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Recent Advances in Chest
Radiography
1
H. Page McAdams, MD
Ehsan Samei, PhD
James Dobbins III, PhD
Georgia D. Tourassi, PhD
Carl E. Ravin, MD
There have been many remarkable advances in conven-
tional thoracic imaging over the past decade. Perhaps the
most remarkable is the rapid conversion from film-based
to digital radiographic systems. Computed radiography is
now the preferred imaging modality for bedside chest
imaging. Direct radiography is rapidly replacing film-based
chest units for in-department posteroanterior and lateral
examinations. An exciting aspect of the conversion to dig-
ital radiography is the ability to enhance the diagnostic
capabilities and influence of chest radiography. Opportuni-
ties for direct computer-aided detection of various lesions
may enhance the radiologist’s accuracy and improve effi-
ciency. Newer techniques such as dual-energy and tempo-
ral subtraction radiography show promise for improved
detection of subtle and often obscured or overlooked lung
lesions. Digital tomosynthesis is a particularly promising
technique that allows reconstruction of multisection im-
ages from a short acquisition at very low patient dose.
Preliminary data suggest that, compared with conven-
tional radiography, tomosynthesis may also improve de-
tection of subtle lung lesions. The ultimate influence of
these new technologies will, of course, depend on the
outcome of rigorous scientific validation.
娀 RSNA, 2006
1
From the Department of Radiology, Duke Advanced Im-
aging Laboratories, Duke University Medical Center, Box
3808, Durham, NC 27710. Received September 14,
2005; revision requested October 24; revision received
November 15; accepted January 2, 2006; final version
accepted January 6. Supported by National Institutes of
Health grant R01 CA80490 and a research agreement
with from GE Healthcare. Address correspondence to
H.P.M. (e-mail: Page.mcadams@duke.edu).
姝 RSNA, 2006
REVIEWS AND COMMENTARY
䡲
STATE OF THE ART
Radiology: Volume 241: Number 3—December 2006 663
Note: This copy is for your personal non-commercial use only. To order presentation-ready
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D
espite recent advances in cross-
sectional imaging of the thorax,
chest radiography remains the
mainstay for diagnosis of many pulmo-
nary diseases. In most instances, it is
the first—and frequently the only—di-
agnostic imaging test performed in pa-
tients known to have or suspected of
having a thoracic abnormality. In the
United States, and very likely in the
world, chest radiography remains the
most commonly performed diagnostic
imaging test overall.
In the more than 100 years since
the discovery of the x-ray, technologic
advances have resulted in many im-
provements in chest radiography (1).
Progress in film-based imaging led to
the development of excellent screen-
film systems designed specifically for
chest radiography (1). More recently,
advances in electronics and computer
technology have resulted in rapid devel-
opment in digital image receptors and
displays. Further, rapid development of
image-processing techniques and of ad-
vanced applications such as dual-energy
and temporal subtraction radiography,
digital tomosynthesis, and computer-
aided detection (CAD) and diagnosis
(CADx) promise to substantially im-
prove the way chest radiography is
practiced in the future.
In this article, we will discuss the
inherent challenges of chest radiogra-
phy and the specific advances made to
address these challenges, including new
digital detector and image display tech-
nologies, developments in image-pro-
cessing techniques and CAD and CADx
applications for chest radiography, ad-
vanced applications such as dual-energy
and temporal subtraction radiography,
and chest tomosynthesis.
Challenges
To better appreciate the recent ad-
vances in chest radiography, we must
first review some of the inherent chal-
lenges of the technique, because these
challenges have been the prime motiva-
tors behind most of the developments.
These challenges include but are not
limited to issues related to image area
and patient body habitus, latitude and
dynamic range of x-ray transmission
through the chest, scattered radiation,
overlap of anatomic structures, and per-
ceptual limitations.
Image Area and Body Habitus
The chest is one of largest and thickest
body parts that is imaged on a routine
basis. The typical imaging field in an
adult readily exceeds 40-cm, particu-
larly for patients with a large body hab-
itus. This large field of view imposes
challenging constraints on the size of the
image receptor, given that the receptor
must also provide consistent and uni-
form response over the entire field. This
large field of view also increases the
contribution of scattered radiation to
the image, degrading the image’s inher-
ent quality. Given the marked increase
in obesity in the United States over the
past 20 years (2) among both children
and adults, these issues will continue to
pose considerable challenges to chest
radiography in the future (Fig 1). For
example, the authors of a recent study
(3) found that the number of chest ra-
diographs that were considered limited
because of body habitus had more than
doubled during a 14-year period at one
hospital.
Latitude and Dynamic Range
The wide latitude of x-ray transmission
through the thorax imposes a funda-
mental limit on the visualization of sub-
tle abnormalities on conventional chest
radiographs. For a typical x-ray beam
used in chest radiography, the regional
variations in transmission through the
thorax can extend over two orders of
magnitude (4) (Fig 2). Ideally, an imag-
ing system should have enough latitude
to capture and effectively display this
wide range, or at least the diagnostically
meaningful part, of the x-ray transmis-
sion. However, coverage of such wide
latitude can limit depiction of minute
differences associated with subtle low-
contrast lesions. Maintaining wide lati-
tude while preserving visualization of
low-contrast features in the image is a
particular challenge for chest radiogra-
phy (1). This large variation in x-ray
opacity of anatomic structures is the
primary reason that the modality uses
the highest range of x-ray energy set-
tings (typically 100–150 kVp) of all di-
agnostic imaging procedures, at the cost
of increased scatter and reduced inher-
ent contrast.
Scattered Radiation
The combined use of high x-ray photon
energy in conjunction with a thick body
part and a large field of view results in a
large amount of scattered radiation in
chest radiography compared with that
in other x-ray imaging modalities. Scat-
tered x-rays can account for 95% of the
detected x-ray flux in the mediastinum
and up to 70% in the lung in radio-
graphs acquired without a grid (Fig 3)
Essentials
䡲
Chest radiography remains the
mainstay for diagnosis of many
thoracic diseases.
䡲 Recent developments in chest ra-
diography have been primarily
driven by recognized challenges
and limitations of the technique.
䡲 Computed radiographic, and now
full-field flat-panel detector, sys-
tems have replaced or are rapidly
replacing conventional film-based
systems for chest image acquisi-
tion.
䡲 Selection of image-processing pa-
rameters and display devices has
a profound and fundamental ef-
fect on the appearance of the digi-
tal chest image.
䡲 The rapid conversion from
screen-film to digital chest image
acquisition has greatly facilitated
advances such as computer-aided
detection and diagnosis, dual-en-
ergy or temporal subtraction im-
aging, and tomosynthesis.
Published online
10.1148/radiol.2413051535
Radiology 2006; 241:663–683
Abbreviations:
CAD ⫽ computer-aided detection
CADx ⫽ computer-aided diagnosis
CCD ⫽ charge-coupled device
CMOS ⫽ complementary metal-oxide semiconductor
CR ⫽ computed radiography
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
664 Radiology: Volume 241: Number 3—December 2006
(6,7). Scattered radiation has the dele-
terious effects of degrading contrast and
increasing image noise. While this re-
duction in contrast can be remedied
with postprocessing, at least in digital
radiography, the contribution of scat-
tered radiation to image noise may not
be readily correctable. Further, in-
creased obesity in the U.S. population,
as noted earlier, has had a notable ef-
fect on the increased level of scattered
radiation in chest radiography.
