Data Analysis framework in Brain Imaging STAT 992: Image Analysis March 23, 2004 Moo K. Chung
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Transcript of Data Analysis framework in Brain Imaging STAT 992: Image Analysis March 23, 2004 Moo K. Chung
Data Analysis framework in Brain Imaging
STAT 992: Image AnalysisMarch 23, 2004
Moo K. ChungDepartment of Statistics
Department of Biostatistics and Medical InformaticsW.M. Keck Brain Laboratory
University of Wisconsin-Madison
http://www.stat.wisc.edu/~mchung
Acknowledgement:Acknowledgement:
Presentation based on Will Penny, Jason LerchPresentation based on Will Penny, Jason Lerch
and Thomas Nichols’s PowerPoint slidesand Thomas Nichols’s PowerPoint slides
Some images based on Thomas Hoffman’s researchSome images based on Thomas Hoffman’s research
Brain Image AnalysisBrain Image AnalysisBrain Image AnalysisBrain Image Analysis
• Brain Image Analysis is a total science. Brain Image Analysis is a total science. • Before Images are transformed into a proper format for Before Images are transformed into a proper format for
data analysis, it will go through a bunch of image data analysis, it will go through a bunch of image processing procedures. processing procedures.
• If we can get extract proper data out of images, half of If we can get extract proper data out of images, half of the problems are already solved.the problems are already solved.
• Brain Image Analysis is a total science. Brain Image Analysis is a total science. • Before Images are transformed into a proper format for Before Images are transformed into a proper format for
data analysis, it will go through a bunch of image data analysis, it will go through a bunch of image processing procedures. processing procedures.
• If we can get extract proper data out of images, half of If we can get extract proper data out of images, half of the problems are already solved.the problems are already solved.
realignment &motion
correction
smoothing
normalisation
General Linear Modelmodel fittingstatistic image
corrected p-values
image data parameterestimatesdesign
matrix
anatomicalreference
kernel
StatisticalParametric Map
Random Field Theory
fMRI processingsteps
MRI processing stepsMRI processing steps MRI processing stepsMRI processing steps
Montreal Neurological Institute image processing pipeline
Non-uniformity correctionNon-uniformity correctionNon-uniformity correctionNon-uniformity correction
Native Corrected
nu_correct native.mnc corrected.mnc
Classification/segmentationClassification/segmentationClassification/segmentationClassification/segmentation
classify_clean final.mnc classified.mnc
Tissue classification/segmentationClustering algorithm based onmaximum likelihood mixture model (Hartigan, 1975)
Automatic skull stripping
3 different tissue types
Binary masks: 0 or 1
Gray matter White matter
Gaussian kernel smoothing
MaskingMaskingMaskingMasking
cortical_surface classified.mnc mask.obj 1.5surface_mask2 classified.mnc mask.obj masked.mnc
Image registration
Corpus callosum (CC) is thewhite matter brain substructurethat connects hemispheres.
We have 16 autistic subjects and 12 normal subjects. Quantify the CC shape difference between two groups?
Group 1 Group 2
How do we compare shapes?
Pixel by pixel comparison causes anatomical mismatching.
Solution: image registration. The aim of image registration is to find a smooth one-to-one mapping that matches homologous anatomies together.
Nonlinear image registration Estimate a continuous 3D map that matches two brain images.
He introduced deformable grid and deformation of homologous biological structures
Thompson, D. W. (1917) On growth and form. Cambridge University Press, Cambridge.
Nonlinear image registration based on Nonlinear image registration based on basis function expansionbasis function expansion
Nonlinear image registration based on Nonlinear image registration based on basis function expansionbasis function expansion
300 subjects average template
Warping into average blurred template reduce the probability of complete mismatch.
warping
Warped brain
Large scale automatic image analysis
Subject 1 Subject 2 Subject 3 Subject 498Subject 499
Subject 500
template
. . . .
