- Original research
- Open Access
Image quality analysis of 44Sc on two preclinical PET scanners: a comparison to 68Ga
EJNMMI Physics volume 7, Article number: 16 (2020)
44Sc has been increasingly investigated as a potential alternative to 68Ga in the development of tracers for positron emission tomography (PET). The lower mean positron energy of 44Sc (0.63 MeV) compared to 68Ga (0.83 MeV) can result in better spatial image resolutions. However, high-energy γ-rays (1157 keV) are emitted at high rates (99.9%) during 44Sc decay, which can reduce image quality. Therefore, we investigated the impact of these physical properties and performed an unbiased performance evaluation of 44Sc and 68Ga with different imaging phantoms (image quality phantom, Derenzo phantom, and three-rod phantom) on two preclinical PET scanners (Mediso nanoScan PET/MRI, Siemens microPET Focus 120).
Despite the presence of high-energy γ-rays in 44Sc decay, a higher image resolution of small structures was observed with 44Sc when compared to 68Ga. Structures as small as 1.3 mm using the Mediso system, and as small as 1.0 mm using the Siemens system, could be visualized and analyzed by calculating full width at half maximum. Full widths at half maxima were similar for both isotopes. For image quality comparison, we calculated recovery coefficients in 1–5 mm rods and spillover ratios in either air, water, or bone-equivalent material (Teflon). Recovery coefficients for 44Sc were significantly higher than those for 68Ga. Despite the lower positron energy, 44Sc-derived spillover ratio (SOR) values were similar or slightly higher to 68Ga-derived SOR values. This may be attributed to the higher background caused by the additional γ-rays. On the Siemens system, an overestimation of scatter correction in the central part of the phantom was observed causing a virtual disappearance of spillover inside the three-rod phantom.
Based on these findings, 44Sc appears to be a suitable alternative to 68Ga. The superior image resolution makes it an especially strong competitor in preclinical settings. The additional γ-emissions have a small impact on the imaging resolution but cause higher background noises and can effect an overestimation of scatter correction, depending on the PET system and phantom.
68Ga is the most commonly used isotope in metal-organic radiotracers for positron emission tomography (PET). It is well established in the diagnostics of prostate cancer ([68Ga]Ga-PSMA-11) or neuroendocrine neoplasms ([68Ga]Ga-DOTA-TOC) [1, 2]. Due to its promising physical properties, 44Sc has been increasingly investigated as an alternative to 68Ga. The development of a 44Ti/44Sc generator system [3,4,5] and the possibility to produce 44Sc with a cyclotron using calcium targets [6,7,8] are poised to ensure the availability of the isotope.
44Sc decays by positron emission and electron capture at rates of 94.3% and 5.7%, respectively. The mean positron energy (Eβmean) of 44Sc is 0.63 MeV and thereby lower than that of 68Ga (Eβmean = 0.83 MeV). As a result, the smaller positron range in tissue theoretically results in better spatial image resolutions. 44Sc is thus an interesting isotope that may be used in preclinical and clinical PET studies.
Compared to 68Ga, 44Sc emits high-energy γ-rays (1157 keV) at high rates of 99.9% per decay during its stabilization process (Fig. 1). 68Ga emits γ-rays at low rates of 3.6%. Although these prompt γ-emissions occur above the energy window of a PET scan (typically 400–600 keV), they can appear in that window by losing energy through Compton scattering, thereby influencing imaging acquisition. As with other non-pure positron emitters such as 86Y or 124I, additional γ-emissions may lead to random coincidences as well as multiple coincidences of which both can cause reduced qualitative and quantitative imaging quality . Most of these coincidences are insufficiently corrected by standard scatter- and attenuation correction methods. As a consequence, the background noise increases and a loss in contrast can be observed. Notably, these co-emissions can lead to higher radiation doses in patients and medical personnel.
