We would like to thank Brain Products GmbH for providing their equipment, expertise and help in producing this work. We would also like to thank Glyn Spencer, University of Nottingham, in assisting with the production of the video. We also thank Engineering and Physical Science Research Council (EPSRC), EP/J006823/1 and University of Nottingham for funding this research.

1. Preparing the Experimental Setup
<ol>
	<li>Prior to the subject's arrival set up the EEG equipment in the control room where the scanner operator will sit. Connect the laptop computer to the EEG hardware as shown in Figure 1. Note: all triggers from peripheral devices and the MR scanner must have durations of more than 200 &mu;sec to be detected by the EEG system.</li>
	<li>Set up the stimulus computer; in this study, we use a visual stimulus; markers are read into the BrainVision Recorder at the beginning and end of each stimulation period.</li>
	<li>Ensure the workspace for recording the data is set to the highest temporal resolution available and correct filter settings. For the majority of studies AC-coupling with a filter of 0.016-250 Hz is optimal although DC-coupling or a higher (1 kHz) low-pass filter may be required if ultra low or high frequency neuronal signals are of interest, respectively.</li>
	<li>Check the markers from the scanner and stimulus presentation to confirm that they are being recorded by the EEG system correctly. Turn on the synchronization of the scanner and EEG clocks using the BrainVision Recorder control panel. Then check if synchronization is successful; if the set up is correct the green icon and "Sync On" dot will appear.</li>
	<li>Set up the MR scanner in the conventional way; here we're using the body transmit RF coil and a 32 channel head receive RF coil. When possible, it is best to use a head-sized transmit coil to minimize the risk of RF heating of the EEG cap and associated cables. However on most scanners, the head transmit coil cannot be used in conjunction with a multi-element receiver coil, which leads to a sub-optimal set up for acquisition of fMRI data (in particular parallel imaging speed-up is not possible). We are using this specific head receive coil because it incorporates an access port which allows the cables from the EEG cap to run along a straight path out of the scanner.</li>
	<li>Ensure the MR sequences to be run are set up. The fMRI sequence must use a slice TR which is a multiple of the EEG clock period (200 &mu;sec). If using a Philips MR system the Philips Timing calculator can be used to determine the possible slice and TR combinations.</li>
	<li>Make one final check that all equipment is recording as expected.</li>
</ol>
2. Subject Arrival
<ol>
	<li>Ask the subject to arrive with clean hair and wearing comfortable, non-metallic clothing.</li>
	<li>Explain to the subject the purpose of the experiment and what will happen.</li>
	<li>Ask the subject to fill out forms that are used to establish that there are no contra-indications for MR scanning and that the subject consents to participation in the experiment. Check the forms before proceeding. In this study the approval of the local ethics committee has been obtained and all subjects gave informed consent.</li>
	<li>Measure the head-circumference and select the appropriately sized cap (i.e. the smallest available cap that is larger than the head size). Place the cap on the head starting at the front of the head and pulling backwards. Position the cap correctly, such that Cz electrode is sited half way between the nasion and inion and also centered left-right.</li>
	<li>Connect the electrodes to the head by: moving hair out of the way, applying alcohol and then Abralyte gel. Attach the ECG electrode to the base of the back using a similar method to that used for the cap electrodes. This electrode is used to measure the heartbeat. The positioning at the base of the back is recommended to maximize the signal to noise of the R-peak in the ECG trace as well as for subject comfort.</li>
	<li>Work on the contacts so as to reduce the impedances of electrodes on the head to less than 10 k&Omega; (excluding the resistance of the internal resistors in each electrode) . ECG and EOG resistance may be higher as the signals are stronger and good connections can be hard to achieve, but must be kept below 50k&Omega;.</li>
	<li>Check the EEG data quality is satisfactory by visually inspecting the data on the monitor screen.</li>
</ol>
3. Recording Outside of the MR Scanner
(Optional: Only Required if You Wish to Compare EEG Data Quality from Inside and Outside the MR Scanner)
<ol>
	<li>Set up the presentation apparatus and EEG equipment outside the scanner (in a location where the magnetic field is low). Ensure that the setup is as similar as possible to that used inside the MR scanner (in particular the subject should be supine and a similar process of stimulus presentation should be used).</li>
	<li>Perform the experiment and record the data in a similar way to that used inside the scanner (see Section 4).</li>
</ol>
4. Setting Subject up Inside the MR Scanner
<ol>
	<li>Ask the subject to be seated whilst you set up the EEG equipment in the MR scanner room.</li>
	<li>Take the amplifier into the shielded room and place it on a table at the back of the scanner. Attach the amplifier to a long fiber optic cable. Pass the fiber optic cable through the waveguide and attach it to the BrainAmp USB adaptor in the control room (Figure 1).</li>
	<li>Register the patient in the MR scanner patient data-base.</li>
	<li>Take the subject into the room and ask them to lie on the scanner bed.</li>
	<li>Give the subject earplugs, head-phones and call button, and ensure that they are comfortable.</li>
	<li>Put the head coil over the subject's head. The EEG cables must leave the head coil along the shortest path possible. Now pad the subject's head to minimize head movement.</li>
