Masahisa Onoguchi.et al.

SJC. 2020; 1(3): 82 - 89

Larix Publications

Singapore Journal of Cardiology
https://sjcjournal.com/

Vol. 1, Issue 3, 2020

ISSN: 2737-4025

Original Article
Prerequisite for projection data and reconstruction not to cause truncation artifacts in myocardial perfusion single- photon
emission computed tomography: Phantom study
Kotatsu Tsuboi1, 2, Masahisa Onoguchi*2, Mitsuo Sugimoto3, Takayuki Shibutani2, Akio Nagaki4 and Akihiro Kikuchi5*1 Department of Radiological Technology, Hamamatsu Red Cross Hospital, Japan
2 Department of Quantum Medical Technology, Graduate School of Medical Sciences, Kanazawa University, Japan
3 Department of Radiology, Nagoya Daini Red Cross Hospital, Japan
4 Department of Radiological Technology, Kurashiki Central Hospital, Japan
5 Department of Radiological Technology, Faculty of Health Sciences, Hokkaido University of Science, Japan*onoguchi@staff.kanazawa-u.ac.jp
Received on: 31-08-2020; Revised and Accepted on: 09-09-2020

ABSTRACT

Myocardial perfusion single-photon emission computed tomography (SPECT) studies are used widely in the evaluation and diagnosis ofcoronary artery disease. Although one method to improve the spatial resolution is zooming acquisition, truncation artifact occurs inreconstructed tomographic images. To date, it is unclear how much truncation (area and radioactivity) of projection data would affectmyocardial image.
The aim of this study is to investigate the combination of truncated projection data conditions and image reconstruction methods that
do not require re-examination. We used a cylindrical and anthropomorphic torso phantom with 99mTc solution, and shifted the
projection data to simulate truncated liver tissue. SPECT images were acquired using a dual-detector gamma camera and reconstructedusing filtered back projection (FBP) and ordered subset expectation maximization (OSEM) to create transverse images. We comparedtruncation data and reference data (none truncated projection data) for count profile curve, uniformity, myocardial counts, and %uptake.
Our findings indicate that prerequisite for truncation data and image reconstruction method would not affect the myocardial image,when the area of truncation was < 17.5% and the count of the truncation portion was lower than that in the myocardium using FBP.
Keywords: Myocardium, single-photon emission computed tomography, filtered back projection.

1.

INTRODUCTION:

Myocardial perfusion single-photon emission computed
tomography (SPECT) studies are used widely in theevaluation and diagnosis of coronary artery disease [1].
However, the spatial resolution for SPECT imaging is lower*Corresponding author:
Masahisa Onoguchi,
Department of Quantum Medical Technology, Graduate
School of Medical Sciences, Kanazawa University Kodatsuno
5-11-80, Kanazawa, Ishikawa 920-0942, Japan.
Email: onoguchi@staff.kanazawa-u.ac.jp
Phone: +81 76 265 2526
DOI: doi.org/10.46978/sjc.20.1.2.14

than that of other modalities. One method to improve thespatial resolution is zooming
acquisition[2].
The
acquisition may cause the loss of right-side bodyradioactivity outside the field of view (FOV), if heart is placedin the center of acquisition orbit. According to the principle of
tomography, images cannot be reconstructed accurately using
truncated projection data [3]. Therefore, an artifact, known asa truncation artifact occurs in reconstructed tomographic
images [4- 10].
Most studies of truncation artifacts in myocardial perfusion
SPECT have reported on the effects of the attenuation maps
generated from a truncated transmission data on thereconstructed image [4-7]. On the other hand, a few studies
have investigated whether the truncation artifact affects the
myocardial image without attenuation correction if the
myocardial image is not truncated outside the FOV at any© 2020, SJC. All Rights Reserved

Truncation artifacts in Myocardial Perfusion SPECT

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Masahisa Onoguchi.et al.

