Dependence of treatment planning accuracy in peptide receptor radionuclide therapy on the sampling schedule
© Maaß et al. 2016
Received: 5 November 2015
Accepted: 16 March 2016
Published: 25 March 2016
Peptide receptor radionuclide therapy (PRRT) plays an important role in the treatment of neuroendocrine tumors (NET). Pre-therapeutic dosimetry using the area under the measured time-activity curve (AUC) is important. The sampling schedule for this dosimetry determines the accuracy and reliability of the obtained AUC.
The aim of this study was to investigate the effect of reduced number of measurement points (i.e., gamma camera image acquisition or serum measurements) on treatment planning accuracy in PRRT using 111In-labeled-diethylenetriaminopentaacetic acid-octreotide (DTPAOC; Octreoscan™).
Pre-therapeutic biokinetic data of 15 NET patients were investigated using a recently developed physiologically based pharmacokinetic (PBPK) model. Two parameter sets were determined (standard or iterative approach) and used for calculation of time-integrated activity coefficients (TIACs) for the tumor, kidneys, liver, spleen, serum, and whole body. TIACs obtained using the full data sets were used as reference. To evaluate the effect of sampling on individual treatment planning, reduced sampling schedules were generated omitting either 1, 2, 3, or 4 organ and serum measurements or all serum measurements for each patient. Relative deviations (RDs) between these and reference TIACs were calculated and used as criterion for treatment planning accuracy. An RD < 0.1 was considered acceptable.
When omitting serum measurements, TIAC accuracy remained acceptable (RD < 0.1) for the standard approach. The kidney TIACs could be estimated for both approaches with acceptable RDs using two time points (t = 4 h; 2 d); tumor RDs were <0.3. The iterative approach reduced the range of RD, but did not further reduce the number of needed measurement points (i.e., to achieve an RD <0.1). For both approaches RDs for liver, spleen and whole body were larger than 0.1. However, in the clinical setting these RDs are less relevant as liver and spleen are not organs at risk due to the low absorbed doses.
When using a priori information of a PBPK model structure combined with Bayesian information about PBPK model parameter distribution, the administered activity could be determined with acceptable accuracy using only two time points (4 h, 2 d) and thus allow a considerable reduction of needed data for individual dosimetry.
KeywordsPhysiologically based pharmacokinetic (PBPK) modeling Peptide receptor radionuclide therapy (PRRT) Optimal sampling schedule Neuroendocrine tumor (NET) Time-integrated activity coefficient (TIAC)
Peptide receptor radionuclide therapy (PRRT) is performed in the treatment of neuroendocrine tumors (NET), where somatostatin analogues (DOTATOC, DOTATATE) are radiolabeled with 177Lu, 90Y, or 111In for pre-therapeutic and therapeutic purposes [1–3]. Treatment planning is based on pre-therapeutic measurements using 111In-labeled analogues, especially when 90Y is used as a radiolabel for therapy . Several nuclear medicine centers determine the therapeutic absorbed dose based on the area under the pre-therapeutic time-activity curve [5–7]. These areas are normalized by the administered activity yielding time-integrated activity coefficients (TIACs; formerly: residence times ), which are directly proportional to the absorbed doses. Thus, for a precise evaluation of the therapeutic absorbed doses, a reliable and accurate estimation of these areas is essential. This is performed by applying a model, e.g., a sum of exponential functions or physiologically based pharmacokinetic (PBPK) models . Recent work  showed pre-therapeutic and therapeutic biodistributions may change depending on the injected amount of peptide as well as the used peptide. In using a PBPK model, these changes can be described and predicted. Additionally, a PBPK model allows implementation of a priori information, which increases the ratio of number of measurements and fit parameters. A value for that ratio of >3  is sufficient for accurate determination of parameter values and AUCs. On the contrary, using, e.g., five measurement points, this value is 2.5 or 1.25 if using 1 or 2 exponentials.
The model parameters influence the estimation of the area under the time-activity curves (AUCs). A reliable and accurate estimation of the fit parameters in turn is affected by the sampling schedule [10–13].
The reduction of the number of required measurement time points would reduce patient burden and radiation exposure to staff. Therefore, it is important to know the dependence of the sampling schedule on treatment planning accuracy.