	<li>Move the subject into the scanner bore, ensuring that electrodes Fp1 and Fp2 are at isocentre of the MR scanner in the z-direction. This is normally achieved by aligning these two electrodes with the light that is used to position the subject before they enter the bore.</li>
	<li>Attach the EEG cap to the amplifier at the rear of the scanner. Ensure that there are no wire loops in the EEG leads (as these can lead to RF heating and also cause larger EEG artifacts to be induced) and that the cabling is isolated from MR scanner vibrations as much as possible; here we use a cantilevered beam to achieve this isolation.</li>
</ol>
5. Recording Inside the Scanner
<ol>
	<li>Talk to the subject from the console room to confirm that they can hear the scanner operator and are OK.</li>
	<li>A second experimenter starts the EEG monitoring, checking for noisy electrodes in the traces, as well as for the green "Sync On" dot at the bottom of the screen.</li>
	<li>The clear effect of the cryo-pumps on the recording can be seen (see Figure 2). Therefore, switch off these pumps during data acquisition, following manufacturer guidelines.</li>
	<li>Ask the subject to move their head by a small amount. The importance of keeping the head still can be seen from the large voltages in the EEG recording that result from small head movements.</li>
	<li>Test the recording of neuronal activity by asking the subject to open and close their eyes. Look for occipital alpha activity. This will test whether you are measuring physiological signals rather than noise. If an alpha signal cannot be seen on a subject (which occurs in some subjects) it is possible to test for neuronal activity by performing a short run of the experimental paradigm without the MR scanner running and to look for the averaged evoked potential.</li>
	<li>The pulse artifact can clearly be seen in the raw data (see Figure 2) particularly on electrodes over the temples. Use the ECG trace to correct this artifact in real time using RecView (or in post processing software packages).</li>
	<li>As soon as each MRI scan begins the gradients will cause large artifacts in the EEG data.</li>
	<li>When the fMRI experiment is ready to start, - with the stimulus presentation system in a ready state - then begin saving the EEG data by following the steps shown.</li>
	<li>Now start the experiment, checking that the markers from the stimulus presentation and the MR scanner can be seen in BrainVision Recorder. Here the stimulus consists of a full-field radial checkerboard at 100% contrast. The reversal rate is 2 Hz such that an evoked response will occur every 500 msec and a marker is placed in the EEG file at each image reversal.</li>
	<li>The EEG data quality will appear to be very poor, but it can be cleaned up, either on-line in RecView or during post processing. In order for the gradient artefact correction to work without compromising the recording of neuronal signals, the stimulus presentation must not be locked to the TR and the frequency of stimulus repetition must not be equal to the slice repetition frequency.</li>
	<li>Gradient artefact correction must be carried out prior to pulse artefact correction (see Figures 3 and 4). Data may then be segmented according to stimulus presentation and analyzed with numerous techniques; the simplest of which is averaging for investigation of evoked responses (see Figure 6).</li>
</ol>
6. Debriefing the Subject
<ol>
	<li>Once the scanning is complete, take the subject out of the scanner and help them to take off the EEG cap.</li>
	<li>Allow them to wash their hair.</li>
	<li>They are now free to leave.</li>
</ol>
7. Clearing up at the End of Experiment
<ol>
	<li>Pack up the EEG equipment as required by your laboratory. If the MR manufacturer requires it, make sure that the synchronization hardware is unplugged at the end of each session and not left attached to the scanner electronics.</li>
	<li>Finally, the EEG cap must be cleaned. To do this, soak the cap in water (normally for approximately 5 min) or a water and disinfectant mixture (the disinfectant should be selected according relevant pathogen spectrum and disinfectant recommendation of the cap manufacturer. Exposure time and disinfectant concentration must follow the guidelines of the disinfectant manufacturer.). Then use a toothbrush to clean away residual gel. It is very important to clean the cap fully to ensure the proper performance of the cap when subsequently used.</li>
</ol>
8. Analysis
<ol>
	<li>Here, real time EEG analysis has been demonstrated, however it is also possible and normally desirable to post-process the EEG data. This can be done in a number of analysis packages such as Brain Products Analyzer 2 or EEGLAB.</li>
	<li>Gradient and pulse artifact correction can be performed using a variety of methods such as: average artifact subtraction18,19 (commonly used for gradient correction and often used for pulse artifact correction), independent component analysis20,21 or optimal basis sets22 (for pulse artifact correction).</li>
	<li>Data may then be analyzed in the time or frequency domain to look at evoked responses and on-going oscillatory activity.</li>
	<li>Here, we recorded the ECG trace using the Brain Products system so as to obtain information necessary for pulse artifact correction. In the standard setup the ECG trace is recorded by means of a dedicated electrode placed on the back of the subject. In our lab we use also a non-standard solution, which employs a vectrocardiogram to generate the cardiac trace (this solution is available only with the Philips physiological monitoring equipment). We have found this can be useful if a clean trace cannot be obtained using the conventional ECG set-up.</li>
</ol>

