|
subjectkey |
GUID |
|
Required |
The NDAR Global Unique Identifier (GUID) for research subject |
NDAR*
|
|
|
|
src_subject_id |
String |
20
|
Required |
Subject ID how it's defined in lab/project |
|
|
subject_id |
|
interview_date |
Date |
|
Required |
Date on which the interview/genetic test/sampling/imaging/biospecimen was completed. MM/DD/YYYY |
|
|
|
|
interview_age |
Integer |
|
Required |
Age in months at the time of the interview/test/sampling/imaging. |
0::1440
|
Age is rounded to chronological month. If the research participant is 15-days-old at time of interview, the appropriate value would be 0 months. If the participant is 16-days-old, the value would be 1 month.
|
|
|
sex |
String |
20
|
Required |
Sex of subject at birth |
M;F; O; NR
|
M = Male; F = Female; O=Other; NR = Not reported
|
gender |
|
scan_type |
String |
50
|
Required |
Type of Scan |
MR diffusion; fMRI; MR structural (MPRAGE); MR structural (T1); MR structural (PD); MR structural (FSPGR); MR structural (FISP); MR structural (T2); PET; ASL; microscopy; MR structural (PD, T2); MR structural (B0 map); MR structural (B1 map); single-shell DTI; multi-shell DTI; Field Map; X-Ray; static magnetic field B0; pCASL: ASL; MR: T2star; MR: FLAIR; Localizer scan; MR structural (FLASH); MR structural (MP2RAGE); MR structural (TSE); MR structural (T1, T2); 2D gradient echo; MR structural (MPnRAGE); Magnetic Resonance Spectroscopy(MRS); Neuromelanin MRI (NM-MRI); Functional Near Infrared Spectroscopy(fNIRS); MT; Magnetic Resonance Elastography (MRE); T1rho Spin-lock image
|
|
|
|
t1_cjv |
Float |
|
Conditional |
coefficient of joint variation (CJV): The cjv of GM and WM was proposed as objective function by [Ganzetti2016] for the optimization of INU correction algorithms. Higher values are related to the presence of heavy head motion and large INU artifacts. Lower values are better. |
|
|
|
|
t1_cnr |
Float |
|
Conditional |
contrast-to-noise ratio (CNR): The cnr [Magnota2006], is an extension of the SNR calculation to evaluate how separated the tissue distributions of GM and WM are. Higher values indicate better quality. |
|
|
|
|
t1_efc |
Float |
|
Conditional |
The EFC [Atkinson1997] uses the Shannon entropy of voxel intensities as an indication of ghosting and blurring induced by head motion. Lower values are better. The original equation is normalized by the maximum entropy, so that the EFC can be compared across images with different dimensions. |
|
|
|
|
t1_fber |
Float |
|
Conditional |
The FBER [Shehzad2015], defined as the mean energy of image values within the head relative to outside the head [QAP-measures]. Higher values are better. |
|
|
|
|
t1_fwhm_avg |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
t1_fwhm_x |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
t1_fwhm_y |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
t1_fwhm_z |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
t1_icvs_csf |
Float |
|
Conditional |
The ICV fractions of CSF, GM and WM. They should move within a normative range. |
|
|
|
|
t1_icvs_gm |
Float |
|
Conditional |
The ICV fractions of CSF, GM and WM. They should move within a normative range. |
|
|
|
|
t1_icvs_wm |
Float |
|
Conditional |
The ICV fractions of CSF, GM and WM. They should move within a normative range. |
|
|
|
|
t1_inu_med |
Float |
|
Conditional |
summary statistics (max, min and median) of the INU field as extracted by the N4ITK algorithm [Tustison2010]. Values closer to 1.0 are better. |
|
|
|
|
t1_inu_range |
Float |
|
Conditional |
summary statistics (max, min and median) of the INU field as extracted by the N4ITK algorithm [Tustison2010]. Values closer to 1.0 are better. |
|
|
|
|
t1_qi_1 |
Float |
|
Conditional |
Detect artifacts in the image using the method described in [Mortamet2009]. The QI1 is the proportion of voxels with intensity corrupted by artifacts normalized by the number of voxels in the background. Lower values are better. |
|
|
|
|
t1_qi_2 |
Float |
|
Conditional |
Mortamet's quality index 2 (QI2) is a calculation of the goodness-of-fit of a chi-2 distribution on the air mask, once the artifactual intensities detected for computing the QI1 index have been removed [Mortamet2009]. |
|
|
|
|
t1_rpve_csf |
Float |
|
Conditional |
the rPVe of CSF, GM and WM. Lower values are better. |
|
|
|
|
t1_rpve_gm |
Float |
|
Conditional |
the rPVe of CSF, GM and WM. Lower values are better. |
|
|
|
|
t1_rpve_wm |
Float |
|
Conditional |
the rPVe of CSF, GM and WM. Lower values are better. |
|
|
|
|
t1_size_x |
Integer |
|
Conditional |
extent in number of voxels |
|
|
|
|
t1_size_y |
Integer |
|
Conditional |
extent in number of voxels |
|
|
|
|
t1_size_z |
Integer |
|
Conditional |
extent in number of voxels |
|
|
|
|
t1_snr_csf |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
