Pre-clinical quantitative imaging and mouse-specific dosimetry for 111In-labelled radiotracers
© The Author(s). 2016
Received: 24 August 2016
Accepted: 14 November 2016
Published: 25 November 2016
Accurate quantification in molecular imaging is essential to improve the assessment of novel drugs and compare the radiobiological effects of therapeutic agents prior to in-human studies. The aim of this study was to investigate the challenges and feasibility of pre-clinical quantitative imaging and mouse-specific dosimetry of 111In-labelled radiotracers.
Attenuation, scatter and partial volume effects were studied using phantom experiments, and an activity calibration curve was obtained for varying sphere sizes. Six SK-OV-3-tumour bearing mice were injected with 111In-labelled HER2-targeting monoclonal antibodies (mAbs) (range 5.58–8.52 MBq). Sequential SPECT imaging up to 197 h post-injection was performed using the Albira SPECT/PET/CT pre-clinical scanner. Mice were culled for quantitative analysis of biodistribution studies. The tumour activity, mass and percentage of injected activity per gram of tissue (%IA/g) were calculated at the final scan time point and compared to the values determined from the biodistribution data. Delivered 111In-labelled mAbs tumour absorbed doses were calculated using mouse-specific convolution dosimetry, and absorbed doses for 90Y-labelled mAbs were extrapolated under the assumptions of equivalent injected activities, biological half-lives and uptake distributions as for 111In.
For the sphere sizes investigated (volume 0.03–1.17 ml), the calibration factor varied by a factor of 3.7, whilst for the range of tumour masses in the mice (41–232 mg), the calibration factor changed by a factor of 2.5. Comparisons between the mice imaging and the biodistribution results showed a statistically significant correlation for the tumour activity (r = 0.999, P < 0.0001) and the tumour mass calculations (r = 0.977, P = 0.0008), whilst no correlation was found for the %IA/g (r = 0.521, P = 0.29). Median tumour-absorbed doses per injected activity of 52 cGy/MBq (range 36–69 cGy/MBq) and 649 cGy/MBq (range 441–950 cGy/MBq) were delivered by 111In-labelled mAbs and extrapolated for 90Y-labelled mAbs, respectively.
This study demonstrates the need for multidisciplinary efforts to standardise imaging and dosimetry protocols in pre-clinical imaging. Accurate image quantification can improve the calculation of the activity, %IA/g and absorbed dose. Diagnostic imaging could be used to estimate the injected activities required for therapeutic studies, potentially reducing the number of animals used.
Keywords111In Pre-clinical Image quantification Partial volume effect Dosimetry Radiolabelled antibodies SPECT HER2
Molecular imaging enables minimally-invasive visualisation of molecular and cellular biological processes in living organisms. It plays an important role in cancer drug development and in monitoring disease progression and tumour response to therapeutic interventions [1–3]. Animal models are both cost effective and versatile and therefore have been essential in cancer research. Ex vivo biodistribution and/or autoradiography studies are traditionally used to investigate the uptake characteristics of novel radiolabelled tracers prior to translation to in-human clinical trials. However, these methods are limited, as they require animals to be culled at various time points and the pharmacokinetics are based on data from different animals at different times. Conversely, SPECT and PET pre-clinical imaging enables the prospect of longitudinal studies and therefore has the potential to provide quantitative measurements of radiotracer biodistribution and to reduce the number of animals required per study, which is both more cost effective and more ethical than traditional methods .
Absolute image quantification is essential to evaluate imaging biomarkers and to accurately determine the distribution of the uptake of novel radiotracers to evaluate their toxicity and efficacy profile in small animals prior to use in human studies. It is also necessary for dosimetry calculations and therefore has the potential to improve our understanding of the biological mechanisms of radiation-induced cell damage [5, 6] and to better inform the comparison of therapeutic radiotracers. The accuracy of pre-clinical molecular imaging can be degraded by several factors including attenuation, scatter, partial volume, motion and animal handling . The effects of attenuation and scatter are of less importance than in clinical imaging due to the smaller size of the subjects involved. However, multiple studies have shown that the effects can be significant for radionuclides emitting low-energy gamma rays and larger-sized rodents [8–13]. The spatial resolution of the imaging system also affects quantification due to the partial volume effect, particularly in the case of small animals. The majority of studies to investigate partial volume effects in pre-clinical imaging have focused on PET [14–16]. Few correction methods are available  and commercial imaging systems do not provide correction and/or compensation methods for partial volume effects.
