EEG analysis - Event-Related Potentials (ERPs)

This tutorial shows how to perform standard ERP analyses in MNE-Python. Most of the material here is covered in other tutorials too, but for convenience the functions and methods most useful for ERP analyses are collected here, with links to other tutorials where more detailed information is given.

As usual we’ll start by importing the modules we need and loading some example data. Instead of parsing the events from the raw data’s stim channel (like we do in this tutorial), we’ll load the events from an external events file. Finally, to speed up computations we’ll crop the raw data from ~4.5 minutes down to 90 seconds.

# Authors: The MNE-Python contributors.
# License: BSD-3-Clause
# Copyright the MNE-Python contributors.

import matplotlib.pyplot as plt
import numpy as np
import pandas as pd

import mne

root = mne.datasets.sample.data_path() / "MEG" / "sample"
raw_file = root / "sample_audvis_filt-0-40_raw.fif"
raw = mne.io.read_raw_fif(raw_file, preload=False)

events_file = root / "sample_audvis_filt-0-40_raw-eve.fif"
events = mne.read_events(events_file)

raw.crop(tmax=90)  # in seconds (happens in-place)
# discard events >90 seconds (not strictly necessary, but avoids some warnings)
events = events[events[:, 0] <= raw.last_samp]

Opening raw data file /home/circleci/mne_data/MNE-sample-data/MEG/sample/sample_audvis_filt-0-40_raw.fif...
    Read a total of 4 projection items:
        PCA-v1 (1 x 102)  idle
        PCA-v2 (1 x 102)  idle
        PCA-v3 (1 x 102)  idle
        Average EEG reference (1 x 60)  idle
    Range : 6450 ... 48149 =     42.956 ...   320.665 secs
Ready.

The file that we loaded has already been partially processed: 3D sensor locations have been saved as part of the .fif file, the data have been low-pass filtered at 40 Hz, and a common average reference is set for the EEG channels, stored as a projector (see Creating the average reference as a projector in the Setting the EEG reference tutorial for more info about when you may want to do this). We’ll discuss how to do each of these below.

Since this is a combined EEG/MEG dataset, let’s start by restricting the data to just the EEG and EOG channels. This will cause the other projectors saved in the file (which apply only to magnetometer channels) to be removed. By looking at the measurement info we can see that we now have 59 EEG channels and 1 EOG channel.

raw.pick(["eeg", "eog"]).load_data()
raw.info

Reading 0 ... 13514  =      0.000 ...    90.001 secs...

	General
	MNE object type	Info
	Measurement date	2002-12-03 at 19:01:10 UTC
	Participant	Unknown
	Experimenter	Unknown
	Acquisition
	Sampling frequency	150.15 Hz
	Channels
	EEG	59 and 1 bad
	EOG	1
	Head & sensor digitization	146 points
	Filters
	Highpass	0.10 Hz
	Lowpass	40.00 Hz
	Projections	Average EEG reference (off)

Channel names and types

In practice it is quite common to have some channels labeled as EEG that are actually EOG channels. Raw objects have a set_channel_types() method that can be used to change a channel that is mislabeled as eeg to eog.

You can also rename channels using rename_channels(). Detailed examples of both of these methods can be found in the tutorial The Raw data structure: continuous data.

In our data set, all channel types are already correct. Therefore, we’ll only remove a space and a leading zero in the channel names and convert to lowercase:

channel_renaming_dict = {name: name.replace(" 0", "").lower() for name in raw.ch_names}
_ = raw.rename_channels(channel_renaming_dict)  # happens in-place

Note

The assignment to a temporary name _ (the _ = part) is included here to suppress automatic printing of the raw object. You do not have to do this in your interactive analysis.

Channel locations

The tutorial Working with sensor locations describes how sensor locations are handled in great detail. To briefly summarize: MNE-Python distinguishes montages (which contain 3D sensor locations x, y, and z, in meters) from layouts (which define 2D sensor arrangements for plotting schematic sensor location diagrams). Additionally, montages may specify idealized sensor locations (based on, e.g., an idealized spherical head model), or they may contain realistic sensor locations obtained by digitizing the 3D locations of the sensors when placed on a real person’s head.

