Open Access

Left ventricular function assessment using 123I/99mTc dual-isotope acquisition with two semi-conductor cadmium–zinc–telluride (CZT) cameras: a gated cardiac phantom study

  • Tanguy Blaire1, 2, 3Email author,
  • Alban Bailliez1, 2, 3,
  • Fayçal Ben Bouallegue4,
  • Dimitri Bellevre4,
  • Denis Agostini2, 4 and
  • Alain Manrique2, 4
EJNMMI Physics20163:27

https://doi.org/10.1186/s40658-016-0163-2

Received: 29 June 2016

Accepted: 1 November 2016

Published: 11 November 2016

Abstract

Background

The impact of increased energy resolution of cadmium–zinc–telluride (CZT) cameras on the assessment of left ventricular function under dual-isotope conditions (99mTc and 123I) remains unknown.

The Amsterdam-gated dynamic cardiac phantom (AGATE, Vanderwilt techniques, Boxtel, The Netherlands) was successively filled with a solution of 123I alone, 99mTc alone, and a mixture of 123I and 99mTc. A total of 12 datasets was acquired with each commercially available CZT camera (DNM 530c, GE Healthcare and DSPECT, Biosensors International) using both energy windows (99mTc or 123I) with ejection fraction set to 33, 45, and 60 %. End-diastolic (EDV) and end-systolic (ESV) volumes, ejection fraction (LVEF), and regional wall motion and thickening (17-segment model) were assessed using Cedars-Sinai QGS Software. Concordance between single- and dual-isotope acquisitions was tested using Lin’s concordance correlation coefficient (CCC) and Bland–Altman plots.

Results

There was no significant difference between single- or simultaneous dual-isotope acquisition (123I and 99mTc) for EDV, ESV, LVEF, or segmental wall motion and thickening. Myocardial volumes using single- (123I, 99mTc) and dual-isotope (reconstructed using both 123I and 99mTc energy windows) acquisitions were, respectively, the following: EDV (mL) 88 ± 27 vs. 89 ± 27 vs. 92 ± 29 vs. 90 ± 26 for DNM 530c (p = NS) and 82 ± 20 vs. 83 ± 22 vs. 79 ± 19 vs. 77 ± 20 for DSPECT (p = NS); ESV (mL) 40 ± 1 vs. 41 ± 2 vs. 41 ± 2 vs. 42 ± 1 for DNM 530c (p = NS) and 37 ± 5 vs. 37 ± 1 vs. 35 ± 3 vs. 34 ± 2 for DSPECT (p = NS); LVEF (%) 52 ± 14 vs. 51 ± 13 vs. 53 ± 13 vs. 51 ± 13 for DNM 530c (p = NS) and 52 ± 16 vs. 54 ± 13 vs. 54 ± 14 vs. 54 ± 13 for DSPECT (p = NS); regional motion (mm) 6.72 ± 2.82 vs. 6.58 ± 2.52 vs. 6.86 ± 2.99 vs. 6.59 ± 2.76 for DNM 530c (p = NS) and 6.79 ± 3.17 vs. 6.81 ± 2.75 vs. 6.71 ± 2.50 vs. 6.62 ± 2.74 for DSPECT (p = NS). The type of camera significantly impacted only on ESV (p < 0.001).

Conclusions

The new CZT cameras yielded similar results for the assessment of LVEF and regional motion using different energy windows (123I or 99mTc) and acquisition types (single vs. dual). With simultaneous dual-isotope acquisitions, the presence of 123I did not impact on LVEF assessment within the 99mTc energy window for either CZT camera.

Keywords

CZT SPECT Myocardial perfusion imaging Myocardial innervation imaging Dual-isotope acquisition mIBG Dynamic phantom DNM 530c DSPECT

Background

The measurement of left ventricular (LV) ejection fraction (LVEF), end-diastolic volume (EDV), and end-systolic volume (ESV) using cardiac SPECT has been widely validated in comparison to other imaging techniques [1, 2]. Gated perfusion SPECT with 99mTc-labelled tracer is commonly used for prognosis assessment and clinical decision-making [3]. In addition, cardiac sympathetic innervation can be directly imaged with 123I-meta-iodobenzylguanidine (123I-mIBG), a radiolabelled norepinephrine analogue [4] that reflects neuronal integrity by visualising reuptake and retention in cardiac sympathetic terminals [5]. Previous studies using serial 123I-mIBG and 201thallium acquisitions have suggested that myocardial sympathetic innervation is compromised after myocardial infarction [68]. Due to the enhanced sensitivity of neural tissue to ischemia, regional sympathetic denervation exceeds the extent of the perfusion defect [9]. Comparing sympathetic innervation and viability is of potential interest to assess the risk of ventricular arrhythmias after myocardial infarction (MI) [10, 11].