t1_snr_gm |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
t1_snr_total |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
t1_snr_wm |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
t1_snrd_csf |
Float |
|
Conditional |
Dietrich's SNR (SNRd) as proposed by [Dietrich2007], using the air background as reference. |
|
|
|
|
t1_snrd_gm |
Float |
|
Conditional |
Dietrich's SNR (SNRd) as proposed by [Dietrich2007], using the air background as reference. |
|
|
|
|
t1_snrd_total |
Float |
|
Conditional |
Dietrich's SNR (SNRd) as proposed by [Dietrich2007], using the air background as reference. |
|
|
|
|
t1_snrd_wm |
Float |
|
Conditional |
Dietrich's SNR (SNRd) as proposed by [Dietrich2007], using the air background as reference. |
|
|
|
|
t1_spacing_x |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in x direction |
|
|
|
|
t1_spacing_y |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in y direction |
|
|
|
|
t1_spacing_z |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in z direction |
|
|
|
|
t1_summary_bg_k |
Float |
|
Conditional |
background kurtosis |
|
|
|
|
t1_summary_bg_mad |
Float |
|
Conditional |
background median absolute deviation |
|
|
|
|
t1_summary_bg_mean |
Float |
|
Conditional |
background mean |
|
|
|
|
t1_summary_bg_median |
Float |
|
Conditional |
background median absolute deviation |
|
|
|
|
t1_summary_bg_n |
Float |
|
Conditional |
background count of voxels |
|
|
|
|
t1_summary_bg_p05 |
Float |
|
Conditional |
background 5th percentile |
|
|
|
|
t1_summary_bg_p95 |
Float |
|
Conditional |
background 95th percentile |
|
|
|
|
t1_summary_bg_stdv |
Float |
|
Conditional |
background standard deviation |
|
|
|
|
t1_summary_csf_k |
Float |
|
Conditional |
cerebrospinal fluid kurtosis |
|
|
|
|
t1_summary_csf_mad |
Float |
|
Conditional |
cerebrospinal fluid median absolute deviation |
|
|
|
|
t1_summary_csf_mean |
Float |
|
Conditional |
cerebrospinal fluid mean |
|
|
|
|
t1_summary_csf_median |
Float |
|
Conditional |
cerebrospinal fluid median absolute deviation |
|
|
|
|
t1_summary_csf_n |
Float |
|
Conditional |
cerebrospinal fluid count of voxels |
|
|
|
|
t1_summary_csf_p05 |
Float |
|
Conditional |
cerebrospinal fluid 5th percentile |
|
|
|
|
t1_summary_csf_p95 |
Float |
|
Conditional |
cerebrospinal fluid 95th percentile |
|
|
|
|
t1_summary_csf_stdv |
Float |
|
Conditional |
cerebrospinal fluid standard deviation |
|
|
|
|
t1_summary_gm_k |
Float |
|
Conditional |
grey matter kurtosis |
|
|
|
|
t1_summary_gm_mad |
Float |
|
Conditional |
grey matter median absolute deviation |
|
|
|
|
t1_summary_gm_mean |
Float |
|
Conditional |
grey matter mean |
|
|
|
|
t1_summary_gm_median |
Float |
|
Conditional |
grey matter median absolute deviation |
|
|
|
|
t1_summary_gm_n |
Float |
|
Conditional |
grey matter count of voxels |
|
|
|
|
t1_summary_gm_p05 |
Float |
|
Conditional |
grey matter 5th percentile |
|
|
|
|
t1_summary_gm_p95 |
Float |
|
Conditional |
grey matter 95th percentile |
|
|
|
|
t1_summary_gm_stdv |
Float |
|
Conditional |
grey matter standard deviation |
|
|
|
|
t1_summary_wm_k |
Float |
|
Conditional |
white matter kurtosis |
|
|
|
|
t1_summary_wm_mad |
Float |
|
Conditional |
white matter median absolute deviation |
|
|
|
|
t1_summary_wm_mean |
Float |
|
Conditional |
white matter mean |
|
|
|
|
t1_summary_wm_median |
Float |
|
Conditional |
white matter median absolute deviation |
|
|
|
|
t1_summary_wm_n |
Float |
|
Conditional |
white matter count of voxels |
|
|
|
|
t1_summary_wm_p05 |
Float |
|
Conditional |
white matter 5th percentile |
|
|
|
|
t1_summary_wm_p95 |
Float |
|
Conditional |
white matter 95th percentile |
|
|
|
|
t1_summary_wm_stdv |
Float |
|
Conditional |
white matter standard deviation |
|
|
|
|
t1_tpm_overlap_csf |
Float |
|
Conditional |
The overlap of the TPMs estimated from the image and the corresponding maps from the ICBM nonlinear-asymmetric 2009c template. |
|
|
|
|
t1_tpm_overlap_gm |
Float |
|
Conditional |
The overlap of the TPMs estimated from the image and the corresponding maps from the ICBM nonlinear-asymmetric 2009c template. |
|
|
|
|
t1_tpm_overlap_wm |
Float |
|
Conditional |
The overlap of the TPMs estimated from the image and the corresponding maps from the ICBM nonlinear-asymmetric 2009c template. |
|
|
|
|
t1_wm2max |
Float |
|
Conditional |
The overlap of the TPMs estimated from the image and the corresponding maps from the ICBM nonlinear-asymmetric 2009c template. |
|
|
|
|
t2_cjv |
Float |
|
Conditional |
coefficient of joint variation (CJV): The cjv of GM and WM was proposed as objective function by [Ganzetti2016] for the optimization of INU correction algorithms. Higher values are related to the presence of heavy head motion and large INU artifacts. Lower values are better. |
|
|
|
|
t2_cnr |
Float |
|
Conditional |
