This study was sponsored by the National Institute of Information and Communications Technology of Japan (NICT).
The authors thank the MRI physicists and technologists at the Center for Information and Neural Networks for their dedication in acquiring good quality MRI data.
Dr. Khoo is funded by Grant-in-Aid for Scientific Research (Nos. 18H06261, 19K21353, 20K09368) from the Ministry of Education, Culture, Sports, Science, and Technology of Japan and a grant by the National Institute of Information and Communications Technology of Japan (NICT), and was supported by Mark Rayport and Shirley Ferguson Rayport fellowship in epilepsy surgery and the Preston Robb fellowship of the Montreal Neurological Institute (Canada), a research fellowship of the Uehara Memorial Foundation (Japan). She received a sponsored award from the Japanese Epilepsy Society, support from the American Epilepsy Society (AES) Fellows program, and travel bursary from the International League Against Epilepsy (ILAE).
Dr. Tani is funded by Grant-in-Aid for Scientific Research (No. 17K10895) from the Ministry of Education, Culture, Sports, Science, and Technology of Japan and received research support from Mitsui-Kousei Foundation, funding for a trip from Medtronic, royalties from the publication of articles (Gakken Medical Shujunsha, Igaku-shoin), and honoraria from serving as speaker (Medtronic, Daiichi-Sankyo Pharmaceuticals, Eisai Pharmaceuticals).
Dr. Oshino is funded by Grant-in-Aid for Scientific Research (No. 17K10894) from the Ministry of Education, Culture, Sports, Science, and Technology of Japan. He received royalties from the publication of articles (Medicalview, Igaku-shoin), and honoraria from serving as speaker (Insightec, Eisai Pharmaceuticals, Daiichi-Sankyo Pharmaceuticals, UCB, Otsuka Pharmaceuticals, Teijin Pharma, Yamasa Corporation).
Dr. Fujita is funded by Grant-in-Aid for Scientific Research (No. 19K18388) from the Ministry of Education, Culture, Sports, Science, and Technology of Japan.
Dr. Gotman is funded by the Canadian Institutes of Health Research (No. FDN 143208).
Dr. Kishima is funded by Grant-in-Aid for Scientific Research (Nos. 18H04085, 18H05522, 16K10212, 16K10786) from the Ministry of Education, Culture, Sports, Science, and Technology of Japan, Cross-ministerial Strategic Innovation Promotion Program (No. SIPAIH18E01), Japan Agency for Medical Research and Development, and Japan Epilepsy Research Foundation.