SJC. 2020; 1(3): 82 - 89

projection view, but the radioactivity of body tissue istruncated at some views [8-10]. Image reconstructed fromtruncated projection data display various artifacts anddistortions. A ring- shaped high-count artifact that appears on
the truncation edge is one of the truncation artifacts[5,7,8,10]. Apart from the artifacts, truncated projection
data affect counts and uniformity in reconstructedmyocardial image if truncated area becomes large [8-10]. Also,
severity of truncation artifact by the difference of image
reconstruction method have been discussed in previous
studies [9-10].
Few studies have attempted to investigate the influence ofradioactivity concentration in truncation portion such as lungor liver on the myocardial image. In addition, it has not beenfound that how much area of truncation affects the myocardial
image. Moreover, Rohmer et al. found that small inaccuracies
in image reconstructed from truncated projection data havelittle effect on clinical interpretation [8]. For these reasons,even if the projection data was truncated in clinicalexamination, we could not determine the need for reexamination.
We hypothesized that the effect of truncation artifacts for the
myocardial image depends on the area and radioactivity
concentration in the truncation portion and the difference ofimage reconstruction method. The aim of this study is toinvestigate the necessary prerequisite for projection data
conditions and image reconstruction method that do not
require re-examination.
2.

METHODS

2.1 Phantoms
A cylindrical phantom (JSP type, Kyoto Kagaku Co., Ltd., Kyoto,
Japan) was used. The cylindrical phantom had a diameter andheight of 22.0 cm. The phantom was filled with 90.0 kBq/mL of
99mTc solution. Moreover, an anthropomorphic torso
phantom (HL type, Kyoto Kagaku Co., Ltd., Kyoto, Japan)
containing shapes of the normal myocardium, lungs, spine, andliver was also used. The phantom was representative of thetorso of a medium-sized adult. The myocardium was filled with
90.0 kBq/mL of 99mTc solution. The liver was filled withvarying concentrations of 99mTc solution so that the heart–
liver relative radioactivity concentration ratios (HLradioactivity ratios) were 1:0.25, 1:0.5, and 1:1.0. We also
prepared a water-filled liver so that the HL radioactivity ratio
was 1:0. The left ventricular cavity, right ventricle, andmediastinum were filled with water. The lungs contained
beads of polystyrene foam without radioactivity. The liver was
the truncated region.
2.2 Acquisition and image processing
SPECT images were acquired using a dual-detector gamma
camera (BrightView, Philips Healthcare, Cleveland, OH, USA)equipped with a low-energy high-resolution collimator. A totalof 64 projection images were obtained from a 180° ellipticalorbit (90° per detector) with a 40.9-cm detector mask (zoom,
1.46) and matrix size of 64×64. The projection data wereacquired for 30 s per projection. A 20% energy window was set
symmetrically over 140 keV of 99mTc. Projection data were
processed using the JETStream Workspace (Philips
Healthcare), and images were reconstructed using filtered
back projection (FBP) and ordered subset expectation
maximization (OSEM) to create transverse images. In FBP, apreprocessing Butterworth filter with a cutoff frequency of
0.39 cycles/cm, an order of 8, and a ramp filter were used.
In OSEM, a preprocessing Butterworth filter with a cutoff
frequency of 0.39 cycles/cm and an order of 8 were used with
3 iterations and 16 subsets. The parameters are the sameas the clinical default reconstruction in our institution. No
attenuation or scatter correction was used. The cylindricalphantom was placed in the center of the FOV and used as areference image. The center of rotation in SPECT was shiftedfrom the center of the phantom while being visuallymonitored with an emission monitor at the anterior viewof projection data, and images were obtained to truncate
the right side (toward the liver) of the phantom. A
reference image and truncation images with 4 different
areas of truncation were acquired (c1–c4). In theanthropomorphic torso phantom, a reference image andtruncation images with 3 different areas of truncation wereacquired (a1–a3). SPECT images were acquired 6 times at eachposition. Count profile curves were determined in thehorizontal direction of the center of the transverse image forthe cylindrical phantom. In the anthropomorphic torso
phantom, the count profile curves were determined in thehorizontal direction at the level of the heart. The area oftruncation was calculated
Using the following equation:
Area of truncation = (A-B) / A×100%,
where A is the phantom diameter of the reference image in the
FOV and B is the phantom diameter in the truncation image inthe FOV (Fig. 1). The A and B of the diameters were calculated
from the count profile curve. The transverse images of thecylindrical and anthropomorphic torso phantoms are shown in
Fig. 2. In the cylindrical phantom, the areas of truncation for c1,
c2, c3, and c4 were 18.2 ± 0, 29.7 ± 0, 37.8 ± 0, and 51.4 ± 0%,
respectively. In the anthropomorphic torso phantom, the areasof truncation for a1, a2, and a3 were 17.5 ± 2.1, 32.9 ± 1.4, and49.1 ± 1.4%, respectively. The projection data for the anteriorview are presented in Fig. 3. The liver-to-myocardium countratios per pixel were 1.21 ± 0.02, 2.32 ± 0.22, and 4.03 ± 0.10
for HL radioactivity ratios 1:0.25, 1:0.5, and 1:1.0, respectively.
We used the Daemon Research Image Processor (FUJIFILM
Toyama Chemical Co., Ltd, Tokyo, Japan) in the image analysis
and quantitative perfusion SPECT (Cedars-Sinai Medical
Center, Los Angeles, CA, USA), version 7.0, in the polar map
creation.