This dataset has realistic digitized 3D sensor locations saved as part of the .fif file, so we can view the sensor locations in 2D or 3D using the plot_sensors() method:

raw.plot_sensors(show_names=True)
fig = raw.plot_sensors("3d")

• 
• 

If you’re working with a standard montage like the 10–20 system, you can add sensor locations to the data with raw.set_montage('standard_1020') (see Working with sensor locations for information on other standard montages included with MNE-Python).

If you have digitized realistic sensor locations, there are dedicated functions for loading those digitization files into MNE-Python (see Reading sensor digitization files for discussion and Supported formats for digitized 3D locations for a list of supported formats). Once loaded, the digitized sensor locations can be added to the data by passing the loaded montage object to set_montage().

Setting the EEG reference

As mentioned, this data already has an EEG common average reference added as a projector. We can view the effect of this projector on the raw data by plotting it with and without the projector applied:

for proj in (False, True):
    with mne.viz.use_browser_backend("matplotlib"):
        fig = raw.plot(
            n_channels=5, proj=proj, scalings=dict(eeg=50e-6), show_scrollbars=False
        )
    fig.subplots_adjust(top=0.9)  # make room for title
    ref = "Average" if proj else "No"
    fig.suptitle(f"{ref} reference", size="xx-large", weight="bold")

• 
• 

Using matplotlib as 2D backend.
Using qt as 2D backend.
Using matplotlib as 2D backend.
Using qt as 2D backend.

The referencing scheme can be changed with the function mne.set_eeg_reference() (which by default operates on a copy of the data) or the raw.set_eeg_reference() method (which always modifies the data in-place). The tutorial Setting the EEG reference shows several examples.

Filtering

MNE-Python has extensive support for different ways of filtering data. For a general discussion of filter characteristics and MNE-Python defaults, see Background information on filtering. For practical examples of how to apply filters to your data, see Filtering and resampling data. Here, we’ll apply a simple high-pass filter for illustration:

raw.filter(l_freq=0.1, h_freq=None)

Filtering raw data in 1 contiguous segment
Setting up high-pass filter at 0.1 Hz

FIR filter parameters
---------------------
Designing a one-pass, zero-phase, non-causal highpass filter:
- Windowed time-domain design (firwin) method
- Hamming window with 0.0194 passband ripple and 53 dB stopband attenuation
- Lower passband edge: 0.10
- Lower transition bandwidth: 0.10 Hz (-6 dB cutoff frequency: 0.05 Hz)
- Filter length: 4957 samples (33.013 s)

[Parallel(n_jobs=1)]: Done  17 tasks      | elapsed:    0.0s

	General
	Filename(s)	sample_audvis_filt-0-40_raw.fif
	MNE object type	Raw
	Measurement date	2002-12-03 at 19:01:10 UTC
	Participant	Unknown
	Experimenter	Unknown
	Acquisition
	Duration	00:01:31 (HH:MM:SS)
	Sampling frequency	150.15 Hz
	Time points	13,515
	Channels
	EEG	59 and 1 bad
	EOG	1
	Head & sensor digitization	146 points
	Filters
	Highpass	0.10 Hz
	Lowpass	40.00 Hz
	Projections	Average EEG reference (off)

Evoked responses: epoching and averaging

The general process for extracting evoked responses from continuous data is to use the Epochs constructor, and then average the resulting epochs to create an Evoked object. In MNE-Python, events are represented as a NumPy array containing event latencies (in samples) and integer event codes. The event codes are stored in the last column of the events array:

np.unique(events[:, -1])

The Working with events tutorial discusses event arrays in more detail. Integer event codes are mapped to more descriptive text using a Python dictionary usually called event_id. This mapping is determined by your experiment (i.e., it reflects which event codes you chose to represent different experimental events or conditions). The Sample data uses the following mapping:

event_dict = {
    "auditory/left": 1,
    "auditory/right": 2,
    "visual/left": 3,
    "visual/right": 4,
    "face": 5,
    "buttonpress": 32,
}

Now we can proceed to epoch the continuous data. An interactive plot allows us to click on epochs to mark them as “bad” and drop them from the analysis (it is not interactive on this documentation website, but will be when you run epochs.plot() in a Python console).