The research ethics committee of Osaka University Hospital and the safety committee of the Center for Information and Neural Networks (CiNET) approved the protocol (Osaka University Hospital Approval Nos. 18265 and 19259; CiNET Approval Nos. 2002210020 and 2002120020). All subjects provided written informed consent for their participation.
1. Preparation of the experimental setup
<ol>
	<li>Connect the MRI-compatible EEG and bipolar amplifiers to the battery packs (ensure that they are fully charged) and to the recording computer.</li>
	<li>Ensure that the workspace of the recording software is correctly set up. Set the amplitude resolution to 0.5 &#181;V to avoid amplifier saturation; set the frequency filters according to the frequency band of interest. Set the sampling rate at 5,000 Hz (maximum possible for the amplifiers used in this protocol), regardless of the frequency band of interest. 
	NOTE: Amplitude resolution at 0.5 &#181;V corresponds to a maximum value of 16.38 mV, which is sufficient to record the gradient artifact, considering that gradient artifact peaks can reach amplitudes over 100-fold more than those of spontaneous scalp EEG (approximately 10-100 &#181;V) at high speeds (&#62;1,000-fold faster than the rate of change of ongoing EEG). Theoretically, the sampling rate should be at least twice as high (Nyquist theorem) as the highest frequency in the gradient switching spectrum, in order to accurately sample the high-frequency gradient-switching artifacts and detect the true onset of each volume&#39;s gradient activity for subsequent removal12,18. However, increasing the sample rate results in large file sizes, which require significant investment for data storage and may also impede subsequent post-processing. Using the syncing device makes it unnecessary to raise the sample rate to improve synchronization between the EEG and MR clocks (see step 1.4). A sampling rate of 5,000 Hz is adequate for usual EEG/event-related potential (ERP) recordings, and higher sample rates do not improve data quality because the subsequent artifact correction process, which involves down sampling of the data to a frequency below 500 Hz and additional low-pass filtering, eliminates all high-frequency gradient correction residuals that may exist18.</li>
	<li>Refer to the manual for details regarding the proper settings of the recording software needed for EEG acquisition in the MRI, which differs from that outside the MRI.</li>
	<li>Check whether markers from the scanner, i.e., the markers for clock synchronization (sync on by default) and volume trigger (R128 by default), are periodically displayed in the online EEG recording. The sync on display indicates that the MRI scanner and EEG clocks are synchronized, and R128 indicates that the volume triggers are recorded for subsequent post-processing. The MRI scanner and EEG clocks are synchronized using the SyncBox device, which detects the scanner clock output (usually 10 MHz and above), downsamples, and outputs the clock signal (and the synchronization markers) to the USB2 interface. 
	NOTE: The USB2 interface sends the EEG data from all of the amplifiers, which are phase locked to the scanner clock signal, to the recording computer18. Periodic sync on markers are triggers generated from the scanner electrical pulse to synchronize the EEG signal sampling by the MR scanner rate, a requisite for scanner artifact correction. Volume triggers are used to identify MR volume scan onset time for scanner artifact correction during offline EEG processing19.</li>
	<li>Set up the MRI scanner according to the need and availability. It is best to use a transmit and receive head radio frequency (RF)-coil to minimize the risk of RF heating. However, a whole body transmit RF-coil and a 20-channel head receive only RF-coil were used here because a transmit and receive head coil was not available for the scanner used (typically the case for most modern scanners).</li>
	<li>Load a 10 mL syringe (or several as needed) with the abrasive conductive gel for application of the EEG cap. One could preload the abrasive gel in a 50 mL large-capacity plastic syringe for fluid dispensing and fill the 10 mL syringe with the gel prior to the subject&#39;s arrival. 
	&#8203;NOTE: Application of a 32-channel EEG cap typically consumes about 20-25 mL of gel.</li>
</ol>
2. Applying the EEG cap and ECG electrode
<ol>
	<li>At recruitment, ask the subject to complete a checklist of potential contraindications for MRI. Confirm that the subject has no contraindications for MRI prior to arrival. 
	NOTE: In general, any subject who qualifies for MRI can participate in an EEG-fMRI study. The exclusion criteria are: non-cooperative or non-compliant subjects; those with underlying conditions (e.g., chronic back pain), which prevent them from lying supine for a certain period of time (typically at least 1 h); or subjects who may be unable to lie still on the MRI table during the scan. Movement not only hampers the quality of both EEG and fMRI data but also imposes a potential hazard to the subjects themselves (e.g., induces current in the wires and cables that may cause stimulation). In the case of task-based acquisition, the language comprehension ability of the subject should also be considered (avoid subjects who are unable to understand the instructions). In this study, 32 healthy volunteers (mean age, 40 years; 17 women) and 25 patients with epilepsy (mean age, 31 years; 13 women) were recruited.</li>
	<li>Ask the subjects to wash their hair with shampoo without conditioner or wax before arrival.</li>
	<li>Explain the purpose of the experiment and next steps to the subject.</li>
	<li>Measure the head circumference (i.e., occipital frontal circumference) by wrapping a flexible non-stretchable measuring tape around the head over the supraorbital ridges and the occiput and select an appropriately sized cap. Use a cap that is 1 cm larger than the head circumference, and always ask the subject whether the cap is comfortable once placed (i.e., not too tight).</li>
	<li>After placing the cap at the approximate position over the subject&#39;s head, using the same measuring tape, measure the lengths of the inion-nasion arc, defined as the arc over the midline of the head extending from the occiput to the bridge of the nose, and the peri-auricular arc, defined as the arc extending between the ears that crosses the midpoint of inion-nasion arc, over the cap. Mark the intersection of the inion-nasion arc and the peri-auricular arc (the point where the midpoints of both arcs meet, AKA Cz), and slide the cap over the head so that the position of electrode Cz is adjusted to this intersection. Ensure that the cap is not rotated horizontally by manually checking whether electrodes Fz, Pz, Oz, Reference, and Ground are positioned over the inion-nasion arc.</li>
	<li>Expose the skin underneath each electrode by displacing the hair to the side of the electrode using the back of a cotton swab.</li>
	<li>Rub the skin beneath each electrode by quickly spinning a cotton swab containing 70% alcohol solution placed through the opening of the electrode.</li>
	<li>Apply a small amount of the abrasive conductive gel (~0.2 mL) in the opening and abrade the skin by quickly spinning a cotton swab in a similar fashion.</li>
	<li>Monitor the impedance of the electrode (displayed by the recording software) and repeat the abrasion as stated in step 2.8 until the impedance drops at least below 20 k&#937;20, preferably as low as possible (below 5 k&#937;)21.</li>
	<li>Fill the opening with the same gel (usually ~0.5 mL) once the impedance is satisfactory. Do not apply excessive gel in the opening to avoid bridging between electrodes. Move to the next electrode if the impedance is unsatisfactory despite repeated abrasion and come back later because sometimes the impedance continues to drop with time after applying the gel.</li>
	<li>Repeat steps 2.6-2.9 for all of the scalp EEG electrodes.</li>
	<li>Before placing the ECG electrode at the back, ask the subject to sit upright without flexing the neck.</li>
	<li>Make sure that the ECG electrode wire is straight when placing the ECG electrode at the back but keep some allowance for laying the ECG electrode wire along the curve of the neck, to avoid displacement of the electrode when the subject lays down on the MRI table. Place the ECG electrode 2-3 cm left from the median furrow, which can be identified as the vertical indentation along the midline of the back. The vertical position varies depending on the subject&#39;s height; it is typically positioned on the lower back approximately on the line that extends between the tips of the scapula in a subject of about 160 cm.</li>
	<li>Rub the skin underneath the ECG electrode with an alcohol swab.</li>
	<li>Attach the ECG electrode to the skin using a double-sided adhesive ring and repeat steps 2.8-2.9. The adhesive ring also serves as a padding to avoid direct contact of the electrode with the skin.</li>
	<li>Fold the dry alcohol cotton swab into four, and place it on the ECG electrode. Tape it to the skin using a surgical tape (medical adhesive tape). Tape the ECG electrode wire to the skin up to the shoulder.</li>
</ol>
3. Apply the carbon wire loop (if a bipolar amplifier is available)
<ol>
	<li>Place a set of pre-braid carbon wire (diameter 1 mm)9 consisting of six loops (diameter 10 cm) over the cap in a position such that the bundle of the wires come in parallel with the bundle of the electrodes on the top of the head.</li>
	<li>Use surgical tape (1 x 2 cm) to secure the loops around the electrodes, so that the loops cover the head with each loop covering evenly almost an equal area (i.e., both the fronto-temporal, both the temporo-occipital, the occipital, and the vertex). Alternatively, one could also sew the loops to the EEG-cap, if applicable. 
	&#8203;NOTE: The carbon wire loops on the head serve to capture movement, including ballistocardiogram (BCG). These signals are used for the removal of BCG artifacts from the EEG during offline EEG processing9.</li>
</ol>
4. Securing the cap and carbon wire loops
<ol>
	<li>Make sure that the EEG electrodes are not forming loops.</li>
	<li>Wrap the subject&#39;s head with an elastic bandage over the EEG cap and the carbon loops. The bandage serves to press the EEG electrode tightly onto the skin, to reduce MRI machinery-induced vibration of the electrodes and prevent the gel from spilling onto the pillow when placing the subject inside the MR scanner (see step 5).</li>
	<li>Make sure that the bandage covers all of the electrodes and is not too tight by asking whether the subject feels uncomfortable pressure on the head while applying the bandage.</li>
</ol>
5. Placing the subject in the MR scanner
<ol>
	<li>In the case of resting-state acquisition, instruct the subject to apply MRI-compatible earbuds in the ears. In the case of task-based acquisition, instruct the subject to apply the MRI-compatible headset or earphones as per the requirement of the experiment. Make sure that the subject can hear through both sides of the headset or earphones.</li>
	<li>Place an MRI-compatible flat memory foam pillow in the lower half of the head coil before asking the subject to lie down and place the head in the coil.</li>
	<li>After positioning the head appropriately (top of the head placed as close as possible to the top of the head coil), place the electrode and carbon wire bundles straight through the top opening of the head coil.</li>
	<li>Add memory foam pillows to the top of the head, forehead, and temporal area. The pillows should appropriately fill up all spaces left within the head coil while not compressing the subject&#39;s head too tightly.
	<ol>
		<li>Make sure that the pillows are not squeezing the head while placing the upper half of the head coil and while closing the coil. Adjust the pillows or change to smaller size pillows if too tight. In this way, the pillows serve to hold the electrode wires to reduce MRI machinery-induced vibration on the electrode wires and to restrain head movements while maintaining the comfort of the subject during the scan.</li>
		<li>Place a half cylinder-shape memory foam pillow at the back of the neck so that the ECG electrode wire is sandwiched well between the pillow and the neck. The portion of ECG electrode wire that passes at the back below the shoulder is indeed sandwiched between the back of subject and the MRI table and is thus immobilized by the subject&#39;s own weight.</li>
	</ol>
	</li>
	<li>In the case of a task-based acquisition, after placing all of the memory foam pillows, make sure that the headset or earphones are not displaced by testing again if the subject can still hear through both sides of the headset or earphones. After closing the head coil, place the mirror and instruct the subject to adjust the mirror (in the case of the task that requires visual stimuli). Instruct the subject to adjust the mirror if necessary, after moving the table in order to place the subject&#39;s head at the isocenter of the MRI bore.</li>
	<li>Connect the amplifiers placed at the back of the MRI bore to the recording computer placed in the console room using the optic fibers provided.</li>
	<li>After connecting the EEG/ECG electrodes and the carbon wire loops to the EEG and the bipolar amplifiers at the back of the MRI bore, switch on the amplifiers. Again, check the impedance of all electrodes to make sure that they are still low (at least below 20 k&#937;). Remove the subject&#160;from the MR scanner for adjustment if there is any electrode with high impedance.</li>
</ol>
6. Configuration of the wires and amplifiers
<ol>
	<li>Arrange all of the wires between the outlet of the top opening of the head coil and the amplifiers (including the electrodes and carbon wire bundles, the connector box, and the ribbon wires) so that they are placed straight and at the center of the MRI bore. This is important to minimize MRI-induced current.</li>
	<li>Place one carbon wire loop around the ribbon cable going from the EEG/ECG electrodes connector box to the amplifier and connect all of the carbon wire loops (see step 5.7) to the input box of the bipolar amplifier (EXG MR). This loop serves mainly to capture the vibrations caused by the Helium pump9.</li>
	<li>To minimize MRI machinery-induced vibration, immobilize the wires by sandwiching all of them with MR-safe and non-ferromagnetic sandbags all along the way between the outlet of the top opening of the head coil and the amplifiers. Also, place sandbags on the amplifiers. These sandbags, measured 330 mm x 240 mm x 50 mm and weighing 4 kg, are supplied by the EEG manufacturer.</li>
	<li>Position the amplifiers outside the bore of the magnet, which is allowed by the length of the cables as supplied by the manufacturer.</li>
</ol>
7. EEG-fMRI data acquisition
<ol>
	<li>Make sure that the subject is comfortable with the positioning before leaving the scanner room, to avoid unnecessary subject movement during the acquisition. Instruct the subject to press the alarm button if necessary (i.e., in case of emergency or if the subject feels an uncomfortable sensation). Communicate with the subject from the console room to confirm that the subject can hear the operator. Tell the subject that loud noises are expected during data acquisition. Instruct the subject as required for the experiment, and instruct the subject not to move during data acquisition.</li>
	<li>Start the EEG recording before starting fMRI acquisition. Typically, the following images are acquired sequentially: scout images (two-dimensional) for positioning the fMRI field of view, fMRI, and structural images for co-registering the fMRI images during postprocessing. Shim sequences were run prior to acquiring each type of image for calibration of appropriate parameters. 
	NOTE: It is important to use MRI sequences that are proven safe with amplifiers to maintain safety, and to avoid any damage to the amplifiers18. Details regarding the sequences considered safe will not be discussed in detail. Readers are encouraged to consult the user manual or the support team. In general, gradient echo sequences are recommended and spin echo sequences or any sequence with equivalent RF emission parameters, which can cause excessive RF-induced heating, should be avoided. Heating can be indirectly quantified using metrics that measure the amount of RF exposure, such as specific energy absorption rate (SAR) and the root mean square value of B1+ averaged over 10 s (B1+rms). Recently, B1+rms, dependent on the imaging parameters but independent of the subjects&#39; body mass22, is becoming the new standard to specify the limit. For example, the B1+rms thresholds for acquisition at 3 T using the Brain Products EEG cap are 1 &#181;T for the current standard cap and 1.5 &#181;T for the new standard EEG cap with a shorter (10 cm) bundled cable23. Flip angle, number of slices, and repetition time (TR) are parameters that need to be considered to keep SAR and B1+rms low. A small flip angle (&#60;90&#176;) is recommended. The number of slices and TR can be adjusted as long as the resulting sequence is below the threshold of B1+rms23.</li>
	<li>Upon starting the acquisition, make sure again markers from the scanner (see 1.4) are periodically displayed in the online EEG recording.</li>
</ol>