The aim of this study was to explore the challenges and potential role of quantitative pre-clinical SPECT imaging as an alternative for biodistribution studies. Methods used in the clinical setting were applied to a pre-clinical study to investigate image quantification and mouse-specific dosimetry of 111In-labelled monoclonal antibodies (mAbs) targeting HER2-positive tumours. In particular, the influence of tumour size on quantification accuracy was investigated.
Immunoconjugate preparation and radiolabelling
The HER2-targeting mAbs used in this study were the commercially available trastuzumab (Herceptin®, Roche) and ICR12, developed at The Institute of Cancer Research, London [18, 19]. The bifunctional chelator 2-(4-isothiocyanatobenzyl)-diethylenetriaminepentaacetic acid (pSCN-Bn-DTPA, Macrocyclics, US) was conjugated to ICR12 and trastuzumab. Additionally, 2-(4-isothiocyanatobenzyl)-1, 4, 7, 10-tetraazacyclododecane-1, 4, 7, 10-tetraacetic acid (p-SCN-Bn-DOTA, Macrocyclics, US) was conjugated to trastuzumab. The immunoconjugates (50–80 μg) were radiolabelled with 111In (ca 42 MBq) (Perking Elmer, US) in acetate buffer (pH = 4). All reactions were performed as described previously [20, 21]. The use of different radioimmunoconjugates does not affect the results of this study, as the primary aims were to investigate the feasibility and challenges of image quantification and dosimetry in pre-clinical studies, rather than to compare the radiotracers.
Tumour cell line and animals
Radioimmonucongugate, level of activity (Ainj) and quantity of antibody (mAbinj) injected for the six mice included in the study
Mice were anesthetised by inhalation of a 2% isoflurane/O2 mixture (Virbac, UK) and placed on the scanner bed. A 1% isoflurane gas mixture was maintained during acquisition. The imaging study was performed using the Albira SPECT/PET/CT tri-modal pre-clinical scanner (Bruker), which allows fully registered anatomical and functional imaging [22, 23]. The CT component is co-planar with the SPECT crystals and has transverse and axial fields of view (FOV) of 65 mm. The SPECT sub-system comprises two opposing heads, each with a single 100 × 100 × 4 mm2 CsI(Na) crystal and a position sensitive photomultiplier tube. All acquisitions were performed with a single-pinhole collimator and transverse and axial FOVs of 80 mm and 60 mm, respectively. An energy window width of 20% was placed on the lower gamma-ray emission of 111In at 171 keV. The scans were reconstructed using default parameters, the ordered subsets expectation maximization (OSEM) method with two iterations and five subsets into a 110 × 110 matrix with voxel size of 0.75 mm. The images were not corrected for attenuation, scatter or partial volume effects, as these are not provided by the manufacturer. The six mice were imaged at 4, 24, 48, 72 and 96 h post-injection (pi), and two mice were additionally imaged at 168 and 197 h post-injection. A CT (45 kV, 0.2 mA, 80 mSv) and a 15 min SPECT acquisition were performed at each time point.
In-built attenuation and scatter corrections are not available in the Albira system. Therefore, a simple phantom experiment was used to investigate their combined effect. A 2.3 mm-radius sphere was filled with 32.6 MBq of 111In (0.1 HCl) and attached to a 30.4 ml cylindrical phantom (diameter 25 mm, length 92 mm) to simulate a subcutaneous tumour in the flank of a mouse. The phantom was placed on a moveable platform adjustable to sub-millimetre precision and scanned in ten positions: five axial positions in the centre and five positions 8 mm off-centre from the FOV trans-axially. The experiment was performed with the cylindrical phantom filled with air and water. The mean counts in the sphere were compared for both cases to assess the effects of attenuation and scatter within the mice.