Overlay of Anatomic Structures
In its conventional form, chest radiogra-
phy involves the projection of a three-
dimensional structure onto a two-dimen-
sional image. In this process, anatomic
features such as ribs, lung vessels, heart,
mediastinum, and diaphragm overlay
each other in a pattern that can be re-
ferred to as anatomic noise (8). Anatomic
Figure 1
Figure 1: Chest radiographs obtained with computed radiography (CR) technique and grid in morbidly obese patient with signs and symptoms of pulmonary edema.
(a) Anteroposterior image is limited by body habitus and was interpreted as showing possible edema. (b) Posteroanterior image obtained 30 minutes later shows no evi-
dence of edema.
Figure 2
Figure 2: Graph shows dy-
namic range of an image as func-
tion of thickness of soft tissue
penetrated and peak voltage (5).
Max ⫽ maximum, Min ⫽ mini-
mum.
Figure 3
Figure 3: Graph shows scatter fractions in
lung, mediastinum, and diaphragm regions with-
out a grid (black bars), with a grid (white bars), and
with a slot-scan device (gray bars). Note marked
reduction in scatter with slot-scan device.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
Radiology: Volume 241: Number 3—December 2006 665
noise can have a detrimental effect on the
ability of the observer to detect abnor-
malities of concern. The projection of
ribs is of particular concern for detec-
tion of lung nodules, because the ribs
overlay about 75% of the area of the
lungs (9). Furthermore, a substantial
portion of the lungs is projected over
the heart and diaphragm regions of the
image (1), affecting the contrast of po-
tential lung lesions on the image.
The appearance of lung nodules on
chest radiographs is of particular con-
cern. The similarity of a lesion’s appear-
ance to that of the background anatomy
in which it is located causes the conspi-
cuity of the lesion to be poor. This phe-
nomenon can result in up to 30% of
pulmonary nodules being missed on ini-
tial chest radiographs (10), even though
the nodules could be observed retro-
spectively. Purely on the basis of inher-
ent contrast, a nodule as small as 3 mm
in diameter should be visible on chest
radiographs, even in the presence of
scattered radiation; however, it is rare
to detect nodules smaller than about 8
mm on chest radiographs, owing to the
influence of anatomic noise. A great
deal of work has been performed on the
effect of anatomic noise on nodule de-
tectability, beginning with the work of
Kundel and colleagues (11,12) several
decades ago. More recently, Samei et al
(13) demonstrated that anatomic back-
ground is far more important than
quantum noise in limiting the detectabil-
ity of lung nodules (Fig 4).
Perceptual Limitations
Medical images are generally of little
value until an expert reader interprets
them. Thus, the perceptual and cog-
nitive processes involved in reading a
medical image have a direct bearing
on its clinical utility and effectiveness.
These processes are of particular im-
portance in chest radiography because
of the complexity of the tasks and the
confounding effect of anatomic noise,
as noted earlier in this article (14).
Anatomic noise can hinder detection
through two processes: (a) local influ-
ence, or “camouflaging,” and (b) global
influence, or “confusion” (15). The local
effect obscures the definition of an ab-
normality by means of patterns immedi-
ately surrounding or overlaying it. For
the global effect, however, the detect-
ability of an abnormality (eg, a nodule)
is influenced by the degree of its distinc-
tiveness from similar structures created
by the global noise characteristics of the
background.
Perceptual errors can occur at both
the visual and the cognitive level. In-
completeness of the search task may
lead to about 55% of the missed lesions.
These errors occur when the observer
fails to look at the territory of the lesion
(30%) (11,16) or when he or she does
not fix his or her eyes on the territory
for a dwell time of at least 0.3 second
(25%) (17). Cognitive errors (account-
ing for 45% of missed lesions) can occur
when the fixation time on an abnormal-
ity candidate exceeds the above limit
(eg, a nodule is recognized), but the
observer commits a decision-making er-
ror by calling the case negative (11).
Results of prior studies suggest that
perceptual errors can be reduced by pro-
viding radiologists with fixation feedback
(18) and by using systematic search strate-
gies, coning devices, and double reading of
chest radiographs (19). CAD (further dis-
cussed later), with its ability to offer a com-
plete search of the image data, has the po-
tential to reduce certain types of perceptual
error. The most effective method by far,
however, is the reduction or elimination of
anatomic noise, which has been shown to
be the main factor limiting the detection of
subtle lung nodules (13).
Detector Developments
The imaging receptor (or detector) is a
key component of chest radiography. In
the past few decades, changes in recep-
tor technology have brought about one
of the most important advances in chest
radiography, leading to improved image
quality and new image acquisition tech-
niques. This section will summarize the
most important developments in this
area. Because most advances have been
focused on digital technologies, they will
be the main focus of this section. The
Table provides a summary of the current
commercially available digital receptor
technologies for chest radiography.
Analog Chest Radiography
Chest radiography is conventionally per-
formed with analog screen-film recep-
tors. In the most common implementa-
tion, these receptors are made of double-
emulsion light-sensitive film sandwiched
between two layers of phosphor screens.
The screens serve as the primary medium
to convert x-ray photons to light photons,
which are subsequently detected by the
film emulsion, where the ionic silver of
the emulsion is converted to metallic
silver. Subsequent chemical processing
washes the desensitized chemicals away,
leaving the residual metallic silver behind
to form the x-ray image (20).
While screen-film receptors have
Figure 4
Figure 4: Images in middle-aged woman with
history of right partial mastectomy for breast can-
cer who presented for routine follow-up. (a) Pos-
teroanterior chest radiograph was interpreted as
normal. (b) Transverse computed tomographic
(CT) scan shows 8-mm nodule (arrowhead) in
right lower lobe that was obscured by overlying
breast implant, diaphragm, and rib shadows on a.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
666 Radiology: Volume 241: Number 3—December 2006
been in continual use for many years,
their inherent characteristics have im-
posed certain limitations on the practice
of chest radiography. Owing to the lim-
ited light range sensitivity of film, repre-
sented by the Hurter and Driffield re-
sponse of the receptor (Fig 5), the range
of x-ray exposures that can be recorded
by a screen-film detector is limited.
Only a narrow range of exposures can
be reliably represented on the film with
acceptable contrast; exposures above
or below this range will be represented
suboptimally. Given the large variability
in radiopacity of organs in the thoracic
cavity, this characteristic leads to two
limitations of analog chest radiography:
(a) suboptimal contrast renditions at
the extremes of the attenuation range of
the thorax and (b) susceptibility to sub-
optimal image acquisition due to under-
or overexposure.
In recent years, most technical de-
velopments have focused on digital tech-
nologies (discussed later). The latest de-
velopment in analog chest radiographic
receptors, now over 13 years old, is an
improvement on traditional screen-film
chest techniques; this development in-
volves combining two different emul-
sions and screens with an anticrossover
layer that is opaque until the film is de-
veloped. This asymmetric screen-film
technology, developed and marketed by
Eastman Kodak (Rochester, NY), im-
proves the contrast of fine-detail anat-
omy by using a thin front screen while
maintaining good overall image noise
through improved x-ray detection in a
thick rear screen (4,21). The overall re-
ceptor has a markedly wider acceptable
exposure window and contrast sensitiv-
ity that provide a better balance be-
tween contrast sensitivity and latitude
while maintaining good quantum mottle
properties.
Figure 5 shows the Hurter and Drif-
field curves for a typical chest radiogra-
phy screen-film system in comparison
with a typical digital detector.