500 MRIs will be warped into a template and anatomical differences can be compared at a common reference frame.
Estimating Nonlinear Image Registration
•Elastic deformation based
•Fluid dynamics based
•Intensity correlation based
•Bayesian approach
Image Registration
Similarity measure
Variational approach
PDE approach
x'= y'= z'= -1.212161e+02 -1.692117e+02 1.239336e+00+ 2.846339e+00 9.860215e-01 -4.670216e-03 x+ 4.541216e-01 3.344188e+00 -1.022118e-02 y+ 2.277959e+00 1.849708e+00 9.958860e-01 z+ -9.744798e-03 -4.951447e-03 1.253383e-05 x^2+ -4.519879e-03 -4.248561e-03 -2.655254e-05 x*y+ -9.122374e-04 -9.371881e-03 4.040382e-05 y^2+ -1.624103e-02 -3.371953e-03 2.356452e-06 x*z+ -3.519974e-03 -2.799626e-02 9.228041e-05 y*z+ -1.572948e-02 -1.688950e-03 5.386545e-05 z^2+ 2.495023e-05 4.120123e-06 3.604820e-08 x^3+ 3.232645e-06 1.739698e-05 1.044795e-07 x^2*y+ 1.074305e-05 4.357408e-06 -9.302004e-10 x*y^2+ -1.059526e-06 1.699618e-05 1.166377e-07 y^3+ 5.512034e-06 9.330769e-06 -2.219099e-08 x^2*z+ 1.275631e-05 -9.233413e-06 1.236940e-07 x*y*z+ -5.236010e-07 3.234824e-05 -6.819396e-07 y^2*z+ 9.506628e-05 1.214112e-05 -1.238024e-07 x*z^2+ 2.016546e-05 1.475354e-04 -1.693465e-08 y*z^2+ 3.377913e-06 -7.093638e-05 -2.757074e-07 z^3
3rd order polynomial warping
Curve registration by dynamic time warping algorithm-Thomas Hoffmann, Honors B.Sc. thesis.
Image smoothing
Kernel smoothingKernel smoothingKernel smoothingKernel smoothing
Anisotropic Gaussian kernel smoothing
It will smooth out signals along the eigenvectors. The amount ofsmoothing is proportional to the eigenvalues. So it will basicallysmooth out along the principal eigenvector.
Isotropic kernel Anisotropic kernel
Isotropic Gaussian kernel smoothing
Principal eigenvalues > 0.6
10mm FWHM 20mm FWHM
Anisotropic Smoothing= Edge Enhancement
Before
After diffusion smoothing
initial mean curvature diffusion smoothing estimate
Inner surface = gray/white matter interface
Flattened map showing smoothing
initial mean curvature 20 iterations 100 iterations
0.00
0.01
WHY WE SMOOTH? See next slide
Smooth T random fields
6.5
-6.5
-2.0
2.0
Autocorrelation:Autocorrelation:PrecoloringPrecoloring
Autocorrelation:Autocorrelation:PrecoloringPrecoloring
• Temporally blur, smooth your dataTemporally blur, smooth your data– This induces This induces more more dependence!dependence!
– But we exactly know the form of the dependence inducedBut we exactly know the form of the dependence induced
– Assume that intrinsic autocorrelation is negligible relative to Assume that intrinsic autocorrelation is negligible relative to smoothingsmoothing
• Then we know autocorrelation exactlyThen we know autocorrelation exactly• Correct GLM inferences based on “known” Correct GLM inferences based on “known”
autocorrelationautocorrelation
• Temporally blur, smooth your dataTemporally blur, smooth your data– This induces This induces more more dependence!dependence!