To quantify the level of activity in the in vivo SPECT scans, phantom studies were performed to convert from measured counts to units of activity (MBq). Three spherical phantoms with volumes of 0.03, 0.12 and 1.17 ml were filled with activity concentrations in the range of 7.7–10.2 MBq/ml of 111In (0.1 M HCl) to investigate partial volume effects and to calibrate the SPECT images. Each sphere was attached to a 30.4 ml cylindrical phantom (diameter 25 mm, length 92 mm) filled with 0.1 M HCl solution to provide a realistic scatter and attenuation medium.
Each phantom was scanned using a 15-min acquisition and reconstructed with the same parameters as for the in vivo study.
Image-based convolution dosimetry was performed using in-house software , developed in C# and C++, using the .Net framework and the open source library Visualization Toolkit VTK (http://www.vtk.org) . Three-dimensional absorbed dose distributions were obtained from the convolution of a voxelised-cumulated activity distribution and a voxel S-value kernel. The SPECT scans were co-registered using a rigid mutual information algorithm, and these were used to obtain the time-activity curves and to calculate the cumulated activity at the voxel level. A trapezoidal or exponential extrapolation method was used for the intermediate phases, depending on whether the activity between the two time points increased or decreased respectively. For the uptake phase, it was assumed that the activity at the time of administration was zero and linearly increased to the first scan time. For the last phase, exponential decay with physical half-life was assumed from the last scan point to infinity to avoid any bias introduced by registration errors and redistribution of uptake at the voxel level. Voxel- S value kernels were generated with an application developed using the EGS++ class library within the general purpose EGSnrc Monte Carlo (MC) code [26, 27], previously validated by comparison with available resources . Kernels for 111In and 90Y with 0.75 mm voxels in a soft-tissue homogeneous medium were generated. Simulations were carried out without variance reduction techniques and with 107 histories to maintain the statistical uncertainty below 1% at central and nearest neighbouring voxels. The decay spectra used for the simulations were obtained from the RADTABS software .
Due to insufficient contrast between the tumour and the surrounding muscle tissue on the CT images, tumours were outlined in the SPECT images using a thresholding method using the PMOD software (PMOD Technologies). The threshold was varied until the tumour edge in the SPECT scan matched the visible tumour edge in the CT image. The thresholded final SPECT images were used to calculate the tumour masses assuming a density of 1 g/cm3 and the tumour activity using the calibration curve obtained from the phantom experiment. The tumour uptake, determined as the percentage injected activity per gram of tissue (%IA/g), was then calculated from the activity and mass of the tumour at the final scan time point. The tumour absorbed doses delivered by 111In-labelled mAbs and those that would have been delivered by 90Y-labelled mAbs were extrapolated to demonstrate the feasibility of pre-therapy-image-based treatment planning for therapeutic studies. The assumptions of equivalent injected activities, biological half-lives and uptake distributions for 90Y-labelled mAbs as for the 111In-labelled mAbs were made.
The mice were euthanized by cervical dislocation immediately following the final scan: 96 h for four mice and 197 h for the remaining two mice. The tumours were dissected and weighed, and the radioactivity was measured in a WIZARD2 automatic gamma counter (PerkinElmer, UK). Tumour uptake (%IA/g), activity and mass were calculated. Comparisons between the three radiotracers were beyond the scope of this study.
Comparison between imaging and biodistribution
The activity, mass and %IA/g in the tumour calculated from the last SPECT scan were compared with those obtained from the biodistribution study, which is considered to be the gold standard measurement.
Median and range were used to describe continuous variables. Pearson’s correlation coefficients and regression analysis were used to quantify and identify relations between variables. Two-sided P values below 0.05 were considered significant.
Immunoconjugate preparation and radiolabelling
For the attenuation/scatter phantom experiment, the mean counts in the sphere were on average 3% lower in the presence of the water-filled cylinder than with the air-filled cylinder.
Mass, activity and uptake in the tumour determined from the biodistribution (bio) and imaging (im) studies and their relative percentage differences (diff), and delivered (111In) and extrapolated (90Y) tumour absorbed doses per injected activity (D/A) for the six mice included in the study
A median tumour mass of 83 mg (range 41–232 mg) was obtained from the biodistribution data, with a median activity of 0.093 MBq (range 0.015–0.335 MBq) and a median %IA/g of 48% (range 33–66%).