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New MRI Safety Labels &amp; Devices Available from: <a target="_blank" href="https://www.ismrm.org/smrt/E-Signals/2016FEBRUART/eSig_5_1_hot_2.htm">https://www.ismrm.org/smrt/E-Signals/2016FEBRUART/eSig_5_1_hot_2.htm</a> (2016)</li><li>Brain Products GmbH. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Conditions+for+safe+use+of+BrainAmp+MR+amplifiers+and+accessories+in+the+MR+environment.">Conditions for safe use of BrainAmp MR amplifiers and accessories in the MR environment.</a> Performing simultaneous EEG-fMRI measurements. , 26-32 (2020).</li><li>Allen, P. 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R., Lemieux, L. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Identification+of+EEG+events+in+the+MR+scanner:+the+problem+of+pulse+artifact+and+a+method+for+its+subtraction.">Identification of EEG events in the MR scanner: the problem of pulse artifact and a method for its subtraction.</a> Neuroimage. 8 (3), 229-239 (1998).</li><li>Cecotti, H., Ries, A. J. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Best+practice+for+single-trial+detection+of+event-related+potentials:+Application+to+brain-computer+interfaces.">Best practice for single-trial detection of event-related potentials: Application to brain-computer interfaces.</a> International Journal of Psychophysiology. 111, 156-169 (2017).</li></ol>

The authors report no disclosures relevant to the manuscript.

