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FOREWORD
I am so excited about the launch of this new edition of the in preparing to tackle radiological physics…and the American
Case Review Series. We had not, until now, been able to bring a Board of Radiology Core and Certifying exams.
comprehensive imaging physics volume to the series. We have, The approach here is unique in that it is case-based and relies
however, had the excellent Duke Review of MRI physics edi- on imaging studies to make the teaching points, as opposed to
tion that was published in 2012 and is due for another release lots of equations and diagrams and dry text. Perfect for the Case
shortly. There was a gap. Review Series.
Who better to write the content for this new volume than Welcome to the series, gentlemen!
the person whose name is associated with great teaching on the Please enjoy!
subject—Professor Walter Huda. Huda and physics go together David M. Yousem, MD, MBA
like salt and pepper. He was the best “catch” of the Case Review Professor of Radiology
Series, and we have benefited from it. He asked for the support Director of Neuroradiology
of Drs. R. Brad Abrahams and William Sensakovic to create the Russell H. Morgan Department of Radiology Science
dynamic trio.We feel certain that these stellar authors have cre- The Johns Hopkins Medical Institutions
ated an edition that will assist residents and trainees at all levels Baltimore, Maryland
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PREFACE
The incorporation of radiological physics into the American followed by a short discussion. There is an illustrated figure
Board of Radiology Core and Certifying examinations has made or artifact simulation paired with each discussion to comple-
a dramatic impact on radiology physics education. This has ment the topic. Despite the intimate relationship of physics
been a welcome change to the many clinically minded trainees and mathematics, we have attempted to limit the appearance of
and educators in the field of radiology. Despite the abundance numbers and equations in this book. Although the memoriza-
of high-quality physics resources, few authors have framed tion of certain numbers is unavoidable, most of the numbers
the discussion of physics using a case-based and image-rich provided in the following cases were added to give a “ballpark”
approach. We hope that the addition of this book to the Case idea of values or to illustrate specific examples.
Review Series will fill this gap. There is an ever-increasing focus on patient safety in medi-
Although physics is the foundation of radiology, many of us cine, and it is our responsibility to balance the clinical benefit
often overlook its importance in our daily clinical work. There and the negative consequences of imaging studies. While the
can sometimes be a disconnect between the granularity of phys- first 12 chapters of this book focus on the physics of radiologi-
ics and the real-world needs of patient X on our exam table. cal modalities, the last two chapters are dedicated to radiation
Even though there is not always a direct connection between doses and safety topics. These chapters will be a great resource
every clinical image and physics principle, understanding the for both exam preparation and the clinical practice of radiology.
underlying concepts of radiological physics will pay dividends Unlike other topics in radiology, radiological physics is not
to the reader for years to come. Throughout your career you something that can be predominantly learned at the worksta-
will be tasked with optimizing image quality, troubleshooting tion. Combining didactics, reading, self-study, practice ques-
artifacts, purchasing equipment, and building on your knowl- tions, and clinical learning is the best approach to mastering
edge as new technologies emerge. the basic principles of radiological physics. We hope that you
This book follows the familiar structure of other books in the enjoy this case-based approach to learning and wish you the
Case Review Series. The chapters are generally broken down best in your exciting career.
into modalities, with each case highlighting a specific topic.
The case begins with a clinical image and several multiple- R. Brad Abrahams
choice questions pertaining to the physics principle of interest. Walter Huda
The answers and explanations are shown on the reverse page, William F. Sensakovic
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CONTENTS
Radiographic Imaging 1
Mammographic Imaging 27
Single-Photon Emission Computed Tomography and Positron Emission Tomography Imaging 177
Index 381
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CHAPTER 1 Radiographic Imaging
C A S E 1 .1
A B
Fig. 1.1
1. What is most likely to be affected by the choice of a radio- 3. What is most likely reduced when focal spot size is in-
graphic focal spot size? creased?
A. Radiographic mottle A. Grid artifacts
B. Lesion contrast B. Image mottle
C. Spatial resolution C. Lesion contrast
D. Image artifacts D. Motion blur
2. Increasing what parameter will most likely result in the 4. What radiographic examination most likely uses a small fo-
largest increase in focal spot blur? cal spot?
A. Geometric magnification A. Extremity
B. X-ray tube voltage B. Skull
C. X-ray tube current C. Chest
D. Exposure time D. Abdomen
1
ANSWERS
C A S E 1 .1
Tungston target
Focal Spot Heated filament (anode)
Fig. 1.1 Chest radiograph in an adult patient (A) using a large focal (cathode) Anode angle
spot and hand radiograph of a pediatric patient (B) using a small (15°)
Electrons
focal spot.
X-ray beam
C. Spatial resolution is the image quality metric that is af-
1.
fected by the focal spot because a larger focus increases Fig. 1.2 Electrons flow from the cathode to the anode, colliding with
focal spot blur, especially when there is geometric magnifi- the tungsten target and producing x-rays.
cation.The focal spot has no effect at all on mottle, contrast,
or artifacts.