Comparison between imaging and biodistribution
This study investigated the challenges associated with pre-clinical imaging and mouse-specific dosimetry and compared the mass, activity and %IA/g in the tumour obtained from the imaging and the ex vivo biodistribution data. A statistically significant correlation was observed between the tumour activity and mass as calculated from the biodistribution and imaging data at 96 and 197 h following injection of 111In-labelled mAbs targeting HER2-positive tumours. However, a correlation was not found between uptake as calculated from the imaging and the biodistribution data. Finucane et al assessed the quantification accuracy of 111In pre-clinical imaging and concluded that imaging could replace some dissection studies for the assessment of radiotracer biodistribution in mouse models . Their conclusions were based on a comparison of the tumour activity calculated from the SPECT scan and the percentage of injected activity (%IA) determined from the biodistribution data and therefore did not include the influence of the mass into the %IA/g calculation. The discrepancies in the uptake calculations observed in our study are not fully understood, and more studies are needed to assess the reproducibility of measurements and to elucidate the interplay of the different variables in the calculation of uptake prior to the complete replacement of ex vivo biodistribution studies.
Accurate calculation of subcutaneous xenograft tumour volume is a key element of pre-clinical studies, as it is used as a metric to assess tumour growth and to quantify response to therapy, as well as for image quantification and dosimetry. Our results showed that for the range of tumours observed in this mouse cohort, the calibration factor to convert from counts to activity changed by a factor of 2.5, which can potentially lead to significant errors in the quantification of tumour activity, uptake and absorbed dose. These differences are likely due to partial volume effects, as the median tumour diameter observed in this study was 5.4 mm (range 4.3–7.6 mm), and the measured average axial spatial resolution for 111In was 2.1 (±0.4) mm. The investigation of the combined effects of attenuation and scatter showed only a 3% error on image quantification, which is small compared with the limitations of the spatial resolution and partial volume effects. Attenuation and scatter will play an important role for larger size rodents and low energy emitting radionuclides. For example, Hwang et al found that the measured concentration of activity in a volume of interest in the centre of a rat-sized water-filled cylinder was reduced by up to 50% for 125I and up to 25% for 99mTc . Our study was limited in that it only assessed the impact of attenuation/scatter, partial volume and limited spatial resolution. However, image quantification will also be affected by other factors. Optimisation of the number of iterations used for image reconstruction could lead to improved spatial resolution and thus reduce partial volume effects. Motion and image co-registration can also result in significant image blurring. It is therefore essential to standardise and harmonise the imaging protocols in pre-clinical imaging to decrease the variability in the calculation of tumour activity, %IA and absorbed dose, which are key parameters in the evaluation of novel radiotracers.
Tumour and organ masses can also have a significant impact on tabulated S values for organ and tumour-absorbed dose calculations. Several authors have studied the impact of various voxel-based mouse dosimetric reference models and found large variations in S-values due to the variability of the anatomical features [34–37]. Our study was based on convolution dosimetry, which accounts for heterogeneity in the uptake distribution at the voxel level. Tumour absorbed doses were calculated from outlining the absorbed dose distributions, neglecting tumour size changes that could occur following the administration of the radiotracer. Future studies could include magnetic resonance and/or ultrasound imaging to improve the accuracy and precision of tumour volume assessment [38, 39], which in turn will improve mass, activity, uptake and absorbed dose calculations.
The dosimetry methodology used in this study showed the feasibility of treatment planning in pre-clinical studies, where absorbed doses can be extrapolated for any radionuclide from a given uptake distribution. This could ease experimental planning for therapeutic radiotracers by informing the level of injected activity required to deliver a given absorbed dose, in particular for theragnostic agents, with the potential to reduce the number of animals used.
This study demonstrates the need for multidisciplinary efforts to standardise imaging and dosimetry protocols in pre-clinical imaging before replacing ex vivo biodistribution studies. Accurate image quantification can have a large impact on improving the calculation of mass, activity, uptake and absorbed doses and therefore has the potential to improve treatment response studies and the comparison of novel radiotracers.
