Theranostics 2014; 4(7):708-720. doi:10.7150/thno.8156
Targeted Radionuclide Therapy with A 177Lu-labeled Anti-HER2 Nanobody
1. Radiobiology Unit, Molecular and Cellular Biology Expert Group, Belgian Nuclear Research Center (SCK•CEN), Mol, Belgium.
2. In vivo Cellular and Molecular Imaging Laboratory (ICMI), Vrije Universiteit Brussel (VUB), Brussels, Belgium.
3. Structural Biology Research Center, Vlaams Instituut voor Biotechnologie (VIB), Brussels, Belgium.
4. Laboratory of Cellular and Molecular Immunology, Vrije Universiteit Brussel (VUB), Brussels, Belgium.
5. Department of Pathology, OLV Hospital Aalst, Aalst, Belgium.
6. Department of Pathology, UZ Brussel, Brussels, Belgium.
7. Department of Nuclear Medicine, UZ Brussel, Brussels, Belgium.
# Share senior authorship.
D'Huyvetter M, Vincke C, Xavier C, Aerts A, Impens N, Baatout S, De Raeve H, Muyldermans S, Caveliers V, Devoogdt N, Lahoutte T. Targeted Radionuclide Therapy with A 177Lu-labeled Anti-HER2 Nanobody. Theranostics 2014; 4(7):708-720. doi:10.7150/thno.8156. Available from http://www.thno.org/v04p0708.htm
RIT has become an attractive strategy in cancer treatment, but still faces important drawbacks due to poor tumor penetration and undesirable pharmacokinetics of the targeting vehicles. Smaller radiolabeled antibody fragments and peptides feature highly specific target accumulation, resulting in low accumulation in healthy tissue, except for the kidneys. Nanobodies are the smallest (MW < 15 kDa) functional antigen-binding fragments that are derived from heavy chain-only camelid antibodies.
Here, we show that the extend of kidney retention of nanobodies is predominantly dictated by the number of polar residues in the C-terminal amino acid tag. Three nanobodies were produced with different C-terminal amino-acid tag sequences (Myc-His-tagged, His-tagged, and untagged). Dynamic planar imaging of Wistar rats with 111In-DTPA-nanobodies revealed that untagged nanobodies showed a 70 % drop in kidney accumulation compared to Myc-His-tagged nanobodies at 50 min p.i.. In addition, coinfusion of untagged nanobodies with the plasma expander Gelofusin led to a final reduction of 90 %. Similar findings were obtained with different 177Lu-DTPA-2Rs15d nanobody constructs in HER2pos tumor xenografted mice at 1 h p.i.. Kidney accumulation decreased 88 % when comparing Myc-His-tagged to untagged 2Rs15d nanobody, and 95 % with a coinfusion of Gelofusin, without affecting the tumor targeting capacity. Consequently, we identified a generic method to reduce kidney retention of radiolabeled nanobodies. Dosimetry calculations of Gelofusin-coinfused, untagged 177Lu-DTPA-2Rs15d revealed a dose of 0.90 Gy/MBq that was delivered to both tumor and kidneys and extremely low doses to healthy tissues. In a comparative study, 177Lu-DTPA-Trastuzumab supplied 6 times more radiation to the tumor than untagged 177Lu-DTPA-2Rs15d, but concomitantly also a 155, 34, 80, 26 and 4180 fold higher radioactivity burden to lung, liver, spleen, bone and blood.
Most importantly, nanobody-based targeted radionuclide therapy in mice bearing small estiblashed HER2pos tumors led to an almost complete blockade of tumor growth and a significant difference in event-free survival between the treated and the control groups (P < 0.0001). Based on histology analyses, no evidence of renal inflammation, apoptosis or necrosis was obtained.
In conclusion, these data highlight the importance of the amino acid composition of the nanobody's C-terminus, as it has a predominant effect on kidney retention. Moreover, we show successful nanobody-based targeted radionuclide therapy in a xenograft model and highlight the potential of radiolabeled nanobodies as a valuable adjuvant therapy candidate for treatment of minimal residual and metastatic disease.
Keywords: HER2, nanobody, targeted radionuclide therapy, 177-Lutetium.
RIT has become an attractive therapeutic application, as it has the ability to target both the primary tumor site as well as disseminated diseased tissue. However, poor tumor penetration and undesirable pharmacokinetics limit the efficacy of RIT with radiolabeled mAbs. Nowadays, only two agents are approved for commercial use, Yttrium-90 ibritumomab (Zevalin, Biogen-Idec Pharmaceuticals) and Iodine-131 tositumomab (BEXXAR, GlaxoSmithKline), both used to treat indolent B-cell lymphoma.
The treatment of epithelial-based tumors is more difficult, as the actual dose delivered to tumors remains often inadequate, due to the dose-limiting toxicity to healthy tissues (1, 2). However, recent advances in the development of recombinant protein or peptide-derived targeting probes highlight the potential of overcoming these limitations. Indeed, many small radiolabeled antibody fragments and peptides feature highly specific but moderate target accumulation and are rapidly cleared from the blood, resulting in low accumulation in healthy tissue. However, since kidneys are the major excretion routes, intense accumulation of radioactivity in the renal cortical region is observed. High kidney retention is a well-described phenomenon (3,4). Although small size facilitates rapid clearance through the glomeruli in the kidneys, it is followed by a firm interaction with the negatively-charged lumen of the tubular system. This is attributed to the endocytic receptors megalin and cubulin, which are highly present in the renal proximal tubuli and are involved in the process of protein reabsorption. For targeted radiotherapy using long-lived radioisotopes, the intense kidney retention becomes a major dosimetric concern in terms of renal tissue toxicity and often limits its applicability. Radiation nephropathy has indeed been observed in several patients after PRRT using radiolabeled somatostatin analogues (5-7). Recently, several countermeasures were described to reduce kidney retention of radiolabeled targeting probes (8-10), of which positively charged amino acid and/or Gelofusin coinfusions became standard practice in PRRT. Gelofusin consists of succinylated bovine gelatin molecules and is clinically used as a plasma expander. In the past, it has been shown to enhance excretion of megalin ligands. Moreover, kidney retention of radiolabeled octreotide analogs is reduced with about 45 % upon infusion of Gelofusin. A combination of Gelofusin and L-lysine could reduce kidney uptake even further (9).