Digital Chest Radiography
While screen-film receptors have been
the main technology for acquiring chest
Summary of Selected Commercial Digital Chest Radiography Systems
Manufacturer or Provider Product Family Size (cm)
Pixel Pitch
(m) X-ray Absorbing Material*
CR
Agfa Healthcare CR 25.0, 75.0, DX-S 36 ⫻ 43 ⱖ100 Ba halide
Eastman Kodak Directview CR 35 ⫻ 43 ⱖ97 Ba halide
Fujifilm Medical Clearview, Velocity, SmartCR, XG5000 35 ⫻ 43,
43 ⫻ 43
ⱖ100 Ba halide
Konika Minolta XpressCR, IQue CR 35 ⫻ 43 175 Ba halide
Orex PcCR 1417 ACL, ACLxy 35 ⫻ 43 100 Ba halide
Philips Medical Systems Compano, Corado, Cosima X 35 ⫻ 43 ⱖ100 Ba halide
Indirect flat panel
GE/Perkin Elmer Revolution XQ/i, XR/d 41 ⫻ 41 200 CsI (Tl), undisclosed thickness
Trixell Pixium 4600TM; Siemens: Thorax/Vertix/Multix FD, Axoim Aristos;
Philips: Digital Diagnost Infimed and Listem: Stingray Quantum:
Q-RAD (CsI), QV (CsI)
43 ⫻ 43 143 CsI (Tl), ⬃550 m thick
Canon Canon: CXDI; Agfa: ADR Thorax; Quantum: Q-RAD (GOS), QV
(GOS); Siemens: Axiom Multix M
43 ⫻ 43 160 Gd
2
O
2
S (Tb), ⬃200 m thick
Direct flat panel
Direct Ray Hologic: Epex, Radex; Eastman Kodak: DirectViewDR; DEL: EPEX,
RADEX
35 ⫻ 43 139 Amorphous Se, ⬃500 m
thick
Anrad Toshiba: DynaDirect 35 ⫻ 35 150 Amorphous Se, ⬃1000 m
thick
Edge Medical Quix DR systems 43 ⫻ 43 120 Amorphous Se, undisclosed
thickness
CCD- and CMOS-based
†
SwissRay ddR 35 ⫻ 43 167 CsI, undisclosed doping
Wuestec DX2000 35 ⫻ 43 120 Gd
2
O
2
S(Tb)
Imaging Dynamics Xplorer 43 ⫻ 43 108 Gd
2
O
2
S(Tb)
Oy ImixAB Imix 2000 40 ⫻ 40 200 Gd
2
O
2
S(Eu)
Delft Diagnostic Imaging Thorascan 44 ⫻ 44 162 CsI(Tl), ⬃500 m thick
Cares Built Cares Built: Clarity 7000; Lodox: Statscan 43 ⫻ 43 60 Gd
2
O
2
S(Tb)
Star V-Ray Tradix 4000 43 ⫻ 43 140 Gd
2
O
2
S(Tb)
*Ba⫽ barium, CsI ⫽ cesium iodide, Eu ⫽ europium, Gd ⫽ gadolinium, O ⫽ oxygen, S ⫽ sulfur, Se ⫽ selenium, Tl ⫽ thallium, Tb ⫽ terbium.
†
CCD ⫽ charge-coupled device, CMOS ⫽ complementary metal-oxide semiconductor.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
Radiology: Volume 241: Number 3—December 2006 667
radiographs until recently, the use of
digital radiography has been on the rise
and is expected to replace analog tech-
nology in the near future. Digital radiog-
raphy has also enabled the implementa-
tion of picture archiving and communi-
cation systems, which have their own
associated advantages. There have been
six main forces driving the transition to
digital:
1. Decoupling of acquisition and dis-
play functions of the acquisition device
in digital radiography makes it possible
to optimize either of those functions in-
dependently—for example, by optimiz-
ing display contrast independently of
the exposure level.
2. Availability of the image data in
an electronic form makes it possible to
postprocess the image for optimal display
and to display the images on the more
flexible soft-copy viewing workstations.
3. Availability of the image data in
an electronic form makes it possible to
archive the data electronically, which
uses less space and requires less labor
for storage.
4. Availability of the image data in
an electronic form makes it possible to
distribute images widely and to make
copies of images available concurrently
to multiple users.
5. Most digital radiography systems
have integrated acquisition and pro-
cessing units in the same physical sys-
tem, eliminating the need to handle the
cassettes and thus improving the work-
flow for image acquisition in the depart-
ment.
6. Most digital radiography systems
are able to acquire multiple images in a
rapid sequence, enabling new advanced
imaging applications that require the ac-
quisition of multiple images from the
chest, as will be discussed in a later
section of this article.
Because of these advantages, digital
radiography has been a main focus of
new developments in chest radiogra-
phy. Differing technologies have been
the basis of the development of various
commercial products, which are sum-
marized below.
In comparing various chest radiog-
raphy systems, a common metric, de-
tective quantum efficiency, has been
used as a basis of comparison. Detective
quantum efficiency describes the inher-
ent signal-to-noise performance of an
imaging system per unit incident expo-
sure to the detector (22). Most com-
monly reduced to its value at zero spa-
tial frequency, various chest radiogra-
phy systems offer a detective quantum
efficiency in the range of 20%–70%
(23,24). These values are reflective of
the system performance in the absence
of scattered radiation. Most recently, a
new metric, termed effective detective
quantum efficiency, has been intro-
duced that further accounts for the
presence of scattered radiation (25), re-
flecting the inherent signal-to-noise per-
formance of an imaging system in actual
clinical use.
CR Systems
CR was the first commercial digital im-
aging modality widely used in chest im-
aging (26) and currently is still the most
common technology for acquiring digital
chest radiographs, especially for bed-
side applications. The technology is
based on photostimulable properties of
barium halide phosphors. With a cas-
sette similar to that used in screen-film
radiography, the phosphor screen is ex-
posed to x-rays. After exposure, the
cassette is transported to a computed
radiography reader device, which sub-
jects the screen to a scanning laser beam.
The laser releases the energy locally de-
posited by x-rays on the screen, causing
the screen to fluoresce. The released light
is used to form the image after it is col-
lected by a light guide, digitized, and asso-
ciated with the geometric location of the
laser beam at the time of stimulation. The
digital image data are then processed for
presentation.
Since its commercial introduction
more than 2 decades ago, CR has been
under continuous improvement. The
most recent advances include the collec-
tion of photostimulated light from both
sides of the screen, leading to improved
detective quantum efficiency (currently
available only for mammography) (27),
the use of line scanning and light collec-
tion technology for improved speed
(28), and the use of structured phos-
phor for improved detection efficiency
without associated loss in resolution
(29).
In the most common implementa-
tion, CR devices produce image quality
that tends to be lower than that for
other digital radiography systems (23),
but CR systems possess certain opera-
tional and economic advantages that
cause them to remain competitive with
other digital modalities. Those advan-
tages can be summarized as follows:
(a) In the most common implementa-
tion, CR cassettes are identical in size to
screen-film cassettes, making it possible
to retrofit existing analog radiography
rooms; (b) the fact that the CR reader
and cassettes are separate entities
makes the technology extremely conve-
nient for bedside applications; and
(c) the separation of CR reader and cas-
sette makes it further possible to have
one (higher-cost) CR reader used in
reading multiple (lower-cost) CR cas-
settes, which allows one CR reader to
serve multiple radiography rooms and
reduces the up-front cost of the transi-
tion to digital radiography.
