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# Spatially independent activity patterns in functional MRI data during the Stroop color-naming task

## Abstract

A method is given for determining the time course and spatial
extent of consistently and transiently task-related activations from
other physiological and artifactual components that contribute to
functional MRI (fMRI) recordings. Independent component analysis (ICA)
was used to analyze two fMRI data sets from a subject performing 6-min
trials composed of alternating 40-sec Stroop color-naming and control
task blocks. Each component consisted of a fixed three-dimensional
spatial distribution of brain voxel values (a “map”) and an
associated time course of activation. For each trial, the algorithm
detected, without *a priori* knowledge of their spatial or
temporal structure, one consistently task-related component activated
during each Stroop task block, plus several transiently task-related
components activated at the onset of one or two of the Stroop task
blocks only. Activation patterns occurring during only part of the fMRI
trial are not observed with other techniques, because their time
courses cannot easily be known in advance. Other ICA components were
related to physiological pulsations, head movements, or machine noise.
By using higher-order statistics to specify stricter criteria for
spatial independence between component maps, ICA produced improved
estimates of the temporal and spatial extent of task-related activation
in our data compared with principal component analysis (PCA). ICA
appears to be a promising tool for exploratory analysis of fMRI data,
particularly when the time courses of activation are not known in
advance.

Univariate methods for the analysis of functional MRI (fMRI) data
typically examine each brain volume element or voxel individually, to
determine whether the activity level at that voxel reaches a
prespecified criterion for task-related activity. A common criterion is
a predetermined level of significance for a statistic, such as the
Student *t* (1) or Kolmogorov–Smirnov (2) statistic, under
the null hypothesis that the distribution of a voxel’s values during
the behavioral control task is identical to that during performance of
the experimental task(s). Correlational analysis (3) determines whether
the similarity between a voxel’s time course and a prediction of the
task-related modulation, the reference function, exceeds a specified
threshold. These methods then assemble individually selected (or
“active”) voxels, ignoring statistical relationships between
voxels, to create a spatially distributed map demonstrating areas of
significant activation.

To enhance the statistical power of standard analysis techniques based
on correlation or univariate statistical tests, fMRI experimenters
often use alternating task-block designs in which the subject performs
two or more tasks successively in alternating 20- to 40-sec blocks. By
averaging over a number of task-block cycles, small consistently
task-related (CTR) differences in hemodynamic activation can be
detected. Isolated stimulus paradigms, such as that employed by Buckner
*et al.* (4), avoid overlapping hemodynamic responses produced
by more rapid stimulus presentation rates, but interpretation of the
responses still involves averaging responses over many different
stimulus presentations.

Averaging over task blocks or individual stimuli assumes stationarity of brain responses and reduces the sensitivity of fMRI analyses to changes in brain activation occurring during only one or more portions of a trial (5). Such transiently task-related (TTR) activations potentially may arise from shifts in subject performance strategy, from variations in subject arousal, attention, or effort, or from changes in brain activation produced by learning or habituation. It is desirable, therefore, to find techniques for analyzing fMRI data that do not involve averaging over trials or blocks and that are capable of detecting TTR activations.

Determining the spatiotemporal extent of transiently or consistently task-related activations by invariate techniques is also problematic because treating each voxel independently ignores relationships between voxels and, hence, between brain regions. Even when activities of voxels in a spatially distributed group individually meet a certain criterion, it cannot necessarily be inferred that the group forms a single processing area. For example, it is possible that the time courses from two voxels each may be both correlated with the reference function for a task above a given threshold, yet be uncorrelated with each other. Complementary multivariate techniques attempt to circumvent this problem by extracting the spatial and temporal structure of distributed brain systems that sum to the measured fMRI signals.

One such technique, principal component analysis (PCA), is commonly used for data decomposition and dimension reduction (6). PCA measures the covariance between all pairs of voxels and then finds the orthogonal spatial maps, or eigenimages, that capture the greatest variance in the data. The first eigenimage represents the combination of voxels explaining the largest source of variance between pairs of voxels, the second eigenimage represents the largest source of residual variance orthogonal to the first eigenimage, and so on. The measured fMRI signals thus can be parsimoniously summarized by projecting them onto a reduced set of the eigenimages, usually those capturing a predetermined amount (e.g., >95%) of the variance in the data. However, because performance-related fMRI changes are only a small part of total signal variance, projecting the data onto orthogonal eigenimages capturing the greatest variance in the data may prove ill-suited for detecting task-related activations. In addition, if these involve activations of numerous voxels simultaneously, analysis methods based solely on voxel-pair relationships may not accurately detect the full spatiotemporal extent of the activations.