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The production of this article was sponsored by Brain Products GmbH. Pierluigi Castellone is an employee of Brain Products GmbH, which manufactures some instruments and software used in this article.

General Advice Since the physical layout of all scanner rooms is different we recognize that you may not be able to position your EEG amplifiers outside the bore of the magnet. In this case a good compromise is to place the amplifiers on a thick rubber pad so as to decouple them from the scanner vibrations as much possible. If you find that the gradient artifact correction is not working well, then check the times between volume or slice markers, as it is likely in this case that the TR that has been input to the MR console is not precisely the TR that is being generated. In this case you will need to contact the relevant MR scanner manufacturer for further assistance.
The most important steps in the process of EEG data acquisition during simultaneous fMRI are those taken to ensure that all external noise sources have been minimized (e.g. cyrocooler pumps and vibration of the EEG equipment). To allow optimal gradient artifact correction it is important to ensure that the EEG and MR scanner clocks are synchronized, the slice TR is a multiple of the scanner clock period and that the subject is optimally positioned. To ensure optimal pulse artifact correction many techniques require a clean cardiac trace from which R-peaks can be detected, we suggest that this can be best achieved using a VCG, although it is also possible with a well-positioned ECG lead. If using the ECG then it is recommended to place this at the base of the back to maximize the signal to noise ratio of the R-peak with the added benefit of this being an easier site to access than a position near the heart23. Positioning the ECG lead on the chest results in motion artifacts due to respiration being added to the trace from this lead as well as causing the gradient artifact to vary over time. This can result in the trace saturating and/or gradient artifact correction not working due to template variability and therefore is not recommended.
General Discussion EEG-fMRI is a powerful tool for studying brain function, as the high temporal resolution of EEG can be combined with the high spatial resolution of fMRI. To date, a number of studies have used this multi-modal approach to gain a better understanding of brain function. EEG-fMRI has been applied to healthy volunteers in order to investigate the correlation between oscillatory rhythms (measured with EEG) and blood oxygenation responses (using BOLD fMRI) e.g. 2,3. It has also been used to study whether characteristics of the evoked signal can explain the variance in the BOLD signal on a trial-by- trial basis4,5. In clinical studies the main use of the technique has been to investigate the foci of interictal epileptic discharges which are inherently difficult to localize non-invasively6,7. These examples show the power of this multi-modal imaging tool. However, to enable the study of such phenomena, it is important to have access to the best possible quality of EEG and MRI data. To achieve this inside the MR scanner it is important to have the best experimental set-up and also to choose the most appropriate analysis methods. The optimal analysis methods will to some extent depend upon the research question of interest, as will the correction methods used for removal of artifacts. For example the size and number of movements that have occurred during the recording will determine the most effective combination of algorithms for removing the gradient artifact. However, the optimal experimental set-up of the EEG and fMRI hardware is relatively independent of particular research questions. The guidelines outlined here are therefore of general value and can be followed in experiments using different EEG and MR scanner hardware than we used.
Here we have demonstrated the acquisition methods which should be followed to acquire high quality EEG and fMRI data. We used a visual stimulus based on a previously employed stimulus paradigm 24. However, the same techniques for data acquisition can be applied regardless of the paradigm used to stimulate the brain activity of interest. When choosing your paradigm it should be noted that the quality of the EEG data that can be achieved when recording inside the MR environment with the techniques currently available to users (and described here) still place some limitations on the brain activity which may be studied: there are particular difficulties in recording EEG activity in low (&lt;5 Hz) and high frequency (&gt;80 Hz) bands where residual pulse and gradient artifacts may reside. Additionally, care must be taken when choosing the paradigm so that the possibility of subject movement related to the task is minimized. This is a problem because motion artifacts in the EEG data are often difficult to correct and small artifacts can be difficult to identify clearly, although they still may dominate neuronal signals. These motion artifacts can cause spurious but plausible correlations with the fMRI data17.
Post-processing methods for simultaneous EEG-fMRI are numerous and as such their discussion is beyond the scope of this work. As previously mentioned the gradient and pulse artifact can be removed using a number of techniques which include average artifact subtraction18,19, independent component analysis20,21, optimal basis sets22 and beamformers25. Often a combination of these methods may be employed23 and the performance of the methods is dependent upon factors such as the magnetic field strength and the paradigm used. The optimal post-processing methods for a specific study will also depend on the signals to extract from the data, whether these are oscillatory rhythms or evoked potentials may have an influence on the post-processing methods employed.
Whilst there is considerable on-going research targeting improved data acquisition and analysis methods for simultaneous EEG-fMRI, it is already possible, using the techniques described here, to answer important neuroscience questions which require the combination of the high spatial resolution of fMRI and the excellent temporal resolution of EEG.

Simultaneous electroencephalography (EEG) and functional Magnetic Resonance imaging (fMRI) allows the excellent temporal resolution of EEG to be combined with the high spatial accuracy of fMRI. There are a number of ways in which the data from these two modalities can be combined 1, but all rely on the acquisition of high quality EEG and fMRI data. To date, simultaneous EEG-fMRI has been used to study the correlation between oscillatory rhythms (measured with EEG) and blood oxygenation responses (using blood oxygenation level dependent (BOLD) fMRI) e.g. 2,3. It has also been used to study whether the characteristics of the evoked signal can explain the variance in the BOLD signal on a trial-by- trial basis4,5. In clinical studies the main use of the technique has been to investigate the foci of interictal epileptic discharges, which can help in surgical planning and are currently difficult to localize non-invasively6,7. To achieve the fusion of EEG and fMRI data which is desired, it is essential to have high quality data from both modalities. However, EEG data acquired during simultaneous fMRI are affected by several artifacts, including the gradient artefact (due to the changing magnetic fields required for fMRI), the pulse artefact (linked to the cardiac cycle) and movement artifacts (resulting from movements in the strong magnetic field of the scanner, as well as muscle activity). These artifacts are significantly larger than the neuronal activity of interest and therefore reduction (at source) and correction of the artifacts (via post-processing) are both needed to enable successful implementation of simultaneous EEG-fMRI.
The post-processing methods currently available for correcting the gradient and pulse artifacts require a number of criteria to be satisfied during data acquisition in order to produce high quality EEG data. Over the previous decade the optimal experimental set-up for recording high quality data has evolved as our understanding of the causes of the artifacts 8-10 has improved and we have learnt how to modify experimental methods so as to reduce the artifacts at source 11,12 and to improve the performance of post-processing correction algorithms. These developments include improving the sampling of the gradient waveforms through synchronization of scanner clocks 13,14 and use of a vectocardiogram15,16 to provide a cleaner cardiac trace than the traditional ECG. The vectocardiogram trace is derived from four electrodes placed on the chest with a stringent low-pass filter employed14-16. As a result the trace is relatively unaffected by gradient artifacts and is insensitive to the blood flow artifact making R-peak detection easier. However, the facility to record a vectocardiogram is not available on all MRI scanners and therefore will only be mentioned briefly in this study. The importance of the minimization of artifacts and stringent cleaning of data has been highlighted by the recent demonstration that motion artifacts recorded in the EEG data can correlate with BOLD activity unrelated to the task of interest, producing spurious results if extreme care is not taken throughout the experimental process 17.
The method presented here represents the current optimal approach for obtaining high quality EEG and fMRI data simultaneously using MR hardware and pulse sequences which are widely available, along with commercially supplied EEG equipment. Implementation of the suggested acquisition method, in conjunction with the use of appropriate post-processing methods, will yield EEG and fMRI data that can be used to answer a number of important neuroscience questions.

