 Original research
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Investigation of posttherapeutic imagebased thyroid dosimetry using quantitative SPECT/CT, iodine biokinetics, and the MIRD’s voxel S values in Graves’ disease
EJNMMI Physics volume 7, Article number: 6 (2020)
Abstract
Background
Before radioiodine therapy for Graves’ disease, the estimated thyroidabsorbed dose is calculated based on various clinical parameters. However, the actual accumulation of iodine in the thyroid during radioiodine therapy is not determined. We validated the feasibility of posttherapeutic imagebased thyroid dosimetry through quantitative singlephoton emission computed tomography (SPECT) imaging and thyroid biokinetics and expanding the Medical Internal Radiation Dose Committee’s (MIRD) voxel dosimetry guidelines.
Methods
Fortythree patients with Graves’ disease who underwent radioiodine therapy were chosen as subjects for this retrospective analysis. We acquired patients’ SPECT images 24 h after oral administration. SPECT images were quantified using system volume sensitivity to calculate timeintegrated activity coefficients on a voxel basis. Absorbed dose was obtained by convolving MIRD guideline voxel S values with timeintegrated activity coefficients. To determine accuracy, we compared the results obtained using the posttherapeutic imagebased absorbeddose method (D̅_{image,PVC}) with absorbed doses calculated using the method described by the European Association of Nuclear Medicine (pretherapeutic method; D_{EANM}).
Results
Using imagebased dosimetry as posttherapeutic dosimetry, we visualized the local accumulation and absorbed dose distribution of iodine in the thyroid. Furthermore, we determined a strong correlation (Pearson’s correlation coefficient = 0.89) between both dosimetries, using the regression equation: D̅_{image,PVC} = 0.94 × D_{EANM} + 1.35.
Conclusion
Posttherapeutic imagebased doses absorbed in the thyroid resembled those of pretherapeutic EANM methodbased absorbed doses. Additionally, the posttherapeutic imagebased method had the advantage of visualizing thyroid iodine distribution, thus determining local dose distributions at the time of treatment. From these points, we propose that posttherapeutic imagebased dosimetry could provide an alternative to standard pretherapeutic dosimetry to evaluate dose response.
Background
Graves’ disease is an autoimmune disease of the thyroid, and the main treatment options are medication (betablockers or antithyroid drugs), radioiodine therapy (iodine131), and thyroidectomy [1]. Radioiodine therapy for Graves’ disease has been a popular and effective treatment for more than 50 years [2, 3]. The therapeutic effect of radioiodine therapy for Graves’ disease relates to the amount of administered radioactivity, or thyroidabsorbed dose [4, 5]. Several methods for calculating absorbed dose [6,7,8] include Marinelli et al.’s [8] or the European Association of Nuclear Medicine (EANM) guideline’s methods [9, 10]. Using the EANM guidelines, absorbed dose is determined based on thyroid volume, radioiodine uptake (RIU), and effective iodine halflife. However, the actual accumulation of iodine in the thyroid at the time of radioiodine therapy can only be estimated because these calculations use formulae to determine administered radioactivity before treatment. Furthermore, these formulae assume homogeneous uptake of iodine in the thyroids of patients with Graves’ disease.
An alternative to pretherapeutic calculation, quantitative measurements using singlephoton emission computed tomography (SPECT) visualize the actual uptake and distribution of iodine in the thyroid and calculate the absorbed dose of iodine131 at the time of radioiodine therapy. If this imagebased absorbed dose is calculated as posttherapeutic dosimetry, we can directly grasp the local accumulation and dose distribution of iodine131 during treatment. Although previous studies have utilized radioactive tracers to measure the absorbed radiation doses of organs or tumors from SPECT images [11, 12], to the best of our knowledge, this approach is yet to be used to measure absorbed doses in the thyroid or for treating Graves’ disease.
In this study, we validated the feasibility of the posttherapeutic imagebased dosimetry for Graves’ disease, applying quantitative SPECT measurements and thyroid biokinetics, thus expanding the Medical Internal Radiation Dose Committee’s (MIRD) voxel dosimetry guidelines [13,14,15,16].
Methods
Patients
