Disadvantages of Spherical/Polar Revolute Coordinate System.
Mapping Tissue Microstructure using Spherical Polar ... · 05-05-2016 · Mapping Tissue...
Transcript of Mapping Tissue Microstructure using Spherical Polar ... · 05-05-2016 · Mapping Tissue...
Mapping Tissue Microstructure using Spherical PolarFourier Diffusion MRI
Jian Cheng
National Institutes of Health
May 5, 2016
Outline
1 Problems and Objective
2 Compressed Sensing Reconstruction Using SPFI
3 DMRITOOL
4 Conclusion
Outline
1 Problems and Objective
2 Compressed Sensing Reconstruction Using SPFI
3 DMRITOOL
4 Conclusion
Diffusion MRI Data Processing Pipeline
Diffusion Data in 6D space
3D x-space (spatial space) and 3D R-space (diffusion displacement space)
Ensemble Average Propagator (EAP) P(R)
EAP field: P(x,R); ODF field: Φk(x,R)
[Descoteaux 2008, Hagmann 2006]
EAP profile P(R0r)Orientation DistributionFunction (ODF) Φk(r)
Φk(r) def= 1Z
∫ ∞0
P(Rr)RkdR
Diffusion Weighted Imaging (DWI)
The Pulse Gradient Spin-Echo (PGSE)sequence [Stejskal and Tanner 1965]
Narrow pulse assumption (δ � ∆)E(q) F3D⇐⇒ P(R)
[Callaghan, 1991]
q = qu F3D⇐⇒ R = Rr
E(q) = S(q)S(0) q = γδG/2π
Fourier relationP(R) =
∫E(q)e−2πiq·Rdq
E(q) =∫
P(R)e−2πiq·RdR
Diffusion Tensor Imaging (DTI)
Free diffusion, Gaussian diffusion assumption [Basser 1994]
P(R) = 1√(4πτ)3|D|
exp(− 1
4τ RTD−1R)
D =3∑
i=1λiv ivT
i
Diffusion tensor model [Basser 1994]
E(q) = S(q)/S(0) = exp(−4π2τqTDq) = exp(−buTDu)
b = 4π2τ‖q‖2
Tensor estimation (> 6 DWIs)
Modeling Beyond DTI: HARDI
Sampling in DTI, in Cartesian grid, single shell and multiple shells
sampling in DTI
Diffusion Tensor Imaging (DTI)[Basser1994]
Dense Cartesian grid
Diffusion Spectrum Imaging (DSI)[Callaghan 1991; Wedeen 2000, 2005]
Single shell sampling
sHARDI:Q-Ball Imaging (QBI), exact QBI[Tuch 2004; Descoteaux 2007; Aganj 2010]Diffusion Orientation Transform (DOT)[Ozarslan 2006]......
Multiple shell or arbitrarily sampling
mHARDI:Diffusion Propagator Imaging (DPI)[descoteaux 2010]Spherical Polar Fourier Imaging (SPFI)[Assemlal 2009; Cheng 2010]Simple Harmonic Oscillator basedreconstruction and estimation (SHORE,MAP-MRI)[Ozarslan 2009, 2013; Cheng 2011a]...
P(R) =∫
E(q)e−2πiq·Rdq, b = 4π2τ‖q‖2
Problems
Reconstruction:1 Reconstruction of continuous diffusion signal from its limited number of
samples with noise.2 Reconstruction of diffusion propagator which is the Fourier transform of
diffusion signal under some condition.3 Extract some other quantities: ODF, return-to-origin probability, anisotropy,
axon dimeter, etc.
Objective
1 Robust reconstruction from limited number of samples with noise.Continuous diffusion signal modelRobus reconstruction algorithmGood sampling scheme
2 Closed form solutions: solve reconstruction problems simultaneously.Continuous diffusion signal model with good Mathematical properties.
Outline
1 Problems and Objective
2 Compressed Sensing Reconstruction Using SPFI
3 DMRITOOL
4 Conclusion
Prior knowledge and assumption in reconstruction
Reconstruction signal in 1D space from its samples.
q
E(q)
1
No assumption on signal (E(q) ∈ C1(R))): cannot perform reconstructionMaximal frequency (DSI): Nyquist sampling rate.Gaussian assumption (DTI) : one sample, break Nyquist rate.
Prior knowledge V.S. Assumption
Diffusion signal model
A general signal model and its reconstruction:
mina
∑s
(f (qs|a)− Es)2 + R(a)
DTI:min
D
∑s
(exp(−4π2τq2
s Dqs)− Es)2
minD
∑s
(q2
s Dqs + 14π2τ
log(Es))2
linear representation model:
E(q) =∑
iBi(q)ai
mina
∑s
(∑i
Bi(qs)ai − Es
)2
+ R(a)
Model and regularization are designed based on prior knowledge orassumption
Sparsity prior
Assumption: the latent signal can be sparsely represented by a givendictionary.
