Keywords: epilepsy, seizure, monitoring, surgery, electrodes
Epilepsy is a chronic neurological disorder characterized by abnormal electrographic discharges in the brain that cause seizures and a range of behavioral manifestations. Presently, many patients with epilepsy are antiepileptic drug resistant or have systemic side-effects due to the antiepileptic drugs. These patients with refractory focal epilepsy may benefit from epilepsy surgery. However, a successful surgical treatment is dependent upon adequate localization of the epileptogenic zone (EZ).1 Non-invasive localization techniques such as scalp electroencephalography (EEG), positron emission tomography (PET), magnetic resonance imaging (MRI), ictal single-photon emission computed tomography (SPECT), magnetoencephalography (MEG), and EEG-functional MRI (EEG-fMRI) can help in the identification of the EZ, which sometimes allows some patients to go directly on to resective surgery.1,2 When non-invasive techniques fail to adequately localize the EZ, an invasive EEG study is generally required. These invasive EEG studies involve implanting intracerebral electrodes to allow direct recording from the brain. A variety of intracranial electrodes are available for such invasive studies: subdural strip or grid, depth, epidural, and foramen ovale electrodes;3-6 these differ in method of insertion, accuracy, risks, and limitations.7,8 The choice of electrodes depends on the areas to be sampled. Figure 1A and C show the traditional method of performing an invasive EEG study.
Intracranial electrodes are more sensitive to brain activities than extracranial electrodes because they are closer to the EZ. Whereas extracranial electrodes record signals generated from a large cortical surface, intracranial electrodes record the synchronous firing of many neurons throughout a few millimeters of cortex across the diameter of an electrode contact. However, using intracranial electrodes has some disadvantages, including a small risk of infection, edema, and hemorrhage.1,8 Thus, it is best to limit the number of electrodes implanted to delineate the EZ for safety purposes.9,10 Restrictions on the number of electrodes may, however, cause insufficient coverage to allow identification of the EZ. Erroneous identification of the EZ translates into a poor epilepsy surgery outcome.
Intracerebral electrodes have been in use since the 1950s, but few improvements have been made except for the development of the shank microelectrode array and the micro electrocorticography grid electrode to record high-frequency oscillations, which are primarily used for research purposes.11-14 Because of the small electrode-tissue interface compared to the area of EZ, these microelectrodes have different electrical characteristics than subdural electrodes. Commercial companies (eg, Ad-Tech Medical Instrument Corporation, Racine, WI, USA or PMT Corporation, Chanhassen, MN, USA) use common manufacturing methods for developing intracerebral subdural electrodes (diameter 4-5 mm). These commercial electrodes have silicone rubber (polydimethylsiloxane [PDMS]) as insulation and substrate material, platinum or stainless steel as electrode material, and stainless steel for wiring.14 Gold (Au) has been used in subdural electrodes,15 but no significant improvements in intracerebral electroencephalography (icEEG) recording have been reported.
The motivation for the work presented here was that currently used electrodes have several limitations. Mechanical resistance of electrode-wire generates noise that degrades the icEEG recording.15 Chemical reactions at the electrode-tissue interface produce ions that are toxic to tissues.16 Moreover, many materials (eg, stainless steel, tungsten, and titanium) need corrosion protection (ie, passive film),16 but this protection often dissolves because of faradic reaction in the passive film.17 Other unresolved problems include wiring material, poor connection at the electrode-wire interface, and visualization of implanted electrodes on post-implantation scans or MRIs. Finally, current intracerebral EEG recordings use many wired connections that limit the patient’s freedom of movement and increase the risk of brain infections.
The icEEG recording is characterized by low-amplitude signals (microvolt range) and low-frequency bandwidth. The available instruments have relatively poor noise performance for low-spectral neural signal amplification. Moreover, other low-spectral noises generated from electrodes and the electrode-tissue interface combine with instrument noise to modulate the neural signal and degrade the signal-to-noise ratio (SNR). We have previously demonstrated several front-end preamplifiers for noise reduction.18,19 However, optimum SNR values can also be obtained by improving intracranial electrode contacts.20
We propose a novel subdural electrode-based recording system (Figure 1B) featuring attributes that could potentially facilitate larger sampling areas with lower morbidity: mini-grids (Figure 1D) connected as needed, a single exit cable, wireless transmission, grid notches and holes, edge markers and a numbering system, low-impedance electrode contacts and wiring, and a wireless recording system.