Nanobodies are the smallest antigen-binding fragments (MW around 14 kDa) derived from heavy chain-only antibodies naturally occuring in camelids (11). These minimal-sized recombinant antigen-binding fragments are rapidly cleared from blood, highly soluble in aqueaous solution and highly robust. They associate specifically and efficiently with their cognate target (12). Their potential as in vivo diagnostic tracers is well documented, targeting a variety of extracellular tumor cell biomarkers such as CEA (13), EGFR (14), HER2 (15,16) and PSMA (17).
In this study, we focus on nanobody-based targeted radionuclide therapy of HER2pos xenografted tumors, using the therapeutic radionuclide 177Lu (T1/2 = 6.72 days, <Eβ> = 133 keV). HER2 is overexpressed in a series of human cancer types such as breast, ovarian, colorectal and urothelial carcinomas (18). Its incidence for breast cancer ranges around 20-30 % and is often associated with a higher recurrence rate and a shorter time to relapse (19). Recently we reported the identification and characterization of an anti-HER2 nanobody, referred to as 2Rs15d, for clinical translation. Its selection was based on a complete screening of 38 anti-HER2 nanobodies that were derived from heavy chain-only antibodies and raised by immunizing a dromedary (15). To this end, nanobodies were 99mTc-labeled by means of site-specific conjugation of a 99mTc-tricarbonyl core at the imidazole residues of the C-terminal His-tag of the protein. Subsequently, the characterisation of 68Ga-labeled 2Rs15d was also described in terms of clinical immuno-PET imaging (16). Finally, the His-tagged anti-HER2 2Rs15d was also radiolabeled with 177Lu and biodistribution was assessed in xenografted mice (20). In the latter study we demonstrated that the bifunctional chelator 1B4M-DTPA was the preferred chelator for 177Lu-labeling as it exhibited the most favorable biodistribution. Overall, specific tumor targeting and low background tissue uptake was observed but, as expected, kidney accumulation was predominant and persistent. In the current study we therefore aim to optimize the nanobody format for reduced kidney retention. Next, its biodistribution in healthy wistar rats and a xenografted mouse model were assessed, followed by a dosimetric analysis. Finally, nanobody-based targeted radionuclide therapy was performed in mice bearing HER2pos tumors.
Materials and Methods
Cell line and culture conditions
The human ovarian cancer cell line SKOV3 (HER2pos) was obtained from American Type Culture Collection (ATCC, Manassas, VA, USA). SKOV3-LUC (HER2pos/Luciferasepos) was made in-house by transfecting the SKOV3 cells with luciferase-encoding lentiviral particles, as described previously (21). SKOV3 cells were cultured using McCoy's 5A medium, SKOV3-LUC in DMEM medium. Both media were enriched with 10 % fetal bovine serum, L-Glutamine (2 mM), 100 U/mL of penicillin and 0.1 mg/mL streptomycin. Cells were grown in a humidified atmosphere with 5 % CO2 at 37 °C. Prior to use for in vitro and in vivo purposes, cells were detached by using trypsin-EDTA. All media and supplements were obtained from Life Technologies (Paisley, UK).
Nanobody production and purification
Anti-HER2 nanobodies 2Rs15d, 2Rb17c and 1R136b were produced with 3 types of C-terminal amino acid tags: untagged (nanobody), His-tag (nanobody-HHHHHH), and Myc-His-tag (nanobody-AAAEQKLISEEDLNGAA-HHHHHH). Nanobodies were expressed in bacteria and purified, as described previously (22). Briefly, the sequences were re-cloned into an expression vector either containing a His-tag (pHEN6), a Myc-His-tag (pHEN18), or devoid of any tag (pHEN21). The recombinant vectors were transformed into E. coli WK6 cells for nanobody expression and extraction of periplasmic proteins. His- and Myc-His-tagged nanobodies were further purified by affinity chromatography on His-Select Nickel Affinity Gel (GE Healthcare). Untagged control nanobody BcII10, recognizing a bacterial enzyme (23), and both untagged 2Rb17c and 1R136b were purified on protein A Sepharose beads (GE Healthcare). The production of untagged 2Rs15d was performed according to Xavier and coworkers (16). Final purification of all nanobodies was perfomed through size-exclusion chromatography using Superdex 75 16/60 columns (GE Healthcare) in PBS. Protein purity and integrity were evaluated using SEC on Superdex 75 10/30 (GE Healthcare) in PBS, at flow rate 0.5 mL/min. In addition, ESI-Q-ToF-MS (Waters,Micromass) was performed, in positive mode.
Nanobody sequence analysis
The impact of the C-terminal deviations on the polarity of a nanobody was estimated with the Zimmerman polarity score plot (24). In short, amino acids in the nanobody sequence were given a polarity index value based on the dipole moments of the side chains. These values were then plotted with Graphpad Prism.
