Granger Causality Analysis of fMRI Data:...
Transcript of Granger Causality Analysis of fMRI Data:...
Granger Causality Analysis of fMRI Data:
Techniques, Caveats and Applications
Xiaoping Hu
Wallace H. Coulter Department of Biomedical Engineering
Emory University and Georgia Tech
Atlanta, GA, USA
fMRI Deriving Connectivity
• Functional connectivity
– “Temporal correlations between remote
neurophysiological events” neurophysiological events”
• Effective connectivity
– “Influence one neuronal system exerts over
another”
Friston et al
Granger Causality Analysis• Granger causality is based
on the concept of temporal precedence information
• If including past values of Y improves the prediction of future values of X, then Y is said to have a causal
Time n
T
I
M
Y is said to have a causal influence on X
• Originally invented by Granger for stock market prediction and awarded Nobel prize in economics in 2003
Time series X Time series Y
Time n-k
M
E
Multivariate Granger Causality and Directed
Transfer Function
• Let X(t)=(x1(t),x2(t),... xk(t)) be the data vector wherein xk is the time series, a multivariate autoregressive model with model parameters A(n) of order p is given by
• Transforming the equation to the frequency domain, one has the transfer matrix, H(f)(=A-
1(f)), or the non-normalized directed transfer
∑=
+−=
p
n
tntnt1
)()()()( EEEEXXXXAAAAXXXX
)()()()()( 1 fEfHfEfAfX ==−
1(f)), or the non-normalized directed transfer function (DTF).
• H(f) is multiplied by partial coherence to emphasize direct connections and summed over all frequencies to obtain direct DTF, where the partial coherence is given by
and Mij(f) is the minor of the cross-spectrum matrix between the time series.
∑=
f
ijijij ffhdDTF )()( η
)()(
)()(
2
fMfM
fMf
jjii
ij
ij =η
Statistical Testing using Surrogate Data
Original DataRetain Power
SpectrumRandomize Phase
Surrogate DataCalculate dDTFon Surrogates
2500 Times
EmpiricalNull
Distribution
Original time series
Phase randomized
0 10 20 30 40
NULL SURROGATE DISTRIBUTION
Significant !
Deshpande et al, HBM, 30: 1361-1373, 2009.
5s
12s
fMRI Impulse-Response Function
τ
2s
Courtesy of Y. Yang, NIDA
A Poor Man’s Application of
Granger Analysis: Investigation
of Slow Causal Influencesof Slow Causal Influences
Motor Fatigue Experiment
• Subjects repeated a hand contraction task guided
by visual feedback (50% maximum force). The
duration of each contraction was 3.5 s, followed
by a 6.5 s rest. by a 6.5 s rest.
• The fatigue task lasted 20 minutes, with a total of
120 contractions performed by each subject.
• fMRI images acquired at every 2 seconds.
Deshpande et al., HBM (2009)
ROIs and Integrated Time Courses
■
▲
*
♥
◄
■ SMA
▲ M1
* S1
♥ P
◄ PM
0 100 200 300 400 500 600-15
-10
-5
0
5
10
15
Time (TRs)0 20 40 60 80 100 120
10
15
20
25
30
35
40
Time
Deshpande et al., HBM (2009)
Effective Connectivity during Fatigue
SMA
M1
PM C
P
S1
SMA
M1
PM C
P
S1
SMA
M1
PM C
P
S1
First Window Middle Window Last Window
Deshpande et al., HBM (2009)
• In window 1, the strong output from S1 indicates fine tuning of motor activity by sensory feedback.
• In window 2, cerebellum’s role increases indicating more motor control; the shift from window 1 to window 2 likely reflects learning.
• In window 3, the connectivity pattern is similar to that of window 2 but there is a general reduction in connectivity due to fatigue.
Network from raw time series
SMA
M1
P
S1
SMA
M1
P
S1
SMA
M1
P
S1
window 1 window 2 window 3
PM C PM C PM C
• Networks derived from the raw data exhibit more
causal paths that are less significant, with no
apparent driving node(s) and little change with
time.