Proposed novel intracranial recording system
The proposed subdural mini-grid and/or strip electrodes are meant to be implanted independently over suspected areas of epileptogenicity through a craniotomy (Figure 2). One or two main grid electrode(s) hold(s) all the electrodes and connect(s) to the implantable wireless icEEG recorder (Figure 1B). After the implantation of intracranial electrodes, the patient can undergo an MRI study to verify the positioning of implanted electrodes and then long-term video-EEG recording for localization of the EZ. The shapes and attributes of the new subdural electrodes and recording system are described below.
Figure 2 Illustration of the proposed novel subdural mini-grid electrodes.
The subdural mini-grid electrode is a 4×4 matrix (height, 40 mm; width, 40 mm; thickness, 0.6 mm). The dimensions of grid electrodes are smaller than the conventional grid to fit curved regions of the brain.
Commercial subdural grid electrodes may cause brain swelling.21 To minimize the risk of brain swelling, each mini-grid has six holes to allow circulation of cerebrospinal fluid.
The mini-grid electrode is designed to fit on the human brain cortical surface. Each mini-grid has four notches for better flexibility to allow a better fit with the curved cortical surface.
Edge and numbering markers are included in the grid electrodes to facilitate their identification on the post-implantation MRI. All materials used in the electrodes are MRI compatible and take into account the magnetic resonance (MR)-susceptibility artifacts generated by metal contacts.
The mini-grids are connected to one another using custom-made contactors that enhance electrical and mechanical connections. The connectors provide internal routing of electrical wiring. Shorter wires reduce resistance in the electrical paths. Moreover, the connectors provide stronger mechanical strength and the mini-grids do not move and overlap. This mini-grid electrode system may better adapt to the anatomy and different curvatures of various brain regions.
One exit cable
All the electrical paths are internally routed; thus, all the cables are merged in one exit cable coated with Teflon that connects to the implantable device for wireless icEEG recording or to the skin for wired recording. A single exit cable or wireless transmission should reduce the risk of infections.
Electrode and wiring materials
The quality of icEEG recordings is dependent on the choice of electrode material. We have previously shown that pure platinum (Pt) or pure Au electrodes provided higher conductivity than commercial electrodes.22 Therefore, contacts of the mini-grid electrodes are made of pure Pt or Au, and wire connections between the electrodes (thickness, 0.05 mm) and amplifiers are made using the same materials used for electrodes but with 0.1 mm diameter wires.
Electrode-wire junction manipulation
Electrode impedance can potentially be further improved by manipulating the electrode-wire junction. Two types of junctions are used for in vitro impedance analysis experiments: an electrode-wire touch junction and manipulation of an electrode-wire junction using conductive silver epoxy (SE).
Wireless recording system
The wireless recording system contains a preamplifier and a wireless data transceiver. The preamplifier has tunable gain with an input-referred root-mean-square (RMS) noise of ~1 μV and an accurate analog to digital converter with 24-bit resolution. The wireless chip has an serial peripheral interface interface and a media access control layer module. The low-power wireless system uses a custom frequency-shift keying transceiver (402–405 MHz) for icEEG recording transmission. The Medical Implant Communication Service transceiver offers high throughput up to 800 kbps and automatic error handling and flow control with bit-error rate below (10−10).
Methods and materials
Fabrication of mini-grid electrodes
Figure 3 illustrates the subdural mini-grid electrode fabrication process. This process has three steps: mold construction, electrode-wire junction manipulation, and assembly and packaging.
Figure 3 Flow chart of the subdural mini-grid electrode fabrication process.
The molds were designed using computer aided three-dimensional interactive application (CATIA) software (Waltham, MA, United States) and fabricated using high-speed precision 3-axis computer numerical controlled (CNC) vertical machining (Huron speed machine). The design and dimensions of the molds are shown in Figure 4A and B.
Two types of electrode-wire connections were used to reduce impedance and improve icEEG recording performance: electrode-wire touch connections and electrode-SE-wire connections.
Assembly and packaging
Electrodes and wires were assembled on the mold (Figure 4C) and PDMS was poured (Figure 4D). After 20 minutes of heating at 1,100°C (Figure 4E), subdural electrode arrays were encapsulated with a thin PDMS substrate and released from the mold (Figure 4F and G).
Compositional analyses of the electrode contacts were performed using a scanning electron microscope (SEM) and an electron-probe microanalysis with energy dispersive spectrometry quantitative technique (Oxford Instrumentation Company, Abingdon, Oxfordshire,United Kingdom).