The new cadmium–zinc–telluride (CZT) detectors offer higher photon sensitivity and dramatically increased spatial energy resolution compared with standard cameras. The advanced technical capabilities of these dedicated cardiac cameras enable combined assessment of myocardial innervation and perfusion within a single imaging session, using a dual injection of 123I-mIBG and a 99mTc-labelled perfusion tracer. Bellevre et al. [12] recently demonstrated the feasibility of determining heart-to-mediastinum ratio of 123I-mIBG uptake in patients with heart failure using dual-isotope imaging with a CZT camera (DSPECT) and combined 99mTc-tetrofosmin injection to localise the heart within the thorax.

Despite their increased energy resolution, the scatter fraction remains high with CZT cameras (30 vs. 34 % with conventional Anger gamma cameras) [13]. Moreover, the tailing effect in the energy spectrum towards lower energies due to incomplete charge collection [14] (Fig. 1) may specifically affect count statistics with CZT cameras. These two phenomena may impact on image acquisition within the 99mTc photopeak during a 123I/99mTc dual-isotope acquisition, further compromising the accuracy of ventricular function assessment using gated SPECT with 99mTc-labelled tracer. This situation remains however to be investigated.
Fig. 1

Energy spectra using DNM 530c. Typical single 123I, single 99mTc, and simultaneous (123I and 99mTc) point source (1.7 MBq) energy spectra using DNM 530c without in-object scatter. Notice the low tailing effect and the down-scatter of 123I towards 99mTc in the dual isotope condition

The aim of this study was to evaluate the impact of simultaneous dual-isotope (123I/99mTc) acquisition on the assessment of global and regional left ventricular function in the 99mTc photopeak using two commercially available CZT cameras, Discovery NM 530c (DNM 530c, GE Healthcare, Milwaukee, WI, USA) and DSPECT (Biosensors International, Caesarea, Israel).

Methods

Gated phantom studies

We used the Amsterdam gated (Agate) dynamic phantom (Vanderwilt techniques, Boxtel, The Netherlands) as a reference for volume and LVEF measurements [15]. This phantom is a realistic 3-D water-filled torso with two thin membranes simulating endocardial and epicardial walls with known ejection fraction (Fig. 2). The compartment between these membranes was successively filled with a solution of 123I alone, 99mTc alone, and a mixture of 123I and 99mTc (22/44 kBq/mL, respectively) simulating the myocardial wall. The cardiac phantom stroke volume was controlled by a programmable adjustable pumping system, and an ECG-triggered signal was produced at a constant heart rate. Four datasets (single 123I, single 99mTc, dual 123I, and 99mTc) were acquired using three different ejection fractions (33 and 45 % to mimic LV dysfunction and 60 % to simulate normal LV function) on each camera (DNM 530c and DSPECT) with the following parameters: 10-min acquisition and 70-bpm contraction rate. EDV, ESV, LVEF, and regional wall thickening and motion (17-segment model) were assessed using Quantitative Gated SPECT software (QGS, Cedars-Sinai Medical Center, Los Angeles, CA). The acquisition parameters were as follows: 70 × 70 matrix for the DNM 530c system and 64 × 64 for the DSPECT with a total of 120 projections recorded by each block in the heart area defined on a short prescan acquisition [13]. The energy window was asymmetric for both cameras, 140 keV (−10 + 5 %) for 99mTc and 159 keV (−5 + 10 %) for 123I, for each acquisition.
Fig. 2

The AGATE dynamic gated phantom. The AGATE dynamic gated phantom with fillable cardiac set, successively filled with a solution of 123I alone, 99mTc alone, and a mixture of 123I and 99mTc

CZT cameras

We successively used (i) a DNM 530c equipped with a multiple pinhole collimator and 19 stationary CZT detectors that simultaneously image 19 cardiac views, each detector being composed of four 5-mm-thick elements of 32 × 32 pixels (pixel size 2.46 × 2.46 mm) [16] and (ii) a DSPECT operating with nine mobile blocks of pixelated CZT detectors (pixel size 2.46 × 2.46 mm) associated with a wide-angle square-hole tungsten collimator, recording a total of 120 projections by each block [13]. All SPECT data were acquired and reconstructed using the parameters currently recommended for clinical routine and provided by each manufacturer, leading to a reconstructed pixel size of 4 × 4 × 4 and 4.92 × 4.92 × 4.92 mm for DNM 530c and DSPECT, respectively. No attenuation correction was performed.