Flat-Panel Detectors
While CR technology currently has the
largest number of installations in the
digital radiography market, with its no-
table advantages in terms of cost and
utility for bedside applications, its dis-
advantages in terms of image quality per
unit dose and suboptimal workflow (ow-
Figure 5
Figure 5: Hurter and Driffield curves of analog
screen-film (InSight; Eastman Kodak) and digital
(CR) systems. Detector signal is optical density for
screen-film system and relative digital value for
the digital system.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
668 Radiology: Volume 241: Number 3—December 2006
ing to the physical separation of the ac-
quisition and processing functions) pro-
vide opportunities for another notewor-
thy technology, the flat-panel detector.
Made possible by advances in the
fabrication of flat-panel displays for the
computer industry, flat-panel detectors
are made of thin layers of amorphous
silicon thin-film transistors (TFTs) de-
posited on a piece of glass. The TFT
layer is coupled with an x-ray absorptive
layer. Depending on the material, there
are two types of flat-panel detector. In-
direct flat-panel detectors use a phos-
phor screen, most commonly cesium io-
dide, to convert the x-rays to light pho-
tons, which are subsequently detected
by the photodiode array associated with
the TFT layer and are converted to
charge deposited in the capacitors asso-
ciated with each TFT (24,30). Direct
flat-panel detectors use instead a photo-
conductor layer, most commonly amor-
phous selenium that converts the x-ray
energy directly to charge, which is
subsequently directed to the collecting
TFT-capacitor array through the appli-
cation of a strong electric field (31,32).
After exposure, the charge on the ca-
pacitors is collected line by line and pixel
by pixel by using the associated gate and
data lines, forming the raw digital image
data for processing and display.
Flat-panel detectors are relatively
new, and there continue to be a number
of new developments in the technology.
Most noteworthy are the use of x-ray cap-
ture materials with higher inherent ab-
sorption efficiency, improvement in the
electronics to increase the frame rate and
bit-depth resolution of the images, and
use of flexible substrates in place of glass
to enable more rugged and damage-resis-
tant detectors, which can perhaps make
these detectors practical for bedside ap-
plications (33).
Flat-panel detectors have three note-
worthy advantages compared with other
digital radiographic technologies. These
advantages can be summarized as fol-
lows:
1. With the use of structured phos-
phor in indirect detectors and the appli-
cation of an electric potential in direct
detectors, the x-ray–sensitive layer of
these detectors can be notably thicker
than that of competing technologies.
This makes it possible to have increased
x-ray detection efficiency with minimal
loss of resolution. Consequently, patient
dose can be reduced without degrada-
tion of image quality (34).
2. Flat-panel detectors can acquire
multiple images in a short time. Current
frame rates of 30 frames per second are
available in the most recent models.
This makes it possible to acquire multi-
ple images of the patient with different
techniques or from different directions
with minimal motion blur. This feature
facilitates the use of these detectors for
a host of advanced applications such as
tomosynthesis and dual-energy imaging.
3. With integration of the acquisi-
tion and processing units, flat-panel de-
tectors offer improved workflow com-
pared with that of CR.
CCD- and CMOS-based Detectors
In the past few years, CCD and CMOS
cameras have provided an alternative
technology for the acquisition of digital
chest radiographs. With these detec-
tors, the x-ray energy is first converted
to light within a phosphor layer. The
light is then directed to a single or a
multitude of CCD or CMOS cameras
that detect the light image and form the
radiograph (35). An important compo-
nent of these detectors is the coupling of
the phosphor layer and the camera.
Since most CCD and CMOS sensors are
limited in size, it is necessary to demag-
nify the original light image generated
on the phosphor screen so that it can be
entirely captured by the camera. This is
accomplished by using either a fiberop-
tic coupler or a lens system. In either
case there is a loss of efficiency, since
only a small fraction of the light photons
generated by the phosphor are detected
by the camera(s). Consequently, the in-
herent efficiency of these detectors is
limited (34).
New developments in these types of
detectors have been focused on more
efficient coupling between the phosphor
and the camera, the use of larger sen-
sors to minimize demagnification, and
improvements in phosphor efficiency.
These advances have led to the develop-
ment of detectors with detection effi-
ciencies notably higher than those of
previous-generation CCD or CMOS de-
vices. These detectors are generally less
expensive than other digital technolo-
gies.
Slot-Scan Technology
As noted earlier, scattered radiation is
of notable concern in chest radiogra-
phy. Over the years, various techniques
have been developed to reduce the con-
tribution of scattered photons to the x-
ray image, including the use of antiscat-
ter grids (36,37), which are used in
most current chest radiography sys-
tems, and air gaps (38). While these
techniques can reduce scatter substan-
tially (36), they also lead to increased
patient dose, as well as a reduced field
of view in cases of an air gap. These
fundamental limitations can be over-
come with the use of scanning beam and
slit devices (37,39–42).
A recent commercial product has
taken advantage of slot-scan technology
to reduce the amount of scattered radi-
ation on digital chest radiographs (43).
The detector consists of a cesium iodide
scintillation layer fiberoptically coupled
to a series of linear CCDs. With no anti-
scatter grid in place, a narrow-fan x-ray
beam synchronized with the movement
of the detector assembly scans the pa-
tient. The image data are continuously
read from the CCDs as the patient is
scanned by using the time-integration
method (44,45). After scanning, the im-
age data are processed for optimal dis-
play.
The main advantage of this technol-
ogy is superior scatter rejection with
little effect on the detection of primary
radiation. This can notably enhance the
effective detection efficiency of the im-
aging system. Results from a recent
study (25) show that this enhancement
can more than compensate for the in-
herent efficiency limitation of CCD-
based detectors, leading to improved
image quality at reduced dose.
The technologies described in the
preceding paragraphs represent the
bulk of commercial offerings for digital
chest radiography. There are a number
of other technologies that are currently
under development, however, including
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
Radiology: Volume 241: Number 3—December 2006 669
those related to new sensor materials
and new detector designs such as photon-
counting devices. Commercial implemen-
tation of these technologies awaits further
development.
Image-processing Developments
Image data acquired with radiographic
detectors cannot be viewed without ad-
ditional processing and proper display.
In the case of screen-film images, the
film must be chemically processed and
is eventually displayed on a light box. In
the case of digital images, digital pro-
cessing is required before a clinician can
view the images. Since most of the re-
cent developments in chest radiography
have focused on digital modalities, this
section will outline the current state of
digital image-processing methods for
optimal presentation of digital images,
as well as hardware components of soft-
copy display devices. Readers inter-
ested in the current state of film-pro-
cessing techniques are advised to con-
sult two publications focused on that
topic (20,46).
In recent years, the increasingly dig-
ital nature of chest radiography, as well
as advances in computer technology,
have facilitated the application of com-
puterized image analysis for improv-
ing the clinical efficacy of chest radio-
graphs. As a general rule, computerized
medical image analysis aims to reduce
both the perceptual and the cognitive
errors that burden the diagnostic inter-
pretation process. Consequently, the
latest image-processing developments in
chest radiography fall into two general
application areas: (a) techniques to im-
prove visual presentation and soft-copy
reading of radiographs and (b) techniques
to automate diagnostic interpretation of
such images. For the most part, these
techniques are application dependent.