A decomposition method suitable for detecting task-related activations should be consistent with fundamental neurophysiological principles regarding the spatial extent of neural activity during the performance of psychomotor tasks. The principle of localization (7) implies that each psychomotor function is performed in a small set of brain areas, different for each function. This is based on a large body of empirical knowledge correlating psychomotor deficits with regions of cerebral damage, for example, the characteristic language deficits seen after damage to Wernicke’s and Broca’s areas.

We assume that an appropriate goal for the decomposition of fMRI data into cognitively and physiologically meaningful components is the determination of separate groups of multifocal anatomical brain areas that are coactivated during the acquisition of the fMRI slices throughout the experimental trial. Artifacts secondary to subtle movements (8), machine noise (9), and cardiac and respiratory pulsations (10), which may make up the bulk of variability in the measured fMRI signals, should have spatial patterns of activity separate from the localization of brain areas involved in task-related activation. Specifically, with such a model, each fMRI scan can be considered the sum of a mean activity level at each time point plus activations (or suppressions) belonging to one or more spatially independent components. Each individual component may be described by a graded spatial distribution or map and an associated time course of activation.

Here we use a recently developed statistical technique, independent component analysis (ICA) (11, 12), to determine the three-dimensional brain topographies and time courses of activations associated with spatially independent components that together sum to the measured fMRI signals recorded during the performance of a Stroop color-naming task. Our results suggest that ICA can be used effectively to isolate the spatiotemporal extent of both consistently and transiently task-related activations from artifacts and other sources of variability that comprise the fMRI signals.

## Independent Component Analysis

Separating fMRI data into independent spatial components involves
determining three-dimensional brain maps and their associated time
courses of activation that together sum to the observed fMRI data. The
primary assumption is that the component maps, specified by fixed
spatial distributions of values (one for each brain voxel), are
spatially independent. This means that, if
*p _{k}*(

*C*) specifies the probability distribution of the voxel values

_{k}*C*in the

_{k}*k*component map, then the joint probability distribution of all

^{th}*N*components factorizes: 1 This is equivalent to saying that voxel values in any one map do not convey any information about the voxel values in any of the other maps. This is a much stronger criterion than merely assuming that map values of voxel pairs from different components are uncorrelated, i.e., 2 where

*M*is the number of voxels and

*C*is the

_{ij}*j*value in the

^{th}*i*component map. This is because Eq. 1 implies that higher order correlations, or polynomial sums of map voxel values, are also zero. For example, for two maps, 3 for all natural numbers

^{th}*p*and

*q*.

With these assumptions, fMRI signals recorded from one or more sessions
can be separated by the ICA algorithm of Bell and Sejnowski (11, 12)
into a number of independent component maps with unique, associated
time courses of activation. Assuming that the data are mixtures of
spatially independent components, the algorithm determines an unmixing
matrix, *W*, from which the component maps and time courses of
activation can be computed (see Appendix). The matrix of
component map values, *C*, can then be computed by multiplying
the observed data by *W*,
4a
where *X* is the (row mean-zero) *N* by
*M* fMRI signal data matrix (*N*, the number of time
points in the trial, and *M*, the number of brain voxels)
obtained by removing the mean signal level from each time point. In
matrix notation, this simplifies to:
4b
Noise in the data is not explicitly modeled, but instead is
included in one or more of the components. The number of components
determined by the algorithm is equal to the number of input time points
in the data. Note that although a nonlinear function is used in the
determination of *W* (described in the Appendix),
*W* still provides a linear decomposition of the data.

To determine whether a given component map is influenced by its requirement to be spatially independent of other maps, the data may be reconstructed with one or more of the components removed and the resultant data matrix may be separated again by using the ICA algorithm (see Appendix).

## Methods

A subject volunteer participated in two 6-min trials of a Stroop color-naming task. Each trial consisted of five 40-sec control blocks alternating with four 40-sec experimental task blocks. A 1.5 T General Electric Signa MRI system was used to monitor brain activity by using blood oxygen level-dependent (BOLD) contrast. Ten 64 × 64 echo planar, gradient-recalled (TR = 2,500 msec, TE = 40 msec) axial images (5-mm thick, 1-mm interslice gap) with a 24-cm field of view were collected at 2.5-sec sampling intervals, corresponding to 146 images for each slice.