A. Focal spot blur always increases with increasing geomet-
2.
ric magnification. When magnification mammography is
performed, it is essential to use a very small focal spot (0.1
mm) to reduce focal spot blur. Increasing the tube voltage,
tube current, and exposure time will have no significant ef-
fect on focal spot blur.
D. When the focal spot is increased, this usually means that
3.
the power incident on the target can be increased. Increas-
ing power will mean that exposure time can be reduced,
which helps to minimize motion blur. Focal spot size will
not affect grid artifacts, mottle, or contrast in radiographic
images.
A. Use of a small focal spot in an extremity exam is impor-
4.
tant to reduce focal blur and improve the chance of de-
tecting (small) hairline fractures. Large focal spots are used
in the skull, chest, and abdomen to reduce exposure times,
and where detection of small features is unlikely to be a
major diagnostic task.
Comment
The focal spot in radiography is the size of the x-ray tube Fig. 1.3 With no geometric magnification, there is no focal spot blur
region that produces x-rays. When electrons hit the target (upper image). When the object-to-detector distance is increased,
located in the x-ray tube anode, x-rays are produced. The the image is magnified and blurred (middle image). Switching from
power used in x-ray tubes is much greater than in an aver- a large focal spot to a small focal spot is essential to reduce image
age domestic home (e.g., 100 kW vs. 4 kW), and overheating unsharpness with geometric magnification (lower image).
issues can be important in radiologic imaging. For this reason,
the target is arranged to be at a small angle (e.g., 15 degrees) small focal spot power limit. In most of radiography, the key
so that a large area is irradiated but appears relatively small issue is a reduction of the exposure time and thereby the corre-
when viewed from the patient perspective (Fig. 1.2). The sponding amount of motion blur. Accordingly, a large focal spot
size of the focal spot influences image sharpness (blur), with is essential where exposure times must be minimized (chest).
larger focal spots typically resulting in blurrier images than When the amount of image detail becomes important, such
small ones (Fig. 1.3). The focal spot poses a fundamental limit as detection of hairline fractures in extremity imaging, a small
on the sharpness of any image. Once such a limit is reached, focal spot is used. When the imaged body part is not very
use of smaller pixels will not translate into improved imaging attenuating, the amount of radiation required to penetrate the
resolution performance. patient will be less. Although using a small focal spot in extrem-
The amount of focal blur is critically dependent on the ity imaging increases exposure time, this is counteracted by
amount of geometric magnification. The amount of geometric improved radiation penetration so that motion blur does not
magnification is determined by the distance from an object to become problematic.
the image receptor, relative to the distance from the focal spot
to the image receptor. As geometric magnification increases, References
focal spot blur also increases, requiring the use of smaller focal Bushberg JT, Seibert JA, Leidholdt EM Jr, Boone JM. X-ray production, x-ray tubes,
spots (see Fig. 1.3). Geometric magnification is sometimes used and x-ray generators. In: The Essential Physics of Medical Imaging. 3rd ed.
in interventional neuroradiology and requires special x-ray Philadelphia: Wolters Kluwer; 2012:181–184.
tubes with exceptionally small focal spots. Huda W. Image quality. In: Review of Radiological Physics. 4th ed. Philadelphia:
Wolters Kluwer; 2016:36–37.
Most conventional x-ray tubes use two focal spot sizes, a
Huda W. Radiography. In: Review of Radiological Physics. 4th ed. Philadelphia:
small one (0.6 mm) and a large one (1.2 mm). The power limit Wolters Kluwer; 2016:91–99.
on the large focal spot (100 kW) is four times greater than the
2
C A SE 1. 2
Fig. 1.4
1. What is impacted the most when milliampere-seconds (mAs) 3. Which of the following detectors is expected to be quan-
is adjusted? tum mottle limited for chest radiography?
A. Mottle A. Scintillator (cesium iodide)
B. Contrast B. Photoconductor (selenium)
C. Sharpness C. Photostimulable phosphor (PSP) (BaFBr)
D. Artifacts D. A, B, and C
2. Which radiographic examination most likely uses the low- 4. How will quadrupling the mAs used to perform a bedside
est mAs? radiograph affect the amount of noise (mottle) in the im-
A. Skull age?
B. Extremity A. Quadrupled
C. L-spine B. Doubled
D. Abdomen C. Halved
D. Quartered
3
ANSWERS
C A SE 1. 2 Comment
Consider a conventional chest x-ray where the selected x-ray
Tube Output and Mottle tube voltage is set at 120 kV.The x-ray tube current will be sev-
eral hundred mA (e.g., 400 mA), and the exposure time will be
Fig. 1.4 Chest radiograph with extremely low mAs. Note the visible very short (e.g., 2.5 ms).The total x-ray intensity (x-ray tube out-
noise in the image.
put) is the product of the tube current and exposure time and,
in this instance, equal to 1 mAs. For an abdominal radiograph,
A. The number of photons used to create any radiographic
1.
the tube current would likely be several hundred mA (say, 400
image will affect only the amount of mottle. Quadrupling
mA), but the exposure time would be much longer to penetrate
the number of photons will halve the amount of mottle.
the much thicker body part (say, 50 ms). The total x-ray inten-
The mAs generally has no effect on contrast, sharpness, or
sity in this abdominal radiograph would be 20 mAs, or 20 times
the artifacts in the resultant image.
greater than the chest x-ray. When more radiation is required,
B. An extremity would use an mAs that is very low and
2. this is achieved by increasing the tube current, the exposure
much less than a skull, L-spine, or abdomen. Two useful time, or both.The ideal scenario is to increase the tube current,
benchmarks in radiography are 1 mAs for a chest radio- but because focal spot power loading (i.e., heating) will also
graph (posteroanterior [PA]) and 20 mAs for an abdomen increase, this may not always be possible.