Prior to display, each digital image
commonly undergoes a series of process-
ing steps (Fig 6). Broadly speaking, these
processes can be divided into two parts:
preprocessing and postprocessing.
Image Preprocessing
Image preprocessing consists of two com-
ponents: correction and scaling (47). Ne-
cessitated by the intrinsic nonuniformity
of digital detectors, the first type of pro-
cessing includes image corrections for de-
tector defects or nonuniformities often
present on raw digital images. The non-
uniformities include stationary patterns
of the detector, thickness nonuniformities
of the capture element of the detector,
pixel dropouts, “dead” (inactive) pixels,
dead columns and rows, and dark current
variations. The corrections often require
periodic flat-field calibration processes
for the detector. These include one-di-
mensional shading corrections in the
case of CR and linear CCD-based detec-
tors and two-dimensional flat-field cor-
rection for flat-panel detectors and two-
dimensional CCD- and CMOS-based
systems. In either method, an averaged,
normalized flat-field image (map) is
used to normalize the original image to
remove the patterns.
The second type of preprocessing is
scaling. One of the advantages of digital
radiography is the wide range of expo-
sures within which the detector is able
to provide a consistent response. This
enables the acquisition of high-latitude
chest radiographs with less susceptibil-
ity to over- and underexposure. How-
ever, the dynamic range of the detector
is beyond the perception capability of
the human visual system, and full-data
presentation leads to considerable con-
trast reduction. Identification of the an-
atomically relevant range of exposures
is essential for optimal display of the
image.
This task is typically achieved through
two steps. First, the collimated area is
segmented to identify the exposed area
and thus exclude unexposed areas from
further analysis. Second, the anatomi-
cally relevant range of exposures in the
exposed area is identified. The most
common technique for this task is histo-
gram analysis of the image data. On the
basis of the expected general distribu-
tion of pixel values in the anatomic area
of interest, the image system marks the
range of the detector signal of interest
to be used for postprocessing.
Image Postprocessing
Once the raw image data are corrected
for inherent “flaws” and the useful range
of image data is identified, the data un-
dergo image postprocessing. Digital ra-
diography has utilized various digital
postprocessing algorithms for enhanced
image display of chest radiographs.
Broadly speaking, these algorithms can
be categorized into three types: gray-
scale processing, edge enhancement,
and multifrequency processing (48,49).
Gray-scale processing.—This pro-
cess involves the conversion of detector
signal values to display values. In this
process, the display intensities of an im-
age are changed by means of either a
look-up table or windowing and level-
ing. Most systems employ a response
look-up table similar to the Hurter and
Driffield response of screen-film sys-
tems, so that digital chest radiographs
look similar to conventional film images.
Edge enhancement.—This process
aims to enhance fine details within the
image by manipulating the high-fre-
quency content of the radiograph, most
commonly by using a variant of the un-
sharp masking technique in which a
blurred version of the image is formed,
and a fraction of the resultant image is
subtracted from to the original image.
The process is commonly used to com-
pensate for the lower inherent resolu-
tion performance of CR images. How-
ever, its use is often balanced against
the implied enhancement of quantum
mottle within the image and the unusu-
ally textured appearance of the lungs.
Multifrequency processing.—While
edge enhancement offers only a simplis-
tic modification of spatial frequencies
on the radiograph, multifrequency pro-
cessing involves a more flexible manipu-
lation of multiple portions of the fre-
quency spectrum. The image is initially
decomposed into multiple frequency
components. The component images
are then weighted and added back to-
gether. If the processing parameters are
set optimally, the resultant image can
compress the overall dynamic range of
the image while at the same time en-
hance local contrast. This is of particu-
lar utility in chest radiography, where
the details of opaque regions of the im-
age are made visible with no compro-
mise in the contrast in the lung regions.
The widely used MUSICA multiscale im-
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
670 Radiology: Volume 241: Number 3—December 2006
age-processing package offered by Agfa
(Greenville, SC) is an example of this
type of processing (50).
While these algorithms have en-
abled flexibility in the presentation qual-
ity of chest radiographs, most chest ra-
diography systems are set up to provide
digital chest radiographs that mimic the
appearance of screen-film images, with
varying degrees of success. While it is
possible to use the appearance flexibility
of digital radiographs to optimize the
system in terms of diagnostic perfor-
mance, that task has remained largely
untackled. One reason, perhaps, has
been the large number of abnormalities
of interest on chest radiographs, each of
which might need to be optimized inde-
pendently. Furthermore, there is uncer-
tainty as to the extent that image post-
processing algorithms can improve the
presentation of subtle lesions without
similar enhancement of anatomic pat-
terns and increased false-positive rates.
Display Developments
Once processed, the digital chest radio-
graph must be viewed by a radiologist.
Soft-copy display is an essential element
of contemporary digital chest radiogra-
phy, because many advantages of digital
imaging cannot be realized without soft-
Figure 6
Figure 6: Effects of various (a– c) gray-scale and (d–f) equalization postprocessing schemes on appearance of a posteroanterior chest radiograph. Gray-scale pro-
cessing improves contrast of image features with a corresponding reduction in latitude (ie, range of data that is properly displayed). Equalization, on the other hand, pro-
vides improved visualization of details without a corresponding reduction in latitude. (Image courtesy of M. J. Flynn, PhD, Henry Ford Hospital, Detroit, Mich.)
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
Radiology: Volume 241: Number 3—December 2006 671
copy display. The conventional method
to display digital radiographs has been
on cathode-ray tubes, which currently
still dominate the market (51). More
recently, however, active-matrix liquid-
crystal displays are rapidly replacing
cathode-ray tubes in many facilities (52–
54). The advantages of liquid-crystal dis-
plays include improved resolution, re-
duced weight, smaller form factor, re-
duced reflection, improved bit depth, and
improved luminance range (55), although
their disadvantages in terms of angular
response and structured noise have not
yet been fully addressed (56–58).
Another recent trend in soft-copy
display has been the increased accep-
tance of color monitors, some of which
have shown acceptable technical perfor-
mance (59) for radiographic applica-
tions. With cathode-ray tubes, a mono-
chrome monitor offers important ad-
vantages over a color monitor in terms
of image quality due to improved bright-
ness, reduced glare, reduced reflection,
and improved resolution (55). There-
fore, color cathode-ray tubes have not
demonstrated adequate performance
for clinical use. Current color liquid-
crystal displays, however, do not have
the same drawbacks as do color cathode-
ray tubes, other than reduced brightness,
which can be tolerated given the fact that
most current liquid-crystal displays have
better luminance response. The use of
color monitors offers the advantage of be-
ing able to accommodate applications
other than image viewing on the same
device, with workflow and multitasking
advantages. Color monitors would also
make it possible to take advantage of
color for viewing multidimensional chest
images on the same display. Current
commercial offerings also have enabled
the luminance calibration of color dis-
plays to the gray-scale standard display
function (60). It is thus expected that
color liquid-crystal displays will gradually
replace the monochrome monitors in
clinical practice.
Application Developments
As noted earlier, discerning subtle le-
sions in chest radiographs is made diffi-
cult by the confluence of anatomy that
overlies the lesion. An early attempt at
overcoming poor lesion conspicuity
was equalization radiography (61,62).
Equalization was developed to improve
the visibility of lesions in dense regions
of the chest such as the mediastinum
and the retrocardiac and retrodiaphrag-
matic areas. With screen-film radiogra-
phy, these areas of the chest were typi-
cally underexposed and showed poor le-
sion contrast owing to the shape of the
Hurter and Driffield curve of the film.