This protocol highlighted the important points for the safe simultaneous EEG-fMRI acquisition of good quality data.
Some common errors resulting in difficult-to-remove artifacts on EEG as well as troubleshooting techniques are as follows. First, choosing subjects that are compliant and cooperative and ensuring their comfort during data acquisition can prevent premature termination due to subject movements (steps 2.1 and 5.4). Second, impedance not dropping below 20 k&#937; after repeated abrasion of the scalp (step 2.9) is most likely due to inadequate brushing after use. Thoroughly brushing each opening of the EEG electrodes when washing the cap prevents this problem. Third, inappropriate settings of the hardware and software can result in saturation of the EEG signals that subsequently hamper artifact removal during offline EEG processing. Lastly, to prevent the recording of saturated EEG signals, maintain the impedance of each electrode below 20 k&#937; after placing the subject in the MR scanner prior to data acquisition; adequately diminish mechanical vibrations by immobilizing the EEG cap (which also means the subject&#39;s head), cables and wires; monitor the raw EEG signal online with the recording software and make sure that the sampling rate and amplitude resolution are correctly set up.
The simultaneous acquisition of EEG and fMRI raises important safety issues related to RF-induced heating and switching gradient-induced currents due to the presence of electrical wires connected to the subject in the rapidly changing magnetic field5. These safety issues have been largely minimized over the years following research findings that have enhanced knowledge of this aspect and led to large improvements in the technology of MRI-compatible EEG equipment. Nevertheless, careless preparation without adequate knowledge or not taking safety precautions places the subjects in danger. For instance, loops that form anywhere within the circuit induce current and possible heat injury. Acquisition with the electrodes at high impedance not only hampers the EEG data quality but also poses a potential hazard to the subject (thermal injury due to high current density). The same hazard applies to broken electrodes. Cables placed in close proximity to the MR bore wall, in other words, far from the center, also pose a potential heating hazard to the subject (heating due to antenna effect)25. This protocol emphasizes the following safety aspects: no loops form within the circuit between the subject and the amplifier, all electrodes have low impedance during the MRI scan, and all cables are placed in the center of the bore. Beginner operators are advised to undergo training and follow the manufacturer&#39;s guidelines found in the user manual and demonstration videos20 to avoid any safety concerns.
The major causes of artifacts found on EEG-fMRI are switching gradient of the MRI, BCG, or the subject&#39;s gross or subtle movements (face movements, clenching, swallowing etc.). In some MRI setups, artifacts caused by the helium pump and ventilators also significantly compromise the EEG signals. MR gradient artifacts are rather consistent in the waveforms and can be sufficiently corrected using a template-based subtraction technique if they are fully recorded without distortion using amplifiers with a sufficient dynamic range24. BCG artifacts are usually corrected using either the subtraction technique26, independent component analysis6, optimal basis set8, or a combination of these techniques10. Recently, artifact removal using simple regression based on signals acquired simultaneously with carbon wire loops has been developed7,9. The protocol presented here illustrates the technical aspect, with the aim of providing an introductory guide for those who are interested in using this method. This method removes BCG, subtle subject movements, and helium pump artifacts and the resulting EEG signals are reportedly superior to those corrected using other methods7,9. However, larger motion artifacts, especially those containing swaying movements, are not removable even using this method7. Despite the improvement of these artifact-removal methodologies over the years, inconsistent artifacts, including those caused by MRI machinery-induced vibration are still difficult to remove. Moreover, the more extensive the artifact removal procedure, the higher the risk of losing some real EEG signals. Therefore, good preparation that can minimize the inconsistent artifacts remains most important in EEG-fMRI acquisition. In this protocol, these artifacts are minimized by using: (1) an elastic bandage to wrap the head and memory foam pillows to immobilize the head in the head coil, to reduce possible vibration of the wires while maintaining the subject&#39;s comfort; (2) cotton and medical adhesive tape to reduce vibration of the ECG electrode wire that may not be fully immobilized by the subject&#39;s own weight (partially floating between the subject and the table especially in a thin subject); and (3) sandbags to immobilize the cables placed in the MRI bore. These are important techniques to minimize difficult-to-removed MRI machinery-induced vibration artifacts, which have not been described in the previously published EEG-fMRI protocol20. In that protocol, subjects were placed in the scanner without additional wrapping over the EEG cap and padding around the head, and cables were only taped at a few points without immobilization using sandbags. Based on 20 years of experience at the Montreal Neurological Institute, we realized that those measures may contribute to the susceptibility of the electrode wires and cables to MRI machinery-induced vibration, although they are rarely emphasized in most EEG-fMRI studies6. Minimizing the MRI machinery-induced vibration subsequently leads to better quality and readability of the EEG, which is particularly useful for identifying subtle changes or events in the EEG6, such as small epileptic discharges in epilepsy studies and single-trial ERPs in neurocognitive studies.
The detection of ERPs in EEG signals is a prerequisite for cognitive neuroscience studies. In contrast to the classic grand average response across trials, ERP single-trial detection, which provides insights into brain dynamics in response to a particular stimulus, is becoming a new target in modern cognitive neuroscience studies and non-invasive brain-computer interface research27. Application of the present protocol may contribute to increasing efficiency in these research fields.
The protocol is best suited for the MRI-compatible EEG system used in this study. Nevertheless, we believe that the important points may also be applicable to other MRI-compatible EEG systems.

Functional magnetic resonance imaging (fMRI) provides a measure of neuronal activity through hemodynamic responses by measuring blood-oxygen-level-dependent (BOLD) changes during an electrographic event. Simultaneous electroencephalography (EEG) and fMRI (EEG-fMRI) is a non-invasive research tool that combines the synergic properties of scalp EEG (good temporal resolution) and fMRI (good spatial resolution), allowing better localization of the site responsible for the generation of electrographic events detectable in EEG. It was first developed in the 1990s for the use in the epilepsy field1,2 and has subsequently been used in neuroscience research since the 2000s3,4. With the increase in knowledge regarding the safety5 and continuous development of techniques for the removal of MRI-induced artifacts on EEG3,6,7,8,9,10, it is currently a tool that is widely utilized in both neuroscience and clinical research11.
EEG-fMRI is acquired either at rest or during a task, depending on the research question. In general, resting state acquisition allows the identification of structures involved in the generation of a particular EEG feature (e.g., waveform, rhythm, frequencies, power) and helps in understanding the variable spontaneous brain activities11. A number of neuroscience studies and most clinical studies, especially those on epilepsy12, acquire EEG-fMRI at rest11. Task-based acquisition allows the identification of cerebral areas and the brain electrical activities assigned or related to a specific task and helps establish the link between the electrical activities and cerebral areas associated with the task. Task-based acquisition is mainly utilized in neuroscience studies11 and some clinical studies13. Most task-based EEG-fMRI acquisitions use an event-related design. The type of modeling used for integrating EEG and fMRI data determines whether the efficiency or detection power should be maximized in designing the task14. Please see the studies by Menon et al.14 and Liu et al.15,16 for details on the task design.
Although data acquisition during EEG-fMRI may appear straightforward, the preparation is experience-demanding. A protocol for guiding proper preparation for data acquisition is important to ensure both the safety and yield (i.e., analyzable and reliable data). Despite the existence of various techniques to remove MRI-induced EEG artifacts, inconsistent artifacts in the EEG recorded, especially those related to machinery-induced vibration of the wires and subjects&#39; gross movements, are still difficult to completely remove; therefore, these artifacts need to be minimized during data acquisition.
This article presents a straightforward protocol that utilizes readily available MRI-compatible medical products. The protocol provides important steps that ensure data quality, particularly the quality of EEG data, which is key to the success of an EEG-fMRI study. This protocol was developed based on the 20-year experience of the EEG-fMRI research team at the Montreal Neurological Institute12,17 and was further modified for use at Osaka University, which benefits both inexperienced and expert operators.