Conjugation of 1B4M-DTPA and CHX-A''-DTPA to nanobodies
A 10-fold molar excess of bifunctional chelator 1B4M-DTPA (for 177Lu) or CHX-A''-DTPA (for 111In) was conjugated for 3 h at RT to the free ε-amino-groups of lysines in the nanobodies in 600 µl of 0.05 M sodium carbonate buffer (pH 8.5). The conjugation reaction was quenched by reducing the pH of the mixture to pH 7.0. Nanobody-chelator was purified on Superdex 75 10/30 (GE Healthcare) in 0.1 M ammonium acetate buffer pH 7.0. The mean degree of conjugation was evaluated with ESI-Q-ToF-MS (Waters, Micromass), in positive mode.
Preparation of 111In- and 177Lu-DTPA-nanobodies
Nanobodies were labeled with 177Lu as previously described (20). Carrier-free 177Lu was obtained from ITG (Garching, Germany) as a chloride solution, with a specific activity of 3000 GBq/mg. Radiolabeling with 111In was performed similarly. 111InCl3 was purchased from Mallinckrodt (Petten, The Netherlands) with a specific activity of 1850 GBq/mg.
The necessary amount of 177Lu/111In was added to a test vial containing metal-free 0.1 M ammonium acetate buffer pH 5.0, to reach an end volume of 200 µL. Then, 25-100 µg of nanobody-DTPA (1 mg/mL) was added and incubated for 30 min at RT. The radiolabeled nanobody solution was purified on a disposable Nap-5 gelfiltration column (GE Healthcare) and pushed through a 0.22 µm filter. Radiochemical purity was assessed using iTLC with 0.2 M citric acid as mobile phase, and with either analytical radio-HPLC or radio-SEC. Radio-HPLC was performed using a polystyrene divinylbenzene copolymer reversed-phase column (PLRP-S 300 Å, 5 μm, 250/4 mm, Agilent, Diegem, Belgium). Here, a mixture of 0.1% TFA in H2O and ACN was used as eluent with the following gradient: 0-5 min 25% ACN; 5-7 min 25-34% ACN; 7-10 min 75-100% ACN; 10-25 min 100% ACN at a flow rate of 1 ml / min. Radio-SEC was done on Superdex 75 5/150GL using PBS as mobile phase at a flow rate of 0.3 mL / min.
Untagged 111In-DTPA-2Rs15d, used for dynamic planar scintigraphy studies, consisted of a nanobody: 111In ratio of 7:1. For the ex vivo biodistribution experiments with untagged 177Lu-DTPA-2Rs15d a ratio of 9:1 (nanobody: 177Lu) was achieved, while for targeted radionuclide therapy, samples of untagged 177Lu-DTPA-2Rs15d with a nanobody: 177Lu ratio of 3:1 were used.
Preparation of 177Lu-DTPA-Trastuzumab
Conjugation of 1B4M-DTPA to Trastuzumab was performed based on the protocol described by Sampath and coworkers, to yield a DTPA:Trastuzumab ratio of 5:1 (34). Briefly, a 100-fold molar excess of bifunctional chelator 1B4M-DTPA was conjugated overnight at RT to the free ε-amino-groups of lysines in Trastuzumab (Herceptin®, Hoffman-La Roche, Missis-sauga, ON, USA) in 3500 µl of 0.05 M sodium carbonate buffer (pH 8.5). The reaction was quenched by reducing the pH to 7.0. DTPA-Trastuzumab was purified on Superdex 75 10/30 (GE Healthcare) in 0.1 M ammonium acetate buffer pH 7.0. The degree of conjugation was evaluated with ESI-Q-ToF-MS (Waters, Micromass), in positive mode. The necessary amount of 177Lu was added to a test vial containing metal-free 0.1 M ammonium acetate buffer pH 5.0, to reach an end volume of 200 µL. Then, 100-250 µg DTPA-Trastuzumab (2.4 mg/mL) was added and incubated for 30 min at RT. 177Lu-DTPA-Trastuzumab was purified on a disposable Nap-5 gelfiltration column (GE Healthcare) and pushed through a 0.22 µm filter. Radiochemical purity was assessed using iTLC and radio- SEC, as described above.
Healthy male Wistar rats (255 ± 53 g body weight) were used in dynamic planar scintigraphy studies. Female athymic nude mice (20 ± 5 g body weight) were inoculated with 8 x 106 SKOV3 cells in PBS, s.c. in the right hind leg, under 2.5 % isoflurane anesthesia (Abbott, Ottignies-Louvain-la-Neuve, Belgium). Tumors reached a size of 205 ± 68 mm3, for biodistribution purposes. SKOV3-LUC xenografts were obtained by inoculating female athymic mice with 3 x 106 SKOV3-LUC cells in the right hind leg. Tumors were grown to reach 26 ± 5 mm3, for targeted radiotherapy purposes. The animal protocols were approved by the ethical committee of the Vrije Universiteit Brussel.
Kidney retention of 111In-DTPA-nanobodies in healthy Wistar rats
Wistar rats (n=3) were anesthetized by an i.p. injection of 250 μL pentobarbital, prior to an i.v. injection of 111In-DTPA-nanobodies (35.8 ± 5.4 MBq). In a separate group, the 111In-DTPA-untagged nanobodies were additionally coinjected in parallel with 80 mg/kg Gelofusin (40 g/l, Braun Medical, Diegem, Belgium). To record the fast in vivo kinetics of radiolabeled nanobodies, dynamic planar imaging was performed immediately after injection (100 frames of 30 s). Time activity curves of the kidneys were generated using AMIDE Medical Image Data Examiner software, as previously described (25). ROIs were drawn around total body and kidneys, to calculate the radioactivity retained in kidneys relative to the total injected activity (% IA).
