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Single wall carbon nanotube (SWCNT) constructs were covalently appended with radiometal-ion chelates (1,4,7,10-tetraazacyclododecane-1,4,7,10-tetraacetic acid [DOTA] or desferrioxamine B [DFO]) and the tumor neovascular-targeting antibody E4G10. The E4G10 antibody specifically targeted the monomeric vascular endothelial-cadherin (VE-cad) epitope expressed in the tumor angiogenic vessels. The construct specific activity and blood compartment clearance kinetics were significantly improved relative to corresponding antibodyalone constructs. We performed targeted radioimmunotherapy with a SWCNT-([225Ac]DOTA) (E4G10) construct directed at the tumor vasculature in a murine xenograft model of human colon adenocarcinoma (LS174T). The specific construct reduced tumor volume and improved median survival relative to controls. We also performed positron emission tomographic (PET) radioimmunoimaging of the tumor vessels with a SWCNT-([89Zr]DFO)(E4G10) construct in the same murine LS174T xenograft model and compared the results to appropriate controls. Dynamic and longitudinal PET imaging of LS174T tumor-bearing mice demonstrated rapid blood clearance (<1 hour) and specific tumor accumulation of the specific construct. Incorporation of the SWCNT scaffold into the construct design permitted us to amplify the specific activity to improve the signal-to-noise ratio without detrimentally impacting the immunoreactivity of the targeting antibody moiety. Furthermore, we were able to exploit the SWCNT pharmacokinetic (PK) profile to favorably alter the blood clearance and provide an advantage for rapid imaging. Near-infrared three-dimensional fluorescent-mediated tomography was used to image the LS174T tumor model, collect antibody-alone PK data, and calculate the number of copies of VE-cad epitope per cell. All of these studies were performed as a single administration of construct and were found to be safe and well tolerated by the murine model. These data have implications that support further imaging and radiotherapy studies using a SWCNT-based platform and focusing on the tumor vessels as the target.
Advances in cancer diagnosis and therapy require improvements in the agents used to image and treat disease. Valuable modifications include those that enable these agents to specifically target disease, increase signal-to-noise, rapidly clear from the blood, and incorporate multiple imaging and therapeutic modalities. Carbon nanomaterials are being investigated as delivery platforms for diagnostic and therapeutic cargoes to target disease.1,2 Pharmacokinetic (PK) studies of soluble, covalently-functionalized, radiolabeled carbon nanotubes (CNTs) have demonstrated rapid blood compartment clearance, high specific activity (SA), multimodal imaging capability, renal elimination, and tumor-specific accumulation in vivo.3–6 Implementation of an imaging and therapeutic drug construct that is designed to target, report location, and irradiate the tumor vessels is a key strategic modification that will take advantage of the single wall CNT (SWCNT)-based construct’s chemical, radiochemical, and PK properties.
Many cancers are characterized by an extensive angiogenic, aberrant vascular network that supports the tumor proliferation and survival. The endothelial vessels in tumors often do not exhibit the same organizational hierarchy of arterioles, capillaries, and venules present in normal tissue. Instead, tumor vessels are tortuous and have abnormal component and structural composition. Endothelial cells in these tumors are inefficiently and irregularly joined with holes, gaps, and defects; pericytes are absent or loosely associated with vessels; and basement membranes are inefficiently applied relative to typical normal tissues. The pore diameters of tumor typically range from 40 to 80 nm. Large interendothelial junctions in cancerous tissue may be as large as 500 nm, whereas in healthy tissue, these junctions are ~8 nm.7 Angiogenic endothelial cells express the monomeric vascular endothelial-cadherin (VE-cad) epitope on the cell surface that upon dimerizing with another monomeric copy of VE-cad on an adjoining cell surface leads to the formation of tight adherens junctions between the cells.8–12 The antibody E4G10 binds only to the monomeric VE-cad and not to the homodimeric form (the binding region is masked in the homodimers that form the tight cell–cell contacts), thus conferring the specificity for targeting angiogenic and poorly joined endothelial cells in vivo while not binding to normal endothelium or the LS174T tumor.
