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p-Isothiocyanatobenzyl-desferrioxamine: a new bifunctional chelate for facile radiolabeling of monoclonal antibodies with zirconium-89 for immuno-PET imaging

  • Lars R. Perk
  • Maria J. W. D. Vosjan
  • Gerard W. M. Visser
  • Marianne Budde
  • Paul Jurek
  • Garry E. Kiefer
  • Guus A. M. S. van DongenEmail author
Open Access
Original Article

Abstract

Purpose

Immuno-PET is an emerging imaging tool for the selection of high potential antibodies (mAbs) for imaging and therapy. The positron emitter zirconium-89 (89Zr) has attractive characteristics for immuno-PET with intact mAbs. Previously, we have described a multi-step procedure for stable coupling of 89Zr to mAbs via the bifunctional chelate (BFC) tetrafluorophenol-N-succinyldesferal (TFP-N-sucDf). To enable widespread use of 89Zr-immuno-PET, we now introduce the novel BFC p-isothiocyanatobenzyl-desferrioxamine B (Df-Bz-NCS) and compare its performance in 89Zr-immuno-PET with the reference BFC TFP-N-sucDf.

Methods

Three mAbs were premodified with Df-Bz-NCS and labeled with 89Zr at different pHs to assess the reaction kinetics and robustness of the radiolabeling. Stability of both 89Zr-Df-Bz-NCS- and 89Zr-N-sucDf-conjugates was evaluated in different buffers and human serum. Comparative biodistribution and PET studies in tumor-bearing mice were undertaken.

Results

The selected conjugation conditions resulted in a chelate:mAb substitution ratio of about 1.5:1. Under optimal radiolabeling conditions (pH between 6.8–7.2), the radiochemical yield was >85% after 60 min incubation at room temperature, resulting in radioimmunoconjugates with preserved integrity and immunoreactivity. The new radioimmunoconjugate was very stable in serum for up to 7 days at 37°C, with <5% 89Zr release, and was equally stable compared to the reference conjugate when stored in the appropriate buffer at 4°C. In biodistribution and imaging experiments, the novel and the reference radioimmunoconjugates showed high and similar accumulation in tumors in nude mice.

Conclusions

The novel Df-Bz-NCS BFC allows efficient and easy preparation of optimally performing 89Zr-labeled mAbs, facilitating further exploration of 89Zr-immuno-PET as an imaging tool.

Keywords

Positron emission tomography Zirconium-89 Bifunctional chelate Desferrioxamine Antibodies Radiolabeling 

Introduction

Presently, hundreds of monoclonal antibodies (mAbs) and mAb fragments are under clinical development because of their excellent potential for diagnosis and systemic treatment of cancer and other pathological conditions [1]. Positron emission tomography (PET) offers an attractive imaging option to confirm and quantify selective tumor uptake of such targeting molecules [2, 3, 4].

To enable PET imaging of intact mAbs and mAb-fragments (immuno-PET), an appropriate positron emitter, with a half-life (t1/2) that is compatible with the time needed to achieve optimal tumor-to-nontumor ratios (typically 2–4 days for intact mAbs, and 2–4 h for mAb-fragments), has to be securely coupled to the targeting molecule. Among others, the following positron emitters for immuno-PET are under investigation at the moment: gallium-68 (68 Ga; t1/2: 1.13 h), fluorine-18 (18F; t1/2: 1.83 h), copper-64 (64Cu; t1/2: 12.7 h), yttrium-86 (86Y; t1/2: 14.7 h), bromine-76 (76Br; t1/2: 16.2 h), zirconium-89 (89Zr; t1/2: 78.4 h), and iodine-124 (124I; t1/2: 100.3 h). Another important consideration in the choice of a positron emitter is whether the mAb or mAb fragment becomes internalized after binding to the target antigen. In that case, a positron emitter is needed that residualizes in the target cell after internalization, like 68Ga, 64Cu, 86Y, and 89Zr, to enable imaging at optimal contrast. These radionuclides have to be attached via chelating agents to mAbs and mAb-fragments.

For the imaging of intact mAbs with PET, we recently described the large-scale production of 89Zr and a strategy for labeling mAbs with 89Zr via a multi-step synthesis using a succinylated-derivative of desferrioxamine B (N-sucDf ) as bifunctional chelate [5]. The utility of this approach was clearly demonstrated through high-quality 89Zr-mAb-PET images reported in preclinical and clinical studies [6, 7, 8, 9, 10, 11, 12, 13]. The choice of desferrioxamine B is attractive because it is used clinically in a safe way for many years. The upcoming commercialization of 89Zr will make this radionuclide broadly available for research and clinical applications.

A shortcoming of the aforementioned labeling approach is that the multi-step procedure is relatively complicated and time-consuming, and therefore challenging with respect to Good Manufacturing Practice (GMP) compliancy. We now introduce a newly developed p-isothiocyanatobenzyl-derivative of desferrioxamine B (Df-Bz-NCS; Macrocyclics, TX) that enables an efficient and rapid preparation of 89Zr-labeled mAbs.

The chemical characterization of Df-Bz-NCS, its subsequent coupling to mAbs, and the radiolabeling of Df-Bz-NCS conjugated mAbs with 89Zr, are described. The in vitro stability of 89Zr-Df-Bz-NCS-mAb conjugates is compared with the corresponding 89Zr-N-sucDf-mAb conjugates. In addition, comparative biodistribution and animal-PET studies are presented.