Statistical analysis

Values are presented as mean ± SD. A linear model analysis evaluated the effect of camera, acquisition type (single- vs. dual-isotope), isotope (123I vs. 99mTc), and the interaction between camera type and isotope. Continuous mean values were compared using the Wilcoxon signed-rank test or Mann–Whitney U test when appropriate. Relationship between DNM 530c and DSPECT results were assessed using Pearson’s (r) correlation coefficient, Bland–Altman limit-of-agreement, and Lin’s concordance correlation coefficient (CCC), a measure of both precision and bias [17, 18]. Lin’s CCC measures the equivalence of two measurement methods. The accuracy (i.e. the deviation of the best fit line from the line of identity) was assessed using the bias correction factor calculated as C.b = CCC/r, r being Pearson’s correlation coefficient. The values of r and CCC were characterised using the Landis and Koch scale (0.2–0.4: fair; 0.4–0.6: moderate; 0.6–0.8: substantial; 0.8–1.0: almost perfect) [19]. A p value <0.05 was considered statistically significant.

Statistical analyses were performed using R software (R Foundation for Statistical Computing, version 3.2.4, Vienna, Austria) except the linear model analysis performed using JMP 11 (SAS institute, Cary, NC).

Results

The mean values of overall cardiac volumes (EDV and ESV), LVEF, and regional wall motion and thickening using single- and dual-isotope acquisitions with DNM 530c and DSPECT are shown in Table 1 and illustrated in Figs. 3 and 4.
Table 1

Results for each camera

Camera

DNM 530c

DSPECT

Energy window

123I

99mTc

123I

99mTc

Acquisition type

Single

Dual

Single

Dual

Single

Dual

Single

Dual

EDV (mL)

88 ± 27

92 ± 29

89 ± 27

90 ± 26

82 ± 20

79 ± 19

83 ± 22

77 ± 20

ESV (mL)

40 ± 1*

41 ± 2*

41 ± 2*

42 ± 1*

37 ± 5

35 ± 3

37 ± 1

34 ± 2

LVEF (%)

52 ± 14

53 ± 13

51 ± 13

51 ± 13

52 ± 16

54 ± 14

54 ± 13

54 ± 13

Motion (mm)

6.72 ± 2.82

6.86 ± 2.99

6.58 ± 2.52

6.59 ± 2.76

6.79 ± 3.17

6.71 ± 2.50

6.81 ± 2.75

6.62 ± 2.74

Thickening (%)

47.7 ± 30.6

47.1 ± 29.9

45.4 ± 27.7

44.3 ± 29.2

44.2 ± 28.8

42.7 ± 23.6

42.2 ± 24.5

41.5 ± 26.7

Phantom study results for each camera model expressed as mean ± SD. EDV, ESV, LVEF, and thickening and motion mean values for 99mTc and 123I isotope in two acquisition types (single or dual), for both energy windows (123I and 99mTc) on each camera (DNM 530c and DSPECT). *p < 0.0001 vs. DSPECT

Fig. 3

DNM 530c and DSPECT 99mTc and 123I uptake. Single 123I (a) and single 99mTc (b). Simultaneous 123I (c) and 99mTc (d) end-systolic apical short axis uptake for DNM 530c (upper row) and DSPECT (lower row) for LVEF 50%

Fig. 4

DNM 530c and DSPECT end-systolic volume rendering, volume (mL), and filling (mL/s). End-systolic volume rendering, volume (mL), and filling (mL/s) in single 99mTc (a) and dual 99mTc (b) condition using DNM 530c (upper row) and DSPECT (lower row)

Linear model analysis demonstrated that the type of camera but not the acquisition mode (i.e. single- or dual-isotope) impacted on volume measurements. Post hoc Mann–Whitney test showed that this impact was only observed for the ESV measurements (p < 0.0001) whereas EDV, LVEF, and segmental wall motion were similar for the two cameras.