(anteroposterior [AP]). The former is one of the low values The mAs is a relative indicator of x-ray tube output and is
implemented in radiography, and the latter is one of the increased whenever “more radiation” is required to create a
high values. radiologic image. It is important to note that knowledge of the
mAs does not permit a definitive determination of the amount
D. All medical imaging systems are normally operated at ex-
3. of radiation that is being emitted. X-ray tube output depends
posure levels that guarantee that they are quantum mottle on a number of additional factors, including x-ray tube design,
limited. What this means is that the only technical way to tube voltage, and x-ray beam filtration. The absolute amount of
reduce mottle is to use more photons to create the image, radiation incident on the patient is given by the entrance air
which will also increase the patient dose. kerma (Kair), which is approximately 1 mGy for a lateral skull
C. The noise is halved when the number of photons is qua-
4. x-ray. The absolute amount of radiation incident on the image
drupled. When four images are added together, the signal is receptor is much lower than entrance Kair and typically 3 μGy.
quadrupled. Because noise is random, adding four images The radiation intensity at the image receptor is much lower
together will only double the noise. The overall improve- because of patient attenuation, increased distance from the
ment by adding N images together in any imaging modality focus, and losses in the antiscatter grid. It is helpful to think of
is usually given by N0.5. mAs as analogous to the tachometer in a car, where increasing
Electrons
mAs
(quadruple)
Target
Photons
Noise
(half )
Fig. 1.5 Quadrupling the mAs will result in a fourfold increase in the number of x-rays produced but will reduce image noise only by half.
Increasing mAs will not increase the photon energy or beam quality, and so the contrast of all lesions will remain exactly the same. On the left,
lesion contrast is the same as on the right, but lesion visibility is inferior because of higher noise.
4
revolutions per minute (rpm) will increase car speed. However, Random noise is important because it limits the visibility
it is the speedometer that tells you the absolute speed, which of low-contrast lesions. Noise is irrelevant when the lesion
depends on engine design and the gear you are in (≡ Kair). has high contrast, irrespective of whether the lesion is large
Noise is any unwanted signal in a medical image and can be or small. However, to assess the visibility of any lesion, it is
considered to be structured or random. A rib cage in a chest important to take into account both the amount of contrast
radiograph may mask a lung lesion, as an example of structured and the corresponding level of noise.The contrast-to-noise ratio
(or anatomic) noise. When a detector is uniformly irradiated, (CNR) is a number that is used to assess how lesion visibility is
not every pixel has exactly the same value, and there will be a affected when radiographic techniques (kV and mAs) are modi-
salt-and-pepper appearance that is called mottle (noise). Quan- fied. When mAs is increased, contrast is unchanged and noise
tum mottle results from the discrete nature of x-ray photons is reduced, so the CNR increases and the lesion becomes more
and is the only important source of random noise in x-ray– visible. When automatic exposure control (AEC) systems are
based imaging. The only technical way to reduce the amount used, noise is “fixed” so that lesion CNR is solely determined by
of mottle in an x-ray–based image is to increase the number the choice of voltage. For AEC exposures, high voltages reduce
of photons interacting with the detector, either by improving contrast and vice versa.
detection efficiency or by using more photons (Fig. 1.5). The References
latter method of using more photons by increasing the mAs
Huda W. Image quality. In: Review of Radiological Physics. 4th ed. Philadelphia:
used will also increase patient dose. It is possible to reduce the
Wolters Kluwer; 2016:33–40.
apparent mottle using image-processing techniques, but these Huda W, Abrahams RB. Radiographic techniques, contrast, and noise in X-ray imag-
come at a cost in terms of imaging performance. For example, ing. AJR Am J Roentgenol. 2015;204(2):W126–W131.
averaging four pixels together will result in less random inter-
pixel fluctuations, but spatial resolution performance will also
be reduced.
5
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C A SE 1.3
A B
Fig. 1.6
1. X-ray beam quality is independent of which x-ray beam fac- 3. Which parameter is generally independent of lesion con-
tor? trast?
