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Honours Year Project Report
Detection of Femur Fractures in X-ray
Images using Intensity Gradient Maps
By
Lim Sher Ee Dennis
Department of Computer Engineering
School Of Computing
National University of Singapore
2003/2004
ii
Honours Year Project Report
Detection of Femur Fractures in X-ray
Images using Intensity Gradient Maps
By
Lim Sher Ee Dennis
Department of Computer Engineering
School Of Computing
National University of Singapore
2003/2004
Project No: H40340
Advisor: A/Prof Leow Wee Kheng
Deliverables:
Report: 1 Volume
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Abstract
Doctors inspect numerous x-ray images everyday. However, with only a low percentage
of the images actually showing fractures, the task is very tedious and exhausting, possibly
resulting in inaccurate diagnosis by the doctors. With the advent of digital x-rays, we are
now able to use computers to ease the doctors’ workload. An automated fracture
detection technique would be able to screen out all obvious cases, thus leaving only the
doubtful cases and final diagnosis for the doctors to handle. We implemented a method to
detect fractures from x-ray images using intensity gradient maps. With the focus of our
work being femur fractures, we adaptively segment the femur images into overlapping
regions. The intensity gradient direction of each region is ascertained and an intensity
gradient map is generated. The intensity gradient maps are then converted into difference
maps and then classified with a SVM classifier, with positive results. The results
complement existing algorithms, resulting in a multi-classifier that produces high fracture
detection rate and classification accuracy.
Subject Descriptors
I.4.7 Feature Measurement
I.4.9 Applications
Keywords:
Fracture detection, intensity gradient maps, adaptive sampling, classification
Implementation software and hardware
Intel Pentium 4 desktop PC, Windows XP Professional, Matlab 6.5r13
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Acknowledgements
First and foremost, I would like to thank my supervisor, A/Prof Leow Wee Kheng, for his
support and help throughout the course of the project. His sound advice and excellent
suggestions allowed me to get through quite a few tight patches. His knowledge of the
subject at hand and innovative ideas on how to tackle problems are truly astounding
Next, I would like to thank Chen Ying for his sound guidance and help on matters of
implementation. Over the course of the project, I have troubled him numerous times with
my problems, and he has always been patient and always tried to help to the best of his
abilities.
I would also like to thank my fellow students who are working on the same main project.
Our discussions together with the professor about our research have been most
informative and the sharing of knowledge has indeed increased my knowledge on the
subject.
Next on the list are my friends in SoC. Some I have known for years, others for just a few
months. The fun and laughter that we shared has helped me this stressful period.
Last but not least, I would like to thank my girlfriend for all her support. I also thank her
for her understanding of the long periods of time when I was half buried in code and
paper.
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Table of Contents ABSTRACT.....................................................................................................................III
ACKNOWLEDGEMENTS ...........................................................................................IV
LIST OF FIGURES ...................................................................................................... VII
LIST OF TABLES .......................................................................................................VIII
CHAPTER 1: INTRODUCTION.................................................................................... 1
1.1 MOTIVATION.............................................................................................................. 1
1.2 STRUCTURE OF FEMUR............................................................................................... 2
1.2.1 The Upper Extremity (proximal extremity)........................................................ 3
1.2.1.1 The Head (caput femoris) ............................................................................... 3
1.2.1.2 The Neck (collum femoris) .............................................................................. 3
1.2.1.3 The Trochanters .............................................................................................. 4
1.2.2 The Trabeculae .................................................................................................. 4
1.3 BACKGROUND............................................................................................................ 5
1.4 RESEARCH OBJECTIVES ............................................................................................. 6
1.4.1 Analysis of femur x-ray ...................................................................................... 7
1.5 CONTRIBUTIONS TO RESEARCH .................................................................................. 8
1.6 ORGANIZATION OF REPORT........................................................................................ 9
CHAPTER 2: RELATED WORK ................................................................................ 10
2.1 OSTEOPOROSIS......................................................................................................... 10
2. 2 FRACTURE DETECTION ............................................................................................ 10
CHAPTER 3: FEATURE EXTRACTION .................................................................. 11
3.1 OVERVIEW................................................................................................................ 11
3.1.1 Noise Removal ................................................................................................. 11
3.1.2 Adaptive Sampling (Yap et al, 2003) ............................................................... 12
3.1.3 Extraction of intensity gradient direction from a sub-region .......................... 15
3.1.4 Compilation of Intensity Gradient Maps ......................................................... 16
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3.2 IMPLEMENTATION DETAILS. ..................................................................................... 19
3.2.1 Median Filtering .............................................................................................. 19
3.2.2 Adaptive Sampling (Yap et al. 2003) ............................................................... 19
3.2.3 Extraction of intensity gradient direction from a sub-region .......................... 20
3.2.4 Compilation of Intensity Gradient Maps ......................................................... 22
CHAPTER 4: CLASSIFICATION ............................................................................... 23
4.1 CONVERT IG MAPS TO DIFFERENCE MAPS ................................................................ 23
4.2 NAÏVE BAYES CLASSIFIER ....................................................................................... 24
4.3 SVM CLASSIFIER ..................................................................................................... 26
CHAPTER 5: RESULTS ............................................................................................... 28
5.1 RESULTS FROM NAÏVE BAYES CLASSIFIER................................................................ 28
5.1.1 Left femur results with Bayes classifier. .......................................................... 28
5.1.2 Right femur results with Bayes classifier......................................................... 30
5.2 RESULTS FROM SVM CLASSIFIER............................................................................. 31
5.2.1 Left femur results with SVM classifier. ............................................................ 32
5.2.2 Right femur results with SVM classifier........................................................... 33
5.3 COMPARISON OF RESULTS FROM BOTH CLASSIFIERS................................................. 34
5.4 RESULTS FROM EXISTING CLASSIFIERS ..................................................................... 34
5.5 COMBINING CLASSIFIERS ......................................................................................... 35
5.6 PREVIOUSLY UNDETECTED FRACTURES FOUND BY INTENSITY-BASED APPROACH .... 36