epochs = mne.Epochs(raw, events, event_id=event_dict, tmin=-0.3, tmax=0.7, preload=True)
fig = epochs.plot(events=events)

Not setting metadata
132 matching events found
Setting baseline interval to [-0.2996928197375818, 0.0] s
Applying baseline correction (mode: mean)
Created an SSP operator (subspace dimension = 1)
1 projection items activated
Using data from preloaded Raw for 132 events and 151 original time points ...
1 bad epochs dropped
You seem to have overlapping epochs. Some event lines may be duplicated in the plot.

It is also possible to automatically drop epochs (either when first creating them or later on) by providing maximum peak-to-peak signal value thresholds (passed to Epochs as the reject parameter; see Rejecting Epochs based on peak-to-peak channel amplitude for details). You can also do this after the epochs are already created using drop_bad():

reject_criteria = dict(eeg=100e-6, eog=200e-6)  # 100 µV, 200 µV
epochs.drop_bad(reject=reject_criteria)

    Rejecting  epoch based on EEG : ['eeg03']
    Rejecting  epoch based on EEG : ['eeg01', 'eeg02', 'eeg03', 'eeg04', 'eeg06', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg01', 'eeg02', 'eeg03', 'eeg04', 'eeg06', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg01', 'eeg02', 'eeg03', 'eeg04', 'eeg06', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg01', 'eeg02', 'eeg03', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg01', 'eeg02', 'eeg03', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg01']
    Rejecting  epoch based on EEG : ['eeg03', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg03', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg07']
    Rejecting  epoch based on EEG : ['eeg03', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg03', 'eeg07']
    Rejecting  epoch based on EEG : ['eeg07']
    Rejecting  epoch based on EEG : ['eeg07']
    Rejecting  epoch based on EEG : ['eeg03']
    Rejecting  epoch based on EEG : ['eeg25']
    Rejecting  epoch based on EEG : ['eeg25']
17 bad epochs dropped

	General
	MNE object type	Epochs
	Measurement date	2002-12-03 at 19:01:10 UTC
	Participant	Unknown
	Experimenter	Unknown
	Acquisition
	Total number of events	114
	Events counts	auditory/left: 25 auditory/right: 27 buttonpress: 4 face: 5 visual/left: 28 visual/right: 25
	Time range	-0.300 – 0.699 s
	Baseline	-0.300 – 0.000 s
	Sampling frequency	150.15 Hz
	Time points	151
	Metadata	No metadata set
	Channels
	EEG	59 and 1 bad
	EOG	1
	Head & sensor digitization	146 points
	Filters
	Highpass	0.10 Hz
	Lowpass	40.00 Hz
	Projections	Average EEG reference (on)

Next, we generate a barplot of which channels contributed most to epochs getting rejected. If one channel is responsible for many epoch rejections, it may be worthwhile to mark that channel as “bad” in the Raw object and then re-run epoching (fewer channels with more good epochs may be preferable to keeping all channels but losing many epochs). See Handling bad channels for more information.

epochs.plot_drop_log()

Epochs can also be dropped automatically if the event around which the epoch is created is too close to the start or end of the Raw object (e.g., if the epoch would extend past the end of the recording; this is the cause for the “TOO_SHORT” entry in the plot_drop_log() plot).

Epochs may also be dropped automatically if the Raw object contains annotations that begin with either bad or edge (“edge” annotations are automatically inserted when concatenating two or more Raw objects). See Rejecting bad data spans and breaks for more information on annotation-based epoch rejection.