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2.3. Image evaluation

3.2. Uniformity (CVs)

The mean count profile curves were determined in thehorizontal direction of the center from the average of fivetransverse images of the cylindrical phantom. The countprofiles curves for the truncation image were visuallycompared with those of the reference image. Additionally,
we investigated the uniformity in the FOV of the truncation
data. The rectangular region of interest (ROI) was manually set
on the cylindrical phantom in the FOV (Fig. 4). The coefficientsof variation (CVs) of the truncation image were comparedwith those of the reference image. The CV was calculated asfollows:

Results of the CVs are shown in Fig. 6. In FBP, the differences in
the CVs were not observed between the reference andtruncation data. However, in OSEM, an increase in the CVs wasobserved in c2, c3, and c4 of the truncation data compared tothose of the reference data. The CVs were higher with theincreasing area of truncation (The CVs of the reference, c2, c3,
and c4 were 6.4 ± 1.0, 7.8 ± 1.2, 9.0 ± 1.4, and 14.3 ± 2.3,
respectively.)CV (%) = SD / mean × 100,
where SD and mean are the standard deviation and averagevalue in the ROIs, respectively.
In the anthropomorphic torso phantom, we compared the
myocardial counts of the truncation image with those of thereference image in the ROI on the myocardium of threeconsecutive slices of the transverse image. Moreover, the %uptake was calculated using the standard 17-segment model ofthe left ventricle [11]. In segments 7-17, the average % uptakesof the truncation image were compared to those of thereference image.
2.4. Statistical analysis
Continuous valuables were expressed as the mean ± SD. The
CVs at each degree of truncation versus the reference image
using the cylindrical phantom were compared using one-way
repeated-measures analysis of variance. The Friedman test
was used to compare the myocardial counts between thetruncation and reference images. For the % uptake comparisonof the polar map, the coin method was used after the Friedman
test. The exact P-value in a small paired sample in many ties in
the 6 observations was calculated using the R package “coin,” aclass of permutation test. A post hoc analysis with Bonferroni
correction was performed.
A P-value of <0.05 was considered to be statistically significant.
All statistical analyses were performed using EZR (Saitama
Medical Center, Jichi Medical University, Saitama, Japan), agraphical user interface for R 3.3.1 (R Foundation for StatisticalComputing, Vienna, Austria) [12].
3. RESULTS
3.1. Count profile curve
In the evaluation of the cylindrical phantom, both FBP and
OSEM produced a high-count artifact in the truncation portionof the phantom in transverse images (Fig. 5). Compared with
FBP, the artifact of OSEM was higher with a larger area oftruncation. Moreover, in OSEM, a larger fluctuation in the countprofile curve was observed near the high-count artifact thanthat in FBP.

