Radiological examination frequency and collective effective dose from pediatric computed tomography (CT) in Sudan BY: Mohammed Ibrahim Abdoelgabbar Mohammed B. Sc. (mathematics and Physics) 2006 / University of Khartoum A thesis Submitted in partial fulfillment of the requirements for the degree of Master of Science in Physics Supervisor: Dr. Ibrahim Idris Suliman Department of Physics Faculty of Science University of Khartoum August 2011
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Radiological examination frequency and collective effective dose from pediatric computed tomography (CT) in Sudan
BY:
Mohammed Ibrahim Abdoelgabbar Mohammed
B. Sc. (mathematics and Physics) 2006 / University of Khartoum
A thesis Submitted in partial fulfillment of the requirements for the degree of Master of Science in Physics
Supervisor: Dr. Ibrahim Idris Suliman
Department of Physics
Faculty of Science
University of Khartoum
August 2011
Dedication
To
My family: mother, father, brother, and sisters
All my teachers who guided me
My sincere friends
My colleagues
And every one who love me
Acknowledgment
I would like to express my grateful thanks to Dr Ibrahim Idris suliman the head of SSDL –radiation safety institute – Sudan atomic energy commission for his guidance, help, advising, directing, and carefully review of the research.
And I would like to thank Dr.abdoelmonem Adam for his great help, also I would thank the staff of all CT departments that I had visit to do my research survey for their kind cooperation.
It is a great pleasure to acknowledge all those people who had given me tremendous help and support in completing this study
Finally, I am especially grateful to my family for their support though all my life stage
المستخلص
في انتباه خاص من ناحية الوقاية من االشعاعاستخدام االشعة المؤينة يحتاج التصوير الطبي لالطفال ب
استخدام االشعة المقطعية في التصوير الطبي يتسبب في ارتفاع قيمة .ية اصابتهم بالسرطان احتمال
. ومحاولة تقليلها ما امكن ذلك الجرعاتالجرعات االشعاعية للمرضي والجمهور لذلك البد من تقدير تلك
هذه الدراسة الي حساب العدد الكلي لفحوصات االشعة المقطعية لالطفال خالل السنة باالضافة الي تهدف
لحساب الجرعة الجماعية . شعة المقطعية لالطفالحساب الجرعة الجماعية الفعالة الناتجة عن استخدام اال
اء مسح علي عشر مستشفيات لحصر عدد الفحوصات التي تجري خالل والعدد السنوي للفحوصات تم اجر
دراسة سابقة لحساب من الجرعة الفعالة الناتجة عن تلك الفحوصات تم الحصول عليها.اليوم
حساب ومن ثم تم .لفحوصات االشعة المقطعية لالطفال الجرعات الفعالة
الجرعة الجماعية الفعالة الناتجة عن فحوصات لفعالة وعدد الفحوصات السنوي و آانت الجرعة الجماعية ا
حيث آانت البطن تكرارا آان فحص اعلي الفحوصات )man.Sv196(المقطعية لالطفال هي االشعة
عن فحص البطن الذي آانت نسبته للجرعة الكلية نتجت فعالةاعلي جرعة جماعية ) .32(%نسبته المئوية
)%49( .
وهي الجرعة التي حددتها المصادر العلمية man.Sv500عن بكثير تقل man.Sv196هذه الجرعة
Abstract
The pediatric medical imaging using ionizing radiation requires special attention in terms of
radiation protection for risk of cancer. The use of CT in medical imaging cause the high value of
radiation doses to patients and the public for that to be a measure of dose and try to decrease as
much as possible. The study aimed to assess the frequency and collective effective dose for
populations from pediatric CT procedures in Sudan. The annual collective dose form pediatric
CT examination had been calculated by a survey done at 10 hospitals providing data of
examination frequency per month. The annual examination frequency and annual collective
effective dose had been calculated by multiplying the effective dose of each examination by the
frequency. The results were calculated and discussed providing that the annual collective
effective dose from pediatric CT examinations is (169 man.Sv). The highest percentage
examination frequency was for abdomen (32%).The highest percentage contribution to total to
the total dose from pediatric CT examination was for abdomen (49%).The calculated annual
examination frequency and annual collective effective dose had been compared with the results
of literature and other studies to evaluate the estimated values.