Deshpande et al., HBM (2009)
Effect of Slow Sampling and
Hemodynamic Response on Fast
Causal InfluencesCausal Influences
BOLD Signal and LFP
Logothetis, Nature, 2001
Simulations
• LFP signal X sampled at 1ms interval. Y obtained by shifting it by d ms
• Hemodynamic impulse response modeled by modeled by Gamma functions
A = time to peak
W = full width at half maximum
K = scaling factor
• TR=0.5, 1, 1.5 and 2 seconds
Desphande & Hu, NeuroImage, 52: 884-96, 2010.
fMRI simulation from LFP
Original LFP time series X(red)→Y(blue): 0.3Y(blue)→X(red): 0.0024
LFP convolved with HRF
X(red)→Y(blue): 1.8Y(blue)→X(red): 0.7
X(red)→Y(blue): 80Y(blue)→X(red): 21
HRF Difference (0.5 s) Opposite the Neuronal Delay
X(red)→Y(blue): 44Y(blue)→X(red): 12
No Noise
Noise (SNR=50) added to simulated
fMRI
X(red)→Y(blue): 29±5Y(blue)→X(red): 15±4
HRF Difference (0.5 s) Opposite the Neuronal Delay
preserving HRF shape
HRFs shifted in time; shape preserving (results below)
HRFs with different rise time; shape altering (results above)
Physiologically feasible model
Aguirre et al, NeuroImage 1998
preserving (results below) shape altering (results above)
No Noise
X(red)→Y(blue): 0.85Y(blue)→X(red): 1.73
SNR=50
X(red)→Y(blue): 0.9 ± 0.3Y(blue)→X(red): 1.6 ± 0.2
Reverse directioninferred
Desphande, Sathian & Hu. Effect of Hemodynamic Variability on
Granger Causality Analysis of fMRI. NeuroImage 52: 884-96, 2010.
•In the absence of HRF variability, even tens of milliseconds of
neuronal delay can be inferred from GC analysis of fMRI.
•In the presence of HRF delays which oppose neuronal delays, the
minimum detectable neuronal delay may be hundreds of milliseconds.
•In the more realistic scenario of unknown neuronal and hemodynamic
delays within their normal physiological range, the accuracy of
detecting the correct multivariate network from fMRI is well above
chance and up to 90% with faster sampling.
•Under all conditions, faster sampling and low measurement noise
improve the sensitivity of GC analysis of fMRI data.
• Aim: to investigate the neural circuitry underlying tactile spatial acuity at the human finger pad
• Spatial task: linear, 3-dot arrays, applied to the immobilized right index finger pad using a computer-
Tactile Spatial Acuity Experiment
finger pad using a computer-controlled, MRI-compatible, pneumatic stimulator
• Control task: Temporal offset stimulus instead of spatial offset
Stilla et al., J Neurosci 07
• Activity specific for
spatial processing
revealed activity in a
distributed fronto-
parietal cortical
network
• Levels of activity in
right posterior right posterior
intraparietal sulcus
(pIPS) significantly
predicted individual
acuity thresholds
Stilla et al., J Neurosci 07
135• Multivariate Granger
causality
relationships among
selected ROIs
• Top: Better
2
66 • Top: Better
• Bottom: Poorer
Stilla et al., J Neurosci, 27, 11091, 2007
What determines acuity ?
• Regression shows that in the better group, the paths predicting acuity converged from the left postcentral sulcus and right frontal eye field onto converged from the left postcentral sulcus and right frontal eye field onto the right pIPS.