3.3. Myocardial counts
Figure 7 shows the results of the myocardial count. In the HL
radioactivity ratio 1:0 of FBP, the differences in the myocardial
count were not observed between the truncation and referencedata.
However, in the HL radioactivity ratios 1:0.25 and 1:0.5 of FBP,
an increase in the myocardial count was observed in a2 and a3
data compared to those in the reference data. In the HL
radioactivity ratio 1:1.0, an increase in the myocardial count
was observed in a1, a2, and a3 data compared to those in thereference data. The myocardial counts for the reference, a1, a2,
and a3 were 132.3 ± 2.2, 135.5.4 ± 1.6, 147.4 ± 1.7, and 173.0 ±
1.5, respectively. Compared with the reference data, themyocardial count increase rates of a3 in FBP were 1.09, 1.15,
and 1.31 for the HL radioactivity ratios of 1:0.25, 1:0.5, and
1:1.0, respectively. In OSEM, the differences in the myocardial
count were not observed between the reference and truncation
data in the HL radioactivity ratios 1:0 and 1:1.0. In the HL
radioactivity ratio 1:0.25 in OSEM, an increase in the
myocardial count was observed in a1, a2, and a3 datacompared to those in the reference data. The myocardial
counts for the reference, a1, 2, and a3 were 285.1 ± 5.8, 312.1± 4.1, 313.3 ± 4.4, and 309.5 ± 6.6, respectively. In the HL
radioactivity ratio 1:0.5, an increase in the myocardial count
was observed only in a3 data compared to that in the reference
data. 3.4% uptake Figure 8 presents the % uptake of the polar
map for the reference and truncation data. In the HL
radioactivity ratio 1:0 and a1 of both FBP and OSEM, thedifference in % uptake for the truncation data was notobserved in all segments compared with those for thereference data. In the HL radioactivity ratio 1:0.25 of FBP, thedifference in % uptake was observed in a3 data compared tothat in the reference data. In the HL radioactivity ratios 1:0.5
and 1:1.0 of FBP, the difference in % uptake was observed in
a2 and a3 data compared to those in the reference data.
All % uptakes of the different segments in the truncation data
were higher than those in the reference data in FBP. In the
HL radioactivity ratios 1:0.25, 1:0.5, and 1:1.0 of OSEM, thedifference in % uptake was observed in a2 and a3 datacompared to those in the reference data. The % uptake ofdifferent segments increased in a2 of the HL radioactivity
ratios 1:0.25 and 1:0.5. In a2 of the HL radioactivity ratio 1:1.0
and a3 of the HL radioactivity ratios 1:0.25, 1:0.5, and 1:1.0, the% uptake increased and decreased, respectively.
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In a3 of the HL radioactivity ratio 1:1.0, the % uptake
decreased in segments 7, 8, 13, 14, 15, and 17 and increased insegments 9, 10, 11, and 12 compared to those in the reference
data.
4.

DISCUSSION

In this study, the effect of truncated projection data on
myocardial image in myocardial perfusion SPECT wasinvestigated using cylindrical and anthropomorphic torso
phantoms for FBP and OSEM.
We shifted the projection data to simulate truncated livertissue and investigated the uniformity and count of the
myocardial image in the FOV. Our results supported the
hypothesis that the effect of truncation artifacts depends on
the area and radioactivity concentration in the truncation
portion, and the difference in the image reconstruction
method.
In both FBP and OSEM, the truncation data introduced a highcount artifact at the truncation edge in the cylindrical phantom.
However, the count profile curve on the truncation data in
OSEM was observed a larger high-count artifact and a larger
fluctuation compared with those in the FBP. As a result, an
increase in CVs was observed in the truncation data of the
OSEM compared to those in the reference data with a larger
area of truncation. An increase of CVs means decrease inuniformity within FOV. A previous study indicated thattruncated transmission CT data generated artifacts anddistortion in image reconstructed by the maximum likelihood
expectation maximization (MLEM) compared to that in the
FBP, especially for higher degrees of truncation [5]. The study
also noted that the cold ring artifact near the truncation edge
occurred in MLEM. Taking our results of the CVs into account,in the truncation data, OSEM may receive a greater influence
on reconstructed images than FBP. Therefore, we consider thatthe image reconstructed by OSEM has lower uniformity within
FOV than FBP.
In the anthropomorphic torso phantom, the area andradioactivity concentration in the truncated liver tissue waschanged. Then, the myocardial count on the transverse image
and the % uptake of the polar map were compared between
the reference and truncation data. We initially had to confirm
that there was no difference in the myocardial count and polar
map at each heart position within the FOV between thereference and truncation data of non-radioactivity in thetruncation portion (HL radioactivity ratio 1:0) [13, 14]. As aresult, both FBP and OSEM showed no difference in the
myocardial count and polar map in any truncation area
compared to those in the reference data (HL radioactivity ratio
1:0 in Figs. 7 and 8). Rohmer et al. used a mathematical cardiac
torso phantom to simulate a small cardiac SPECT camera thatwould be the liver outside the FOV [8]. The simulation was
conducted under the condition of only a HL radioactivity
ratio 1:1.0. They reported that myocardial counts increased in