Fortyfive consecutive patients with Graves’ disease who underwent radioiodine therapy as outpatients from December 2014 to April 2018 were included in this retrospective analysis. Two of the 45 patients were excluded from the analysis for the following reasons: one due to insufficient dietary iodine restriction, and another for inaccurate measurements during the thyroid iodine131 uptake test. A final 43 patients (7 males, 36 females) were included in this study. The average patient age was 51 ± 16 years. Because 5 patients underwent radioiodine therapy twice during this period, our analysis eventually included 48 cases. From 2 weeks before treatment, all patients were subjected to dietary iodine restriction and discontinued antithyroid drugs. In addition, patients underwent a nonenhanced neck CT examination (Aquilion 64 or Aquilion PRIME SP; Canon Medical Systems, Otawara, Japan) for thyroid volumetry. Contour extractions of the thyroid from CT images (5 mm slice thickness) were performed manually by one radiologist (nuclear medicine physician). The sum of the thyroid volume obtained from each slice was denoted as the total thyroid volume.
Subsequently, using a thyroid uptake system (AZ800; Anzai Medical, Tokyo, Japan), which has a monophotomultiplier tube and 2 in. (diameter) × 2 in. (thickness) NaI crystal, a thyroid iodine131 uptake test (radioactivity = 3.7 MBq) was performed for all patients to predict the thyroidabsorbed dose during radioiodine therapy. RIU measurements were carried out 3, 24, 96, and 168 h after oral administration, and the effective iodine halflife was calculated by approximating RIUs after 24 h as a monoexponential function. Using Marinelli et al.’s formula, administered radioactivity during radioiodine therapy was derived using the total thyroid volume, RIU at 24 h after administration, and effective iodine halflife [8]. Our hospital planned a thyroidabsorbed radiation dose of approximately 200–250 Gy. The nuclear medicine physician also adjusted the absorbed dose according to the clinical symptoms of each patient. In Japan, the administered radioactivity for outpatients with Graves’ disease has an upper limit of 500 MBq due to legal regulations. Therefore, we did not administer more than 500 MBq for these patients.
EANMbased thyroid dosimetry (pretherapeutic dosimetry); D _{EANM}
We retrospectively calculated EANM guidelinebased absorbed dose for each of the 48 cases. The iodine131 uptake fraction of the thyroid at time t [RIU(t)] was modeled as a biexponential function using the 2compartment model based on the iodine131 biokinetics (Eq. 1) [9,10,11]:
where k_{t} denotes the biokinetic transfer rate from the blood pool to the thyroid, k_{B} denotes the transfer rate from the blood pool to renal clearance or radioactive decay, and k_{T} denotes the rate of transfer from the thyroid to hormone excretion or radioactive decay. First, we obtained k_{t}, k_{B}, and k_{T} fitting the four RIU time points using the LevenbergMarquardt method (GNU Octave software version 4.4.1) to Eq. 1 [10, 17]. Then, the absorbed dose D_{EANM} (Gy) was calculated using Eqs. 2 and 3 from the EANM guidelines [9,10,11] and Hänscheid’s methods [17]:
where A is the administered radioactivity (MBq), \( \overline{E} \) is the mean deposition energy per iodine131 decay (Eq. 3), and V is thyroid volume in milliliters obtained by neck CT images. Here, the density of the thyroid was assumed to be 1 g/mL.
Imagebased thyroid dosimetry (posttherapeutic dosimetry); D _{image}
For our study, the posttherapeutic absorbed dose was calculated for each voxel on the basis of the MIRD’s guidelines for voxel dosimetry using SPECT images. Patients’ SPECT images were acquired using a Symbia T6 (Siemens Healthcare, Erlangen, Germany) 24 h after oral administration to confirm iodine uptake in the thyroid. SPECT images were acquired using the following parameters: high energy (HE) collimation, a 128 × 128 matrix, 20 s/projection, and total 60 projections (360° acquisition orbit). SPECT images were then reconstructed using ordered subset expectation maximization with depthdependent threedimensional resolution recovery (OSEM3D; 15 subsets, 30 iterations, no postfilter) with CTbased attenuation correction and energy windowbased scatter correction (15% main window centered at 364 keV, 15% sub window to touch the lower and upper of the main window). To calculate imagebased absorbed doses, it was necessary to estimate the radioactivity of each voxel from SPECT images. Prior to dosimetry, we used a cylindrical phantom (16 cm diameter, 15 cm depth, 3016 mL volume) filled with uniform iodine131 (78 MBq), to obtain the system volume sensitivity (S_{vol}), which is the conversion factor used for calculating radioactivity from SPECT counts, according to the method described by Zeintl et al. (Eq. 4) [18, 19]:
where A_{phantom} is the decay corrected activity (MBq), T_{phantom} is the scan duration (s), V_{voxel} is the voxel volume (mL), C_{phantom} is the mean count in the SPECT image, and V_{phantom} is the cylindrical phantom volume (mL).
Next, SPECT counts were converted into timeintegrated activity coefficients in order to apply voxel S values (mGy MBq^{−1} sec^{−1}), as recommended by the MIRD [13,14,15,16]. Radioactivity for each voxel (MBq/voxel) was obtained by dividing the acquired SPECT counts (C_{thyroid}) of each point (x, y, z) by the scan duration (T_{thyroid}) and multiplying by S_{vol}. SPECT images were obtained 24 h after oral administration; therefore, radioactivity per voxel at oral administration [A_{0}(x, y, z)] was calculated by dividing the SPECT counts by pretherapeutic RIU (24 h) (Eq. 5):
Since radioactivity at time t was calculated by multiplying the administered radioactivity by RIU(t), timeintegrated activity coefficients [\( \overset{\sim }{A} \) (x, y, z)] were derived by integrating over the whole range (Eq. 6). Furthermore, we obtained absorbed doses for each voxel [D_{image}(x,y,z)] by convolving the S value kernel (k_{s}) of 11 × 11 × 11 voxels (33 × 33 × 33 mm) (Eq. 7). According to Peters et al. [20] and Bockisch et al. [21], there is little difference between RIU at therapeutic and test doses. Therefore, we used the test dose RIU for our calculations:
The thyroidabsorbed dose was obtained by extracting the thyroid region from the whole absorbeddose image. Box plots for thyroidabsorbed dose distributions were then generated for all patients. To check the accuracy of D_{image} values, we compared them to the D_{EANM} values. SPECT images often have partial volume effects resulting from the deterioration of spatial resolution; therefore, we assumed that the absorbed dose calculated using our imagebased dosimetry would also be influenced by these effects. When determining mean thyroidabsorbed doses, we acquired a weighting factor based on the geometry transfer matrix (GTM) concept (Eq. 8) [22] for thyroid volume; to correct the partial volume effect (called partial volume correction; PVC), we divided mean D_{image} in thyroid region, \( {\overline{D}}_{\mathrm{image}} \), by this weighting factor, W_{PVC} (Eq. 9):
where V_{voxel} is the voxel volume (mL) and \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \) is the partial volume corrected mean of D_{image} in the thyroid region, \( {\overline{D}}_{\mathrm{image}} \). Before the PVC, we visually confirmed no iodine131 uptake outside the thyroid in the SPECT/CT images. The thyroid region in the SPECT image was determined using a threshold equal to the CTbased thyroid volume, V. The spatial resolution of the SPECT image in the x, y, z direction was measured using a line source (1 mm diameter) to obtain a threedimensional (3D) point spread function [23]. Then, a binary image was created by setting the volume of interest (VOI) corresponding to the thyroid volume in the SPECT image, in which a value of 1 was given to the area within the thyroid VOI and 0 corresponded to the area outside the VOI. Convolution of the binary image with the 3D point spread function blurs the region of interest in the range of 0–1 to create a distribution (the regional spread function; RSF) [22]. By comparing the RSF and the original VOI, it was possible to determine how many SPECT counts remained in the VOI or spillout. The PVC based in the GTM corrects for spillout from the thyroid VOI.
Statistical analysis
The statistical software R (software package version 3.5.1 for Windows) was used in this study. Using single regression analysis, we derived a regression equation for comparing EANMbased absorbed doses (D_{EANM}) and mean imagebased absorbed doses that incorporate PVC (\( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \)) or no PVC (\( {\overline{D}}_{\mathrm{image}} \)). In addition, the BlandAltman analysis was performed for comparison between D_{EANM} and both \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \) and \( {\overline{D}}_{\mathrm{image}} \).
We used the Bonferronicorrected WilcoxonMannWhitney test to assess the relationship between therapeutic outcomes (hypothyroidism, euthyroidism, and hyperthyroidism) and the thyroidabsorbed dose calculated from each method. p values < 0.05 were considered statistically significant.
Results
Table 1 summarizes patient details, including thyroid volume, RIU at 24 h, effective iodine halflife, administered radioactivity, D_{EANM}, and mean D_{image} with/without PVC (\( {\overline{D}}_{\mathrm{image}} \), \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \)). Mean thyroid volume and RIU at 24 h were 32.7 ± 15.1 mL (range = 12.0–77.4) and 0.66 ± 0.16 (range = 0.19–0.94), respectively. Mean effective iodine halflife and administered radioactivity were 6.14 ± 1.31 days (range = 2.98–9.16) and 397 ± 94 MBq (range = 222–481), respectively. Mean D_{EANM} calculated by EANMbased thyroid dosimetry was 230.2 ± 56.7 Gy (range = 104.3–362.3). Compared to mean D_{EANM}, \( {\overline{D}}_{\mathrm{image}} \) and \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \) were 132.6 ± 32.2 Gy (range = 53.1–200.7) and 217.9 ± 59.8 Gy (range = 95.7–348.6), respectively.