Stimuli spanning a visual angle of 2° by 3° were presented one at a time by overhead projector onto a screen placed at the base of the magnet. In control blocks, the subject was simply required to covertly name the color of a displayed rectangle (red, blue, or green). During experimental Stroop-task blocks, the subject was required to covertly name the discordant color of the script used to print a color name. For example, if the word “green” was presented in blue script, the subject was to covertly “say” the word “blue” without vocalizing or activating the muscles of articulation.

Voxels corresponding to active brain regions were determined by examining their mean signal values. These were found to have a bimodal probability distribution. The local minimum between the two peaks of a third-order polynomial fitted to the voxel mean-value histogram determined a cutoff value. Voxels with mean signal values above the cutoff value were assumed to represent active brain signals. Voxels with weaker signal means were found to be almost exclusively outside the head and therefore were eliminated from subsequent analyses.

Data were temporally smoothed by using a three-point filter based on a Hanning window (2). The three points were shifted along the window by 250 msec for each successive slice to decrease the time misalignments induced by the successive 250-msec acquisition delays between slices. For each time point, the filtered BOLD signals from all brain voxels were placed into a row of the data matrix after subtracting the mean voxel value for the time point from each voxel.

An ICA algorithm (11, 12) was applied separately to the data matrix from each of the two trials (see Appendix). Around 60 min on an Alphaserver 2100 (Digital Equipment Corporation, Maynard, MA) was required for convergence. For comparison, the eigenimages from each trial were determined by using standard PCA techniques, along with their associated time courses. To explore the effects of higher-order statistics on determining uncorrelated spatial maps, the fourth-order cumulant ICA technique proposed by Comon (13), computationally more expensive than the ICA algorithm (around 390 min of computer time to analyze one trial), was also used to find partially independent maps and associated time courses.

The computed ICA component maps were read into the functional neuroimaging display program mcw afni (14) for display and registration with structural T1-weighted MRI brain images for the subject.

Convolving the task block design with a 7.5-sec-long rectangular function (to take into account the lags caused by the hemodynamic response) created a task reference function. The reference function was then correlated with the time courses of the individual voxel time courses and the ICA and PCA components.

To display voxels contributing most strongly to a particular component map, the values in each map were scaled to z-scores. Voxels with absolute z-scores greater than some threshold (e.g., |z| > 2) were considered to be the “active” voxels of that component. Negative z-scores indicate voxels whose BOLD signals are modulated opposite to the given time course of activation for the component. (Here, z-scores are used only for descriptive purposes and have no particular statistical significance).

## Results

The application of ICA to a 6-min Stroop trial produced 144 component maps and their associated time courses. Some spatial ICA component maps contained multifocal groupings of active voxels, whereas others, typically those explaining the least variance in the data, had diffuse, noise-like, or “speckled” spatial distributions. All component maps had a super-Gaussian distribution of voxel values, i.e., having more values around zero and longer tails compared with a Gaussian distribution of the same variance, resulting in sparse maps after thresholding. Some components were slowly varying, quasi-periodic with a period of ∼12 sec, or had sharp changes in their time courses or ring-like spatial distributions suggesting head movements (Fig. 1). These will be described in more detail elsewhere.

Only one component from each trial had a CTR time course closely
matching the reference function for the trials (*r* =
0.92 and 0.68) (Fig. 2). In
contrast, many principal components had projections that were somewhat
correlated with the reference function. The principal components whose
projections most correlated with the reference function
(*r* = 0.46 and *r* = 0.45) differed both
spatially and temporally with the ICA CTR component (Fig. 2). The
fourth-order cumulant technique for ICA proposed by Comon (13) provided
one component in each trial whose time course was correlated to the
reference function (*r* = 0.85 and 0.71) almost the same
as that found by the Bell and Sejnowski algorithm for ICA (Fig. 2).

The right column of Fig. 3 superimposes the four 80-sec task cycles of the ICA CTR component for both Stroop trials. Several details of the shape of CTR-component activation were reproducible across experimental/control blocks (Fig. 3). The bottom right plot shows the mean of the eight CTR component task-cycle activations in the two trials, superimposed on one cycle of the reference function. Note that the mean time course of activation was not precisely predicted by the reference function. The CTR component time course suggested that the true hemodynamic response or brain activation during each 40-sec Stroop task block was not constant, but tended to decline after 20 sec on task, and had an unexpectedly long (8-sec) rise time.

