Fmri Preprocessing Pipeline Guide

Research Planning Protocol

Before executing the domain-specific steps below, you MUST:

1. State the research question — What analysis will follow preprocessing and what does it require?
2. Justify the preprocessing choices — Why these steps in this order? What alternatives were considered?
3. Declare expected quality metrics — What motion thresholds, SNR values, and exclusion criteria will you use?
4. Note assumptions and limitations — What does this pipeline assume about the data? Where could it mislead?
5. Present the plan to the user and WAIT for confirmation before proceeding.

For detailed methodology guidance, see the research-literacy skill.

⚠️ Verification Notice

This skill was generated by AI from academic literature. All parameters, thresholds, and citations require independent verification before use in research. If you find errors, please open an issue.

Pipeline Order Decision Tree

The standard preprocessing order is well-established, but branch points exist depending on the analysis type. The canonical order is:

1. DICOM to NIfTI conversion (BIDS format)
2. Discard non-steady-state volumes
3. Slice timing correction (conditional)
4. Motion correction (rigid body)
5. Distortion correction (fieldmap-based)
6. Coregistration (functional to structural)
7. Spatial normalization (to MNI/template space)
8. Smoothing (conditional on analysis type)

Decision points:

Is your TR < 1 second (e.g., multiband)?
 |
 +-- YES --> Skip slice timing correction; use temporal derivative in GLM instead
 | (Sladky et al., 2011; HCP consortium recommendation)
 |
 +-- NO --> Apply slice timing correction before motion correction
 (AFNI and SPM convention; Sladky et al., 2011)

What is your analysis type?
 |
 +-- Task activation (univariate GLM)
 | --> Full pipeline with smoothing (FWHM = 2-3x voxel size)
 |
 +-- Resting-state connectivity
 | --> Full pipeline + aggressive confound regression; smoothing 4-6 mm
 |
 +-- MVPA / multivariate decoding
 --> Full pipeline WITHOUT smoothing (or minimal, <= 2 mm)
 Smooth only after first-level pattern extraction

Core Preprocessing Steps

Step 1: DICOM to NIfTI Conversion

Convert raw DICOM files to NIfTI format organized in BIDS (Brain Imaging Data Structure; Gorgolewski et al., 2016). BIDS standardizes file naming and metadata, enabling automated pipeline tools like fMRIPrep to detect acquisition parameters automatically.

Tools: dcm2niix (Li et al., 2016), heudiconv, BIDScoin

Step 2: Discard Non-Steady-State Volumes

The first few volumes of an fMRI run are acquired before the MR signal reaches T1 equilibrium, producing artificially high signal intensity. Discard the first 3-5 volumes (approximately 5-10 seconds) unless the scanner automatically acquired dummy scans (Poldrack et al., 2011, Ch. 5).

Domain insight: Modern scanners often acquire dummy scans that are not saved. Check the acquisition protocol. fMRIPrep detects non-steady-state volumes automatically using signal intensity changes.

Step 3: Slice Timing Correction

Within each TR, slices are acquired sequentially (not simultaneously), creating temporal offsets of up to one full TR between first and last slices. Slice timing correction (STC) interpolates each slice to a common time point (Sladky et al., 2011).

Order debate: STC before motion correction is standard in AFNI and SPM. FSL applies STC after motion correction. Both are acceptable; the optimal order depends on the level of motion and slice acquisition pattern (Parker & Razlighi, 2019). Ideally, joint correction would be applied (Roche, 2011), but this is not yet standard in major packages.

Step 4: Motion Correction

Align all volumes to a reference volume using 6-parameter rigid body (3 translation, 3 rotation) transformation (Jenkinson et al., 2002). This is the single most critical preprocessing step.

Domain insight: Motion correction is inherently imperfect because each slice within a volume was acquired at a different time. When the head moves during a TR, each slice has a slightly different rigid-body transformation, but whole-volume correction applies a single transformation. This is an unavoidable limitation (Jenkinson et al., 2002).

Output: Save the 6 motion parameters for use as confound regressors in the GLM (see fmri-glm-analysis-guide).

Step 5: Distortion Correction

EPI images suffer geometric distortions along the phase-encoding direction due to B0 field inhomogeneities. Distortions are worst near air-tissue boundaries: orbitofrontal cortex, anterior temporal lobes, and inferior temporal regions (Jezzard & Balaban, 1995).