Electrical impedance spectroscopy
Impedances of the proposed electrodes were electrically characterized in vitro using electrochemical impedance spectroscopy (impedance analyzer, HIOKI 3522 LCR) in standard physiological saline solution (0.9% NaCl). Conductivity of the solution (Rs) was measured using a conductivity meter (Cole-Parmer, model 1481–40; Montreal, Quebec, Canada ). The impedances of the new electrodes and commercial electrodes were measured as bipolar configurations. Figure 7A shows the experimental setup. The corresponding equivalent circuit is shown in Figure 7B.
The total equivalent impedance is where Rw1,2 is the wire resistance, Cp1,2 is the double layer capacitance, Rp1,2 the charge transfer resistance, and Rs the resistance of the solution. Thus, the impedance of an electrode (Zi) is the combination of Rw1/2, Cp1/2 and Rp1/2.
icEEG recording performance of proposed subdural contacts compared to commercially available subdural contacts
These studies were conducted at the CHUM–Notre-Dame Hospital and CHU-Ste-Justine Hospital. All procedures for the use and care of animals for these experiments complied with the policy and guidelines of the Canadian Council for Animal Care (CCAC). Experimental protocols were approved by the Comité Institutionnel des Bonnes Pratiques Animales en Recherche (CIBPAR) at the CHU Sainte-Justine Research Center, Université de Montréal. The recordings obtained with the proposed subdural contacts were compared with recordings made in human epileptics with commercial electrodes as part of their usual clinical care at the CHUM-Notre-Dame Hospital. Use of these recordings was approved by the CHUM ethics committee.
Animals and surgical electrode implantation procedure
Two groups of male Sprague Dawley rats (P80, ~450–580 g) underwent craniotomies under general anesthesia (ie, induction: 4% isoflurane in 0.1 l/min (liter per minute) of O2 and 0.05 mg/kg buprenorphine, maintenance: 2% isoflurane in 0.5 l/min (liter per minute) of O2 as shown in Figure 5A. Twenty minutes before surgery, the animals were pretreated with atropine 0.1% (subcutaneously, to minimize airway secretions), lactated Ringer’s solution US Pharmacopeia (USP) (2 mL subcutaneously, for hydration and electrolytes), and lidocaine 2.5% (subcutaneously, for local anesthesia). Next, a small slit (1 cm) was made in the skin overlying the head to expose the skull.
Three holes were drilled on the skull to place two anchor screws and one reference screw (1.25 mm in diameter) on top of the cerebellum as shown in Figure 5B. Craniotomy windows were drilled out starting at 1 mm caudal to the bregma coronal suture on the skull and the dura was carefully opened using a 30 G × 1/2 in syringe needle tip. The electrode implants were placed directly on top of the cortex using a stereotaxic micro-manipulator apparatus with steady forceps arms (Stoelting Co., Wood Dale, IL, USA) and was left there for 2 minutes while the brain was hydrated. A piece of gelfoam (<1 mm thick), covering the craniotomy window space, was placed on top of the implant to keep the site moist, stabilize the electrode, minimize vibrations, and protect the brain from the extrinsic milieu. The surgical site surface, remaining skull, anchors, cannula sides, and reference screws were covered/sealed with dental cement leaving only the tip of the injection site (cannula silicon entry), recording sites, and reference outputs visible (Plastics One, Inc., Roanoke, VA, USA).
After the implantation, animals received postoperative care for 3 consecutive days (enrofloxacin 10 mg/kg, subcutaneously, and buprenorphine 0.05 mg/kg, subcutaneously). After a 10 day postoperative recovery period, the freely-moving animals were placed in a Plexiglas cylinder cage surrounded by a Faraday tent to undergo video-EEG recording. EEG and animal behavior were recorded simultaneously with a Stellate Harmonie System (Stellate Systems v 6.2e; Montreal, QC, Canada) linked to a 32-channel Lamont amplifying unit and an infrared video camera positioned 1.5 m in front of the cages. Three separate observers blinded to the treatment groups reviewed the video-EEGs to detect spontaneous recurrent seizures and clinically associated behaviors.
icEEG recordings and performance evaluation
Recording performance of the proposed subdural contacts was first tested in two different rat experimental groups and compared with icEEG recordings from human patient groups using commercial electrodes. Recording quality was evaluated by the SNR of the icEEG recording and the SNR was measured using Equation 2.
where i=1, 2, 3, … N, Vin is icEEG recording, Vn,1 is noise1 and Vn,2 is noise2 (noise1 is primarily instrumentation or flicker noise and noise2 is higher frequency thermal noises; the details and graphical illustration are presented in the Results section). SNR of icEEG recording improves with signal strength in the icEEG frequency band while reducing noise1 and noise2.