One aspect of improving the prediction accuracy of a PBPK model is using a priori knowledge, for example, the information about the parameter distribution in the investigated patient population. This information can be introduced into a PBPK model as Bayes parameter values, i.e., an implementation of population mean values and their respective standard deviation. In treatment planning of leukemia patients using radiolabeled anti-CD66 antibodies, this improved model performance and allowed an accurate prediction of biodistribution of the therapeutic agent .
However, population information, e.g., in the form of Bayes parameters [15–18], has not yet been implemented into a PBPK model to optimize or simplify the sampling schedule, i.e., to reduce the number of measurements without scrutinizing estimation accuracy.
The aim of this work was to investigate the effect of sampling schedules with fewer measurement points on treatment planning accuracy for PRRT using 111In-labeled diethylenetriaminopentaacetic acid-octreotide (DTPAOC; Octreoscan™, Mallinckrodt plc, Chesterfield, UK) using a PBPK model and Bayes parameters. Two different algorithms were employed to determine the Bayes parameter values.
In total, data of 15 patients with proven neuroendocrine tumors (NETs) were included in the study. Radiolabeling was performed as described elsewhere . Planar whole-body scans using a double-head γ-camera (Siemens, Erlangen, Germany) were performed at 0.75, 4 h, 1, 2, and 3 or 5 d after the administration of 8.1 ± 0.5 μg radiolabeled DTPAOC (Octreoscan™, Mallinckrodt plc, Chesterfield, UK) with a mean 111In activity of 143 ± 17 MBq for prediction of the absorbed doses . The quality control of the product was performed as described in the instruction leaflet. In all cases, the radiochemical purity was above 98 %. Images were attenuation and scatter corrected as described in . Organ activity values were determined for accumulating organs using ULMDOS software , with scatter correction and an effective attenuation correction based on the first whole-body measurement in conjugate view mode. Blood samples were drawn at 5 min, 0.5, 1, 2, 4 h, and 1, 2, 3, or 5 d.
To describe the biodistribution of radiolabeled peptides, a recently developed PBPK model  was used. Physiological processes, e.g., absorption, distribution, internalization, and excretion (ADME) were implemented. Distribution of the injected peptide was modeled via blood flow circulating between the organs (tumor, kidneys, liver, and spleen). These organs show high somatostatin receptor subtype 2 (sst2) expression and/or unspecific uptake (mainly the kidneys). Free passage of the peptide between interstitial and vascular spaces was assumed for the tumor, liver, and spleen . Other organs were merged into one compartment (rest).
The intravenous injection of the radiolabeled compound into the patients was modeled as a bolus injection in the main blood compartment.
The PBPK model consists of two equal subsystems, which are connected by the competition of labeled and unlabeled peptide for the same receptors and physical decay of the label. Specific binding to somatostatin receptors subtype 2 and degradation of bound peptide was considered. The kidney model describes unspecific uptake as well as release of still intact peptide back into the serum .
Within the PBPK model, different types of parameters were used: Model parameters refer to all parameters used in the PBPK model, may they be fitted or fixed parameters. Fitting parameters are those of the model parameters whose values are estimated in the fitting process. They can be set as adjustable or Bayes parameters. Adjustable parameters may have an upper and lower bound but no further constraints, whereas Bayes parameters have a constraint in the form of a mean value and a standard deviation.
To evaluate the impact of a priori population information on optimizing the sampling schedule (i.e., to reduce the number of measurement points), two different algorithms were employed to determine population Bayes parameter values. For the first algorithm (standard approach), the software Simulation, Analysis, and Modeling (SAAM II; version 2.3, The Epsilon Group, Charlottesville, USA) was used . This software provides a framework for model development. Using the built-in Rosenbrock optimization algorithm, the model parameters were fitted to biokinetic data.
For the second algorithm (iterative approach), the software PopKinetics (version 2.2, The Epsilon Group, Charlottesville, USA) was used. For both approaches, the same optimizer was used and the main difference is how Bayes parameters were determined. A more detailed description of both algorithms is presented in the following subsections.
All organ activity measurements were used during the fitting process (simultaneous fitting of all data). However, the effects on TIAC estimation accuracy were only evaluated for the tumor and kidney as these are the target and dose-limiting organs of this therapy.
Either set of Bayes parameter values derived from the standard and iterative approach algorithms was implemented as starting values in the PBPK model to predict time-integrated activity coefficients for different sampling schedules.