<table border="1">
	<tbody>
		<tr>
			<td>Name of Reagent/Material</td>
			<td>Company</td>
			<td>Catalog Number</td>
			<td>Comments</td>
		</tr>
		<tr>
			<td>3T MR scanner</td>
			<td>&nbsp;</td>
			<td>&nbsp;</td>
			<td>Here we use a Philips Achieva but any MR scanner should work.</td>
		</tr>
		<tr>
			<td>BrainVision Recorder</td>
			<td>Brain Products GmbH</td>
			<td>BP-00010</td>
			<td>1st License item</td>
		</tr>
		<tr>
			<td>BrainVision RecView</td>
			<td>Brain Products GmbH</td>
			<td>BP-00051</td>
			<td>basis module</td>
		</tr>
		<tr>
			<td>BrainAmp MR plus</td>
			<td>Brain Products GmbH</td>
			<td>BP-01840</td>
			<td>single amplifier</td>
		</tr>
		<tr>
			<td>BrainAmp USB Adapter</td>
			<td>Brain Products GmbH</td>
			<td>BP-02041</td>
			<td>BUA64</td>
		</tr>
		<tr>
			<td>SyncBox</td>
			<td>Brain Products GmbH</td>
			<td>BP-02675</td>
			<td>SyncBox complete</td>
		</tr>
		<tr>
			<td>Fibre Optic cables and USB connectors</td>
			<td>Brain Products GmbH</td>
			<td>BP-02300 (FOC5) BP-02310 (FOC20) BP-02042 USB2 Cable)</td>
			<td>These come with the above listed equipment.</td>
		</tr>
		<tr>
			<td>BrainCap MR</td>
			<td>EASYCAP GmbH</td>
			<td>BP-03000-MR</td>
			<td>32 channel EEG cap for use in MR</td>
		</tr>
		<tr>
			<td>Abralyte 2000 conductive Gel</td>
			<td>Brain Products GmbH</td>
			<td>FMS-060219</td>
			<td>Conductive and abrasive gel to connect electrodes to scalp</td>
		</tr>
		<tr>
			<td>Isopropyl Alcohol BP</td>
			<td>Brain Products GmbH</td>
			<td>FMS-060224</td>
			<td>To be applied before Abralyte Gel. Isopropylalcohol 70% (60 ml)-for degreasing the skin</td>
		</tr>
		<tr>
			<td>Cotton tipped swab</td>
			<td>Brain Products GmbH</td>
			<td>FMS-060234</td>
			<td>For application of Abralyte and Isopropyl Alcohol. Cotton Swabs Non-sterile, 100 pieces</td>
		</tr>
	</tbody>
</table>

best current practice for obtaining high quality eeg data during simultaneous fmri

Simultaneous EEG-fMRI allows the excellent temporal resolution of EEG to be combined with the high spatial accuracy of fMRI. The data from these two modalities can be combined in a number of ways, but all rely on the acquisition of high quality EEG and fMRI data. EEG data acquired during simultaneous fMRI are affected by several artifacts, including the gradient artefact (due to the changing magnetic field gradients required for fMRI), the pulse artefact (linked to the cardiac cycle) and movement artifacts (resulting from movements in the strong magnetic field of the scanner, and muscle activity). Post-processing methods for successfully correcting the gradient and pulse artifacts require a number of criteria to be satisfied during data acquisition. Minimizing head motion during EEG-fMRI is also imperative for limiting the generation of artifacts.
Interactions between the radio frequency (RF) pulses required for MRI and the EEG hardware may occur and can cause heating. This is only a significant risk if safety guidelines are not satisfied. Hardware design and set-up, as well as careful selection of which MR sequences are run with the EEG hardware present must therefore be considered.
The above issues highlight the importance of the choice of the experimental protocol employed when performing a simultaneous EEG-fMRI experiment. Based on previous research we describe an optimal experimental set-up. This provides high quality EEG data during simultaneous fMRI when using commercial EEG and fMRI systems, with safety risks to the subject minimized. We demonstrate this set-up in an EEG-fMRI experiment using a simple visual stimulus. However, much more complex stimuli can be used. Here we show the EEG-fMRI set-up using a Brain Products GmbH (Gilching, Germany) MRplus, 32 channel EEG system in conjunction with a Philips Achieva (Best, Netherlands) 3T MR scanner, although many of the techniques are transferable to other systems.