<table border="1" fo:keep-together.within-page="1" fo:keep-with-next.within-page="always">
	<tbody>
		<tr>
			<td>BrainAmp EXG MR</td>
			<td>Brain Products, GmBH, Germany</td>
			<td></td>
			<td>MRI-compatible bipolar amplifier</td>
		</tr>
		<tr>
			<td>BrainAmp MR Plus</td>
			<td>Brain Products, GmBH, Germany</td>
			<td></td>
			<td>MRI-compatible EEG amplifier</td>
		</tr>
		<tr>
			<td>BrainCap MR</td>
			<td>Brain Products, GmBH, Germany</td>
			<td></td>
			<td>MRI-compatible EEG cap</td>
		</tr>
		<tr>
			<td>ESPA elastic bandage</td>
			<td>Toyobo co., Ltd.</td>
			<td></td>
			<td>elastic bandage for for wrapping the subject&#39;s head</td>
		</tr>
		<tr>
			<td>One Shot Plus P EL-II alcohol swab</td>
			<td>Shiro Jyuji, Inc.</td>
			<td></td>
			<td>Alcohol swab for preparing the skin</td>
		</tr>
		<tr>
			<td>Power Pack</td>
			<td>Brain Products, GmBH, Germany</td>
			<td></td>
			<td>MRI-compatible battery pack for electric supply of the amplifiers</td>
		</tr>
		<tr>
			<td>SyncBox</td>
			<td>Brain Products, GmBH, Germany</td>
			<td></td>
			<td>Phase synchronization between the EEG equipment and the MRI scanner</td>
		</tr>
		<tr>
			<td>USB 2 Adapter (BUA)</td>
			<td>Brain Products, GmBH, Germany</td>
			<td></td>
			<td>USB Adaptor to connect the amplifiers to the recording computer</td>
		</tr>
		<tr>
			<td>V19 abrasive conductive gel</td>
			<td>Brain Products, GmBH, Germany</td>
			<td></td>
			<td>Abrasive gel for the application of the EEG-cap</td>
		</tr>
		<tr>
			<td>Yu-ki Ban GS Medical adhesive tape</td>
			<td>Nitoms, Inc.</td>
			<td></td>
			<td>medical adhesive tape to secure the ECG electrode and carbon wire loops</td>
		</tr>
	</tbody>
</table>

reliable acquisition of electroencephalography data during simultaneous electroencephalography and functional mri

Simultaneous electroencephalography (EEG) and functional magnetic resonance imaging (fMRI), EEG-fMRI, combines the complementary properties of scalp EEG (good temporal resolution) and fMRI (good spatial resolution) to measure neuronal activity during an electrographic event, through hemodynamic responses known as blood-oxygen-level-dependent (BOLD) changes. It is a non-invasive research tool that is utilized in neuroscience research and is highly beneficial to the clinical community, especially for the management of neurological diseases, provided that proper equipment and protocols are administered during data acquisition. Although recording EEG-fMRI is apparently straightforward, the correct preparation, especially in placing and securing the electrodes, is not only important for safety but is also critical in ensuring the reliability and analyzability of the EEG data obtained. This is also the most experience-demanding part of the preparation. To address these issues, a straightforward protocol that ensures data quality was developed. This article provides a step-by-step guide for acquiring reliable EEG data during EEG-fMRI using this protocol that utilizes readily available medical products. The presented protocol can be adapted to different applications of EEG-fMRI in research and clinical settings, and may be beneficial to both inexperienced and expert operators.

Upon placing the EEG cap using this protocol, the impedance of each electrode usually drops below 20 k&#937; (Figure 1). Representative EEG signals obtained from a subject (20-year-old man) who participated in a neurocognitive study, and a different subject (19-year-old woman) who participated in an epilepsy study using this protocol in the same MR scanner are shown in Figure 2 and Figure 3, respectively. The subject who underwent neurocognitive testing was instructed to keep the eyes open but stay still while performing a visual task as instructed. The subject for the epilepsy study was instructed to close the eyes and sleep, as epileptic activities are typically more frequent during sleep. The EEG signals acquired from both studies were similar before processing (Figure 2); the MRI gradient artifact obscured the real EEG signals. The EEG signals from both studies were processed offline as follows: MRI artifacts were removed using the subtraction method24; and BCG, movements, and Helium pump artifacts were removed using the regression of signals recorded from the carbon wire loops7,9. The resultant EEG signals (Figure 3B) from both studies were of analyzable quality without visible contamination of BCG artifacts (Figure 3A). Epileptic activities were clearly seen on the EEG during the epilepsy study (Figure 3B). On the EEG acquired during the neurocognitive study, blinking, eye movement, and muscle artifacts were seen, especially in the frontal leads (Fp1 and Fp2) after artifact removal (Figure 3B) due to the nature of the study, and may be further removed using other methods depending on the need. No artifact originating from machinery vibrations was seen on post-processed EEG signals acquired during both studies (Figure 3B comparable to EEG signals acquired outside MRI as shown in&#160;Figure 3C). No artifact originating from the EEG electrodes was seen on the MR images acquired simultaneously (Figure 4).
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/62247/62247fig01.jpg" /> 
Figure 1: Representative EEG electrodes impedance that dropped below 5 k&#937; upon application of a 32-channel EEG cap on a subject who participated in a neurocognitive study. Each round colored circle represents an EEG electrode, with the electrode name written within the circle; the position of each circle represents the position of each electrode on the EEG cap. The color bar and the numbers on the right represent the range of the impedance being measured (0-5 k&#937; in this case); green color indicates that the impedance value is lower than the Good level value, and red color indicates Bad level. In this example, electrodes CP1, O1, Oz, O2, and ECG are indicated in light green, which means that the impedances of these electrodes were 2 k&#937;; the rest of the electrodes are indicated in dark green, which means that the impedances of these electrodes were 0 k&#937;. <a href="https://www.jove.com/files/ftp_upload/62247/62247fig01large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" class="xfigimg" src="/files/ftp_upload/62247/62247fig02.jpg" /> 
Figure 2: EEG signal before processing. Note that the MRI gradient artifact obscured the real EEG signals. <a href="https://www.jove.com/files/ftp_upload/62247/62247fig02large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" class="xfigimg" src="/files/ftp_upload/62247/62247fig3v2.jpg" /> 
Figure 3: Representative EEG signals from subjects who participated in neurocognitive and epilepsy studies. EEG signals on the top row were from a neurocognitive study and those on the bottom row were from an epilepsy study. EEG signals were processed offline. (A) EEG signals after MRI gradient artifact removal. The boxes in light blue indicate BCG artifacts. (B) EEG signals after artifact removal using regression of signals recorded from the carbon wire loops. (C) EEG signals recorded outside MRI using the same EEG equipment. EEG signals were shown in referential montage (reference at FCz); EEG in bipolar montage (each channel represents the voltage difference between a pair of adjacent electrodes) of the same segment is also shown for EEG acquired during an epilepsy study to ease the visualization of epileptic activities. The blue arrowheads (B and C, top row) indicate blinking (high-amplitude slow downward deflections/diphasic potentials at Fp1 and Fp2), the black arrowhead (B, top row) indicates eye movement resulting from a saccade or a spontaneous change of gaze (small, rapid deflections at Fp1 and Fp2), and the green rectangles (B, top row) indicate alpha rhythm seen on the EEG acquired during a neurocognitive study. The low-amplitude and high-frequency activities predominantly at Fp1 and Fp2 are muscle artifacts (thickening of the EEG tracing, top row). The red arrowheads (B and C, bottom row) indicate the time points at which epileptic activities were identified on EEG acquired during an epilepsy study (sharp downward or upward deflections that are sometimes followed by a slow wave). <a href="https://www.jove.com/files/ftp_upload/62247/62247fig3v2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" class="xfigimg" src="/files/ftp_upload/62247/62247fig04.jpg" /> 
Figure 4: Representative MRI data acquired from a subject using this protocol. Note that the EEG electrodes did not cause visible artifacts on the MR images acquired simultaneously. (A) magnetization prepared rapid acquisition with gradient echo image; (B) echo planar imaging. <a href="https://www.jove.com/files/ftp_upload/62247/62247fig04large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>

Watch this Scientific Journal Video about Reliable Acquisition of Electroencephalography Data during Simultaneous Electroencephalography and Functional MRI at JoVE.com

Reliable Acquisition of Electroencephalography Data during Simultaneous Electroencephalography and Functional MRI

This article provides a straightforward protocol for acquiring good quality electroencephalography (EEG) data during simultaneous EEG and functional magnetic resonance imaging by utilizing readily available medical products.