A. Tube voltage (kV) A. Tube output (mAs)
B. Tube output (mAs) B. Tube voltage (kV)
C. Filter thickness (mm) C. Beam filtration (mm)
D. Filter atomic number (Z) D. Grid ratio (10:1)
2. What will happen to patient dose and lesion contrast when 4. How will reducing the display window width impact lesion
0.1 mm Cu is added as a filter in a pediatric x-ray examina- contrast in the image?
tion performed using an AEC system? A. Increase
A. Increase; Increase B. No effect
B. Increase; Decrease C. Reduce
C. Decrease; Increase
D. Decrease; Decrease
7
ANSWERS
C A SE 1.3 Comment
When x-rays interact with patients, the two most important
Beam Quality and Contrast processes are photoelectric absorption and Compton scatter.
As photon energy increases in the human body, the likeli-
Fig. 1.6 (A) and (B) Frontal chest radiograph in a patient with mul- hood of an interaction decreases. As a result, increasing photon
tiple metastatic pulmonary masses. The image taken at higher kV (B)
has lower soft tissue contrast.
energy will increase the amount of radiation that is transmitted
through the patient. The penetrating power of an x-ray beam,
B. Tube output (mAs) has no effect on x-ray beam quality.
1. which reflects its average energy, is quantified by the thickness
Voltage and beam filtration are important variables that of aluminum (mm) that attenuates half of the x-ray beam inten-
radiologists have to adjust the beam quality in any radio- sity. For example, the average voltage in abdominal radiography
graphic examination. Average x-ray beam energy can also is 80 kV, where the corresponding beam quality is approxi-
be adjusted by changing the filter thickness or x-ray beam mately 3 mm aluminum. If the average energy is reduced, less
filter atomic number. aluminum is required to halve the x-ray beam intensity, and
when the average energy increases, more aluminum would be
D. The addition of 0.1 mm Cu to an x-ray beam will prefer-
2. required to halve the x-ray beam intensity. X-ray beam quality
entially eliminate low-energy photons, resulting in a more affects patient dose for examinations performed using AEC with
penetrating beam. To maintain the same radiation intensity a fixed Kair at the image receptor. As the x-ray beam becomes
at the image receptor, less radiation is required to be inci- more penetrating, fewer photons need to be used to achieve
dent on the patient, so the dose is reduced. The difference the required Kair at the image receptor, resulting in a decrease
in transmitted radiation between a lesion and the surround- in patient dose.
ing background is always reduced when energy increases, A lesion must transmit more or less radiation than the sur-
so contrast goes down. rounding tissues to be observable. The lesion will appear darker
when more radiation is transmitted. Conversely, the lesion
A. The mAs used to generate a radiographic image never
3. will appear lighter when less radiation is transmitted. Photon
affects contrast. If a lesion transmits 10% less radiation than energy is the most important determinant of subject contrast
do the surrounding tissues, this will be true at 1 mAs and at in radiography, with lower photon energies increasing contrast
1000 mAs. Contrast is reduced when voltage and filtration and vice versa. Photon energy increases with increasing x-ray
increase and is reduced when the amount of scatter in an tube voltage, as well as increasing x-ray beam filtration. These
image is increased, which occurs at lower grid ratios. increases would generally be expected to reduce the amount
A. When the window width is reduced, contrast in the
4. of contrast in all radiographic images (Fig. 1.7).
displayed image will increase. Conversely, wide windows Changes in contrast are highly dependent on the atomic
always reduce displayed image contrast. number of the lesion relative to that of soft tissues (Z = 7.5).
Fig. 1.7 This retained surgical lap pad can be easily seen in the left image, where kV is low and mAs is high. Patient dose is high because of the
need to use a lot of radiation to achieve a given amount at the image receptor. Raising the kV markedly reduces the contrast between the sponge
and surrounding tissue, but very little radiation is now needed because of the increased penetration to achieve the same radiation intensity at
the image receptor.
8
When the lesion atomic number is similar to that of tissue, with 200 in the surrounding tissues. The appearance of a lesion
changes in contrast with x-ray photon energy will be modest. in any radiographic image can always be adjusted by modify-
However, for high (or low) atomic number lesions, increas- ing the display characteristics (window/level settings). In chest
ing photon energy will markedly reduce lesion contrast. For computed tomography (CT), a narrow window is used to visu-
example, angiographic studies performed at high voltages (120 alize soft tissues. When a wide chest CT window is used to see
kV) will have very poor contrast in comparison with those per- all the tissues within the lung, perceived differences between
formed at an optimal voltage of 70 kV that matches the average soft tissues in the displayed image will “disappear.”
photon energy to that of the iodine K-edge (i.e., 33 keV).
Scatter reduces contrast but does not influence resolution References
or mottle. A lesion that transmits 50 photons compared with Huda W. Image quality. In: Review of Radiological Physics. 4th ed. Philadelphia:
100 for surrounding tissues has a 50% contrast. Adding 100 scat- Wolters Kluwer; 2016:31–33.
ter photons to all locations of this image would reduce the con- Huda W, Abrahams RB. Radiographic techniques, contrast, and noise in X-ray imag-
trast to 25% because there are now 150 in the lesion compared ing. AJR Am J Roentgenol. 2015;204(2):W126–W131.
9
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C A SE 1.4
Fig. 1.8
1. What is most likely to be adversely affected by an increase 3. What is the typical exposure index (EI) for an adult body
in exposure time in radiography performed using AEC? radiograph?