The authors would like to acknowledge Kicki Frisch for her support on the development of the dosimetry software.
This work was supported by Cancer Research UK and Engineering and Physical Sciences Research Council support to the Cancer Imaging Centre at The Institute of Cancer Research (ICR) and the Royal Marsden Hospital NHS Foundation Trust (RMH) in association with Medical Research Council and Department of Health C1060/A10334, C1060/A16464.
The study was conceived and designed by AMDB, SEC, GDF and TS. CDP and RP were responsible for radiolabelling with the participation of AH and JKS. CB and GKM assisted with the cell and animal work, and SAE procured the ICR12 antibody. SEC and TS collected the imaging data. AMDB drafted the manuscript. AMDB and SEC analysed the data. All authors proposed valuable comments, revise the manuscript critically for important intellectual content and approved the final manuscript.
The authors declare that they have no competing interests.
Consent for publication
All experiments were performed in compliance with licences issued under the UK Animals (Scientific Procedures) Act 1986 and following local ethical review and the United Kingdom National Cancer Research Institute Guidelines for Animal Welfare in Cancer Research.
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.
- Weissleder R. Molecular imaging in cancer. Science. 2006;312(5777):1168–71. doi:10.1126/science.1125949.View ArticlePubMedGoogle Scholar
- Willmann JK, van Bruggen N, Dinkelborg LM, Gambhir SS. Molecular imaging in drug development. Nat Rev Drug Discov. 2008;7(7):591–607. doi:10.1038/nrd2290.View ArticlePubMedGoogle Scholar
- Kircher MF, Hricak H, Larson SM. Molecular imaging for personalized cancer care. Mol Oncol. 2012;6(2):182–95. doi:10.1016/j.molonc.2012.02.005.View ArticlePubMedGoogle Scholar
- Workman P, Aboagye EO, Balkwill F, Balmain A, Bruder G, Chaplin DJ, et al. Guidelines for the welfare and use of animals in cancer research. Br J Cancer. 2010;102(11):1555–77. doi:10.1038/sj.bjc.6605642.View ArticlePubMedPubMed CentralGoogle Scholar
- Bentzen SM. Preventing or reducing late side effects of radiation therapy: radiobiology meets molecular pathology. Nat Rev Cancer. 2006;6(9):702–13. doi:10.1038/nrc1950.View ArticlePubMedGoogle Scholar
- Pouget JP, Lozza C, Deshayes E, Boudousq V, Navarro-Teulon I. Introduction to radiobiology of targeted radionuclide therapy. Front Med (Lausanne). 2015;2(12):12. doi:10.3389/fmed.2015.00012.Google Scholar
- Vanhove C, Bankstahl JP, Krämer SD, Visser E, Belcari N, Vandenberghe S. Accurate molecular imaging of small animals taking into account animal models, handling, anaesthesia, quality control and imaging system performance. EJNMMI Physics. 2015;2(1):1–25. doi:10.1186/s40658-015-0135-y.View ArticleGoogle Scholar
- Seo Y, Wong KH, Hasegawa BH. Calculation and validation of the use of effective attenuation coefficient for attenuation correction in In-111 SPECT. Med Phys. 2005;32(12):3628–35. doi:10.1118/1.2128084.View ArticlePubMedGoogle Scholar
- Hwang AB, Franc BL, Gullberg GT, Hasegawa BH. Assessment of the sources of error affecting the quantitative accuracy of SPECT imaging in small animals. Phys Med Biol. 2008;53(9):2233–52. doi:10.1088/0031-9155/53/9/002.View ArticlePubMedPubMed CentralGoogle Scholar
- Chen CL, Wang Y, Lee JJ, Tsui BM. Toward quantitative small animal pinhole SPECT: assessment of quantitation accuracy prior to image compensations. Mol Imaging Biol. 2009;11(3):195–203. doi:10.1007/s11307-008-0181-0.View ArticlePubMedGoogle Scholar
- Wu C, De Jong JR, Gratama van Andel HA, van der Have F, Vastenhouw B, Laverman P, et al. Quantitative multi-pinhole small-animal SPECT: uniform versus non-uniform Chang attenuation correction. Phys Med Biol. 2011;56(18):N183–93. doi:10.1088/0031-9155/56/18/N01.View ArticlePubMedGoogle Scholar