5.7 PRESENTLY STILL UNDETECTED FRACTURES. ........................................................... 37
CHAPTER 6: FUTURE WORKS & CONCLUSION ................................................ 39
6.1 FUTURE WORKS....................................................................................................... 39
6.1.1 Improve Method for extraction of intensity gradient direction ....................... 39
6.1.2 Development of more complex methods of combining the classifiers ............. 39
6.1.3 Research into new techniques for fracture detection....................................... 39
6.2 CONCLUSION............................................................................................................ 40
REFERENCES................................................................................................................ 41
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List of Figures Fig 1.1: The femur bone (left) and a close up of the upper
extremity (right) …………………………………………………………………………. 2
Fig 1.2: Neck-Shaft Angle ………………………………………………………………. 3
Fig 1.3: X-ray image (left) and diagram (right) showing the
trabeculae in the upper extremity ……………………………………………………….. 5
Fig 1.4: 2 x-ray images showing the consistency of intensity
changes across images …………………………………………………………………... 7
Fig 3.1: Algorithm flow diagram for feature extraction phase ………………………….11
Fig 3.2: A simple example of how noise could cause errors
in our algorithm ………………………………………………………………………….12
Fig 3.3: Examples of femur x-ray images, showing the variations
in shape and size ………………………………………………………………………..13
Fig 3.4: Results of adaptive sampling ………………………………………………….. 14
Fig 3.5: Healthy Femur Intensity Gradient Maps ……………………………………… 17
Fig 3.6: Fractured Femur Intensity Gradient Maps ……………………………………. 18
Fig 3.7: The diagrams above show the directions of the intensity
gradient. ………………………………………………………………………………... 21
Fig 5.1: Graph showing classification accuracy vs. number of principal
components …………………………………………………………………………….. 29
Fig 5.2: Graph showing fracture detection rate vs. number of principal
components …………………………………………………………………………….. 29
Fig 5.3: Graph showing classification accuracy vs. number of principal
components …………………………………………………………………………….. 30
Fig 5.4: Graph showing fracture detection rate vs. number of principal
components …………………………………………………………………………….. 31
Fig 5.5: Fracture that is only detected by intensity-based approach……………………. 37
Fig 5.6: Example of a difficult fracture to detect……………………………………….. 38
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List of Tables Table 4.1: table showing the a priori probabilities and the number of principal
components used in this project ……………………………………………………….. 26
Table 4.2: Table showing the parameters used by the SVM classifier………………… 27
Table 5.1: Table showing left side results using different parameters…………………. 32
Table 5.2: Table showing right side results using different parameters. ………………. 33
Table 5.3: comparison of the 2 classifiers ……………………………………………... 34
Table 5.4: results from previous work …………………………………………………. 34
Table 5.5: Table showing some of the best results from combining the classifiers …….36
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Chapter 1: Introduction
1.1 Motivation
Osteoporosis is an ailment which is rated by the World Health Organisation as the second
greatest healthcare problem in the world, with 13 percent of all men and about 40 percent
of all women possibly suffering from an osteoporotic fracture. Everyday, doctors visually
inspect numerous hip x-ray images for signs of fracture. The actual numbers are daunting:
the number of hip fractures occurring due to osteoporosis alone was 1.7 million
worldwide in 1990 and this is expected to rise to 6.3 million by 2050 (International
Osteoporosis Foundation, 2002). However, as the above figures account only for a small
portion of all the x-ray images taken, we can see that the task quickly becomes tiring and
judgement errors may occur due to fatigue. With increasing life expectancy and
population increase, the doctors’ job can only become more daunting.
At the Singapore General Hospital, the doctors diagnose about 350 cases of hip fractures
annually. Statistics have shown that these fractured cases only take up approximately 11
percent of all the hip x-rays taken. For each x-ray, the doctors conduct two rounds of
visual examination before making a diagnosis. They make their diagnosis based on
certain rules which involve the shape, geometry and texture of the femur x-ray. So you
can see that the entire process is rather time-consuming and taxing on the doctors. It has
been found that due to fatigue, a doctor may misdiagnose a fracture. This could have
serious implications for the patient.
To help doctors with their task, we can employ a computer to take over some of the work
a doctor has to do. This is possible due to the advent of digital x-ray technology, which
opens up new possibilities in the storage, retrieval and analysis of x-ray images.
Computers are unaffected by fatigue and can thus maintain a high level of efficiency
indefinitely. They can also perform the fracture detection process faster, thus saving time.
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However, while a computer cannot totally supplant the experience and professional
knowledge of doctors, it can act as an aide. It can pre-screen all the images and classify
the more obvious cases, leaving the doctors with only the second examination and
possibly some of the less obvious cases which the program cannot classify accurately.
This will help alleviate some of the burden on the doctors.
Computer techniques that can detect fractures from x-rays are now available, but before
we go into more detail about them, we shall first have an overview of the structure of the
femur, which is the bone on which the fracture detection techniques have been focusing
on.
1.2 Structure of Femur
The femur is the longest and strongest bone in the skeleton. It is almost cylindrical in the
greater part of its extent. The femur, like other long bones, is divisible into a body and
two extremities. For our research, we shall focus on the upper extremity.
Fig 1.1: The femur bone (left) and a close up of the upper extremity (right)
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1.2.1 The Upper Extremity (proximal extremity).
The upper extremity presents for examination a head, a neck, a greater and a lesser
trochanter. See figure 1.1 for an illustration
1.2.1.1 The Head (caput femoris)
The head is globular and forms a hemisphere. It is directed upward and a little forward,
with the greater part of its convexity being above and in front. Its surface is smooth,
coated with cartilage in the fresh state, except over an ovoid depression, the fovea capitis
femoris, which is situated a little below and behind the center of the head. This is where
the ligament is attached to.
1.2.1.2 The Neck (collum femoris)
The neck is a flattened pyramidal process of bone, which connects the head with the body.
In an adult, the neck forms an angle of about 125° with the body. This angle is known as
the neck-shaft angle. In figure 1.2, the neck-shaft angle is represented by θ.
Fig 1.2: Neck-Shaft Angle
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1.2.1.3 The Trochanters
The trochanters are prominent processes which afford leverage to the muscles that rotate
the thigh on its axis. There are two of them, the greater and the lesser.
The Greater Trochanter (trochanter major) is a large, irregular, quadrilateral projection
which is situated at the junction of the neck with the upper part of the body. It is directed
a little lateralward and backward, and, in the adult, is about 1 cm. lower than the head. It
has two surfaces and four borders.
The Lesser Trochanter (trochanter minor) is a conical projection which varies in size in
different subjects; it projects from the lower and back part of the base of the neck.
1.2.2 The Trabeculae
Mathematical analysis (Koch, 1917) revealed the remarkable adaptation of the inner
structure of the bone to the mechanical requirements due to the load on the femur head
(Fig.1.3). The ability of the femur to bear the weight of the upper-body is due to two
main bundles of lines known as the trabeculae. Broadly, the trabeculae consist of the
medial (compressive) system and the lateral (tensile) system. The medial system of
trabeculae passes through the body near the lesser trochanter and spreads upwards and
outwards. The lateral system of trabeculae begins 1 inch below the lower border of the
greater trochanter, arching across the neck and ending in the lower portion of the head.