Materials and methods

Materials, monoclonal antibodies, cell lines, and radioactivity

All reagents were obtained from Sigma-Aldrich (St. Louis, MO) unless otherwise stated. No special measures were taken regarding working under strict metal-free conditions. Deionized water (18 MΩ) was used in all reactions. Df-Bz-NCS was obtained from Macrocyclics (cat. no. B-705). MAb cetuximab (Erbitux; 2.0 mg/ml) directed against the epidermal growth factor receptor (EGFR) was purchased from Merck (Darmstadt, Germany) [14]. Selection, production, and characterization of chimeric mAb U36 (cU36; 11.53 mg/ml) directed against CD44v6 has been described elsewhere [15]. MAb rituximab (MabThera; 10 mg/ml) directed against CD20 was purchased from Roche Nederland BV (Woerden, The Netherlands).

The human epidermoid cervical carcinoma cell line A431 and the CD20+ B-cell lymphoma cell line Ramos were both obtained from the American Type Culture Collection (www.atcc.com, ATCC number: CRL-1555 and CRL-1596, respectively). The head and neck squamous cell carcinoma (HNSCC) cell line FaDu was obtained from Karl-Heinz Heider (Boehringer Ingelheim, Vienna, Austria)[16], and the HNSCC cell line UM-SCC-11B was obtained from Dr. T.E. Carey (Ann Arbor, MI)[17].

89Zr (T1/2 = 78.4 h, β+ = 22.6%; ~2.7 GBq/ml in 1 M oxalic acid) was produced by BV Cyclotron VU (Amsterdam, The Netherlands) by a (p,n) reaction on natural yttrium-89 (89Y) and isolated with a hydroxamate column [5].

Characterization of p-Isothiocyanatobenzyl-desferrioxamine (Df-Bz-NCS)

Synthesis of the new ligand 1-(4-isothiocyanatophenyl)-3-[6,17-dihydroxy-7,10,18,21-tetroxo-27-[N-acetylhydroxyamino)-6,11,17,22-tetraazaheptaeicosane)thiourea (p-isothiocyanato-benzyl-desferrioxamine; Df-Bz-NCS) was performed by Macrocyclics (Dallas, TX) as described before [18]. In short, Desferrioxamine B mesylate (Df; Desferal, Novartis, Basel) was dissolved in isopropanol/water while gently stirring. A chloroform solution of 1,4-phenylendiisothiocyanate and triethyl amine was then added and the reaction progress was monitored by reverse-phase HPLC. Upon completion, the reaction mixture was extracted with 0.1 M HCl. The lower organic layer was concentrated in vacuo to remove the chloroform but not the isopropanol. The remaining organic solution was purified by reverse-phase preparative HPLC using a water/acetonitrile gradient [Detector: UV/VIS at 275 nm. Column: Phenomenex Luna C18(2) (250 × 50 mm, 10 μm). Sample prep: Direct injection of the isopropanol solution. Mobile phase: 0–10 min 40/60 A/B; 10–15 min ramp 40/60 to 90/10 A/B; 15–25 min 90/10 A/B; A = CH3CN, B = H2O. Flow rate = 100 ml/min. Retention time of product was ~10 min. Desired fractions were placed at −20°C to precipitate the product. The final product was isolated by filtration as a white solid (41% yield).

Analytical data

1H NMR (D6-DMSO): δ 1.21 (m, −CH2, 6H), 1.38 (m, −CH2, 4H), 1.95 (s, −CH3, 3H), 2.27 (m, −CH2, 4H), 2.99 (m, CH2, 4H), 3.45 (m, CH2, 8H), 7.35 (d, 2,6-ArH, J = 8.9 Hz, 2H), 7.75 (d, 3,5 = ArH, J = 8.9 Hz, 2H), 7.75 (m, N-H, 2H), 7.88 (bs, N-H, 1H), 9.59 (m, N-OH, 4H). 13C NMR: δ 19.18 (CH3), 22.34, 22.35, 22.44, 24.88, 24.90, 24.94, 24.96, 24.98, 26.42, 26.88, 27.66, 28.78, 28.79, 28.83, 37.28, 37.92, 42.57, 42.60, 42.63, 45.67, 45.97, 121.92, 123.50, 124.98, 131.58, 138.17 (N=C=S), 169.00 (C=O), 170.20 (C=O), 170.84 (C=O), 179.02 (C=S). Elemental analysis calculated (%) for C33H52N8O8S2: C 52.64, H 6.96, N 14.88, S 8.52, found C 52.43, H 7.08, N 14.81, S 8.59. m/z: (ESI+); 775 (100% [M+Na]+), (ESI-); 751 (100% [M-H]). Chromatographic purity: >98% Detector: UV/VIS at 225 nm. Column: Restek Ultra IBD (100 × 4.6 mm, 3 μm, 100 A). Sample prep: a 1.0 mg/ml solution prepared in DMSO. Mobile phase: 0–10 min ramp 5/95 to 95/5 A/B; 10–15 min 95/5 A/B; A = 0.1% TFA in CH3CN, B = 0.1% TFA in H2O.

