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IMAGE QUALITY IN EXTENDED ARC FILTERED DIGITAL
TOMOSYNTHESIS
C. Badea, Z. Kolitsi and N. Pallikarakis
Department of Medical Physics, University of Patras, Patras 26500, Greece
Correspondence: Nicolas Pallikarakis, Department of Medical Physics,
University of Patras, Patras 26500, Greece
Tel: +30-61-996112
Fax:+30-61-999855
e-mail: [email protected]
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Abstract
Purpose: To study image quality in Filtered Digital Tomosynthesis (FDTS)
tomograms as a function of their reconstruction arc, using isocentrically
acquired, fluoroscopic projection data.
Material and Methods: Both Digital Tomosynthesis (DTS) and Cone Beam CT
(CBCT) reconstruction algorithms are based on backprojection and use cone
beam projection data as input. Under limited angle conditions, CBCT is reduced
to FDTS, where only a subset of projection data used for reconstruction.
The effect of the reconstruction arc on the spatial resolution, slice thickness,
contrast sensitivity, shape distortion and artifacts, was also experimentally
studied. The investigation was performed using both simulated and actual
fluoroscopic images.
Results and Conclusion: Image quality in terms of spatial resolution, slice
thickness, shape distortion and artifacts, improved with increasing
reconstruction arc and was optimized at 1800, while contrast continued to
improve as the arc was increased to 3600. However DTS was assessed to be
the technique of choice when reconstruction arcs of less than 40 degrees are
used. Consequently, FDTS may be successfully implemented in applications
involving extended arc reconstructions, in the range between 400 delimiting the
DTS domain and 3600 corresponding to CBCT.
Key words: tomosynthesis digital; imaging; volume; angiography.
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Cone Beam CT (CBCT) has been used with radiotherapy simulators, to produce
therapeutic-quality images, as those obtained using the systems’ CT option,
which satisfy the data specification for 3D treatment planning software (2).
CBCT exploits cone beam projection data acquired over a complete arc by
using a planar detector such as an image intensifier (3). There are, however,
situations where collecting projection data over 3600 is not feasible; in such
cases, limited angle reconstruction methods may be used.
DTS is a method of limited angle reconstruction of tomographic images,
produced at variable heights, on the basis of a set of angular projections (5).
The DTS reconstruction algorithms simulate classical tomography by either
translating and adding the projection images (8) or by deploying the
backprojection method, to transfer and deposit data at the intersection of each
ray with the plane of reconstruction (6). In all approaches, a limitation in the size
of sampling arc arises from the restricted movement of the tube-detector
assembly. DTS tomograms are invariably affected by tomographic noise, i.e.
blurred images of structural detail, lying outside the plane of interest, and
superimposed over the focused image of the fulcrum plane. Several
contributions have focused on enhancing the quality of these images by a
variety of methods involving post-processing of tomograms (1, 9), or by pre-
processing of projections (7, 11). Filtered Digital Tomosynthesis (FDTS)
involves the application of filtering to the projection data, followed by
backprojection (11).
This article comprises a study of image quality for FDTS reconstructed
tomograms using data collected with isocentric fluoroscopic units, such as the
radiotherapy simulator or the angiographic units. The effect of the reconstruction
arc on spatial resolution, slice thickness, contrast sensitivity, shape distortion
and artifacts, was experimentally investigated.
Material and Methods
Both DTS and CBCT reconstruction algorithms are based on backprojection and
use cone beam projection data as input. Under limited angle conditions, CBCT
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is reduced to FDTS, with only a subset of projection data used for
reconstruction.
The overall effect of filtering of projection images as well as the variation of a
basic set of image quality parameters as a function of the reconstruction arc
was investigated using simulated projection data and geometries of the
radiotherapy simulator. Simulated projections were generated with the use of a
software data generator for radiographic imaging investigations (12).
Additionally, a subjective visual assessment of image quality under different
reconstruction arcs, using DTS and FDTS was performed on tomograms
obtained using actual angiographic projection data from a contrast-enhanced
sheep lung. The phantom was imaged with the Philips DVI, Digital Angiographic
unit, operated at a source to isocenter distance equal to 67.5 cm and a source
to image intensifier distance equal to 92.5 cm. The imaging chain had a limiting
resolution of 12 lp/cm. Projection images were acquired every 20 over a 1200
arc using a DTS prototype system (10). All projections were filtered along each
row with a standard ramp filter and a Hamming window.
The following image characteristics were studied:
(i) Spatial resolution
Spatial resolution was measured using a simulated bar pattern phantom with
line pairs varying in size from 1 to 20 lp/cm. The object was considered to have
a thickness of 1mm and to be inclined at 450 with respect to the source detector
rotation plane. The oblique orientation of the bars was chosen in order to
provide visual information on the system’s ability to filter out noise at various
distances from the coronal plane of the phantom (13). The source to isocenter
distance was set to 100 cm and the source to image intensifier distance to 130
cm. The imaging chain was considered to have a limiting resolution of 20 lp/cm.