Visually, the absorbed dose distribution for thyroids (Fig. 1) appeared homogeneous in most cases, although some cases displayed a heterogeneous distribution (patient nos. 1, 2, 7, 9, and 29). Three cases (patient nos. 1, 2, and 7) became hypothyroidism, and the other two cases with more heterogeneous dose distribution (patient nos. 9 and 29) became euthyroidism. D_{EANM} is calculated as a single value due to the assumption that iodine131 is homogeneously distributed in the thyroid. In comparison, D_{image} calculates the absorbed dose for each voxel, so the absorbed dose [D_{image}(x,y,z)] varies from voxel to voxel. As a result, the thyroidabsorbed dose calculated using our imagebased dosimetry was observed as a dose distribution (Fig. 2). Note that PVC is not applied to the dose distribution in Fig. 2. Mean maximum and minimum D_{image} values for the thyroid region were 297.8 ± 83.2 Gy (range = 136.6–512.9) and 69.6 ± 18.4 Gy (range = 29.8–107.5), respectively.
Figure 3a shows the relationship between D_{EANM} and mean D_{image} without PVC (\( {\overline{D}}_{\mathrm{image}} \)). There was a strong correlation (Pearson’s correlation coefficient = 0.82) between the conventional method (D_{EANM}) and imagebased method (\( {\overline{D}}_{\mathrm{image}} \)), using the regression equation: \( {\overline{D}}_{\mathrm{image}}=0.47\times {D}_{\mathrm{EANM}}+4.89 \) (95% confidence intervals (CI) of slope and yintercept = 0.37–2.19 (p < 0.001) and 0.56–47.59 (p = 0.03), respectively). Figure 3b shows the BlandAltman plot between D_{EANM} and \( {\overline{D}}_{\mathrm{image}} \). There were fixed bias (paired t test, p < 0.001) and proportional bias (Pearson’s correlation coefficient = − 0.72 [95% CI = − 0.84 to − 0.55]). Fixed bias was − 97.7 Gy (95% CI = − 107.9 to − 87.4), that is, \( {\overline{D}}_{\mathrm{image}} \) was lower than D_{EANM} in the same patient.
Similarly, Fig. 4a shows the relationship of D_{EANM} and mean D_{image} with PVC (\( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \)). There was also a strong correlation (Pearson’s correlation coefficient = 0.89) between both methods with the regression equation: \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}}=0.94\times {D}_{\mathrm{EANM}}+1.35 \) (95% confidence intervals (CI) of slope and yintercept = 0.80–1.08 (p < 0.001) and − 32.2–34.8 (p = 0.94), respectively). Figure 4b shows the BlandAltman plot between D_{EANM} and \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \) in three therapeutic outcomes. There was also fixed bias (paired t test, p < 0.01) but no proportional bias (Pearson’s correlation coefficient = 0.11 (95% CI = − 0.17–0.39]). The fixed bias was − 12.4 Gy (95% CI = − 20.3 to − 4.4); \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \) was almost equivalent to D_{EANM} in the same patient. Twelve of 16 cases whose therapeutic outcomes were euthyroidism or hyperthyroidism fell below the regression line in Fig. 4.
In the scan and reconstruction conditions of this study, the spatial resolution (full width at half maximum [FWHM]) in the x, y, and z directions were 11.0, 10.4, and 11.0 mm, respectively. The weighting factor, W_{PVC}, for each case can be calculated from the 3D point spread function and the thyroid volume in the SPECT image (Eq. 8). The relationship between the W_{PVC} calculated using the GTM method (range = 0.45–0.80) and thyroid volume for each case is shown in Fig. 5.
Table 2 shows the relationship between therapeutic outcomes and thyroidabsorbed dose calculated from each method (D_{EANM}, \( {\overline{D}}_{\mathrm{image}} \), and \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \)). Thirtytwo cases (67%) analyzed in this study eventually had hypothyroidism. However, there was no significant difference between the three therapeutic outcomes with any of the methods.
Discussion