– But we exactly know the form of the dependence inducedBut we exactly know the form of the dependence induced
– Assume that intrinsic autocorrelation is negligible relative to Assume that intrinsic autocorrelation is negligible relative to smoothingsmoothing
• Then we know autocorrelation exactlyThen we know autocorrelation exactly• Correct GLM inferences based on “known” Correct GLM inferences based on “known”
autocorrelationautocorrelation
[Friston, et al., “To smooth or not to smooth…” NI 12:196-208 2000]
Autocorrelation:Autocorrelation:PrewhiteningPrewhitening
Autocorrelation:Autocorrelation:PrewhiteningPrewhitening
• Statistically optimal solutionStatistically optimal solution• If know true autocorrelation exactly, canIf know true autocorrelation exactly, can
undo the dependenceundo the dependence– DeDe-correlate your data, your model-correlate your data, your model
– Then proceed as with independent dataThen proceed as with independent data
• Problem is obtaining accurate estimates of Problem is obtaining accurate estimates of autocorrelationautocorrelation– Some sort of regularization is requiredSome sort of regularization is required
• Spatial smoothing of some sortSpatial smoothing of some sort
• Statistically optimal solutionStatistically optimal solution• If know true autocorrelation exactly, canIf know true autocorrelation exactly, can
undo the dependenceundo the dependence– DeDe-correlate your data, your model-correlate your data, your model
– Then proceed as with independent dataThen proceed as with independent data
• Problem is obtaining accurate estimates of Problem is obtaining accurate estimates of autocorrelationautocorrelation– Some sort of regularization is requiredSome sort of regularization is required
• Spatial smoothing of some sortSpatial smoothing of some sort
fMRI example
Basic fMRI ExampleBasic fMRI ExampleBasic fMRI ExampleBasic fMRI Example
• Time series at Time series at each voxel.each voxel.
• Time series at Time series at each voxel.each voxel.
one stimulus
two stimuli
fMRI time series modeling
A Linear ModelA Linear ModelA Linear ModelA Linear Model
Intensity
Tim
e = 1 2+ + erro
r
x1 x2
• ““Linear” in Linear” in parameters parameters 11
&& 22
• ““Linear” in Linear” in parameters parameters 11
&& 22
… … in matrix form.in matrix form.… … in matrix form.in matrix form.
XY
=
+YY X
N
1
N N
1 1p
p
N: Number of scans, p: Number of regressors
left right left right
subject 20
subject 41
left rightleftright
OSL fitting of subject 20 left amygdala
OSL fitting of subject 20 right amygdala
Generalized Least Squares (GLS) Estimation
HRF snake attacking snake crawling fish swimming
AFNI resultsubject 20right amygdala
HRF reconvolved with the initial stimuli
Black: HR based on OSLRed: HR based on GSL
In this particular example, GSL can get the dip OSL can not get.
Whitening by GSL correlation
Multiple Testing ProblemMultiple Testing ProblemMultiple Testing ProblemMultiple Testing Problem
• Inference on statistic imagesInference on statistic images– Fit GLM at each voxelFit GLM at each voxel
– Create statistic images of effectCreate statistic images of effect
• Which of 100,000 voxels are significant?Which of 100,000 voxels are significant? =0.05 =0.05 5,000 false positives! 5,000 false positives!
• Inference on statistic imagesInference on statistic images– Fit GLM at each voxelFit GLM at each voxel
– Create statistic images of effectCreate statistic images of effect
• Which of 100,000 voxels are significant?Which of 100,000 voxels are significant? =0.05 =0.05 5,000 false positives! 5,000 false positives!
t > 0.5 t > 1.5 t > 2.5 t > 3.5 t > 4.5 t > 5.5 t > 6.5
MCP Solutions:MCP Solutions:Measuring False PositivesMeasuring False Positives
MCP Solutions:MCP Solutions:Measuring False PositivesMeasuring False Positives
• Familywise Error Rate (FWER)Familywise Error Rate (FWER)– Familywise ErrorFamilywise Error
• Existence of one or more false positivesExistence of one or more false positives
– FWER is probability of familywise error FWER is probability of familywise error corrected corrected PP-value-value
• False Discovery Rate (FDR)False Discovery Rate (FDR)– R voxels declared active, V falsely soR voxels declared active, V falsely so
• Observed false discovery rate: V/RObserved false discovery rate: V/R
– FDR = E(V/R) FDR = E(V/R) Q-valueQ-value
– This is a relative measure.This is a relative measure.
• Familywise Error Rate (FWER)Familywise Error Rate (FWER)– Familywise ErrorFamilywise Error
• Existence of one or more false positivesExistence of one or more false positives
– FWER is probability of familywise error FWER is probability of familywise error corrected corrected PP-value-value
• False Discovery Rate (FDR)False Discovery Rate (FDR)– R voxels declared active, V falsely soR voxels declared active, V falsely so
• Observed false discovery rate: V/RObserved false discovery rate: V/R
– FDR = E(V/R) FDR = E(V/R) Q-valueQ-value
– This is a relative measure.This is a relative measure.