Projection images were generated at every 20 over a 3600 arc. Both DTS and
FDTS tomograms were reconstructed at various reconstruction arcs. Spatial
resolution was assessed by means of the Square Wave Response Function
(SWRF), determined over the complete range of spatial frequencies.
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(ii) Slice Thickness
Slice thickness was measured using the same set of data described above.
Measurements were performed for each spatial frequency by means of the Full
Width at Half Maximum (FWHM) of the intensity profiles taken along the
transverse axis of the corresponding pair of bars (4).
(iii) Contrast sensitivity
A second electronic phantom was designed for contrast sensitivity
investigations, consisting of an ellipsoid containing six equally sized spheres
(R=0.5 cm), equidistantly spaced and with their centers along the long diameter
of the middle coronal slice of the phantom. The spheres were of varying
densities ranging from 0 to 2.00 g/cm3 providing background contrast variations
of 2%, 5%, 10%, 20%, 30% and 100%. Contrast sensitivity, defined as the
difference in signal strength between the structure of interest and the
background was studied as a function of the reconstruction arc. For each
sphere, the arc needed to establish a minimum 2% contrast relative to the
background, was determined.
(iv) Shape distortion and artifacts
Artifacts and shape distortions are present in limited angle reconstructions. In
order to assess them, a spherical phantom was used, composed of a high
density material, placed inside a homogeneous medium of unit density. The
phantom was imaged with its center positioned on the isocenter. Central axial
tomograms, coinciding with the sampling plane, were reconstructed for different
reconstruction arcs and the ratios of the FWHM of the diameter profiles along
the horizontal and vertical directions were used for assessment of shape
distortions.
Results
Fig. 1 shows the SWRF plots using both the DTS and FDTS tomograms. The
slice thickness variation with the size of reconstruction arc for both DTS and
FDTS are presented in Fig. 2. Studies for a high (5 lp/cm) and a low (1 lp/cm)
spatial frequency are shown on the same graph. Contrast sensitivity for a range
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of background contrast conditions is given in the table. Shape distortion
dependency on the reconstruction arc is shown in Fig. 3. The effect of
increasing reconstruction arc on images of anatomic content is shown in Fig. 4,
for reconstructed tomograms of the contrast-injected sheep-lung phantom.
Three parallel coronal planes at 5 mm spacing distance were reconstructed with
DTS and FDTS using reconstruction arcs of 400 and 1200, respectively.
Discussion
The extent of the reconstruction arc has a significant impact on spatial
resolution (Fig.1). In the higher frequency range the two techniques provide
comparable results for arcs smaller than 1200. However, for larger
reconstruction arcs, FDTS demonstrates a clear advantage. On the other hand,
DTS may be considered the technique of choice when reconstruction arcs in the
range of 400 or less are used. An increase in the arc results in tomograms of
finer slice thickness (Fig.2). As shown by the table, high contrast structures,
such as vascular structures or markers used in radiotherapy, may be detected
under limited angle conditions, while low contrast structures will appear only on
extended arc reconstructions. In fact, our results show that, a full 3600
reconstruction i.e., CBCT, is necessary to detect a 2% contrast variation to the
background. The shape distortions present in limited arc reconstructions,
introduce problems (axial elongations) when defining contours of otherwise
discernable structures. Again, as seen in Fig. 3, reconstruction arcs of 1800 or
larger are required to eliminate such shape distortions. The same conclusion
can be drawn from the slice thickness results, shown in Fig. 2, not surprisingly,
since both concepts are related to the filtering of out-of-plane information.
Consequently, image quality in terms of, high contrast spatial resolution, slice
thickness, shape distortion and artifacts, improves with the reconstruction arc
and is optimized at 1800, while contrast continues to improve when the arc is
increasing towards 3600.
Conclusions
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Based on the above observations, it may be stated that the sampling range
between 400 and 3600, delimited by DTS and CBCT respectively, is the domain
where FDTS can be applied to the advantage of applications where sampling
over an extended arc is possible. FDTS with an extended arc may even
successfully substitute CBCT in applications, where densitometric information is
not required.
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References
1) BADEA C., KOLITSI Z. & PALLIKARAKIS N.: A wavelet-based method for removal
of out-of-plane structures in digital tomosynthesis. Comput Med Imaging
Graph. 22 (1998), 309.
2) CHO P., JOHNSON R. & GRIFFIN T.: Cone-beam CT for radiotherapy
applications. Phys. Med. Biol. 40 (1995), 1863.