A. Noise (mottle) A. 3
B. Patient dose B. 30
C. Geometric magnification C. 300
D. Image sharpness D. 3000
2. What improves when exposure time is increased on a table- 4. Which radiographic examination is most likely to make use
top examination (i.e., no AEC)? of AEC?
A. Lesion contrast A. Skull
B. Image mottle B. Extremity
C. Gridline artifacts C. Infant body
D. Motion blur D. Bedside chest
11
ANSWERS
X-ray
timer
Fig. 1.9 (A) The rectangles illustrate the typical location of the automatic exposure control (AEC) detectors in chest radiography. (B) The AEC
detects the radiation intensity at the image receptor (air kerma) in predefined regions, which enables the exposure to be terminated when the
correct amount of radiation has been reached. In this way, the amount of mottle in the image is always fixed so that the right amount of radia-
tion is always used to create an image.
12
C A SE 1. 5
A B
Fig. 1.10
1. What part of an x-ray tube produces differential x-ray at- 3. What should be reduced to minimize the heel effect in radi-
tenuation that is called the heel effect? ography?
A. Cathode A. SID
B. Housing B. Anode angle
C. Filter C. Cassette size
D. Target D. A, B, and C
2. Changing what parameter is unlikely to influence the mag- 4. In what type of radiograph would x-ray tube orientation be
nitude of the heel effect in radiographic imaging? most important?
A. Tube output (mAs) A. Chest
B. Source-to-image receptor distance (SID) B. Skull
C. X-ray tube anode angle C. Abdomen
D. Radiographic receptor size D. Extremities
13
ANSWERS
C A SE 1. 5 toward the cathode pass through less of the target than those
that travel toward the anode.The tungsten target has a very high
atomic number (Z = 74), which attenuates almost as much as lead
Heel Effect (Pb) (Z = 82). As a result, the x-ray beam intensity at the anode
Fig. 1.10 (A) and (B) Frontal views of the abdomen demonstrating side of an x-ray tube has a reduced intensity when compared
how the appearance of an image changes when an x-ray tube is ro- with the corresponding radiation intensity at the cathode side
tated through 180 degrees. The top part of image B is more exposed of an x-ray tube. All commercial x-ray tubes label the anode side
(darker) due to increased exposure at the cathode side of the x-ray on the tube housing to enable operators to “know” the direction
tube (i.e., heel effect). with the highest (cathode) and lowest (anode) intensities.
As the anode angle is reduced, there is a greater differential
D. It is the differential attenuation in the tungsten target
1. distance in path lengths that travel in the anode and cathode
that causes the heel effect. X-rays traveling in the anode directions, which increases the heel effect. Conversely, increasing
direction traverse much more of the strongly attenuating the anode angle will reduce the magnitude of the heel effect, but
tungsten (Z = 74), which results in a weaker x-ray intensity this is never eliminated (see Fig. 1.11). The heel effect increases
at the anode side of the x-ray tube (Fig. 1.10). The filter will with increasing distance from the central axis, so it is much more
attenuate all x-rays equally, and the cathode and housing pronounced with large cassette sizes. A small cassette size will
play no role in x-rays that are directed toward the patient. capture the central region of the x-ray beam where differences
A. The heel effect is not affected by the mAs used in radiog-
2. in path length between opposite edges will be reduced (smaller
raphy. When the anode side is 25% weaker than the central heel effect). As the SID increases, an image receptor will increas-
beam, this will be true at 1 mAs and 1000 mAs. The heel ef- ingly capture only the central part of the x-ray beam, where the
fect increases with reduced SID, reduced anode angle, and magnitude of the heel effect is smaller. It is only at shorter SIDs
for larger image receptors based on irradiation geometry. that the heel effect becomes of increased importance.
The heel effect is always present in all x-ray–based imaging
C. When the cassette size is reduced, it is only the central
3. systems and is used to improve the resultant imaging perfor-
region of the x-ray beam that is being used, which is more mance. In chest radiography, the more intense cathode side is
uniform than the larger beam. Reducing the SID and anode directed toward the abdomen, which attenuates much more
angle will increase the heel effect. than the chest and benefits from increased x-ray intensities.
A. In a chest x-ray, the anode should point toward the upper
4. The less intense anode side is directed toward the upper tho-
chest region, which is much less attenuating. In all the other racic region, where x-ray attenuation is much lower than in the
examinations, the patient is “more uniform” than the chest, abdomen. Similarly, in mammographic imaging, the cathode
and the orientation of the x-ray tube (heel effect) is thus of side points toward the chest wall, whereas the anode side is
less importance. directed toward the nipple. In CT, the anode-cathode axis is ori-
ented perpendicular to the axial image plane to ensure that the
Comment detected projections are not influenced by the heel effect.