Group 1: basal activity recordings for 3 weeks with one subdural electrode contact on each side of the rat brain
The rats in Group 1 underwent two rectangular craniotomies (4×6 mm) on top of both hemispheres (Figure 5C). The proposed subdural pure Au contact was positioned over the left hemisphere and the pure Pt electrode contact over the other through craniotomy windows (Figure 5D). Basal icEEG activities and animal behaviors were monitored 12 hours per day (6 hours during the day, from 12 pm to 6 pm, and 6 hours at night, from 12 am to 6 am). Here, only basal activity was recorded to better evaluate SNR in recordings and electrode-tissue reaction.
Group 2: induction of cortical seizures in vivo in rats using 4-aminopyridine
For seizure induction and detection experiments, rats from Group 2 were implanted with a subdural contact with a PDMS coated micro-cannula (1.5 mm diameter and 10 mm length) by drilling a wider rectangular craniotomy (4×9 mm) only on the right side of the skull (Figure 5E and F; zoom inset of Figure 6). To induce focal seizures of different durations in these rats, animals were injected with 4-aminopyridine ([4-AP]; a selective blocker of the Kv1 family of voltage-activated K+ channels) at doses of 30, 100, and 200 nmol (all diluted in 2 μL of sterile 0.9% saline and sonicated for two minutes to obtain a uniform suspension and adequate dilution of the drug). The injection was performed using a 10 μL reservoir of 4-AP solution in a Hamilton syringe (26 G) that was positioned using a stereotaxic apparatus and injected through the PDMS micro-cannula orifice into the adjacent region of the anterior part of the subdural electrode. The syringe needle orifice was stereotaxically positioned at 11 mm downward from the top of the cannula for intracortical (~0.5–1 mm below the pial surface of the sensorimotor cortex) 4-AP solution injection (2 μL, over 10 minutes at 0.2 μL/min). As for Group 1, 12 hours of basal activities were recorded but only over 24 hours. The next day, the rats were anesthetized with isoflurane and injected with 4-AP before being put back into a recording chamber to recover while being monitored for 40 minutes for seizures. These experiments were done to prove better SNR in seizure activity recordings and evaluate seizure signal recording performance using the proposed electrodes as compared with commercially available subdural electrodes.
Group 3: comparative studies with human patients
For comparative studies, we obtained recordings from two human patients (24- and 36-year-old men) with intractable partial epilepsy who had undergone previous icEEG invasive studies for epilepsy surgeries. The signal analyzed in patient one came from a commercially available subdural electrode (Ad-Tech Medical Instruments) positioned over the right frontotemporal region; and in patient two came from the electrode contact positioned over the left orbitofrontal region. The icEEG signal was recorded for 2 to 3 weeks. SNR in the recordings was compared with icEEG recordings performed in rats using the proposed electrodes.
MRI visualization of subdural mini-grids
MRI appearance of the new electrodes was tested by placing them in a gel solution (0.9% NaCl with 14 g gelatin) and scanning them using a 1.5 T Phillips MRI scanner.
Validation of wireless transmission of icEEG recordings
The icEEG was recorded in vivo from rats’ cortex using Stellate Inc.’s video-EEG wired recording system and the wireless recording device was tested in vitro using the wired recordings by evaluating the distortion between the original wired and the wirelessly re-recorded EEG. Figure 6 shows the functional block diagrams of both recording systems. Moreover, this wireless device recorded 32 channels at 2 kHz sampling with 24-bit resolution. The front-end of this system has a tunable gain (1 to 12) and an on-chip delta-sigma analog-to-digital converter.
After long-term icEEG recordings using our proposed pure Pt or Au electrode contacts, histological examinations were carried out in the rats. The animals were first perfused through the heart using phosphate-buffered saline and 4% paraformaldehyde. The brains were then blocked stereotaxically within the skull, removed, post-fixed for 2 hours at 4°C in a 4% paraformaldehyde phosphate-buffered saline solution (PBS) and cryoprotected in graded sucrose in 0.1 M phosphate buffer (pH 7.4) for 48 hours and frozen until processed. The blocks were cut in a series of 50 μm thick sections in the coronal plane; sections were stained with a cresyl violet for Nissl substance and histological examinations were performed.