Simultaneous electroencephalography (EEG) and functional magnetic resonance imaging (fMRI), EEG-fMRI, combines the complementary properties of scalp EEG ...

reliable-acquisition-electroencephalography-data-during-simultaneous

Research

JoVE Journal

Neuroscience

4.3K Views.  Osaka University Graduate School of Medicine. Ons protocol biedt belangrijke stappen die de gegevenskwaliteit garanderen, met name de kwaliteit van elke gegevens, wat de sleutel is tot het succes van een gelijktijdig EEG-fMRI-onderzoek, maar zelden wordt benadrukt. Dit protocol is eenvoudig en gebruikt alleen direct beschikbare medische producten, daarom is het zeer gemakkelijk te volgen. Dit protocol leidt tot een betere kwaliteit en leesbaarheid van het EEG dat gelijktijdig met fMRI is verkregen, wat vooral nuttig is voor het identific...

Video: Reliable Acquisition of Electroencephalography Data during Simultaneous Electroencephalography and Functional MRI

Functional Mapping with Simultaneous MEG and EEG

We use magnetoencephalography (MEG) and electroencephalography (EEG) to locate and determine the temporal evolution in brain areas involved in the processing of simple sensory stimuli. We will use somatosensory stimuli to locate the hand somatosensory areas, auditory stimuli to locate the auditory cortices, visual stimuli in four quadrants of the visual field to locate the early visual areas. These type of experiments are used for functional mapping in epileptic and brain tumor patients to locate eloquent cortices. In basic neuroscience similar experimental protocols are used to study the orchestration of cortical activity. The acquisition protocol includes quality assurance procedures, subject preparation for the combined MEG/EEG study, and acquisition of evoked-response data with somatosensory, auditory, and visual stimuli. We also demonstrate analysis of the data using the equivalent current dipole model and cortically-constrained minimum-norm estimates. Anatomical MRI data are employed in the analysis for visualization and for deriving boundaries of tissue boundaries for forward modeling and cortical location and orientation constraints for the minimum-norm estimates.

We use magnetoencephalography (MEG) and electroencephalography (EEG) to map brain areas involved in the processing of simple sensory stimuli.

We use magnetoencephalography (MEG) and electroencephalography (EEG) to locate and determine the temporal evolution in brain areas involved in the ...

Investigating Social Cognition in Infants and Adults Using Dense Array Electroencephalography (dEEG)

Dense array electroencephalography (dEEG), which provides a non-invasive window for measuring brain activity and a temporal resolution unsurpassed by any other current brain imaging technology1,2, is being used increasingly in the study of social cognitive functioning in infants and adults. While dEEG is enabling researchers to examine brain activity patterns with unprecedented levels of sensitivity, conventional EEG recording systems continue to face certain limitations, including 1) poor spatial resolution and source localization3,4,2) the physical discomfort for test subjects of enduring the individual application of numerous electrodes to the surface of the scalp, and 3) the complexity for researchers of learning to use multiple software packages to collect and process data. Here we present an overview of an established methodology that represents a significant improvement on conventional methodologies for studying EEG in infants and adults. Although several analytical software techniques can be used to establish indirect indices of source localization to improve the spatial resolution of dEEG, the HydroCel Geodesic Sensor Net (HCGSN) by Electrical Geodesics, Inc. (EGI), a dense sensory array that maintains equal distances among adjacent recording electrodes on all surfaces of the scalp, further enhances spatial resolution4,5,6 compared to standard dEEG systems. The sponge-based HCGSN can be applied rapidly and without scalp abrasion, making it ideal for use with adults7,8, children9,10,11, and infants12, in both research and clinical4,5,6,13,14,15 settings. This feature allows for considerable cost and time savings by decreasing the average net application time compared to other dEEG systems. Moreover, the HCGSN includes unified, seamless software applications for all phases of data, greatly simplifying the collection, processing, and analysis of dEEG data.
The HCGSN features a low-profile electrode pedestal, which, when filled with electrolyte solution, creates a sealed microenvironment and an electrode-scalp interface. In all Geodesic dEEG systems, EEG sensors detect changes in voltage originating from the participant's scalp, along with a small amount of electrical noise originating from the room environment. Electrical signals from all sensors of the Geodesic sensor net are received simultaneously by the amplifier, where they are automatically processed, packaged, and sent to the data-acquisition computer (DAC). Once received by the DAC, scalp electrical activity can be isolated from artifacts for analysis using the filtering and artifact detection tools included in the EGI software. Typically, the HCGSN can be used continuously for only up to two hours because the electrolyte solution dries out over time, gradually decreasing the quality of the scalp-electrode interface.
In the Parent-Infant Research Lab at the University of Toronto, we are using dEEG to study social cognitive processes including memory, emotion, goals, intentionality, anticipation, and executive functioning in both adult and infant participants.

Investigating Social Cognition in Infants and Adults Using Dense Array Electroencephalography dEEG

Dense array electroencephalography is being used increasingly to study social cognitive functions in infants and adults. Here we present an established methodology that represents a significant improvement on conventional methodologies for studying EEG in infants and adults.

Dense array electroencephalography (dEEG), which provides a non-invasive window for measuring brain activity and a temporal resolution unsurpassed by any ...