Equalization modulated the incident in-
tensity onto the patient in such a way
that a higher exposure was delivered to
the dense regions, and a lower exposure
was delivered to the unobscured lungs.
This process forced all of the thoracic
regions into the higher-contrast “linear”
portion of the film response curve. Stud-
ies indicated significantly improved de-
tection of lesions when equalization was
used (62,63). Despite its promise, equal-
ization has largely disappeared from clin-
ical use because of the edge-enhanced
appearance imposed on the images,
which some found difficult to interpret,
and also because of the more recent
transition to digital imaging and away
from screen-film radiography.
The advent of digital chest radiogra-
phy in the 1980s enabled the develop-
ment of new techniques to improve the
detection of subtle lesions. These tech-
niques included algorithms, typically
coupled with methodological innova-
tions that used some aspect of imaging
physics to improve conspicuity, and/or
image subtraction strategies. Three no-
table techniques are dual-energy imag-
Figure 7
Figure 7: Dual-energy subtraction radiography in healthy middle-aged woman. Conventional (a) posteroanterior, (b) bone-subtracted, and (c) soft-tissue–subtracted
images are normal except for scoliosis. Note improved depiction of vascular anatomy in b.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
672 Radiology: Volume 241: Number 3—December 2006
ing, temporal subtraction imaging, and
digital tomosynthesis. All of these tech-
niques are implemented by using a con-
ventional chest radiography system cou-
pled with a digital imaging receptor.
Dual-Energy Subtraction Imaging
Dual-energy subtraction imaging can be
used to generate images of two indepen-
dent tissue types, most commonly bone
and soft tissue. The dual-energy tech-
nique distinguishes bone from soft tis-
sue by using the known energy depen-
dence of x-ray attenuation in soft tissue
and in bone. Calcified structures attenu-
ate far more heavily, by means of photo-
electric absorption, than do soft-tissue
structures; thus, the contrast of calcium
diminishes with increases in beam en-
ergy much faster than does the contrast
of soft tissue. Thus, if two images are
acquired at different beam energies, the
image obtained at the lower energy will
show a larger fraction of contrast from
bone than from soft tissue. These two
images may be combined in such a way
that the soft-tissue or calcium compo-
nents can be exactly isolated. Typically,
an image containing only calcified struc-
tures and an image containing only soft-
tissue structures are generated (Fig 7).
Thus, dual-energy subtraction radiogra-
phy can improve lung nodule conspicu-
ity by eliminating overlying anatomic
noise from the bones. The technique
can also be used to better demonstrate
calcium in lesions (64–68).
Although the dual-energy technique
was proposed as early as the 1950s (69), it
was not until practical digital radiographic
detectors became available in the 1980s
that dual-energy imaging was clinically fea-
sible for chest applications. There cur-
rently are two commercially available
methods for accomplishing dual-energy
imaging. These methods are based on dif-
ferent types of detectors. The first
method, based on CR storage-phosphor
plates, was developed in the late 1980s
(70–72). It generates low- and high-en-
ergy images by exposing a sandwich of
two CR plates with a copper filter be-
tween. The first plate records the stan-
dard chest image at a spectral beam
energy typical of conventional chest ra-
diography. The second plate records a
higher mean spectral beam energy, due
to beam hardening that occurs in the
intervening copper filter; this second
plate has worse image noise, however,
due to the loss of beam flux from the
copper filter. The low- and high-energy
images are recorded simultaneously
with the CR dual-energy method, with a
single x-ray exposure to the patient.
The second commercially available
dual-energy method uses flat-panel de-
tectors (73). In this embodiment, a
sandwich detector configuration is not
practical, so two separate x-ray expo-
sures are made of the patient. The first
exposure is at a standard voltage for
chest radiography (typically, 120 kV),
and the second is acquired at a lower
voltage (typically, 60 kV). These images
are separated in time by up to several
hundred milliseconds, so there is the
potential for some motion of patient
anatomy between exposures, thus giv-
ing rise to some potential edge artifacts
in the resulting tissue and bone im-
ages. However, the image quality of the
flat-panel dual-energy images is much
higher than that of the CR embodiment,
owing to better energy separation be-
tween the low- and high-energy beams,
higher x-ray flux in the high-energy im-
age, and better detective quantum effi-
ciency of the flat-panel detector, relative
to those of CR. Image postprocessing is
accomplished with the flat-panel dual-
energy images to mitigate anatomic mis-
registration between the low- and high-
energy images, but some slight edge ef-
fects still persist (Fig 8).
Considerable attention has been
given to optimizing the acquisition and
processing methods for dual-energy im-
aging. The effects of scattered radiation
have been considered (71,74–76), as
has the importance of accurate account-
ing for beam hardening in the separa-
tion of tissue and bone (77,78). It is also
important to include some type of post-
processing for noise suppression, re-
gardless of which dual-energy method is
used, because of the inherent decrease
in signal-to-noise ratio with dual-energy
relative to the ratio with conventional
chest radiography (79). Some of these
processing methods have been summa-
rized in a recent publication (80).
Dual-energy methods have been in
clinical use for several years, and there
are data in the literature that indicate
that dual-energy imaging can improve
detection and classification of pulmo-
nary nodules. Early reports (65,67,
70,81) indicated statistically significant
improvements in the detection of pul-
monary nodules and patterns of calcifi-
cation (Fig 9). Recent studies in which a
flat-panel dual-exposure system (Revo-
lution XQ/i; GE Healthcare, Milwaukee,
Wis) was used showed the clinical effi-
cacy of dual-energy subtraction for the
detection of calcified chest abnormali-
ties (82) and noncalcified pulmonary
nodules (83). For 37 calcified chest le-
sions, radiologists’ sensitivity signifi-
cantly increased from 36% to 66%,
while specificity remained constant at
73% (82). Statistically significant but
smaller improvements in sensitivity,
specificity, and confidence were also ob-
served for 59 noncalcified pulmonary
nodules ranging from 0.2 to 2.5 cm in
diameter (83).
Dual-energy imaging has also been
investigated for other applications. It
has been shown (84), for example, to
improve detection of coronary artery
Figure 8
Figure 8: Soft-tissue subtracted image from
dual-energy chest radiograph in patient with right
aortic arch. Excess cardiac motion results in in-
complete subtraction of soft-tissue components
and considerable artifact (arrow) at left cardiac
border.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
Radiology: Volume 241: Number 3—December 2006 673
and other cardiac calcifications (Fig 10).
On the other hand, dual-energy imaging
does not seem to improve detection of
interstitial disease (85).
The clinical use of dual-energy tech-
niques in chest imaging is still evolving.
Some institutions advocate dual-energy
radiography for all chest examinations,
precisely because one does not know, a
priori, which patients will have previ-
ously undiagnosed pulmonary nodules.
Other institutions, however, have ap-
plied dual-energy imaging more selec-
tively to subsets of patients in whom
nodules are more likely. Additional clin-
ical experience will likely be necessary
before a consensus is reached on the
best practices for the use of dual-energy
techniques in chest imaging.