contrast-to-noise ratio (CNR): The cnr [Magnota2006], is an extension of the SNR calculation to evaluate how separated the tissue distributions of GM and WM are. Higher values indicate better quality. |
|
|
|
|
t2_efc |
Float |
|
Conditional |
The EFC [Atkinson1997] uses the Shannon entropy of voxel intensities as an indication of ghosting and blurring induced by head motion. Lower values are better. The original equation is normalized by the maximum entropy, so that the EFC can be compared across images with different dimensions. |
|
|
|
|
t2_fber |
Float |
|
Conditional |
The FBER [Shehzad2015], defined as the mean energy of image values within the head relative to outside the head [QAP-measures]. Higher values are better. |
|
|
|
|
t2_fwhm_avg |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
t2_fwhm_x |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
t2_fwhm_y |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
t2_fwhm_z |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
t2_icvs_csf |
Float |
|
Conditional |
The ICV fractions of CSF, GM and WM. They should move within a normative range. |
|
|
|
|
t2_icvs_gm |
Float |
|
Conditional |
The ICV fractions of CSF, GM and WM. They should move within a normative range. |
|
|
|
|
t2_icvs_wm |
Float |
|
Conditional |
The ICV fractions of CSF, GM and WM. They should move within a normative range. |
|
|
|
|
t2_inu_med |
Float |
|
Conditional |
summary statistics (max, min and median) of the INU field as extracted by the N4ITK algorithm [Tustison2010]. Values closer to 1.0 are better. |
|
|
|
|
t2_inu_range |
Float |
|
Conditional |
summary statistics (max, min and median) of the INU field as extracted by the N4ITK algorithm [Tustison2010]. Values closer to 1.0 are better. |
|
|
|
|
t2_qi_1 |
Float |
|
Conditional |
Detect artifacts in the image using the method described in [Mortamet2009]. The QI1 is the proportion of voxels with intensity corrupted by artifacts normalized by the number of voxels in the background. Lower values are better. |
|
|
|
|
t2_qi_2 |
Float |
|
Conditional |
Mortamet's quality index 2 (QI2) is a calculation of the goodness-of-fit of a chi-2 distribution on the air mask, once the artifactual intensities detected for computing the QI1 index have been removed [Mortamet2009]. |
|
|
|
|
t2_rpve_csf |
Float |
|
Conditional |
the rPVe of CSF, GM and WM. Lower values are better. |
|
|
|
|
t2_rpve_gm |
Float |
|
Conditional |
the rPVe of CSF, GM and WM. Lower values are better. |
|
|
|
|
t2_rpve_wm |
Float |
|
Conditional |
the rPVe of CSF, GM and WM. Lower values are better. |
|
|
|
|
t2_size_x |
Integer |
|
Conditional |
extent in number of voxels |
|
|
|
|
t2_size_y |
Integer |
|
Conditional |
extent in number of voxels |
|
|
|
|
t2_size_z |
Integer |
|
Conditional |
extent in number of voxels |
|
|
|
|
t2_snr_csf |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
t2_snr_gm |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
t2_snr_total |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
t2_snr_wm |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
t2_snrd_csf |
Float |
|
Conditional |
Dietrich's SNR (SNRd) as proposed by [Dietrich2007], using the air background as reference. |
|
|
|
|
t2_snrd_gm |
Float |
|
Conditional |
Dietrich's SNR (SNRd) as proposed by [Dietrich2007], using the air background as reference. |
|
|
|
|
t2_snrd_total |
Float |
|
Conditional |
Dietrich's SNR (SNRd) as proposed by [Dietrich2007], using the air background as reference. |
|
|
|
|
t2_snrd_wm |
Float |
|
Conditional |
Dietrich's SNR (SNRd) as proposed by [Dietrich2007], using the air background as reference. |
|
|
|
|
t2_spacing_x |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in x direction |
|
|
|
|
t2_spacing_y |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in y direction |
|
|
|
|
t2_spacing_z |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in z direction |
|
|
|
|
t2_summary_bg_k |
Float |
|
Conditional |
background kurtosis |
|
|
|
|
t2_summary_bg_mad |
Float |
|
Conditional |
background median absolute deviation |
|
|
|
|
t2_summary_bg_mean |
Float |
|
Conditional |
background mean |
|
|
|
|
t2_summary_bg_median |
Float |
|
Conditional |
background median absolute deviation |
|
|
|
|
t2_summary_bg_n |
Float |
|
Conditional |
background count of voxels |
|
|
|
|
t2_summary_bg_p05 |
Float |
|
Conditional |
background 5th percentile |
|
|
|
|
t2_summary_bg_p95 |
Float |
|
Conditional |
background 95th percentile |
|
|
|
|
t2_summary_bg_stdv |
Float |
|
Conditional |
background standard deviation |
|
|
|
|
t2_summary_csf_k |
Float |
|
Conditional |
cerebrospinal fluid kurtosis |
|
|
|
|
t2_summary_csf_mad |
Float |
|
Conditional |
cerebrospinal fluid median absolute deviation |
|
|
|
|
t2_summary_csf_mean |
Float |
|
Conditional |
cerebrospinal fluid mean |
|
|
|
|
t2_summary_csf_median |
Float |
|
Conditional |