Now that we’ve dropped all bad epochs, let’s look at our evoked responses for some conditions we care about. Here, the average() method will create an Evoked object, which we can then plot. Notice that we select which condition we want to average using square-bracket indexing (like for a dictionary). This returns a subset with only the desired epochs, which we then average:

l_aud = epochs["auditory/left"].average()
l_vis = epochs["visual/left"].average()

These Evoked objects have their own interactive plotting method (though again, it won’t be interactive on the documentation website). Clicking and dragging a span of time will generate a topography of scalp potentials for the selected time segment. Here, we also demonstrate built-in color-coding the channel traces by location:

fig1 = l_aud.plot()
fig2 = l_vis.plot(spatial_colors=True)

• 
• 

Scalp topographies can also be obtained non-interactively with the plot_topomap() method. Here, we display topomaps of the average evoked potential in 50 ms time windows centered at -200 ms, 100 ms, and 400 ms.

l_aud.plot_topomap(times=[-0.2, 0.1, 0.4], average=0.05)

Considerable customization of these plots is possible, see the docstring of plot_topomap() for details.

There is also a built-in method for combining butterfly plots of the signals with scalp topographies called plot_joint(). Like in plot_topomap(), you can specify times for the scalp topographies or you can let the method choose times automatically as shown here:

l_aud.plot_joint()

Projections have already been applied. Setting proj attribute to True.

Global field power (GFP)

Global field power [1][2][3] is, generally speaking, a measure of agreement of the signals picked up by all sensors across the entire scalp: if all sensors have the same value at a given time point, the GFP will be zero at that time point. If the signals differ, the GFP will be non-zero at that time point. GFP peaks may reflect “interesting” brain activity, warranting further investigation. Mathematically, the GFP is the population standard deviation across all sensors, calculated separately for every time point.

You can plot the GFP using evoked.plot(gfp=True). The GFP trace will be black if spatial_colors=True and green otherwise. The EEG reference does not affect the GFP:

for evk in (l_aud, l_vis):
    evk.plot(gfp=True, spatial_colors=True, ylim=dict(eeg=[-12, 12]))

• 
• 

To plot the GFP by itself, you can pass gfp='only' (this makes it easier to read off the GFP data values, because the scale is aligned):

l_aud.plot(gfp="only")

The GFP is the population standard deviation of the signal across channels. To compute it manually, we can leverage the fact that evoked.data is a NumPy array, and verify by plotting it using plain Matplotlib commands:

gfp = l_aud.data.std(axis=0, ddof=0)

# Reproducing the MNE-Python plot style seen above
fig, ax = plt.subplots()
ax.plot(l_aud.times, gfp * 1e6, color="lime")
ax.fill_between(l_aud.times, gfp * 1e6, color="lime", alpha=0.2)
ax.set(xlabel="Time (s)", ylabel="GFP (µV)", title="EEG")

Averaging across channels with regions of interest

Since our sample data contains responses to left and right auditory and visual stimuli, we may want to compare left versus right regions of interest (ROIs). To average across channels in a given ROI, we first find the relevant channel indices. Revisiting the 2D sensor plot above, we might choose the following channels for left and right ROIs, respectively:

left = ["eeg17", "eeg18", "eeg25", "eeg26"]
right = ["eeg23", "eeg24", "eeg34", "eeg35"]

left_ix = mne.pick_channels(l_aud.info["ch_names"], include=left)
right_ix = mne.pick_channels(l_aud.info["ch_names"], include=right)

Now we can create a new Evoked object with two virtual channels (one for each ROI):

roi_dict = dict(left_ROI=left_ix, right_ROI=right_ix)
roi_evoked = mne.channels.combine_channels(l_aud, roi_dict, method="mean")
print(roi_evoked.info["ch_names"])
roi_evoked.plot()

Applying baseline correction (mode: mean)
['left_ROI', 'right_ROI']

Comparing conditions

If we wanted to contrast auditory to visual stimuli, a useful function is mne.viz.plot_compare_evokeds(). By default, this function will combine all channels in each evoked object using GFP (or RMS for MEG channels); here instead we specify to combine by averaging, and restrict it to a subset of channels by passing picks:

evokeds = dict(auditory=l_aud, visual=l_vis)
picks = [f"eeg{n}" for n in range(10, 15)]
mne.viz.plot_compare_evokeds(evokeds, picks=picks, combine="mean")

combining channels using "mean"
combining channels using "mean"

We can also generate confidence intervals by treating each epoch as a separate observation using iter_evoked(). A confidence interval across subjects could also be obtained by passing a list of Evoked objects (one per subject) to the plot_compare_evokeds() function.

evokeds = dict(
    auditory=list(epochs["auditory/left"].iter_evoked()),
    visual=list(epochs["visual/left"].iter_evoked()),
)
mne.viz.plot_compare_evokeds(evokeds, combine="mean", picks=picks)

combining channels using "mean"
combining channels using "mean"

We can also compare conditions by subtracting one Evoked object from another using the mne.combine_evoked() function (this function also supports pooling of epochs without subtraction).

aud_minus_vis = mne.combine_evoked([l_aud, l_vis], weights=[1, -1])
aud_minus_vis.plot_joint()

Projections have already been applied. Setting proj attribute to True.