Domain warning: If no fieldmap data were acquired, fMRIPrep can perform fieldmapless distortion correction using nonlinear registration to the T1, but this is less accurate than fieldmap-based methods. Always acquire fieldmap data when possible.

Step 6: Coregistration

Align the functional (EPI) image to the subject's structural (T1-weighted) image. This enables projecting functional results onto anatomical space and provides the bridge to template normalization.

• Method: Boundary-based registration (BBR; Greve & Fischl, 2009) is preferred over intensity-based methods for EPI-to-T1 alignment because it uses white matter boundaries, which are well-defined in both modalities
• Always visually inspect the coregistration overlay (functional edges on structural image)

Step 7: Spatial Normalization

Warp each subject's brain to a standard template space to enable group-level comparisons.

Domain warning: Always visually inspect normalization quality. Check that major sulci (central sulcus, Sylvian fissure) and subcortical structures (caudate, putamen) align with the template. Poor normalization is a common but silent source of error in group analyses.

Step 8: Spatial Smoothing

Smoothing with a Gaussian kernel increases SNR, satisfies the smoothness assumptions of Random Field Theory, and reduces inter-subject anatomical variability (Mikl et al., 2008).

Domain warning: Smoothing before MVPA is one of the most common preprocessing errors. For multivariate analyses, skip smoothing during preprocessing entirely. If group-level smoothing is needed, apply it only after the first-level pattern analysis is complete (Misaki et al., 2013).

Step 9: Confound Regression

Confound regression removes variance from non-neural sources. This step is typically performed during the statistical model (GLM) rather than as a separate preprocessing step, but the preprocessing pipeline must output the confound time series.

For detailed confound regression guidance, see the fmri-glm-analysis-guide skill.

Key confounds to extract during preprocessing:

• 6 motion parameters (from Step 4) and their temporal derivatives and squared terms (24-parameter model; Friston et al., 1996)
• Framewise displacement (FD; Power et al., 2012)
• DVARS (Power et al., 2012)
• aCompCor components from white matter and CSF (Behzadi et al., 2007)
• Global signal (optional; controversial for connectivity analyses; Murphy & Fox, 2017)

Pipeline Variants by Analysis Type

fMRIPrep as the Recommended Standard

fMRIPrep (Esteban et al., 2019) is recommended as the default preprocessing tool for most fMRI studies. It provides:

• Automated, analysis-agnostic preprocessing that adapts to the specific dataset
• Transparent, reproducible workflow with detailed visual reports for QC
• Best-in-breed algorithms: ANTs for normalization, FreeSurfer for surface reconstruction, MCFLIRT/ANTs for motion correction
• BIDS-compatible input and output
• Comprehensive confound time series output (motion, CompCor, FD, DVARS)

What fMRIPrep does NOT do:

• Smoothing (intentionally left to the user because the optimal kernel depends on analysis type)
• Temporal filtering (left to the GLM stage)
• Confound regression (outputs confounds but does not regress them)
• Statistical analysis

Domain insight: fMRIPrep outputs the preprocessed BOLD data in both MNI space and native space. For MVPA, use the native-space output. For group analyses, use the MNI-space output.

Common Pitfalls

1. Smoothing before MVPA: Spatial smoothing destroys the fine-grained voxel patterns that multivariate methods rely on. Skip smoothing entirely for MVPA and searchlight analyses (Misaki et al., 2013)

2. Wrong interpolation for final reslicing: Use sinc or spline interpolation for the final reslice step. Trilinear interpolation is acceptable during motion parameter estimation but introduces blurring in final images (Poldrack et al., 2011, Ch. 5)

3. Not checking normalization quality: Normalization can fail silently, especially in populations with atypical anatomy (older adults, patients with lesions, pediatric). Always visually inspect the overlap of normalized functional images with the template

4. Motion-connectivity confound in resting-state: Head motion creates spurious short-distance correlations and reduces long-distance correlations in functional connectivity (Power et al., 2012). For resting-state analyses, use stringent motion thresholds (FD < 0.2 mm; Power et al., 2014) and aggressive confound regression (Ciric et al., 2017)

5. Skipping distortion correction: Without distortion correction, orbitofrontal and anterior temporal signals are mislocalized by several millimeters. This is especially problematic for studies of emotion, reward, and memory, which involve these regions (Jezzard & Balaban, 1995)

6. Applying band-pass filtering for task fMRI: Band-pass filtering (0.01-0.1 Hz) is appropriate for resting-state connectivity analysis but removes task-related signal in event-related and block designs. For task fMRI, use only high-pass filtering in the GLM

7. Not discarding non-steady-state volumes: The first few volumes have inflated signal intensity. If not removed, they can bias motion estimates and inflate variance (Poldrack et al., 2011, Ch. 5)

For detailed step-by-step parameters and software-specific guidance, see references/step-by-step-pipeline.md. For quality control metrics, thresholds, and exclusion criteria, see references/quality-control.md.