Various thyroidabsorbed dose calculation methods have been devised previously [6,7,8, 17]; however, none was imagebased, and all assumed that iodine uptake by the thyroid is homogeneous. Furthermore, these calculation methods were designed to determine administered radioactivity before radioiodine therapy. Therefore, there is no effective method for determining absorbed doses after radioiodine therapy. The pretherapeutic dosimetry described by Marinelli et al. or in the EANM guidelines can only be estimated [8,9,10]. Iodine uptake by the thyroid does not always conform to the models used to determine their calculation formulae. As a result, there is a difference between the estimated and actual absorbed doses. In contrast to these methods, we herein examined the effectiveness of the posttherapeutic dosimetry based on quantitative SPECT imaging and thyroid biokinetics by expanding the MIRD’s guidelines for voxel dosimetry. Because this method uses RIU values and SPECT images taken at the time of treatment, the distribution of iodine131 in the thyroid is directly reflected in the absorbed dose distribution, and it is possible to visualize local iodine uptake in the thyroid. Although previous studies have also utilized SPECT imaging to calculate absorbed doses for oncology [11, 12], no reports demonstrate its application to Graves’ disease.
From posttherapeutic SPECT images, we observed that iodine uptake and absorbed dose may not always be homogeneously distributed in the thyroid (Fig. 1). Generally, Graves’ disease increases iodine uptake of the thyroid in a diffuse manner [1]. Therefore, a homogenous distribution of radioactivity is expected, and as such is a presumption when calculating absorbed dose using the conventional method. However, we noted several cases in which the absorbed dose was heterogeneous (Fig. 1), which supports the possibility that uptake of iodine differs locally in Graves’ disease. These local differences in iodine uptake would therefore widen the range of absorbed doses. Posttherapeutic imagebased dosimetry could help to reduce inaccuracies in thyroid dose calculations by accounting for local differences in iodine uptake.
Furthermore, the absorbed dose was widely distributed for each patient (Fig. 2). One reason for this observation could be explained by the partial volume effect caused by the low spatial resolution of SPECT; in this study, several methods were used to suppress the degradation of spatial resolution, including OSEM3D, increasing the update number (subset number × iteration number), and the absence of a postfilter. However, it was not possible to completely eliminate the influence of spatial resolution deterioration. Therefore, the broad distribution of absorbed doses was likely influenced by the partial volume effect to some extent. Moreover, the mean D_{image} decreased 0.45–0.80 times without PVC depending on the thyroid volume (Fig. 5). With the deterioration of spatial resolution, SPECT counts in the thyroid spillout of this region. As a result, the dose distribution is skewed towards lower values due to the partial volume effect. Analyzing the results with and without PVC, PVC is necessary to compare D_{EANM} as pretherapeutic dosimetry and D_{image} as posttherapeutic dosimetry. Prior to this study, we also tried voxelbyvoxel PVC by the LucyRichardson method [24], but this method resulted in Gibbs artifacts on the SPECT image. We determined that the imagebased absorbed dose should not be calculated from images with Gibbs artifacts, and we have abandoned the application of this method. Using higherresolution SPECT images using image restoration or superresolution techniques could, therefore, result in more accurate determinations of absorbed dose distribution.
Absorbed doses determined using the conventional EANMbased and imagebased methods (D_{EANM} and \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \), respectively) had a strong correlation, but there was fixed bias (Fig. 4). This correlation implies that posttherapeutic imagebased dosimetry provides an appropriate alternative to standard pretherapeutic dosimetry to evaluate dose response. This also accounts for heterogeneity in iodine uptake by the thyroid by providing additional information, including dose distribution.
Both the rate of therapeutic outcomes and the likelihood of developing hypothyroidism increase with increasing thyroidabsorbed radioactivity doses [4, 5, 20, 25]. However, cutoff values for absorbed dose have yet to be established for radioiodine therapy for Graves’ disease, possibly because there has previously been no clear way to determine absorbed doses after treatment. Using the posttherapeutic imagebased method here (i.e., absorbed dose distribution and \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \)), it may be possible to identify a clear relationship between therapeutic outcomes and dose distribution in the thyroid. Our hospital aims to treat Graves’ disease with radioiodine therapy, achieving iatrogenic hypothyroidism that has been completely compensated to the euthyroid state with oral levothyroxine. Therefore, the administered radioactivity