In vivo tumor targeting of 177Lu-DTPA-nanobodies
SKOV3 tumor-bearing mice (n=3) were injected i.v. with each of the 177Lu-DTPA-2Rs15d nanobody formats (21.5 ± 1.7 MBq). In a separate group, 177Lu-DTPA-untagged 2Rs15d was co-injected with 150 mg/kg Gelofusin. Mice were euthanized and dissected 1 h p.i., tissues were weighed and radioactivity was counted with an automated gamma counter (Cobra Inspector 5003, Canberra Packard, USA). The amount of radioactivity present in the different tissues was expressed as % IA/g tissue.
Comparative dosimetry calculation of a single dose 177Lu-DTPA-untagged 2Rs15d and Gelofusin versus 177Lu-DTPA-Trastuzumab
SKOV3 tumor-bearing mice were injected i.v. with either 14.7 ± 1.3 MBq 177Lu-DTPA-untagged 2Rs15d and 150 mg/kg Gelofusin, or 10.1 ± 0.2 MBq 177Lu-DTPA-Trastuzumab. At 1, 3, 6, 24, 48, 72, and 120 h p.i., mice (n=3) were euthanized and dissected to count radioactivity as described above and to obtain tissue biodistribution values expressed as % IA/g. The time point 168 h p.i. was included for the dosimetric calculation of 177Lu-DTPA-Trastuzumab. These values were time integrated to obtain the residence time per gram tissue, following a procedure that was described elsewhere (26). Briefly, the integration between time 0 and 120 h (or 168 h for 177Lu-DTPA-Trastzuzmab) was made using the trapezoid method. The final 2 points were used to estimate the residence time from 120 h to infinity. For each data set, the absorbed doses were calculated. The S values of 177Lu were obtained from RADAR phantoms (www.doseinfo-radar.com/RADARphan.html). The S value for 1 g sphere (0.0233 mGy/MBq s) was used for dose calculations.
Experimental targeted radionuclide therapy with 177Lu-DTPA-untagged 2Rs15d and Gelofusin
When SKOV3-LUC tumors reached a volume of 20-30 mm3 (day 7), animals were randomly categorized into 3 groups (n=8). Mice in each group received 7 i.v. injections (once a week, over a period of 7 weeks) of a volume containing either 20.7 ± 0.4 MBq 177Lu-DTPA-untagged 2Rs15d, 19.3 ± 0.8 MBq 177Lu-DTPA-untagged BcII10, or PBS. All samples were diluted in 150 mg/kg Gelofusin. The study was terminated 125 days after tumor cell inoculation. Animal weights were monitored weekly, as well as tumor growth through caliper measurement. Once every 2 weeks, tumor burden was also visualized using bioluminescence imaging, after i.p. injection of 150 mg/kg Luciferin, according to Keyaerts and coworkers (21). Results were summarized in an event-free survival curve, with events defined as (1) mortality, (2) > 20 % weight loss, (3) ulcerating tumor tissue, or (4) a tumor volume exceeding 250 mm3. At the end of the study, animals were euthanized; dissected and renal tissues were preserved.
Renal samples of 177Lu-dosed and control groups were fixed in formalin for 4 hours, dehydrated and embedded in paraffin. The paraffin sections (3 µm) were processed for staining with H&E, PAS and Masson's trichrome, according to standard protocols. Stained sections were evaluated for necrosis, apoptosis, inflammation and vascular changes in the renal tissue, using light microscopy.
Statistically significant differences in biodistribution were analyzed with the two-tailed t-test, while the event-free survival between treated groups was analyzed using the log-rank test (P < 0.05).
Polarity of nanobodies
As nanobodies are predominantly cleared through the kidneys, these organs inevitably become the dose-limiting organs in targeted radionuclide therapy. Previous exploratory experiments indicated that the C-terminal amino acid tag of the nanobody might have an important impact on the degree of kidney retention. Zimmerman polarity score plots of various 2Rs15d constructs are shown in figure 1. As compared to untagged 2Rs15d, the introduction of 6 histidines mark a high polar region at the C-terminus of His-tagged 2Rs15d. Myc-His-tagged 2Rs15d possesses an even higher C-terminal polarity score, due to the presence of an extra lysine, aspartic acid and 2 glutamic acids, all amino acids with a high polarity index value.
Conjugation of 1B4M-DTPA and CHX-A''-DTPA to nanobodies
CHX-A''-DTPA was used for 111In labeling and 1B4M-DTPA for 177Lu labeling. SEC profiles and ESI-Q-ToF-MS analyses indicated successful conjugation of the bifunctional DTPA-chelators to the different nanobody constructs. SEC profiles of untagged 2Rs15d, untagged 1B4M-DTPA-2Rs15d and untagged CHX-A''-DTPA-2Rs15d are presented in figure 2A-C. DTPA was conjugated to the ε-amino groups of lysine residues, hereby forming a thiourea bond. Therefore, since 2Rs15d contains multiple lysines, the conjugation reaction resulted in a mixture of molecules with 1, 2, and 3 DTPA chelators, as determined by ESI-Q-ToF-MS analysis. The MS profiles of untagged 2Rs15d (MW: 12624 Da), untagged CHX-A''-DTPA-2Rs15d (major peak corresponding to the conjugation of 2 DTPA, MW: 13923) and untagged 1B4M-DTPA-2Rs15d (major peak corresponding to the conjugation of 2 DTPA, MW: 13842) are shown in Additional file 1: supplementary figure 1. Consequently, the dominant conjugation ratio (chelator:nanobody) for both 1B4M-DTPA and CHX-A”-DTPA to untagged 2Rs15d is 2:1. By applying the standardized protocol, a consistent degree of 2:1 (chelator:nanobody) conjugation was also obtained for the nanobodies 2Rb17c and 1R136d.
Zimmerman - polarity score plot for the various 2Rs15d nanobody formats. (A) untagged 2Rs15d; (B) His-tagged 2Rs15d and (C) Myc-His-tagged 2Rs15d. Introduction of charged amino acids at the nanobody's C-terminus has a major impact on the polarity score.(Click on the image to enlarge.)