Key References

• Andersson, J. L. R., Skare, S., & Ashburner, J. (2003). How to correct susceptibility distortions in spin-echo echo-planar images: application to diffusion tensor imaging. NeuroImage, 20(2), 870-888.
• Ashburner, J., & Friston, K. J. (2005). Unified segmentation. NeuroImage, 26(3), 839-851.
• Avants, B. B., Epstein, C. L., Grossman, M., & Gee, J. C. (2008). Symmetric diffeomorphic image registration with cross-correlation. Medical Image Analysis, 12(1), 26-41.
• Behzadi, Y., Restom, K., Liau, J., & Liu, T. T. (2007). A component based noise correction method (CompCor) for BOLD and perfusion based fMRI. NeuroImage, 37(1), 90-101.
• Ciric, R., Wolf, D. H., Power, J. D., et al. (2017). Benchmarking of participant-level confound regression strategies. NeuroImage, 154, 174-187.
• Esteban, O., Birman, D., Schaer, M., et al. (2017). MRIQC: Advancing the automatic prediction of image quality in MRI from unseen sites. PLoS ONE, 12(9), e0184661.
• Esteban, O., Markiewicz, C. J., Blair, R. W., et al. (2019). fMRIPrep: a robust preprocessing pipeline for functional MRI. Nature Methods, 16, 111-116.
• Fonov, V. S., Evans, A. C., Botteron, K., et al. (2011). Unbiased average age-appropriate atlases for pediatric studies. NeuroImage, 54(1), 313-327.
• Friston, K. J., Williams, S., Howard, R., et al. (1996). Movement-related effects in fMRI time-series. Magnetic Resonance in Medicine, 35(3), 346-355.
• Gorgolewski, K. J., Auer, T., Calhoun, V. D., et al. (2016). The brain imaging data structure. Scientific Data, 3, 160044.
• Greve, D. N., & Fischl, B. (2009). Accurate and robust brain image alignment using boundary-based registration. NeuroImage, 48(1), 63-72.
• Jenkinson, M., Bannister, P., Brady, J. M., & Smith, S. M. (2002). Improved optimization for the robust and accurate linear registration and motion correction of brain images. NeuroImage, 17(2), 825-841.
• Jezzard, P., & Balaban, R. S. (1995). Correction for geometric distortion in echo planar images from B0 field variations. Magnetic Resonance in Medicine, 34(1), 65-73.
• Mikl, M., Marecek, R., Hlustik, P., et al. (2008). Effects of spatial smoothing on fMRI group inferences. Magnetic Resonance Imaging, 26(4), 490-503.
• Misaki, M., Luh, W. M., & Bandettini, P. A. (2013). The effect of spatial smoothing on fMRI decoding of columnar-level organization. NeuroImage, 78, 13-22.
• Murphy, K., & Fox, M. D. (2017). Towards a consensus regarding global signal regression for resting state functional connectivity MRI. NeuroImage, 154, 169-173.
• Parker, D. B., & Razlighi, Q. R. (2019). The benefit of slice timing correction in common fMRI preprocessing pipelines. Frontiers in Neuroscience, 13, 821.
• Poldrack, R. A., Mumford, J. A., & Nichols, T. E. (2011). Handbook of Functional MRI Data Analysis. Cambridge University Press.
• Power, J. D., Barnes, K. A., Snyder, A. Z., et al. (2012). Spurious but systematic correlations in functional connectivity MRI networks arise from subject motion. NeuroImage, 59(3), 2142-2154.
• Power, J. D., Mitra, A., Laumann, T. O., et al. (2014). Methods to detect, characterize, and remove motion artifact in resting state fMRI. NeuroImage, 84, 320-341.
• Sladky, R., Friston, K., Trostl, J., et al. (2011). Slice-timing effects and their correction in functional MRI. NeuroImage, 58(2), 588-594.

See references/ for detailed pipeline parameters and quality control procedures.