Model parameters and start values of the fitting parameters
R K [nmol]
2.1 ± 0.8b
R L [nmol]
1.8 ± 0.7b
R S [nmol]
3.5 ± 3.1b
R R [nmol]
7.3 ± 2.5b
V T [l]
0.2 ± 0.3b
f T [ml/min/g]
0.2 ± 0.1b
0.25 ± 0.06b
f ex [%]
96 ± 1.0b
64.4 ± 15.1b
λ deg,T [10−4/min]
1.5 ± 0.6b
λ deg,K [10−4/min]
1.1 ± 0.1b
λ deg,L [10−4/min]
0.5 ± 0.1b
λ deg,S [10−4/min]
1.6 ± 0.1b
λ deg,R [10−4/min]
1.3 ± 0.1b
# of fitting parameters
First, model parameters were fitted to biokinetic data of each patient individually as described in the standard approach above. Second, population mean and standard deviation for all parameters were calculated. Subsequently, these values were introduced as Bayes parameter values for each individual patient, constraining the possible parameter values based on the mean and standard deviation. Iteratively, the algorithm fitted the model parameters anew and updated the values until the convergence criterion or the maximum number of iterations was reached . In contrast to the standard approach, this iterative approach includes only Bayes parameters.
The convergence criterion of the implemented algorithm was set to 10−4, relative and absolute error to 0.01 and 0.1, respectively. The maximum number of iterations was set to 200, and a data-based variance model was chosen. These estimated population parameters were then used as starting values (Table 1).
Overview of the investigated sampling schedules
Number of omitted time points
Number of combinationsa
Total no. of measurementsb
Ratio of no. of measurements to fit parameters
Organ + serum
Organ + serum
Organ + serum
Organ + serum
These artificially generated reduced sampling schedules (total 31/patient) were then implemented in the PBPK model, and the model parameters were fitted again to these data (using either standard or iterative Bayes parameter values as a priori knowledge, Table 1). For each case, AUCs for the tumor, kidneys, liver, spleen, serum, and whole body were calculated by integration of the fitted curves (over 14 d). The obtained AUC values were divided by the amount of radiolabeled substance administered to determine TIACs individually.
Validation and statistical analysis
An RD < 0.1 was considered as an acceptable deviation in treatment planning accuracy in any further analysis.
Coefficients of variation (CV; ratio of standard deviation over the corresponding value) were calculated for all investigated cases to investigate the accuracy of the estimated TIACs.
An overview of the workflow is presented in Fig. 1.
Additionally, the adjusted R 2 values were calculated for all cases and both approaches (i.e., standard and iterative).
Visual inspection showed good fits for all cases and both parameter sets. Accordingly, the adjusted R 2 value was larger than 0.9. The population means and standard deviations for the individual time-integrated activity coefficients ã ref using the standard parameter values were 2.5 ± 4.3, 1.2 ± 0.3, 1.5 ± 0.5, 1.9 ± 1.1, 14.6 ± 4.1, and 0.9 ± 0.1 h for the tumor, kidneys, liver, spleen, whole body, and serum, respectively.
CVs of the estimated TIACs were calculated for all cases and were precise (<25 %) or acceptable (<50 %), except for cases III and IV (Table 2) using the standard parameter set.
Mean relative deviations of the fitted and reference TIACs averaged over all patients and all organs. For cases I to IV, the combination of omitted measurement points that gave the best and worst results in terms of the lowest and largest relative deviation (above and below the dashed line) are presented
Omitted time point
Mean ± SD
Omitted time point
Mean ± SD
1 ± 5
0 ± 4
2 ± 6
−1 ± 6
0 ± 11
0 ± 6
0 ± 7
6 ± 39
1 ± 11
1st, 3rd, 5th
5 ± 17
1st, 3rd, 5th
0 ± 8
2nd, 3rd, 5th
22 ± 58
3rd, 4th, 5th
22 ± 86
1st, 2nd, 4th, 5th
6 ± 13
1st, 3rd, 4th, 5th
16 ± 55
0 ± 3
1 ± 5
Coefficients of variation (CV) of the estimated TIACs for the best cases (Table 3)
Omitted time point
Mean ± SD
Omitted time point
Mean ± SD
7 ± 5
7 ± 4
9 ± 8
5 ± 4
1st, 3rd, 5th
8 ± 9
1st, 3rd, 5th
6 ± 6
1st, 2nd, 4th, 5th
6 ± 3
7 ± 6
7 ± 5
The lowest RDs for the tumor and kidneys (averaged over all patients) are presented in Fig. 3. As expected, TIAC accuracy reduces considerably (i.e., larger RDs) when fewer measurement points were taken into account in combination with parameter values derived using the standard approach. However, the application of population-based parameters (iterative approach) helped to reduce the systematic offset and the range of the RD (min, max), especially for the tumor up to three-fold (Table 3). For both approaches, the RDs of the TIACs in the kidneys were similar for all cases.