FWER MCP Solutions:FWER MCP Solutions:Random Field TheoryRandom Field Theory
FWER MCP Solutions:FWER MCP Solutions:Random Field TheoryRandom Field Theory
• Euler Characteristic Euler Characteristic uu
– Topological MeasureTopological Measure• #blobs - #holes#blobs - #holes
– At high thresholds,At high thresholds,just counts blobsjust counts blobs
– FWERFWER = P(Max voxel = P(Max voxel uu | | HHoo))
= P(One or more blobs | = P(One or more blobs | HHoo))
P( P(uu 1 | 1 | HHoo))
E( E(uu | | HHoo))
• Euler Characteristic Euler Characteristic uu
– Topological MeasureTopological Measure• #blobs - #holes#blobs - #holes
– At high thresholds,At high thresholds,just counts blobsjust counts blobs
– FWERFWER = P(Max voxel = P(Max voxel uu | | HHoo))
= P(One or more blobs | = P(One or more blobs | HHoo))
P( P(uu 1 | 1 | HHoo))
E( E(uu | | HHoo))
Random Field
Suprathreshold Sets
Threshold
Example – 2D Gaussian imagesExample – 2D Gaussian imagesExample – 2D Gaussian imagesExample – 2D Gaussian images
αα = R (4 ln 2) (2 = R (4 ln 2) (2ππ) ) -3/2-3/2 u exp (-u u exp (-u22/2)/2)
For R=100 and α=0.05RFT gives u=3.8
Using R=100 in a Bonferroni correction gives u=3.3
Friston et al. (1991) J. Cer. Bl. Fl. M.
DevelopmentsDevelopmentsDevelopmentsDevelopments
Friston et al. (1991) J. Cer. Bl. Fl. M. (Not EC Method)
2D Gaussian fields
3D Gaussian fields
3D t-fieldsWorsley et al. (1992) J. Cer. Bl. Fl. M.
Worsley et al. (1993) Quant. Brain. Func.
• General form for expected Euler characteristicGeneral form for expected Euler characteristic• 22, , FF, & , & tt fields fields •• restricted search regions restricted search regions
αα = = R Rd d (()) d d ((uu))
• General form for expected Euler characteristicGeneral form for expected Euler characteristic• 22, , FF, & , & tt fields fields •• restricted search regions restricted search regions
αα = = R Rd d (()) d d ((uu))
Unified TheoryUnified TheoryUnified TheoryUnified Theory
Rd (): RESEL count
R0() = () Euler characteristic of
R1() = resel diameter
R2() = resel surface area
R3() = resel volume
d (u): d-dimensional EC density –
E.g. Gaussian RF:
0(u) = 1- (u)
1(u) = (4 ln2)1/2 exp(-u2/2) / (2)
2(u) = (4 ln2) exp(-u2/2) / (2)3/2
3(u) = (4 ln2)3/2 (u2 -1) exp(-u2/2) / (2)2
4(u) = (4 ln2)2 (u3 -3u) exp(-u2/2) / (2)5/2
Au
Worsley et al. (1996), HBM
Expected EC for a stationary Gaussian field
EC densityMinkowski functionals
Adler (1981) , Worsley (1996)
RFT AssumptionsRFT AssumptionsRFT AssumptionsRFT Assumptions
• Model fit & assumptionsModel fit & assumptions– valid distributional resultsvalid distributional results
• Multivariate normalityMultivariate normality– of of componentcomponent images images
• Covariance function of Covariance function of componentcomponent images must be images must be
- Stationary- Stationary (pre SPM99)(pre SPM99)
- - Can be nonstationaryCan be nonstationary
(SPM99 onwards)(SPM99 onwards)
- Twice differentiable- Twice differentiable
• Model fit & assumptionsModel fit & assumptions– valid distributional resultsvalid distributional results
• Multivariate normalityMultivariate normality– of of componentcomponent images images
• Covariance function of Covariance function of componentcomponent images must be images must be
- Stationary- Stationary (pre SPM99)(pre SPM99)
- - Can be nonstationaryCan be nonstationary
(SPM99 onwards)(SPM99 onwards)
- Twice differentiable- Twice differentiable
• SmoothnessSmoothness– smoothness » voxel sizesmoothness » voxel size
• lattice approximationlattice approximation
• smoothness estimationsmoothness estimation