Functional Neuroimaging Using Ultrasonic Blood-brain Barrier Disruption and Manganese-enhanced MRI

Although mice are the dominant model system for studying the genetic and molecular underpinnings of neuroscience, functional neuroimaging in mice remains technically challenging. One approach, Activation-Induced Manganese-enhanced MRI (AIM MRI), has been used successfully to map neuronal activity in rodents 1-5. In AIM MRI, Mn2+ acts a calcium analog and accumulates in depolarized neurons 6,7. Because Mn2+ shortens the T1 tissue property, regions of elevated neuronal activity will enhance in MRI. Furthermore, Mn2+ clears slowly from the activated regions; therefore, stimulation can be performed outside the magnet prior to imaging, enabling greater experimental flexibility. However, because Mn2+ does not readily cross the blood-brain barrier (BBB), the need to open the BBB has limited the use of AIM MRI, especially in mice.
One tool for opening the BBB is ultrasound. Though potentially damaging, if ultrasound is administered in combination with gas-filled microbubbles (i.e., ultrasound contrast agents), the acoustic pressure required for BBB opening is considerably lower. This combination of ultrasound and microbubbles can be used to reliably open the BBB without causing tissue damage 8-11.
Here, a method is presented for performing AIM MRI by using microbubbles and ultrasound to open the BBB. After an intravenous injection of perflutren microbubbles, an unfocused pulsed ultrasound beam is applied to the shaved mouse head for 3 minutes. For simplicity, we refer to this technique of BBB Opening with Microbubbles and UltraSound as BOMUS 12. Using BOMUS to open the BBB throughout both cerebral hemispheres, manganese is administered to the whole mouse brain. After experimental stimulation of the lightly sedated mice, AIM MRI is used to map the neuronal response.
To demonstrate this approach, herein BOMUS and AIM MRI are used to map unilateral mechanical stimulation of the vibrissae in lightly sedated mice 13. Because BOMUS can open the BBB throughout both hemispheres, the unstimulated side of the brain is used to control for nonspecific background stimulation. The resultant 3D activation map agrees well with published representations of the vibrissae regions of the barrel field cortex 14. The ultrasonic opening of the BBB is fast, noninvasive, and reversible; and thus this approach is suitable for high-throughput and/or longitudinal studies in awake mice.

A technique is described for broadly opening the blood-brain barrier in the mouse using microbubbles and ultrasound. Using this technique, manganese can be administered to the mouse brain. Because manganese is an MRI contrast agent that accumulates in depolarized neurons, this approach enables imaging of neuronal activity.

Although mice are the dominant model system for studying the genetic and molecular underpinnings of neuroscience, functional neuroimaging in mice remains ...

Simultaneous Electroencephalography, Real-time Measurement of Lactate Concentration and Optogenetic Manipulation of Neuronal Activity in the Rodent Cerebral Cortex

Although the brain represents less than 5% of the body by mass, it utilizes approximately one quarter of the glucose used by the body at rest1. The function of non rapid eye movement sleep (NREMS), the largest portion of sleep by time, is uncertain. However, one salient feature of NREMS is a significant reduction in the rate of cerebral glucose utilization relative to wakefulness2-4. This and other findings have led to the widely held belief that sleep serves a function related to cerebral metabolism. Yet, the mechanisms underlying the reduction in cerebral glucose metabolism during NREMS remain to be elucidated.
	One phenomenon associated with NREMS that might impact cerebral metabolic rate is the occurrence of slow waves, oscillations at frequencies less than 4 Hz, in the electroencephalogram5,6. These slow waves detected at the level of the skull or cerebral cortical surface reflect the oscillations of underlying neurons between a depolarized/up state and a hyperpolarized/down state7. During the down state, cells do not undergo action potentials for intervals of up to several hundred milliseconds. Restoration of ionic concentration gradients subsequent to action potentials represents a significant metabolic load on the cell8; absence of action potentials during down states associated with NREMS may contribute to reduced metabolism relative to wake.
	Two technical challenges had to be addressed in order for this hypothetical relationship to be tested. First, it was necessary to measure cerebral glycolytic metabolism with a temporal resolution reflective of the dynamics of the cerebral EEG (that is, over seconds rather than minutes). To do so, we measured the concentration of lactate, the product of aerobic glycolysis, and therefore a readout of the rate of glucose metabolism in the brains of mice. Lactate was measured using a lactate oxidase based real time sensor embedded in the frontal cortex. The sensing mechanism consists of a platinum-iridium electrode surrounded by a layer of lactate oxidase molecules. Metabolism of lactate by lactate oxidase produces hydrogen peroxide, which produces a current in the platinum-iridium electrode. So a ramping up of cerebral glycolysis provides an increase in the concentration of substrate for lactate oxidase, which then is reflected in increased current at the sensing electrode. It was additionally necessary to measure these variables while manipulating the excitability of the cerebral cortex, in order to isolate this variable from other facets of NREMS.
	We devised an experimental system for simultaneous measurement of neuronal activity via the elecetroencephalogram, measurement of glycolytic flux via a lactate biosensor, and manipulation of cerebral cortical neuronal activity via optogenetic activation of pyramidal neurons. We have utilized this system to document the relationship between sleep-related electroencephalographic waveforms and the moment-to-moment dynamics of lactate concentration in the cerebral cortex. The protocol may be useful for any individual interested in studying, in freely behaving rodents, the relationship between neuronal activity measured at the electroencephalographic level and cellular energetics within the brain.

A procedure is described for manipulating the activity of cerebral cortical pyramidal neurons optogenetically while the electroencephalogram, electromyogram, and cerebral lactate concentration are monitored. Experimental recordings are performed on cable-tethered mice while they undergo spontaneous sleep/wake cycles. Optogenetic equipment is assembled in our laboratory; recording equipment is commercially available.

Although the brain represents less than 5% of the body  by mass, it utilizes approximately one quarter of the glucose used by the body  at rest1. The ...

Optogenetic Functional MRI

The investigation of the functional connectivity of precise neural circuits across the entire intact brain can be achieved through optogenetic functional magnetic resonance imaging (ofMRI), which is a novel technique that combines the relatively high spatial resolution of high-field fMRI with the precision of optogenetic stimulation. Fiber optics that enable delivery of specific wavelengths of light deep into the brain in vivo are implanted into regions of interest in order to specifically stimulate targeted cell types that have been genetically induced to express light-sensitive trans-membrane conductance channels, called opsins. fMRI is used to provide a non-invasive method of determining the brain's global dynamic response to optogenetic stimulation of specific neural circuits through measurement of the blood-oxygen-level-dependent (BOLD) signal, which provides an indirect measurement of neuronal activity. This protocol describes the construction of fiber optic implants, the implantation surgeries, the imaging with photostimulation and the data analysis required to successfully perform ofMRI. In summary, the precise stimulation and whole-brain monitoring ability of ofMRI are crucial factors in making ofMRI a powerful tool for the study of the connectomics of the brain in both healthy and diseased states.

This protocol describes the steps and data analysis required to successfully perform optogenetic functional magnetic resonance imaging (ofMRI). ofMRI is a novel technique that combines high-field fMRI readout with optogenetic stimulation, allowing for cell type-specific mapping of functional neural circuits and their dynamics across the whole living brain.

The investigation of the functional connectivity of precise neural circuits across the entire intact brain can be achieved through optogenetic functional ...