The half-life of 44Sc is often described to be 3.97 h but a recent study reported a half-life of 4.04 h . In contrast to 68Ga (half-life ~ 68 min), the ~ 4 h half-life of 44Sc allows to observe phenomena with slower kinetics such as the diffusion or excretion of larger biomolecules and metabolism processes. Furthermore, decentralized production of tracers and shipping to satellite PET centers are feasible with 44Sc but difficult to achieve with 68Ga [11, 12]. Table 1 compares the physical properties of 44Sc and 68Ga.
The coordination chemistry of Sc3+ is similar to that of other metal ions such as Lu4+ or Ga3+. Therefore, 44Sc binds to commonly used bifunctional chelating agents such as 1,4,7,10-Tetraazacyclododecane-1,4,7,10-tetraacetic acid (DOTA). Several in vitro and in vivo studies demonstrate the compatibility of 44Sc with different bifunctional DOTA-based chelating agents [13,14,15,16,17]. Experimental studies with [44Sc]Sc-DOTA-TATE or [44Sc]Sc-PSMA-617 showed similar characteristics (e.g., lipophilicity, binding affinity, and biodistribution) like the clinically used therapeutics [177Lu]Lu-DOTA-TATE and [177Lu]Lu-PSMA-617 [11, 17]. From a theragnostic point of view, the availability of the β--emitter 47Sc (half-life = 3.35d) could allow the development of diagnostic/therapy tandems with chemically identical compounds [12, 18, 19]. In addition to preclinical studies on somatostatin analogues and PSMA ligands, 44Sc-labeled cetuximab F(ab’)2 fragments, HER2 affibodies, DOTA-NAPamides, and DOTA-Puromycins have been reported [14, 20,21,22,23,24]. Recently, the AAZTA scaffold was described to be a potent chelator for Sc3+ [25,26,27]. First clinical studies using [44Sc]Sc-DOTA-TOC and [44Sc]Sc-PSMA-617 underline the potential of 44Sc-labeled tracers as promising radiopharmaceuticals, especially when being used for pre-therapeutic dosimetry [28,29,30].
Only few preclinical phantom studies that investigate the resolution and image quality of 44Sc have been published so far [31, 32]. In an attempt to close this gap, we performed an unbiased complementary performance evaluation of 44Sc and 68Ga with three different imaging phantoms on two preclinical PET scanners. Typical image quality parameters, i.e., image resolution, recovery coefficient, and spillover ratios, were assessed for each scanner and isotope and the results were compared and discussed.
To evaluate the performance with 44Sc on preclinical PET-systems, we performed multiple phantom studies on two preclinical PET scanners (Mediso nanoScan PET/MRI, Siemens Focus 120) with three different phantoms (image quality phantom, Derenzo phantom, three-rod phantom) and calculated several objective parameters for image resolution and image quality. The applied activity concentration of 44Sc ranged from 0.15 to 1.31 MBq/ccm depending on the phantom used. With decreasing rod diameter in the phantom, the activity concentration was increased. We performed analog experiments with 68Ga and the PET standard 18F. The particular activity concentrations of 44Sc and 68Ga are listed in Table 2 (values for 18F can be found in the supplementary material (Table S1)). For each phantom, the acquisition time was 30 min. In the following segment, the isotopes, the phantoms, and the PET scanners used in this study are briefly specified.
44Sc was obtained from a 44Ti/44Sc generator that was developed at the Institute of Nuclear Chemistry at Mainz University, Germany . Briefly, ~ 170 MBq of 44Sc were eluted with 20 mL of a mixture consisting of 0.07 M hydrochloric acid and 0.005 M oxalic acid. 44Sc was trapped on a cation exchange resin (AG 50 W-X8) and eluted with 3 mL of a 0.25 M ammonium acetate solution (pH 4). ~ 130 MBq of 44Sc were obtained containing less than 10 Bq of 44Ti-activity . Quality control was performed using thin-layer chromatography (TLC) for chemical purity and gamma-spectroscopy for radionuclidic purity . Measurement of 44Sc radioactivity was performed in a dose calibrator (VDC 405, Veenstra Instruments, Joure, Netherlands) with 18F-settings. A conversion factor of 0.70 to account for absolute 44Sc activity was applied .