X-rays are produced when energetic electrons interact with References
tungsten atoms in the target that are embedded within an anode. Bushberg JT, Seibert JA, Leidholdt EM Jr, Boone JM. X-ray production, x-ray tubes,
These energetic photons are produced at some depth (<1 mm) and x-ray generators. In: The Essential Physics of Medical Imaging. 3rd ed.
in the tungsten and are attenuated as they emerge from the pro- Philadelphia: Wolters Kluwer; 2012:184–186.
duction site and travel toward the patient. Because the target is Huda W. Radiography. In: Review of Radiological Physics. 4th ed. Philadelphia:
angled at approximately 15 degrees (Fig. 1.11), x-rays that travel Wolters Kluwer; 2016:92–94.
Lower Higher
radiation radiation
intensity intensity
Fig. 1.11 In the upper right image, the heel effect occurs because photons produced in the tungsten target are attenuated as they exit and
move toward the patient. If the photon exits toward the cathode (1), there is less tungsten and therefore less attenuation along its path. If the
photon exits toward the anode (2), it is attenuated by a longer path within the target. In the radiograph, the lower intensity on the anode side
is directed to the less attenuating part of the patient (chest), and the higher intensity cathode side is directed to the more attenuating part of
the patient (pelvis).
C A SE 1.6
A B
Fig. 1.12
1. Which radiographic examination is most likely to use a scat- 3. What percentage (%) of primary x-ray photons is typically
ter removal grid? lost in grids used when performing adult abdominal radiog-
A. Skull raphy?
B. Extremity A. 10
C. Infant body B. 30
D. Bedside chest C. 70
D. 90
2. Which grid ratio is typically used to perform a chest x-ray
on a dedicated departmental imaging system? 4. What is the most likely dose reduction (%) in infant radia-
A. 2:1 tion dose when a grid is removed for a follow-up AEC radio-
B. 5:1 graph?
C. 10:1 A. 5
D. 20:1 B. 15
C. 50
D. 90
15
ANSWERS
16
C A SE 1.7
A B
Fig. 1.14
1. Which type of detector is most likely to result in the lowest 3. Image sharpness in digital radiographic imaging is indepen-
patient dose in an abdominal radiograph (80 kV)? dent of which parameter?
A. Gas chamber (xenon) A. Focal spot size
B. Photoconductor (selenium) B. Pixel size
C. Scintillator (cesium iodide) C. Scintillator thickness
D. PSP (BaFBr) D. Technique (kV and mAs)
2. Which type of detector is most likely to result in the sharp- 4. Increasing what parameter is most likely to improve spatial
est images? resolution?
A. Scintillator A. Matrix size
B. PSP B. Focal spot size
C. Photoconductor C. Scintillator thickness
D. A ≈ B ≈ C D. Imaging time
17
ANSWERS
C A SE 1.7 Comment
Scintillators (cesium iodide) absorb x-rays and convert the
Imaging Plates and Resolution absorbed energy into light photons. The magnitude of the
detected light signal, which is then converted into charge for
Fig. 1.14 The chest radiograph (A) uses a larger physical cassette
quantitative detection, is directly proportional to the absorbed
size compared with the foot radiograph (B). With a similar matrix
size of 2000 × 2500, the smaller cassette offers improved spatial x-ray energy. Photoconductors (selenium) absorb x-rays and
resolution (5 line pairs [lp]/mm vs. 3 lp/mm). produce a charge that is collected in a “charge detector” by
the application of a voltage across the photoconductor. Charge
C. A cesium iodide scintillator is an excellent absorber of
1. produced in photoconductors is directly measured, whereas in
incident x-rays because the K-edges of Cs and I (i.e., 36 and scintillators the light produced is subsequently converted into
33 keV, respectively) generally match a typical radiographic charge (i.e., indirect detection). PSPs (BaFBr) absorb and store
beam generated at 80 kV. A typical cesium iodide flat panel a fraction of the absorbed x-ray energy incident during a radio-
detector would likely absorb most (>80%) of the incident graphic examination. The stored energy is released by the appli
radiation, far higher than current xenon, selenium, and BaF- cation of a (red) laser and emits light that is blue. The detected
Br detectors. blue light is a measure of the energy absorbed in each pixel and
is used to generate the radiographic image.
C. When a photoconductor absorbs x-rays, the charge that
2. The type of detector used will influence the amount of detail
is produced is collected by an electric field. This charge in the resultant image. Photoconductors are most likely to result
does not spread out in the way light spreads out in a scintil- in the sharpest images because the charge that is produced at
lator or a PSP. the x-ray interaction site does not diffuse very far before it is
collected by the “charge detectors.” Scintillators generally have
D. kV, mAs, and beam quality have no practical direct effect
3.
average resolution because the light produced at the interac-
on the maximum achievable spatial resolution. In all radio-
tion site diffuses before being detected, which results in blurred
graphic imaging, the imaging system resolution is affected
images. The thicker the scintillator, the greater the light spread-
by the focal spot and the important detector characteristics
ing before being intercepted by the “light detectors” and vice
of detector thickness, as well as the pixel size.
versa (Fig. 1.15). PSPs have the poorest resolution because the
A. Only a larger matrix in the same field of view (i.e., small-
4. incident light used to “read out” the stored data is also subject
er pixels) may improve resolution. However, at some matrix to scattering and can therefore release light in adjacent pixels,
size, one must reach the intrinsic limits to resolution based reducing the resultant image sharpness. Because of the light
on focal blur and the detector characteristics (i.e., thick- scatter problems, there is a limit to the thickness of any PSP
ness). As focal spot size, scintillator thickness, and imaging detector used in radiographic imaging.
time increase, the resultant images will likely be less sharp.