Preparation of 89Zr-labeled Df-Bz-NCS-mAb

cU36, cetuximab, or rituximab were premodified with Df-Bz-NCS (Fig. 1a). In short, while gently shaking, a three-fold molar excess of Df-Bz-NCS (in 20 μl DMSO) was added to the mAb (2–10 mg in 1 ml 0.1 M NaHCO3 buffer, pH 9.0), and incubated for 30 min at 37°C. Nonconjugated chelate was removed by size exclusion chromatography using a PD10 column (GE Healthcare Life Sciences) and 0.9% sodium chloride/gentisic acid 5 mg/ml (pH 5.0) as eluent. Subsequently, Df-Bz-NCS-mAb was labeled with 89Zr at room temperature in a volume of 2 ml for 60 min; to 200 μl 89Zr (37–250 MBq) solution 90 μl 2 M Na2CO3 were added, after 3 min 300 μl 0.5 M HEPES buffer (pH 7.0), 710 μl Df-Bz-NCS-mAb (1–2 mg) and 700 μl 0.5 M HEPES (pH 7.0) were added. Other pH values were obtained by adjusting the HEPES buffer to chosen pH values. Finally, 89Zr-Df-Bz-NCS-mAb was purified by size exclusion chromatography (PD10 column) using 0.25 M sodium acetate/gentisic acid 5 mg/ml buffer (pH 5.5) or 0.9% sodium chloride/gentisic acid 5 mg/ml (pH 5.0) as the mobile phase.
Fig. 1

Schematic representation of mAb modification with the new bifunctional chelate Df-Bz-NCS (1) and subsequent labeling with 89Zr (2) (a). The multi-step reference procedure using desferrioxamine B as starting ligand (b)

Preparation of 89Zr-labeled N-sucDf-mAb

As reference to the new method for 89Zr labeling, Df was also coupled to mAbs via the multi-step procedure as previously described by Verel et al. [5] (Fig. 1b). In short, the chelate Df was succinylated (N-sucDf), temporarily filled with stable iron [Fe(III)], and coupled to the lysine residues of the mAb (cU36 or cetuximab) by means of a tetrafluorophenol-N-sucDf ester. After removal of Fe(III) by transchelation to EDTA at 35°C, the premodified mAb was purified on a PD10 column. Approximately 1 N-sucDf moiety was coupled per mAb molecule. Subsequently, N-sucDf-mAb was labeled with 89Zr in 0.25 M HEPES buffer at pH 7.0; to 200 μl 89Zr (37–185 MBq) solution 90 μl 2 M Na2CO3 were added, after 3 min 300 μl 0.5 M HEPES buffer (pH 7.0), 710 μl N-SucDf-mAb (1–2 mg) and 700 μl 0.5 M HEPES (pH 7.0) were added. Finally, 89Zr-N-sucDf-mAb was purified on a PD10 column using 0.9% sodium chloride/gentisic acid 5 mg/ml (pH 5.0) or 0.25 M sodium acetate/gentisic acid 5 mg/ml buffer (pH 5.5) as the mobile phase.

Analyses

After each preparation of 89Zr-labeled Df-Bz-NCS-mAb or N-sucDf-mAb, the conjugates were analyzed by instant thin-layer chromatography (ITLC) for radiolabeling efficiency and radiochemical purity, and by high-performance liquid chromatography (HPLC) and sodium dodecyl sulfate-polyacrylamide gel electrophoresis (SDS-PAGE) followed by phosphor imager analyses for integrity, and by a cell-binding assay for immunoreactivity.

ITLC analyses of 89Zr-labeled N-sucDf-mAb or Df-Bz-NCS-mAb was performed on silica gel impregnated glass fiber sheets (Pall Corp., East Hills, NY). As the mobile phase, 0.02 M citrate buffer (pH 5.0) was used.

HPLC monitoring of the final products was performed on a Jasco HPLC system using a Superdex 200 10/300 GL size exclusion column (GE Healthcare Life Sciences). As eluent, a mixture of 0.05 M sodium phosphate and 0.15 M sodium chloride (pH 6.8) was used at a flow rate of 0.5 ml/min. Electrophoresis was performed on a Phastgel System (GE Healthcare Life Sciences) using preformed 7.5% SDS-PAGE gels under non-reducing conditions.

The immunoreactivity was determined by measuring binding of 89Zr-cU36, 89Zr-cetuximab, or 89Zr-rituximab (10,000 cpm/ml) to a serial dilution of 0.2% glutaraldehyde-fixed 11B cells or 2% paraformaldehyde-fixed A431, or Ramos cells, respectively, essentially as described by Lindmo et al. [19].

Determination of chelate-to-mAb ratio

The Df-Bz-NCS to mAb molar ratio was determined following a general method as described by Meares et al. [20]. In short, conjugates were labeled according to the aforementioned procedure with a known nanomolar excess of zirconium oxalate solution spiked with 89Zr.

In vitro stability

For assessment of the in vitro stability of 89Zr-Df-Bz-NCS-mAb in comparison with the reference conjugate 89Zr-N-sucDf-mAb, two sets of experiments were performed. In a first set, labeled mAbs were stored at 4°C (storage and transportation conditions) and room temperature in 0.9% NaCl/gentisic acid 5 mg/ml or 0.25 M sodium acetate/gentisic acid 5 mg/ml. Final activity concentration was between 30–40 MBq/ml, specific activity was between 67–86 MBq/mg mAb. At various time points, aliquots were taken and analyzed by ITLC, SDS-PAGE, and HPLC.

In a second set, purified radiolabeled mAbs were added to freshly prepared human serum (1:4 v/v dilution; sodium azide added to 0.02%) at a final concentration of the radiolabeled conjugates of ~1.3 nmol/ml and ~45 MBq/ml. The samples were incubated at 37°C in a CO2-enriched atmosphere (5% CO2). At various time points, aliquots were taken and analyzed by TLC, SDS-PAGE, and HPLC.