cerebrospinal fluid median absolute deviation |
|
|
|
|
t2_summary_csf_n |
Float |
|
Conditional |
cerebrospinal fluid count of voxels |
|
|
|
|
t2_summary_csf_p05 |
Float |
|
Conditional |
cerebrospinal fluid 5th percentile |
|
|
|
|
t2_summary_csf_p95 |
Float |
|
Conditional |
cerebrospinal fluid 95th percentile |
|
|
|
|
t2_summary_csf_stdv |
Float |
|
Conditional |
cerebrospinal fluid standard deviation |
|
|
|
|
t2_summary_gm_k |
Float |
|
Conditional |
grey matter kurtosis |
|
|
|
|
t2_summary_gm_mad |
Float |
|
Conditional |
grey matter median absolute deviation |
|
|
|
|
t2_summary_gm_mean |
Float |
|
Conditional |
grey matter mean |
|
|
|
|
t2_summary_gm_median |
Float |
|
Conditional |
grey matter median absolute deviation |
|
|
|
|
t2_summary_gm_n |
Float |
|
Conditional |
grey matter count of voxels |
|
|
|
|
t2_summary_gm_p05 |
Float |
|
Conditional |
grey matter 5th percentile |
|
|
|
|
t2_summary_gm_p95 |
Float |
|
Conditional |
grey matter 95th percentile |
|
|
|
|
t2_summary_gm_stdv |
Float |
|
Conditional |
grey matter standard deviation |
|
|
|
|
t2_summary_wm_k |
Float |
|
Conditional |
white matter kurtosis |
|
|
|
|
t2_summary_wm_mad |
Float |
|
Conditional |
white matter median absolute deviation |
|
|
|
|
t2_summary_wm_mean |
Float |
|
Conditional |
white matter mean |
|
|
|
|
t2_summary_wm_median |
Float |
|
Conditional |
white matter median absolute deviation |
|
|
|
|
t2_summary_wm_n |
Float |
|
Conditional |
white matter count of voxels |
|
|
|
|
t2_summary_wm_p05 |
Float |
|
Conditional |
white matter 5th percentile |
|
|
|
|
t2_summary_wm_p95 |
Float |
|
Conditional |
white matter 95th percentile |
|
|
|
|
t2_summary_wm_stdv |
Float |
|
Conditional |
white matter standard deviation |
|
|
|
|
t2_tpm_overlap_csf |
Float |
|
Conditional |
The overlap of the TPMs estimated from the image and the corresponding maps from the ICBM nonlinear-asymmetric 2009c template. |
|
|
|
|
t2_tpm_overlap_gm |
Float |
|
Conditional |
The overlap of the TPMs estimated from the image and the corresponding maps from the ICBM nonlinear-asymmetric 2009c template. |
|
|
|
|
t2_tpm_overlap_wm |
Float |
|
Conditional |
The overlap of the TPMs estimated from the image and the corresponding maps from the ICBM nonlinear-asymmetric 2009c template. |
|
|
|
|
t2_wm2max |
Float |
|
Conditional |
The white-matter to maximum intensity ratio is the median intensity within the WM mask over the 95% percentile of the full intensity distribution, that captures the existence of long tails due to hyper-intensity of the carotid vessels and fat. Values should be around the interval [0.6, 0.8]. |
|
|
|
|
bold_dummy_trs |
Integer |
|
Conditional |
Number of volumes (“dummy scans”) discarded by the scanner (as opposed to those discarded by the user post hoc) before saving the imaging file. For example, a sequence that automatically discards the first 4 volumes before saving would have this field as 4. A sequence that doesn’t discard dummy scans would have this set to 0. |
|
|
|
|
bold_dvars_nstd |
Float |
|
Conditional |
D referring to temporal derivative of timecourses, VARS referring to RMS variance over voxels ([Power2012] dvars_nstd) indexes the rate of change of BOLD signal across the entire brain at each frame of data. DVARS is calculated with nipype after motion correction |
|
|
|
|
bold_dvars_std |
Float |
|
Conditional |
D referring to temporal derivative of timecourses, VARS referring to RMS variance over voxels ([Power2012] dvars_nstd) indexes the rate of change of BOLD signal across the entire brain at each frame of data. DVARS is calculated with nipype after motion correction |
|
|
|
|
bold_dvars_vstd |
Float |
|
Conditional |
D referring to temporal derivative of timecourses, VARS referring to RMS variance over voxels ([Power2012] dvars_nstd) indexes the rate of change of BOLD signal across the entire brain at each frame of data. DVARS is calculated with nipype after motion correction |
|
|
|
|
bold_efc |
Float |
|
Conditional |
The EFC [Atkinson1997] uses the Shannon entropy of voxel intensities as an indication of ghosting and blurring induced by head motion. Lower values are better. The original equation is normalized by the maximum entropy, so that the EFC can be compared across images with different dimensions. |
|
|
|
|
bold_fber |
Float |
|
Conditional |
The FBER [Shehzad2015], defined as the mean energy of image values within the head relative to outside the head [QAP-measures]. Higher values are better. |
|
|
|
|
bold_fd_mean |
Float |
|
Conditional |
expresses instantaneous head-motion. MRIQC reports the average FD, labeled as fd_mean. Rotational displacements are calculated as the displacement on the surface of a sphere of radius 50 mm. Along with the base framewise displacement, MRIQC reports the number of timepoints above FD threshold (fd_num), and the percent of FDs above the FD threshold w.r.t. the full timeseries (fd_perc). In both cases, the threshold is set at 0.20mm. [Power2012]: |