The two systems intersect at roughly right-angles at the neck. The trabeculae on all femur
bones possess the same pattern, regardless of age, shape or size.
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Fig 1.3: X-ray image (left) and diagram (right) showing the trabeculae in the upper extremity
1.2.3 The shaft and the lower extremity
The lower extremity and the shaft, also known as the body, form the rest of the femur.
The shaft is a cylindrical structure that is slightly arched, so as to be convex in front, and
concave behind. It is also known as the shaft. The lower extremity comes between the
lower part of the body and the tibia, forming the upper knee joint.
Now that we have a better understanding of the structure of the femur, we now go back to
see what techniques have been developed for x-ray fracture detection.
1.3 Background
As we mentioned in section 1.1, there exists techniques for detecting fractures from x-
rays. The first of such methods is the neck-shaft angle approach (Tian et al, 2003) which
measures the neck-shaft angle mentioned in section 1.2 in order to determine the presence
of a fracture. Another method is the texture orientation analysis approach (Yap et al,
Lateral system Medial system
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2003), which makes use of the trabeculae patterns to detect fractures. Both these methods
achieve satisfactory results individually and when combined into a multi-classifier system,
performed even better. The result for this is given in Yap et al. (2003) and proves that the
two classifiers are complementary to each other.
Although the combined classifiers showed good results, they were still unable to detect a
significant percentage of fractures. As such, another fracture detection technique is
needed to complement the two existing ones, so as to further boost the fracture detection
rate. This is one of the main motivations of this project. Also, this project as well as the
work done in Tian et al. (2003) and Yap et al. (2003) are part of a larger project whose
aim is to deliver a fracture detection system of high classification accuracy. Our project is
a joint venture by the School of Computing (SoC) and the Singapore General Hospital
(SGH). It is also supported by a grant from the National Medical Research Council
(NMRC/0759/2003). A provisional patent has also been filed for the approaches in Tian
et al (2003), Yap et al (2003) as well as this project.
1.4 Research Objectives
The main objective of this project is to create a fracture detection technique which would
help improve the overall classification accuracy of the main x-ray fracture detection
program. This can be split into two smaller objectives, which are:
1. Development of an algorithm for femur fracture detection in x-ray images
based on intensity gradient direction, which is complementary to existing
fracture detection algorithms.
2. Combining this algorithm with the existing algorithms to improve overall
performance.
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The intensity gradient direction of a region is defined as the direction with the largest
gradient magnitude in the region. If we want to develop a fracture detection technique
using intensity gradient direction, we must first take a closer look at some femur x-ray
images to increase our understanding of the subject.
1.4.1 Analysis of femur x-ray
Fig 1.4: 2 x-ray images showing the consistency of intensity changes across images
From the x-ray images in figure 1.4, we can see variations of intensity within the femurs.
This is due to the differences in thickness at the difference parts of the femur. For
example the edges of the shaft are relatively brighter, while the trochanters are darker.
Also the above mentioned characteristics are highly consistent across the range of healthy
femur x-rays. While the absolute intensity values of the points vary, the relative intensity
as compared to other points on the images is quite constant. Also, the intensity gradient
direction of the same region on different images is similar as well. This shows that we
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should be able to use intensity gradient direction as a means of detecting the presence of a
fracture in an image.
Furthermore, we must also look into ways of dealing with the problem of ensuring
correspondence between images. This is necessary because femurs are naturally
occurring shape and thus will exhibit slight variations in shape and size. This needs to be
overcome.
The extracted intensity features must also be represented in such a way that it does not
lose any information about the direction of the intensity gradient. At the same time, it
must be encoded in a format that readily allows for some sort of distance measure to be
formulated, as most classifiers use distance measure to classify a piece of test data.
Next, we need to develop an algorithm that can combine with existing algorithms to
boost the performance of the system. This implies that our algorithm must be
complementary to the existing algorithms. It must be able to correctly classify those
fractures that have been missed by the previous algorithms. Also, we have to consider
different approaches to combining the classifiers so as to give the best results.
1.5 Contributions to research
In our project, we make the following contributions to research in this area and to our
main project which is x-ray fracture detection.
• We developed an algorithm which uses intensity gradient direction to classify x-
ray images.
• We developed a sound representation of directions based on unit vectors.
• We developed an intensity gradient map which can adequately portray the femur
image as a combination of intensity gradient directions.
• We developed an algorithm which is complementary to the existing algorithms.
• We explored various methods of combining classifiers to obtain the best results.
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• We were able to obtain very significant improvement in the fracture detection
results through combining our classifier with existing classifiers.
1.6 Organization of Report
After the introduction, we will continue with an overview of the related works of this
project in chapter 2. This will be followed by a detailed explanation of the project: the
feature extraction phase in chapter 3 and the classification phase in chapter 4. Next,
results obtained via the methods implemented in this project will be shown, along with
the result of combining the intensity-based method with existing classifiers. These will be
done in chapter 5. Last but not least, we discuss any further improvements that can be
done in future and conclude in chapter 6.
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Chapter 2: Related Work
2.1 Osteoporosis
One of the main causes of hip fractures is osteoporosis. Much research has been made in
this region. The main approaches were the use of fractal analysis of x-ray images
(Ruttiman, Webber and Hazeirig, 1992) and texture analysis (T. Southard, K. Southard,
1996). However, these methods detect the onset of osteoporosis by determining the bone
density of the subject and do not actually look for factures.
2. 2 Fracture detection
While the use of x-rays for fracture detection only came about in recent years, the use of
computer aid techniques for fracture detection is nothing new. These earlier works were
mostly non-visual methods. Ryder, King, Olliff and Davies (1993) analyzed acoustic
pulses as they travel along the bone to detect the presence of a fracture. Kaufman et al.
(1990) analyzed mechanical vibrations based on a neural network model, while Singh
and Chauhan (1998) measured electrical conductivity.
The first automated fracture detection technique based on x-rays was work done by Tian
et al. (2003), who used computer vision techniques to measure the neck-shaft angle. This
method was proven to be very reliable for detection of fractures where there is significant
distortion of the neck-shaft angle. Another technique developed in Yap et al. (2003) used
Gabor filters to do a texture analysis on the femur x-rays. He extracted texture orientation
features from the texture pattern left by the trabeculae on the bone to create a texture
orientation map for each image and used a naïve Bayes classifier to classify them. As was
mentioned in section 1.3, these two algorithms complement each other, so the combined
classifier consisting of the two gave higher accuracies than any single algorithm.