Evaluation of in vivo biodistribution

For assessment of biodistribution and the in vivo stability of the new 89Zr-Df-Bz-NCS-mAb conjugate in comparison with the established 89Zr-N-sucDf-mAb conjugate, two sets of experiments were performed with nude mice bearing subcutaneously implanted human xenografts of the HNSCC line FaDu or the vulvar tumor line A431 at two lateral sides. In one experiment, the moderately internalizing cU36 mAb was tested; in the other, the extensively internalizing mAb cetuximab [21]. Female mice (HSD:Athymic Nude-Foxn1 nu , 21–31 g; Harlan) were 8 to 10 weeks old at the time of the experiments. All animal experiments were done according to the NIH Principles of Laboratory Animal Care and Dutch national law (“Wet op de dierproeven”, Stb 1985, 336).

In a first experiment, mice bearing FaDu xenografts (two groups of n = 8) were injected intravenously (i.v.) with either 89Zr-Df-Bz-NCS-cU36 (0.38 ± 0.01 MBq) or the reference compound 89Zr-N-sucDf-cU36 (0.38 ± 0.01 MBq). Unlabeled mAb cU36 was added to the injection mixture to bring the total mAb dose to 100 μg per mouse. At 72 and 144 h post-injection, four mice of each group were anesthetized, bled, killed, and dissected. After blood, tumor, and normal tissues had been weighed, the amount of radioactivity in each sample was measured in a gamma counter. Radioactivity uptake was calculated as the percentage of the injected dose per gram of tissue (%ID/g).

In a second experiment, mice bearing A431 xenografts (two groups of n = 16) were injected i.v. with either 89Zr-Df-Bz-NCS-cetuximab (0.24 ± 0.01 MBq) or the reference compound 89Zr-N-sucDf-cetuximab (0.24 ± 0.01 MBq). Unlabeled cetuximab was added to the injection mixture to bring the total mAb dose to 500 μg per mouse. At 24, 48, 72, and 120 h post-injection, four mice of each group were anesthetized, bled, killed, and dissected, with further processing according to the above procedure.

PET study

PET imaging was performed on a double-crystal-layer HRRT PET scanner (Siemens/CTI), a dedicated small animal and human brain scanner, as described earlier [7, 22]. FaDu xenograft-bearing nude mice (two groups of n = 3) were anesthetized by inhalation of 2% isoflurane, injected with either 4.12 ± 0.04 MBq 89Zr-Df-Bz-NCS-cU36 (~200 μg mAb) or 4.03 ± 0.09 MBq 89Zr-N-sucDf-cU36 (~200 μg mAb) via the retroorbital plexus, and scanned at 72 h post-injection.

Transmission scans for attenuation and scatter correction were routinely obtained with each scan in two-dimensional mode using a single point 137Cs source. Three-dimensional emission scans were acquired in 64-bit list mode during 60 min using a 400–650 keV window. The 64-bit list mode file was first converted into a single-frame histogram using a span of nine, and subsequently reconstructed using a 3D ANW-OSEM reconstruction algorithm with two iterations and 16 subsets and a matrix size of 256 × 256, including corrections for normalization, decay, and dead time. For visualization of the images, Amide’s A Medical Imaging Data Examiner (AMIDE) was used, freely available for download online [23]. Immediately after the PET scan the animals were killed, and blood, tumors, major organs, and tissues were collected, weighed, and counted in a gamma-counter.

Statistical analyses

Differences in tissue uptake between injected conjugates were statistically analyzed for each time point with SPSS 15.0 software using Student’s t-test for unpaired data. Two-sided significance levels were calculated and P < 0.01 was considered statistically significant.

Results

Preparation of 89Zr-Df-Bz-NCS-mAb

89Zr-Df-Bz-NCS-mAb was prepared according to the chemical route as shown in Fig. 1a. First, Df-Bz-NCS is coupled to the lysine groups of a mAb. Conjugation conditions selected for this step comprised the addition of a three-fold molar excess of Df-Bz-NCS to the mAb solution (13–66 nmol mAb), a reaction pH of 9.0, and incubation for 30 min at 37°C. These conditions resulted in a reproducible chelate:mAb substitution ratio of about 1.5:1, irrespective cU36, cetuximab or rituximab was used, as assessed by trace labeling with 89Zr in a standard solution of Zr-oxalate.

In the next step, Df-Bz-NCS-mAbs were labeled with 89Zr in HEPES buffer (final concentration 0.25 M). After 60 min incubation at room temperature at pH 6.8–7.2, the amount of 89Zr trans-chelated from oxalate to Df-Bz-NCS-mAb was always more than 85% (mean, 91.9 ± 4.6%). The time courses of 89Zr-complexation of mAb cU36 conjugated with Df-Bz-NCS at different pHs are shown in Fig. 2. Labeling efficiency was distinctly higher at pH 6.8 and 7.2 than at pH 6.0, 6.2, and 7.4.
Fig. 2

Time course of 89Zr complexation of mAb cU36 conjugated with Df-Bz-NCS at different pH and at room temperature

Labeling of mAb cU36, cetuximab, or rituximab modified with Df-Bz-NCS resulted in overall yields after purification of always >80% (mean, 87.0 ± 4.6%). The radiochemical purity was always >95% (mean, 97.5 ± 0.7%; determined with ITLC and confirmed by HPLC). The immunoreactive fraction of the different 89Zr-Df-Bz-NCS-mAb preparations ranged from 84.1 to 96.8% at the highest cell concentration, and was similar to those of their 131I-labeled counterparts (data not shown). HPLC and SDS-PAGE analyses revealed optimal integrity of the different mAbs after modification and labeling with 89Zr (data not shown).