Figure 3 shows the signal quality to be expected when no artifact correction has been performed. It is clear that any neuronal activity is obscured. Figure 3C shows that the gradient artifact occurs at distinct frequencies which are harmonics of the frequency of slice acquisition in the fMRI sequence, spanning the entire frequency range of the recording. Figure 4 shows the pulse artifact which is revealed once the gradient artifact has been removed using the post-processing method of average artifact subtraction in Analyzer 2 (version 2.0.2). It is clear that there is considerable spatial variation of this artifact and that O1, one of the channels of interest for this visual experiment, displays a particularly large pulse artifact. This artifact has a lower frequency than the gradient artifact (mainly below 10 Hz - Figure 4C) and is linked to the cardiac activity. Figure 5 shows the EEG data quality that can be achieved after gradient and pulse artifact correction; here the pulse artifact was corrected using average artifact subtraction in Analyzer 2 and the R-peaks of the cardiac waveform were detected from the ECG trace. It is clear that the amplitude of the remaining signals are far smaller and therefore neuronal signals are no longer obscured, as shown by the evoked responses obtained in Figures 6 and 7. Figure 6 shows a typical evoked response produced by averaging across all 300 stimuli. However, the variability of this response across blocks can be seen in Figure 7 and it is this natural and unpredictable variation in neuronal responses which may be used to interrogate correlations between the BOLD and EEG responses when simultaneous recordings have been performed.
<img alt="Figure 1" fo:content-width="6in" fo:src="/files/ftp_upload/50283/50283fig1highres.jpg" src="/files/ftp_upload/50283/50283fig1.jpg" /> 
 Figure 1. A schematic diagram of the set-up of the EEG equipment and the connections required between hardware, as described in the protocol. <a href="https://www.jove.com/files/ftp_upload/50283/50283fig1large.jpg" target="_blank"> Click here to view larger figure</a>.
<img alt="Figure 2" fo:content-width="4.5in" fo:src="/files/ftp_upload/50283/50283fig2highres.jpg" src="/files/ftp_upload/50283/50283fig2.jpg" /> 
 Figure 2. Fourier transform of the signal collected on a subject lying still with the cryo-pumps on (red) and off (black) for a representative channel (P7).
<img alt="Figure 3" fo:content-width="2.5in" fo:src="/files/ftp_upload/50283/50283fig3highres.jpg" src="/files/ftp_upload/50283/50283fig3.jpg" /> 
 Figure 3. Ten seconds of raw EEG data recorded during concurrent MRI on 16 different channels (A); focusing on 5 seconds of data from Oz (B); with the associated Fourier transform (C). <a href="https://www.jove.com/files/ftp_upload/50283/50283fig3large.jpg" target="_blank">Click here to view larger figure</a>.
 
<img alt="Figure 4" fo:content-width="2.5in" fo:src="/files/ftp_upload/50283/50283fig4highres.jpg" src="/files/ftp_upload/50283/50283fig4.jpg" /> 
 Figure 4. Ten seconds of EEG data recorded on 16 different channels during concurrent MRI shown after gradient artefact correction using AAS on 16 different channels (A); focusing on 5 seconds of data from Oz (B); with the associated Fourier transform (C). <a href="https://www.jove.com/files/ftp_upload/50283/50283fig4large.jpg" target="_blank">Click here to view larger figure</a>.
 
<img alt="Figure 5" fo:content-width="2.4in" fo:src="/files/ftp_upload/50283/50283fig5highres.jpg" src="/files/ftp_upload/50283/50283fig5.jpg" /> 
 Figure 5. Ten seconds of EEG data recorded on16 different channels during concurrent fMRI, shown after gradient and pulse artefact correction using AAS (A); focusing on 5 seconds of data from Oz (B); with the associated Fourier transform (C). <a href="https://www.jove.com/files/ftp_upload/50283/50283fig5large.jpg" target="_blank">Click here to view larger figure</a>.
 
<img alt="Figure 6" fo:content-width="4.5in" fo:src="/files/ftp_upload/50283/50283fig6highres.jpg" src="/files/ftp_upload/50283/50283fig6.jpg" /> 
 Figure 6. Average EEG evoked response (300 averages) for channels 01 and 02 (left) and associated topographic map for the P120 (right).
<img alt="Figure 7" fo:content-width="4in" fo:src="/files/ftp_upload/50283/50283fig7highres.jpg" src="/files/ftp_upload/50283/50283fig7.jpg" /> 
 Figure 7. Variation of evoked response across blocks for channel O1 (responses have been averaged within 30 sec blocks).

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Best Current Practice for Obtaining High Quality EEG Data During Simultaneous fMRI

Simultaneous electroencephalography (EEG) and functional Magnetic Resonance imaging (fMRI) is a powerful neuroimaging tool. However, the inside of an MRI scanner forms a difficult environment for EEG data recording and safety must be considered whenever operating EEG equipment inside a scanner. Here, we present an optimised EEG-fMRI data acquisition protocol.

Simultaneous  EEG-fMRI allows the excellent temporal resolution of EEG to be combined with the  high spatial accuracy of fMRI. The data  from these two ...

best-current-practice-for-obtaining-high-quality-eeg-data-during

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32.3K Views.  University of Nottingham. Simultaneous electroencephalography (EEG) and functional Magnetic Resonance imaging (fMRI) is a powerful neuroimaging tool. However, the inside of an MRI scanner forms a difficult environment for EEG data recording and safety must be considered whenever operating EEG equipment inside a scanner. Here, we present an optimised EEG-fMRI data acquisition protocol.