FBP when the liver was outside the FOV. Our data were similar
to those reported by them, namely the myocardial counts in thetruncation data increased in FBP compared to those in thereference data. Then, the counts increased with a larger area
and a higher radioactivity concentration of the truncation
portion. A SPECT image is created from the projection data.
The truncated projection data include counts outside the FOV.
It is assumed that the count outside the FOV caused an increasein the myocardial count of the reconstructed image. Owing tothis, with an increasing count in the truncation portion, thecount in the FOV is higher than the true value.
Therefore, we believe that the increase in the myocardial countof the truncation data depends on the area and theradioactivity concentration of the truncation portion in FBP. In
contrast, in OSEM, although an increase in the myocardial
count of a1, a2, and a3 of the HL radioactivity ratio 1:0.25 wasobserved, no increase in the myocardial count wasobserved in the truncation data of the HL radioactivity ratio
1:1.0. The increase in the myocardial count did not show acertain trend in the area and radioactivity of the truncation
portion. These results may be related to the poor uniformity of
OSEM observed in the cylindrical phantom.
In the polar map of FBP, an increased % uptake was observedin a3 for the HL radioactivity ratio 1:0.25 and in a2 and a3 for
HL radioactivity ratios 1:0.5 and 1:1.0 compared with those in
the reference data. The number of segments tended to increase
from the septal side with a larger area and a higher
radioactivity concentration of the truncation portion. The
anthropomorphic torso phantom used in this study wastilted so that the heart and liver were in the same slice on
the transverse image. Thus, the transverse image of the
myocardium became a similar image to the short- axis image(Fig. 3). The truncated liver tissue was the septal side of the
myocardium. Accordingly, we speculate that the segment of %uptake, which was different from that of the reference data,
occurred on the septal side. In the polar map of OSEM, similar
to that of FBP, different % uptakes were observed in a2 and a3
for the HL radioactivity ratios 1:0.25, 1:0.5, and 1:1.0 comparedwith those in the reference data. However, the % uptake ofthe segment not only increased but also decreased
compared to those in the reference data. Laiush et al. reported
that the % bias was negative on the septal, the inferior andlateral sides in OSEM in the truncation data of the livercompared with those in the data without truncation [9]. We
speculate that these phenomena are characteristic of OSEM fortruncation data. In the cylindrical phantom, the radioactivity
concentrations inside and outside the FOV of the truncation
data were similar. On the other hand, the anthropomorphic
torso phantom had a larger liver as the truncation portion.
Even if the radioactivity concentration in the liver was lower
than that in the heart, the count per pixel of the truncated liver
was higher than that in the heart (For example, the liver-tomyocardium count ratio per pixel was 2.32 ± 0.22 for the HL
radioactivity ratio 1:0.5, Fig.3). In OSEM, we assume that the© 2020, SJC. All Rights Reserved

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decrease in uniformity observed in the cylindrical phantom
may have been further enhanced in the anthropomorphic torso
phantom.
For all of these reasons, in FBP, if the area of the truncation is< 17.5% (a1 of the anthropomorphic torso phantom) and thecount of the liver is lower than that in the myocardium on theanterior view of the projection data, we think that thetruncated projection data do not affect the myocardial image.
However, in OSEM, even if the radioactivity concentration in
the truncated liver tissue is lower than that in FBP, themyocardial count may be affected (HL activity ratio 1:0.25 of
OSEM in Fig.7). When performing quantitative assessments,
such as coronary blood flow reserve measurements using
OSEM [15, 16], it should be used for data without truncation.
Even if the radioactivity concentration in the truncation
portion is high, when the area of truncation is ≤ 17.5%, achange in the polar map is not recognized in both FBP and
OSEM compared with those in the data without truncation. In
contrast, when the area of truncation is > 17.5%, the polar map
differs from those in the reference data with a larger area anda higher radioactivity concentration of truncation portion. Our
results suggest that the increase or decrease of % uptake inthe truncation data depends on the reconstruction method.
Although zooming acquisition is useful for improving spatial
resolution of children and patients with a small heart [2], theacquisition may truncate a patient’s body contour. Image
reconstructed by truncated projection data on myocardial
perfusion SPECT has been considered to be inaccurate. It has
been well documented that truncation of the heart inprojection data produces artifacts in the reconstructedmyocardial image [17, 18]. However, if there is no truncationof the heart, to date, it is unclear how much truncation (areaand radioactivity) would affect myocardial image. Based on
the results of this study, it suggests that if the area of truncationis < 17.5% and the count of the truncation portion (including
bowels and liver) is lower than the myocardial count, if using
FBP, the myocardial image is not affected by the truncation
artifact.