|
|
|
|
bold_fd_num |
Float |
|
Conditional |
expresses instantaneous head-motion. MRIQC reports the average FD, labeled as fd_mean. Rotational displacements are calculated as the displacement on the surface of a sphere of radius 50 mm. Along with the base framewise displacement, MRIQC reports the number of timepoints above FD threshold (fd_num), and the percent of FDs above the FD threshold w.r.t. the full timeseries (fd_perc). In both cases, the threshold is set at 0.20mm. [Power2012]: |
|
|
|
|
bold_fd_perc |
Float |
|
Conditional |
expresses instantaneous head-motion. MRIQC reports the average FD, labeled as fd_mean. Rotational displacements are calculated as the displacement on the surface of a sphere of radius 50 mm. Along with the base framewise displacement, MRIQC reports the number of timepoints above FD threshold (fd_num), and the percent of FDs above the FD threshold w.r.t. the full timeseries (fd_perc). In both cases, the threshold is set at 0.20mm. [Power2012]: |
|
|
|
|
bold_fwhm_avg |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
bold_fwhm_x |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
bold_fwhm_y |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
bold_fwhm_z |
Float |
|
Conditional |
The FWHM of the spatial distribution of the image intensity values in units of voxels [Forman1995]. Lower values are better. Uses the gaussian width estimator filter implemented in AFNI's 3dFWHMx |
|
|
|
|
bold_gcor |
Float |
|
Conditional |
Global Correlation (gcor) calculates an optimized summary of time-series correlation as in [Saad2013] using AFNI's @compute_gcor |
|
|
|
|
bold_gsr_x |
Float |
|
Conditional |
Ghost to Signal Ratio (gsr(), labeled in the reports as gsr_x and gsr_y): along the two possible phase-encoding axes x, y |
|
|
|
|
bold_gsr_y |
Float |
|
Conditional |
Ghost to Signal Ratio (gsr(), labeled in the reports as gsr_x and gsr_y): along the two possible phase-encoding axes x, y |
|
|
|
|
bold_prov_set_fd_thresh |
Float |
|
Conditional |
Provisional setting of framewise displacement threshold |
|
|
|
|
bold_size_t |
Float |
|
Conditional |
number of time points |
|
|
|
|
bold_size_x |
Float |
|
Conditional |
extent in number of voxels |
|
|
|
|
bold_size_y |
Float |
|
Conditional |
extent in number of voxels |
|
|
|
|
bold_size_z |
Float |
|
Conditional |
extent in number of voxels |
|
|
|
|
bold_snr |
Float |
|
Conditional |
signal-to-noise ratio (SNR): calculated within the tissue mask. |
|
|
|
|
bold_spacing_tr |
Float |
|
Conditional |
Length of time between the begining of adjacent trs in s |
|
|
|
|
bold_spacing_x |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in x direction |
|
|
|
|
bold_spacing_y |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in y direction |
|
|
|
|
bold_spacing_z |
Float |
|
Conditional |
Distance in mm betwen centers of adjacent voxels in z direction |
|
|
|
|
bold_summary_bg_k |
Float |
|
Conditional |
background kurtosis |
|
|
|
|
bold_summary_bg_mad |
Float |
|
Conditional |
background median absolute deviation |
|
|
|
|
bold_summary_bg_mean |
Float |
|
Conditional |
background mean |
|
|
|
|
bold_summary_bg_median |
Float |
|
Conditional |
background median absolute deviation |
|
|
|
|
bold_summary_bg_n |
Float |
|
Conditional |
background count of voxels |
|
|
|
|
bold_summary_bg_p05 |
Float |
|
Conditional |
background 5th percentile |
|
|
|
|
bold_summary_bg_p95 |
Float |
|
Conditional |
background 95th percentile |
|
|
|
|
bold_summary_bg_stdv |
Float |
|
Conditional |
background standard deviation |
|
|
|
|
bold_summary_fg_k |
Float |
|
Conditional |
foreground kurtosis |
|
|
|
|
bold_summary_fg_mad |
Float |
|
Conditional |
foreground median absolute deviation |
|
|
|
|
bold_summary_fg_mean |
Float |
|
Conditional |
foreground mean |
|
|
|
|
bold_summary_fg_median |
Float |
|
Conditional |
foreground median absolute deviation |
|
|
|
|
bold_summary_fg_n |
Float |
|
Conditional |
foreground count of voxels |
|
|
|
|
bold_summary_fg_p05 |
Float |
|
Conditional |
foreground 5th percentile |
|
|
|
|
bold_summary_fg_p95 |
Float |
|
Conditional |
foreground 95th percentile |
|
|
|
|
bold_summary_fg_stdv |
Float |
|
Conditional |
foreground standard deviation |
|
|
|
|
bold_tsnr |
Float |
|
Conditional |
Temporal SNR (tSNR, tsnr) is a simplified interpretation of the tSNR definition [Kruger2001]. We report the median value of the tSNR map calculated like: where _S_t is the average BOLD signal (across time), and _t is the corresponding temporal standard-deviation map. |
|
|
|
|
accelnumreferencelines |
Float |
|
Recommended |
Acceleration number of reference lines |
|
|
|
|
accelerationfactorpe |
Float |
|
Recommended |
Acceleration factor in the phase encode direction |