Active voxels of these CTR components highly overlapped areas deemed active by standard correlation methods (to be reported elsewhere). Both methods detected activation in Brodmann’s areas 18 and 19 (not involving the calcarine fissure) and in the supplementary motor area and cingulate system. In each of the trials, the ICA method also detected CTR activation in frontal areas including left dorsolateral prefrontal cortex.

In both trials, separating the fMRI data into independent spatial
components also produced several components that appeared TTR (Fig.
4). Most often, these showed a
marked activation at the onset of one or two of the four Stroop task
blocks, especially the first and second blocks (Figs. 1*b* and
4, in trial 1 ) or the second and third blocks (in trial 2). In
contrast to the CTR components, the most active areas of the TTR
components were largely frontal, implying that frontal Stroop
task-related activations differed in strength and spatial distribution
during and across trials.

### Component Removal.

To explore whether the TTR components were affected by the ICA requirement that their spatial distributions be independent of the map voxel values of each other and the CTR component, the CTR component was removed from the first trial by using the method described in the Appendix. The resulting reduced-rank data set was then decomposed by ICA applied to eigenimages of the first 100 eigenvectors (explaining 99.99% of data variance).

Removal of the CTR component had varying effects on the
recomputed independent component maps. For example, Fig.
5 shows a scatter plot comparing
the map voxel values of a suspected artifact (head movement) component
in the two ICA decompositions (i.e., before and after the removal of
the CTR component using the method outlined in the
Appendix). The two spatial distributions are highly similar
(*r* = 0.9), suggesting the removal of the CTR component
had a minimal effect on the spatial distribution of this component.
Similarly, comparisons of map voxel values before and after CTR removal
revealed minimal effects on a quasi-periodic component
(*r* = 0.97) and a slow head movement component
(*r* = 0.82).

Fig. 6*a* shows a TTR
component (*Lower Left*) whose active area overlapped
significantly the active area of the CTR component (*Upper*).
Re-analysis of the data set into spatially independent components with
the CTR component removed (*Lower Right*) yields a component
task-related to the second Stroop block, but with mesial frontal active
areas. A scatter plot comparing the map voxel distributions of the TTR
components before and after the removal of the CTR component reveals
significant differences in the component maps ( Fig. 6*b*,
*r* = 0.23).

### Simulations.

A simulation was performed to test the effect of
component removal on linearly mixed, spatially independent, and
spatially dependent activations. Three simulated activations (one CTR
and two TTR) were added to the data from the first trial in brain
regions with specified distributions D_{CTR},
D_{TTR1}, and D_{TTR2} (Fig.
7 *Upper*). The
D_{CTR} (posterior) and D_{TTR1} (frontal)
distributions were highly overlapped for all but the most highly active
voxels (Fig. 7). The D_{TTR2} (parietal) was independent from
the other two distributions. An ICA decomposition was performed both
before and after removal of D_{CTR} by using the method
outlined in the Appendix.

ICA decomposition on the data including the simulated activations
recovered three components (Fig. 7*b*) with time courses
similar to the added signals. The separated spatial component voxel
values (scaled to z-scores) correlated 0.92, 0.54, and 0.99,
respectively, with the original simulated distributions
D_{CTR}, D_{TTR1}, and D_{TTR2}.
Re-computation of the maps after removal of the CTR component with the
method outlined in the Appendix resulted in a more accurate
separation of the original distributions (*r* = 0.97 and
0.99 with D_{TTR1} and D_{TTR2}, respectively).
Component TTR2 (parietal), with a different spatial distribution to
CTR, was largely unaffected by the removal of the CTR component (Fig. 7
*b* and *c*). Conversely, TTR1, which significantly
overlapped with CTR, was recovered more accurately after CTR removal
(Fig. 7*c*).

## Discussion

The Stroop color-naming task has long been used for the assessment of patients with closed head injury and frontal lobe lesions (15, 16). Although the brain region affected in closed head injury is typically diffuse, frontal lobes and particularly orbitofrontal cortex are most often affected. Previous PET studies of Stroop task performance reported occipital and medial frontal activation (17). The active participation of frontal areas in the CTR components found by ICA for both Stroop task trials confirm the association of Stroop task performance with frontal activation in this subject. An ICA analysis of data from two other subjects, reported elsewhere (18), was similar. As expected, visual and visual-association areas dominated the active maps of these components. Several features of the time course of the CTR components, including a longer than expected rise time and a trend toward decreasing activation during the second half of each 40-sec Stroop block, were similar in each task block. These features differed from the task reference function used in correlation analyses.