Evaluation of the in vitro stability

89Zr-labeled Df-Bz-NCS-mAb and N-sucDf-mAb conjugates were both stored in 0.9% NaCl/gentisic acid 5 mg/ml and in 0.25 M sodium acetate/gentisic acid 5 mg/ml at 4°C over several days to evaluate the in vitro stability. To anticipate effects of insufficient cooling, the conjugates were also analyzed after storage at room temperature (21°C). Storing the 89Zr-Df-Bz-NCS-mAb conjugates in 0.25 M sodium acetate/gentisic acid 5 mg/ml buffer (pH 5.5) at 4°C gave the best results; only 0.9 ± 0.4% of the initially bound 89Zr was dissociated from the mAb after 48 h, and 4.1 ± 1.3% after 144 h. Upon storage in the same buffer at room temperature (21°C), 6.1 ± 1.4% and 10.5 ± 2.1% was dissociated after 48 h and 144 h, respectively. Also upon storage in 0.9% NaCl/gentisic acid 5 mg/ml (pH 5.0) at 4°C the radioimmunoconjugates remained reasonably stable, showing 13.2 ± 2.8% dissociation after 144 h. However, storage in the same buffer at room temperature resulted in rapid release of radioactivity from the conjugate, 48.4 ± 5.7%. The corresponding 89Zr-N-SucDf-mAb conjugates remained very stable, showing less than 5% release after 144 h under all conditions investigated.

The in vitro stability data for the 89Zr-Df-Bz-NCS-cU36 and 89Zr-N-sucDf-cU36 conjugates, when incubated in freshly prepared human serum at 37°C, showed that loss of 89Zr from both conjugates over a 7-day period was very small. The percentages dissociated at day 3 were 2.3 ± 0.1% for the Df-Bz-NCS conjugate and 3.4 ± 0.6% for the N-sucDf conjugate, and at day 7 were 4.0 ± 0.6% for the Df-Bz-NCS conjugate and 4.7 ± 0.5% for the N-sucDf conjugate, respectively.

Evaluation of the in vivo biodistribution

Two sets of biodistribution studies were performed. In the first experiment, 89Zr-Df-Bz-NCS-cU36 and the reference compound 89Zr-N-sucDf-cU36 were injected into FaDu-bearing nude mice. At 72 and 144 h after injection, the average %ID/g of tumor, blood, normal tissue, and gastrointestinal contents was determined (Fig. 3). No significant differences in the biodistribution of both conjugates were found.
Fig. 3

Biodistribution of 89Zr-Df-Bz-NCS-cU36 (black bars) and 89Zr-N-sucDf-cU36 (white bars) in FaDu tumor-bearing nude mice at 72 h (a) and 144 h (b) after injection. Total administered mAb dose: 100 μg. Mean (%ID/g) ± SD at each time point after injection (n = 4 animals per time point for each conjugate)

Only a minor proportion of mAb cU36 internalizes after binding to its target antigen, therefore in the second biodistribution study, the anti-EGFR mAb cetuximab was chosen because of the high rate of internalization. 89Zr-Df-Bz-NCS-cetuximab and the reference compound 89Zr-N-sucDf-cetuximab were injected into A431-bearing nude mice. At 24, 48, 72, and 120 h after injection, the average %ID/g of tumor, blood, normal tissue, and gastrointestinal contents was determined (Fig. 4). The overall biodistribution of the two radioimmunoconjugates was very similar, showing no significant differences except for blood levels at 24 and 120 h after injection (Fig. 4; significant differences (P < 0.01) are indicated with an asterisk). The 89Zr-Df-Bz-NCS-cetuximab tumor accumulation ranged from 15.6 ± 4.4 %ID/g to 23.1 ± 7.1 %ID/g and the 89Zr-N-sucDf-cetuximab accumulation from 12.3 ± 3.2 %ID/g to 25.3 ± 6.1 %ID/g, in the time period between 24 and 120 h post-injection.
Fig. 4

Biodistribution of 89Zr-Df-Bz-NCS-cetuximab (black bars) and 89Zr-N-sucDf-cetuximab (white bars) in A431 tumor-bearing nude mice at 24 h (a), 48 h (b), 72 h (c), and 120 h (d) after injection. Total administered mAb dose: 500 μg. Mean (%ID/g) ± SD at each time point after injection (n = 4 animals per time point for each conjugate). Significant differences (P < 0.01) in biodistribution between both radioimmunoconjugates are marked with an asterisk

PET study

To exclude 89Zr uptake in tissues not evaluated in the biodistribution experiments, a PET imaging study was performed. Representative PET images of FaDu xenograft-bearing nude mice at 72 h after injection with 89Zr-Df-Bz-NCS-cU36 or 89Zr-N-sucDf-cU36 are shown in Fig. 5a or b, respectively. Immuno-PET with both radioimmunoconjugates revealed clear delineation of the tumors (arrows), whereas no prominent uptake of radioactivity was observed in other tissues, except for the liver in which 89Zr residualizes after catabolism of the conjugates.
Fig. 5

HRRT PET images (coronal slices) of two different FaDu xenograft-bearing nude mice at 72 h after injection with 89Zr-Df-Bz-NCS-cU36 (a) or with 89Zr-N-sucDf-cU36 (b). Slices from ventral (left) to dorsal (right). Images demonstrate high level of radiolabeled antibody accumulating in the tumor (arrows point to flank tumors) and low levels of tracer uptake in nontarget tissues

Discussion

Immuno-PET, the tracking and quantification of mAbs and mAb-fragments with PET in vivo, is an emerging novel option to improve diagnostics and to guide mAb-based therapy [2, 3, 4]. Availability of positron emitters with a proper half-life, simple and robust radiochemistry, and advanced animal as well as clinical PET and PET-CT scanners, is crucial in these developments.

