Image volumes were aligned to AC-PC. The fMRI data were analysed with statistical parametric selleck screening library mapping using SPM5 software (Wellcome Department of Cognitive Neurology, London, UK). The first four volumes of all EPI series were excluded from the analysis to allow the magnetisation to approach a dynamic equilibrium. Data processing started with slice time correction and realignment of the EPI datasets. A mean image for all EPI volumes was created, to which individual volumes were spatially realigned by rigid body transformations.

The high-resolution structural image was co-registered with the mean image of the EPI series. Then the structural image was normalised to the Montreal Neurological Institute (MNI) template, and the normalisation parameters were applied to the EPI images to ensure an anatomically informed normalisation. During normalisation the anatomy image volumes were resampled to 1 × 1 × 1 mm3. A filter of 8 mm full-width at half maximum (FWHM) was used. Low-frequency drifts in the time domain were removed by modelling the time series for each voxel by a set of discrete cosine functions to which a cut-off of 128 sec was applied. The subject-level statistical

analyses were performed using a GLM. To analyse the interval estimation task, we built a model with six separate regressors for active 200 msec, active 300 msec, active 400 msec, passive 200 msec, passive 300 msec, passive 400 msec. We also calculated the judgement Veliparib error on each trial, defined as the judged interval duration minus the actual interval duration. Note that a strong intentional the binding effect therefore corresponds to a large and negative value judgement error. We then parametrically modulated the above six regressors

by the judgement error. Movement parameters were included to account for variance associated with head motion. All resulting vectors were convolved with the canonical haemodynamic response function (HRF) and its temporal derivative to form the main regressors in the design matrix (the regression model). The statistical parameter estimates were computed separately for each voxel for all columns in the design matrix. Contrast images were constructed for each individual to compare the relevant parameter estimates for the regressors containing the canonical HRF. Next, a group-level random effects analysis was performed. One-sample t-test was performed for each voxel of the contrast images. The resulting statistical values were thresholded with a level of significance of p < .001 (z > 3.09, uncorrected). To correct for multiple comparisons we applied small volume correction in the SMA and angular gyrus, based on previous neuroimaging findings that SMA houses action–effect links (MNI coordinate: −4 −8 71, Elsner et al., 2002) and that angular gyrus is involved in explicit agency judgements (MNI coordinates: 58 −46 48; −48 −46 56, Farrer et al., 2008).