(Radio-)chromatographic analyses of various untagged 2Rs15d conjugates. (A) unconjugated nanobody, (B) CHX-A”-DTPA-2Rs15d, (C) 1B4M-DTPA-2Rs15d, (D) 177Lu-DTPA-2Rs15d, (E) 111In-DTPA-2Rs15d; (A-C) SEC on Superdex 10/30, (D) radio-SEC on Superdex 75 5/150GL; (E) radio-HPLC on PLRP-S. The R-times of the major peaks are shown in each graph.(Click on the image to enlarge.)
Preparation of 111In- and 177Lu-DTPA-nanobodies
Nanobodies were conjugated with CHX-A''-DTPA for 111In labeling. After radiolabeling, iTLC revealed radiochemical purities of 95.1 ± 1.7 % and > 99 %, before and after SEC purification, respectively. The 2Rs15d nanobody constructs conjugated with 1B4M-DTPA were labeled with 177Lu in high yields as determined by iTLC, i.e. 97.2 ± 2.5 % before and > 99 % after SEC purification. Radiochemical purities were confirmed with radio-HPLC or radio-SEC. The radio-HPLC profile of untagged 111In-DTPA-2Rs15d and the radio-SEC profile of untagged 177Lu-DTPA 2Rs15d are shown in figure 2D-E.
Preparation of 177Lu-DTPA-Trastuzumab
SEC profiles and ESI-Q-ToF-MS analyses indicated successful conjugation of 1B4M-DTPA to Trastuzumab. The radiochemical purity of 177Lu-DTPA-Trastuzumab was 99.5 ± 0.2 % (iTLC) and was confirmed with radio-SEC. SEC profiles of unconjugated Trastuzumab and DTPA-Trastuzumab are shown in Additional file 1: supplementary figure 2, together with the radio-SEC profile of 177Lu-DTPA-Trastuzumab.
Kidney retention of 111In-DTPA-nanobodies in healthy Wistar rats
To confirm that the nanobody's C-terminal polarity strongly influences the degree of kidney retention, Wistar rats were injected with the different 111In-DTPA-nanobody constructs. Representative and equally scaled planar images are shown in figure 3A-D. Finally, whole-body and kidney ROIs were drawn and plotted as a function of time, to obtain the relative amounts of accumulating radioactivity in kidneys (Figure 3E). Highest accumulation of radioactivity in the kidneys was confirmed for Myc-His-tagged 2Rs15d, followed by His-tagged and untagged 2Rs15d, giving values of 52.44 ± 4.70, 36.45 ± 4.28 and 18.24 ± 1.71 % IA at 50 min p.i., respectively. All three curves described a similar parabolic shape. The lowest accumulation in kidneys was observed for untagged 2Rs15d that was coinfused with 80 mg/kg Gelofusin, with a value of only 6.52 ± 0.18 % IA at 50 min p.i. Here the curve described an initial incline of radioactivity followed rapidly by a steady low amount of radioactivity in kidneys. These findings were confirmed for two additional HER2-targeting nanobodies 2Rb17c and 1R136d (Additional file 1: Supplementary Figure 3).
In vivo tumor targeting of the 177Lu-DTPA-2Rs15d nanobodies
SKOV3 tumor xenografted mice (n=3) were injected with the different 177Lu-DTPA-2Rs15d nanobodies. Tumor targeting was not affected by altering the C-terminal tag or by a coinjection with gelofusin, with uptake values of 5.9 ± 0.7 %; 6.4 ± 0.8 %; 6.9 ± 0.4 % and 6.5 ± 0.2 % IA/g for Myc-His-tagged, His-tagged, untagged and untagged nanobody with 150 mg/kg Gelofusin, respectively. More importantly, again substantial differences in kidney uptake were observed, with decreasing values of 195.8 ± 23.7 %; 127.7 ± 2.9 %; 25.8 ± 1.3 % and 10.4 ± 1.7 % IA/g for Myc-His-tagged, His-tagged, untagged, and untagged nanobody together with 150 mg/kg Gelofusin, respectively (Figure 4). Uptake values in the major organs and tissues did not differ significantly.
Accumulation of radioactivity in kidneys in function of time after injection of various 111In-labeled 2Rs15d formats in healthy Wistar rats (n=3); (A-D) A selection of images are shown obtained by gamma camera dynamic scintigraphy; (A) 2Rs15d-Myc-His-tag, (B) 2Rs15d-His-tag, (C) untagged 2Rs15d, (D) untagged 2Rs15d coinfused with 80 mg/kg Gelofusin. (E) Time-activity curves of renal retention in rats (n=3 per condition). Lowest accumulation in kidneys was observed for the 111In-labeled untagged 2Rs15d that was coinfused with 150 mg/kg Gelofusin.(Click on the image to enlarge.)
Ex vivo biodistribution analyses of 177Lu-labeled 2Rs15d constructs in HER2pos tumor xenografted mice, at 1 h p.i. Animals were injected with 21.5 MBq (4 µg) radioconjugates. Columns, mean (n=3); bars, SD. Kidney accumulation decreased significantly by removing the C-terminal amino acid tag, and by a coinfusion with Gelofusin. Tumor targeting was not affected.(Click on the image to enlarge.)