Photons Photons
Thick scintillator
Thin scintillator
C D
Fig. 1.15 When the number of absorbed photons in the detector is kept constant as in the above examples, the patient dose will be lower with
the thicker scintillator (B) than with the thinner scintillator (A). The thin scintillator image (C) is sharper than the thick scintillator image (D)
because of lower light spreading.
18
Different types of detectors have different efficiencies Most digital detectors used in chest radiography (35 × 43 cm)
in absorbing photons, which will influence the radiation have 175-μm pixels, which results in a limiting resolution of
dose because a specified number of absorbed photons are 3 lp/mm.When the cassette physical size is reduced, the matrix
needed to create an image. Cesium iodide is an excellent size is normally unchanged (2000 × 2500) so that a 20 × 25 cm
x-ray absorber because these atoms have K-edge energies of cassette has smaller pixels (100 μm) and improved spatial reso-
33 and 36 keV, which are close to the average photon ener- lution (5 lp/mm). To appreciate these spatial resolution values,
gies generated by 80-kV x-ray voltages. On the other hand, the human eye has a limiting resolution of 5 lp/mm at a nor-
selenium is a very poor absorber because the K-edge is only mal viewing distance of 25 cm (approximately arm’s length).
13 keV, and this material has poor x-ray absorption, especially Radiographic technique factors of kV and mAs, which are of
at higher photon energies. BaFBr in PSP plates is intermedi- paramount importance in influencing a lesion CNR, have no
ate between the good absorption of cesium iodide and the direct effect on spatial resolution in radiographic imaging.
poor absorption of selenium at energies used in radiography.
References
Although the atomic number of BaFBr is much higher than
that of selenium, the read-out mechanism (light lasers) limits Bushberg JT, Seibert JA, Leidholdt EM Jr, Boone JM. Radiography. In: The Essen-
the thickness of material that may be used to ensure ade- tial Physics of Medical Imaging. 3rd ed. Philadelphia: Wolters Kluwer;
2012:231–235.
quate spatial resolution performance. In radiographic imag-
Huda W. X-ray imaging. In: Review of Radiological Physics. 4th ed. Philadelphia:
ing normally performed using x-ray tube voltages ranging Wolters Kluwer; 2016:22–25.
between 60 and 120 kV, indirect cesium iodide detectors will Huda W, Abrahams RB. X-ray-based medical imaging and resolution. AJR Am J
likely result in the lowest patient doses and direct selenium Roentgenol. 2015;204:W393–W397.
detectors will likely result in the highest doses when image
quality (mottle) is kept fixed.
19
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C A SE 1. 8
A B
C D
Fig. 1.16
1. What is the most likely cause of the artifact depicted in Fig. 3. What is the most likely cause of the artifact depicted in Fig.
1.16A? 1.16C?
A. Ghosting A. Ghosting
B. Grid B. Grid
C. Barium (Ba) spill C. Ba spill
D. Motion D. Motion
2. What is the most likely cause of the artifact depicted in Fig. 4. What is the most likely cause of the artifact depicted in Fig.
1.16B? 1.16D?
A. Ghosting A. Ghosting
B. Grid B. Grid
C. Ba spill C. Ba spill
D. Motion D. Motion
21
ANSWERS
Grid
(Correct) (Reversed)
Imaging plate
Grid cutoff
Fig. 1.17 When a grid is installed upside down, the central region will have a normal appearance but appear white (i.e., grid cutoff) toward
the edges.
C A SE 1.9
Fig. 1.18
1. Radiographic examination of what body part likely has the 3. What type of follow-up examination is most likely to use
lowest x-ray tube voltage? decreased x-ray tube output (mAs)?
A. Skull A. Scoliosis
B. Chest B. ICU chest
C. Abdomen C. Extremity
D. Extremity D. Abdomen
2. Radiographic examination of what body part likely has the 4. Decreasing what parameter is most likely to increase the
highest x-ray tube voltage? lesion CNR in radiographic imaging performed using AEC?
A. Skull A. Current (mA)
B. Chest B. Voltage (kV)
C. Abdomen C. Exposure time (s)
D. Extremity D. Focus (mm)
23
ANSWERS
C A SE 1.9
Radiographic Techniques and Diagnostic
Task
Fig. 1.18 Frontal view of the spine in a patient with idiopathic sco-
liosis. Because the clinical question pertains only to high-contrast
bony anatomy, radiation exposure can be reduced because in-
creased noise will not impact diagnosis.
