informative priors for segmentation of medical images
TRANSCRIPT
Motivation Method 1 Method 2 Extensions Conclusion
Informative Priors for Segmentationof Medical Images
Matt Moores1,2, Cathy Hargrave3, Fiona Harden2
& Kerrie Mengersen1
1 Discipline of Mathematical Sciences, Queensland University of Technology2 Discipline of Medical Radiation Sciences, Queensland University of Technology
3 Radiation Oncology Mater Centre, Queensland Health
Bayes on the Beach, 2011
Motivation Method 1 Method 2 Extensions Conclusion
Outline
1 MotivationCone-Beam Computed Tomography
2 Method 1k-means with posterior diffusion
3 Method 2hidden Markov random field
4 Extensions
5 Conclusion
Motivation Method 1 Method 2 Extensions Conclusion
X-Ray Computed Tomography
(a) Fan-Beam CT (b) Cone-Beam CT
Motivation Method 1 Method 2 Extensions Conclusion
Distribution of Pixel Intensity
Hounsfield unit
Fre
quen
cy
−1000 −800 −600 −400 −200 0 200
050
0010
000
1500
0
(a) Fan-Beam CT
pixel intensity
Fre
quen
cy
−1000 −800 −600 −400 −200 0 2000
5000
1000
015
000
(b) Cone-Beam CT
Motivation Method 1 Method 2 Extensions Conclusion
itkBayesianClassifierImageFilter
1 estimate µ using k-means
1 select initial values for µ2 assign each pixel y to the nearest µk
3 recalculate each µk by averaging over the members of k4 repeat steps 2 & 3 until none of the pixel assignments change
2 estimate σ2 for each cluster(mixing proportions are assumed equal)
3 create a matrix y∗:for each pixel yi and each cluster Ck ∼ N(µk, σk),yik = p(yi|µk, σk)
456 classify each pixel yi according to the largest value of yik
Motivation Method 1 Method 2 Extensions Conclusion
itkBayesianClassifierImageFilter
1 estimate µ using k-means1 select initial values for µ2 assign each pixel y to the nearest µk
3 recalculate each µk by averaging over the members of k4 repeat steps 2 & 3 until none of the pixel assignments change
2 estimate σ2 for each cluster(mixing proportions are assumed equal)
3 create a matrix y∗:for each pixel yi and each cluster Ck ∼ N(µk, σk),yik = p(yi|µk, σk)
456 classify each pixel yi according to the largest value of yik
Motivation Method 1 Method 2 Extensions Conclusion
Result (k-means GMM)
(a) Fan-Beam CT (b) Cone-Beam CT
Motivation Method 1 Method 2 Extensions Conclusion
Prior
4 matrix pik representing the prior probability of pixel ibelonging to cluster k
then pixel classification is based on the posterior pik × yik
but:
this has no effect on the number of clusters, nor on theirparameters µk and σk
can’t use the posterior from one classification as the prior foranother, unless the clusters are the same
Motivation Method 1 Method 2 Extensions Conclusion
Result (with prior)
(a) Prior (b) Likelihood
(c) Posterior
Motivation Method 1 Method 2 Extensions Conclusion
Result (with diffusion)
(a) 5 iterations (b) 10 iterations
(c) 50 iterations (d) 1000 iterations
Motivation Method 1 Method 2 Extensions Conclusion
hidden Markov random field
Joint distribution of observed intensities y and unobserved labels z:
p(y, z|µ, τ ) ∝ p(y|µ, τ , z)p(z) (1)
yi|µj , τj , zi=j ∼ N
(µj ,
1
τj
)(2)
p(z) = C(β)−1exp
N∑i=1
αi(zi) + β∑i∼j
wijf(zi, zj)
(3)
simple Potts model (without external field):
p(z) = C(β)−1exp
β∑i∼j
I(zi = zj)
(4)
Motivation Method 1 Method 2 Extensions Conclusion
informative prior for µ and τ
0 1 2 3 4
−10
00−
800
−60
0−
400
−20
00
200
Electron Density
Hou
nsfie
ld u
nit
(a) Fan-Beam CT
0 1 2 3 4
−10
00−
800
−60
0−
400
−20
00
200
Electron Density
pixe
l int
ensi
ty
(b) Cone-Beam CT
Motivation Method 1 Method 2 Extensions Conclusion
external field
In equation (3) earlier, the term exp{∑N
i=1 αi(zi)}
defines an
external field.