This value of dose (196 man.Sv) far less than (500man.Sv) the dose which is set by the scientific
Computed tomography (CT) is a medical imaging modality employing tomography used for
diagnostic and treatment procedures. Digital geometry processing is used to generate a three-
dimensional image of the inside of an object from a large series of two-dimensional X-ray
images taken around a single axis of rotation. Computed tomography was originally known
as the "EMI scan" as it was developed at a research branch of EMI, a company best known
today for its music and recording business. It was later known as computed axial tomography
(CT scan) and body section CT produces a volume of data which can be manipulated,
through a process known as "windowing", in order to demonstrate various bodily structures
based on their ability to block the X-ray beam. Although historically the images generated
were in the axial or transverse plane, orthogonal to the long axis of the body, modern
scanners allow this volume of data to be reformatted in various planes or even as volumetric
(3D) representations of structures. Although most common in medicine, CT is also used in
other fields such as nondestructive materials testing. The use of CT with children has grown
substantially in the past few years. There is also an increased interest in keeping the radiation
dose to children from CT as low as is clinically practical. This article reviews the physical
aspects of CT . Separately and how CT is used in the context of CT to provide the practical
insight necessary to approach this issue. Understanding radiation dosimetry and its potential
for deleterious health effects, having knowledge of the magnitude of the effective dose and
the dose to specific organs from CT, and considering the role of CT in the context of CT will
allow the reader to reduce the radiation dose to the patient without compromising the quality
of the patient’s care. A CT or CAT scan is a diagnostic imaging procedure that uses a
combination of x-rays and computer technology to produce cross-sectional images (often
called "slices"), both horizontally and vertically, of the body [1]. A CT scan shows detailed
images of any part of the body, including the bones, muscles, fat, and organs. CT scans are
more detailed than general x-rays. CT scans also minimize exposure to radiation. In
conventional x-rays, a beam of energy is aimed at the body part being studied. A plate behind
the body part captures the variations of the energy beam after it passes through skin, bone,
muscle, and other tissue. While much information can be obtained from a regular x-ray, a lot
of detail about internal organs and other structures is not available. In computed tomography
CT, the x-ray beam moves in a circle around the body. This allows many different views of
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the same organ or structure, and provides much greater detail. The x-ray information is sent
to a computer that interprets the x-ray data and displays it in 2-dimensional form on a
monitor. While many images are taken during a CT scan, in many cases, the patient receives
less radiation exposure than with a single standard x-ray. CT scans may be done with or
without contrast. "Contrast" refers to a substance taken by mouth or injected into an
intravenous (IV) line that causes the particular organ or tissue under study to be seen more
clearly [1]. Contrast examinations may require you to fast for a certain period of time before
the procedure. Your physician will notify you of this prior to the procedure. CT scans may be
performed to help diagnose tumors, investigate internal bleeding, or check for other internal
injuries or damage. Computed tomography has a wide range of uses in medicine. It can show
cancers in different parts of the body, helping doctors’ measure its spread and apply targeted
treatments. Any abnormal growth or structures such as cysts, tumors, abscesses, kidney or
bladder stones, can be detected as well. CT scans can also be used to help assess areas
of trauma and identify any structural damage. In all cases, computed tomography can provide
for a detailed examination of the body to develop the best and most accurate treatment for the
patient. Computed tomography requires more radiation than traditional x-rays, and the more
detailed and complex the CT scan is, the more radiation exposure the patient receives.
However, for most patients, the risk of allowing a problem like cancer to continue unchecked
is worse than the risks from radiation exposure. Also, the quality of computed tomography is
much higher than a traditional x-ray. It allows for fast identification of things like internal
bleeding, which a traditional x-ray would not be able to detect. Some other problems with
computed tomography are the associated costs, but as technology advance the cost of these
procedures decreases [1].
While computed tomography can provide a lot of important information to a medical team,
CT scanning should be justified. The radiation it involves precludes pregnant women and the
dye that is injected requires nursing mothers to take precautions. Children should not get
them unless it is medically necessary, and even then, repeated exposure should be avoided as
much as possible. Some people cannot physically fit in the machines either, so
accommodations have to be made to aid these people. Also, some areas being scanned could
also be examined on an MRI, or magnetic resonance imaging, and thus are not worth the risk
of computed tomography scan. [1].
1.2 Biological effects of radiations The human body is made up of many organs, and each organ of the body is made up of
specialized cells. Ionizing radiation can potentially affect the normal operation of these cells.
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In this point, we will discuss the potential for biological effects and risks due to ionizing
radiation and put these potential risks into perspective when compared to other occupations
and daily activities. From the biological effects of radiation on human body, radiation effects
are generally divided into two categories [2]:
1.2.1 Stochastic effect:
Stochastic effects are those that occur by chance and consist primarily of cancer and genetic
effects. Stochastic effects often show up years after exposure. As the dose to an individual
increases, the probability that cancer or a genetic effect will also increases. However, at no
time, even for high doses, is it certain that cancer or genetic damage will result. Similarly, for
stochastic effects, there is no threshold dose below which it is relatively certain that an
adverse effect cannot occur. In addition, because stochastic effects can occur in individuals
that have not been exposed to radiation above background levels, it can never be determined
for certain that an occurrence of cancer or genetic damage was due to a specific exposure.
The severity of stochastic effects is independent of the absorbed dose. Under certain exposure
conditions, the effects may or may not occur. There is no threshold and the probability of
having the effects is proportional to the dose absorbed [2]
1.2.2 Characteristics of stochastic effects:
• Severity is independent of absorbed dose
• Threshold does not exist
• Probability of occurrence depends on absorbed dose
1.2.3 Deterministic effect:
Based on a large number of experiments involving animals and other researches, further
supplemented by theoretical studies, it was discovered that severity of certain effects on
human beings will increase with increasing doses. There exists a certain level, the
"threshold", below which the effect will be absent. This kind of effects is called
"deterministic effects".
1.2.4 Characteristics of deterministic effects:
• Damage depends on absorbed dose
• Threshold exists
The following are possible effects of radiation on cells:
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Cells are undamaged by the dose
Ionization may form chemically active substances which in some cases alter the structure of
the cells. These alterations may be the same as those changes that occur naturally in the cell
and may have no negative effect [3].