Concurrent Recording of Co-localized Electroencephalography and Local Field Potential in Rodent

Although electroencephalography (EEG) is widely used as a non-invasive technique for recording neural activities of the brain, our understanding of the neurogenesis of EEG is still very limited. Local field potentials (LFPs) recorded via a multi-laminar microelectrode can provide a more detailed account of simultaneous neural activity across different cortical layers in the neocortex, but the technique is invasive. Combining EEG and LFP measurements in a pre-clinical model can greatly enhance understanding of the neural mechanisms involved in the generation of EEG signals, and facilitate the derivation of a more realistic and biologically accurate mathematical model of EEG. A simple procedure for acquiring concurrent and co-localized EEG and multi-laminar LFP signals in the anesthetized rodent is presented here. We also investigated whether EEG signals were significantly affected by a burr hole drilled in the skull for the insertion of a microelectrode. Our results suggest that the burr hole has a negligible impact on EEG recordings.

This protocol describes a simple method for concurrent recording of co-localized electroencephalography (EEG) and multi-laminar local field potential in an anesthetized rat. A burr hole drilled in the skull for the insertion of a microelectrode is shown to produce negligible distortion of the EEG signal.

Although electroencephalography (EEG) is widely used as a non-invasive technique for recording neural activities of the brain, our understanding of the ...

Microstate and Omega Complexity Analyses of the Resting-state Electroencephalography

Microstate and omega complexity are two reference-free electroencephalography (EEG) measures that can represent the temporal and spatial complexities of EEG data and have been widely used to investigate the neural mechanisms in some brain disorders. The goal of this article is to describe the protocol underlying EEG microstate and omega complexity analyses step by step. The main advantage of these two measures is that they could eliminate the reference-dependent problem inherent to traditional spectrum analysis. In addition, microstate analysis makes good use of high time resolution of resting-state EEG, and the four obtained microstate classes could match the corresponding resting-state networks respectively. The omega complexity characterizes the spatial complexity of the whole brain or specific brain regions, which has obvious advantage compared with traditional complexity measures focusing on the signal complexity in a single channel. These two EEG measures could complement each other to investigate the brain complexity from the temporal and spatial domain respectively.

This article describes the protocol underlying electroencephalography (EEG) microstate analysis and omega complexity analysis, which are two reference-free EEG measures and highly valuable to explore the neural mechanisms of brain disorders.

Microstate and omega complexity are two reference-free electroencephalography (EEG) measures that can represent the temporal and spatial complexities of ...

Combined Transcranial Magnetic Stimulation and Electroencephalography of the Dorsolateral Prefrontal Cortex

Transcranial magnetic stimulation (TMS) is a non-invasive method that produces neural excitation in the cortex by means of brief, time-varying magnetic field pulses. The initiation of cortical activation or its modulation depends on the background activation of the neurons of the cortical region activated, the characteristics of the coil, its position and its orientation with respect to the head. TMS combined with simultaneous electrocephalography (EEG) and neuronavigation (nTMS-EEG) allows for the assessment of cortico-cortical excitability and connectivity in almost all cortical areas in a reproducible manner. This advance makes nTMS-EEG a powerful tool that can accurately assess brain dynamics and neurophysiology in test-retest paradigms that are required for clinical trials. Limitations of this method include artifacts that cover the initial brain reactivity to stimulation. Thus, the process of removing artifacts may also extract valuable information. Moreover, the optimal parameters for dorsolateral prefrontal (DLPFC) stimulation are not fully known and current protocols utilize variations from the motor cortex (M1) stimulation paradigms. However, evolving nTMS-EEG designs hope to address these issues. The protocol presented here introduces some standard practices for assessing neurophysiological functioning from stimulation to the DLPFC that can be applied in patients with treatment resistant psychiatric disorders that receive treatment such as transcranial direct current stimulation (tDCS), repetitive transcranial magnetic stimulation (rTMS), magnetic seizure therapy (MST) or electroconvulsive therapy (ECT).

The protocol presented here is for TMS-EEG studies utilizing intracortical excitability test-retest design paradigms. The intent of the protocol is to produce reliable and reproducible cortical excitability measures for assessing neurophysiological functioning related to therapeutic interventions in the treatment of neuropsychiatric diseases such as major depression.

Transcranial magnetic stimulation (TMS) is a non-invasive method that produces neural excitation in the cortex by means of brief, time-varying magnetic ...

Data Acquisition and Analysis In Brainstem Evoked Response Audiometry In Mice

Brainstem evoked response audiometry (BERA) is of central relevance in the clinical neurophysiology. As other evoked potential (EP) techniques, such as visually evoked potentials (VEPs) or somatosensory evoked potentials (SEPs), the auditory evoked potentials (AEPs) are triggered by the repetitive presentation of identical stimuli, the electroencephalographic (EEG) response of which is subsequently averaged resulting in distinct positive (p) and negative (n) deflections. In humans, both the amplitude and the latency of individual peaks can be used to characterize alterations in synchronization and conduction velocity in the underlying neuronal circuitries. Importantly, AEPs are also applied in basic and preclinical science to identify and characterize the auditory function in pharmacological and genetic animal models. Even more, animal models in combination with pharmacological testing are utilized to investigate for potential benefits in the treatment of sensorineural hearing loss (e.g., age- or noise-induced hearing deficits). Here we provide a detailed and integrative description of how to record auditory brainstem-evoked responses (ABRs) in mice using click and tone-burst application. A specific focus of this protocol is on pre-experimental animal housing, anesthesia, ABR recording, ABR filtering processes, automated wavelet-based amplitude growth function analysis, and latency detection.

Brainstem evoked response audiometry is an important tool in clinical neurophysiology. Nowadays, brainstem evoked response audiometry is also applied in the basic science and preclinical studies involving both pharmacological and genetic animal models. Here we provide a detailed description of how auditory brainstem responses can be successfully recorded and analyzed in mice.

Brainstem evoked response audiometry (BERA) is of central relevance in the clinical neurophysiology. As other evoked potential (EP) techniques, such as ...

Conducting Concurrent Electroencephalography and Functional Near-Infrared Spectroscopy Recordings with a Flanker Task

Concurrent EEG and fNIRS recordings offer an excellent opportunity to gain a full understanding of the neural mechanism of cognitive processing by inspecting the relationship between the neural and hemodynamic signals. EEG is an electrophysiological technology that can measure the rapid neuronal activity of the cortex, whereas fNIRS relies on the hemodynamic responses to infer brain activation. The combination of EEG and fNIRS neuroimaging techniques can identify more features and reveal more information associated with the functioning of the brain. In this protocol, fused EEG-fNIRS measurements were performed for concurrent recordings of evoked-electrical potentials and hemodynamic responses during a Flanker task. In addition, the critical steps for setting up the hardware and software system as well as the procedures for data acquisition and analysis were provided and discussed in detail. It is expected that the present protocol can pave a new avenue for improving the understanding of the neural mechanisms underlying various cognitive processes by using the EEG and fNIRS signals.

The present protocol describes how to perform concurrent EEG and fNIRS recordings and how to inspect the relationship between the EEG and fNIRS data.&#160;

Reliable Acquisition of Electroencephalography Data during Simultaneous Electroencephalography and Functional MRI

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