68Ga was obtained from a 68Ge/68Ga generator based on a TiO2 matrix (Eckert & Ziegler AG, Berlin, Germany). Briefly, ~ 200 MBq of 68Ga were eluted with 5 mL of a 0.1 N hydrochloric acid solution. 68Ga was trapped on a cation exchange resin (AG 50 W-X8) and the resin rinsed with a solution consisting of 80% (v/v) acetone in 0.15 M hydrochloric acid solution . The activity was eluted with a solution consisting of 97.56 (v/v) acetone in 0.05 M hydrochloric acid solution. ~ 180 MBq of 68Ga were obtained containing less than 0.00001% of 68Ge. Quality control was performed using TLC for chemical purity and gamma-spectroscopy for radionuclidic purity [34, 35].
The three phantoms used in this study were configured cylindrically with differently sized drilled holes and chambers (outlines in Fig. 2). All phantoms were made of polymethylmethacrylate to allow for their usage in PET/MRI scanners.
Image quality phantom
The image quality phantom is a standardized phantom (NEMA NU 4-2008) with a length of 63 mm and a diameter of 33.5 mm (Fig. 2b). It consists of a central main chamber that is connected to five rods in the front (Ø = 1, 2, 3, 4, 5 mm) which are located 7 mm around the center as well as two cylindrical chambers in the back (Ø = 8 mm). All three chambers can be filled separately and are not connected to each other. In this study, the main chamber was filled with the radioactive isotope and the two cylindrical chambers in the back were filled with air and water.
The three-rod phantom is a custom-made phantom (based on NEMA NU 2-1994 standard) with a length of 107 mm and diameter of 48 mm (Fig. 2c). It consists of a main chamber and three cylindrical chambers (outside Ø = 15 mm, inside Ø = 11 mm) that are not connected to each other. The main chamber was filled with the radioactive isotope. Each cylindrical chamber was filled with either air, water, or Teflon. Teflon was used to simulate human bone tissue.
The Derenzo phantom is a custom-made phantom similar to that described by Budinger et al. . This cylindrical phantom comprises a length of 61 mm and an inside and outside diameter of 40 mm and 50 mm, respectively (Fig. 2d). A cylindrical block (Ø = 40 mm) with multiple small drills served as an insert. The differently sized rods (Ø = 0.8 mm, 1.0 mm, 1.3 mm, 1.5 mm, 2 mm, and 2.5 mm) are arranged in six sectors. The distance of two neighboring rods is twice the diameter (for diameters 0.8 –1.5 mm).
PET scanners and reconstruction methods
Mediso nanoScan PET/MRI (Scanner 1)
The Mediso nanoScan PET/MRI, in the following referred to as “Scanner 1” is a hybrid small animal scanner consisting of a 12-detector block PET system and a 1-tesla MR system. Every detector block is composed of 39 × 81 lutetium-yttrium oxyorthosilicate (LYSO) crystals with dimensions of 1.12 mm × 1.12 mm × 13.00 mm (total crystal number 37908). The pitch totals 1.17 mm. The axial effective field of view spans 94 mm, whereas the transaxial span depends on the coincidence mode. Three different coincidence modes (1:1, 1:3, and 1:5) are available. Accordingly, the transaxial field of view spans 45, 94, or 120 mm. Each detector block is connected with two photomultipliers covered by a magnetic shield. The PET resolution is 700 μm according to the manufacturer. In this study, all data was obtained in coincidence mode 1:5 and subsequently reconstructed in coincidence mode 1:3. Analytical (2D-FBP, 3DRP) as well as iterative reconstructions (2D-OSEM, 3D-OSEM) are supported. In addition, Mediso offers an iterative reconstruction algorithm (TeraTomo-3D), which is based on a variation of 3D-OSEM/MAP using total variation as a penalty term weighed by a parameter α for regularization.