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Chapter 3: Feature Extraction
The first part of our implementation is the feature extraction phase, in which we extract
the intensity gradient directions from the sub-regions in each image and compile them to
form intensity gradient maps. Reasons for each step and justifications on the methods
used are presented in section 3.1 while implementation details are highlighted in section
3.2
3.1 overview
The flow of processes is shown below in figure 3.1.
Fig 3.1: Algorithm flow diagram for feature extraction phase
3.1.1 Noise Removal
The first step in the intensity feature process is noise removal. This is an important step,
because ours is an intensity-based approach and hence is very susceptible to noise. Noise
Femur Image Femur Contour Points
Noise Removal
Adaptive Sampling
Extract Intensity Gradient Direction
Compile Intensity Gradient Directions
Intensity Gradient Map
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could cause our algorithm to wrongly calculate the intensity gradient direction. For
example, let’s suppose we have a region which looks like figure 3.2, with the black circle
representing noise. The correct intensity gradient direction is represented by the green
arrow. However, our algorithm may wrongly detect the direction due to the noise. This is
represented by the red arrow. We can see that noise has the potential to cause a lot of
errors, hence ultimately diminishing the accuracy of our classifier. Another potential
cause of errors is the trabeculae, which show up as light and dark ridges in x-ray images.
These may result in some error during the intensity gradient direction extraction phase as
well.
Fig 3.2: Here’s a simple example of how noise could cause errors in our algorithm
Our solution to these problems is to apply median filtering to the images. Median
filtering will remove most noise as well as smooth the lines caused by the trabeculae.
This will help to ensure that we more accurately calculate the intensity gradient direction.
3.1.2 Adaptive Sampling (Yap et al, 2003)
The femur is a naturally-occurring shape, which means that across a sample set, there will
be slight variations in shape and size, as can be seen below in fig 3.3. This is due to
various reasons such as the age and gender of the patient. A fracture is also likely to
distort the shape from the norm. Before we can perform intensity feature extraction on
the x-ray images, we must first be able to define regions on each image that correspond to
one on another. Only then will there be a fair and accurate comparison.
13
Fig 3.3: Examples of femur x-ray images, showing the variations in shape and size
The most obvious and the easiest method of ensuring the correspondence of sub-regions
between images would be to normalise the size of the femurs on all the images, but this
will cause distortions to the images which may remove important information, thus
affecting accuracy. A slightly better method would be to fix the number of regions
column-wise and row-wise in the region of interest (ROI). For example, we can define a
bounding box around the femur and divide this into equal numbers of rows and columns
for all images. In this way, we have a form of correspondence of the sub-regions across
images. This is in fact the essence of the adaptive sampling method first developed in
Yap et al. (2003) to be described later. However, there are drawbacks to doing this: much
of the area in the bounding box is actually outside of the femur contour and hence should
14
not be considered for intensity feature extraction. The regions we obtain should all lie
within the contours of the femur image.
This problem is overcome by adaptive sampling. Adaptive sampling only designates sub-
regions in the area bounded by the femur contour, thus removing those regions not within
the contours from any further computation. It also ensures the correspondence of sub-
regions between images. Furthermore, the sub-regions are overlapped so as to improve
coverage. The final result of adaptive sampling is shown in figure 3.4
Fig 3.4: Results of adaptive sampling.
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3.1.3 Extraction of intensity gradient direction from a sub-region
After the adaptive sampling phase, we now perform extraction of the intensity gradient
direction from the sub-regions. This phase is the reason why we had to implement the
noise removal phase mentioned in section 3.1.1. In this phase, we seek to determine the
direction of the maximum intensity gradient magnitude. This is the feature with which we
classify the images.
Since the noise removal phase has removed most anomalies from the sub-region, we find
the maximum intensity gradient magnitude by looking for the point in the image which
has the greatest magnitude difference compared to the centre of the sub-region. The
direction of the intensity gradient is then determined by the position of the point and its
value compared to the value of the centre of the sub-region. Here, we shall define the
direction as going from bright to dim.
The above algorithm is in fact an approximation to the actual formula for calculating
gradient magnitude in a two-dimensional space. That formula is given as
tyxfuyuxf
yxfDtu
),(),(lim),( 21
0
−∆+∆+=
→ (3.1)
where u = [u1,u2] is the unit vector indicating direction and f(x,y) is an equation that
represents the sub-region (Green et al. 2001). In order to obtain the function f(x,y), we
can use a surface-fitting algorithm to fit a polynomial function to the intensities in the
sub-region.
The main reason why this approach was not implemented is that it requires a significant
amount of time to calculate the polynomial function. The math required to compute the
gradient also takes up a fair amount of time. With hundreds of sub-regions in a single
image, the time taken would be too much for actual usage. Also, using the approximation
yielded fairly good results. However, implementation of the actual gradient formula
16
would only improve the accuracy of the feature extraction, and hence can be considered
for future work on this subject.
3.1.4 Compilation of Intensity Gradient Maps
After obtaining the intensity gradient direction of the sub-region, we now compile them
into intensity gradient maps. The purpose of these maps is to give each sample a unique
representation in term of the intensity gradient directions in each of their sub-regions. Just
by viewing the intensity gradient maps, we can see certain patterns form. The directions
are represented by colour in the figures below. The colour wheel at the bottom left of
each table is to give a better idea of the direction. For example, red means 0◦ and cyan
represents 180◦. By using colour to represent the intensity gradient direction in each sub-
region, we provide a visual representation of the intensity gradient maps which a person
can understand easily. Looking at the colour maps, we can see with just a glance whether
there is correspondence or if a region differs from the norm.
From the healthy intensity gradient maps in figure 3.5, we can see a lot of similarities
from the three: The heads are mostly green, the left side of the shaft is mostly orange and
the greater trochanter and the right side of the shaft are rather purple. This proves our
theory that the intensity changes in a femur is consistent across all healthy images.
Next, we look at the fractured intensity gradient maps in figure 3.6. We can see some
differences as compared to the healthy ones. 73_left is deformed and the greater
trochanter is green instead of purple. The left side of the shaft for 82_left is purple and
green instead of orange. These differences are very obvious and will be picked up during
the classification phase. However, not all fractured images will show such differences.
For example, 153_left does not exhibit much difference from the healthy maps, which
could be why it is wrongly classified later.