In both trials, separating the fMRI data into independent spatial
components also produced several components that appeared TTR. Most
often, these showed a marked activation at the onset of one or two of
the four Stroop task blocks, especially the first and second blocks
(Figs. 1*b* and 4, in trial 1) or the second and third blocks
(in trial 2). The most active areas of the TTR components contained
large frontal regions (Fig. 1*b*), implying that frontal
Stroop task-related activations differed in strength and spatial
distribution between task blocks. Analysis methods involving averaging
over task blocks or trials to detect CTR areas of activation
necessarily ignore the possibility of TTR activations, although these
may potentially be of considerable interest. Changes in the amount and
distribution of frontal activation during cognitive performance
reported in several previous PET and fMRI studies have been linked to
changes in stimulus novelty (19), verbal fluency (20), verbal
suppression (21), working memory (22), visual–spatial attention (23),
and language processing (24), all of which may be involved in Stroop
task performance.

Our exploratory results suggest that ICA can be used to discover both transient and/or consistently appearing activations, without requiring either their general or precise time courses to be known in advance of the analysis. In particular, details of the time courses of task-related activations found by ICA for our data were unanticipated and might be expected to differ between subjects. Unlike correlational methods, ICA considers all time points individually, without requiring averaging across stimuli or task blocks (5). For these data, as few as 50 time points seemed sufficient to detect details of the CTR and TTR components. Fewer time points would result in fewer components separated by the ICA algorithm, requiring the noise inherent to the data being distributed among the fewer components. Thus, ICA has several advantages compared with other methods of fMRI analysis including correlation and statistical parametric mapping (SPM) (25), in which the time courses and/or spatial extents of anticipated effects must be modeled explicitly before analysis.

To test whether the segregation into occipital CTR and frontal TTR components was in part a consequence of the spatial independence criterion used by the algorithm, we removed the CTR component from the data. ICA decomposition of this new data set gave several TTR components with both frontal and occipital active areas, but left maps unrelated to task activation relatively unaffected (e.g., a component capturing an apparent head movement artifact, Fig. 5). This, coupled with the simulation results, lends support to the original supposition that the spatial patterns of task-related brain activation are spatially independent from the spatial patterns of activity related to artifacts and other physiological processes. Spatial independence of task-related changes from artifact can also be inferred from the observation that the CTR maps had time courses more closely related to the task reference function as stricter criteria for independence between map voxels were applied, from PCA (second order), Comon’s ICA technique (fourth order), to the higher-order ICA algorithm used here (Appendix). However, the fact that some TTR maps were altered by removal of the CTR component suggests that there is some spatial dependence between these task-related components. Further work is needed to determine more clearly the ways in which CTR component removal affects TTR components, as well as methods for assessing the reliability of ICA maps and time courses.

## Conclusions

ICA is a new method for analyzing fMRI that is able to separate task-related activations from artifactual and other physiological fluctuations in the fMRI signal, including transient brain activity. ICA does not make assumptions about the time courses or spatial extent of activations, and thus appears to be well suited for the detection of both consistently and transiently task-related brain activations as well as separating out artifactual and other physiological processes from fMRI data (8–10). Possibly the greatest promise lies in its potential for separating and measuring multiple neurophysiological processes taking place during learning or other normal and abnormal brain state transitions whose time courses are difficult to predict or measure by other means.

## Acknowledgments

The Heart and Stroke Foundation of Ontario, the Howard Hughes Medical Institute, and the Office of Naval Research supported this research.

## Technical Appendix

### The Extended Independent Component Analysis (ICA) Algorithm.

Bell and Sejnowski (10, 11) have proposed a simple neural network
algorithm for performing ICA. The algorithm iteratively finds a linear
transformation, *W*, that minimizes the statistical dependence
between components:
5
where *W _{S}*, the “sphering
matrix,” is defined,
6
and

*X*is the (row mean-zero)

*N*by

*M*fMRI signal data matrix (

*N*, the number of time points in the trial, and

*M*, the number of brain voxels) obtained by removing the mean signal level from each time point. The sphering matrix makes the maps uncorrelated, whereas

*W*reduces the higher-order correlations between the component maps contained in the rows of

_{H}*C*.