|
|
|
|
acquisitionmatrix |
String |
50
|
Recommended |
Dimensions of the acquired frequency /phase data before reconstruction. Multi-valued: frequency rowsfrequency columnsphase rowsphase columns. ID=DICOM:0018_1310 |
|
|
|
|
cogatlasid |
String |
50
|
Recommended |
URL for task in the cognitive atlas (http://www.cognitiveatlas.org) |
|
|
|
|
cogpoid |
String |
50
|
Recommended |
URL for task in cogpowiki(http://wiki.cogpo.org) |
|
|
|
|
coilcombinationmethod |
Float |
|
Recommended |
Almost all fMRI studies using phased-array coils use root-sum-of-squares (rSOS) combination, but other methods exist. The image reconstruction is changed by the coil combination method (as for the matrix coil mode above), so anything non-standard should be reported |
|
|
|
|
conversionsoftware |
String |
50
|
Recommended |
Software used to convert dicom to nifti |
|
|
|
|
conversionsoftwareversion |
String |
50
|
Recommended |
Release version of the software used to convert dicom to nifti |
|
|
|
|
cardiactriggerdelaytimes |
Float |
|
Recommended |
Cardiac Trigger Delay Times |
|
|
|
|
deviceserialnumber |
String |
200
|
Recommended |
device serial number/ID |
|
|
|
|
echotime |
Float |
|
Recommended |
Time in ms between the middle of the excitation pulse and the peak of the echo produced (kx=0). In the case of segmented k-space, the TE(eff) is the time between the middle of the excitation pulse to the peak of the echo that is used to cover the center of k-space (i.e.,-kx=0, ky=0). ID=DICOM:0018_0081 |
|
|
|
|
echotrainlength |
Float |
|
Recommended |
Number of lines in k-space acquired per excitation of the same volume regardless of the type of echo or the number of frames derived from them. ID:DICOM:0018_0091 |
|
|
|
|
effectiveechospacing |
Float |
|
Recommended |
The "effective" sampling interval, specified in seconds, between lines in the phase-encoding direction, defined based on the size of the reconstructed image in the phase direction. It is frequently, but incorrectly, referred to as "dwell time" (see DwellTime parameter below for actual dwell time). It is required for unwarping distortions using field maps. Note that beyond just in-plane acceleration, a variety of other manipulations to the phase encoding need to be accounted for properly, including partial fourier, phase oversampling, phase resolution, phase field-of-view and interpolation.2 This parameter is REQUIRED if corresponding fieldmap data is present. |
|
|
|
|
flipangle |
Float |
|
Recommended |
Flip angle for the acquisition, specified in degrees. Corresponds to: DICOM Tag 0018, 1314 Flip Angle. |
|
|
|
|
hardcopydevicesoftwareversion |
String |
50
|
Recommended |
Manufacturers designation of the software of the device that created this Hardcopy Image (the printer). Corresponds to DICOM Tag 0018, 101A Hardcopy Device Software Version |
|
|
|
|
imagetype |
String |
50
|
Recommended |
Image Type |
|
|
|
|
imagingfrequency |
Float |
|
Recommended |
Imaging Frequency |
|
|
|
|
inplanephaseencodingdirection |
String |
50
|
Recommended |
The axes of the in-plane phase encoding with respect to the frame. ID:DICOM:0018_1312 |
|
|
|
|
institutionaddress |
String |
50
|
Recommended |
Mailing Address of the institution where the equipment is located.ID:DICOM:0008_0081 |
|
|
|
|
institutionname |
String |
50
|
Recommended |
The name of the institution in charge of the equipment that produced the composite instances. Corresponds to DICOM Tag 0008, 0080 InstitutionName. |
|
|
|
|
inst |
String |
50
|
Recommended |
Text of the instructions given to participants before the scan. This is especially important in context of resting state fMRI and distinguishing between eyes open and eyes closed paradigms. |
|
|
instructions |
|
inversiontime |
Float |
|
Recommended |
The inversion time (TI) for the acquisition, specified in seconds. Inversion time is the time after the middle of inverting RF pulse to middle of excitation pulse to detect the amount of longitudinal magnetization. Corresponds to DICOM Tag 0018, 0082 Inversion Time (please note that the DICOM term is in milliseconds not seconds). |
|
|
|
|
mracquisitiontype |
String |
50
|
Recommended |
Identification of data encoding scheme. ID:DICOM:0018_0023 |
|
|
|
|
magneticfieldstrength |
Float |
|
Recommended |
Nominal field strength of MR magnet in Tesla. ID:DICOM:0018_0087 |
|
|
|
|
manufacturer |
String |
100
|
Recommended |
Manufacturer |
|
|
|
|
manufacturersmodelname |
String |
50
|
Recommended |
Manufacturer's model name of the equipment that produced the composite instances. Corresponds to DICOM Tag 0008, 1090 Manufacturers Model Name |
|
|
|
|
matrixcoilmode |
Float |
|
Recommended |
A method for reducing the number of independent channels by combining in analog the signals from multiple coil elements. There are typically different default modes when using un-accelerated or accelerated (e.g. GRAPPA, SENSE) imaging |