17
Original Image Intensity Gradient Map
1_left (Healthy)
18_left (Healthy)
48_left (Healthy)
Fig 3.5: Healthy Femur Intensity Gradient Maps
18
Original Image Intensity Gradient Map
73_left (Fractured)
82_left (Fractured)
153_left (Fractured)
Fig 3.6: Fractured Femur Intensity Gradient Maps
19
3.2 Implementation details.
3.2.1 Median Filtering
Median filtering is performed on the images prior to the other phases in order to remove
any noise in the region of interest, i.e. the femur. We performed this by applying a 3x3
mask on the image and designating the value of the point at the centre of the mask to be
the median value of the points in the filter.
3.2.2 Adaptive Sampling (Yap et al. 2003)
After performing noise removal, we applied the adaptive sampling algorithm to the
region of interest. First of all, we enclose the femur in a bounding box. The edges of the
bounding box are defined by the femur contour points of the image. The size of the
bounding box is defined by the values xmax, xmin, ymax, ymin, where P is the set of contour
points and
)5.3(,),(),(|
)4.3(,),(),(|)3.3(,),(),(|)2.3(,),(),(|
minminmin
maxmaxmax
maxminmin
maxmaxmax
yyPyxPyxy
yyPyxPyxyxxPyxPyxxxxPyxPyxx
≤∈∀∧∈
≥∈∀∧∈≤∈∀∧∈≥∈∀∧∈
Next we have to define the size of each region. This is dependent on the size femur in
each x-ray image and is given by
)7.3(1
12
)6.3(1
12
minmax
minmax
⎥⎥⎦
⎥
⎢⎢⎣
⎢
++−
=
⎥⎦
⎥⎢⎣
⎢+
+−=
yy
xx
nyy
s
nxx
s
20
where nx, ny are the number of samples row-wise and column-wise respectively. By
defining Sx and Sy in this way for all the images, we ensure that the number of regions
column-wise and row-wise stays constant.
Next, we define the sub-regions in each image by creating regions of size Sx by Sy,
starting from the top-left corner which has coordinates (xmin, ymin), and checking whether
it lies entirely within the contours of the femur on the x-ray image. Only those regions
that satisfy this criterion are preserved, the rest are discarded. To generate the overlap of
the sub-regions, we advance by Sx/2 horizontally or Sy/2 vertically. In the texture
orientation approach (Yap et al, 2003), the values for nx and ny were nx = 14 and ny= 16.
This is to obtain larger sub-regions so as to have enough texture data to determine the
orientation. For our intensity gradient direction approach, we set nx = 28 and ny = 32, so
that the intensity gradient maps are more sensitive and can pick up changes that only
occur in a small area.
3.2.3 Extraction of intensity gradient direction from a sub-region
After applying adaptive sampling to the image, we now compute the point of greatest
magnitude difference to the centre of the sub-region. This is done by creating a new
matrix of the size of the sub-region, with values at each element of the matrix equal to the
value of the centre of the sub-region minus the value at that point in the sub-region.
Letting M be the matrix, and assuming an n by n sub-region:
(3.8)
Where aij is the intensity value at (i,j).
⎥⎥⎥⎥⎥⎥
⎦
⎤
⎢⎢⎢⎢⎢⎢
⎣
⎡
−
⎥⎥⎥⎥⎥⎥
⎦
⎤
⎢⎢⎢⎢⎢⎢
⎣
⎡
=
nnnnnn
center
n
n
n
centercentercentercentercenter
centercentercentercentercenter
centercentercentercentercenter
centercentercentercentercenter
aaaaaa
aaaaaaaaaa
aaaaa
aaaaa
aaaaaaaaaaaaaaa
M
...^...^
...^......^...
...^...
...^...^
...^...
...^...
...^...
4321
334333231
224232221
114131211
21
Next we compute the absolute value of each element in M and obtain the value which is
the largest. The position of this value in the matrix is used to determine the orientation of
the intensity gradient direction. This is basically the angle between the straight-up
direction and a line passing through both the centre of the sub-region and the point that
we found. After determining the orientation, we look at the sign of the value at the point
to determine the direction. A positive sign means the direction is away from the centre, a
negative sign means the direction is towards the centre. This is shown in figure 3.7.
Fig 3.7: The diagrams above show the directions of the intensity gradient. Note that we define
direction as going from a brighter zone to a darker one, hence the arrow in the top image away
from the centre, while the one in the bottom image points towards it.
Now that we have obtained the intensity gradient directions, we now compile the
intensity gradient maps.
22
3.2.4 Compilation of Intensity Gradient Maps
After obtaining the intensity gradient direction of the sub-region, we have to store it in a
format that the computer can understand. This is because the computer treats all values as
numbers, so it cannot make any sense of the data should we store the direction in degrees
or radians. For example, the computer cannot understand that 355◦ is nearer to 0◦ than 90◦.
To solve this, we used a two-dimensional unit vector to store the data. This vector is
denoted by
⎥⎥⎦
⎤
⎢⎢⎣
⎡=
ij
ijiju
θ
θ
cos
sin (3.9)
Where θ is the direction of the intensity gradient (0 degrees is defined as being directly
upwards).
Using the computed intensity gradient directions, an intensity gradient map is generated
via the combining all the various sub-regions into a single map, U = [uij]. After all the
images have been processed, the intensity gradient maps are then passed to the classifiers.
23
Chapter 4: Classification
After the completion of the feature extraction process, we can now use the data we
obtained to detect the presence of fractures in the femur x-rays. This is done via the use
of classifiers which generally predict the presence of fractures in the femur images via
probabilistic or statistical means. In this project, we experimented with two different
classifiers. The first is a naïve Bayes classifier which was also used in Yap et al. (2003).
The second is a Support Vector Machine (SVM) classifier. Both these classifiers require
training data, so a set of images was designated the training set, while the rest comprise
the test set. However, before we can perform classification, we have to reformat the
intensity gradient maps of the samples. This is because the intensity gradient direction is
stored in a two dimensional unit vector, thus making the intensity gradient map a vector
map. In order to perform classification, we need to convert this into a scalar map. This is
done by converting the intensity gradient maps into difference maps.
4.1 Convert IG maps to difference maps
A difference map is a scalar map that expresses the difference between an intensity
gradient map and a mean intensity gradient map. The mean intensity gradient map is
obtained by taking the mean of the healthy samples in the training set. The formula is
(4.1)
where n is the number of healthy samples in the training set.