Cells are damaged, repair the damage and operate normally
Some ionizing events produce substances not normally found in the cell. These can lead to a
breakdown of the cell structure and its components. Cells can repair the damage if it is
limited. Even damage to the chromosomes is usually repaired. Many thousands of
chromosome aberrations (changes) occur constantly in our bodies. We have effective
mechanisms to repair these changes.
Cells are damaged, repair the damage and operate abnormally
If a damaged cell needs to perform a function before it has had time to repair itself, it will
either be unable to perform the repair function or perform the function incorrectly or
incompletely. The result may be cells that cannot perform their normal functions or that now
are damaging to other cells. These altered cells may be unable to reproduce themselves or
may reproduce at an uncontrolled rate. Such cells can be the underlying causes of cancers [3].
Cells die as a result of the damage
If a cell is extensively damaged by radiation, or damaged in such a way that reproduction is
affected, the cell may die. Radiation damage to cells may depend on how sensitive the cells
are to radiation. All cells are not equally sensitive to radiation damage. In general, cells
which divide rapidly and/or are relatively non-specialized tend to show effects at lower doses
of radiation then those which are less rapidly dividing and more specialized. Examples of the
more sensitive cells are those which produce blood. This system (called the hemopoietic
system) is the most sensitive biological indicator of radiation exposure. The relative
sensitivity of different human tissues to radiation can be seen by examining the progression
of the Acute Radiation Syndrome on the following pages [3]
1.3 Principles of radiation protection:
The main objective of radiation protection (RP) is to avoid the deterministic effects by
keeping doses below the relevant threshold and to reduce the probability of stochastic effect
as much as is reasonably achievable.
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In most countries a national regulatory authority works towards ensuring a secure radiation
environment in society by setting requirements that are also based on the international
recommendations for ionizing radiation (ICRP - International Commission on Radiological
Protection) .This shall be achieved by the following requirements [4].
1.3.1 Justification:
No unnecessary use of radiation is permitted, which means that the advantages must
outweigh the disadvantages.
And also the justification is defined as: No practice or source within a practice should be
authorized unless the practice produces sufficient benefit to the exposed individuals or to
society to offset the radiation harm that it might cause; that is: unless the practice is justified,
taking into account social, economic and other relevant factors.“ In proposed and continuing
practices, the justification of practice must be such that the work uses radiation because it
gives benefit (or gain) to the exposed individuals or to society that exceeds radiological risk.
Justification in intervention provides more benefit in comparison to if there were no
intervention.[4]
1.3.2 Limit dose:
Is the normal exposure of individuals shall be restricted so that neither the total effective dose
nor the total equivalent dose to relevant organs or tissues, caused by the possible combination
of exposures from authorized practices, exceeds any relevant dose limit specified, except in
special circumstances provided for in the Standards. Dose limits shall not apply to medical
exposures from authorized practices. Each individual must be protected against risks that are
far too large through individual radiation dose limits [4].
There are different categories of dose limits for:
• Radiation workers
• Members of the public
• Trainees of radiation
• Planned special exposures; and female pregnant workers
1.3.3 Optimization:
In relation to exposures from any particular source within a practice, except for therapeutic
medical exposures, protection and safety shall be optimized in order that the magnitude of
individual doses, the number of people exposed and the likelihood of incurring exposures all
be kept as low as reasonably achievable, economic and social factors being taken into
10
account, within the restriction that the doses to individuals delivered by the source be subject
to dose constraints. Radiation doses should all be kept as low as reasonably achievable. [4]. 1.4 Objectives
1.4.1 General objective:
1. To assess public exposure to ionizing radiation from medical use, specifically from
CT procedures.
1.4.2 Specific objectives:
1. To assess the examination frequency of paediatric CT procedures.
2. To estimate the collective effective dose from pediatric CT examinations.
3. To estimate the collective effective dose from each examination and specify the
contribution to total collective effective dose from pediatric CT procedures.
1.5 Literature review
A study for assessing the frequency of examinations and contribution of each medical
imaging procedure for pediatric had been done in Germany to estimate the percentage change
in collective effective dose for pediatric in Germany [5]. A nation-wide survey of exposure
practice in pediatric CT was conducted in Germany during the period from September 2005
until May 2006 on behalf of the ministry for environmental protection, conservation and
nuclear safety. The survey was based on questionnaires that were first sent to 1640 users of
CT scanners installed in hospitals and private practices, asking for the frequencies of five
types of examinations, subdivided into five age groups. In a subsequent second survey, a
selected number of 72 users, responsible for about two thirds of annual pediatric CT
examinations reported in phase 1, were asked for detailed dose-relevant data (scanner data,
scan protocols, examination-related data and examination frequencies)[5]. These data were
used for individualized dose assessment, depending on the type of scanner and age of the
patient. With return rates of 40 % in the first part and 58% in the second part of the survey,
representative results could be obtained for the five most frequent types of pediatric CT
examination. The most essential findings were: the percentage of pediatric CT examinations
was in the order of only 1% of all CT and thus much smaller than elsewhere (e.g. 6.5% for
USA). The most frequent type of examination was brain (52%), followed by chest (17%) and
entire abdomen (7%) other types of examination were quite rare (less than 5%). The age
distribution for pediatric CT examinations was almost uniform: (0 to 5 years: 40%, 6 to 10
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years: 28%, 11 to 15 years: 32%). Based on the results of this survey, proposals have been
made for diagnostic reference levels that refer to the third quartiles of the observed dose
distributions. In addition, such a way that the doses resulting from their scan protocol settings
could be benchmarked against the proposed reference dose values [5].