– practicallypractically• FWHMFWHM 3 3 VoxDimVoxDim
– otherwiseotherwise• conservativeconservative
• SmoothnessSmoothness– smoothness » voxel sizesmoothness » voxel size
• lattice approximationlattice approximation
• smoothness estimationsmoothness estimation
– practicallypractically• FWHMFWHM 3 3 VoxDimVoxDim
– otherwiseotherwise• conservativeconservative
Random Field Theory Random Field Theory Random Field Theory Random Field Theory
• Closed form results for E(Closed form results for E(uu))– Z, tZ, t, , FF, Chi-Squared Continuous RFs, Chi-Squared Continuous RFs
• Results depend only on RESELsResults depend only on RESELs– RESolution ELementsRESolution ELements
– A volume element of size A volume element of size FWHMFWHMx x FWHMFWHMy y FWHMFWHMzz
– RESEL countRESEL count• Voxel-size-independent measure of volumeVoxel-size-independent measure of volume
• Inferences Inferences dodo notnot depend on stationarity depend on stationarity– Smoothness can varySmoothness can vary
(It is cluster size results that require stationarity)(It is cluster size results that require stationarity)
• Closed form results for E(Closed form results for E(uu))– Z, tZ, t, , FF, Chi-Squared Continuous RFs, Chi-Squared Continuous RFs
• Results depend only on RESELsResults depend only on RESELs– RESolution ELementsRESolution ELements
– A volume element of size A volume element of size FWHMFWHMx x FWHMFWHMy y FWHMFWHMzz
– RESEL countRESEL count• Voxel-size-independent measure of volumeVoxel-size-independent measure of volume
• Inferences Inferences dodo notnot depend on stationarity depend on stationarity– Smoothness can varySmoothness can vary
(It is cluster size results that require stationarity)(It is cluster size results that require stationarity)
Random Field Theory LimitationsRandom Field Theory LimitationsRandom Field Theory LimitationsRandom Field Theory Limitations
• Sufficient smoothnessSufficient smoothness– FWHM smoothness 3-4 times voxel sizeFWHM smoothness 3-4 times voxel size
• Smoothness estimationSmoothness estimation– Estimate is biased when images not so smooth Estimate is biased when images not so smooth
– Estimate is an estimateEstimate is an estimate—sd’s on corr. —sd’s on corr. p-valuesp-values
• Multivariate normalityMultivariate normality– Virtually impossible to checkVirtually impossible to check
• Several layers of approximationsSeveral layers of approximations– E.g., E.g., tt field results conservative for low df field results conservative for low df
• Sufficient smoothnessSufficient smoothness– FWHM smoothness 3-4 times voxel sizeFWHM smoothness 3-4 times voxel size
• Smoothness estimationSmoothness estimation– Estimate is biased when images not so smooth Estimate is biased when images not so smooth
– Estimate is an estimateEstimate is an estimate—sd’s on corr. —sd’s on corr. p-valuesp-values
• Multivariate normalityMultivariate normality– Virtually impossible to checkVirtually impossible to check
• Several layers of approximationsSeveral layers of approximations– E.g., E.g., tt field results conservative for low df field results conservative for low df
Lattice ImageData
Continuous Random Field
ze
ze
ye
ze
xe
ze
ye
ye
ye
xe
ze
xe
ye
xe
xe
var,cov,cov
,covvar,cov
,cov,covvar
Smoothness EstimationSmoothness EstimationSmoothness EstimationSmoothness Estimation
• Roughness Roughness ||||
• Point Response Function Point Response Function PRFPRF
• Roughness Roughness ||||
• Point Response Function Point Response Function PRFPRF
• Gaussian Gaussian PRFPRF
ffxx 0 0
ffyy00 0 ffzz