Lin’s concordance correlation coefficient and Bland–Altman plots (see Tables 2 and 3 and Fig. 5) revealed an almost perfect agreement between single- and dual-isotope acquisitions for assessing segmental wall motion and thickening with 99mTc with both CZT cameras. Conversely, using 123I, the agreement was weaker with both CZT cameras, with a decreased CCC and an increased 95 % CI of the difference between the two measurements on Bland–Altman plots. Pearson’s correlation (r) and CCC were similar, also indicating that no systematic bias was present (C.b > 0.97) between the two cameras and the acquisition mode.
Table 2

DNM 530c and DSPECT concordance correlation coefficients for motion

Motion

 

Pearson’s

 

Bland Altman

r [95 % CI]

CCC [95 % CI]

C.b

Mean diff. [95 % CI]

Regression

R 2

 Acquisition

Isotope

      

  Single

123I

0.94 [0.89–0.96]

0.93 [0.89–0.96]

0.99

0.06 [−2.15;2.28]

y = 0.123x − 0.764

0.107

99mTc

0.95 [0.92–0.97]

0.94 [0.91–0.97]

0.99

0.23 [−1.48;1.94]

y = 0.088x − 0.354

0.071

  Dual

123I

0.90 [0.83–0.94]

0.88 [0.81–0.93]

0.98

−0.15 [−2.8;2.5]

y = −0.188x + 1.13

0.144

99mTc

0.94 [0.90–0.97]

0.94 [0.9–0.97]

1

0.03 [−1.81;1.87]

y = −0.007x + 0.076

0

 Camera

  DSPECT

123I

0.91 [0.86–0.95]

0.89 [0.83–0.93]

0.98

0.08 [−2.57;2.72]

y = 0.248x − 1.599

0.271

99mTc

0.97 [0.95–0.98]

0.97 [0.95–0.98]

1

0.22 [−1.74; 2.18]

y = −0.003x + 0.239

0

  DNM 530c

123I

0.94 [0.90–0.97]

0.94 [0.9–0.97]

1

−0.14 [−2.11;1.84]

y = −0.061x + 0.276

0.031

99mTc

0.97 [0.96–0.99]

0.97 [0.95–0.98]

1

−0.01 [−1.29;1.26]

y = −0.089x + 0.576

0.135

Bland–Altman mean difference (mean diff), regression, and R 2

r, Pearson’s correlation (precision); CCC, Lin’s concordance correlation; C.b, r/CCC = bias factor (trueness)

Table 3

DNM 530c and DSPECT concordance correlation coefficients for thickening

Thickening

 

Pearson’s

 

Bland Altman

r [95 % CI]

CCC [95 % CI]

C.b

Mean diff. [95 % CI]

Regression

R 2

 Acquisition

Isotope

      

  Single

123I

0.93 [0.88–0.96]

0.92 [0.86–0.95]

0.99

−3.59 [−26.45;19.28]

y = −0.063x − 0.694

0.026

99mTc

0.94 [0.90–0.97]

0.93 [0.89–0.96]

0.99

−3.14 [−21.65;15.38]

y = −0.125x + 2.331

0.121

  Dual

123I

0.87 [0.79–0.93]

0.84 [0.75–0.9]

0.97

−4.35 [−33.78;25.08]

y = −0.248x + 6.801

0.191

99mTc

0.94 [0.90–0.97]

0.94 [0.89–0.96]

1

−2.84 [−22.04;16.35]

y = −0.09x + 1.009

0.067

 Camera

  DSPECT

123I

0.88 [0.80–0.93]

0.88 [0.81–0.93]

1

1.43 [−23.87;26.74]

y = 0.208x − 7.608

0.177

99mTc

0.96 [0.93–0.98]

0.96 [0.93–0.98]

1

0.78 [−14.06;15.63]

y = −0.088x + 4.449

0.09

  DNM 530c

123I

0.91 [0.85–0.95]

0.91 [0.85–0.95]

1

0.67 [−24.38;25.71]

y = 0.026x − 0.588

0.004

99mTc

0.96 [0.94–0.98]

0.96 [0.93–0.98]