or prescribed absorbed dose to patients with Graves’ disease has been set higher. Many cases whose therapeutic outcomes were euthyroidism or hyperthyroidism fell below the regression line (Figs. 3 and 4). This might be due to the difference between estimated and actual absorbed doses. However, there was no significant difference between the three therapeutic outcomes with any of the methods (Table 2). The limitation of this study is that we could not identify the relationship between imagebased absorbed doses and therapeutic outcomes because of the retrospective nature of the study. Additional prospective studies are required to further investigate the relationship between posttherapeutic imagebased dosimetry and therapeutic outcomes.
Another limitation is the necessity for pretherapeutic measurements to obtain the individual biokinetic properties in patients as only a single SPECT scan is acquired. According to previous studies [20, 21], we assumed little difference between RIU at therapeutic and test doses. Conversely, there were also reports that the biokinetics of iodine131 at treatment differed from that at uptake test [26, 27]. Canzi et al. reported that iodine131 uptake at treatment was reduced by 12% due to the stunning effect of iodine131 therapeutic activity [27]. Assuming the same biokinetic behavior between pre and posttherapy, each voxel may increase in uncertainty or accrue a systematic error in the absorbed doses obtained. To resolve this uncertainty, we need to carry out multiple SPECT examinations during radioiodine therapy to directly reflect the biokinetics at treatment.
In our study, the administered radioactivity in Graves’ disease was 500 MBq or less. Therefore, we considered that count loss minimally affected this situation, and we did not need to perform the dead time correction. However, in the most recent paper by Gregory et al. [28], they measured the resolving time τ with the same type of SPECT/CT system used in this study (3.796 × 10^{−6} s). Taking into account that the mean count rate of projection right above the thyroid in each patient was 10.7 ± 3.6 kcps in the 15% main window centered at 364 keV, the dead time correction factor for the nonparalyzable model, D_{τ}, calculated from Eq. 10 is 1.04 ± 0.01 (range = 1.01–1.07):
where R_{T} is the true count rates and R_{M} is the measured count rates. Not performing the dead time correction is a limitation of this study.
Assuming the dead time correction is simply performed by multiplying D_{τ} by \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \) for each patient, the regression equation between the dead time corrected \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \), namely \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}}^{\prime } \) and D_{EANM} is \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}}^{\prime } \) = 0.98 × D_{EANM} + 1.23. With this correction, the fixed bias between D_{EANM} and \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}}^{\prime } \) was also eliminated (paired t test, p = 0.454). The fixed bias between D_{EANM} and \( {\overline{D}}_{\mathrm{image},\mathrm{PVC}} \) could be eliminated by performing the strict dead time correction.
We must also consider the option of performing imagebased dosimetry before treatment, although we must be aware that performing this dosimetry may conflict with dietary iodine restrictions. Our country is classified as an iodinesufficient area, and all patients are subjected to strict dietary iodine restriction before treatment. Thus, pretherapeutic imagebased dosimetry is not practical and posttherapeutic imagebased dosimetry proves more reasonable.
Conclusion
In this study, we validated the feasibility of the posttherapeutic imagebased dosimetry for Graves’ disease, applying quantitative SPECT, voxel S values, and RIU values. Posttherapeutic imagebased thyroidabsorbed doses were consistent with those of pretherapeutic EANM methodbased absorbed doses. In addition, a posttherapeutic imagebased method had the advantage of being able to visualize thyroid iodine distribution and hence determine local absorbed dose distributions at the time of treatment. From these points, we suggest that posttherapeutic imagebased dosimetry could provide an appropriate alternative to standard pretherapeutic dosimetry for doseresponse evaluation. Future studies are required to improve the accuracy of dosimetry and identify the relationship between thyroidabsorbed dose at the time of radioiodine therapy and therapeutic outcomes.
Availability of data and materials
The datasets used and/or analyzed during the current study are available from the corresponding author on reasonable request.
Abbreviations
 CI:

Confidence interval
 EANM:

European Association of Nuclear Medicine
 FWHM:

Full width at half maximum
 GTM:

Geometry transfer matrix
 HE:

High energy
 kcps:

Kilocounts per second
 MIRD:

Medical Internal Radiation Dose Committee
 OSEM3D:

Ordered subset expectation maximization with depthdependent threedimensional resolution recovery
 PVC:

Partial volume correction
 RIU:

Radioiodine uptake
 RSF:

Regional spread function
 SPECT:

Singlephoton emission computed tomography
 VOI:

Volume of interest
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The authors thank all current and former Nagoya University Hospital Nuclear Medicine Department staffs who contributed to the acquisition of data included in this study.
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KK is the guarantor of integrity of the entire study. NF and KK contributed to the study concepts and design. NF and KK contributed to the literature research. YK, NF, and SA contributed to the clinical studies. YK, NF, and KK contributed to the experimental studies/data analysis. NF contributed to the statistical analysis. KK and NF contributed to the manuscript preparation. KK contributed to the manuscript editing. All authors read and approved the final manuscript.
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All procedures performed in studies involving human participants were in accordance with the ethical standards of the Ethical Review Committee of Nagoya University Hospital and with the 1964 Helsinki Declaration and its later amendments or comparable ethical standards. This study was approved by the Ethical Review Committee of Nagoya University Hospital (application no. 2018–0179). Since this study analyzed clinical data retrospectively, we did not obtain informed consent directly from each patient. Instead of direct informed consent, we published the research contents on the university web page and provided an optout opportunity.
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Fujita, N., Koshiba, Y., Abe, S. et al. Investigation of posttherapeutic imagebased thyroid dosimetry using quantitative SPECT/CT, iodine biokinetics, and the MIRD’s voxel S values in Graves’ disease. EJNMMI Phys 7, 6 (2020). https://doi.org/10.1186/s4065802002747
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DOI: https://doi.org/10.1186/s4065802002747