Siemens Focus 120 (Scanner 2)
The Siemens Focus 120, in the following referred to as “Scanner 2” is a non-hybrid small animal PET-scanner consisting of four ring detectors built by 96 detector blocks with 12 × 12 LSO crystals with 1.52 mm × 1.52 mm × 10 mm dimension (total crystal number 13824). The pitch totals 1.6 mm. The axial effective field of view spans 76 mm and the transaxial field of view spans 100 mm. Each block is connected with a 12-channel photomultiplier. The PET resolution stated by the manufacturer is ≤ 1400 μm with a volume resolution of 2.5 μl. For the Siemens Focus-120, analytical (2D-FBP, 3DRP) and iterative (2D-OSEM, 3D-OSEM, 3D-MAP, 3D-OSEM/MAP) reconstruction algorithms are available. The combined 3D-OSEM/MAP algorithm results in improved image resolution by taking scanner geometry and the point spread function of the detector response into account . Additionally, a smoothing factor restricting values of neighboring voxels was applied.
In this study, an energy discrimination window of 400–600 keV on Scanner 1 and of 350–650 keV on Scanner 2 was set. For reconstruction, the TeraTomo-3D reconstruction algorithm (12 iterations, 6 subsets, 0.4 × 0.4 × 0.8 mm3 voxel size) with normal regularization (α = 0.0005) and 3D OSEM/MAP reconstruction algorithm (256 × 256 matrix, 2 OSEM iterations, 6 subsets, 18 MAP iterations, 0.4 × 0.4 × 0.4 mm3 voxel size) with a smoothing factor of 0.02 was applied. The used reconstruction algorithm with the abovementioned reconstruction settings were recommended by the vendors. All reconstructions included dead time correction, decay correction, normalization, and correction for random coincidence. Acquisition parameters as total coincidence rate, delayed random rate and dead time correction factors are compiled in the supplement material (Table S1). Scatter and attenuation correction were based on a MR-material-map obtained with the Mediso nanoScan PET/MRI or, at the Siemens Focus 120, on a prior transmission scan with 57Co.
Parameters for image quality and image resolution
The following parameters were calculated based on volume-of-interest (VOI) data extracted by PMOD (version 3.606, PMOD Technologies LLC, Zürich, Switzerland).
The recovery coefficient (RC) is part of the National Electrical Manufacturers Association (NEMA) NU 4-2008 standard protocol and can be used to evaluate image quality. The RC describes the decrease of reconstructed activity compared to the true activity in smaller structures. This phenomenon is known as the partial volume effect (PVE), depends on the size of the PET crystals, and occurs if structures are smaller than 2.5 times of the detector size. According to the NEMA protocol, RC was assessed by the equation Maxrod/MeanRV, while Maxrod was the maximum activity concentration in the averaged 10 mm central part of each radioactive rod of the image quality phantom, measured by circular region of interest. MeanRV describes the measured mean activity concentration of a reference cylindrical VOI inside the main chamber.
The spillover ratio (SOR) was calculated in the cold inserts of the three-rod phantom (air, water, and Teflon) and of the image quality phantom (air, water) by the equation Meancold/MeanRV.Meancold describes the measured mean activity concentration in a cylindrical volume in the non-radioactive (“cold”) area inside the rods with the half rod diameter according to NEMA standard protocols. MeanRV describes an activity concentration of a reference VOI inside the main chamber. The error was calculated by the error propagation using standard deviations of average. In addition, SOR outside the phantom was measured in a hollow cylindrical volume around the three-rod phantom.
The spatial resolution was measured by calculating the full width at half maximum (FWHM) in rods inside the Derenzo phantom. A line-profile across the center of representative inner rods was drawn on a transversal image. The profile was extracted and used to calculate the rod’s FWHM by curve fitting using a multi-parameter Gaussian function. Based on the FWHM calculation, both image quality (contrast) and image resolution (discrimination of two adjacent rods) were assessed. Goodness of fit was derived by using the standard errors of the fit parameters.
The results of the 44Sc and 68Ga measurements are presented in the following. All measurements were also performed with 18F and the results are presented in the supplementary material (Tables S2 – S4) as this study focusses on the analysis of 44Sc and the comparison with its chemical competitor 68Ga.