- Hutton BF, Buvat I, Beekman FJ. Review and current status of SPECT scatter correction. Phys Med Biol. 2011;56(14):R85–112. doi:10.1088/0031-9155/56/14/R01.View ArticlePubMedGoogle Scholar
- Konik A, Madsen MT, Sunderland JJ. GATE simulations of small animal SPECT for determination of scatter fraction as a function of object size. Nucl Sci, IEEE Transactions on. 2012;59(5):1887–91. doi:10.1109/TNS.2012.2205403.View ArticleGoogle Scholar
- Chen CH, Muzic Jr RF, Nelson AD, Adler LP. Simultaneous recovery of size and radioactivity concentration of small spheroids with PET data. J Nucl Med. 1999;40(1):118–30.PubMedGoogle Scholar
- Hoffman EJ, Huang SC, Phelps ME. Quantitation in positron emission computed tomography: 1. Effect of object size. J Comput Assist Tomogr. 1979;3(3):299–308.View ArticlePubMedGoogle Scholar
- Mannheim JG, Judenhofer MS, Schmid A, Tillmanns J, Stiller D, Sossi V, et al. Quantification accuracy and partial volume effect in dependence of the attenuation correction of a state-of-the-art small animal PET scanner. Phys Med Biol. 2012;57(12):3981–93. doi:10.1088/0031-9155/57/12/3981.View ArticlePubMedGoogle Scholar
- Srinivas SM, Dhurairaj T, Basu S, Bural G, Surti S, Alavi A. A recovery coefficient method for partial volume correction of PET images. Ann Nucl Med. 2009;23(4):341–8. doi:10.1007/s12149-009-0241-9.View ArticlePubMedGoogle Scholar
- Styles JM, Harrison S, Gusterson BA, Dean CJ. Rat monoclonal antibodies to the external domain of the product of the C-erbB-2 proto-oncogene. Int J Cancer. 1990;45(2):320–4. doi:10.1002/ijc.2910450219.View ArticlePubMedGoogle Scholar
- Dean CJ, Eccles SA, Valeri M, Box G, Allan S, McFarlane C, et al. Rat MAbs to the product of the c-erbB-2 proto-oncogene for diagnosis and therapy in breast cancer. Cell Biophys. 1993;22(1-3):111–27.View ArticlePubMedGoogle Scholar
- Sosabowski JK, Mather SJ. Conjugation of DOTA-like chelating agents to peptides and radiolabeling with trivalent metallic isotopes. Nat Protoc. 2006;1(2):972–6. doi:10.1038/nprot.2006.175.View ArticlePubMedGoogle Scholar
- Cooper MS, Sabbah E, Mather SJ. Conjugation of chelating agents to proteins and radiolabeling with trivalent metallic isotopes. Nat Protoc. 2006;1(1):314–7. doi:10.1038/nprot.2006.49.View ArticlePubMedGoogle Scholar
- Sanchez F, Orero A, Soriano A, Correcher C, Conde P, Gonzalez A, et al. ALBIRA: a small animal PETSPECTCT imaging system. Med Phys. 2013;40(5):051906. doi:10.1118/1.4800798.View ArticlePubMedGoogle Scholar
- Spinks TJ, Karia D, Leach MO, Flux G. Quantitative PET and SPECT performance characteristics of the Albira Trimodal pre-clinical tomograph. Phys Med Biol. 2014;59(3):715–31. doi:10.1088/0031-9155/59/3/715.View ArticlePubMedGoogle Scholar
- Frisch KJ, Denis-Bacelar AM, Falzone N, Gear J, Flux G. qDose - a software application for 3D dosimetry in radionuclide therapy. Eur J Nucl Med Mol Imaging. 2014;41(2):S221–705. doi:10.1007/s00259-014-2901-9.Google Scholar
- Schroeder W, Martin K, Lorensen B. The Visualization Toolkit: An Object-Oriented Approach to 3D Graphics 4th Edition. Kitware; 2006. ISBN-13:978-1930934191.Google Scholar
- Kawrakow I. Accurate condensed history Monte Carlo simulation of electron transport. I. EGSnrc, the new EGS4 version. Med Phys. 2000;27(3):485–98. doi:10.1118/1.598917.View ArticlePubMedGoogle Scholar
- Kawrakow I, Mainegra-Hing E, Tessier F, Walters BRB. The EGSnrc C++ class library. Ottawa: NRC Report PIRS-898 (rev A); 2009.Google Scholar
- Denis-Bacelar AM, Romanchikova M, Chittenden S, Saran FH, Mandeville H, Du Y, et al. Patient-specific dosimetry for intracavitary 32P-chromic phosphate colloid therapy of cystic brain tumours. Eur J Nucl Med Mol Imaging. 2013;40(10):1532–41. doi:10.1007/s00259-013-2451-6.