Video: Best Current Practice for Obtaining High Quality EEG Data During Simultaneous fMRI

Method for Simultaneous fMRI/EEG Data Collection during a Focused Attention Suggestion for Differential Thermal Sensation

In the present work, we demonstrate a method for concurrent collection of EEG/fMRI data. In our setup, EEG data are collected using a high-density 256-channel sensor net. The EEG amplifier itself is contained in a field isolation containment system (FICS), and MRI clock signals are synchronized with EEG data collection for subsequent MR artifact characterization and removal. We demonstrate this method first for resting state data collection. Thereafter, we demonstrate a protocol for EEG/fMRI data recording, while subjects listen to a tape asking them to visualize that their left hand is immersed in a cold-water bath and referred to, here, as the cold glove paradigm. Thermal differentials between each hand are measured throughout EEG/fMRI data collection using an MR compatible temperature sensor that we developed for this purpose. We collect cold glove EEG/fMRI data along with simultaneous differential hand temperature measurements both before and after hypnotic induction. Between pre and post sessions, single modality EEG data are collected during the hypnotic induction and depth assessment process. Our representative results demonstrate that significant changes in the EEG power spectrum can be measured during hypnotic induction, and that hand temperature changes during the cold glove paradigm can be detected rapidly using our MR compatible differential thermometry device.

We present a protocol for concurrent collection of EEG/fMRI data, and synchronized MR clock signal recording. We demonstrate this method using a unique paradigm whereby subjects receive &#x2018;cold glove&#x2019; instructions during scanning, and EEG/fMRI data are recorded along with hand temperature measurements both before and after hypnotic induction.

In the present work, we demonstrate a method for concurrent collection of EEG/fMRI data. In our setup, EEG data are collected using a high-density ...

Simultaneous EEG Monitoring During Transcranial Direct Current Stimulation

Transcranial direct current stimulation (tDCS) is a technique that delivers weak electric currents through the scalp. This constant electric current induces shifts in neuronal membrane excitability, resulting in secondary changes in cortical activity. Although tDCS has most of its neuromodulatory effects on the underlying cortex, tDCS effects can also be observed in distant neural networks. Therefore, concomitant EEG monitoring of the effects of tDCS can provide valuable information on the mechanisms of tDCS. In addition, EEG findings can be an important surrogate marker for the effects of tDCS and thus can be used to optimize its parameters. This combined EEG-tDCS system can also be used for preventive treatment of neurological conditions characterized by abnormal peaks of cortical excitability, such as seizures. Such a system would be the basis of a non-invasive closed-loop device. In this article, we present a novel device that is capable of utilizing tDCS and EEG simultaneously. For that, we describe in a step-by-step fashion the main procedures of the application of this device using schematic figures, tables and video demonstrations. Additionally, we provide a literature review on clinical uses of tDCS and its cortical effects measured by EEG techniques.

Transcranial direct current stimulation (tDCS) is a non-invasive brain stimulation technique that has shown initial therapeutic effects in several neurological conditions. The main mechanism underlying these therapeutic effects is the modulation of cortical excitability. Therefore, online monitoring of cortical excitability would help guide stimulation parameters and optimize its therapeutic effects. In the present article we review the use of a novel device that combines simultaneous tDCS and EEG monitoring in real time.

Transcranial  direct current stimulation (tDCS) is a technique that delivers weak electric  currents through the scalp. This constant electric current ...

Simultaneous Scalp Electroencephalography (EEG), Electromyography (EMG), and Whole-body Segmental Inertial Recording for Multi-modal Neural Decoding

Recent studies support the involvement of supraspinal networks in control of bipedal human walking. Part of this evidence encompasses studies, including our previous work, demonstrating that gait kinematics and limb coordination during treadmill walking can be inferred from the scalp electroencephalogram (EEG) with reasonably high decoding accuracies. These results provide impetus for development of non-invasive brain-machine-interface (BMI) systems for use in restoration and/or augmentation of gait- a primary goal of rehabilitation research. To date, studies examining EEG decoding of activity during gait have been limited to treadmill walking in a controlled environment. However, to be practically viable a BMI system must be applicable for use in everyday locomotor tasks such as over ground walking and turning. Here, we present a novel protocol for non-invasive collection of brain activity (EEG), muscle activity (electromyography (EMG)), and whole-body kinematic data (head, torso, and limb trajectories) during both treadmill and over ground walking tasks. By collecting these data in the uncontrolled environment insight can be gained regarding the feasibility of decoding unconstrained gait and surface EMG from scalp EEG.

Simultaneous Scalp Electroencephalography EEG, Electromyography EMG, and Whole-body Segmental Inertial Recording for Multi-modal Neural Decoding

Development of an effective brain-machine-interface (BMI) system for restoration and rehabilitation of bipedal locomotion requires accurate decoding of user's intent. Here we present a novel experimental protocol and data collection technique for simultaneous non-invasive acquisition of neural activity, muscle activity, and whole-body kinematics during various locomotion tasks and conditions.

Recent  studies support the involvement of supraspinal networks in control of bipedal  human walking. Part of this evidence  encompasses studies, ...