Figure: manual contours of the organs of interest.
Motivation Method 1 Method 2 Extensions Conclusion
external field II
Prior probabilities αi(zi) for each pixel can be generated bysimulation, based on:
geometry of each organ, from the treatment plan
variability in size and position, from published studies
Axis prostate seminal vesicles
Ant-Post x = 0.1, sd = 4.1 mm x = 1.2, sd = 7.3 mm
Sup-Inf x = −0.5, sd = 2.9 mm x = −0.7, sd = 4.5 mm
Left-Right x = 0.2, sd = 0.9 mm x = −0.9, sd = 1.9 mm
Table: Mean x and standard deviation sd of observed [5] variability inposition, along three axes: anteroposterior (Ant-Post); superoinferior(Sup-Inf); & lateral (Left-Right) relative to the patient.
Motivation Method 1 Method 2 Extensions Conclusion
Jacobian matrix
Figure: discrete Laplacian 52
Motivation Method 1 Method 2 Extensions Conclusion
hybrid model
Chen & Metaxas [6, 7] define the object boundary implicitly as thezero level set of a cost function:
∂φi∂t
=
[λ1Mi +5λ2Pi ·
(5φi‖ 5 φi‖
)− (λ2Pi + λ3)5 ·
(5φi‖ 5 φi‖
)](5)
where:
Mi is the inflation force (total gradient magnitude)
Pi is the local image force at each pixel(probability of pixel j belonging to object i)
non-overlapping constraint
5 ·(5φi‖5φi‖
)is the local curvature
(surface smoothness constraint)
Motivation Method 1 Method 2 Extensions Conclusion
Summary
Two Bayesian approaches to medical image segmentation:
k-means with posterior diffusion(itkBayesianClassifierImageFilter)
hidden Markov random field(PyMCMC)
Potential extensions to Potts MRF:
external field defined by size and position of objects
hybrid Level Set model
Motivation Method 1 Method 2 Extensions Conclusion
References I
P. Teo, G. Sapiro and B. Wandell (1997) Creating connectedrepresentations of cortical gray matter for functional MRIvisualization. IEEE Trans. Med. Imag. 16: 852-863.
J. Melonakos, K. Krishnan and A. Tannenbaum (2006)An ITK Filter for Bayesian Segmentation:itkBayesianClassifierImageFilter The Insight Journalhttp://hdl.handle.net/1926/160
Strickland, C. M., Denham, R. J., Alston, C. L., & Mengersen, K. L.(2011) PyMCMC : a Python package for Bayesian Estimation usingMarkov chain Monte Carlo. Journal of Statistical Software (In Press)
C. Alston, K. Mengersen, C. Robert, J. Thompson, P. Littlefield, D.Perry and A. Ball (2007) Bayesian mixture models in a longitudinalsetting for analysing sheep CAT scan images. ComputationalStatistics & Data Analysis 51(9): 4282-4296.
Motivation Method 1 Method 2 Extensions Conclusion
References II
S.J. Frank, L. Dong, R. J. Kudchadker, R. De Crevoisier, A. K. Lee,R. Cheung, S. Choi, J. O’Daniel, S. L. Tucker, H. Wang, et al.(2008) Quantification of Prostate and Seminal Vesicle InterfractionVariation During IMRT. International Journal of RadiationOncology*Biology*Physics 71(3): 813-820.
T. Chen and D. Metaxas (2005) A hybrid framework for 3D medicalimage segmentation. Medical Image Analysis 9(6): 547-565.
T. Chen, S. Kim, J. Zhou, D. Metaxas, G. Rajagopal & N. Yue(2009) 3D Meshless Prostate Segmentation and Registration inImage Guided Radiotherapy. In Proceedings of MICCAI 43-50.
P. Thevenaz, T. Blu & M. Unser (2000) Interpolation Revisited.IEEE Trans. Medical Imaging 19(7): 739–758.
Motivation Method 1 Method 2 Extensions Conclusion
Acknowledgements
Bayesian Research & Applications Group at QUT
Radiation Oncology Mater Centre:
Emmanuel Baveas
Rebecca Owen
Timothy Deegan
Steven Sylvander
John Baines
Dr. Michael Poulsen