- Eckerman KF, Endo A. MIRD: radionuclide data and decay schemes. Reston: Society of Nuclear Medicine; 2007.Google Scholar
- Allan SM, Dean CJ, Eccles S, Sacks NP. Clinical radioimmunolocalization with a rat monoclonal antibody directed against c-erbB-2. Cell Biophys. 1994;24-25:93–8.View ArticlePubMedGoogle Scholar
- Smellie WJ, Dean CJ, Sacks NP, Zalutsky MR, Garg PK, Carnochan P, et al. Radioimmunotherapy of breast cancer xenografts with monoclonal antibody ICR12 against c-erbB2 p185: comparison of iodogen and N-succinimidyl 4-methyl-3-(tri-n-butylstannyl)benzoate radioiodination methods. Cancer Res. 1995;55(23 Supp):5842s–6s.PubMedGoogle Scholar
- Bakir MA, Eccles S, Babich JW, Aftab N, Styles J, Dean CJ, et al. c-erbB2 protein overexpression in breast cancer as a target for PET using iodine-124-labeled monoclonal antibodies. J Nucl Med. 1992;33(12):2154–60.PubMedGoogle Scholar
- Finucane CM, Murray I, Sosabowski JK, Foster JM, Mather SJ. Quantitative accuracy of low-count SPECT imaging in phantom and in vivo mouse studies. Int J Mol Imaging. 2011;2011:8. doi:10.1155/2011/197381.View ArticleGoogle Scholar
- Hindorf C, Ljungberg M, Strand SE. Evaluation of parameters influencing S values in mouse dosimetry. J Nucl Med. 2004;45(11):1960–5.PubMedGoogle Scholar
- Boutaleb S, Pouget JP, Hindorf C, Pelegrin A, Barbet J, Kotzki PO, et al. Impact of mouse model on preclinical dosimetry in targeted radionuclide Therapy. Proc IEEE. 2009;97(12):2076–85. doi:10.1109/Jproc.2009.2026921.View ArticleGoogle Scholar
- Mauxion T, Barbet J, Suhard J, Pouget JP, Poirot M, Bardies M. Improved realism of hybrid mouse models may not be sufficient to generate reference dosimetric data. Med Phys. 2013;40(5):052501. doi:10.1118/1.4800801.View ArticlePubMedGoogle Scholar
- Kostou T, Papadimitroulas P, Loudos G, Kagadis GC. A preclinical simulated dataset of S-values and investigation of the impact of rescaled organ masses using the MOBY phantom. Phys Med Biol. 2016;61(6):2333–55. doi:10.1088/0031-9155/61/6/2333.View ArticlePubMedGoogle Scholar
- Montelius M, Ljungberg M, Horn M, Forssell-Aronsson E. Tumour size measurement in a mouse model using high resolution MRI. BMC Med Imaging. 2012;12(1):1–7. doi:10.1186/1471-2342-12-12.View ArticleGoogle Scholar
- Ayers GD, McKinley ET, Zhao P, Fritz JM, Metry RE, Deal BC, et al. Volume of preclinical xenograft tumors is more accurately assessed by ultrasound imaging than manual caliper measurements. J Ultrasound Med. 2010;29(6):891–901.PubMedPubMed CentralGoogle Scholar