|
|
|
|
multibandaccelerationfactor |
Float |
|
Recommended |
The multiband factor, for multiband acquisitions. |
|
|
|
|
numberofaverages |
Float |
|
Recommended |
Number of times a given pulse sequence is repeated before any parameter is changed. ID:DICOM:0018_0083 |
|
|
|
|
numberofphaseencodingsteps |
Float |
|
Recommended |
Total number of lines in k-space in the "y" direction collected during acquisition. ID:DICOM:0018_0089 |
|
|
|
|
num_vols_disc_scanner |
Float |
|
Recommended |
Number of volumes (“dummy scans”) discarded by the scanner (as opposed to those discarded by the user post hoc) before saving the imaging file. For example, a sequence that automatically discards the first 4 volumes before saving would have this field as 4. A sequence that doesn’t discard dummy scans would have this set to 0. |
|
|
|
|
num_vols_disc_user |
Float |
|
Recommended |
Number of volumes ("dummy scans") discarded by the user before including the file in the dataset. If possible, including all of the volumes is strongly recommended. Please note that the onsets recorded in the _event.tsv file should always refer to the beginning of the acquisition of the first volume in the corresponding imaging file - independent of the value of NumberOfVolumesDiscardedByUser field. |
|
|
|
|
numbershots |
Float |
|
Recommended |
The number of RF excitations need to reconstruct a slice or volume. Please mind that this is not the same as Echo Train Length which denotes the number of lines of k-space collected after an excitation. |
|
|
|
|
parallelacquisitiontechnique |
String |
50
|
Recommended |
The type of parallel imaging used (e.g. GRAPPA, SENSE). Corresponds to DICOM Tag 0018, 9078 Parallel Acquisition Technique. |
|
|
|
|
par_red_fact_inplane |
Float |
|
Recommended |
The parallel imaging (e.g, GRAPPA) factor. Use the denominator of the fraction of k-space encoded for each slice. For example, 2 means half of k-space is encoded. Corresponds to DICOM Tag 0018, 9069 Parallel Reduction Factor In-plane. |
|
|
|
|
partialfourier |
String |
50
|
Recommended |
The fraction of partial Fourier information collected. Corresponds to DICOM Tag 0018, 9081 Partial Fourier. |
|
|
|
|
patientposition |
String |
50
|
Recommended |
Description of imaging subject's position relative to the equipment. ID:DICOM:0018_5100 |
|
|
|
|
percentphasefieldofview |
Float |
|
Recommended |
Ratio of field of view dimension in phase direction to field of view dimension in frequency direction, expressed as a percent. ID:DICOM:0018_0094 |
|
|
|
|
percentsampling |
Float |
|
Recommended |
Fraction of acquisition matrix lines acquired, expressed as a percent. ID:DICOM:0018_0093 |
|
|
|
|
phaseencodingdirection |
String |
50
|
Recommended |
Possible values: i, j, k, i-, j-, k-. The letters i, j, k correspond to the first, second and third axis of the data in the NIFTI file. The polarity of the phase encoding is assumed to go from zero index to maximum index unless - sign is present (then the order is reversed - starting from the highest index instead of zero). PhaseEncodingDirection is defined as the direction along which phase is was modulated which may result in visible distortions. Note that this is not the same as the DICOM term InPlanePhaseEncodingDirection which can have ROW or COL values. This parameter is REQUIRED if corresponding fieldmap data is present or when using multiple runs with different phase encoding directions (which can be later used for field inhomogeneity correction). |
|
|
|
|
pixelbandwidth |
Float |
|
Recommended |
Reciprocal of the total sampling period, in hertz per pixel. ID:DICOM:0018_0095 |
|
|
|
|
protocolname |
String |
50
|
Recommended |
Description of the conditions under which the Series was performed. ID:DICOM:0018_1030 |
|
|
|
|
pulsesequencedetails |
String |
50
|
Recommended |
Information beyond pulse sequence type that identifies the specific pulse sequence used (i.e. "Standard Siemens Sequence distributed with the VB17 software," "Siemens WIP ### version #.##," or "Sequence written by X using a version compiled on MM/DD/YYYY"). |
|
|
|
|
pulsesequencetype |
String |
50
|
Recommended |
A general description of the pulse sequence used for the scan (i.e. MPRAGE, Gradient Echo EPI, Spin Echo EPI, Multiband gradient echo EPI). |
|
|
|
|
receivecoilname |
String |
50
|
Recommended |
Information describing the receiver coil. Corresponds to DICOM Tag 0018, 1250 Receive Coil Name, although not all vendors populate that DICOM Tag, in which case this field can be derived from an appropriate private DICOM field |
|
|
|
|
repetitiontime |
Float |
|
Recommended |