Comparative dosimetry calculation of a single dose 177Lu-DTPA-untagged 2Rs15d and Gelofusin versus 177Lu-DTPA-Trastuzumab
The biodistribution data are presented in Table 1. For untagged 177Lu-DTPA-2Rs15d nanobody, the highest tumor uptake values were observed at early time points and decreased from 6.50 ± 0.24 % IA/g at 1 h p.i. to 2.15 ± 0.11 % IA/g at 48 h p.i. and to 1.15 ± 0.16 % IA/g at 120 h p.i. Kidney uptake values peaked at 10.36 ± 1.73 % IA/g 1 h p.i. and then decreased to 2.08 ± 0.29 % IA/g at 48 h p.i. and 0.40 ± 0.29 % IA/g at 120 h p.i. Bone activity was low, indicating there was no substantial release of 177Lu. Radioactivity concentration in the other major organs and tissues was low, with values below 0.5 % IA/g at early time points, and decreasing over time. In contrast, tumor uptake of 177Lu-DTPA-Trastuzumab was low at early time points and increased from 1.07 ± 0.31 % IA/g to 28.09 ± 0.58 % IA/g at 96 h and 17.13 ± 2.00 % IA/g at 168 h p.i. Blood values were high with 23.32 ± 4.36 % IA/g at 1h and still 10.69 ± 1.77 % IA/g at 168 h p.i. At all-time points the radioactive concentrations in additional organs (especially in liver, lung and spleen) remained much higher than for untagged 177Lu-DTPA-2Rs15d.
The dosimetry calculations are presented in table 2. For untagged 177Lu-labeled 2Rs15d, the highest radiation absorbed dose was delivered to tumor and kidneys, with an equivalent value of 0.9 Gy/MBq, while the radiation burden to other healthy tissues was very low. 177Lu-DTPA-Trastuzumab on the other hand delivered a calculated dose to the tumor of 5.55 Gy/MBq. However, radiation to blood, liver, spleen and lung was also high and estimated to be 4.18, 1.72, 1.60 and 1.55 Gy/MBq, respectively.
Ex vivo biodistribution of (A) untagged 177Lu-DTPA-2Rs15d nanobody coinfused with 150 mg/kg Gelofusin and (B) 177Lu-DTPA-Trastuzumab, in HER2pos xenografted mice (n=3 per time point).
|Organ||1 h p.i.||3 h p.i.||6 h p.i.||24 h p.i.||48 h p.i.||72 h p.i.||96 h p.i.||120 h p.i.||168 h p.i.|
NOTE: Each data point presents an average ± SD and is expressed as % IA/g.
Dosimetry calculation of untagged 177Lu-DTPA-2Rs15d nanobody coinfused with 150 mg/kg Gelofusin, and of 177Lu-DTPA-Trastuzumab, in HER2pos xenografted mice.
NOTE: Dosimetry data are expressed as Gy/MBq
Experimental targeted radionuclide therapy with 177Lu-DTPA-untagged 2Rs15d and Gelofusin
Mice bearing small SKOV3-LUC tumors were i.v. injected with either untagged 177Lu-DTPA-2Rs15d, untagged 177Lu-DTPA-BcII10 (a non-targeting control nanobody) or the vehicle PBS, all coinjected with 150 mg/kg Gelofusin. For both the PBS-treated (n=8) and 177Lu-DTPA-BcII10-treated animals (n=8), the tumor volume of all animals already exceeded the value of 250 mm3 between day 33 and 75 after inoculation, as measured with a caliper (Figure 5B). All animals from the control groups were euthanized at day 85 due to the development of large tumors (> 1 cm3), as shown in Figure 5B. No statistically significant difference was observed in event-free survival between both control groups. In contrast, up to day 125 no substantial increase in tumor size was observed among the mice that were treated with untagged anti-HER2 177Lu-DTPA-2Rs15d (n=8). Remarkably, 5 out of 8 mice were completely free of tumor burden, as confirmed by bioluminescence imaging (Figure 5A). The other 3 mice developed small, LUCpos, but no palpable tumors. One animal in this group had to be euthanized due to a weight loss of more than 20 % (day 95). Overall, event-free survival was significantly longer for the treated group compared to the control groups that received PBS (P < 0.0001) or 177Lu-DTPA-BcII10 (P < 0.0001), respectively (Figure 6A). Histopathological analyses of renal tissues showed no differences between the experimental groups. The glomeruli, the tubuli and the vasculature were morphologically normal and no necrosis was noted. The interstitium was not broadened or fibrotic, and was free of inflammatory cells. No protein casts could be observed (figure 6B).
Tumor growth monitoring during targeted radionuclide therapy. Tumor volumes were quantified using (A) bioluminescence imaging (ph/s/cm2/sr) or (B) caliper measurements (mm3), in function of time (days). Animals (n=8 per group) were treated with a weekly injection of untagged 177Lu-labeled 2Rs15d (20.7 ± 0.4 MBq) and in the control groups with PBS or 177Lu-labeled BCII10 (19.3 ± 0.8 MBq). All treatments occurred with a 150 mg/kg Gelofusin coinjection. In terms of tumor growth, important differences were observed between both control groups and the treated group, for both caliper and bioluminescence measurements.(Click on the image to enlarge.)
(A) Event-free survival during targeted radionuclide therapy. Events are defined as 1. Mortality; 2. > 20 % weight loss; 3. Ulcerating tumor tissue; 4. Tumor volume > 250 mm3. Animals (n=8 per group) were treated with a weekly injection of untagged 177Lu-labeled 2Rs15d (20.7 ± 0.4 MBq) and in the control groups with PBS or 177Lu-labeled BCII10 (19.3 ± 0.8 MBq). All treatments occurred with a 150 mg/kg Gelofusin coinjection. (B) Renal histopathology. Kidneys of 177Lu-dosed animal groups were compared to the PBS-treated animal group. Sections were H&E stained and examined for evidence of renal toxicity. No differences in renal histology were observed between the animal groups that received (B.1) PBS, (B.2) untagged 177Lu-labeled BCII10 or (B.3) untagged 177Lu-labeled 2Rs15d.(Click on the image to enlarge.)