By applying the above formula, we obtain the following properties:
⎪⎩
⎪⎨
⎧>
= ∑ ∑= =
−
otherwise
ncifuumij
n
k
n
kijkijkij
0
2||||1 1
1
][ ijmM =
24
• Each femur sample will vary slightly from the others and hence will contain sub-
regions which do not have a corresponding sub-region in other samples. Those
sub-regions that only appear in less than half of the samples are considered
insignificant and hence set to zero.
• The direction of a sub-region in the mean intensity gradient map is the sum of the
directions in the corresponding sub-regions in the healthy training samples.
After obtaining the mean intensity gradient map, we make use of it to obtain the
difference maps V for all the samples in both the training and test sets. The formula is
given as
⎪⎩
⎪⎨⎧
⋅−
====
otherwisemu
muifvvV
ijij
ijijijij ||1
00],[
(4.2)
The difference maps obtained will return low values at regions where the direction agrees
with that of the corresponding region in the mean intensity gradient map, and high values
should the directions disagree. Using these scalar maps, we perform classification to
detect those femurs that are fractured.
4.2 Naïve Bayes Classifier
The first of the classifiers we tried is the naïve Bayes classifier used in Yap et al. (2003).
To use this, we first need to perform PCA on the difference maps. The reason we perform
PCA is that we need to reduce the dimensionality of the data. This is because the Bayes
classifier needs to use the covariance matrix of the set of difference maps. If we use the
difference maps directly, the covariance matrix would be enormous.
After performing PCA, we now take a look at the Bayes classifier itself. A Bayes
classifier classifies sample data through the comparison of a posteriori possibilities. It
25
models the two types of femur classifications – healthy and fractured – into two clusters
which follow a Gaussian distribution. These Gaussians can each be described by two
parameters: the mean class feature vector y and the class covariance matrix C. These are
defined as
}))({(},{ TyyyyECyEy −−== (4.3)
We can then calculate the conditional probability of a feature vector y, given that it
belongs to class c. The formula is
))()(21exp(
||)2(
1)|( 1 yyCyyC
cyP T
d−−−= −
π (4.4)
However, we want to compare the a posteriori possibilities, i.e. P(healthy | y) and
P(fractured | y). By applying Bayes’ rule, we can obtain the a posteriori possibilities,
which are
(4.5)
(4.6)
where P(healthy) and P(fractured) are the a priori possibilities which can be obtained by
calculating the percentages from the femur samples and P(y) is the probability of a
feature vector being y. the values for P(healthy) and P(fractured) can be found in the table
below (figure 4.1). The number of principal components also found in figure 4.1 is the
settings for which the best results were obtained for this Bayes classifier. Later in the
results section, we will show how we obtain these values. Using equations (4.5) and (4.6),
the condition for a feature vector y to be classified as fractured works out to be
)()()|()|(
)()()|()|(
yPfracturedPfracturedyPyfracturedP
yPhealthyPhealthyyPyhealthyP
=
=
26
P(y | fractured) P(fractured) > P(y | healthy)P(healthy) (4.7)
and the condition for y to be classified as healthy becomes
P(y | healthy) P(healthy) > P(y | fractured)P(fractured) (4.8)
Left Femur Right Femur
a priori probabilities (healthy) 0.85 0.92
a priori probabilities (fractured) 0.15 0.08
No. of principal components 14 9
Table 4.1: table showing the a priori probabilities and the number of principal components used
in this project
4.3 SVM classifier
Support vector machines (SVM) were discussed in Vapnik et al. (1992) based on the
Structural Risk Minimization principle from statistical learning theory. They are a state-
of-the-art technique for classification and regression problems, and can also be applied to
clustering and principal component analysis. SVM classifiers work by remapping inputs
and then finding a decision hyper-plane. It then uses this hyper-plane to perform
classification. SVM classifiers are simple and efficient to train and use, making them
very popular amongst researchers.
The original SVM classifier was created as a linear classifier, so an optimal classification
would require linear separability of the classes. However, with femur fractures and all
fractures in general, the location of the fracture and the type of the fracture can vary in
countless ways, making it almost impossible to ensure linear separability. Fortunately,
one of the features of SVM classifiers is the use of kernel functions. Kernel functions are
27
)||||exp()( 2
2
σµ−
=xxz
basically representations of the basis function. The first SVM classifier mentioned above
used a linear function for its kernel function. For our project, we need to use a non-linear
kernel function in order to find a decision hyper-plane which can correctly classify the
femur fractures
The kernel function we used in our implementation is the radial basis function (RBF). It
has the form
(4.9)
where x is an n-dimensional vector, µ is an n-dimensional vector called the centre of the
radial basis function, ||.|| denotes Euclidean distance, and σ is the width parameter. The
RBF kernel function provided the best classification results in our tests.
The SVM classifier we used was created by Anton Schwaighofer. It is a Matlab
implementation. Some parameters that we used are listed below. The width parameter
refers to the σ from equation (4.9). The weight parameters seen below are used to deal
with the imbalance training data set. It was mentioned that only about 11 percent of all
femur x-ray samples show fractures. This is also true in our training data. Hence we
assign different levels of importance to the healthy and fractured samples to offset this
imbalance. As with the number of principal components in figure 4.1, we will explain
how we obtain the parameters below later in chapter 5.
Left Femur Samples Right Femur Samples
Width Parameter (σ) 2 8
Weight (healthy) 15 8.2
Weight (fractured) 100 100
Table 4.2: Table showing the parameters used by the SVM classifier.
Using the classifiers, we obtained the results shown in the next chapter.
28
Chapter 5: Results
For the training and testing of the classifiers, we had 324 training samples and 108 test
samples. The same training and testing sets are used for both the Bayes classifier and the
SVM classifier.
5.1 Results from naïve Bayes classifier
As we applied PCA to the difference maps to reduce the dimensionality of the data, we
need to ascertain the best number of principal components to use. This was done via trial
and error. In the following, we show the results of running the classifier using different
number of principal components. Section 5.1.1 shows the results on left femurs, while
section 5.1.2 shows the results of the right femurs. The ranges of principal components of
the two sections are chosen because they give mostly non-trivial results for the testing
images. The ranges are different for right and left femur samples because the make up of
the left and right sample sets are different.
5.1.1 Left femur results with Bayes classifier.
We present our results in two graphs. The first one plots the classification accuracy of the
classifier again the number of principal components used (figure 5.1) and the other plots
the fracture detection rate against the number of principal components (figure 5.2).