On both scanners, the measured RCs decreased with decreasing rod diameters. Without scatter and attenuation correction, the RC decreased from 0.95 in 5 mm rods to 0.17 in 1 mm rods on Scanner 1 and from 1.00 to 0.27 on Scanner 2, respectively. Linear interpolated RC curves of 44Sc on both scanners are shown in Fig. 3. With scatter and attenuation correction, a slight increase (mean: + 12.5%) of RC values was observed on Scanner 1 (Fig. 3a). The RC ranged from 1.07 in 5 mm rod to 0.23 in 1 mm rod. On Scanner 2, a slightly decrease (mean: − 13.2%) was observed when scatter and attenuation correction were applied (Fig. 3b). The RC ranged from 0.96 in 5 mm rod to 0.16 in 1 mm rod. In Fig. 3 c and d, calculated RC values of 44Sc are compared with RC values of 68Ga on both PET scanners. On both scanners, 44Sc revealed significantly higher RC-values than 68Ga with a mean difference of 40.8% on Scanner 1 and 43.1% on Scanner 2.
SOR using three-rod phantom
On both scanners, without scatter and attenuation correction, the highest SOR for 44Sc was observed in air followed by water and Teflon. The SOR in different media is illustrated in Fig. 4. When scatter and attenuation correction were applied on Scanner 1, SOR values decreased by 32.4% in air outside (0.370 to 0.250), by 58.4% in air inside (0.310 to 0.129) and by 83.3% in Teflon (0.024 to 0.004). No decrease was observed in water (Fig. 4a). In contrast, on Scanner 2, attenuation and scatter correction led to an extensive decrease in any medium (Fig. 4b). SOR decrease ranged from 78.1% in air outside the phantom (0.178 to 0.039), up to 100% (to 0.000) in any media inside the phantom. This extensive decrease of SOR was not observed using 68Ga. In case of the latter, the decrease ranges from 35.8% in water to 75.9% in air (Fig. 4d). A comparison of SOR values obtained with either 44Sc or 68Ga on both Scanner systems is shown in Fig. 4e and f. On Scanner 1, higher SORs were observed with 44Sc outside of the phantom. In all other non-radioactive inserts, no significant disparities in SORs were found (Fig. 4e) between 44Sc and 68Ga. In contrast, on Scanner 2, a significantly lower SOR was observed for 44Sc in any media (Fig. 4f). A visual confirmation of the observed SOR in different transaxial slices of the three-rod phantom is given in Fig. 5.
SOR using image quality phantom
On both scanners, using three-rod phantom without scatter and attenuation correction, higher SOR for 44Sc was observed in air than in water (Fig. 4). When scatter and attenuation correction were applied, SOR values decreased by 66.3% (0.383 to 0.129) in air and by 67.8% (0.199 to 0.064) in water on Scanner 1. On Scanner 2, attenuation and scatter correction led to a substantial decrease of SOR in air by 98.0% (0.342 to 0.07) and to no decrease of SOR in water. As shown in Fig. 4 e and f, no relevant disparities in SOR between 44Sc and 68Ga were observed on either scanner.
In case of 44Sc, structures as small as 1.3 mm or 1.0 mm can be visualized using Scanner 1 or Scanner 2, respectively. The FWHM dependency on rod diameter on both scanners is shown in Fig. 6. By applying scatter and attenuation correction, the FWHM could be partly decreased or remained similar. On Scanner 2, a steady decrease of the FWHM from 2.5 to 1.0 mm rod diameter was observed. In contrast, on Scanner 1, the FWHM was similar in the range from 2.5 to 1.5 mm rod diameter but a remarkable increase was overserved in the range from 1.5 to 1.0 mm. In comparison to 68Ga, smaller structures were identified using 44Sc. On Scanner 1, structures of sizes up to 1.3 mm were identified with 44Sc and structures of sizes up to 1.5 mm were identified with 68Ga. On Scanner 2, structures of sizes up to 1.0 mm were identified with 44Sc and structures of sizes up to 1.3 mm were identified with 68Ga. The FWHM calculations for Scanner 1 resulted in similar values for both nuclides. Significantly, lower values for 44Sc were calculated for Scanner 2 in case of rod diameters ≤ 1.5 (Fig. 6d). Summed transversal slices of the Derenzo phantom with 44Sc and 68Ga are depicted in Fig. 7.