• These connections were selective for the spatial task
• Their weights predicted the level of right pIPS activity
• Conclusion: The optimal strategy for fine tactile spatial discrimination involves interaction in the pIPS of a top-down control signal, possibly attentional, with somatosensory cortical inputs, reflecting either visualization of the spatial configurations of tactile stimuli or engagement of modality independent circuits specialized for fine spatial processing
Stilla et al., J Neurosci 07
Comparing functional connectivity and
Granger-based effective connectivity
Eff
ective C
onnectivity
Matr
ix
"Better" group "Poor" group
Functional C
onnectivity
Matr
ix
R=-0.08, p=0.45 R=-0.02, p=0.85
Correlation-purged Granger Causality
• Given n time series X(t) = [x1(t) x2(t) … xn(t)], the traditional VAR model of order p is given below
X(t) = A(1)X(t-1) + A(2)X(t-2) + ... + A(p)X(t-p) + E(t)
where A(1) … A(p) are the coefficients of the model and E(t) is the model error
• In order to account for the zero-lag correlation effects, we introduce the zero-• In order to account for the zero-lag correlation effects, we introduce the zero-lag term
X(t) = A' (0)X(t) + A' (1)X(t-1) + A' (2)X(t-2) + ... + A' (p)X(t-p) + E' (t)
• The inclusion of the zero-lag term affects the value of other coefficients and hence A'(1) … A' (p) ≠ A(1) … A(p)
• GC obtained from A'(1) … A' (p) are linearly independent of zero-lag correlation, which we call correlation-purged GC (CPGC)
Deshpande & Hu, TBME, 57: 1446-1456, 2010
Simulation
• CASE 1: Consider two time series x(n) and y(n) modeled as a first order VAR process such that the causal influence between them is zero but the instantaneous correlation is nonzero
==
10.5
0.51Covand
00
00A(1)
• Assuming x(n) and y(n) represent LFPs sampled at 1ms, they were convolved with HRF and downsampled 1000/2000 times to simulate convolved with HRF and downsampled 1000/2000 times to simulate fMRI series with TRs of 1 s and 2 s
• CASE 2: Subsequently, in order to demonstrate the efficacy of CPGC for recovering neuronal causal influences from fMRI, we generated x(n)and y(n) such that a unidirectional causal influence exists from x(n) to y(n) with no correlation between them. The corresponding fMRI time series, x' (n) and y' (n), were derived and zero-lag correlation, GC and CPGC were calculated from them
Deshpande & Hu, TBME, 57: 1446-1456, 2010
TRZero-lag correlation Granger causality Correlation-purged Granger causality
x' (n) ↔ y' (n) x' (n) → y' (n) y' (n) → x' (n) x' (n) → y' (n) y' (n) → x' (n)
1 s 0.49 ± 0.05 0.47 ± 0.01 0.47 ± 0.01 0.01 ± 0.02 0.01 ± 0.02
2 s 0.49 ± 0.06 0.40 ± 0.07 0.40 ± 0.07 0.00 ± 0.09 0.00 ± 0.09
TRZero-lag correlation Granger causality Correlation-purged Granger causality
x' (n) ↔ y' (n) x' (n) → y' (n) y' (n) → x' (n) x' (n) → y' (n) y' (n) → x' (n)
1 ms 0.5 ± 0.09 0.00 ± 0.01 0.00 ± 0.01 0.00 ± 0.01 0.00 ± 0.01
Simulation 1: Only correlation and no causality in LFP data
TRZero-lag correlation Granger causality Correlation-purged Granger causality
x' (n) ↔ y' (n) x' (n) → y' (n) y' (n) → x' (n) x' (n) → y' (n) y' (n) → x' (n)
1 s 0.29 ± 0.09 0.47 ± 0.1 0.27 ± 0.09 0.21 ± 0.02 0.01 ± 0.02
2 s 0.29 ± 0.09 0.40 ± 0.09 0.20 ± 0.07 0.14 ± 0.02 0.00 ± 0.02
TRZero-lag correlation Granger causality Correlation-purged Granger causality
x' (n) ↔ y' (n) x' (n) → y' (n) y' (n) → x' (n) x' (n) → y' (n) y' (n) → x' (n)
1 ms 0.0 ± 0.09 0.5 ± 0.01 0.0 ± 0.01 0.5 ± 0.01 0.0 ± 0.01
Simulation 2: Only causality and no correlation in LFP data
Deshpande & Hu, TBME, 57: 1446-1456, 2010
Functional connectivity
• Temporal correlations of low frequency
fluctuations exist in the brain, even at “rest”– Biswal et al. Magn Reson Med 34:537 (1995)
• Connectivity of functionally related areas
– Examples: Motor, visual, language, “default mode”
networks
• Can characterize changes in brain state
Resting State Networks (RSNs)
• Internally directed cognitive processing (specifically, self
referential and mental simulation) by Default Mode
Network (DMN)
• Obtained using posterior cingulate (PCC) seed
• Internally directed cognitive processing (specifically, memory encoding and retrieval ) by Hippocampal Cortical
Memory Network (HCMN)
• Obtained using hippocampus (HC) seed
• Externally directed cognitive processing by Dorsal
Attention Network (DAN)
• Obtained using middle temporal (MT) seed
• Executive control of anti-correlated DMN/HCMN and