5.

CONCLUSION

We investigated the effect of truncated projection data on the
myocardial image in myocardial perfusion SPECT using
cylindrical and anthropomorphic torso phantoms for FBP and
OSEM. The findings indicated that a prerequisite for truncation
data and image reconstruction methods would not affect the
myocardial image, when the area of truncation was < 17.5%
and the count of the truncation portion was lower than that in
the myocardium using FBP. The authors declare no conflicts ofinterest.
6.

FIGURE LEGENDS

Fig.1 Phantom diameter of the reference image (A) and thetruncation image (B) in the FOV.
a. Cylindrical phantom. b. Anthropomorphic torso phantom.

4.1 Limitations
This study has several limitations. We used only a 180° orbit
acquisition. Corrections such as scatter, attenuation, andcollimator aperture were not used. There is a possibility thatthe result may be different by a 360° orbit. The present
experimental results were obtained using cylindrical andanthropomorphic torso phantoms. Further clinical studies onpatients are needed to confirm the validity of our results inclinical practice, particularly for children, and patients with asmall heart.

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Fig.2 Transverse images of the cylindrical phantom (a) andanthropomorphic torso phantom (b) of the HL radioactivity
ratio 1:0:5

Larger fluctuation was observed in truncation data of OSEM
(arrows).

Fig.6 The CVs of the cylindrical phantom
Fig.3 Projection data for the anterior view of theanthropomorphic torso phantom.

Fig.4 Rectangular region of interest on the cylindrical phantom
for uniformity
a. Reference image. b. Truncation image.

Fig.5 Count profile curves of the cylindrical phantom. The
count profile curves were normalized to the maximum count of
the phantom edge on the opposite side of the truncation.

Fig 7. Results of the myocardial count. In FBP, the myocardial
counts tended to increase with a larger area and a higher
radioactivity concentration of the truncation portion. In OSEM,
this tendency was not observed.

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3. Gullberg GT, Zeng GL, Datz FL, Christian PE, Tung CH, et al.
(1992) Review of convergent beam tomography in single
photon emission computed tomography. Phys Med Biol(37):507-534.
https://iopscience.iop.org/article/10.1088/00319155/37/3/002
4. Manglos SH. (1992) Truncation artifact suppression in conebeam radionuclide transmission CT using maximum likelihood
techniques: evaluation with human subjects. Phys Med Biol(37):549-62.
https://iopscience.iop.org/article/10.1088/00319155/37/3/004
5. Gregoriou GK, Tsui BM, Gullberg GT. (1998) Effect oftruncated projections on defect detection in attenuationcompensatedfanbeam cardiac SPECT. J Nuc Med (39):
166-175. http://jnm.snmjournals.org/content/39/1/166.long
6. Celler A, Dixon KL, Chang Z, Blinder S, Powe J, Het al. (2005)
Problems created in attenuation-corrected SPECT images
artifacts in attenuation maps: A simulation study. J Nucl Med(46):335-344.
http://jnm.snmjournals.org/content/46/2/335.long
7. Chen J, Galt JR, Case JA, Ye J, Cullom SJ, et al. (2005)
Transmission scan truncation with small-field-of-view
dedicated cardiac SPECT systems: Impact and automatedqualitycontrol.
J
Nucl
Cardiol(5):567-573.
https://link.springer.com/article/10.1016%2Fj.nuclcard.200
5.04.013

Fig.8 The % uptake of polar map. Dotted and hatched areas are
assigned to increase and decrease segment of truncated datacompared with reference data.
7.

REFERENCES

1. Nishimura T, Nakajima K, Kusuoka H, Yamashina A,
Nishimura S. (2008) Prognostic study of risk stratification
among Japanese patients with ischemic heart disease usinggated myocardial perfusion SPECT: J-ACCESS study. Eur J
NucMol
imaging(35):319-328.
https://link.springer.com/article/10.1007/s00259-0070608-x
2. Nakajima K, Taki J, Higuchi T, Kawano M, Taniguchi M, et al.
(2000) Gated SPET quantification of small hearts:
mathematical simulation and clinical application. Eur J Nucl
Med(27):1372-1379.
https://link.springer.com/article/10.1007%2Fs0025900002
99