Warning

The code above yields an equal-weighted difference. If you have different numbers of epochs per condition, you might want to equalize the number of events per condition first by using epochs.equalize_event_counts() before averaging.

Grand averages

To compute grand averages across conditions (or subjects), you can pass a list of Evoked objects to mne.grand_average(). The result is another Evoked object.

grand_average = mne.grand_average([l_aud, l_vis])
print(grand_average)

Setting channel interpolation method to {'eeg': 'spline'}.
Interpolating bad channels.
    Automatic origin fit: head of radius 91.0 mm
Computing interpolation matrix from 59 sensor positions
Interpolating 1 sensors
Setting channel interpolation method to {'eeg': 'spline'}.
Interpolating bad channels.
    Automatic origin fit: head of radius 91.0 mm
Computing interpolation matrix from 59 sensor positions
Interpolating 1 sensors
Identifying common channels ...
<Evoked | 'Grand average (n = 2)' (average, N=2), -0.29969 – 0.69928 s, baseline -0.299693 – 0 s, 60 ch, ~3.0 MiB>

For combining conditions it is also possible to make use of HED tags in the condition names when selecting which epochs to average. For example, we have the condition names:

list(event_dict)

We can select the auditory conditions (left and right together) by passing:

epochs["auditory"].average()

	General
	MNE object type	EvokedArray
	Measurement date	2002-12-03 at 19:01:10 UTC
	Participant	Unknown
	Experimenter	Unknown
	Acquisition
	Aggregation	average of 52 epochs
	Condition	0.48 × auditory/left + 0.52 × auditory/right
	Time range	-0.300 – 0.699 s
	Baseline	-0.300 – 0.000 s
	Sampling frequency	150.15 Hz
	Time points	151
	Channels
	EEG	59 and 1 bad
	Head & sensor digitization	146 points
	Filters
	Highpass	0.10 Hz
	Lowpass	40.00 Hz
	Projections	Average EEG reference (on)

See Subselecting epochs for more details on that.

The tutorials The Epochs data structure: discontinuous data and The Evoked data structure: evoked/averaged data have many more details about working with the Epochs and Evoked classes.

Amplitude and latency measures

It is common in ERP research to extract measures of amplitude or latency to compare across different conditions. There are many measures that can be extracted from ERPs, and many of these are detailed (including the respective strengths and weaknesses) in chapter 9 of Luck [4] (also see the Measurement Tool in the ERPLAB Toolbox [5]).

This part of the tutorial will demonstrate how to extract three common measures:

• Peak latency

• Peak amplitude

• Mean amplitude

Peak latency and amplitude

The most common measures of amplitude and latency are peak measures. Peak measures are basically the maximum amplitude of the signal in a specified time window and the time point (or latency) at which the peak amplitude occurred.

Peak measures can be obtained using the get_peak() method. There are two important things to point out about get_peak(). First, it finds the strongest peak looking across all channels of the selected type that are available in the Evoked object. As a consequence, if you want to restrict the search to a group of channels or a single channel, you should first use the pick() or pick_channels() methods. Second, the get_peak() method can find different types of peaks using the mode argument. There are three options:

• mode='pos': finds the peak with a positive voltage (ignores negative voltages)

• mode='neg': finds the peak with a negative voltage (ignores positive voltages)

• mode='abs': finds the peak with the largest absolute voltage regardless of sign (positive or negative)

The following example demonstrates how to find the first positive peak in the ERP (i.e., the P100) for the left visual condition (i.e., the l_vis Evoked object). The time window used to search for the peak ranges from 0.08 to 0.12 s. This time window was selected because it is when P100 typically occurs. Note that all 'eeg' channels are submitted to the get_peak() method.