In the present report, we have described a method for labeling mAbs with the long-lived positron emitter 89Zr using the novel bifunctional chelate Df-Bz-NCS. 89Zr has attractive characteristics for immuno-PET with intact mAbs, especially when these mAbs become internalized upon binding to their cellular target. Radioimmunoconjugates produced by this method were stable in storage buffer as well as in human serum in vitro. Biodistribution and imaging experiments showed high and selective accumulation in tumors in nude mice.

The chelate Df has frequently been used for radiolabeling of mAbs in the past, but these conjugates have never been evaluated clinically [24, 25, 26, 27]. More recently, Verel et al. [5] developed a sophisticated method for stable coupling of 89Zr to mAbs using a succinylated-derivative of Df, which was used as the reference method in the present study (Fig. 1b). 89Zr-labeled mAbs prepared according to this method have been successfully tested preclinically and clinically [6, 7, 8, 9, 10, 11, 12, 13]. In the past and ongoing clinical studies, neither adverse reactions nor significant changes in blood and urine values were observed after injection of these conjugates. Moreover, no antibody responses directed against the Df chelate were observed, indicating that its immunogenicity is low [8]. These data illustrate that 89Zr-labeled Df-mAbs can be used safely in patients. However, a shortcoming of the aforementioned method is that the multi-step procedure is relatively complicated and time-consuming, and therefore challenging with respect to GMP compliance.

Now we introduce p-isothiocyanatobenzyl-derivative of Df (Df-Bz-NCS) that might provide an efficient and rapid preparation of 89Zr-labeled mAbs. Bifunctional chelates bearing isothiocyanate as the reactive group for conjugation to mAbs or other biologicals are frequently used [28]. The isothiocyanate group of the bifunctional chelate forms a thiourea bond with a primary amine of the protein or mAb.

Coupling of Df-Bz-NCS to mAbs was very efficient. A reproducible chelate:mAb substitution ratio of 1.5:1 was obtained in a typical conjugation reaction with several different mAbs using only a three-fold molar excess of Df-Bz-NCS. The chelate:mAb substitution ratio was chosen to be kept below 2 to avoid alteration of the pharmacokinetics and immunoreactivity of the mAb [29, 30].

The rate of complexation of 89Zr into the Df-Bz-NCS conjugate was very similar as compared to the reference N-sucDf conjugate reported by Verel et al. [5], indicating that the different chemical linkages (e.g., = S instead of =O group in the side chain, which might be involved in 89Zr4+ coordination) have no influence on the complexation rate. At the pH-optimum, almost quantitative complexation was reached after 30 min at room temperature. The resulting radioimmunoconjugates showed no impairment of immunoreactivity and integrity of the mAbs.

Radioimmunoconjugates were stored in various media to find the optimal conditions for storage and transportation over several days. The 89Zr-Df-Bz-NCS-mAb can best be stored at 4°C in sodium acetate buffer in the presence of the antioxidant gentisic acid. Under these conditions, only a minor portion of the initially bound 89Zr was dissociated from the mAb after 144 h. The need for protection of the radioimmunoconjugate against radiation damage during storage has been shown in previous studies [5, 31]. The presence of the antioxidant ascorbic acid during storage of high-dose 90Y— or 131I-labeled mAbs proved to be beneficial, however, ascorbic acid cannot be used during storage of 89Zr-labeled Df-mAbs, because this reagent causes detachment of 89Zr from Df by reducing Zr4+ to Zr2+ [5].

Under certain storage conditions, the new 89Zr-Df-Bz-NCS conjugate is slightly less stable than the reference radioimmunoconjugate, and it is important to be aware of this. Especially the presence of Cl--ions in the storage buffer impaired the integrity of the radioimmunoconjugates, most likely due to the radiation-induced formation of OCl-ions reacting with the SH-group of the enolised thiourea-unit. The thus formed intermediary sulphenyl chloride bonds, and sulphonyl chloride bonds arising upon further oxidation, are known to undergo a series of reactions, among which are coupling reactions and cleavage of methionyl peptide bonds. ITLC data also indicated that most of the deterioration is not detachment of 89Zr from the Df-chelate itself, but disruption of the Zr-Df unit.

The in vitro stability of the 89Zr-Df-Bz-NCS conjugate and the 89Zr-N-sucDf conjugate was also compared in freshly prepared human serum at 37°C. The stability of both conjugates under these conditions was very comparable and high, showing less than 4.7% release after a 7-day incubation period. Serum acts as an oxidisable scavenger and protects against directs hits to the mAb molecule, minimizing the radiation-induced deterioration of the mAb. Comparable in vitro stability data of 89Zr-N-sucDf conjugates were previously reported by our group [21].

To investigate whether the new linker used for coupling of Df to the mAbs affects the biodistribution properties in mice, two sets of biodistribution experiments were performed. In the first experiment, the biodistribution of 89Zr-Df-Bz-NCS-cU36 and the reference compound 89Zr-N-sucDf-cU36 was compared in FaDu-bearing nude mice. In this model, no significant differences in the biodistribution between both conjugates were found. However, only a minor proportion of mAb cU36 internalizes after binding to its target antigen, therefore in the second biodistribution study the anti-EGFR mAb cetuximab was chosen because of the high rate of internalization [21]. Also in this model, a very similar biodistribution was found. Nevertheless, some significant differences were found, e.g. blood levels at 24 and 120 h after injection. Overall, both studies indicate that the different linkers used do not affect the biodistribution properties in nude mice. Moreover, none of the normal organs showed an adverse high uptake. The aforementioned results were confirmed in comparative immuno-PET studies with both chelates. PET images did not show accumulation of radioactivity in bone, which would have been indicative of free 89Zr.