Unless otherwise specified, we define *W* as
*W _{H}W_{S}*. The
algorithm attempts to maximize the entropy

*H()*of

*y*, a nonlinear transform by a specified function

*g()*of the computed map matrix. It does this by iteratively updating the elements of

*W*by using small batches of data vectors drawn at random from {

_{H}*W*} without substitution, according to 7 where ɛ is a small learning rate and the vector

_{S}X*ŷ*is composed of elements: 8 The

*W*

_{H}

^{T}

*W*term in Eq. 7 avoids matrix inversion and speeds convergence. During training, the learning rate is reduced gradually until the weight matrix

_{H}*W*stops changing appreciably.

_{H}The form of the nonlinearity *g()* plays an important role in
the success of the algorithm. The ideal form for *g()* is the
cumulative density function (c.d.f.) of the distributions of the voxel
values in the component maps. In practice, if we choose *g()*
to be a logistic sigmoid function *g*(*C*) = (1 +
*exp*(−*C*))^{−1}, as in ref.
11, the algorithm is limited to separating sources with super-Gaussian
distributions, but is otherwise relatively insensitive to the exact
probability distributions of the component maps. For this choice of
*g()*, *ŷ* = 1 − 2 *y.*

The ICA learning rule has been extended to components with either sub-
or super-Gaussian distributions (26) by approximating the estimated
probability density function (p.d.f.) by a fourth-order Edgeworth
approximation, as derived by Girolami and Fyfe (27), giving
9
where *K*_{4} is the diagonal matrix of
kurtosis values for the computed component map value distributions
*C*, defined by,
10
Intuitively, for super-Gaussian components
(*K*_{4} > 0), the
(sign(*K*_{4})) term is an anti-Hebbian rule
that tends to push the probability density of *C* toward
sparse distributions, whereas for sub-Gaussians
(*K*_{4} < 0), the corresponding term is a
Hebbian rule that tends to push the densities of *C* toward
sub-Gaussian distributions.

### Component Removal.

Removal of one or more component(s) can be
accomplished by
11
where *Wa*^{−1} is the inverse of
*W* with columns corresponding to the component(s) to be
removed subsequently set to zero, and *X _{a}*
is the reconstructed data with the given component(s) removed.

Matrix *X _{a}* in Eq. 11 will now be
of reduced rank and cannot be separated by the ICA algorithm. Using
principal component analysis (PCA) to reduce the dimension of

*X*averts this problem: 12 where

_{a}*V*is

_{p}*n*by

*p*(

*p*<

*n*) matrix whose columns are the unit length eigenvectors of the covariance matrix, 〈

*X*

_{a}X_{a}

^{T}〉, corresponding to the

*p*largest eigenvalues, V

_{p}

^{T}is transpose of

*V*, and

_{p}*X*is calculated from Eq. 10.

_{a}*A*is a now smaller but full-rank matrix of eigenimages of

_{p}*X*. The number

_{a}*p*may be taken as the number of eigenvectors required to explain a predetermined proportion of the variance in the original data (e.g., >99%). ICA decomposition of the resulting eigenimages,

*A*, gives, 13 where

_{p}*C*is the

_{a}*p*by

*n*matrix of component maps, and

*W*is the computed unmixing matrix.

_{E}Substituting for *A _{p}* from Eq. 11
gives:
14
or
15
whence
16
giving
17
since

*V*

_{p}V_{pT}=

*I*because eigenvectors are mutually orthogonal. Finding the

*p*time courses (of length

*n*) associated with each of the

*p*maps can now be determined by examining the columns of the matrix, 18

## Footnotes

↵† To whom reprint requests should be addressed at: Computational Neurobiology Laboratory, Salk Institute for Biological Studies, 10010 North Torrey Pines Road, La Jolla, CA 92037-1099. e-mail: martin{at}salk.edu.

This paper was presented at a colloquium entitled “Neuroimaging of Human Brain Function,” organized by Michael Posner and Marcus E. Raichle, held May 29–31, 1997, sponsored by the National Academy of Sciences at the Arnold and Mabel Beckman Center in Irvine, CA.

## ABBREVIATIONS

- TTR,
- transiently task-related;
- CTR,
- consistently task-related;
- ICA,
- independent component analysis;
- fMRI,
- functional MRI

- Copyright © 1998, The National Academy of Sciences

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