The decrease of measured RCs of 44Sc with decreasing rod diameters may be explained by the impact of the positron range as well as the partial volume effect. Due to the positron range, a spatial distribution of the reconstructed activity that is larger than that of the geometrical rod diameter is observed. Thus, compared to the true activity, the reconstructed activity decreases with smaller rod diameter, leading to smaller RC values. On both scanners, RC values for 44Sc (Eβmean = 0.63 MeV) were significantly higher than those for 68Ga (Eβmean = 0.83 MeV). This expected behavior can be explained by the different positron energies and the resulting different positron ranges. A higher positron range leads to a larger distribution of the reconstructed activity and thus a lower RC. To the best of our knowledge, a comparable assessment of RCs for 44Sc has not been published to date. In Fig. 8, the RC values for 44Sc, as obtained from Scanner 2 in this study, are compared to RC values of different isotopes (18F, 68Ga, 89Zr, 124I) that were reported by Disselhorst et al. using similar reconstruction methods . The RC values obtained for 68Ga in this study are similar to those reported by Disselhorst et al., which indicates that a comparison of both datasets is feasible. As expected, the RC values of 44Sc (Eβmean = 0.63 MeV) range between 89Zr (Eβmean = 0.40 MeV) and 124I (Eβmean = 0.82 MeV). It can be concluded that RC values mostly depend on the positron energy. Furthermore, additional γ-emissions by 44Sc appear to play a minor role in the determination of RC values but cause larger error intervals.
Without scatter and attenuation correction, the highest SOR was expectedly observed in air, followed by water and Teflon. This observation can be explained by the differences in material densities that influence positron deceleration. Applying scatter and attenuation correction on Scanner 1 caused a decrease in SOR values in both phantoms. 44Sc-derived SOR values obtained from air inside, water, and Teflon were similar or slightly higher (in case of air outside) to 68Ga-derived SOR values. This is surprising since 44Sc has a smaller positron energy. This finding likely results from the additional γ-emission during 44Sc decay. The γ-emission might also explain the higher error intervals observed for 44Sc. The γ-emission increased the background noise, which also led to an increase in measured activity in areas that are apparently free of activity. This phenomenon was described in previous studies for other non-pure positron emitters such as 124I, 76Br, and 86Y [39,40,41]. To the best of our knowledge, no SOR values for 44Sc have been reported to date in literature. On Scanner 2, we observed a significant decrease of SOR values with a virtual disappearance of spillover inside the three-rod phantom. This was caused by overestimation of scatter correction that results from additional γ-emissions. In Fig. 9 a and b, the normalized activity and scatter profiles of 44Sc and 68Ga in the three-rod phantom are compared. They differ in the activity profile with significantly higher radial tails for 44Sc due to higher background noise caused by γ-emissions. The reconstruction software of Scanner 2 offers a possibility to adjust the scatter correction for none-pure PET isotopes by modification of the tail fitting for scatter estimation. The standard correction factor in this modification was tested for 86Y but did not fit for 44Sc in this case. As shown in Fig. 9 a, when using this standard setting, the simulated scatter profile modeled to the 44Sc raw data was too high, especially in the center part of the three-rod phantom. This overestimation of calculated scatter for non-pure positron emitters led to over-subtraction in the central part. Using the image quality phantom, the overcorrection was not as prominent as with the three-rod phantom (Fig. 9c, d), which may be attributed to geometrical differences of the phantoms. This issue is also noted in the literature and consequently, different approaches for prompt γ-corrections have been proposed . A suitable correction of additional γ-emissions is necessary and should be applied in further phantom studies.