Conclusions

In the present study we evaluated the newly developed bifunctional chelate Df-Bz-NCS for radiolabeling of mAbs with 89Zr for PET-imaging. The two-step procedure allows efficient and rapid preparation of 89Zr-labeled mAbs. Resulting 89Zr-Df-Bz-NCS-mAb conjugates appeared optimal with respect to radiochemical purity, integrity, and immunoreactivity. Furthermore, the radioimmunoconjugates were stable in serum in vitro and comparative biodistribution and imaging experiments showed high and selective accumulation in tumors in nude mice. Special emphasis should be given to the storage conditions. The recent commercialization of 89Zr and the availability of an easy-to-use radiolabeling strategy using Df-Bz-NCS allow further exploration of 89Zr-immuno-PET as an imaging tool for the selection of high potential candidate mAbs for therapy as well as for the selection of patients with the highest chance of benefit from mAb-based therapy [2].

Notes

Acknowledgments

This project was financially supported by the Dutch Technology Foundation (STW, grants VBC.6120 and 10074) and partly supported by the European Union FP7, ADAMANT. The publication reflects only the authors’ views. The European Commission is not liable for any use that may be made of the information contained. The authors thank the technical staff of BV Cyclotron VU and the Radionuclide Centre for supply and processing of 89Zr, Marc Huisman for PET analyses, and Marijke Stigter-van Walsum for technical assistance with animal studies.

Conflict of interest

none.