# Define a function to print out the channel (ch) containing the
# peak latency (lat; in msec) and amplitude (amp, in µV), with the
# time range (tmin and tmax) that was searched.
# This function will be used throughout the remainder of the tutorial.
def print_peak_measures(ch, tmin, tmax, lat, amp):
    print(f"Channel: {ch}")
    print(f"Time Window: {tmin * 1e3:.3f} - {tmax * 1e3:.3f} ms")
    print(f"Peak Latency: {lat * 1e3:.3f} ms")
    print(f"Peak Amplitude: {amp * 1e6:.3f} µV")


# Get peak amplitude and latency from a good time window that contains the peak
good_tmin, good_tmax = 0.08, 0.12
ch, lat, amp = l_vis.get_peak(
    ch_type="eeg", tmin=good_tmin, tmax=good_tmax, mode="pos", return_amplitude=True
)

# Print output from the good time window that contains the peak
print("** PEAK MEASURES FROM A GOOD TIME WINDOW **")
print_peak_measures(ch, good_tmin, good_tmax, lat, amp)

** PEAK MEASURES FROM A GOOD TIME WINDOW **
Channel: eeg55
Time Window: 80.000 - 120.000 ms
Peak Latency: 86.578 ms
Peak Amplitude: 6.508 µV

The output shows that channel eeg55 had the maximum positive peak in the chosen time window from all of the 'eeg' channels searched. In practice, one might want to pull out the peak for an a priori region of interest or a single channel depending on the study. This can be done by combining the pick() or pick_channels() methods with the get_peak() method.

Here, let’s assume we believe the effects of interest will occur at eeg59.

# Fist, return a copy of l_vis to select the channel from
l_vis_roi = l_vis.copy().pick("eeg59")

# Get the peak and latency measure from the selected channel
ch_roi, lat_roi, amp_roi = l_vis_roi.get_peak(
    tmin=good_tmin, tmax=good_tmax, mode="pos", return_amplitude=True
)

# Print output
print("** PEAK MEASURES FOR ONE CHANNEL FROM A GOOD TIME WINDOW **")
print_peak_measures(ch_roi, good_tmin, good_tmax, lat_roi, amp_roi)

** PEAK MEASURES FOR ONE CHANNEL FROM A GOOD TIME WINDOW **
Channel: eeg59
Time Window: 80.000 - 120.000 ms
Peak Latency: 86.578 ms
Peak Amplitude: 5.713 µV

While the peak latencies are the same in channels eeg55 and eeg59, the peak amplitudes differ. This approach can also be applied to virtual channels created with the combine_channels() function and difference waves created with the mne.combine_evoked() function (see aud_minus_vis in section Comparing conditions above).

Peak measures are very susceptible to high frequency noise in the signal (for discussion, see [4]). Specifically, high frequency noise positively biases peak amplitude measures. This bias can confound comparisons across conditions where ERPs differ in the level of high frequency noise, such as when the conditions differ in the number of trials contributing to the ERP. One way to avoid this is to apply a non-causal low-pass filter to the ERP. Low-pass filters reduce the contribution of high frequency noise by smoothing out fast (i.e., high frequency) fluctuations in the signal (see Background information on filtering). While this can reduce the positive bias in peak amplitude measures caused by high frequency noise, low-pass filtering the ERP can introduce challenges in interpreting peak latency measures for effects of interest [6][7].

If using peak measures, it is critical to visually inspect the data to make sure the selected time window actually contains a peak. The meth:get_peak method detects the maximum or minimum voltage in the specified time range and returns the latency and amplitude of this peak. There is no guarantee that this method will return an actual peak. Instead, it may return a value on the rising or falling edge of a peak we are trying to find.

The following example demonstrates why visual inspection is crucial. Below, we use a known bad time window (0.095 to 0.135 s) to search for a peak in channel eeg59.