29
Fig 5.1: Graph showing classification accuracy vs. number of principal components (left)
Fig 5.2: Graph showing fracture detection rate vs. number of principal components (left)
Training Samples
Test Samples
Test Samples
Training Samples
30
We can see from the above figures that the classification accuracy for the test cases is
maximised with 13 or 14 principal components, and the fracture detection rate from 13 to
15 principal components. Hence, choosing 14 principal components is a good value for
this classifier.
5.1.2 Right femur results with Bayes classifier.
We present our results in two graphs, similar to the format in section 5.1.1. The first
graph shows the classification accuracy (figure 5.3) and the next shows the fracture
detection rate (fig 5.4).
The peak value for the classification accuracy of the test cases is at 9 principal
components. Also, fracture detection rate is highest at 7 to 9 principal components.
Therefore 9 is a good number of principal components to use for the right side femurs.
Fig 5.3: Graph showing classification accuracy vs. number of principal components (right)
Test Samples
Training Samples
31
Fig 5.4: Graph showing fracture detection rate vs. number of principal components (right)
From the above, we justified our setting of the number of principal components to 14 and
9 for the left and right femurs respectively. The actual results obtained by using this set of
parameters will be discussed together with the results from the SVM classifier later on.
5.2 Results from SVM classifier
When using the SVM classifier, the parameters we need to set are σ, the width of the
radial basis function, and the weights for the healthy and fractured training samples. We
present our findings in 2 tables, one for left images (Table 5.1) and one for right (Table
5.2). Due to the infinite number of parameters, we shall only show here the range of
parameters which gave significant results.
Test Samples
Training Samples
32
5.2.1 Left femur results with SVM classifier.
For both tables, we fix the weight of fractured samples at 100 and only change the weight
of the healthy samples. FDR means fracture detection rate, FAR is false alarm rate and
CA is classification accuracy.
Weight of healthy samples
σ 2 5 8 10 12 15 17 20
FDR 50 50 50 37.5 12.5 12.5 12.5 12.5
FAR 10.9 4.3 2.2 2.2 2.2 2.2 2.17 2.17
1
CA 83.3 88.9 90.7 88.9 85.2 85.2 85.2 85.2
FDR 100 50 50 50 50 50 50 50
FAR 80.4 6.5 4.3 4.3 2.2 2.2 2.2 2.2
2
CA 31.5 87 88.9 88.9 90.7 90.7 90.7 90.7
FDR 100 100 62.5 50 50 50 50 50
FAR 100 71.7 21.7 10.9 6.5 4.3 4.3 4.3
5
CA 14.8 38.9 75.9 83.3 87 88.9 88.9 88.9
FDR 100 100 100 75 62.5 50 50 50
FAR 100 100 60.87 30.4 19.6 8.7 6.5 4.3
7.5
CA 14.8 14.8 48.15 70.4 77.8 85.2 88.9 88.9
FDR 100 100 100 100 87.5 50 50 50
FAR 100 100 95.65 67.4 43.5 13 8.7 2.2
10
CA 14.8 14.8 18.52 42.6 61.1 81.5 85.19 90.7
FDR 100 100 100 100 100 100 87.5 12.5
FAR 100 100 100 100 100 95.65 52.17 0
20
CA 14.8 14.8 14.8 14.8 14.8 18.51 53.7 87
Table 5.1: Table showing left side results using different parameters. All numbers are percentages.
The shaded boxes denote the best results
33
5.2.2 Right femur results with SVM classifier.
Weight of healthy samples
σ 6.5 7 7.5 8 8.5 9 9.5
FDR 80 60 20 20 20 20 0
FAR 14.3 6.1 0 0 0 0 0
7
CA 85.2 90.7 92.6 92.6 92.6 92.6 90.74
FDR 80 80 80 60 20 20 20
FAR 26.5 20.4 12.2 2 0 0 0
8
CA 74.1 79.6 87 94.4 92.6 92.6 92.6
FDR 100 100 80 80 80 20 20
FAR 46.9 30.6 26.5 14.3 6.1 0 0
9
CA 57.4 72 74 85.2 92.6 92.6 92.6
FDR 100 100 100 80 80 60 20
FAR 73.5 55.1 38.78 28.6 14 2 0
10
CA 33.3 50 64.8 72.2 85.2 94.4 92.6
FDR 100 100 100 100 80 80 20
FAR 85.71 73.5 57.1 44.9 28.6 10.2 0
11
CA 22.2 33.3 48.1 59.3 72.2 88.9 92.6
FDR 100 100 100 100 100 80 0
FAR 95.9 93.8 75.5 65 44.9 22.5 0
12
CA 12.96 16.6 31.5 40.7 59.3 77.8 90.7
Table 5.2: Table showing right side results using different parameters. All numbers are
percentages. The shaded boxes denote the best results
From the results in sections 5.2.1 and 5.2.2, we can see which combinations provide the
best results. Using these as a gauge, we tweak the parameters to try to get even better
results. In the case of the right femur images, we managed to reduce the false alarm rate
to zero percent through tweaking. We end up with σ = 2, healthy weight = 15 and
fractured weight = 100 for the left femur images and σ = 8, healthy weight = 8.2 and
fractured weight = 100 for the right femur images.
34
5.3 Comparison of results from both classifiers
We combine the result of left and right femurs for each classifier and compare the overall
results with each other. The results are shown in the table in table 5.3
IG(Bayesian) IG(SVM)
Fracture detection rate 46.15% 53.85%
False alarm rate 3.15% 1.05%
Classification accuracy 90.74% 93.52%
Table 5.3: comparison of the 2 classifiers
IG(Bayesian) is the results of using the naïve Bayes classifier while IG(SVM) is that of
the SVM classifier. As we can see, the SVM classifier gave overall better results. Next
we take a look at results from previous work done by Tian et al. (2003) and Yap et al.
(2003). The table was compiled by Chen, Yap, Leow, Howe and Png (2004)
5.4 Results from existing classifiers
texture Combined NSA
Bayes SVM NSA
or
Bayes
NSA
or
SVM
Bayes
or
SVM
1 of 3 2 of 3
Fracture
detection rate
61.5% 46.2% 69.2% 76.9% 76.9% 76.9% 84.6% 61.5%
False alarm
rate
3.2% 0.0% 3.2% 3.2% 6.3% 3.2% 6.3% 0.0%
Classification
accuracy
92.6% 93.5% 93.5% 94.4% 91.7% 94.4% 92.6% 95.4%
Table 5.4: results from previous work
35
Comparing the results of using the SVM classifier on the intensity gradient maps with the
neck-shaft angle (NSA) and texture results (Table 5.4), we can see that our intensity-
based method fares no worse, attaining a classification accuracy of 93.5% which equals
that of the texture methods. While our method attained a lower fracture detection rate
than the NSA and texture (SVM) methods, its false alarm rate is lower than theirs.