Brenner and Hall published an article in 2007 by which stated that up to 2% of all carcinomas
in the USA could be secondary to CT radiations [7]. Advances in science and technology
showed that the use of CT has its own indications [7]. The same protocol should be followed
in different hospitals as well. Basic principles of radiation protection should be monitored. As
much as possible, both technician and radiologist must be present during computerized
tomography for children, and MRI and ultrasound should be replaced if possible [7].
The other study had been done by Institute of Public Health in Romania for survey of
diagnostic pediatric radiology and the resulted effective dose. The purpose of their study was
to update the annual frequency of X-ray examinations and the pattern of pediatric radiology
in 2000 year in Romania [8]. Also, to assess in terms of effective dose the magnitude of
pediatric patient exposure during conventional X-ray examinations, selected by their high
frequencies or their relatively high doses delivered to patient. The annual effective doses
from all medical examinations for the average pediatric patients were: 0.85 mSv for 0 years
old , 0.53 mSv for 1 year old, 0.56 mSv for 5 years old , 0.72 mSv for 10 years old and 0.74
mSv for 15 year old. The resulting annual collective effective dose was evaluated at 872
man.Sv, with the largest contribution of pelvis and hip examinations. However, this value
could be much larger because the CT annual use increased in 2000 y up to 3.1% of total
examinations from a negligible one of 0.1% in previous survey. According to their study, the
pediatric X-ray examinations represented 12% of all medical procedures performed in 2000 y
in Romania. Current pattern of pediatric radiology shows a mean increase of CT
frequency of 3.1% of total annual X-ray procedures. The annual effective doses from
conventional X-ray procedures ranged from 0.53 mSv (age subgroup 5 y) to 0.85 mSv (new
born babies). The annual collective dose of paediatric patients from conventional X-ray
procedures was 872 manSv with the highest contribution of pelvis, hip and spine
examinations [8].
In Belgium, a study was performed to evaluate the examination protocols used for common
CT procedures of pediatric patients at different hospitals in order to determine whether
adjustments related to patient size are made in scanning parameters, and to compare patient
doses with proposed reference levels. Three pediatric hospitals and one non-pediatric hospital
participated in the study [9]. Weighted CT dose-index (CTDIw), dose–length product (DLP)
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and effective dose (E) were evaluated for three patient ages (1 year, 5 years and 10 years) and
three common procedures (brain, thorax and abdomen). CTDIw and DLP values higher than
the reference levels were found for all types of evaluated examination. E ranged from 0.4
mSv to 2.3 mSv, 1.1 mSv to 6.6 mSv, and 2.3 mSv to 19.9 mSv for brain, thorax and
abdomen examinations, respectively. All centers but one adapted their protocols as a function
of patient size. However, no common trend in the selection of protocol was observed. Some
centers divided the whole range of patient size into only two/three groups by age, while
others classified, the patients into six groups by weight. It was also observed that some
centers used the same mAs for the total range of patient sizes and decreased the pitch factor
for small children, which resulted in higher doses. They envisage the importance of careful
selection of technical scan parameters. They also conclude that, If CT parameters used for
pediatric patients are not adjusted on the basis of examination type, age and/or size of the
child, then some patients will be exposed to an unnecessarily high radiation dose during CT
examinations [9].
1.6 Thesis outlines
Chapter one:
This chapter includes the object and general introduction and the benefit of this study, and also literature review and previous study had been done on the field of the study to get more information about basic concepts and methods of assessing the public exposure , and biological effects of radiation and the radiation protection principle are mentioned in brief notes.
Chapter two:
This chapter describes the physics of computed tomography (CT) considering CT dosimetry and the units, and also the CT principles and generations and properties of each generation, and radiation physics and radiation quantities and units were reviewed in this chapter.
Chapter three:
This chapter explores the materials and methods used in this study and the survey for collecting data information about examination frequency and estimate the collective effective dose from pediatric CT.
Chapter four:
Chapter four based on the presentation of obtained results in tables and figures, and includes the discussion of the results compared with the literature and international studies.
Chapter five:
This chapter introduces the conclusion which had been figured out from this study.
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Chapter Two
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Chapter Two:
Physics of Computed Tomography
2.1 CT principles
The use of CT in children has grown substantially in the past few years. There is also an
increased interest in keeping the radiation dose to children from CT as low as is clinically
practical. In previous years there were huge number of researches and studies were done at
many countries in the world to identify the operation of each radio diagnostic modalities in
collective effective dose.
The principles of CT were first developed by Radon in 1917. Radon's treatise proved that an
image of an unknown object could be produced if one had an infinite number of projections
through the object. Although the mathematical details are beyond the scope of this text, we
can understand the basic idea behind tomographic imaging with an example taken from
radiography. With plain film imaging, the three-dimensional (3D) anatomy of the patient is
reduced to a two-dimensional (2D) projection image. The density at a given point on an
image represents the x-ray attenuation properties within the patient along a line between the
x-ray focal spot and the point on the detector corresponding to the point on the image.