# Get BAD peak measures
bad_tmin, bad_tmax = 0.095, 0.135
ch_roi, bad_lat_roi, bad_amp_roi = l_vis_roi.get_peak(
    mode="pos", tmin=bad_tmin, tmax=bad_tmax, return_amplitude=True
)

# Print output
print("** PEAK MEASURES FOR ONE CHANNEL FROM A BAD TIME WINDOW **")
print_peak_measures(ch_roi, bad_tmin, bad_tmax, bad_lat_roi, bad_amp_roi)

** PEAK MEASURES FOR ONE CHANNEL FROM A BAD TIME WINDOW **
Channel: eeg59
Time Window: 95.000 - 135.000 ms
Peak Latency: 99.898 ms
Peak Amplitude: 1.487 µV

If all we had were the above values, it would be unclear if they are truly identifying a peak in the ERP. In fact, the 0.095 to 0.135 s time window actually does not contain the true peak, which is shown in the top panel below. The bad time window (highlighted in orange) does not contain the true peak (the pink star). In contrast, the time window defined initially (0.08 to 0.12 s; highlighted in blue) returns an actual peak instead of a just a maximum or minimum in the searched time window. Visual inspection will always help you to convince yourself that the returned values are actual peaks.

fig, axs = plt.subplots(nrows=2, ncols=1, layout="tight")
words = (("Bad", "missing"), ("Good", "finding"))
times = (np.array([bad_tmin, bad_tmax]), np.array([good_tmin, good_tmax]))
colors = ("C1", "C0")

for ix, ax in enumerate(axs):
    title = "{} time window {} peak".format(*words[ix])
    l_vis_roi.plot(axes=ax, time_unit="ms", show=False, titles=title)
    ax.plot(lat_roi * 1e3, amp_roi * 1e6, marker="*", color="C6")
    ax.axvspan(*(times[ix] * 1e3), facecolor=colors[ix], alpha=0.3)
    ax.set_xlim(-50, 150)  # Show zoomed in around peak

Need more than one channel to make topography for eeg. Disabling interactivity.
Need more than one channel to make topography for eeg. Disabling interactivity.

Mean Amplitude

Another common practice in ERP studies is to define a component (or effect) as the mean amplitude within a specified time window. One advantage of this approach is that it is less sensitive to high frequency noise (compared to peak amplitude measures), because averaging over a time window acts as a low-pass filter (see discussion in the previous section Peak latency and amplitude).

When using mean amplitude measures, selecting the time window based on the effect of interest (e.g., the difference between two conditions) can inflate the likelihood of finding false positives in your results [8]. There are other, and better, ways to identify a time window to use for extracting mean amplitude measures. First, you can use an a priori time window based on prior research. A second option is to define a time window from an independent condition or set of trials not used in the analysis (e.g., a “localizer”). A third approach is to define a time window using the across-condition grand average. This latter approach is not circular because the across-condition mean and condition difference are independent of one another. The issues discussed above also apply to selecting channels used for analysis.

The following example demonstrates how to pull out the mean amplitude from the left visual condition (i.e., the l_vis Evoked object) from selected channels and time windows. Stimulating the left visual field increases neural activity of visual cortex in the contralateral (i.e., right) hemisphere. We can test this by examining the amplitude of the ERP for left visual field stimulation over right (contralateral) and left (ipsilateral) channels. The channels used for this analysis are eeg54 and eeg57 (left hemisphere), and eeg59 and eeg55 (right hemisphere). The time window used is 0.08 (good_tmin) to 0.12 s (good_tmax) as it corresponds to when the P100 typically occurs. The P100 is sensitive to left and right visual field stimulation. The mean amplitude is extracted from the above four channels and stored in a pandas.DataFrame.

# Select all of the channels and crop to the time window
channels = ["eeg54", "eeg57", "eeg55", "eeg59"]
hemisphere = ["left", "left", "right", "right"]
l_vis_mean_roi = l_vis.copy().pick(channels).crop(tmin=good_tmin, tmax=good_tmax)

# Extract mean amplitude in µV over time
mean_amp_roi = l_vis_mean_roi.data.mean(axis=1) * 1e6

# Store the data in a data frame
mean_amp_roi_df = pd.DataFrame(
    {
        "ch_name": l_vis_mean_roi.ch_names,
        "hemisphere": ["left", "left", "right", "right"],
        "mean_amp": mean_amp_roi,
    }
)

# Print the data frame
print(mean_amp_roi_df.groupby("hemisphere").mean(numeric_only=True))

            mean_amp
hemisphere
left       -0.279764
right       0.685840

As demonstrated in this example, the mean amplitude was higher and positive in right compared to left hemisphere channels. It should be reiterated that both spatial and temporal windows used in the analysis should be determined in an independent manner (e.g., defined a priori from prior research, a “localizer” or another independent condition) and not based on the data you will use to test your hypotheses.

