Title: ANALYSIS OF A LOCALLY VARYING INTENSITY TEMPLATE FOR SEGMENTATION OF KIDNEYS IN CT IMAGES
1ANALYSIS OF A LOCALLY VARYING INTENSITY TEMPLATE
FOR SEGMENTATION OF KIDNEYS IN CT IMAGES
- MANJARI I RAO
- UNIVERSITY OF NORTH CAROLINA AT CHAPEL HILL
2OVERVIEW
- Introduction
- Background
- Materials and Methods
- Results
- Conclusions and Discussion
3External Beam Radiation Therapy
- (Image Types CT, MRI, Ultrasound, PET etc.)
- Simulation
- Treatment Planning
4Segmentation
- Segmentation is a process of extraction of
information from an image in such a way that the
output image contains much less information than
the original one, but the little information that
it contains is much more relevant to the purpose
of the task . - Medical Image Segmentation Extraction of
anatomical structures such as the kidney.
5Segmentation in Treatment Planning
- Manual Segmentation
- Computer-based models
- Combination techniques
6Virtual Simulation
- Combination of simulation and treatment planning
- Detect tumor sites from different viewpoints
- Design irradiation beam and orientation
- Calculate dose distribution
- Presence of patient not required
7Manual Segmentation - Limitations
- Dependent on the experience of the operator
- Inter-operator and Intra-operator variability
- Difficult to identify 3D structures on a 2D slice
- Complexity is increased due to presence of
infiltrating tumor and disease
8OVERVIEW
- Introduction
- Background
- Materials and Methods
- Results
- Conclusions and Discussion
9Shape Representation Using Medial Models
- A medial axis is the locus of centers of spheres
that are bitangent to the surface of the object
being represented - The center point of each such sphere is a point
on the medial surface - M-reps are a class of medial models
10Object Representation via M-reps
- An m-rep consists of a grid of medial atoms, each
of which is made of a hub and a pair of spokes - The atoms in an m-rep define the following
- A medial position x in the mesh
- Two vectors of length r, which is the radius of
the bitangent sphere inscribed inside the object.
The vectors are the spokes that point to these
points of tangency. - The angle T formed between each of the spokes and
the angular bisector b. - A frame F (n,b,b-), where n is normal to both b
and b-, which defines the tangent plane to the
medial sheet at x. - The curvature ? of the object about a point.
-
11Object Representation via M-reps
- M-reps define an object-based intrinsic
coordinate system represented by - (u, v, t, ? ), where u and v represent the row
and column corresponding to the position of the
atom in the medial mesh - t indicates which side of the medial locus the
point lies on t -1 or 1 for internal medial
points and varies around the crest - from -1 through 0 at the boundary to 1
- ? measures the distance along the spokes from
the boundary, with ? gt 0 outside and ? lt 0 inside
the boundary and ? -1 at the medial locus
?
?
u
t
v
12Object Representation via M-reps
- The medial locus is a curve for objects in 2D and
a sheet for objects in 3D - It is sparsely sampled to produce an approximate
surface of the m-rep or the implied boundary.
13Segmentation using M-reps
- Transformation of the whole kidney model based on
both the similarity transform and Principal
Geodesic Analysis or PGA -translation, rotation,
scaling of the entire model and shape variation
according to the principal modes of variation of
a mean model.
14Segmentation using M-reps
- Deformation of each medial atom in the
model-translation, rotation and scaling of each
individual atom of the medial mesh.
15Segmentation using M-reps
- Atom deformation in this step is based on
- Geometric Typicality - Calculated by relating an
atoms coordinates predicted by the stage
immediately previous to the current deformation
stage, and by its neighbors at the current stage.
- Geometry to Image Match Calculated based on a
template defined in a collar region about the
boundary.
16Segmentation using M-reps
- Fine-scale surface refinement, i.e., each surface
tile of the implied surface is shifted along its
normal to optimize the objective function. This
scale was not used in the present study.
17Kidney Segmentation
- Surrounded by crowded soft tissue environment
most soft tissue does not contrast well against
its background. - High risk due to radiation exposure during
treatment of abdominal and pelvic tumors. Hence,
important in segmentation during treatment
planning. - Simple organ, can be represented by a
single-figure m-rep
18Kidney as an object of interest for this study
- Variation of intensities along the boundary of
the kidney - Examples
19 20 21OVERVIEW
- Introduction
- Background
- Materials and Methods
- Results
- Conclusions and Discussion
22Training and Target Images
- Training Images
- To generate a mean kidney m-rep model
- To generate intensity profiles for the locally
varying template
23Training Images
- CT Images Siemens Somatom Plus 4 scanner
- Raster resolution (number of pixels per slice)
512 x 512 - Pixel size ranged from 0.098mm2 to 0.156mm2
24Criteria for selection of Training Images
- Presence of whole kidney(s)
- Position of patient during scan
25Criteria for selection of Training Images
- Absence of contrast agent
- Absence of tumor, disease or kidney stones
26Criteria for selection of Training Images
- No more than moderate motion artifacts
27Criteria for selection of Training Images
- Margin of at least 2cm on the superior and
inferior edges of the kidney. - Slice thickness less than or equal to 5mm per
slice.