E(q) =∑
iBi(q)ai , E = Ma
Sparsity:‖a‖0 =
∑iδ(ai = 0)
Sparsity assumption is always true because the dictionary can bedevised to have atoms which are similar with the signal itself.
Basic of Compressed Sensing
Basis pursuit deionising:
minx‖x‖1 s.t. ‖Ax − y‖2 ≤ δ (Pδ
1 )
Theorem (Stability of (Pδ1 ) [Donoho 2006])
For the problem (Pδ1 ) defined by (A, y, δ), if x0 ∈ Rn satisfies ‖x0‖0 < 1+1/µ(A)
4and ‖Ax0 − y‖2 ≤ δ, then the solution xδ1 of the problem (Pδ
1 ) obeys
‖xδ1 − x0‖22 ≤4δ2
1− µ(A)(4‖x0‖0 − 1)
We have to choice to make the estimation error ‖xδ1 − x0‖22 small, consideringA = MD
1 make µ(A) small =⇒ sampling matrix design for M2 make ‖x0‖0 small =⇒ dictionary learning for D
Compressed Sensing Reconstruction
Several variants:Prior knowledge on signal representation error:
minx‖x‖1, s.t.‖Ax − b‖2 ≤ δ
Prior knowledge on sparsity:
minx‖Ax − b‖2, s.t.‖x‖1 ≤ δ
No above prior knowledges:
minx‖Ax − b‖2 + λ‖x‖1
Reconstruction in dMRI
Reconstruction:1 Reconstruction of continuous diffusion signal from its limited number of
samples with noise.2 Reconstruction of diffusion propagator which is the Fourier transform of
diffusion signal under some condition.3 Extract some other quantities: ODF, return-to-origin probability, anisotropy,
etc.Ideas: compressed sensing reconstruction using a good basis:
1 Complete continuous basis (capture complexity)2 Sparse representation (capture prior knowledge).3 Analytical Fourier transform: simultaneously reconstruction of diffusion signal
and diffusion propagator.4 Closed form solutions for features (ODF, RTO, anisotropy, etc).
Spherical Polar Fourier Imaging (SPFI)
Spherical Polar Fourier expression of signals [Assemlal 2008, 2009]
E(q) =N∑
n=0
L∑l=0
l∑m=−l
anlmGn(q|ζ)Y ml (u) BSPF
nlm(q) = Gn(q|ζ)Y ml (u)
Gaussian Laguerre polynomialGn(q) = κn(ζ) exp
(− q2
2ζ
)L1/2
n ( q2
ζ ), κn(ζ) =[
2ζ3/2
n!Γ(n+3/2)
]1/2
Sparsity of SPF basis
Scale parameterSignal anisotropy
Analytical Transforms in SPFI
P(R) is analytically obtained from Fourier dual SPF (dSPF) basis [Cheng 2010a]
P(Rr) =N∑
n=0
L∑l=0
l∑m=−l
anlmFnl(R)Y ml (r) BdSPF
nlm (R) = Fnl(R)Y ml (r)
Fourier dual SPF (dSPF) basis, orthonormal basis in R-space
BdSPFnlm (R) =
∫R3 BSPF
nlm(q)e−2πiqT Rdq = Fnl(R)Y ml (r)
Fnl(R) = 4(−1)l/2 ζ0.5l+1.5πl+1.5Rl0
Γ(l+1.5) κn(ζ)∑n
i=0(−1)i(n+0.5n−i
) 1i!2
0.5l+i−0.5Γ(0.5l + i + 1.5)1F1( 2i+l+32 ; l + 3
2 ;−2π2R2ζ)
A linear transform from {anlm} to EAP profile represented by SH basisFor a given R0, EAP profile
P(R0r) =L∑
l=0
l∑m=−l
cPlm(R0)Y m
l (r), cPlm(R0) =
N∑n=0
anlmFnl(R0)
Analytical Transforms in SPFI
Linear transform for ODF by Tuch Φt(r) def= 1Z∫∞
0 P(Rr)dR [Cheng 2010b]
Φt(r) =L∑
l=0
l∑m=−l
cΦtlmY m
l (r)
Linear transform for ODF by Wedeen Φw(r) def=∫∞
0 P(Rr)R2dR [Cheng 2010b]
Φw(r) =L∑
l=0
l∑m=−l
cΦwlm Y m
l (r)
Analytical transform avoids the numerical error{E(qi)}→{anlm}→{cP
lm(R0)}, {cΦtlm}, {c
Φwlm }, RTO, MSD, PFA, NG, RTAP
RTO: return-to-origin probability, P(0).MSD: mean-squared displacement,
∫R3 P(R2)R2RdR
PFA: propogator fractional anisotropy.NG: non-gaussianity.RTAP: return-to-axis probability.