|||| = (4ln(2)) = (4ln(2))3/23/2 / (f / (fxx f fyy f fzz))
• RESEL COUNTRESEL COUNT
RR33(() = ) = (()) / (f / (fxx f fyy f fzz))
αα = R = R33(() (4ln(2))) (4ln(2))3/23/2 ( (u u 2 2 -1) exp(--1) exp(-u u 22/2) / (2/2) / (2))22
• Gaussian Gaussian PRFPRF
ffxx 0 0
ffyy00 0 ffzz
|||| = (4ln(2)) = (4ln(2))3/23/2 / (f / (fxx f fyy f fzz))
• RESEL COUNTRESEL COUNT
RR33(() = ) = (()) / (f / (fxx f fyy f fzz))
αα = R = R33(() (4ln(2))) (4ln(2))3/23/2 ( (u u 2 2 -1) exp(--1) exp(-u u 22/2) / (2/2) / (2))22
Approximate the peak of the Covariance function with a Gaussian
Cluster and Set-level InferenceCluster and Set-level InferenceCluster and Set-level InferenceCluster and Set-level Inference
• We can increase sensitivity by trading off anatomical specificityWe can increase sensitivity by trading off anatomical specificity
• Given a voxel level threshold u, we can computeGiven a voxel level threshold u, we can compute the likelihood (under the null hypothesis) of getting n or more connected the likelihood (under the null hypothesis) of getting n or more connected
components in the excursion set ie. a cluster containing at least n voxelscomponents in the excursion set ie. a cluster containing at least n voxels
CLUSTER-LEVEL INFERENCECLUSTER-LEVEL INFERENCE
• Similarly, we can compute the likelihood of getting cSimilarly, we can compute the likelihood of getting c clusters each having at least n voxelsclusters each having at least n voxels
• We can increase sensitivity by trading off anatomical specificityWe can increase sensitivity by trading off anatomical specificity
• Given a voxel level threshold u, we can computeGiven a voxel level threshold u, we can compute the likelihood (under the null hypothesis) of getting n or more connected the likelihood (under the null hypothesis) of getting n or more connected
components in the excursion set ie. a cluster containing at least n voxelscomponents in the excursion set ie. a cluster containing at least n voxels
CLUSTER-LEVEL INFERENCECLUSTER-LEVEL INFERENCE
• Similarly, we can compute the likelihood of getting cSimilarly, we can compute the likelihood of getting c clusters each having at least n voxelsclusters each having at least n voxels
Suprathreshold cluster testsSuprathreshold cluster testsSuprathreshold cluster testsSuprathreshold cluster tests
• Primary threshold Primary threshold uu– examine connected components examine connected components
of excursion setof excursion set
– Suprathreshold clustersSuprathreshold clusters
– Reject Reject HHWW for clusters of voxels for clusters of voxels WW of size of size SS > > ss
• Localisation Localisation (Strong control)(Strong control)
– at cluster levelat cluster level
– increased powerincreased power– esp. high resolutions esp. high resolutions ((ff MRI MRI))
• Thresholds, Thresholds, pp –values –values– Pr(Pr(SS
maxmax > > ss H H ) )
Nosko, Friston, (Worsley)Nosko, Friston, (Worsley)
– Poisson occurrence Poisson occurrence (Adler)(Adler)
– Assumme form for Pr(Assumme form for Pr(SS==ss||SS>0)>0)
• Primary threshold Primary threshold uu– examine connected components examine connected components
of excursion setof excursion set
– Suprathreshold clustersSuprathreshold clusters
– Reject Reject HHWW for clusters of voxels for clusters of voxels WW of size of size SS > > ss
• Localisation Localisation (Strong control)(Strong control)
– at cluster levelat cluster level
– increased powerincreased power– esp. high resolutions esp. high resolutions ((ff MRI MRI))
• Thresholds, Thresholds, pp –values –values– Pr(Pr(SS