1

1.08 [−14.5;16.65]

y = −0.053x + 3.446

0.037

Bland–Altman mean difference (mean diff), regression, and R 2

r, Pearson’s correlation (precision); CCC, Lin’s concordance correlation; C.b, r/CCC = bias factor (trueness)

Fig. 5

Lin’s CCC and Bland–Altman motion for DNM 530c and DSPECT. Lin’s CCC for DSPECT 123I (a) and 99mTc (c), DNM 530c 123I (e), and 99mTc (g) motion and Bland–Altman plots for DSPECT 123I (b) and 99mTc (d), DNM 530c 123I (f), and 99mTc (h) motion for single and dual acquisitions

Discussion

Our results demonstrated the feasibility of LVEF evaluation using gated perfusion SPECT with CZT cameras. On simultaneous dual radionuclide acquisitions, the 99mTc photopeak was unaffected by 123I scatter and crosstalk. To our knowledge, this is the first dual-isotope gated phantom study evaluating ventricular function using the two commercially available CZT cameras (DNM 530c and DSPECT).

Dual-isotope acquisition with CZT cameras remains a challenging technique. Impaired myocardial innervation leads to low myocardial 123I-mIBG uptake, requiring a dual-isotope protocol to localise the heart [12]. Due to the small field-of-view of the dedicated CZT cardiac cameras, a scout view is mandatory to localise the heart and correctly centre the field-of-view prior to SPECT acquisition. In addition, most of the patients referred for 123I-mIBG assessment have an ischemic cardiomyopathy with heart failure (66 % in the ADMIRE-HF study [20]). In this clinical setting, the dual-isotope protocol allows a simple and efficient co-registration of innervation and perfusion studies and thus a robust assessment of innervation-perfusion mismatch. The measurement of LV function is a key step of prognosis assessment and may potentially be altered when using CZT cameras with a simultaneous dual-isotope protocol due to the down-scatter, crosstalk, and tailing effect of 123I in the 99mTc photopeak.

Our results demonstrated that DNM 530c provided higher systolic volumes compared to the DSPECT camera. This camera effect on volume assessment is likely related to spatial resolution. Imbert et al. [21] reported the following classification of measured central spatial resolution: DNM 530c (6.7 mm) and DSPECT (8.6 mm). These results are concordant with previous findings by Bailliez et al. [22] showing in both phantom and patients that LV volumes were higher using the DNM 530c model compared to DSPECT and to Anger camera equipped with cardiofocal collimators.

Our results also demonstrated that, in comparison with single 99mTc acquisition, dual 123I/99mTc acquisition did not compromise the assessment of ventricular function using the 99mTc photopeak. In some patients with severe heart failure, the sole use of 123I-mIBG SPECT can lead to suboptimal localisation of the heart because of the CZT camera’s narrow field-of-view, particularly when cardiac mIBG uptake is very low and the left ventricle is dilated. A dual-isotope protocol acquisition using both perfusion and innervation tracers provides a clear perfusion image and a perfect registration that allows the definition of the heart contours and thus an accurate measurement of 123I-mIBG uptake [12].

In the clinical setting, simultaneous dual-radionuclide acquisition provides perfectly registered functional images leading to a reduced imaging time. In cardiac SPECT, several dual-radionuclide imaging protocols have been proposed. Simultaneous 99mTc-sestamibi/123I-BMIPP imaging was proposed for assessing rest perfusion and fatty acid metabolism at the same time in patients with recent myocardial infarction [23, 24]. The dual-isotope acquisition protocol using 201Tl and 123I-mIBG is well documented on conventional Anger cameras, using the triple-energy window [25] for scatter and crosstalk correction. Simultaneous perfusion and sympathetic innervation imaging with 123I-mIBG and 99mTc-labelled tracers enables the evaluation of innervation-flow mismatch and may provide valuable information to target the trigger zone in the setting of ventricular arrhythmia [4, 26]. In a recent study, Gimelli et al. [11, 27] using sequential 123I-mIBG and 99mTc-tetrofosmin myocardial SPECT demonstrated a relevant association between innervation derangement (123I-mIBG) and myocardial synchronicity (99mTc-tetrofosmin).