The example can be modified to extract the mean amplitude from all channels and store the resulting output in a pandas.DataFrame. This can be useful for statistical analyses conducted in other programming languages.

# Extract mean amplitude for all channels in l_vis (including `eog`)
l_vis_cropped = l_vis.copy().crop(tmin=good_tmin, tmax=good_tmax)
mean_amp_all = l_vis_cropped.data.mean(axis=1) * 1e6
mean_amp_all_df = pd.DataFrame(
    {"ch_name": l_vis_cropped.info["ch_names"], "mean_amp": mean_amp_all}
)
mean_amp_all_df["tmin"] = good_tmin
mean_amp_all_df["tmax"] = good_tmax
mean_amp_all_df["condition"] = "Left/Visual"
with pd.option_context("display.max_columns", None):
    print(mean_amp_all_df.head())
    print(mean_amp_all_df.tail())

  ch_name  mean_amp  tmin  tmax    condition
0   eeg01 -1.689513  0.08  0.12  Left/Visual
1   eeg02 -0.078492  0.08  0.12  Left/Visual
2   eeg03 -0.381191  0.08  0.12  Left/Visual
3   eeg04 -1.609264  0.08  0.12  Left/Visual
4   eeg05 -1.113717  0.08  0.12  Left/Visual
   ch_name  mean_amp  tmin  tmax    condition
55   eeg56  2.064174  0.08  0.12  Left/Visual
56   eeg57 -0.259681  0.08  0.12  Left/Visual
57   eeg58  0.156472  0.08  0.12  Left/Visual
58   eeg59  0.802306  0.08  0.12  Left/Visual
59   eeg60  0.878811  0.08  0.12  Left/Visual

References

[1]

Dietrich Lehmann and Wolfgang Skrandies. Reference-free identification of components of checkerboard-evoked multichannel potential fields. Electroencephalography and Clinical Neurophysiology, 48(6):609–621, 1980. doi:10.1016/0013-4694(80)90419-8.

[2]

Dietrich Lehmann and Wolfgang Skrandies. Spatial analysis of evoked potentials in man—a review. Progress in Neurobiology, 23(3):227–250, 1984. doi:10.1016/0301-0082(84)90003-0.

[3]

Micah M. Murray, Denis Brunet, and Christoph M. Michel. Topographic ERP analyses: A step-by-step tutorial review. Brain Topography, 20(4):249–264, 2008. doi:10.1007/s10548-008-0054-5.

[4] (1,2)

Steven J Luck. An Introduction to the Event-Related Potential Technique. The MIT Press, Cambridge, MA, 2nd edition, 2014. ISBN 978-0-262-52585-5. URL: https://mitpress.mit.edu/books/introduction-event-related-potential-technique-second-edition.

[5]

Javier Lopez-Calderon and Steven J. Luck. Erplab: an open-source toolbox for the analysis of event-related potentials. Frontiers in Human Neuroscience, 2014. doi:10.3389/fnhum.2014.00213.

[6]

Guillaume A. Rousselet. Does filtering preclude us from studying ERP time-courses? Frontiers in Psychology, 2012. doi:10.3389/fpsyg.2012.00131.

[7]

Rufin VanRullen. Four common conceptual fallacies in mapping the time course of recognition. Frontiers in Psychology, 2011. doi:10.3389/fpsyg.2011.00365.

[8]

Steven J. Luck and Nicholas Gaspelin. How to get statistically significant effects in any ERP experiment (and why you shouldn’t). Psychophysiology, 54(1):146–157, 2017. doi:10.1111/psyp.12639.