Consequently, with a conventional radiograph of the patient's anatomy, information with
respect to the dimension parallel to the x-ray beam is lost [10].
A single transmission measurement through the patient made by a single detector at a given
moment in time is called a ray. A series of rays that pass through the patient at the same
orientation is called a projection or view. There are two projection geometries that have been
used in CT imaging. The more basic type is parallel beam geometry, in which all of the rays
in a projection are parallel to each other. In fan beam geometry, the rays at a given projection
angle diverge and have the appearance of a fan. All modern CT scanners incorporate fan
beam geometry in the acquisition and reconstruction process. The purpose of the CT scanner
hardware is to acquire a large number of transmission measurements through the patient at
different positions. The acquisition of a single axial CT image may involve approximately
800 rays taken at 1,000 different projection angles, for a total of approximately 800,000
transmission measurements. Before the axial acquisition of the next slice, the table that the
patient is lying on is moved slightly in the cranial- caudal direction (the "z-axis" of the
scanner), which positions a different slice of tissue in the path of the X-ray beam for the
acquisition of the next image [23].
16
In many ways CT scanning works very much like other X-ray examinations. X-rays are a
form of radiation—like light or radio waves—that can be directed at the body. Different body
parts absorb the X-rays in varying degrees. In a conventional x-ray exam, a small burst of
radiation passes through the body, recording an image on photographic film or a special
image recording plate. Bones appear white on the x-ray; soft tissue shows up in shades of
gray and air appears black. With CT scanning, numerous x-ray beams and a set of electronic
x-ray detectors rotate around the patient. At the same time, the examination table is moving
through the scanner, so that the x-ray beam follows a spiral path. A special computer program
processes this series of pictures, or slices of the body, to create two-dimensional cross-
sectional images, which are then displayed on a monitor.[10].
CT imaging is sometimes compared to looking into a loaf of bread by cutting the loaf into
thin slices. When the image slices are reassembled by computer software, the result is a very
detailed multidimensional view of the body's interior. Refinements in detector technology
allow new CT scanners to obtain multiple slices in a single rotation. These scanners, called
"multislice CT" or "multidetector CT," allow thinner slices to be obtained, resulting in more
detail of the body, in a shorter period of time.
Modern CT scanners are so fast that they can scan through large sections of the body in just a
few seconds. Such speed is beneficial for all patients especially children, the elderly and
critically ill. For some CT exams, a contrast material is used to enhance visibility in the area
of the body being studied [10].
2.2 CT generations
2.2.1 First CT Generation Data Collection:
The first commercial scanner invented by Hounsfield, was introduced in 1973. This scanner
acquired data with an x-ray beam collimated to a narrow “pencil” beam directed to a single
detector on the other side of the patient; the detector and the beam were aligned in a scanning
frame. A single projection was acquired by moving the tube and detector in a straight-line
motion (translation) on opposite sides of the patient Fig (2.1).
17
Fig (2.1)
Fig (2.1) shows the first-generation CT scanner, which used a parallel x-ray beam with
translate-rotate motion to acquire data.[10]
To acquire the next projection, the frame rotated 1°, and then translated in the other direction.
This process of translation and rotation was repeated until 180 projections were obtained. The
earliest versions required about 4.5 minutes for a single scan and thus were restricted to
regions where patient motion could be controlled (the head). Since procedures consisted of a
series of scans, procedure time was reduced somewhat by using two detectors so that two
parallel sections were acquired in one scan. Although the contrast resolution of internal
structures was unprecedented, images had poor spatial resolution and very poor z-axis
resolution ( 13-mm section thickness) Fig (2.2).
Fig (2.2)
Fig (2) shows CT image of the head obtained with an early CT scanner. The scan plane
resolution is on the order of 3 mm for a field of view of 25 cm with an 80 × 80 matrix and a
z-axis resolution of approximately 13 mm. [10].
2.2.2 Second-Generation CT Scanners:
The main impetus for improvement was in reducing scan time ultimately to the point that
regions in the trunk could be imaged. By adding detectors angularly displaced, several
18
projections could be obtained in a single translation. For example, one early design used three
detectors each displaced by 1°. Since each detector viewed the x-ray tube at a different angle,
a single translation produced three projections. Hence, the system could rotate 3° to the next
projection rather than 1° and had to make only 60 translations instead of 180 to acquire a
complete section Fig (2.3). Scan times were reduced by a factor of three. Designs of this type
had up to 53 detectors, were ultimately fast enough (tens of seconds) to permit acquisition
during a single breath hold, and thus were the first designs to permit scans of the trunk of the
body. Because rotating anode tubes could not withstand the wear and tear of rotate-translate
motion, this early design required a relatively low output stationary anode X-ray tube. The
power limits of stationary anodes for efficient heat dissipation were improved somewhat with
the use of asymmetrical focal spots (smaller in the scan plane than in the z-axis direction), but
this resulted in higher radiation doses due to poor beam restriction to the scan plane.
Nevertheless, these scanners required slower scan speeds to obtain adequate x-ray flux at the
detectors when scanning thicker patients or body parts [10].
Fig (2.3)
Fig (2.3) shows the second-generation CT scanner, which used translate-rotate motion to
acquire data. [10].