Despite a significant increase in energy resolution and sensitivity, the scatter fraction with the CZT camera is still high, evaluated up to 30 vs. 34 % with conventional Anger cameras [13]. Due to incomplete charge collection and intercrystal scatter, the CZT detectors are subjected to a tailing effect below the photopeak that may lead to an overcorrection of photon scatter when using a conventional triple-energy window method [28]. Recently, Fan et al. for the DNM 530c [29] and Holstensson et al. for the DSPECT [30] presented a model-based correction algorithm which extracts the useful primary counts of 99mTc and 123I from projection data, taking into account the tailing effect to correct the scatter and crosstalk in 99mTc–123I dual imaging. In the present study, we did not apply any tailing effect correction and observed no significant impact on ventricular function assessment.

All reconstructions were performed using the vendor’s workstation and available software for both cameras. Routinely, scatter and crosstalk correction is not performed on the DNM 530c camera. Image data from DSPECT were corrected for scatter and crosstalk but not for the tailing effect. In our study, the ratio between 123I and 99mTc concentration was set to 1:2, which is representative of the low 123I-mIBG myocardial uptake, observed in severe heart failure. Under these specific conditions, the absence of scatter and crosstalk correction using the DNM 530c did not affect ventricular function assessment using 99mTc acquisitions. In severe heart failure, 123I-mIBG myocardial uptake is low and we assumed that the crosstalk and scatter of 123I in the 99mTc photopeak had no consequences.

Limitations of the study

Due to the design of the phantom, EDV and ESV were not predetermined. The phantom was filled under static equilibrium conditions at atmospheric pressure to provide a reproducible ejection fraction. Based on this equilibrium, ejection fraction was imposed by injecting a stroke volume into the ventricular cavity [15, 22]. As a consequence, true EDV and ESV were not known and thus could not be compared with measured volumes.

As we used only commercially available software, scatter and crosstalk were corrected with DSPECT but not with DNM 530c. However, our results displayed no critical differences between the single-isotope and dual-isotope 99mTc window, even with the DNM 530c. At best, the demonstration could be made by comparing the results obtained with and without scatter and crosstalk corrections. However, the aim of our study was to compare the results obtained with the two CZT cameras using the dedicated commercially available software to mimic routine clinical conditions.

Conclusions

In this phantom study, the two CZT cameras (DNM 530c and DSPECT) provided similar results for ventricular function assessment (EDV, ESV, and LVEF) with single- (separate 123I and 99mTc acquisitions) and simultaneous dual-isotope (123I and 99mTc) acquisitions. Further studies are needed to evaluate perfusion match and mismatch using 123I-mIBG and 99mTc-labelled tracers.

Declarations

Acknowledgements

The authors thank Nathaniel Roth for his technical assistance. This work was conducted as part of the FHU REMOD-VHF project.

Authors’ contribution

TB and AM: design of the study, data acquisition, analysis and interpretation of data, drafting of manuscript. AB and DB: data acquisition, analysis of data, and drafting of manuscript. FBB: statistical analysis, analysis of data and critical revision. DA: interpretation of data, drafting of manuscript. All authors read and approved the final manuscript.

Competing interests

The authors declare that they have no competing interests.

Open AccessThis article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.

Authors’ Affiliations

(1)
Nuclear Medicine, UF 5881, Groupement des Hôpitaux de l’Institut Catholique de Lille
(2)
Normandie Univ, UNICAEN, Signalisation, électrophysiologie et imagerie des lésions d’ischémie-reperfusion myocardique
(3)
Nuclear Medicine, IRIS, Hôpital Privé Le Bois
(4)
Nuclear Medicine, CHU Cote de Nacre