24
C A S E 1 .1 0
A B
Fig. 1.20
1. What is the patient entrance Kair (mGy) for a lateral skull 3. How many adult body radiographic examinations would be
radiograph? needed to give the same amount of radiation as a typical
A. 0.1 fluoroscopy-guided gastrointestinal (GI) study?
B. 1 A. 1
C. 10 B. 10
D. 100 C. 100
D. 1000
2. What is the kerma area product (KAP) (Gy-cm2) for an AP
skull x-ray examination? 4. How many adult body radiographic examinations would be
A. 0.1 needed to give the same amount of radiation as a typical
B. 1 interventional radiologic procedure?
C. 10 A. 1
D. 100 B. 10
C. 100
D. 1000
25
ANSWERS
C A S E 1 .1 0
Incident Air Kerma and Kerma Area Product
Fig. 1.20 Lateral (A) and frontal (B) radiographs of the skull in a
patient with Gorlin syndrome.
Beam
B. For an adult lateral skull x-ray, 1 mGy is most likely inci-
1. area (A)
dent on the patient. The amount that reaches the detector
will be much lower (0.003 mGy) because of attenuation in
the patient and inverse square law drop in intensity, as well
as loss of primary photons in the grid.
B. An AP skull x-ray examination in an adult will likely use
2.
1 Gy-cm2 of radiation. Chest x-rays would likely be two or
three times lower and abdominal radiographs two or three
times higher.
B. A KAP in a GI/genitourinary examination is at least 10
3. Entrance
Gy-cm2, which is an order of magnitude higher than in radi- air kerma (kair)
ography.
Kerma Area Product (KAP) = kair x Area
C. A KAP in an IR procedure is at least 100 Gy-cm2, which is
4.
Fig. 1.21 The intensity of the x-ray beam (i.e., photons per mm2) is
two orders of magnitude higher than in radiography. given by air kerma (kair) and is measured in mGy. The corresponding
Comment x-ray beam area (A) is measured in cm2. The kerma area product
(KAP) is expressed in Gy-cm2, where 1 Gy-cm2 is 1000 mGy-cm2.
Patient entrance Kair values generally depend on x-ray tube The KAP is often referred to as the dose area product (DAP), and
characteristics, x-ray technique (mAs and kV), and distance these two terms are synonymous.
from the focus to the patient entrance. The radiation intensity
from any source falls off according to the Inverse Square Law
(1/[distance]2), where doubling the distance reduces the inten- of 3 higher. In pediatric radiography, entrance Kair is lower
sity by a factor of 4. The entrance Kair for a lateral skull x-ray is because patients are thinner and KAP is much lower because
approximately 1 mGy and about twice this value for the more the corresponding x-ray beam areas are also lower.
attenuating AP projection when radiographs are obtained with Radiologists and technologists are responsible for the x-ray
systems that employ an AEC. Radiographs of much less attenuat- beam quantity and quality that is incident on a patient. These
ing body parts (PA chest) require an entrance Kair of approxi- factors will depend on patient characteristics, and the specified
mately 0.1 mGy, whereas those for much more attenuating diagnostic imaging task for which the examination is being per-
regions (lateral lumbar spine) would require a Kair of about 10 formed. Medical physicists can convert values of incident radia-
mGy. Kair is independent of the x-ray beam cross-sectional area tion into corresponding patient doses and risks. To do this, it is
and therefore cannot account for the total amount of radiation essential that account is taken of both technical factors such as
used in any radiographic examination. the x-ray beam quality and quantity, as well as exam type that
When the average Kair (mGy) value of the x-ray beam inci- includes the body region (e.g., chest) and the specific projec-
dent on the patient is multiplied by the corresponding x-ray tion used (e.g.,AP).A complete assessment of patient doses and
beam cross-sectional area (cm2), one obtains the KAP. The KAP, risks should also include the important patient characteristics
also known as the dose area product (DAP), measures the total including size and patient demographics.
amount of radiation incident on the patient because it accounts
for the beam area (Fig. 1.21). When the value of Kair is 1 mGy, References
and the x-ray beam has an area of 1000 cm2 (approximately 30 Huda W. Kerma-area product in diagnostic radiology. AJR Am J Roentgenol.
× 30 cm), the KAP is 1 Gy-cm2. The average KAP for a complete 2014;203(6):W565–W569.
radiographic examination is 1 Gy-cm2. Chest x-ray examinations Huda W. Patient dosimetry. In: Review of Radiological Physics. 4th ed. Philadel-
phia: Wolters Kluwer; 2016:47–48.
are approximately a factor of 3 lower than this average value,
Huda W. Radiography. In: Review of Radiological Physics. 4th ed. Philadelphia:
and abdominal x-ray examinations are approximately a factor Wolters Kluwer; 2016:100.
26
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Language: English
SINK OR SWIM?
A Novel.
BY THE AUTHOR OF
“RECOMMENDED TO MERCY,”
ETC.
IN THREE VOLUMES.
VOL. I.
LONDON:
TINSLEY BROTHERS, 18 CATHERINE ST. STRAND.
1868.
LONDON:
ROBSON AND SON, GREAT NORTHERN PRINTING WORKS,
PANCRAS ROAD, N.W.
SINK OR SWIM?
CHAPTER I.