28OVERVIEW
- Introduction
- Background
- Materials and Methods
- Results
- Conclusions and Discussion
29Image Match based on a Template
- A target pattern at different locations in an
image - maximum response when the intensity
values of the pixels in the image correlate to
the values at the same locations specified by the
template - Determined by training the model on a population
of user-approved segmentations or the answers
30Image match based on a Template
- For an m-rep, the template is defined in the
collar region about the boundary - The width of this region ranged from 0.3r to
0.3r with 0 at the boundary in this study - The template thus corresponds to a Gaussian
centered about the boundary with a standard
deviation of 0.15
31Locally varying intensity template
- Function of figural positions along the boundary
of an m-rep - Generated from a population of training images
- Several profile types as compared to the
Gaussian which had only one
32Training
- Manual segmentation of kidneys from the training
data set - Conversion of resulting contours into blurred
binary images - Deformation of an m-rep model into the blurred
binary images to generate a mean model with
principal geometric modes of variation via PGA - Segmentation of the training kidneys by deforming
the mean model into the gray-scale training
images
33Training
- Generation of intensity profiles at many points
on the surface of the segmented kidneys - Classification of the each of the intensity
profiles into one of three categories, based on
the best match among three analytic filter types - Final Step Segmentation of kidneys in the target
images using the locally varying intensity
template to compute image match
34Manual segmentation
- Software used for radiation treatment planning
similar to drawing tools - Contours were traced on each cross-sectional
slice - Intensity windowing to enhance the quality of the
displayed image
35Manual Slice-by-slice contouring using
Anastruct-Editor
36Generation of Training Binary Images
- Output of hand-segmentation series of contour
stacks - Converted to binary images (have two intensity
values, 0 for black and 1 for white) - Gaussian smoothing operator was used to blur the
images. The ? of the operator was approximately
1mm
37Generation of the mean kidney m-rep
- Single figure mesh of 15 atoms (5 rows and 3
columns) was fit into each of the training
blurred binary images - The mean model and the corresponding principal
modes of variation were obtained from this
population of m-reps - Initial m-rep was replaced by the mean and the
process was iterated until convergence
38Generation of the locally varying Kidney Template
- Initial Analytic Filters
- Light-to-dark - higher intensities in the kidney
as compared to surrounding structures - Dark-to-light - lower intensities in the kidney
as compared to surrounding structures - Notch - similar intensities in the kidney as well
as surrounding structures with a narrow dark
region in between
39Initial Analytic Filters
Intensity
Points along the normal
40- Image corresponding to the light-to-dark filter
41- Image corresponding to the dark-to-light filter
42- Image corresponding to the notch filter
43Generation of Profiles for the Template
- End points of the spokes of the outer atoms in
the medial lattice of an m-rep are linked
together to form a quadrangular mesh surface - Surface was subdivided to provided a natural
framework for defining the boundary at 2562
points on the surface of the m-rep
44Generation of a Profiles for the Template
- At each of the 2562 boundary points, normals were
drawn (length from - -0.3r to 0.3r with 0 at the boundary as defined
by the collar) - Each normal was sampled at 11 points for each of
the 2562 boundary points
45Generation of Profiles for the Template
- Segmentation of the training blurred binary
images with the mean kidney m-rep - Generation of profiles for each m-rep in this
population with intensity information from
corresponding gray-scale images
46Generation of the locally varying Kidney Template
- Responses of the profiles to each of the three
analytic filters, given by the dot product, - X.Y ?xiyi , i 1,2,, n,
- X -vector representing the profile
- Y -vector representing the filter
- The highest response among the three filters for
each point determined the filter type
classification for that point -
47Classification of the profiles according to
responses
40.66
16.82
-34.74
48Converged Mean Filters
Intensity
Points along the normal
49Filter distribution on the surface of the left
and right kidneys in the templates
Left Kidney
Right Kidney
50Segmentation of Target Images
51Segmentation of Target Images
Axial View
Coronal View
52Segmentation of Target Images
Axial View
Coronal View
53Accuracy Evaluation
- VALMET Software package involving voxel-based
comparision - Volume overlap - intersection of the two volumes
divided by their union - Maximum Surface Distance or Hausdorff Distance -
the largest distance between two surfaces (Not
symmetric) - Mean absolute surface distance - how much on
average the two surfaces differ (Also not
symmetric)
Curve 1
a
b
Curve 2
54OVERVIEW
- Introduction
- Background
- Materials and Methods
- Results
- Conclusions and Discussion
55Comparison using VALMET Gaussian Vs Locally
Varying Template
- 24 Target Cases (12 left and 12 right kidneys)
- Segmentations were compared to human
segmentations performed by two experts - Average increase in volume overlap over all the
cases - 1.3 - Mean surface separation between human
segmentations and M-rep segmentation -0.33cm for
the Gaussian template and 0.32cm for the locally
varying template
56Comparison using VALMET Gaussian Vs Locally
Varying Template
Rater B Vs M-rep
Rater A Vs M-rep
57Results (Contd.)
Axial View
Coronal View
58Results (Contd.)
Axial View
Coronal View
59Results (Contd.) Error in Human Segmentation
Coronal View
Sagittal View
60Results (Contd.)
Coronal View
Sagittal View
61OVERVIEW
- Introduction
- Background
- Materials and Methods
- Results
- Conclusions and Discussion
62Analysis of the Results
- Locally varying template based segmentation
showed improvement for 65 of the cases - Achieved a greater degree of automation in the
entire segmentation process
63Analysis of the Results
Coronal View
Axial View
64Analysis of the Results
Axial View
Coronal View
65Instances of Human Intervention
Axial View
Coronal View
66Instances of Human Intervention
Axial View
Coronal View
67Future Directions
- More than three filter types to define the
template - Statistical evaluation of variation of profiles
along the boundary - Templates based on weighted profiles, responses
which are neighbor dependent - Higher density m-rep model