Tensorial SPFI: affinely transformed representation
Limitation of SPF basis: inefficient to represent highly anisotropic signal.Tensorial SPFI (inspired by MAP-MRI [Ozarslan 2013] ): D = QΛ2QT , QTQ = I
E(qu | D) =√
|Λ|N∑
n=0
L∑l=0
l∑m=−l
anlmGn
(q√
uT Du | ζ0
)Y m
l
(ΛQT u
‖ΛQT u‖
)
P(Rr | D) =1√|Λ|
∑nlm
anlmFnl
(R√
rT D−1r | ζ0
)Y m
l
(Λ−1QT r
‖Λ−1QT r‖
)Isotropic tensor ⇒ general tensor.Efficient to represent anisotropic signal.
Tensorial SPFI: affinely transformed representation
CS Reconstruction: [Cheng 2010, 2011]
mina′‖M′a′ − e′‖22 + ‖Ha′‖1
Constraint: E(0) = 1CS Reconstruction using learned basis: [Cheng 2013, 2015]
minc‖M′Wc − e′‖22 + ‖Vc‖1
Learned basis M′WOriginal basis + learned regularization HW, if we set a′ = Wc and V = HW.Full regularization matrix.
My journey:L2 SPFI (2010) ⇒ L1 SPFI (2011) ⇒ DL-SPFI (2013) ⇒ DL-TSPFI (2015)
Learning the Dictionary using Synthetic Signals
Real signal: limited samples with noise.Synthetic signal:
tensor model, cylinder modelmany samples without noise from given modelsMSPF is orthonormal matrixLearn a dictionary in model-free method using model-based priors.
Sparsity of Tensors
321 orientations, different FA, same MD D0 = 0.7× 10−3.
0 0.1 0.2 0.3 0.4 0.5 0.6 0.7 0.8 0.90
20406080
100120140160180
FA (MD=0.6× 10−3 mm2/s)
Num
ber
ofN
onze
roCo
effici
ents SPF, single tensor
DL-SPF, single tensor
TSPF, DL-TSPF, single tensor
SPF, mixture of tensors
DL-SPF, mixture of tensors
TSPF, mixture of tensor
DL-TSPF, mixture of tensor
0 0.1 0.2 0.3 0.4 0.5 0.6 0.7 0.8 0.90
20406080
100120140160180
FA (MD=1.1× 10−3 mm2/s)N
umbe
rof
Non
zero
Coeffi
cien
ts SPF, single tensor
DL-SPF, single tensor
TSPF, DL-TSPF, single tensor
SPF, mixture of tensors
DL-SPF, mixture of tensors
TSPF, mixture of tensors
DL-TSPF, mixture of tensors
Figure: Synthetic Experiments. The average number of non-zero coefficients for SPF,DL-SPF, TSPF and DL-TSPF basis.
Note: MD range in learning process is [0.5, 0.9]× 10−3mm2/s
Synthetic Data Using Cylinder Model
RMSE in reconstruction
30 35 40 45 50 55 60 65 70 75 80 85 900
0.01
0.02
0.03
0.04
0.05
Crossing Angle (no noise)
RMSE
l1-SPFI
DL-SPFI
DL-TSPFI
30 35 40 45 50 55 60 65 70 75 80 85 900
0.05
0.1
0.15
0.2
0.25
Crossing Angle (SNR=20)
RMSE
l1-SPFI
DL-SPFI
DL-TSPFI
Real DSI Data
DSI scheme. Results from 515 samples V.S. result from 171 samples,RMSE = 2.82%
Real DSI Data
Results from 515 samples V.S. result from 171 samples, RMSE = 2.82%
TSPFI coefficients SPFI coefficients TSPFI DWI SPFI DWI
Real HCP Data
3 shells with b values 1000,2000,3000. 90 samples per shell.
FA eap profile 15µm
Real HCP Data
MSD RTO RTAP
NG PFA FA
Outline
1 Problems and Objective
2 Compressed Sensing Reconstruction Using SPFI
3 DMRITOOL
4 Conclusion
DMRITOOL
https://diffusionmritool.github.ioOpen source software in c++ and matlab.What?
Reconstruction in diffusion MRI: EAP, ODF, fiber ODF, scalar maps.Uniform sampling scheme design, sub-sampling.Data visualization: nifti image, spherical function field (ODF, EAP profile).Data simulation using mixture of tensor (or cylinder) model.
Why?Reproducible research, fair comparison.Useful for users.
Outline
1 Problems and Objective
2 Compressed Sensing Reconstruction Using SPFI
3 DMRITOOL
4 Conclusion
Conclusion
Compressed sensing reconstructionL2 SPFI (2010) ⇒ L1 SPFI (2011) ⇒ DL-SPFI (2013) ⇒ DL-TSPFI (2015)Analytic dictionary ⇒ dictionary learningClosed form solutions for variant features (ODF, anisotropy, RTO, MSD).
Software: https://diffusionmritool.github.io
Acknowledgement
NIH: Peter J. Basser, Richard Leapman, Ruiliang Bai, Alexandru Avram, DanBenjamini, Elizabeth Hutchinson, Okan Irfanoglu, Michal KomloshUNC: Pew-Thian Yap, Dinggang Shen, Hongtu ZhuCAS: Tianzi JiangINRIA: Rachid Deriche, Aurobrata Ghosh
Thank you!Questions?