The time in seconds between the beginning of an acquisition of one volume and the beginning of acquisition of the volume following it (TR). Please note that this definition includes time between scans (when no data has been acquired) in case of sparse acquisition schemes. This value needs to be consistent with the pixdim[4] field (after accounting for units stored in xyzt_units field) in the NIfTI header. This field is mutually exclusive with VolumeTiming and is derived from DICOM Tag 0018, 0080 and converted to seconds. |
|
|
|
|
scanoptions |
String |
50
|
Recommended |
Parameters of ScanningSequence. Corresponds to DICOM Tag 0018, 0022 Scan Options. |
|
|
|
|
scanningsequence |
String |
50
|
Recommended |
Description of the type of data acquired. Corresponds to DICOM Tag 0018, 0020 Scanning Sequence. |
|
|
|
|
sequencename |
String |
50
|
Recommended |
Manufacturers designation of the sequence name. Corresponds to DICOM Tag 0018, 0024 Sequence Name. |
|
|
|
|
sequencevariant |
String |
50
|
Recommended |
Variant of the ScanningSequence. Corresponds to DICOM Tag 0018, 0021 Sequence Variant. |
|
|
|
|
sliceencodingdirection |
String |
50
|
Recommended |
Possible values: i, j, k, i-, j-, k- (the axis of the NIfTI data along which slices were acquired, and the direction in which SliceTiming is defined with respect to). i, j, k identifiers correspond to the first, second and third axis of the data in the NIfTI file. A - sign indicates that the contents of SliceTiming are defined in reverse order - that is, the first entry corresponds to the slice with the largest index, and the final entry corresponds to slice index zero. When present, the axis defined by SliceEncodingDirection needs to be consistent with the ‘slice_dim’ field in the NIfTI header. When absent, the entries in SliceTiming must be in the order of increasing slice index as defined by the NIfTI header. |
|
|
|
|
softwareversions |
String |
50
|
Recommended |
Manufacturers designation of software version of the equipment that produced the composite instances. Corresponds to DICOM Tag 0018, 1020 Software Versions |
|
|
|
|
taskdescription |
String |
50
|
Recommended |
Longer description of the task. |
|
|
|
|
taskname |
String |
50
|
Recommended |
Name of the task. No two tasks should have the same name. Task label (task-) included in the file name is derived from this field by removing all non alphanumeric ([a-zA-Z0-9]) characters. For example task name faces n-back will corresponds to task label facesnback. A RECOMMENDED convention is to name resting state task using labels beginning with rest. |
|
|
|
|
totalreadouttime |
Float |
|
Recommended |
This is actually the "effective" total readout time , defined as the readout duration, specified in seconds, that would have generated data with the given level of distortion. It is NOT the actual, physical duration of the readout train. If EffectiveEchoSpacing has been properly computed, it is just EffectiveEchoSpacing * (ReconMatrixPE - 1).3 . This parameter is REQUIRED if corresponding "field/distortion" maps acquired with opposing phase encoding directions are present (see 8.9.4). |
|
|
|
|
totalscantimesec |
Float |
|
Recommended |
Total time of the scan in seconds |
|
|
|
|
transmitcoilname |
String |
50
|
Recommended |
Name of transmit coil used. ID:DICOM:0018_1251 |
|
|
|
|
variableflipangleflag |
String |
50
|
Recommended |
Flip angle variation applied during image acquisition. ID:DICOM:0018_1315 |
|
|
|
|
acq_id |
String |
50
|
Recommended |
Acquisition ID |
|
|
|
|
run_id |
String |
50
|
Recommended |
Run ID |
|
|
|
|
session_id |
String |
20
|
Recommended |
session ID/screening ID |
|
|
|
|
contrast_bolus_ingredient |
String |
50
|
Recommended |
Active ingredient of agent. Values MUST be one of: IODINE, GADOLINIUM, CARBON DIOXIDE, BARIUM, XENON Corresponds to DICOM Tag 0018,1048. |
|
|
|
|
grad_set_type |
String |
50
|
Recommended |
It should be possible to infer the gradient coil from the scanner model. If not, e.g. because of a custom upgrade or use of a gradient insert set, then the specifications of the actual gradient coil should be reported independently |
|
|
|
|
mr_transmit_coil_seq |
String |
50
|
Recommended |
This is a relevant field if a non-standard transmit coil is used. Corresponds to DICOM Tag 0018, 9049 MR Transmit Coil Sequence |
|
|
|
|
partial_fourier_dir |
String |
50
|
Recommended |
The direction where only partial Fourier information was collected. Corresponds to DICOM Tag 0018, 9036 Partial Fourier Direction. |
|
|
|
|
image_modality |
String |
20
|
Recommended |
Image modality |
MRI; PET; CT; SPECT; ultrasound; FA; X-Ray; spectroscopy; microscopy; DEXA; fNIRS
|
Computed Radiography; Computed Tomography; External Camera Photography; FA; General Microscopy; MRI; Magnetic Resonance; Magnetic Resonance Spectroscopy; Nuclear Medicine; Single Photon Emission Computed Tomography; Ultrasound
|
|
|
quest_instruct |
String |
4,000
|
Recommended |
Questionnaire Instructions |
|
Questionnaire Instructions
|
|