Overall, the acceptance criterion for the standard approach was fulfilled when omitting the time point t = 2 h or when omitting the serum measurements (Table 3). Using the population-based parameter values, the criterion was not fulfilled for any case I–V.
For the kidneys, the criterion was fulfilled in any case when using either standard- or population-based parameter values (averaged over all patients), except for case IV (iterative approach). However, for the tumor, only case V (omitting all serum measurements) for the standard approach fulfilled the acceptance criterion.
The RDs for the liver, spleen, and the whole body did not fulfill the criterion. Moreover, they were not considered in any further analysis, as these organs are neither dose limiting nor express a considerable sst2 receptor density.
In general, the presented PBPK model could describe the investigated data adequately in all cases, i.e., visual inspection and the coefficients of variation for the TIACs were precise or acceptable (Table 4; ).
Including population information as a priori knowledge during the fitting process helped to considerably improve prediction accuracy and reduce the corresponding standard deviations when averaged over all organs and all patients (Table 3). When looking at the accuracy of TIAC estimation for tumor (averaged over all patients) for each case (Fig. 3), the application of population information reduced the range of accuracy as well; for the kidneys, the accuracy seems minorly affected indicating that the information about the population implemented in the model was sufficient to compensate for a reduced data set.
The differences in TIAC estimation for the liver, spleen, and the whole body were not further considered, as these organs are neither dose limiting nor express a considerable sst2 receptor density .
Omitting the serum measurements had a minor effect on the accuracy for both the tumor and kidneys for the standard investigation. Therefore, these measurement points may be omitted in future treatment planning, when the same (or at least a sufficiently similar) sampling schedule is considered. Note, however, that these data may nevertheless be needed for proper calculation of red bone marrow absorbed dose.
Based on the provided sampling schedule, the estimated TIACs were set as reference. However, this sampling schedule may be inherently suboptimal. If fewer measurement points are considered, the influence of each single remaining data point will become more prominent. Clearly, the number of fitting parameters limits the number of required measurements to achieve a sufficiently precise estimation of TIACs and hence absorbed doses. When looking at the estimated standard deviations of the fitting parameters (for both approaches, standard, and iterative), these increase with decreasing number of measurements (results not shown). This in turn was reflected in the estimation of the TIACs. Therefore, conducting a precise estimation of TIACs is limited if too many time points (measurements) are omitted. To overcome this problem, simulations could be performed to determine when (in contrast to how often) the biodistribution should be measured. This may reduce the standard deviations of the fitting parameters and may yield a globally optimal sampling schedule.
A possible limitation of the presented study was the number of investigated patients (N = 15). To evaluate that the patient population is of sufficient size, e.g., to determine reliable parameter values, the Jackknife resampling method may be applied . This method investigates the impact of a single patient with respect to the full population and to the outcome of the fitting procedure (i.e., parameter values and thus TIACs values).
Further reduction in the size of the measurement data may be achieved by improving the quality of the data, i.e., when using PET imaging or by implementing more a priori knowledge about the population and the investigated disease. Further research could also be aimed at designing more individualized optimal sampling schedules. Subgroups of patients may be based on differences in pharmacokinetic properties (e.g., kidney clearance) or general biodistribution. For these groups, an optimal sampling schedule may be determined by possibly reducing the location and/or number of measurement points even further. However, this approach needs the assumption that patients can be categorized into sufficient different subgroups. This information would also be required a priori to any modeling to ensure that the correct sampling schedule is assigned for a certain patient group.
The sampling schedule considerably affects estimation accuracy of time-integrated activity coefficients and thus treatment planning for NET patients in PRRT with 111In-DTPAOC.
In this patient group, the combination of individual and population information in the PBPK model showed the least effect on the estimation accuracy when the second time point (t = 2 h) or all serum measurements were omitted. Thus, in the future treatment planning, these data points may be omitted, if the absorbed dose to the red bone marrow is not of interest. The absorbed dose in the kidneys may be determined with acceptable accuracy using only two time points (4 h and 2 d).