Open Access

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References

  1. 1.
    Carter PJ. Potent antibody therapeutics by design. Nat Rev Immunol. 2006;6:343–57.CrossRefPubMedGoogle Scholar
  2. 2.
    van Dongen GAMS, Visser GWM, Lub-de Hooge MN, de Vries EG, Perk LR. Immuno-PET: a navigator in monoclonal antibody development and applications. Oncologist. 2007;12:1379–89.CrossRefPubMedGoogle Scholar
  3. 3.
    Wu AM. Antibodies and antimatter: the resurgence of immuno-PET. J Nucl Med. 2009;50:2–5.CrossRefPubMedGoogle Scholar
  4. 4.
    Nayak TK, Brechbiel MW. Radioimmunoimaging with longer-lived positron-emitting radionuclides: potentials and challenges. Bioconjug Chem. 2009;20:825–41.CrossRefGoogle Scholar
  5. 5.
    Verel I, Visser GWM, Boellaard R, Stigter-van Walsum M, Snow GB, van Dongen GAMS. 89Zr immuno-PET: comprehensive procedures for the production of 89Zr-labeled monoclonal antibodies. J Nucl Med. 2003;44:1271–1281.PubMedGoogle Scholar
  6. 6.
    Dijkers E, Lub-de Hooge MN, Kosterink JG, et al. Characterization of 89Zr-trastuzumab for clinical HER2 immunoPET imaging. J Clin Oncol. 2007;25:3508. (meeting abstracts).Google Scholar
  7. 7.
    Perk LR, Stigter-van Walsum M, Visser GWM, et al. Quantitative PET imaging of Met-expressing human cancer xenografts with 89Zr-labelled monoclonal antibody DN30. Eur J Nucl Med Mol Imaging. 2008;35:1857–67.CrossRefPubMedGoogle Scholar
  8. 8.
    Borjesson PKE, Jauw YWS, Boellaard R, et al. Performance of immuno-positron emission tomography with zirconium-89-labeled chimeric monoclonal antibody U36 in the detection of lymph node metastases in head and neck cancer patients. Clin Cancer Res. 2006;12:2133–40.CrossRefPubMedGoogle Scholar
  9. 9.
    Nagengast WB, de Vries EG, Hospers GA, et al. In vivo VEGF imaging with radiolabeled bevacizumab in a human ovarian tumor xenograft. J Nucl Med. 2007;48:1313–19.CrossRefPubMedGoogle Scholar
  10. 10.
    Verel I, Visser GWM, Boerman OC, et al. Long-lived positron emitters zirconium-89 and iodine-124 for scouting of therapeutic radioimmunoconjugates with PET. Cancer Biother Radiopharm. 2003;18:655–61.CrossRefPubMedGoogle Scholar
  11. 11.
    Verel I, Visser GWM, Boellaard R, et al. Quantitative 89Zr immuno-PET for in vivo scouting of 90Y-labeled monoclonal antibodies in xenograft-bearing nude mice. J Nucl Med. 2003;44:1663–70.PubMedGoogle Scholar
  12. 12.
    Brouwers A, Verel I, Van Eerd J, et al. PET radioimmunoscintigraphy of renal cell cancer using 89Zr-labeled cG250 monoclonal antibody in nude rats. Cancer Biother Radiopharm. 2004;19:155–63.CrossRefPubMedGoogle Scholar
  13. 13.
    Perk LR, Visser OJ, Stigter-van Walsum M, et al. Preparation and evaluation of 89Zr-Zevalin for monitoring of 90Y-Zevalin biodistribution with positron emission tomography. Eur J Nucl Med Mol Imaging. 2006;33:1337–45.CrossRefPubMedGoogle Scholar
  14. 14.
    Mendelsohn J, Baselga J. Epidermal growth factor receptor targeting in cancer. Semin Oncol. 2006;33:369–85.CrossRefPubMedGoogle Scholar
  15. 15.
    Schrijvers AH, Quak JJ, Uyterlinde AM, et al. MAb U36, a novel monoclonal antibody successful in immunotargeting of squamous cell carcinoma of the head and neck. Cancer Res. 1993;53:4383–90.PubMedGoogle Scholar
  16. 16.
    Rangan SR. A new human cell line (FaDu) from a hypopharyngeal carcinoma. Cancer. 1972;29:117–21.CrossRefPubMedGoogle Scholar
  17. 17.
    Welters MJ, Fichtinger-Schepman AM, Baan RA, et al. Relationship between the parameters cellular differentiation, doubling time and platinum accumulation and cisplatin sensitivity in a panel of head and neck cancer cell lines. Int J Cancer. 1997;71:410–15.CrossRefPubMedGoogle Scholar
  18. 18.
    Bifunctional hydroxamic acid ligands and method of synthesis. Jurek P. PCT WO 2008/124467Google Scholar
  19. 19.
    Lindmo T, Boven E, Cuttitta F, Fedoroko J, Bunn PA Jr. Determination of the immunoreactive fraction of radiolabeled monoclonal antibodies by linear extrapolation to binding at infinite antigen excess. J Immunol Methods. 1984;72:77–89.CrossRefPubMedGoogle Scholar
  20. 20.
    Meares CF, McCall MJ, Reardan DT, Goodwin DA, Diamanti CI, McTique M. Conjugation of antibodies with bifunctional chelating agents: isothiocyanate and bromoacetamide reagents, methods of analysis, and subsequent addition of metal ions. Anal Biochem. 1984;142:68–78.CrossRefPubMedGoogle Scholar
  21. 21.
    Perk LR, Visser GWM, Vosjan MJWD, et al. 89Zr as a PET surrogate radioisotope for scouting biodistribution of the therapeutic radiometals 90Y and 177Lu in tumor-bearing nude mice after coupling to the internalizing antibody cetuximab. J Nucl Med. 2005;46:1898–06.PubMedGoogle Scholar
  22. 22.
    de Jong HWAM, van Velden FHP, Kloet RW, Buijs FL, Boellaard R, Lammertsma AA. Performance evaluation of the ECAT HRRT: an LSO-LYSO double-layer high-resolution, high-sensitivity scanner. Phys Med Biol. 2007;52:1505–26.CrossRefPubMedGoogle Scholar
  23. 23.
    Loening AM, Gambhir SS. AMIDE: a free software tool for multimodality medical image analysis. Mol Imaging. 2003;2:131–37.CrossRefPubMedGoogle Scholar
  24. 24.
    Yokoyama A, Ohmomo Y, Horiuchi K, et al. Deferoxamine, a promising bifunctional chelating agent for labeling proteins with gallium: Ga-67 DF-HSA: concise communication. J Nucl Med. 1982;23:909–14.PubMedGoogle Scholar
  25. 25.
    Koizumi M, Endo K, Kunimatsu M, et al. 67Ga-labeled antibodies for immunoscintigraphy and evaluation of tumor targeting of drug-antibody conjugates in mice. Cancer Res. 1988;48:1189–94.PubMedGoogle Scholar
  26. 26.
    Pochon S, Buchegger F, Pelegrin A, et al. A novel derivative of the chelon desferrioxamine for site-specific conjugation to antibodies. Int J Cancer. 1989;43:1188–94.CrossRefPubMedGoogle Scholar
  27. 27.
    Meijs WE, Haisma HJ, Klok RP, et al. Zirconium-labeled monoclonal antibodies and their distribution in tumor-bearing nude mice. J Nucl Med. 1997;38:112–18.PubMedGoogle Scholar
  28. 28.
    Liu S. Bifunctional coupling agents for radiolabeling of biomolecules and target-specific delivery of metallic radionuclides. Adv Drug Deliv Rev. 2008;60:1347–70.CrossRefPubMedGoogle Scholar
  29. 29.
    van Gog FB, Visser GWM, Klok RP, van der Schors R, Snow GB, van Dongen GAMS. Monoclonal antibodies labeled with rhenium-186 using the MAG3 chelate: relationship between the number of chelated groups and biodistribution characteristics. J Nucl Med. 1996;37:352–62.PubMedGoogle Scholar
  30. 30.
    Kukis DL, DeNardo GL, DeNardo SJ, et al. Effect of the extent of chelate substitution on the immunoreactivity and biodistribution of 2IT-BAT-Lym-1 immunoconjugates. Cancer Res. 1995;55:878–84.PubMedGoogle Scholar
  31. 31.
    Chakrabarti MC, Le N, Paik CH, De Graff WG, Carrasquillo JA. Prevention of radiolysis of monoclonal antibody during labeling. J Nucl Med. 1996;37:1384–88.PubMedGoogle Scholar

Copyright information

© The Author(s) 2009

Authors and Affiliations

  • Lars R. Perk
    • 1
  • Maria J. W. D. Vosjan
    • 1
  • Gerard W. M. Visser
    • 2
  • Marianne Budde
    • 1
  • Paul Jurek
    • 3
  • Garry E. Kiefer
    • 3
  • Guus A. M. S. van Dongen
    • 1
    • 2
    • 1
    Email author
  1. 1.Department of Otolaryngology/Head and Neck SurgeryVU University Medical CenterAmsterdamThe Netherlands
  2. 2.Nuclear Medicine & PET ResearchVU University Medical CenterAmsterdamThe Netherlands
  3. 3.Macrocyclics Inc.DallasUSA

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