References

  1. Hachamovitch R, Berman DS, Kiat H, Cohen I, Friedman JD, Shaw LJ. Value of stress myocardial perfusion single photon emission computed tomography in patients with normal resting electrocardiograms: an evaluation of incremental prognostic value and cost-effectiveness. Circulation. 2002;105(7):823–9.View ArticlePubMedGoogle Scholar
  2. Marcassa C, Bax JJ, Bengel F, Hesse B, Petersen CL, Reyes E, et al. Clinical value, cost-effectiveness, and safety of myocardial perfusion scintigraphy: a position statement. Eur Heart J. 2008;29(4):557–63.View ArticlePubMedGoogle Scholar
  3. Thomas GS, Miyamoto MI, Morello 3rd AP, Majmundar H, Thomas JJ, Sampson CH, et al. Technetium 99m sestamibi myocardial perfusion imaging predicts clinical outcome in the community outpatient setting. The Nuclear Utility in the Community (NUC) Study. J Am Coll Cardiol. 2004;43(2):213–23.View ArticlePubMedGoogle Scholar
  4. Carrio I, Cowie MR, Yamazaki J, Udelson J, Camici PG. Cardiac sympathetic imaging with mIBG in heart failure. JACC Cardiovasc Imaging. 2010;3(1):92–100.View ArticlePubMedGoogle Scholar
  5. Morozumi T, Kusuoka H, Fukuchi K, Tani A, Uehara T, Matsuda S, et al. Myocardial iodine-123-metaiodobenzylguanidine images and autonomic nerve activity in normal subjects. J Nucl Med. 1997;38(1):49–52.PubMedGoogle Scholar
  6. McGhie AI, Corbett JR, Akers MS, Kulkarni P, Sills MN, Kremers M, et al. Regional cardiac adrenergic function using I-123 meta-iodobenzylguanidine tomographic imaging after acute myocardial infarction. Am J Cardiol. 1991;67(4):236–42.View ArticlePubMedGoogle Scholar
  7. Bengel FM, Barthel P, Matsunari I, Schmidt G, Schwaiger M. Kinetics of 123I-MIBG after acute myocardial infarction and reperfusion therapy. J Nucl Med. 1999;40(6):904–10.PubMedGoogle Scholar
  8. Simoes MV, Barthel P, Matsunari I, Nekolla SG, Schomig A, Schwaiger M, et al. Presence of sympathetically denervated but viable myocardium and its electrophysiologic correlates after early revascularised, acute myocardial infarction. Eur Heart J. 2004;25(7):551–7.View ArticlePubMedGoogle Scholar
  9. Matsunari I, Schricke U, Bengel FM, Haase HU, Barthel P, Schmidt G, et al. Extent of cardiac sympathetic neuronal damage is determined by the area of ischemia in patients with acute coronary syndromes. Circulation. 2000;101(22):2579–85.View ArticlePubMedGoogle Scholar
  10. Bax JJ, Kraft O, Buxton AE, Fjeld JG, Parizek P, Agostini D, et al. 123I-mIBG scintigraphy to predict inducibility of ventricular arrhythmias on cardiac electrophysiology testing: a prospective multicenter pilot study. Circ Cardiovasc Imaging. 2008;1(2):131–40.View ArticlePubMedGoogle Scholar
  11. Gimelli A, Liga R, Giorgetti A, Genovesi D, Marzullo P. Assessment of myocardial adrenergic innervation with a solid-state dedicated cardiac cadmium-zinc-telluride camera: first clinical experience. Eur Heart J Cardiovasc Imaging. 2014;15(5):575–85.View ArticlePubMedGoogle Scholar
  12. Bellevre D, Manrique A, Legallois D, Bross S, Baavour R, Roth N, et al. First determination of the heart-to-mediastinum ratio using cardiac dual isotope (123I-MIBG/99mTc-tetrofosmin) CZT imaging in patients with heart failure: the ADRECARD study. Eur J Nucl Med Mol Imaging. 2015;42(12):1912–9.View ArticlePubMedGoogle Scholar
  13. Erlandsson K, Kacperski K, van Gramberg D, Hutton BF. Performance evaluation of D-SPECT: a novel SPECT system for nuclear cardiology. Phys Med Biol. 2009;54(9):2635–49.View ArticlePubMedGoogle Scholar
  14. Leo W. Techniques for nuclear and particle physics experiments. 2nd ed. Berlin: Spinger; 1994.View ArticleGoogle Scholar
  15. Visser JJ, Sokole EB, Verberne HJ, Habraken JB, van de Stadt HJ, Jaspers JE, et al. A realistic 3-D gated cardiac phantom for quality control of gated myocardial perfusion SPET: the Amsterdam gated (AGATE) cardiac phantom. Eur J Nucl Med Mol Imaging. 2004;31(2):222–8.View ArticlePubMedGoogle Scholar