Figure 7A and B shows the fabricated molds for the new subdural electrodes. Two types of subdural grid electrodes were fabricated, one with pure Au contacts (Figure 7C) and the other with pure Pt contacts (Figure 7D). These electrodes were scanned using SEM imaging and their material composition was analyzed using an energy dispersive spectrometry quantitative technique. The SEM images and compositional analyses of the electrode contacts showed 99.90% purity for both electrodes.20 Figure 7G shows a photograph of the 4×5.5 cm wireless icEEG recording device. Details of experimental results are described to follow.
The in vivo icEEG recording at 200 Hz sampling frequency is generally located in the low-frequency bandwidth (3 to 40 Hz). Flicker noise is predominant in lower frequencies (<3 Hz) and higher frequency noise is primarily located at >40 Hz because of the sampling frequency limitations and thermal noise.19 Therefore, recorded signals were divided into three main frequency bands (ie, noise1, icEEG, and noise2 as shown in Figure 8D). Figure 8D–F show comparative studies on impedance magnitude of commercial subdural electrodes (Ad-Tech Medical Instruments) and the proposed subdural electrodes. Figure 8D shows the significantly lower impedance of the proposed pure Au and pure Pt electrodes as compared to the commercial electrodes. Moreover, Figure 8E shows that the impedance of Pt electrodes is reduced by attaching wire with SE. However, the Au-electrode-silver-epoxy-Au-wire increases impedance compared to Au-electrode-Au-wire (Figure 8F).
icEEG recording performance
Basal activity recordings
Figure 9 shows five-second samples of in vivo icEEG recordings using commercial subdural electrodes and the proposed Pt and Au electrode contacts. The icEEG recording using commercial subdural electrodes (Figure 9A) had severe low- and high-spectral noise because of higher electrode impedance. The recordings using the proposed pure Pt and pure Au electrode contacts (Figure 9B and C) had lower noises while recording neural activities efficiently. Moreover, the higher conductivity of the proposed electrodes makes it possible to translate more neural activities into icEEG recordings. Power spectral densities (PSD) of Figure 9A and C demonstrate recording efficacy in the 3 to 40 Hz bandwidth while suppressing the noises in lower and higher frequencies. Figure 9D illustrates that PSD of the recording using commercial subdural electrodes had the highest noise effect on the lower and higher frequency bands, whereas recordings using the proposed pure Pt and pure Au electrode contacts had the lowest noise effect.
4-AP drug administration and seizure activity recording
After the 4-AP injection, the rats were attached to the video-EEG recording system and various seizure signals were recorded for ~40 minutes (Figure 10). The epileptiform activity induced was characterized by an initial hypersynchronous brain wave activity followed by trains of poly-spikes, with low-amplitude and low-frequency spike-wave complexes that increased after the first few minutes. The corresponding convulsive behaviors (eg, myoclonus and tonico-clonic) were ranked with a modified Racine’s scale of 0 to 5 (Table 1) in Figure 10.23
Figure 10 Histogram of seizure events induced by 200 nmol 4-AP injections.
Table 1 4-Ap induced seizure behavior in terms of the Modified Racine’s Scale
To evaluate recording performance, electrographic seizure signals recorded from humans using commercial subdural electrodes (Figure 11A) were compared to 4-AP induced seizure signals recorded using the proposed pure Pt (Figure 11C) and pure Au (Figure 11E) electrode contacts. The corresponding frequency analysis of the recordings showed continuous degradation of lower-spectral noise in Figure 11B and reduced noise in Figure 11D and F). Additional evidence for noise reduction is illustrated in Figure 12. The PSD of seizure activities in Figure 11A recorded using the commercial electrodes had highest noise effect on lower and higher frequency bands. However, the recordings using the proposed pure Pt and pure Au electrode contacts (Figure 11C and E had lowest noise effect. The impact of average noises and the SNR of the recordings are shown numerically in Table 2. The icEEG recording using commercial subdural electrodes had the worst SNR (−4.84 dB) at seizure onset because of higher RMS noise at 47.49 μV in the low-frequency band (LFB) and 1.61 μV in the high-frequency band (HFB). The proposed pure Pt and pure Au electrode contacts reduced a significant amount of noise and achieved higher SNRs. The highest SNR (6.67 dB) was recorded at seizure onset using pure Au electrodes.
Figure 11 Electrographic seizure recordings and corresponding frequency analysis.
Figure 12 Power spectral density of the electrographic seizure recordings using commercial, proposed Pt and Au subdural electrodes.