The alpha particle-emitting radionuclide actinium-225 (225Ac; t1/2 = 10 days) attached to monoclonal antibodies (immunoglobulin [Ig]G) has been used as the therapeutic effector moiety in a number of preclinical studies13–18 and is currently in clinical use.19–21 Alpha particles are charged helium nuclei that travel ~50–80 μm, which is similar to the dimensions of vessels within a tumor. The alpha particle track lengths appropriately match the vessel dimensions, and a single traversal through a cell of a high linear energy transfer (LET) alpha particle can be acutely cytotoxic.22,23 Typical tumor vasculature is <100 μm in diameter, and smaller vessels are <10 μm in diameter. In addition, individual alpha particles are able to kill a target cell due to their deposition of 5–8 MeV in a short ionizing track that is several cell diameters in length.23 This highly concentrated field of ionizing radiation may also irradiate the cancer stem cell population that can be found in the adjacent perivascular niche of some tumors.24–26 Alpha particles are very potent cytotoxic agents in proximity to the targeted tissue but will largely spare normal tissue; it is this characteristic that offers clear advantages to other known forms of radiation as a means of selective cell killing. We have previously demonstrated the utility of 225Ac-radiolabeled E4G10 constructs to target and irradiate tumor vascular endothelium in animal models, improve survival, control tumor growth, and normalize the vessels27 and also the ability of the construct to target and eradicate bone marrow-derived endothelial progenitors.28
Zirconium-89 (89Zr) is now being developed as one of the most promising new immuno-positron emission tomography (PET) agents for in vivo imaging of cancer.29–34 PET is based on coincidence detection of a positron-emitting radionuclide from 2 coincident 511 keV annihilation photons emitted simultaneously in opposite directions.35 The clinical use of PET has emerged as an important diagnostic imaging modality for humans because it provides extremely sensitive, quantitative, and functional information that is different from the information obtainable with other largely anatomical imaging modalities.35 The physical decay properties of 89Zr (t1/2 = 78.41 hours; electron capture = 76.6%; β+ = 22.3%) are well suited for use in the design of imaging agents with extended PK profiles. Recently, reported improvements in the separation chemistry of 89Zr from the yttrium-89 (89Y) target material have yielded a facile process for production of clinical-grade, high SA 89Zr using a small cyclotron.30 This process should lead to more widespread use of this radionuclide.
The rationale for using SWCNTs as the scaffold in our construct design is the following: SWCNTs are made almost entirely of carbon, are nonimmunogenic, and can be chemically modified.36–38 The commercially available SWCNTs have a diameter of 1–2 nm and lengths of 100–1,000 nm. Thus, SWCNTs have extremely high aspect ratios with estimated surface areas of 1,600 m2/g. On the atomic level, SWCNTs have highly regular structures with defined periodicity. For every 100 nm of length, a SWCNT can have up to 12,200 carbon atoms and weighs 150,000 Da, providing numerous sites (typically 1 in 95 carbons was modified) for chemical modifications and anchoring chemical, biological, and radionuclide moieties.3–6 SWCNTs that have been chemically functionalized with sidewall amino groups exhibit aqueous solubility and reactivity towards a variety of reagents under mild bioconjugation conditions.3–6,36–39 The SWCNTs appended with amines and the metal-ion chelate 1,4,7,10-tetraazacyclododecane-1,4,7,10-tetraacetic acid (DOTA) were water soluble (~20 g/L) and studied in vivo in animal models.3–6 Our data showed that these SWCNTs rapidly (t1/2 < 1 hour) cleared the blood and prototype SWCNT constructs (diameter = ~1 nm; length = ~300 nm; moleculer weight = ~500 kD) were predominantly eliminated intact within minutes via glomerular filtration through the renal pathway. Renal excretion was found to be facilitated by the high aspect ratio of SWCNT, which confers lower rotational diffusivity; thus, the CNT tends to orient with the blood flow allowing easy access to the glomerular pores.6 Other recent work described the enzymatic degradation of functionalized SWCNT in vitro and in vivo, offering the potential for metabolic decomposition of CNT drug constructs.40–43 Further, toxicity studies have confirmed the safe in vivo use of functionalized SWCNT.44–47 Taken together, these data on renal elimination, enzymatic degradation, and lack of toxicity support continued investigation of SWCNT as a platform in drug development.
We hypothesize that CNT constructs can be covalently multifunctionalized with copies of targeting moieties and different reporting and therapeutic radionuclides and, thereby, increase signal-to-noise ratio and be used to image tumor vessels and improve the therapeutic index. The underlying rationale for this approach is that we are specifically targeting the aberrant and angiogenic tumor vessels and delivering a dose of short range (1–4 cell diameters), high energy (several million electron volts) cytotoxic alpha particles to the targeted area. In addition, we will report the location of the drug construct. This approach is novel because it will examine the attributes of targeted radioimmunotherapy (RIT) with alpha particle generators, sensitive and quantitative PET imaging, and the specificity of the targeting E4G10 antibody in combination with the unique nanomaterial properties of SWCNT.