2.2.3 Third-Generation CT Scanners:
Designers realized that if a pure rotational scanning motion could be used, then it would be
possible to use higher-power, rotating anode x-ray tubes and thus improves scan speeds in
thicker body parts. One of the first designs to do so was the so-called third generation or
rotate-rotate geometry. In these scanners, the x-ray tube is collimated to a wide, fan-shaped x-
ray beam and directed toward an arc-shaped row of detectors. During scanning, the tube and
19
detector array rotate around the patient fig (4), and different projections are obtained during
rotation by pulsing the x-ray source or by sampling the detectors at a very high rate. The
number of detectors varied from 300 in early versions to over 700 in modern scanners. Since
the slam-bang translational motion was replaced with smooth rotational motion, higher-
output rotating anode x-ray tubes could be used, greatly reducing scan times. One aspect of
this geometry is that rays in a single projection are divergent rather than parallel to each
other, as in earlier designs. Beam divergence required some modification of reconstruction
algorithms, and sampling considerations required scanning an additional arc of one fan angle
beyond 180°, although most scanners rotate 360° for each scan. Nearly all current helical
scanners are based on modifications of rotate-rotate designs. Typical scan times are on the
order of a few seconds or less, and recent versions are capable of sub second scan times.
Fig (2.4)
Fig (2.4) shows the third-generation CT scanner, which acquires data by rotating both the x-
ray source with wide fan beam geometry and the detectors around the patient. Hence, the
geometry is called rotate-rotate motion. [10]
2.2.4 Fourth-Generation CT Scanners
This design evolved nearly simultaneously with third-generation scanners and also eliminated
translate-rotate motion. In this case, only the source rotates within a stationary ring of
detectors Fig (2.5).
20
Fig (2.5)
Fig (2.5) shows the fourth-generation CT scanner, which uses a stationary ring of detectors
positioned around the patient. Only the x-ray source rotates with wide fan beam geometry,
while the detectors are stationary. Hence, the geometry is called rotate-stationary motion. The
x-ray tube is positioned to rotate about the patient within the space between the patient and
the detector ring. One clever version, which is no longer produced, moved the x-ray tube out
of the detector ring and tilted the ring out of the x-ray beam in a wobbling motion as the tube
rotated. This design permitted a smaller detector ring with fewer detectors for a similar level
of performance. Early fourth-generation scanners had some 600 detectors and later versions
had up to 4,800. Within the same period, scan times of fourth-generation designs were
comparable with those of third-generation scanners. One limitation of fourth-generation
designs is less efficient use of detectors, since less than one-fourth are used at any point
during scanning. These scanners are also more susceptible to scatter artifacts than third-
generation types, since they cannot use anti scatter collimators. CT scanners of this design are
no longer commercially available except for special-purpose applications.
Until around 1990, CT technology had evolved to deliver scan plane resolutions of 1–2
lp/mm, but z-axis resolution remained poor and inter scan delay was problematic due to the
stop-start action necessary for table translation and for cable unwinding, which resulted in
longer examination times. The z-axis resolution was limited by the choice of section
thickness, which ranged from 1 to 10 mm. For thicker sections, the partial volume averaging
between different tissues led to partial volume artifacts. These artifacts were reduced to some
extent by scanning thinner sections. In addition, even though it was possible to obtain 3D
images by stacking thin sections, inaccuracy dominated due to involuntary motion from scan
to scan. The step like contours could be minimized by overlapping of CT sections at the
expense of a significant increase in radiation to the patient. Also, the conventional method of
section-by-section acquisition produced misregistration of lesions between sections due to
21
involuntary motion of anatomy in subsequent breath holds between scans. It was soon
realized that if multiple sections could be acquired in a single breath hold, a considerable
improvement in the ability to image structures in regions susceptible to physiologic motion
could result. However, this required some technological advances, which led to the
development of helical CT scanners. [10].
2.3 Radiation field quantities (radiometric)
2.3.1 Fluence
Fluence is the flux (either particle or radiative flux) integrated over time. For particles, it is defined as the total number of particles that intersect a unit area in a specific time interval of interest, and has units of m–2 (number of particles per meter squared). Fluence can also be used to describe the energy delivered per unit area [11]. Suppose dN particles pass through an infinitesimal area da. Then, the particle fluence is:
Ф = ………….. [2.1]
2.3.2 Energy Fluence:
The energy Fluence (ψ) is the quotient dR by da where dR is the radiant energy incident on a sphere of cross-sectional area da. Thus:
ψ = ……………………………. [2.2]
The unit is J/m2 [11].
2.4 Physical quantities
2.4.1 Kerma and kerma rate:
The kerma K is the quotient dEtr by dm, where dEtr is the sum of the initial kinetic energies of all the charged particles liberated by uncharged particles in a mass dm of material, thus:
K= dEtr / dm …………………………… [2.3]
The SI unit of Kerma is J/kg or Gy Gy can be used for any type of radiation. Kerma rate K: is quotient dK by dt, where dk is the increment of kerma in the time interval dt thus:
K=dK / dt …………………………… [2.4]
The unit is Jkg-1 s-1 .If the special name gray is used, the unit of kerma is (Gy/s) [11].