Cortical Source Analysis of High-Density EEG Recordings in Children

EEG is traditionally described as a neuroimaging technique with high temporal and low spatial resolution. Recent advances in biophysical modelling and signal processing make it possible to exploit information from other imaging modalities like structural MRI that provide high spatial resolution to overcome this constraint1. This is especially useful for investigations that require high resolution in the temporal as well as spatial domain. In addition, due to the easy application and low cost of EEG recordings, EEG is often the method of choice when working with populations, such as young children, that do not tolerate functional MRI scans well. However, in order to investigate which neural substrates are involved, anatomical information from structural MRI is still needed. Most EEG analysis packages work with standard head models that are based on adult anatomy. The accuracy of these models when used for children is limited2, because the composition and spatial configuration of head tissues changes dramatically over development3.&#160;
In the present paper, we provide an overview of our recent work in utilizing head models based on individual structural MRI scans or age specific head models to reconstruct the cortical generators of high density EEG. This article describes how&#160;EEG recordings are acquired, processed, and analyzed with pediatric populations at the London Baby Lab, including laboratory setup, task design, EEG preprocessing, MRI processing, and EEG channel level and source analysis.&#160;

In recent years, there has been increasing interest in estimating the cortical sources of scalp measured electrical activity for cognitive neuroscience experiments. This article describes how high density EEG is acquired and how recordings are processed for cortical source estimation in children from the age of 2 years at the London Baby Lab.

EEG is traditionally described as a neuroimaging technique with high temporal and low spatial resolution. Recent advances in biophysical modelling and ...

Transcranial Direct Current Stimulation and Simultaneous  Functional Magnetic Resonance Imaging

Transcranial direct current stimulation (tDCS) is a noninvasive brain stimulation technique that uses weak electrical currents administered to the scalp to manipulate cortical excitability and, consequently, behavior and brain function. In the last decade, numerous studies have addressed short-term and long-term effects of tDCS on different measures of behavioral performance during motor and cognitive tasks, both in healthy individuals and in a number of different patient populations. So far, however, little is known about the neural underpinnings of tDCS-action in humans with regard to large-scale brain networks. This issue can be addressed by combining tDCS with functional brain imaging techniques like functional magnetic resonance imaging (fMRI) or electroencephalography (EEG).
In particular, fMRI is the most widely used brain imaging technique to investigate the neural mechanisms underlying cognition and motor functions. Application of tDCS during fMRI allows analysis of the neural mechanisms underlying behavioral tDCS effects with high spatial resolution across the entire brain. Recent studies using this technique identified stimulation induced changes in task-related functional brain activity at the stimulation site&#160;and also in more distant brain regions, which were associated with behavioral improvement. In addition, tDCS administered during resting-state fMRI allowed identification of widespread changes in whole brain functional connectivity.
Future studies using this combined protocol should yield new insights into the mechanisms of tDCS action in health and disease and new options for more targeted application of tDCS in research and clinical settings. The present manuscript describes this novel technique in a step-by-step fashion, with a focus on technical aspects of tDCS administered during fMRI.

Transcranial direct current stimulation (tDCS) is a noninvasive brain stimulation technique. It has successfully been used in basic research and clinical settings to modulate brain function in humans. This article describes the implementation of tDCS and simultaneous functional magnetic resonance imaging (fMRI), to investigate the neural basis of tDCS effects.

Transcranial direct current stimulation (tDCS) is a noninvasive brain stimulation technique that uses weak electrical currents administered to the scalp ...

Topographical Estimation of Visual Population Receptive Fields by fMRI

Visual cortex is retinotopically organized so that neighboring populations of cells map to neighboring parts of the visual field. Functional magnetic resonance imaging allows us to estimate voxel-based population receptive fields (pRF), i.e., the part of the visual field that activates the cells within each voxel. Prior, direct, pRF estimation methods1 suffer from certain limitations: 1) the pRF model is chosen a-priori and may not fully capture the actual pRF shape, and 2) pRF centers are prone to mislocalization near the border of the stimulus space. Here a new topographical pRF estimation method2 is proposed that largely circumvents these limitations. A linear model is used to predict the Blood Oxygen Level-Dependent (BOLD) signal by convolving the linear response of the pRF to the visual stimulus with the canonical hemodynamic response function. PRF topography is represented as a weight vector whose components represent the strength of the aggregate response of voxel neurons to stimuli presented at different visual field locations. The resulting linear equations can be solved for the pRF weight vector using ridge regression3, yielding the pRF topography. A pRF model that is matched to the estimated topography can then be chosen post-hoc, thereby improving the estimates of pRF parameters such as pRF-center location, pRF orientation, size, etc. Having the pRF topography available also allows the visual verification of pRF parameter estimates allowing the extraction of various pRF properties without having to make a-priori assumptions about the pRF structure. This approach promises to be particularly useful for investigating the pRF organization of patients with disorders of the visual system.

It is important to obtain unbiased estimates of visual population receptive fields (pRFs) by functional magnetic resonance imaging. We use mild regularization constraints to estimate pRF topography without a-priori assumptions about pRF shape, allowing us to choose specific pRF models post-hoc. This is particularly advantageous in subjects with visual-pathway lesions.

Visual cortex is retinotopically organized so that neighboring populations of cells map to neighboring parts of the visual field. Functional magnetic ...

fMRI Validation of fNIRS Measurements During a Naturalistic Task

We present a method to compare brain activity recorded with near-infrared spectroscopy (fNIRS) in a dance video game task to that recorded in a reduced version of the task using fMRI (functional magnetic resonance imaging). Recently, it has been shown that fNIRS can accurately record functional brain activities equivalent to those concurrently recorded with functional magnetic resonance imaging for classic psychophysical tasks and simple finger tapping paradigms. However, an often quoted benefit of fNIRS is that the technique allows for studying neural mechanisms of complex, naturalistic behaviors that are not possible using the constrained environment of fMRI. Our goal was to extend the findings of previous studies that have shown high correlation between concurrently recorded fNIRS and fMRI signals to compare neural recordings obtained in fMRI procedures to those separately obtained in naturalistic fNIRS experiments. Specifically, we developed a modified version of the dance video game Dance Dance Revolution (DDR) to be compatible with both fMRI and fNIRS imaging procedures. In this methodology we explain the modifications to the software and hardware for compatibility with each technique as well as the scanning and calibration procedures used to obtain representative results. The results of the study show a task-related increase in oxyhemoglobin in both modalities and demonstrate that it is possible to replicate the findings of fMRI using fNIRS in a naturalistic task. This technique represents a methodology to compare fMRI imaging paradigms which utilize a reduced-world environment to fNIRS in closer approximation to naturalistic, full-body activities and behaviors. Further development of this technique may apply to neurodegenerative diseases, such as Parkinson&#8217;s disease, late states of dementia, or those with magnetic susceptibility which are contraindicated for fMRI scanning.