Table 2 Comparative study of average icEEG recordings in vivo
MRI visualization of subdural mini-grids
All Au and Pt plates in the fabricated grid electrodes were visualized in MRI images. Moreover, electrodes, four edge markers, and three numbering markers were individually identified in the images.
Validation of wireless transmission of icEEG recordings
The wireless icEEG recording system was implemented on a printed circuit board and validated using the wired recorded icEEG from rats. Figure 13A and B shows icEEG recordings from the wired Stellate Harmonie System and from the new wireless system. The icEEGs were transmitted wirelessly at 250 Hz sampling frequency without degradation of signal quality. Normalized RMS deviation between the original and wirelessly recorded signal was on average 2%. The total power consumption of the wireless recording system was 15 mW. Heat dissipation resulting in a 10°C temperature increase is deemed safe for the cortex tissue. This corresponds to 15 to 80 mW/cm2 power density,24 depending on the heat conductivity of the device encapsulation materials. The power density of the device presented herein was 0.57 mW/cm2.
Figure 13 icEEG recordings.
Post icEEG brain histology
Histology showed Nissl substance and labeled cells on the cerebral cortex. The cytoarchitecture of the somatosensory cortices was similar between both brain hemispheres underneath the pure Pt (right) and pure Au (left) subdural electrode contacts in Group 1 rats (Figure 14). The exposed regions were compared to other sensory regions (not exposed to electrode contacts) such as the visual cortex. Clear cytoarchitectonic borders were detected between the primary and secondary sensory cortices. Neocortical laminar organization and cellular densities (eg, neurons and glial cells) did not appear to be altered by the implants. The rest of the tissues exposed to the electrodes were found to be normal.25
Invasive studies involve implanting intracerebral electrodes to allow direct EEG recordings from brain and subsequently provide precise localization of the EZ, which is key to a successful epilepsy surgical treatment. Although various kinds of subdural and depth electrodes are reported in the literature,11–13 and some of them are commercially available,14 the proposed mini-grid electrode and wireless recording system described in this paper have capabilities and characteristics that make them particularly appropriate for local field potential and high-frequency oscillation recordings in animals and humans. A practical grid electrode must satisfy certain technical (eg, lower impedance and higher SNR) and physiological (eg, biocompatibility, MRI compatible) criteria. The proposed grid electrodes demonstrated approximately 80-fold lower impendence and 6 dB higher SNR than the commercial electrodes evaluated. Moreover, we used electrode contact and subtract materials, which are widely used in human intracerebral recordings and approved by the US Food and Drug Administration (FDA) for human implantation. In addition, these materials are MRI compatible and visible in the MRI imaging for the post-electrode implantation reconstruction.
After the implantation and recording using the mini-grid electrode, no abnormalities in the brain tissue were observed. In addition, the wireless recording system has some important features (eg, high resolution, 24-bit analog-to-digital conversion, 2 kHz sampling rate) that allows recording small amplitude (1–5 μV) high-frequency oscillations (<500 Hz), whereas the icEEG recordings digitized with lower bit precision may result in complete loss of the low-amplitude high-frequency oscillation.
We present early work on a new intracerebral recording system to improve localization of the EZ with lower morbidity. The proposed novel subdural mini-grid electrodes have a new shape and several attributes designed to address problems with the electrodes that are available: notches, holes, connectors, a single exit cable, and wireless transmission. The new subdural electrodes were fabricated using a molding process and the pure Pt or pure Au electrode contacts were encapsulated with PDMS. The electrical characteristics of the pure Pt or pure Au electrodes were analyzed in vitro and their impedances were significantly lower than those of commercial electrodes. The Au contact had better electrical impedance spectroscopy properties in the icEEG recording frequency band than the pure Pt contact. These electrodes were successfully implanted on rats and a series of in vivo recording experiments were performed. The experimental results demonstrated 50% fewer flicker and thermal noises than commercial electrodes, excellent signal stability, improved SNR by up to 6 dB, and no evidence of tissue damage. Further validation of the system in humans is required to reproduce the results found for animals.
The authors are grateful for support from Natural Sciences and Engineering Research Council of Canada, the Canada Research Chair in Smart Medical Devices, the Microsystems Strategic Alliance of Québec (ReSMiQ), the SAVOY Foundation, Epilepsy Canada, the CHU Sainte-Justine Foundation of the CHU Sainte-Justine, and the Foundation of Stars.
The authors report no conflicts of interest in this work.
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