22
2.4.2 Absorbed dose:
Absorbed dose is a physical quantity to measure the radiation energy absorbed by unit mass of substances. Under normal circumstances, the larger the absorbed dose, the larger will be the hazard,
The absorbed dose D is the quotient dE by dm, where dE is the mean energy imparted to matter of mass dm, thus:
D = ……………………… [2.5]
The Units: RAD (Radiation Absorbed Dose) 1 rad = 100 ergs/g’ Gray (Gy) SI unit used to measure absorbed dose is the gray (Gy).1 Gy = 100 rad
2.4.3 Exposure Exposure is the quantity most commonly used to express the amount of radiation delivered to a point. The conventional unit for exposure is the roentgen (R), and the SI unit is the coulomb per kilogram of air (C/kg):
X = ……………………….. [2.6]
1 R = 2.58 x 10-4 C/kg , 1 C/kg = 3876 R
The reason exposure is such a widely used radiation quantity is that it can be readily measured. All forms of radiation measurement are based on an effect produced when the radiation interacts with a material. The specific effect used to measure exposure is the ionization in air produced by the radiation.[11]. 2.5 Radiation protection quantities:
2.5.1 Organ and tissue dose:
The mean absorbed dose in a specific tissue or organ is given by the symbol DT .It is equal to the ratio of the energy imparted, ET, of the tissue or organ thus:
DT =ET/mT ……………………. [2.7]
The mean absorbed dose in a specific tissue or organ is sometimes simply referred to as the organ dose [20]
23
2.5.2 Equivalent dose:
The equivalent dose is the absorbed dose averaged over a tissue multiplied by the appropriate radiation-weighting factor.
HT=WR*DT ……………………. [2.8]
The unit: J/kg. The special name for the unit of equivalent dose is sievert (Sv). The radiation-weighting factor WR allows for difference in the relative biological effectiveness of the incident radiation in producing stochastic effects at low doses in tissue or organ T .For x-ray energies used in diagnostic radiology, WR is taken to be unity. [11]
2.5.3 Effective dose:
The effective dose E is the sum of all equivalent doses of external and internal irradiation, absorbed by all tissues and organs, regarding weighting factors of the tissues and organs, describing whole body exposure.
wT = tissue or organ T weighting factor describing particular tissue or organ T sensibility for radiation. The unit is J/kg the special name is sievert (Sv). 2.5.4 Collective Effective dose:
It Describes radiation exposure of populations to different sources of radiation, If a measure of the radiation exposure in a population is desired, the collective effective dose can be calculated:
S = ∑ i Ei Ni ………………… [2.11]
where Ei is the mean effective dose to population subgroup i
Ni is the number of individuals in population subgroup. The Units: is J/kg the special name is (man Sv) [11].
2.6 CT dosimetry
2.6.1 CTDI:
The main dosimetric quantity used in CT is the computed tomography dose index (CTDI),
which is defined as the integral of the dose profile along a line parallel to the axis of rotation
for a single scan, divided by the nominal slice thickness [12].
24
CTDI = ∞∞ dz …………………. [2.12]
where: D (z) = the radiation dose profile along the z-axis
N = the number of tomographic sections imaged in a single axial scan. This is equal to the
number of the data channels used in particular scan. The value of N may be less than or equal
to the maximum number of data channels available on the system, and T = the width of the
tomographic section along the z-axis imaged by one data channel .In multiple – detector –row
(multi -slice) CT scanner, several detector elements may be grouped together to from one
data channel [12]. In single –detector –row (single -slice) CT, the z-axis collimation (T) is the
nominal scan width. The CTDI may be assessed free in air or in phantoms, and the
measurement may be done with ionization chambers.
In X-ray diagnostics, only parts of the human body are exposed during an examination, and
due to the relatively low energy of photons, the energy deposition is very inhomogeneous.
Furthermore, different kinds of tissues and organs have different sensitivities for radiation. In
order to take these circumstances into account, The CTDI is the primary dose measurement
concept in CT. [12].
2.6.2 CTDI100
Represents the accumulated multiple scan dose at the center of a 100 mm scan and
underestimates the accumulated dose for longer scan length.
CTDI100 = dz …………………. [2.13]
In the case of CTDI100, the integration limits are 50 mm, which corresponds to the 100
mm length of the commercially available pencil ionization number. [12].
The pencil chamber of active length ℓ is not really measuring exposure (X), or air kerma, but
rather the integral of the single rotation dose profile D (z). Although the exposure (or air
kerma) Meter may convert the charge collected into an apparent exposure reading in
roentgens (R) (or air kerma reading in milligray [mGy]), the measured value, called the
“meter reading,” actually Represents the average exposure (or air kerma) over the chamber
length ℓ, That is:
25
Meter reading = ℓ ℓ/
ℓ/ dz = .ℓ ℓ/
ℓ/ dz …………….. [2.14]
where f is the f-factor (exposure-to-dose conversion factor, D = f · X).
The dose distribution within the body cross section imparted by a CT scan is much more
homogeneous than that imparted by radiography, but is still somewhat larger near the skin
than in the body center.[12].
2.6.3 Weighted CTDIw
The CTDI varies across the field of view (FOV). For example, for body CT imaging, the
CTDI Is typically a factor or two higher at the surface than at the center of the FOV. The
average CTDI across the FOV is estimated by the Weighted CTDI (CTDIw) where:
CTDIw = CTDI100, center + CDTI 100, edge …………… [2.15]
The values of 1/3 and 2/3 approximate the relative areas represented by the center and edge
values, The CTDIw is a useful indicator of scanner radiation output for a specific kVp , and
also represents the average absorbed radiation dose over the x and y directions at the center
of the scan from a series of axial scans.[12].