In the present study we describe nanobody-based targeted radionuclide therapy in tumor xenografted mice, using the therapeutic radionuclide 177Lu. β-emitting radionuclides such as 177Lu produce particles with a mean energy of 0.1-1 MeV and a range of 1-10 mm, and possess the ability to target multiple cell diameters. Effective antibody-based RIT applications are still limited, as mAbs show poor tumor penetration and non-specific accumulation of radioactivity in organs and tissues, with bone marrow toxicity as the major dose-limiting factor (myelotoxicity). In 2005, Persson and coworkers presented an experimental study on 177Lu-labeled anti-HER2 mAb Pertuzumab in HER2pos tumor xenografted mice (28). Here, high accumulation in tumor tissue was measured, with values of 8 % IA/g and 20 % IA/g at day 1 and 3 respectively. However, at these time points blood values were still at 8 % IA/g and 3 % IA/g. At day 1 values of 3-5 % IA/g were measured in organs like kidney, liver and spleen, which only slowly decreased over time. More recently, Ray and coworkers described similar observations in a biodistribution study with 177Lu-labeled anti-HER2 mAb Trastuzumab versus a non-specific 177Lu-labeled mAb HuIgG in HER2pos xenografted mice (27). Although high tumor uptake values were observed using 177Lu-Trastuzumab (16.24 ± 4.18 % IA/g at 24 h p.i. and 19.08 ± 3.23 % IA/g at 48 h p.i.), they also registered tumor uptake values of 7.51 ± 1.98 and 7.41 ± 0.73 % IA/g at the same time points after injecting 177Lu-HulgG. Moreover, non-specific accumulation in healthy tissues remained high at all-time points, with still 10.06 ± 2.75 % IA/g in blood and 6.70 ± 1.71, 5.69 ± 2.12, and 4.24 ± 0.62 % IA/g in respectively liver, spleen and kidney, 96 h after injecting 177Lu-Trastuzumab. We confirmed these data by performing an ex vivo biodistribution analyses of 177Lu-DTPA-Trastuzumab in SKOV3 xenografted mice. Tumor uptake of 177Lu-DTPA-Trastuzumab was low at early time points and increased from 1.07 ± 0.31 % IA/g to 28.09 ± 0.58 % IA/g at 96 h and 17.13 ± 2.00 % IA/g at 168 h p.i. Blood values were high with 23.32 ± 4.36 % IA/g at 1h and still 8.72 ± 0.88 % IA/g at 168 h p.i. Highly perfused organs like liver, lung, kidney and spleen showed significant retention of radioactivity up to 168 h p.i.
Different alternatives aiming to compensate for these limitations are currently under investigation: co-administration of anti-angiogenic agents, extracorporeal elimination, pre-targeting, or engineering of smaller antibody-derived vectors (1). The approach of smaller antibody-derived vectors is supported by their much faster target tissue accumulation and their low background retention of radioactivity. However, one drawback of using small molecular vectors remains the high kidney accumulation caused by intracellular entrapment of radioactivity due to non-specific tubular reuptake after glomerular filtration. We recently described successful radiolabeling of the His-tagged anti-HER2 nanobody 2Rs15d with 177Lu, using the bifunctional chelator 1B4M-DTPA. Specific tumor targeting was observed, with low background tissue and organ uptake except for the kidneys, which was the main limitation for a clinical application of nanobody-based targeted radionuclide therapy (20). Therefore, finding countermeasures to reduce the degree of kidney retention was a main priority. Strategies to reduce the kidney uptake of radiolabeled protein- or peptide-based vectors have already been investigated intensively. For example, coinfusion with a mixture of 150 mg/kg Gelofusin and 1.2 g/kg L-lysine could reduce renal uptake of a 99mTc-labeled anti-EGFR nanobody with 45 % (10). Gelofusin also reduced the kidney retention of radiolabeled octreotide analogs to a similar extent (29,30) and a combination of Gelofusin and L-lysine reduced kidney uptake even further (9,31). Alternatively, Wällberg and coworkers demonstrated that amino acid substititions in the C-terminal amino acid sequence of an affibody molecule has a significant impact on the extend of kidney retention (8).
In this study we investigated the influence of the C-terminal amino acid tag on the overall polarity of the nanobody sequence on the one hand, and the degree of kidney retention on the other. Amino-acid tags are regularly linked to proteins such as antibody-fragments, for purification and radiolabeling purposes (His-tag) or for in vitro detection (Myc-tag). However, the introduction of potentially charged amino acids will affect the overall polarity of the protein, and thus also its in vivo behavior. This presumption was eventually confirmed by evaluating the in vivo behavior of different 111In-DTPA-nanobody formats in healthy Wistar rats. The highest activity retained in kidneys was observed for Myc-His-tagged 2Rs15d. Changing Myc-His-tag to His-tag led to a drop in retention of label by 31 %, 50 min p.i. complete removal of the C-terminal amino acid tag lowered kidney retention up to 65 %, as compared to the Myc-His-tagged 2Rs15d. Finally, coinjecting untagged 111In-DTPA-2Rs15d with Gelofusin further reduced kidney retention with an additional 65 %. This observation was confirmed with two other HER2-targeting nanobodies.
A similar trend was observed after injecting the different 2Rs15d formats, radiolabeled with 177Lu, in HER2pos xenografted mice. Figure 4 confirms the observations from the dynamic scans regarding the kidney retention. The highest uptake value in kidney was observed for the Myc-His-tagged format whereas the lowest uptake was attained with the untagged 2Rs15d and 150 mg/kg Gelofusin. Tumor targeting was not affected by either adjusting the C-terminal amino acid tag or coinjecting Gelofusin.