We present a method to compare functional brain activity recorded during a naturalistic task using fNIRS with activity recorded during fMRI.

We present a method to compare brain activity recorded with near-infrared spectroscopy (fNIRS) in a dance video game task to that recorded in a reduced ...

Concurrent Electroencephalography Recording During Transcranial Alternating Current Stimulation (tACS)

Oscillatory brain activities are considered to reflect the basis of rhythmic changes in transmission efficacy across brain networks and are assumed to integrate cognitive neural processes. Transcranial alternating current stimulation (tACS) holds the promise to elucidate the causal link between specific frequencies of oscillatory brain activity and cognitive processes. Simultaneous electroencephalography (EEG) recording during tACS would offer an opportunity to directly explore immediate neurophysiological effects of tACS. However, it is not trivial to measure EEG signals during tACS, as tACS creates a huge artifact in EEG data. Here we explain how to set up concurrent tACS-EEG experiments. Two necessary considerations for successful EEG recording while applying tACS are highlighted. First, bridging of the tACS and EEG electrodes via leaking EEG gel immediately saturates the EEG amplifier. To avoid bridging via gel, the viscosity of the EEG gel is the most important parameter. The EEG gel must be viscous to avoid bridging, but at the same time sufficiently fluid to create contact between the tACS electrode and the scalp. Second, due to the large amplitude of the tACS artifact, it is important to consider using an EEG system with a high resolution analog-to-digital (A/D) converter. In particular, the magnitude of the tACS artifact can exceed 100 mV at the vicinity of a stimulation electrode when 1 mA tACS is applied. The resolution of the A/D converter is of importance to measure good quality EEG data from the vicinity of the stimulation site. By following these guidelines for the procedures and technical considerations, successful concurrent EEG recording during tACS will be realized.

Concurrent Electroencephalography Recording During Transcranial Alternating Current Stimulation tACS

In this article we explain how to set up a concurrent transcranial alternating current stimulation and EEG experiment.

Oscillatory brain activities are considered to reflect the basis of rhythmic changes in transmission efficacy across brain networks and are assumed to ...

Automatic Detection of Highly Organized Theta Oscillations in the Murine EEG

Theta activity is generated in the septohippocampal system and can be recorded using deep intrahippocampal electrodes and implantable electroencephalography (EEG) radiotelemetry or tether system approaches. Pharmacologically, hippocampal theta is heterogeneous (see dualistic theory) and can be differentiated into type I and type II theta. These individual EEG subtypes are related to specific cognitive and behavioral states, such as arousal, exploration, learning and memory, higher integrative functions, etc. In neurodegenerative diseases such as Alzheimer&#39;s, structural and functional alterations of the septohippocampal system can result in impaired theta activity/oscillations. A standard quantitative analysis of the hippocampal EEG includes a Fast-Fourier-Transformation (FFT)-based frequency analysis. However, this procedure does not provide details about theta activity in general and highly-organized theta oscillations in particular. In order to obtain detailed information on highly-organized theta oscillations in the hippocampus, we have developed a new analytical approach. This approach allows for time- and cost-effective quantification of the duration of highly-organized theta oscillations and their frequency characteristics.

Theta activity in the hippocampus is related to specific cognitive and behavioral stages. Here, we describe an analytical method to detect highly-organized theta oscillations within the hippocampus using a time-frequency (i.e., wavelet analysis)-based approach.

Theta activity is generated in the septohippocampal system and can be recorded using deep intrahippocampal electrodes and implantable ...

Simultaneous Transcranial Alternating Current Stimulation and Functional Magnetic Resonance Imaging

Transcranial alternating current stimulation (tACS) is a promising tool for noninvasive investigation of brain oscillations. TACS employs frequency-specific stimulation of the human brain through current applied to the scalp with surface electrodes. Most current knowledge of the technique is based on behavioral studies; thus, combining the method with brain imaging holds potential to better understand the mechanisms of tACS. Because of electrical and susceptibility artifacts, combining tACS with brain imaging can be challenging, however, one brain imaging technique that is well suited to be applied simultaneously with tACS is functional magnetic resonance imaging (fMRI). In our lab, we have successfully combined tACS with simultaneous fMRI measurements to show that tACS effects are state, current, and frequency dependent, and that modulation of brain activity is not limited to the area directly below the electrodes. This article describes a safe and reliable setup for applying tACS simultaneously with visual task fMRI studies, which can lend to understanding oscillatory brain function as well as the effects of tACS on the brain.

Transcranial alternating current stimulation (tACS) is a promising tool for noninvasive investigation of brain oscillations, though its effects are not completely understood. This article describes a safe and reliable setup for applying tACS simultaneously with functional magnetic resonance imaging, which can increase understanding oscillatory brain function and effects of tACS.