In general, observed image resolutions obtained with 44Sc were superior to those obtained with 68Ga. On both PET systems, smaller rod diameters could be visualized and analyzed with 44Sc. 44Sc also showed significantly smaller FWHM than 68Ga in rods with small diameters. This indicates that the spatial resolution is dependent more on the positron energy and the resulting positron range than on prompt γ-emissions. This finding is consistent with the results of several previous phantom studies [31, 38, 42, 43]. In Table 3, the maximum spatial image resolutions in a Derenzo phantom of 44Sc, 68Ga, and of other nuclides are compiled [42, 43]. These previously published data fit well with our data and support the assumption that positron energy and scanner properties are the main factors for the maximum spatial resolution of preclinical PET systems. Despite the better NEMA intrinsic resolution of Scanner 1 that is caused by smaller crystals, tomographic resolution of Scanner 2 was slightly superior. This may be explained by including the resolution recovery in the OSEM3D/MAP reconstruction of Scanner 2 and applying dedicated point spread functions.
Compared to the only phantom study in literature by Bunka et al. that investigated the spatial resolution of 44Sc , we calculated higher FWHM values (discrepancy 43.4-78.2%) which can be explained by different experimental settings (different phantoms, different PET scanners, different reconstruction algorithms) and different analyses (different line profiles, different fit curves, background subtraction). Nevertheless, Bunka et al. also reported smaller FWHM for 44Sc than for 68Ga, which is in accordance with our finding that 44Sc enables imaging with improved resolution.
Based on this image analysis, 44Sc appears to be a suitable alternative to 68Ga. Representative in vivo images are shown in the supplementary section (Figure S1). The animal studies will be reported elsewhere. This phantom study is limited by using only iterative 3D reconstruction algorithms and preselected reconstruction parameters. The argument that 44Sc is a suitable alternative to 68Ga with superior image resolution and recovery, may be true with different reconstruction algorithms as Bunka et al. observed using OSEM-2D . Further studies investigating the optimal reconstruction and reconstruction parameters for 44Sc are needed as standard reconstruction settings used in this study were optimized for 18F. In comparison to 18F, 44Sc showed an expected inferior image quality caused by the ~ 2.5 times higher positron energy (0.63 MeV vs. 0.25 MeV).
The additional γ-emissions not only cause higher background noise and affect scatter correction; they also result in higher radiation dose for the animal or patient. Eppard et al. reported a two times higher absorbed kidney dose (mSv/MBq) with 44Sc than with 68Ga labeled PSMA-617 in patients with metastasized castration-resistant prostate carcinoma . However, by taking advantage of the longer half-life, applied activity could be reduced in many cases. Eppard et al. administrated 50 MBq of 44Sc-PSMA-617 and achieved a comparable image quality as with 120 MBq of 68Ga-PSMA-11 . The higher radiation dose for the technical staff also has to be taken into account. Further radiation shield to protect technical staff may be needed.
Based on this image analysis, 44Sc appears to be a suitable alternative to 68Ga. The superior image resolutions obtained with 44Sc that is caused by its lower positron energy makes it a strong competitor, especially in a preclinical setting. Additional γ-emissions are causing higher background noises and an overestimation of scatter correction in the central part of the phantom, depending on the PET system and the phantom. These additional γ-emissions should be corrected for in further studies to insure they are not distorting image corrections and to allow for quantification of the PET-signal.
Availability of data and materials
The datasets used and analyzed during the current study are available from the corresponding author on reasonable request.
3D reprojection reconstruction
With scatter and attenuation correction
- Eβmean :
Mean positron energy
Filtered back projection
Full width at half maximum
Image quality phantom
Maximum a posteriori image reconstruction
Magnetic resonance imaging
National Electrical Manufactures Association
Ordered subset expectation maximization
Positron emission tomography
Point spread function
Prostate specific membrane antigen
Partial volume effect
- Scanner 1:
Mediso nanoScan PET/MRI
- Scanner 2:
Siemens Focus 120
Without scatter and attenuation correction
Volume of interest
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Rosar, F., Buchholz, H., Michels, S. et al. Image quality analysis of 44Sc on two preclinical PET scanners: a comparison to 68Ga. EJNMMI Phys 7, 16 (2020). https://doi.org/10.1186/s40658-020-0286-3
- Small animal PET
- Phantom study
- Image quality
- Positron energy
- Positron range