8. Rohmer D, Eisner RL, Gullberg GT. (2006) The effect oftruncation on very small cardiac SPECT camera systems.
Lawrence
Berkeley
National
Laboratory.
http://escholarship.org/uc/item/6cj158t7.
9. Lalush DS, Tsui BM. (2000) Performance of ordered-subset
reconstruction algorithms under condition of extreme
attenuation and truncation in myocardial SPECT. J Nucl Med(41):737-44.
http://jnm.snmjournals.org/content/41/4/737.long
10. Sabondjian E, Stodilka RZ, Belhocine T, King ME, Wisenberg
G, et al. (2009) Small field-of-view cardiac SPECT can be
implemented on hybrid SPECT/CT platforms where dataacquisition and reconstruction
areguided b
CT.Nucl Med
Commun (30):718-726.
https://journals.lww.com/nuclearmedicinecomm/Abstract/2009/09000/Small_field_of_view_cardiac_SPECT_can_be.11.aspx
11. American Heart Association Writing Group on Myocardial
Segmentation and Registration for Cardiac
Imaging:,
Cerqueira MD, Weissman NJ, Dilsizian V, Jacobs AK, Kaul S,
et al. (2002) Standardized myocardial segmentation andnomenclature for tomographic imaging of the heart. A© 2020, SJC. All Rights Reserved

Truncation artifacts in Myocardial Perfusion SPECT

https://sjcjournal.com/

Masahisa Onoguchi.et al.

SJC. 2020; 1(3): 82 - 89

statement for healthcare professionals from the Cardiac
Imaging Committee of the Council on Clinical Cardiology of
the American Heart Association. Circulation (105):539542.
https://www.ahajournals.org/doi/10.1161/hc0402.102975?
url_ver=Z39.882003&rfr_id=ori%3Arid%3Acrossref.org&rfr_dat=cr_pub++0
pubmed&12. Kanda Y. (2013) Investigation of the freely available easyto-use software ‘EZR’ for medical statistics. Bone Marrow
Transplant(48):452-458.
https://www.ncbi.nlm.nih.gov/pmc/articles/PMC3590441/
13.Maniawski PJ, Morgan HT, Wackers FJ. (1991) Orbit-related
variation in spatial resolution as a source of artefactual defects
in thallium-201 SPECT. J Nucl Med (32):871-5.
http://jnm.snmjournals.org/content/32/5/871.long
14. Liu YH, Lam PT, Sinusas AJ, Wackers FJ. (2002) Differential
effect of 180°and 360°acquisition orbits on the accuracy of
SPECT imaging: quantitative evaluation in phantoms. J Nucl
Med(43):1115-1124.
http://jnm.snmjournals.org/content/43/8/1115.long
15. Taki J, Fujino S, Nakajima K, Matsunari I, Okazaki H, et al.
(2001) 99mTc-sestamibi retention characteristics during
pharmacologic
hyperemiainhumanmyocardium:comparison with coronary flow reserve measured by
Dopplerflowire.
J
NuclMed(42):1457-1463.
http://jnm.snmjournals.org/content/42/10/1457.long
16. Storto G, Soricelli A, Pellegrino T, Petretta M,Cuocolo A.
(2009) Assessment of the arterial input function for
estimation of coronary flow reserve by single photon
emission computed tomography: comparison of two
different approaches. Eur J Nucl Med (36):2034-2041.
Assessment of the arterial input function for estimation ofcoronary flow reserve
17. Wosnitzer B, Gadiraju R, Depuey G. (2011) The truncation
artifact.
J
Nucl
Cardiol(18):187-191.
https://link.springer.com/article/10.1007%2Fs12350-0109290-7
18. Tsougos I, Alexiou S, theodorou K, Valotassiou V,
Georgoulias P. (2015) The prevalence of a false-positive
myocardial perfusion stress SPET test in a skinny patient,induced by projection truncation. Hell J Nucl Med (18):79-80.
https://pubmed.ncbi.nlm.nih.gov/25679080/e.

Article Citation:
Authors Name. Masahisa Onoguchi. Prerequisite for projection data and reconstruction not to cause truncation artifacts
in myocardial perfusion single- photon emission computed tomography: Phantom study. SJC 2020;1(3): 82 - 89
DOI: doi.org/10.46978/sjc.20.1.2.14© 2020, SJC. All Rights Reserved

Truncation artifacts in Myocardial Perfusion SPECT

https://sjcjournal.com/