Temporal Subtraction Imaging
Another way to improve the visual as-
sessment of chest radiographs is with
temporal image subtraction. Temporal
Figure 9
Figure 9: Dual-energy subtraction radiography in a healthy middle-aged man. (a) Conventional posteroanterior radiograph shows possible lung nodule (arrow) over-
lying right upper lobe. (b) Bone-subtracted image shows small soft-tissue nodule (arrow) in left lung apex, not seen on a. No nodule is seen in right upper lobe. (c) Soft-
tissue–subtracted image confirms that nodule seen on a represents calcification at first costochondral junction (arrow).
Figure 10
Figure 10: Dual-energy subtraction radiography in an elderly man. (a) Soft-tissue–subtracted posteroanterior image shows coronary artery calcification (arrow) not
clearly identified on (b) conventional posteroanterior image. (Image courtesy of R. C. Gilkeson, MD, University Hospital, Cleveland, Ohio.)
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
674 Radiology: Volume 241: Number 3—December 2006
subtraction techniques aim to selec-
tively enhance areas of interval change
by subtracting the patient’s previous ra-
diograph from the current one (86).
The quality of the difference image
strongly depends on the success of the
two-dimensional registration and warp-
ing of the two radiographs so that the
effect of patient positioning variation is
minimized (87–89). Generally, the dif-
ference image appears uniformly gray in
areas of no change. Areas that stand out
in the uniform gray background indicate
interval change (Fig 11). Several studies
(91–98) have shown that temporal sub-
traction improves the visual perception
of subtle abnormalities such as pulmo-
nary nodules, infiltrative opacities, and
diffuse lung disease. A 20% reduction in
the average reading time when tempo-
ral subtraction is used was noted as well
(91). Currently, temporal subtraction is
commercially available in Japan (99).
Digital Tomosynthesis
Section imaging is another method for im-
proving detection of subtle lesions such as
pulmonary nodules. Traditional geomet-
ric tomography, which produces a single
section image at a time, has been known
since the 1930s (100). In recent years,
however, with the advent of multisection
CT and other three-dimensional imaging
modalities, conventional geometric to-
mography has fallen out of favor and is
used today only in limited cases of excre-
tory urography and some skeletal imaging
applications. The difficulties with conven-
tional geometric tomography were that
only a single section could be acquired at
a time, and, if multiple sections were de-
sired, considerable positioning time and
patient dose were required. Digital tomo-
synthesis is a technique that has evolved
from conventional tomography and solves
many of the problems associated with the
earlier technique.
Digital tomosynthesis can produce
an unlimited number of section images
at arbitrary depths from a single set of
acquisition images. A digital detector,
conventional x-ray tube, and computer-
controlled apparatus to move the x-ray
tube are used; during motion of the
tube, a series of projection radiographs
are acquired, and the anatomy at differ-
ent depths in the patient changes orien-
tation in the projection images owing to
parallax. These projection images are
then shifted and added to bring into fo-
cus objects in a given plane. By varying
the amount of shift, different plane
depths can be reconstructed. Objects
outside of the focus plane are rendered
with varying amounts of blur.
A variety of reconstruction ap-
proaches have been investigated for to-
mosynthesis, although the simple shift-
and-add approach is the most common.
It is important to use a deblurring algo-
Figure 11
Figure 11: Temporal subtraction radiography in a
middle-aged patient. (a) Initial posteroanterior radio-
graph was interpreted as normal, even when com-
pared with (b) that from examination performed 1 year
previously. (c) Subtraction image suggests new
masses in both upper lobes (arrows), confirmed on
(d, e) transverse CT scans. Biopsy revealed synchro-
nous lung cancers. (Reprinted, with permission, from
reference 90.)
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
Radiology: Volume 241: Number 3—December 2006 675
rithm to eliminate the residual blur
from structures overlying the planes of
interest. Various approaches for deblur-
ring have been investigated, including ma-
trix-inversion tomosynthesis (101–105),
filtered back projection (106,107), and it-
erative restoration (108). These deblur-
ring methods produce section images
with excellent rendition of anatomy and
effective elimination of structures outside
the section of interest.
Tomosynthesis has been applied
to such diverse applications as angio-
graphic, dental, orthopedic, breast, and
chest imaging (104); currently, the ar-
eas receiving the most clinical and re-
search interest are breast and chest im-
aging. Investigators in our laboratory
are currently conducting an National In-
stitutes of Health–funded clinical trial of
the efficacy of tomosynthesis for im-
proving the detection of pulmonary nod-
ules. As part of this effort, a series of
optimization studies were conducted to
determine the best acquisition and re-
construction parameters for chest imag-
ing applications. It was found that 20° of
vertical motion, 71 projection images,
and 69 reconstructed planes are best
(109). Spacing of reconstructed sec-
tions is typically 3–5 mm. Several adja-
cent sections are averaged to produce a
slab image with much better image qual-
ity than a single thin section, but the
spacing of these sliding-average slabs
remains about 5 mm, sufficient to easily
depict nodules of several millimeters in
diameter. Total x-ray exposure for ac-
quisition of the tomosynthesis projec-
tion images is about equal to that for
one lateral screen-film radiograph.
In a pilot study of 20 human subjects
(110), tomosynthesis provided subjec-
tively far superior visualization of nod-
ules, vasculature, airways, and ribs than
did conventional posteroanterior chest
radiographs (Figs 12–14). In the pilot
study, preliminary evaluation revealed
considerable improvement in the detec-
tion of CT-confirmed nodules with digi-
tal tomosynthesis compared with detec-
tion with conventional posteroanterior
radiographs, but these findings must be
confirmed quantitatively in the larger
ongoing National Institutes of Health
trial. Early indications are that tomo-
synthesis may offer an improvement
over conventional radiography in the vi-
sualization of chest anatomy, particu-
larly pulmonary nodules, at a lower ra-
diation dose than with CT. This tech-
nique may also prove to be less expensive
than CT because of the anticipated cost of
soon-to-be-available commercial equip-
ment. Tomosynthesis is not envisioned as
a replacement for CT (owing to its re-
duced resolution in the depth direction),
but it does appear to offer potential for
improved diagnosis when used as an ad-
junct to conventional chest radiography.
A commercial chest tomosynthesis prod-
uct is being readied for market.
CAD and CADx Systems
Digital image data manipulation paved
the way for the automated diagnostic
interpretation of chest radiographs
as well. CAD and CADx technology
emerged 15 years ago and has slowly but
steadily made its way into the clinical
arena. This rapidly expanding research
field shifts the focus from human percep-
tion to automated decision making. The
clinical role of CAD and CADx technology
is highly debated and continuously evolv-
ing. Currently, CAD technology has a
complementary role in clinical practice
as a second opinion, as long as radiolo-
gists understand the capabilities and
limitations of CAD (99). Any image-
based decision (human or computer-
ized) is always limited by the fundamen-
tal constraints of the imaging modality.
From an engineering point of
view, CAD and CADx systems typically
rely on a carefully selected combination
of elaborate image-processing, pattern-
recognition, and artificial intelligence
techniques. Thus far, the application of
CAD and CADx analysis in chest radiog-
raphy has followed a traditional hierar-
chic model of first detecting and then
characterizing potential abnormalities
(Fig 15) (111). Initially, image-process-
ing algorithms are applied to identify
regions of interest that appear suspi-
cious according to predefined clinical
expectations. Subsequently, detailed im-
age feature analysis seeks to capture the
morphologic and textural characteristics
of the candidate regions. Finally, feature-
based decision analysis is implemented
to provide a definitive assessment of the
candidate regions. The most important
among the advances in decision-making
analysis is the application of artificial
intelligence techniques such as artificial
neural networks and knowledge-based
systems.