The application of a priori knowledge using the iterated approach and physiologically based pharmacokinetic modeling allowed reduction of the standard deviation of the accuracy, but did not help to further reduce the number of measurement points.
All procedures performed in studies involving human participants were in accordance with the ethical standards of the institutional and/or national research committee and with the 1964 Helsinki declaration and its later amendments or comparable ethical standards. Informed consent was obtained from all individual participants included in the study.
The authors gratefully acknowledge grants by the Bundesministerium für Bildung und Forschung (Federal Ministry of Education and Research (BMBF)) and Bundesamt für Strahlenschutz (Federal Office for Radiation Protection (BfS) 3608S04001) for the establishment of the endowed professorship Medizinische Strahlenphysik/Strahlenschutz (Medical Radiation Physics/Radiation Protection). We would also like to gratefully thank the German Research Foundation (DFG) for the support (BE 4393/1-1, GL 236/11-1, and KL 2742/2-1), the MITIGATE project, which received funding from the European Union’s Seventh Framework Programme for research, technological development and demonstration under grant agreement no. 602306 and “Direktorat Jenderal Pendidikan Tinggi” (Directorate General of Higher Education (DIKTI) of Ministry for Research, Technology and Higher Education, Republic Indonesia Grant Number: 2644/E4.4/K/2013).
The authors also acknowledge the financial support of the Deutsche Forschungsgemeinschaft and Ruprechts-Karls-Universität Heidelberg within the funding programme Open Access Publishing.
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.
- Bomanji JB, Papathanasiou ND. 111In-DTPA(0)-octreotide (Octreoscan), 131I-MIBG and other agents for radionuclide therapy of NETs. Eur J Nucl Med Mol Imaging. 2012;39 Suppl 1:S113–25. doi:10.1007/s00259-011-2013-8.View ArticlePubMedGoogle Scholar
- Chalkia MT, Stefanoyiannis AP, Prentakis A, Chatziioannou SN, Liotsou T, Geronikola-Trapali X, et al. Design and clinical implementation of a 99mTc-HYNICTOC-based dosimetric protocol in PRRT of NETs with 90Y-DOTATOC. Phys Med. 2014;30:e81. doi:10.1016/j.ejmp.2014.07.234.View ArticleGoogle Scholar
- Hardiansyah D, Maass C, Attarwala AA, Müller B, Kletting P, Mottaghy FM, et al. The role of patient-based treatment planning in peptide receptor radionuclide therapy. Eur J Nucl Med Mol Imaging. 2015. doi:10.1007/s00259-015-3248-6.PubMedGoogle Scholar
- Glatting G, Bardies M, Lassmann M. Treatment planning in molecular radiotherapy. Z Med Phys. 2013;23(4):262–9. doi:10.1016/j.zemedi.2013.03.005.View ArticlePubMedGoogle Scholar
- Strigari L, Konijnenberg M, Chiesa C, Bardies M, Du Y, Gleisner KS, et al. The evidence base for the use of internal dosimetry in the clinical practice of molecular radiotherapy. Eur J Nucl Med Mol Imaging. 2014;41(10):1976–88. doi:10.1007/s00259-014-2824-5.View ArticlePubMedGoogle Scholar
- Brolin G, Gustafsson J, Ljungberg M, Gleisner KS. Pharmacokinetic digital phantoms for accuracy assessment of image-based dosimetry in 177Lu-DOTATATE peptide receptor radionuclide therapy. Phys Med Biol. 2015;60(15):6131–49. doi:10.1088/0031-9155/60/15/6131.View ArticlePubMedGoogle Scholar
- Minguez P, Flux G, Genolla J, Guayambuco S, Delgado A, Fombellida JC et al. Dosimetric results in treatments of neuroblastoma and neuroendocrine tumors with 131I-metaiodobenzylguanidine with implications for the activity to administer. Med Phys. 2015;42(7):3969-78. doi:10.1118/1.4921807.