maxmax > > ss H H ) )
Nosko, Friston, (Worsley)Nosko, Friston, (Worsley)
– Poisson occurrence Poisson occurrence (Adler)(Adler)
– Assumme form for Pr(Assumme form for Pr(SS==ss||SS>0)>0)
5mm FWHM
10mm FWHM
15mm FWHM
(2mm2 pixels)
Worsley KJ, Marrett S, Neelin P, Evans AC (1992)
“A three-dimensional statistical analysis for CBF activation studies in human brain”Journal of Cerebral Blood Flow and Metabolism 12:900-918
Worsley KJ, Marrett S, Neelin P, Vandal AC, Friston KJ, Evans AC (1995)
“A unified statistical approach for determining significant signals in images of cerebral activation”Human Brain Mapping 4:58-73
Friston KJ, Worsley KJ, Frackowiak RSJ, Mazziotta JC, Evans AC (1994)“Assessing the Significance of Focal Activations Using their Spatial Extent”Human Brain Mapping 1:214-220
Cao J (1999)“The size of the connected components of excursion sets of 2, t and F fields”Advances in Applied Probability (in press)
Worsley KJ, Marrett S, Neelin P, Evans AC (1995)“Searching scale space for activation in PET images”Human Brain Mapping 4:74-90
Worsley KJ, Poline J-B, Vandal AC, Friston KJ (1995)“Tests for distributed, non-focal brain activations”NeuroImage 2:183-194
Friston KJ, Holmes AP, Poline J-B, Price CJ, Frith CD (1996)“Detecting Activations in PET and fMRI: Levels of Inference and Power”Neuroimage 4:223-235
Worsley KJ, Marrett S, Neelin P, Evans AC (1992)
“A three-dimensional statistical analysis for CBF activation studies in human brain”Journal of Cerebral Blood Flow and Metabolism 12:900-918
Worsley KJ, Marrett S, Neelin P, Vandal AC, Friston KJ, Evans AC (1995)
“A unified statistical approach for determining significant signals in images of cerebral activation”Human Brain Mapping 4:58-73
Friston KJ, Worsley KJ, Frackowiak RSJ, Mazziotta JC, Evans AC (1994)“Assessing the Significance of Focal Activations Using their Spatial Extent”Human Brain Mapping 1:214-220
Cao J (1999)“The size of the connected components of excursion sets of 2, t and F fields”Advances in Applied Probability (in press)
Worsley KJ, Marrett S, Neelin P, Evans AC (1995)“Searching scale space for activation in PET images”Human Brain Mapping 4:74-90
Worsley KJ, Poline J-B, Vandal AC, Friston KJ (1995)“Tests for distributed, non-focal brain activations”NeuroImage 2:183-194
Friston KJ, Holmes AP, Poline J-B, Price CJ, Frith CD (1996)“Detecting Activations in PET and fMRI: Levels of Inference and Power”Neuroimage 4:223-235
Multiple Comparisons,Multiple Comparisons,& Random Field Theory& Random Field TheoryMultiple Comparisons,Multiple Comparisons,
& Random Field Theory& Random Field Theory
Ch5 Ch4
Controlling FWER: Permutation TestControlling FWER: Permutation TestControlling FWER: Permutation TestControlling FWER: Permutation Test
• Parametric methodsParametric methods– Assume distribution ofAssume distribution of
maxmax statistic under null statistic under nullhypothesishypothesis
• Nonparametric methodsNonparametric methods– Use Use datadata to find to find
distribution of distribution of maxmax statistic statisticunder null hypothesisunder null hypothesis
– Any max statistic!Any max statistic!
– Due to FisherDue to Fisher
• Parametric methodsParametric methods– Assume distribution ofAssume distribution of
maxmax statistic under null statistic under nullhypothesishypothesis
• Nonparametric methodsNonparametric methods– Use Use datadata to find to find
distribution of distribution of maxmax statistic statisticunder null hypothesisunder null hypothesis
– Any max statistic!Any max statistic!
