Title: Improved Analysis of PET Images for Radiation Therapy: DeBlurring and Automated Segmentation Techniq
1Improved Analysis of PET Images for Radiation
Therapy De-Blurring and Automated Segmentation
Techniques
Issam El Naqa1, Jeffrey Bradley1, Kenneth Biehl1,
Richard Laforest2, Daniel Low1, Joseph Deasy1
1Dept. of Radiation Oncology, 2Dept. of
Radiology Washington University, School of
Medicine St. Louis, MO 63110, USA Partially
supported by NIH grant R01 CA90445
2Problems Objectives
- Motivation
- Higher uptake of Glucose in tumor cell
- Use of 18FDG (Fluorodeoxyglucose )
- Use of sequential CT and PET in the same scanner
to obtain detailed anatomical and functional
images - Problems
- PET imaging degradation due to noise,
attenuation, and scatter - Labor-intensive 3-D contouring of high-uptake
boundaries - Proposed Methods
- Image sharpening via deconvolution
- Auto-segmentation to contour high-uptake tumor
volumes
3Methodology
Input PET image
Initialize Roughly select a contour around tumor
Is PSF known?
No
Apply Deformable model
Yes
Estimate PSF (Blind/Myopic method)
Deconvolution
Segmented tumor
4Evaluation Data Set
- 19 PET/CT co-registered images with a
pathological diagnosis of non-small cell lung
cancer (NSCLC). - Patients were imaged on a Siemens Biograph PET/CT
scanner and had biopsy-proven peripheral lung
cancers surrounded by normal lung tissue on the
staging CT scan. - Maximum uptake of 18F-FDG
- In normal tissues adjacent to suspected lesions
0.84 - In Lesions 12.1
- PET images have a voxel size of 5.1 mm and a
slice thickness of 3mm. The CT images have a
voxel size of 1mm and slice thickness of 5mm.
5Data Example
CT slice
PET slice
Tumor region of interest (TROI)
6PET Deblurring
- The objective is to restore the true image due
to imperfect imaging system. The system could be
represented as
- where g is the observed function, f is the ideal
true image, and h is a characteristic of the
imaging system (PSF), n is additive noise, x is
the spatial coordinate, and is the
convolution operator
- We use, iterative methods based on the
Expectation maximization algorithm (EM)
- The PSF could be incorporated directly if known
or estimated if it is unknown (blind
deconvolution) or partially known (myopic
deconvolution)
7Deblurring Example
Deblurred Tumor ROI
PSF
3x3
5x5
7x7
Support size
8Tumor Segmentation
- Currently used method is 40 threshold of of the
SUV by Erdi et al 1997. Other variations include
tumor-to-background ratio (TBR) by Biehl et al
2004 - Thresholding fails to capture tumor boundaries.
- Proposed methods is Deformable Models.
- Parametric deformable models (e.g., Snakes)
- Too sensitive to initialization and dont adapt
with topological changes - Geometric deformable models (e.g., Level set)
-
and - Where V is a velocity function of contour
curvature and image characteristics and is
the level set function - Less sensitive to initialization and adapt
topologically
9Classical Level set Example
Iteration 200
Iteration 100
Initialization
Iteration 500
Iteration 400
Iteration 300
10Level set contours without edges
- Instead of computing gradients one can solve a
minimal partition problem using a special case of
the Mumford-Shah model - Add spring force control
F2
F1
112D Example of classical level setGeneric image
122D Example of edgeless level setGeneric image
132D Example of classical level setPET
142D Example of edgeless level setPET
153D Example of edgeless level setPET
16Future work
- We would like to improve the deconvolution
process by extracting prior information using
phantom studies - Conduct a comparative study with other
segmentation methods using the CT data and
physician input as ground truth
17Conclusions
- Two methods to improve the analysis of PET images
for treatment planning purposes are presented - Deconvolution is used to improve the visual
quality of PETs by reducing the imaging
degradations - Tumor segmentation by level set method is
proposed in opposite to simple Thresholding - Preliminary results on deconvolution and
segmentation are promising