  16. Bocher M, Blevis IM, Tsukerman L, Shrem Y, Kovalski G, Volokh L. A fast cardiac gamma camera with dynamic SPECT capabilities: design, system validation and future potential. Eur J Nucl Med Mol Imaging. 2010;37(10):1887–902.View ArticlePubMedPubMed CentralGoogle Scholar
  17. Lin L. A concordance correlation coefficient to evaluate reproducibility. Biometrics. 1989;45(1):255–68.View ArticlePubMedGoogle Scholar
  18. Morgan CJ, Aban I. Methods for evaluating the agreement between diagnostic tests. J Nucl Cardiol. 2016;23(3):511–3.Google Scholar
  19. Landis JR, Koch GG. The measurement of observer agreement for categorical data. Biometrics. 1977;33(1):159–74.View ArticlePubMedGoogle Scholar
  20. Jacobson AF, Senior R, Cerqueira MD, Wong ND, Thomas GS, Lopez VA, et al. Myocardial iodine-123 meta-iodobenzylguanidine imaging and cardiac events in heart failure. Results of the prospective ADMIRE-HF (AdreView Myocardial Imaging for Risk Evaluation in Heart Failure) study. J Am Coll Cardiol. 2010;55(20):2212–21.View ArticlePubMedGoogle Scholar
  21. Imbert L, Poussier S, Franken PR, Songy B, Verger A, Morel O, et al. Compared performance of high-sensitivity cameras dedicated to myocardial perfusion SPECT: a comprehensive analysis of phantom and human images. J Nucl Med. 2012;53(12):1897–903.View ArticlePubMedGoogle Scholar
  22. Bailliez A, Lairez O, Merlin C, Piriou N, Legallois D, Blaire T, et al. Left ventricular function assessment using 2 different cadmium-zinc-telluride cameras compared with a gamma-camera with cardiofocal collimators: dynamic cardiac phantom study and clinical validation. J Nucl Med. 2016;57(9):1370–5.View ArticlePubMedGoogle Scholar
  23. Kumita S, Cho K, Nakajo H, Toba M, Kijima T, Mizumura S, et al. Simultaneous assessment of Tc-99m-sestamibi and I-123-BMIPP myocardial distribution in patients with myocardial infarction: evaluation of left ventricular function with ECG-gated myocardial SPECT. Ann Nucl Med. 2000;14(6):453–9.View ArticlePubMedGoogle Scholar
  24. Ouyang J, Zhu X, Trott CM, El Fakhri G. Quantitative simultaneous 99mTc/123I cardiac SPECT using MC-JOSEM. Med Phys. 2009;36(2):602–11.View ArticlePubMedPubMed CentralGoogle Scholar
  25. Ogawa K. Simulation study of triple-energy-window scatter correction in combined Tl-201, Tc-99m SPECT. Ann Nucl Med. 1994;8(4):277–81.View ArticlePubMedGoogle Scholar
  26. Abdulghani M, Duell J, Smith M, Chen W, Bentzen SM, Asoglu R, et al. Global and regional myocardial innervation before and after ablation of drug-refractory ventricular tachycardia assessed with 123I-MIBG. J Nucl Med. 2015;56 Suppl 4:52S–8S.View ArticlePubMedGoogle Scholar
  27. Gimelli A, Liga R, Genovesi D, Giorgetti A, Kusch A, Marzullo P. Association between left ventricular regional sympathetic denervation and mechanical dyssynchrony in phase analysis: a cardiac CZT study. Eur J Nucl Med Mol Imaging. 2014;41(5):946–55.View ArticlePubMedGoogle Scholar
  28. Kacperski K, Erlandsson K, Ben-Haim S, Hutton BF. Iterative deconvolution of simultaneous 99mTc and 201Tl projection data measured on a CdZnTe-based cardiac SPECT scanner. Phys Med Biol. 2011;56(5):1397–414.View ArticlePubMedPubMed CentralGoogle Scholar
  29. Fan P, Hutton BF, Holstensson M, Ljungberg M, Hendrik Pretorius P, Prasad R, et al. Scatter and crosstalk corrections for (99m)Tc/(123)I dual-radionuclide imaging using a CZT SPECT system with pinhole collimators. Med Phys. 2015;42(12):6895.View ArticlePubMedGoogle Scholar
  30. Holstensson M, Erlandsson K, Poludniowski G, Ben-Haim S, Hutton BF. Model-based correction for scatter and tailing effects in simultaneous 99mTc and 123I imaging for a CdZnTe cardiac SPECT camera. Phys Med Biol. 2015;60(8):3045–63.View ArticlePubMedGoogle Scholar

Copyright

© The Author(s). 2016