2.6.4 Normalized weighted CTDI
nCTDIw is the normalized CTDIw per radiographic exposure (mGy(mAs)-1) in the head or
body phantom for the setting of nominal slice thickness and applied potential used for an
examination .nCTDIw is determined for a single slice as in serial scanning.
nCDTIw = ………………. [2.16]
Where C is the tube current x the exposure time (mAs) for single in serial (axial) scanning or
per rotation in helical scanning [12].
2.6.5 Volume CTDIvol
To represent dose for a specific scan protocol, which almost always involves a series of
scans, it is essential to take into account any gaps or overlaps between the x-ray beams from
consecutive Rotations of the x-ray source. This is accomplished with use of a dose descriptor
known as the Volume CTDIw or (CTDIvol), which:
CTDIvol = CTDIvol …………… [2.17]
where I is the table increment per axial scan (mm).Since pitch is the ratio of the table travel
per rotation (I) to the total nominal beam width (N×T)
26
Pitch = ………………… [2.18]
Pitch: was defined as the ratio of the table traveled per x-ray rotation tube to the slice width
(which was typically, but not always equal to the beam collimation. A pitch less than 1.0
indicates overlap of radiation beams, and pitch greater than 1.0 indicates gaps between the
radiation beams.
CTDIvol = × CTDI w……….. [2.19]
The CTDIvol provides a single CT dose parameter, based on a directly and easily measured
quantity, which represents the average dose within the scan volume for a standardized
(CTDI) Phantom. The SI units are milligray (mGy).
CTDIvol is a useful indicator of the dose to a standardized phantom for a specific exam
protocol, because it takes into account protocol-specific information such as pitch. Its value
may be displayed prospectively on the console of newer CT scanners, although it may be
mislabeled on some systems as CTDIw[12].
2.6.6 Dose- length product (DLP):
Dose Length Product is a measure of the dose of ionizing radiation that is incident on patients
in X-ray computed tomography To better represent the overall energy delivered by a given
scan protocol, the absorbed dose can be integrated along the scan length to compute the
examinations of the chest and upper abdomen contributed to approximately 73.2% of the
collective dose from all CT examinations. It was estimated that in Japan, approximately 29.9
million patients undergo CT annually, the study was done for the patient in the age range of
(0-19)year and the estimated annual collective effective dose in Japan was 277.4 *103man. Sv
[13], while as the estimated collective dose in Sudan is (1500 man.Sv) according to this
study.The annual effective dose per person for Japan was estimated to be 2.20 mSv. The
data-sheets were sent to all 126 hospitals and randomly selected 14 (15%) of 94 clinics in
Gunma prefecture which had CT scanner(s), along with CT scan protocols for each
institution surveyed. Age and sex specific patterns of CT examination and factors, which
were responsible for the variation in radiation exposure, were determined. The following
46
table shows the estimated annual number of CT examinations and collective dose in Japan.
We see that the annual collective dose in Japan is very high in comparison with collective
doses in Sudan because of the huge number of the CT devices in Japan. [13]
Table (4.4) shows the estimated annual number of CT examinations and collective dose in
Japan.
CT examination Annual number of CT
examination*106
Annual collective dose
(man.Sv)
Head 9.1 23600
Face 1.4 2800
Neck 10.1 265
.Chest 12.5 120000
Abdomen 6.2 52200
Total 39.3 225100
47
Table(4.5) : Comparison of collective doses to sudanese population with those reported in
other countries .The table shows that the collective dose in Japan is highest with (225100
man.Sv) followed by the collective dose in Sudan with (162man.Sv) and then the collective
dose in Yazd with only (30) man.Sv. [14]
Table (4.5) shows the comparison of collective doses per exam for Yazd , Japan and Sudan
examination collective dose in Japan
2010 (man.Sv)
Collective dose
(man.Sv) Yazd
(2006)
Collective dose (man.Sv)
of this study (Sudan )
Head 23600 9 28
Face 2800 - -
Neck 26500 1 3
Chest 120000 5 24
Abdomen 52200 5 82
Pelvis - 5 5
L.spine - 2 20
Total 225100 30 162
48
Chapter five
Conclusion
49
Chapter Five:
5.1 CONCLUSION
The annual collective effective dose from pediatric CT procedures has been calculated by using results of the survey of the frequency of 8 types of examinations from 10 hospitals and the data of the effective dose per examination from previous study on radiation dose from such examinations. The total annual collective effective dose from all CT procedures performed in the Sudan in both public and private hospitals is calculated to be (169 man.Sv). The study showed that the annual collective dose to population from pediatric CT examinations in Sudan are low compared to doses from such procedures to other nations in particular developed countries. The difference in the development of healthcare systems and usage of CT scanners in medical imaging were taken into consideration. The lowering in estimated collective dose reduces to the lower number of CT scanners and frequency of CT examinations. From comparison with international published data the annual collective dose from CT procedure in Sudan is much lower but it should be surveyed in specific time intervals because of the rapid increase of the number of CT scanners and the use in medical imaging that can be clearly observed from the survey results that most of the CT scanners installed in recent years and most of hospitals and medical centers going to have CT scanners in the near future.
50
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