A comparative ex vivo biodistribution of a single dose untagged 177Lu-DTPA-2Rs15d with 150 mg/kg Gelofusin versus a single dose 177Lu-DTPA-Trastuzumab was evaluated until 120 h and 168 h p.i., respectively. Injecting untagged 177Lu-DTPA-2Rs15d nanobody revealed a fast washout of activity from all non-target organs and tissues. At 48 h p.i., the radioactivity in tumor exceeded the amount present in kidney, resulting in a comparable radiation absorbed dose to tumor and kidneys. The dose delivered to non-targeted tissues like blood, liver, and spleen were extremely low. Moreover, the low dose delivered to bone suggests the absence of free 177Lu. In contrast, although 177Lu-DTPA-Trastuzumab supplied a 6 fold higher dose to the tumor than untagged 177Lu-DTPA-2Rs15d, also the radiation burden to lung, liver, spleen, bone and blood was concomitantly 155, 34, 80, 26 and 4180 fold higher.
In 2004, Adams and coworkers reported RIT in HER2pos xenografts using an Yttrium-90 labeled anti-HER2 diabody (32). Despite the use of a different radioisotope in this study (Indium-111 for imaging, Yttrium-90 for RIT), they observed important differences in ex vivo biodistribution compared to our results with untagged 177Lu-DTPA 2Rs15d nanobody. Although tumor uptake values, measured for the diabody, were higher in the SKOV3 xenograft model (double at 24 h p.i.), non-specific accumulation was also much higher in kidney (7 fold), blood (500 fold), spleen (33 fold) and liver (13 fold), all at 24 h p.i., resulting in observed toxicity in kidneys.
Finally, nanobody-based targeted radionuclide therapy was performed in HER2pos xenografted mice with small tumor volumes of 20-30 mm3, as a preliminary model to mimic minimal residual or micrometastatic disease. Both experimental groups receiving either non-specific 177Lu-labeled BcII10 nanobody or the vehicle PBS group noted no significant differences in terms of tumor growth inhibition. Tumor volumes of all animals in both control groups exceeded already the value of 250 mm3 between day 33 and 75 after inoculation. No animals in the treated group had tumors exceeding 250 mm3 up to day 125. Moreover, 5 out of the 8 treated mice showed complete absence of tumor formation. The other 3 mice developed small, but no palpable tumors, that were however detectable via bioluminescence imaging.
Taken together, the results presented here show a successful application of nanobody-based targeted radionuclide therapy in tumor-bearing mice, using the therapeutic radionuclide Lutetium-177. Since highly specific nanobodies are easily raised against a variety of cancer-related antigens, nanobody-based targeted radionuclide therapy could be introduced in several types of cancer disease.
We have demonstrated that kidney retention is reduced significantly when using untagged nanobodies and coinfusion with 150 mg/kg Gelofusin. Hence, anti-HER2 nanobodies constitute potent small molecular vehicles for targeted radionuclide therapy. Anti-HER2 nanobodies, when radiolabeled with 177Lu, efficiently inhibit growth of HER2 expressing tumors in xenografted mice, without pronounced non-specific radiation to healthy tissues. Moreover, histopathological analyses of renal tissue revealed no visible toxicity.
Supplementary MaterialAdditional File 1
Supplementary Figures 1-3.
RIT: radioimmunotherapy; mAbs: monoclonal antibodies; Molecular Weight: MW; C-terminal: carboxyl-terminal; PRRT: peptide receptor radionuclide therapy; CEA: carcino-embryonic antigen; EGFR: epidermal growth factor receptor; HER2: human epidermal growth factor receptor 2; PSMA: prostate-specific membrane antigen; His-tag: hexahistidine-tag; 177Lu: Lutetium-177; Immuno-PET: immuno-positron emission tomography; PBS: phosphate-buffered saline; 111In: Indium-111; ESI-Q-ToF-MS: Electrospray ionization quadrupole time-of-flight mass spectrometry; RT: room temperature; iTLC: instant Thin Layer Chromatography; R-time: retention time; HPLC: High Performance Liquid Chromatography; SEC: size-exclusion chromatography; TFA: Trifluoroacetic acid; ACN: acetonitrile; Da: Dalton; s.c.: subcutaneous; i.p.: intraperitoneal; i.v.: intravenous; ROIs: regions of interest; p.i.: post-injection; 99mTc: Technetium-99m; H&E: hematoxylin and eosin; PAS: Periodic acid-Schiff; SPECT: Single Photon Emission Computed Tomography; SD: standard deviation; %IA/g: % injected activity per gram tissue; N/A: not available; Gy/MBq: Gray per Megabecquerel.
The 1B4M-DTPA bifunctional chelator was generously donated by Dr. Martin Brechbiel (National Cancer Institute, Bethesda, TX, USA). Matthias D'Huyvetter is funded by a SCK•CEN/VUB grant and the foundation Emmanuel van der Schueren. Tony Lahoutte is a Senior Clinical Investigator of the Research Foundation - Flanders (Belgium) (FWO). The research at ICMI is funded by the Belgian State, Nationaal Kankerplan, Vlaamse Liga tegen Kanker and Vlaamse Stichting tegen Kanker. This work was also supported by FWO-Vlaanderen (Research Project G.013910). We thank Karine Breckpot for providing the luciferasepos cell line, and Cindy Peleman and Arnaud Campsteyn for technical assistance.
The authors have declared that no competing interest exists.
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Corresponding author: Matthias D'Huyvetter, MSc, In vivo Cellular and Molecular Imaging Laboratory, Vrije Universiteit Brussel, Laarbeeklaan 103, 1090 Brussels, Belgium; Tel (+32) 2 477 4991; E-mail: mdhuyvetac.be.