DAN by Fronto-parietal Control Network (FPCN)
• Obtained usinganterior prefrontal (aPFC) seed
Deshpande et al., NeuroImage (2010)
DMN
HCMN
DAN
FPCN
Frontal
Parietal
Temporal
Cingulate
DMN
HCMN
DAN
FPCN
Frontal
Parietal
Temporal
Cingulate
DMN
HCMN
DAN
FPCN
Frontal
Parietal
Temporal
Cingulate
PCC and pIPL: The Transit Hubs
• Central location on layout ideal for this role
• High resting state metabolism
• PCC seed-based correlation analysis will only reveal DMN and HCMN ROIs
• Drives the characterization of different groups of ROIs in different networks
• Functional segregation of different networks is rather a soft boundary
Deshpande et al., NeuroImage (2010)
Memory Encoding
• Predominant inputs to HF from:
• Parietal ROIs provide perceptual content
• DAN ROIs may provide the context, i.e. those perceptual
contents which are being attended to
Deshpande et al., NeuroImage (2010)
Deshpande et al., NeuroImage (2010)
Integration and Control
• aPFC is at the apex of the control hierarchy
• Implicated in integrating the outcomes of multiple cognitive operations
• Integration of internal and external representations from the anti-correlated
DMN/HCMN and DAN systems:
• The input to R aPFC from PCC brings the internal representations from memory
• Inputs from bilateral MT in the DAN bring the information about the external environment
• Our results support Vincent’s hypothesis: aPFC seeded FPCN to be a control network
• SVC successfully learned patterns of functional connectivity
capable of predicting MDD from HCcapable of predicting MDD from HC
– Uncovered differences not discovered by t-test analysis
• Feature selection substantially improved the prediction
accuracy of SVC
– Methods that incorporate reliability performed the best
PCE may affect behavior and functioning by increasing baseline arousal and altering the
excitatory/inhibitory balancing mechanisms involved in cognitive resource allocation.
PCE is associated with activation changes in different regions, so can connectivity changes
across these regions be used to predict PCE?
Medial PFC
Left DLPFCRight
DLPFC
Prediction of PCE status with functional/effective connectivity
Left amygdala Right amygdala
Medial PFC
Left Parietal
cortex
Right Parietal
cortex
ACC
PCC
Deshpande et al., 2010 PLoS ONE 5 (12):e14277
Prediction of PCE status with functional/effective connectivity
Deshpande et al., 2010 PLoS ONE 5 (12):e14277
Correction of HRF latency with breath holding
Breath Holding
3.8 sec 3.8 sec 3.8 sec 3.0 sec 11.4 sec
inhale inhale inhale inhale
get ready
hold release
… 16 repetitions
Face Perception
90 faces randomly presented
ISI = 3.92sec (mean) ± 2.1sec (SD)
2 fMRI scan runs, ~6min
TR = 1sec or 2sec
Chang, Neuroimage 2008
Data Processing
Mean signal
as reference
1. ROI definition by regular GLMV1 and FFA
2. BH modulated cortical voxels
3. Voxel-wise signal latency
ROI signal
extraction4. Voxel-wise
latency correction
Reference
Each voxel
Shift to find the best correlation
FFA
original
V1 original
FFA
corrected
V1 corrected
ShiftLatency
applied
5. Compare GCA results of
uncorrected & corrected dataUncorrected Corrected
Feed into GCA
Results
Effect of temporal resolution on GCA
Block (30sec) design, visual (flashing checker board) motor (finger tapping) task
Parallel imaging with TR=2.4sec, 0.6sec, and 0.3sec, 4 subjects
Six ROIs defined according to fMRI activation
Left LGNRight LGN
Visual
cortex
Left primary
motor
Right primary
motor
SMA
GCA Results
TR=2.4sec LGCN ->
V
TR=0.6sec
TR=0.3sec
LGC -> V
LGN -> Motor
LGC -> V
LGN -> Motor
SMA -> Primary Motor
Time-frequency dynamics of default
mode effective connectivity
Summary
• Granger causality analysis can infer causal influences
(neuronal delays) between different brain regions from
fMRI data although there are limitations.
• Granger causality analysis can also be applied to resting-
state fMRI data to infer instantaneous correlation and
causal influences.
• Connectivity measures, particularly the combination of
functional and effective connectivities, can be used to
improve prediction.
Acknowledgements
• Funding: NIH, Georgia Research Alliance
• Students and Postdocs: Cameron Craddick, Priya
Sanatham, Gopi Deshpande, Stephen LaConte, Zhihao Li, Sanatham, Gopi Deshpande, Stephen LaConte, Zhihao Li,
John Sexton, Andy James, and Scott Peltier
• Collaborators: Claire Coles, Helen Mayberg, Paul
Holtzheimer, Clint Kilts, Krish Sathian, Stephan Hamann,
and Mary Ellen Lynch