– Due to FisherDue to Fisher
5%
Parametric Null Max Distribution
5%
Nonparametric Null Max Distribution
Measuring False PositivesMeasuring False PositivesFWER vs FDRFWER vs FDR
Measuring False PositivesMeasuring False PositivesFWER vs FDRFWER vs FDR
Signal
Signal+Noise
Noise
FWE
6.7% 10.4% 14.9% 9.3% 16.2% 13.8% 14.0% 10.5% 12.2% 8.7%
Control of Familywise Error Rate at 10%
11.3% 11.3% 12.5% 10.8% 11.5% 10.0% 10.7% 11.2% 10.2% 9.5%
Control of Per Comparison Rate at 10%
Percentage of Null Pixels that are False Positives
Control of False Discovery Rate at 10%
Occurrence of Familywise Error
Percentage of Activated Pixels that are False Positives
Controlling FDR:Controlling FDR:Benjamini & Hochberg Benjamini & Hochberg
Controlling FDR:Controlling FDR:Benjamini & Hochberg Benjamini & Hochberg
• Select desired limit Select desired limit qq on E(FDR) on E(FDR)• Order p-values, Order p-values, pp(1)(1) pp(2)(2) ... ... pp((VV))
• Let Let rr be largest be largest ii such that such that
• Reject all hypotheses Reject all hypotheses corresponding tocorresponding to pp(1)(1), ... , , ... , pp((rr))..
• Select desired limit Select desired limit qq on E(FDR) on E(FDR)• Order p-values, Order p-values, pp(1)(1) pp(2)(2) ... ... pp((VV))
• Let Let rr be largest be largest ii such that such that
• Reject all hypotheses Reject all hypotheses corresponding tocorresponding to pp(1)(1), ... , , ... , pp((rr))..
p(i) i/V q
p(i)
i/V
i/V qp-
valu
e0 1
01
Benjamini & Hochberg:Benjamini & Hochberg:Varying Signal ExtentVarying Signal Extent
Benjamini & Hochberg:Benjamini & Hochberg:Varying Signal ExtentVarying Signal Extent
Signal Intensity 3.0 Signal Extent 25.0 Noise Smoothness 3.0
p = 0.019274 z = 2.07
7
FDR Software for SPMFDR Software for SPMFDR Software for SPMFDR Software for SPM
http://www.sph.umich.edu/~nichols/FDR
ReferencesReferencesReferencesReferences
• KM Petersson, TE Nichols, J-B Poline, and AP Holmes.KM Petersson, TE Nichols, J-B Poline, and AP Holmes.Statistical limitations in functional neuroimaging I. Non-inferential methods Statistical limitations in functional neuroimaging I. Non-inferential methods and statistical models. and statistical models. Statistical limitations in functional neuroimaging II. Signal detection and Statistical limitations in functional neuroimaging II. Signal detection and statistical inference. statistical inference. Philosophical Transactions of the Royal Society: Biological SciencesPhilosophical Transactions of the Royal Society: Biological Sciences , , 354:1239-1281, 1999.354:1239-1281, 1999.
• CR Genovese, N Lazar and TE Nichols.CR Genovese, N Lazar and TE Nichols.Thresholding of Statistical Maps in Functional Neuroimaging Using the Thresholding of Statistical Maps in Functional Neuroimaging Using the False Discovery Rate. False Discovery Rate. NeuroImageNeuroImage, 15:870-878, 2002., 15:870-878, 2002.
• KM Petersson, TE Nichols, J-B Poline, and AP Holmes.KM Petersson, TE Nichols, J-B Poline, and AP Holmes.Statistical limitations in functional neuroimaging I. Non-inferential methods Statistical limitations in functional neuroimaging I. Non-inferential methods and statistical models. and statistical models. Statistical limitations in functional neuroimaging II. Signal detection and Statistical limitations in functional neuroimaging II. Signal detection and statistical inference. statistical inference. Philosophical Transactions of the Royal Society: Biological SciencesPhilosophical Transactions of the Royal Society: Biological Sciences , , 354:1239-1281, 1999.354:1239-1281, 1999.
• CR Genovese, N Lazar and TE Nichols.CR Genovese, N Lazar and TE Nichols.Thresholding of Statistical Maps in Functional Neuroimaging Using the Thresholding of Statistical Maps in Functional Neuroimaging Using the False Discovery Rate. False Discovery Rate. NeuroImageNeuroImage, 15:870-878, 2002., 15:870-878, 2002.
http://www.sph.umich.edu/~nichols
Application: Surface data
Corrected P-value
Morphological descriptor
2D Euler characteristic density of t random field
Cortical surface area
Red: Tissue growthBlue: Tissue lossYellow: Structure displacement
Rejection regions.
Yellow = Hotelling’s T^2 field
Cortical thickness change t-map
Curvature change t-map