The overwhelming majority of chest
radiography CAD applications involve
the detection of pulmonary nodules.
There are numerous publications on the
topic (112). The proposed CAD tech-
niques involve painstakingly optimized
combinations of image-processing algo-
rithms (ie, gray-level thresholding, mul-
tiresolution analysis, spatial filtering,
template matching, morphologic and
textural analysis, model-based analysis)
with statistical or artificial intelligence–
based decision models. Typically, mor-
phology-based image processing is ap-
plied to detect nodular-appearing struc-
tures, while more detailed morphologic
and texture analyses follow to eliminate
false-positive nodule candidates. The fi-
nal decision is made by applying a linear
classifier, a neural network, or a rule-
base algorithm that carefully merges the
image findings into a final binary deci-
sion regarding the presence of a nodule
at a particular image location.
Owing to lack of benchmark image
databases, the reported results vary
substantially, and direct comparison is
impossible because of differences in the
size and difficulty level of the private
image data sets. Regardless, for all tech-
niques it is a struggle to maintain a clin-
ically acceptable sensitivity level while
reducing the number of false-positive
detections generated because of over-
lapping ribs or vessels. Several labora-
tory observer studies have tested the
clinical potential of CAD in a comple-
mentary role for lung nodule detection.
Reported results (97,99,113–118) show
that CAD can assist physicians in im-
proving their overall detection rate for
lung nodules.
There is only one commercially
available CAD system in the United
States for the detection of pulmonary
nodules in both digitized and digitally
acquired chest radiographs. The Rapid-
Screen system (Riverain Medical, Mi-
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
676 Radiology: Volume 241: Number 3—December 2006
amisburg, Ohio) was initially approved
for clinical use by the Food and Drug
Administration (FDA) in July 2001. In
evaluation studies presented to the FDA
for premarket approval (119), it was
shown that the system helped radiolo-
gists improve their detection rate for
small lung nodules (9–14.5-mm diame-
ter) by 21%. Other commercial CAD
systems for lung nodule detection are
thus far available only in Japan (120).
Although not clinically available,
several investigators have explored the
feasibility of computerized image analy-
sis for determining the malignancy sta-
tus of pulmonary nodules. The overall
aim is to develop CADx systems that
could potentially reduce the number of
unnecessary diagnostic CT studies.
Some laboratory observer studies have
shown promising results for such an ap-
plication (96,121).
Another popular application of CAD
in chest radiography is in the detection
and differential diagnosis of interstitial
lung disease (ILD). Both tasks are con-
sidered clinically difficult and are often
burdened with subjective assessment
and lack of quantifiable descriptions.
Unlike the case with pulmonary nod-
ules, the radiographic manifestations of
ILD are diverse, and its visual percep-
tion and differentiation rely more
heavily on texture than on morphology.
As a consequence, researchers have fo-
cused their attention on applying so-
Figure 12
Figure 12: Images in middle-aged woman with history of right partial mastec-
tomy for breast cancer who presented for routine follow-up (same patient as in Fig
4). (a) Digital tomosynthesis section image of whole chest and (b) magnified sec-
tion images of right lower lobe clearly show right lower lobe nodule (arrows).
(c) Conventional posteroanterior radiograph is shown for comparison.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
Radiology: Volume 241: Number 3—December 2006 677
phisticated texture-analysis techniques
as the foundation of CAD and CADx
systems targeting ILD (112). Results of
limited observer studies suggest the
clinical potential of these systems for
substantial improvement in radiologists’
performance (96,122–124). However,
more work is needed to establish the
clinical usefulness of these CAD sys-
tems. Finally, other less-well-studied
CAD applications in chest radiography
involve the detection of cardiomegaly
(125), pneumothorax (126,127), inter-
val changes (128), and tuberculosis
(129).
Given the increasingly digital nature
of chest radiography, CAD will most
certainly be an integral part of clinical
practice. However, the existing para-
digm of CAD playing a complementary
role for specific clinical tasks is rather
limited. Beyond improving diagnostic
accuracy, there is high demand regard-
ing general diagnostic tasks (130), in-
terpretive capabilities, interactive na-
ture, and individualized guidance in pa-
tient care (eg, optimal timing for follow-
Figure 13
Figure 13: Images in middle-aged man. (a) Conventional posteroanterior radio-
graph, (b) digital tomosynthesis section image of whole chest, and (c) magnified
section images of right hilum show 15-mm nodule (arrows) overlying right hilum.
Despite relatively large size of this nodule, it cannot be seen on a owing to superim-
position of hilar vessels.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
678 Radiology: Volume 241: Number 3—December 2006
up). Consequently, CAD is expected to
keep evolving to meet the increasing
new challenges of chest radiography.
Clinical Perspective
Over the past decade there have been
remarkable advances in the technology
applied to conventional thoracic imag-
ing. CR has rapidly become the stan-
dard for bedside chest imaging in the
United States. Direct radiography has
rapidly replaced fixed film-based chest
units in most U.S. academic radiology
departments and is rapidly replacing
such units in the community setting as
well. The impetus for these changes can
be largely attributed to the advantages
inherent in digital imaging. Consistently
high-quality images and a marked re-
duction in the number of repeat exami-
nations required because of technical
causes have made digital imaging a fa-
vorite of physicians and technologists
alike. The ability to readily incorporate
digital images into a picture archiving
and communication system (PACS) al-
lows for much improved communica-
tion between radiologists and referring
physicians and has eliminated the prob-
lem of the “lost film.” The improved
availability of critical images and en-
hanced communication provided through
Figure 14
Figure 14: Images in middle-aged man. (a) Conventional posteroanterior radiograph shows possible nodule (arrow) overlying the right first rib. (b) Digital tomosyn-
thesis section images clearly show that this opacity is due to calcification (arrows) at first costochondral junction.
Figure 15
Figure 15: Flow diagram illus-
trates operation of CAD system.
STATE OF THE ART: Recent Advances in Chest Radiography McAdams et al
Radiology: Volume 241: Number 3—December 2006 679
PACS has markedly improved the effi-
ciency of both inpatient and outpatient
health care operations. These improved
efficiencies, combined with the improved
satisfaction on the part of both physicians
and patients, have more than justified the
increased costs associated with these
newer technologies.
Perhaps the most exciting feature of
these new techniques is the evolving op-
portunity to further enhance the diag-
nostic capabilities and impact of digital
chest examinations. In particular, the
opportunities for direct CAD of various
lesions through sophisticated computer
programs, as discussed in this article,
offer the possibility of enhancing the ra-
diologist’s accuracy while at the same
time improving efficiency.
The introduction of newer, hereto-
fore unavailable techniques such as dig-
ital tomosynthesis again hold the prom-
ise of further revolutionizing what has
now become conventional digital chest
imaging. As discussed in this article, the
opportunity to provide tomographic im-
ages of the chest easily and routinely,
thus removing overlying and frequently
confusing background structures, again
holds the promise of substantial im-
provements in the diagnostic accuracy
of conventional chest imaging. Com-
bined with other digitally driven tech-
niques such as dual-energy imaging and
temporal subtraction imaging, the op-
portunities for dramatic improvement
in the diagnostic capabilities of conven-
tional digital chest imaging seem prom-
ising. Obviously, the effect of these new
technologies and of those still to come
will need rigorous scientific validation to
ensure that the reality truly fulfills the
promise of these exciting new advance-
ments.
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