- Kletting P, Kull T, Maaß C, Malik N, Luster M, Beer A, et al. Optimized peptide amount and activity for Y-90-labeled DOTATATE therapy. J Nucl Med. 2015. doi:10.2967/jnumed.115.164699.PubMedGoogle Scholar
- Kletting P, Müller B, Erentok B, Schmaljohann J, Behrendt FF, Reske SN, et al. Differences in predicted and actually absorbed doses in peptide receptor radionuclide therapy. Med Phys. 2012;39(9):5708–17. doi:10.1118/1.4747266.View ArticlePubMedGoogle Scholar
- D’Argenio DZ. Optimal sampling times for pharmacokinetic experiments. J Pharmacokinet Biopharm. 1981;9(6):739–56.View ArticlePubMedGoogle Scholar
- Ogungbenro K, Aarons L. Optimisation of sampling windows design for population pharmacokinetic experiments. J Pharmacokinet Pharmacodyn. 2008;35(4):465–82. doi:10.1007/s10928-008-9097-1.View ArticlePubMedGoogle Scholar
- Tam VH, Preston SL, Drusano GL. Optimal sampling schedule design for populations of patients. Antimicrob Agents Chemother. 2003;47(9):2888–91. doi:10.1128/aac.47.9.2888-2891.2003.View ArticlePubMedPubMed CentralGoogle Scholar
- Siegel JA, Thomas SR, Stubbs JB, Stabin MG, Hays MT, Koral KF, et al. MIRD pamphlet no. 16: techniques for quantitative radiopharmaceutical biodistribution data acquisition and analysis for use in human radiation dose estimates. J Nucl Med. 1999;40(2):37S–61S.Google Scholar
- Maaß C, Kletting P, Beer A, Glatting G. Population based modeling improves treatment planning for leukemia patients. Cancer Biother Radiopharm. 2015;30(7):285–90. doi:10.1089/cbr.2015.1878.View ArticlePubMedGoogle Scholar
- Lainez JM, Orcun S, Pekny JF, Reklaitis GV, Suvannasankha A, Fausel C, et al. Comparison of an assumption-free Bayesian approach with optimal sampling schedule to a maximum a posteriori approach for personalizing cyclophosphamide dosing. Pharmacotherapy. 2014;34(4):330–5. doi:10.1002/phar.1346.View ArticlePubMedGoogle Scholar
- Magni P, Sparacino G, Bellazzi R, Cobelli C. Reduced sampling schedule for the glucose minimal model: importance of Bayesian estimation. Am J Physiol Endocrinol Metab. 2006;290(1):E177–E84. doi:10.1152/ajpendo.00241.2003.View ArticlePubMedGoogle Scholar
- Youdarene R, Woillard JB, Prémaud A, Rousseau A, Debord J, Neely M, et al. Population pharmacokinetics and Bayesian estimation of mycophenolic acid exposure in heart transplant recipients: comparison of two approaches. J Heart Lung Transplant. 2013;32(4):S111. doi:10.1016/j.healun.2013.01.230.View ArticleGoogle Scholar
- Ogungbenro K, Dokoumetzidis A, Aarons L. Application of optimal design methodologies in clinical pharmacology experiments. Pharm Stat. 2009;8(3):239–52.View ArticlePubMedGoogle Scholar
- Glatting G, Landmann M, Kull T, Wunderlich A, Blumstein NM, Buck AK, et al. Internal radionuclide therapy: the ULMDOS software for treatment planning. Med Phys. 2005;32(7):2399. doi:10.1118/1.1945348.View ArticlePubMedGoogle Scholar
- Rippe B, Haraldsson B. Transport of macromolecules across microvascular walls: the two-pore theory. Physiol Rev. 1994;74(1):163–219.PubMedGoogle Scholar
- Barrett PH, Bell BM, Cobelli C, Golde H, Schumitzky A, Vicini P, et al. SAAM II: Simulation, Analysis, and Modeling software for tracer and pharmacokinetic studies. Metabolism. 1998;47(4):484–92.View ArticlePubMedGoogle Scholar
- Kletting P, Schimmel S, Hänscheid H, Luster M, Fernández M, Nosske D, et al. The NUKDOS software for treatment planning in molecular radiotherapy. Z Med Phys. 2015;25(3):264–74. doi:10.1016/j.zemedi.2015.01.001.View ArticlePubMedGoogle Scholar
- Kletting P, Maass C, Reske S, Beer AJ, Glatting G. Physiologically based pharmacokinetic modeling is essential in 90Y-labeled anti-CD66 radioimmunotherapy. PLoS One. 2015;10(5):e0127934. doi:10.1371/journal.pone.0127934.View ArticlePubMedPubMed CentralGoogle Scholar
- Cremonesi M, Ferrari M, Bodei L, Tosi G, Paganelli G. Dosimetry in peptide radionuclide receptor therapy: a review. J Nucl Med. 2006;47(9):1467–75.PubMedGoogle Scholar