Evaluation of Iodine-123 and Iodine-131 SPECT activity quantification: a Monte Carlo study

Abstract

Purpose: The quantitative accuracy of Nuclear Medicine images, acquired for both planar and SPECT studies, is influenced by the isotope-collimator combination as well as image corrections incorporated in the iterative reconstruction process. These factors can be investigated and optimised using Monte Carlo simulations. This study aimed to evaluate SPECT quantification accuracy for ¹²³I with both the low-energy high resolution (LEHR) and medium-energy (ME) collimators and ¹³¹I with the high-energy (HE) collimator.

Methods: Simulated SPECT projection images were reconstructed using the OS-EM iterative algorithm, which was optimised for the number of updates, with appropriate corrections for scatter, attenuation and collimator detector response (CDR), including septal scatter and penetration compensation. An appropriate calibration factor (CF) was determined from four different source geometries (activity-filled: water-filled cylindrical phantom, sphere in water-filled (cold) cylindrical phantom, sphere in air and point-like source), investigated with different volume of interest (VOI) diameters. Recovery curves were constructed from recovery coefficients to correct for partial volume effects (PVEs). The quantitative method was evaluated for spheres in voxel-based digital cylindrical and patient phantoms.

Results: The optimal number of OS-EM updates was 60 for all isotope-collimator combinations. The CF_point with a VOI diameter equal to the physical size plus a 3.0-cm margin was selected, for all isotope-collimator geometries. The spheres' quantification errors in the voxel-based digital cylindrical and patient phantoms were less than 3.2% and 5.4%, respectively, for all isotope-collimator combinations.

Conclusion: The study showed that quantification errors of less than 6.0% could be attained, for all isotope-collimator combinations, if corrections for; scatter, attenuation, CDR (including septal scatter and penetration) and PVEs are performed. ¹²³I LEHR and ¹²³I ME quantification accuracies compared well when appropriate corrections for septal scatter and penetration were applied. This can be useful in departments that perform ¹²³I studies and may not have access to ME collimators.

Keywords: 123I; 131I; Monte Carlo simulations; Quantification accuracy; SIMIND; SPECT.

Fig. 1

Schematic describing basic steps of iterative reconstruction method

Fig. 2

Segmented coronal CT slices of the voxel-based digital patient phantom with spheres' positions for a scenario 1 and b scenario 2

Fig. 3

Normalised counts and ${\text{SD}}_{\text{relative}}$ as a function of OS-EM updates for spheres with diameters of 1.5 cm, 3.0 cm, 4.5 cm, and 6.0 cm, for a ¹²³I LEHR, b ¹²³I ME and c ¹³¹I HE

Fig. 4

Simulated energy spectra of CF_point projection images for a ¹²³I LEHR, b ¹²³I ME and c ¹³¹I HE

Fig. 5

RC as a function of sphere diameter for ¹²³I LEHR, ¹²³I ME and ¹³¹I HE, with the solid lines showing the fitted functions

Fig. 6

Quantification error (%) of spheres of differing diameter in a warm cylindrical phantom, for ¹²³I LEHR, ¹²³I ME and ¹³¹I HE

Fig. 7

Uncorrected projection images (a, c, e), and reconstructed corrected transaxial slices (b, d, f) through the voxel-based digital patient phantom for a, b ¹²³I LEHR, c, d ¹²³I ME and e, f ¹³¹I HE. Profiles through the largest sphere are displayed alongside their respective images. Arrows indicate septal scatter and penetration at peak and trough and at tail region

Fig. 8

Activity quantification errors (%) for spheres in the voxel-based digital patient phantom (scenario 1 and 2), for ¹²³I LEHR, ¹²³I ME and ¹³¹I HE