However this is not the main objective of this project. Our aim is to create a fracture
detection technique which can complement the existing techniques to increase overall
fracture detection rate and classification accuracy.
5.5 Combining Classifiers
With two classifiers developed in this project and three from previous work, we have five
classifiers with which to try and combine. There are various methods that can be used to
combine the results, ranging from simple schemes where a femur is declared fractured as
long as one of the classifiers classify it as such, to more complex schemes that use
penalties and other factors to classify samples. As such combination schemes are an area
of research by themselves; we leave them for future work. In this project, we try various
simple combination methods to see if we can improve on the results of the previous
classifiers, and hence meet one of our main objectives.
As there are many possible ways to combine 5 classifiers, we present a few that have
produced significant results. Shown below in Table 5.5 are some of the best results
obtained from the various possible combinations.
36
1 of 2 [IG(SVM) +
texture(Bayes)]
1 of 3 [IG(SVM) +
texture(Bayes) +
texture (SVM)]
2 of 4 [IG(SVM) +
NSA +
texture(Bayes) +
texture (SVM)]
Fracture detection
rate
84.62% 92.31% 76.92%
False alarm rate 1.05% 4.21% 0.0%
Classification
accuracy
97.22% 95.37% 97.22%
Table 5.5: Table showing some of the best results from combining the classifiers
As can be seen from the table, the first two schemes produced results which are a great
improvement over the previous combined results shown in table 5.4. The first method
which is a combination of IG(SVM) and texture(Bayes), produced a classification
accuracy that outperforms the previous best result by almost two percent. Also, the
second scheme, consisting of IG(SVM), texture(Bayes) and texture (SVM), improved
fracture detection rate by eight percent. This combination will most likely be used for a
field test of the x-ray fracture detection project, barring any new discoveries in the near
future. Lastly, the 2 out of 4 scheme consisting of IG(SVM), NSA, texture(Bayes) and
texture (SVM) shows significant improvement over the previous 2 out of 3 scheme,
outperforming it in both fracture detection and classification accuracy.
From the results above, we have proven that our intensity-based approach is indeed
complimentary to the existing algorithms. Now let’s take a look at an example of a
fracture which was not detected by previous algorithms, but detected by ours.
5.6 Previously undetected fractures found by intensity-based approach
Below in figure 5.5 is an example of an image which can so far only be detected by our
intensity gradient technique.
37
Fig 5.5: Fracture that is only detected by intensity-based approach.
The image above in figure 5.5 shows a fracture which is apparent only because there is a
sudden change in the intensity in the area. As you can see, the texture pattern in the
region remains the same, and the neck-shaft angle is similar to that of a normal bone.
Such a fracture would not be detected by any of the existing techniques, but it is quite
apparent when you view it from an intensity viewpoint. This is further proof that our
approach is complementary to the existing techniques.
However, there are still fractures which are not detected by any algorithm. Further work
would have to be carried out in this area so as to develop techniques which can correctly
classify these fractures. One example of such a fracture is shown below. (Figure 5.6)
5.7 Presently still undetected fractures.
In the image below(figure 5.6), the entire head was crushed into the neck in the direction
parallel to the orientation of the neck. This resulted in little change in the neck-shaft angle.
Also, as the trabeculae in the region run parallel to the neck as well, there is little change
in the texture orientation. As such, the existing techniques could not pick up the fracture.
38
Also, there is no major change in the intensity in the region of the fracture, causing our
intensity gradient approach to misclassify it as a healthy bone. Therefore, other
techniques will have to be created in order to detect such fractures.
Fig 5.6: Example of a difficult fracture to detect.
39
Chapter 6: Future Works & Conclusion
6.1 Future Works
6.1.1 Improve Method for extraction of intensity gradient direction
In section 3.1.3, we gave a reason for not using the more complex algorithm for the
extraction of the intensity gradient direction. While we strongly believe that program
execution time is important for a medical application of this kind, nevertheless we feel
that it is an area worthy of study. Perhaps with time spent on researching it and the proper
hardware, the time taken for executing such complex algorithms may shorten enough to
make it feasible to apply in real life. Use of a surface-fitting technique and the formula
for gradient in two dimensional space may improve the results for this project.
6.1.2 Development of more complex methods of combining the classifiers
At the time of this writing, we are still combining the classifiers using simple schemes. It
may be possible that a more complex scheme may further improve on the results we have
obtained thus far. A paper by Kittler, Hatef, Duin and Matas (1998) made comparisons of
various combination schemes. Research into this area would be of great help to the X-ray
fracture detection project on the whole.
6.1.3 Research into new techniques for fracture detection.
We have mentioned in chapter 5 that there are still some fractures which cannot be
detected using the fracture detection techniques we have now. Work will have to be done
to find new algorithms to detect such fractures.
40
6.2 Conclusion
Fractures are serious afflictions which require careful diagnosis and prompt treatment.
Femur fractures, especially those caused by osteoporosis, are even more serious than
normal, often causing people to become bedridden or even resulting in death. With the
advent of medicine and ever improving quality of life, life expectancy can only be seen to
increase as the years go by. This and the rapidly growing world population only means
that doctors will have more fractures to examine as time goes by. Despite this, it is
nonetheless important to maintain a high level of accuracy in fracture detection, and
computer-aided techniques may be the key to ensuring that patients do not get a wrong
diagnosis. The neck-shaft angle approach (Tian et al, 2003) was the first step towards
using a computer to aid doctors in their work of screening x-ray images. This was
followed by a texture analysis approach (Yap et al, 2003). These two approaches
complemented each other to raise the fracture detection rate higher than what they were
individually capable of. Our method of using the intensity gradient directions for fracture
detection is complementary to these existing algorithms and when combined with them,
improved the performance of the system even more.
In conclusion, our approach of using the intensity gradient direction to determine the
occurrence of a fracture has proven to be successful in doing so, producing results which
are equal to the results obtained by the abovementioned approaches. More importantly,
combining our intensity-based approach with the existing methods has produced a multi-
classifier system which produces results that are significantly better than what could be
obtained in the past. This shows that our project has been able to meet the objectives that
we had set out to achieve. We have developed a technique to extract intensity features
from images, taking into account problems like noise and how we were to represent the
intensity gradient direction. This technique is also complementary to existing algorithms,
as can been seen from the results. Lastly we have successfully determined that our
technique can combine with existing algorithms to improve the performance of the
combined classifiers.
41
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