3) FELDKAMP L., DAVIS L. & KRESS J.: Practical cone-beam algorithm. J. Opt.
Soc. Am. A1 (1984), 612.
4) GOODENOUGH D.J., LEVY J.R. & KASALES C.: Development of phantoms for
spiral CT. Comput. Med. Imaging Graph. 22 (1998), 247.
5) GRANT D.G.: Tomosynthesis: a three-dimensional radiographic imaging
technique. IEEE Trans. Biomed. Eng. 19 (1972), 20.
6) KAMPP T.D.:The Backprojection Method Applied to Classical Tomography.
Med. Phys. 13 (1985), 329.
7) KNUTSSON H.E., EDHOLM P., GRANLUND H.G. & PETTERSON C.U.:
Ectomography ¯¯ a new radiographic reconstruction method. I. Theory and
error estimates. IEEE Trans. Biomed. Eng. 27 (1980), 641.
8) KOLITSI Z., PANAYIOTAKIS G., ANASTASSOPOULOS V., SKODRAS A., &
PALLIKARAKIS N.: A multiple projection algorithm for digital tomosynthesis.
Med. Phys. 19 (1992), 1045.
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9) KOLITSI Z., PANAYIOTAKIS G. & PALLIKARAKIS N.: A method for selective
removal of out-of-plane structures in digital tomosynthesis. Med. Phys. 20
(1993), 47.
10) KOLITSI Z., YOLDASSIS N., SIOZOS T. & PALLIKARAKIS N.: Volume Imaging in
fluoroscopy: a clinical prototype system based on a generalised digital
tomosynthesis technique. Acta Radiol. 37 (1996), 741.
11) LAURITSCH G., HAERER W.: Theoretical framework for filtered back projection
in tomosynthesis. In Proceedings SPIE Conference In Image Processing
3338 San Diego (1998),1127.
12) LAZOS D., KOLITSI Z. & PALLIKARAKIS N.: A software data generator for
radiographic imaging investigations. IEEE Trans Inf. Technol. Biomed. 4(1),
(2000), 76.
13) PETERSSON C.U.: Computer-simulated object for testing principles for
radiographic reproduction of slices, applied to ectomography. Med. Biol.
Eng. Comput. 20 (1982), 425.
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List of Acronyms
DTS Digital Tomosynthesis
FDTS Filtered Digital Tomosynthesis
CBCT Cone Beam CT
FWHM Full Width at Half Maximum
SWRF Square Wave Response Function
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FIGURE CAPTIONS
Fig. 1. SWRF plots for different reconstruction arcs, for (a) DTS and (b) FDTS
reconstructed images. Simulated projection data for a bar pattern phantom have
been used.
Fig. 2. Slice thickness variation in DTS and FDTS with the size of reconstruction
arc. The effect has been studied for a high (5 lp/cm) and a low (1 lp/cm) spatial
frequency.
Fig. 3. Shape distortion and artifacts: the center axial section of the sphere has
been reconstructed and the ratio of the FWHM of the diameter profiles along the
horizontal and the vertical directions was plotted as a function of the
reconstruction arc. An axial tomogram reconstructed using an arc of 600 is
shown in the insert.
Fig. 4. A tomographic sequence of three transversal planes distanced at 0.5 cm
through the angiographic phantom reconstructed using DTS and FDTS at 400
and 1200 reconstruction arcs.
Table. Minimum reconstruction arc required to establish a 2% contrast
detectability for different background contrast.
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0 2 4 6 8 10 12 14 16 18 200.0
0.2
0.4
0.6
0.8
1.0
DTS 40 0
DTS 80 0
DTS 120 0
DTS 180 0
DTS 360 0
SW
RF
Spatial Frequency (lp/cm )
0 2 4 6 8 10 12 14 16 18 200.0
0.2
0.4
0.6
0.8
1.0
FDTS 40 0
FDTS 80 0
FDTS 120 0
FDTS 180 0
FDTS 360 0
SW
RF
Spatial Frequency(lp/cm )
(b)
(a)
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0 20 40 60 80 100 120 140 160 180
0.0
0.5
1.0
1.5
2.0
2.5
3.0
3.5
Slic
e Th
ickn
ess
(cm
)
Reconstruction arc (degrees)
DTS (1 lp/cm)
DTS (5 lp/cm)
FDTS (1 lp/cm)
FDTS (5 lp/cm)
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0 50 100 150 200 250 300 3500.0
0.2
0.4
0.6
0.8
1.0
FWH
M H
OR
IZO
NTA
L / F
WH
M V
ER
TIC
AL
RECONSTRUCTION ARC (degrees)
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Object 1 2 3 4 5 6
Object Contrast 2% 5% 10% 20% 30% 100% Min Arc for contrast detectability 3600 1440 700 360 200 00