Athymic nude mice (NCr nu/nu, male), 4–12 weeks of age, were obtained from Taconic, Germantown, NY, USA. For all in vivo experiments, housing and care were in accordance with the Animal Welfare Act and the Guide for the Care and Use of Laboratory Animals. The animal use protocols were approved by the Institutional Animal Care and Use Committee, Memorial Sloan-Kettering Cancer Center. Human LS174T cells (human colon adenocarcinoma) were expanded in Dulbecco–Vogt Modified Eagle’s media supplemented with glucose, nonessential amino acids, l-glutamine, and 10% fetal bovine serum in an atmosphere of 5% CO2 and air at 37°C. Cells were harvested and mixed with MatrigelTM (BD Biosciences, Palo Alto, CA, USA), and 0.1 mL of ~2–3E6 cells were injected subcutaneously into the right hind flank of each animal.
SWCNTs (Nanolab, Newton, MA, USA) were covalently amine functionalized as described previously.3–6,36–39 The SWCNT-NH2 product was purified from carbonaceous impurities using a C18 Sep-Pak® (Waters, Milford, MA, USA) and analyzed by high-performance liquid chromatography (HPLC), Raman spectroscopy, and transmission electron microscopy (TEM).3–6 Amine loading was determined using the Sarin assay, whereas TEM and Raman spectroscopy were performed as described previously.3–6 Table 1 provides a list of the key drug constructs, the corresponding nomenclature, studies performed, and the SA values for the therapeutic and imaging studies from this work.
The RIT drug Construct I (Figure 1A) was designed to specifically target the tumor vessels and deliver the potent alpha particle-emitting 225Ac radionuclide generator. 13 The key SWCNT precursor to Construct I was assembled by first converting a fraction of the primary amines on the SWCNT-NH2 construct to reactive hydrazinopyridine (HNH) moieties. Briefly, 0.5 g of SWCNTNH 2 was dissolved in 1 mL of 100 mM sodium phosphate (NaH2PO4 and Na3PO4; Sigma-Aldrich, St Louis, MO, USA)/150 mM sodium chloride (NaCl; Sigma-Aldrich), pH 7.8 buffer. Immediately before use, 5.5 mg of succinimidyl 4-hydrazinonicotinate acetone hydrazone (SANH; Solulink Inc, San Diego, CA, USA) was dissolved in 0.2 mL of dry N,N-dimethylformamide (DMF; Sigma-Aldrich). An aliquot of SANH/DMF solution was added to the SWCNT-NH2 to achieve a 0.25-fold mole ratio of SANH to primary amine. The reaction proceeded at ambient temperature for 2–3 hours at pH 7.6. The product, SWCNT-(HNH)(NH2), was purified using size exclusion chromatography (SEC) with a 10 DG gel permeation column (Bio-Rad Laboratories, Hercules, CA, USA) as the stationary phase and metal-free water (MFW; Purelab Plus System, US Filter Corp, Lowell, MA, USA) as the mobile phase. The product was lyophilized to yield a solid that was found to be the desired SWCNT-(HNH)(NH2) construct.
The second step entailed covalently appending multiple copies of 2-(p-isothiocyanatobenzyl)-DOTA (DOTA-NCS; Macrocyclics, Inc, Dallas, TX, USA) to the remaining amines on the water-soluble SWCNT-(HNH)(NH2) construct to yield a SWCNT-(DOTA)(HNH) construct in metal-free conditions at pH 9.5 (adjusted with 1 M metal-free carbonate solution) for 40 minutes at room temperature at a stoichiometry of 10:1 (DOTA-NCS to amine).3–6 The product was purified using a 10 DG gel permeation column with MFW as the mobile phase. The 10 DG column was rendered metal free by washing with 50 mL of 25 mM EDTA (Sigma-Aldrich) followed by rinsing with 250 mL of MFW. The product was lyophilized to yield a solid that was found to be the desired SWCNT-(DOTA)(HNH) construct.
225Ac radionuclide was obtained from the US Department of Energy’s Oak Ridge National Laboratory (Oak Ridge, TN, USA). Methods for radiolabeling and purification of a MFW solution of SWCNT-(DOTA)(HNH) with 225Ac at pH 5 are similar to those described previously.48 Briefly, 0.18 mg of SWCNT-(DOTA)(HNH) in 0.02 mL of MFW was reacted with 0.005 mL of 225Ac in 50 mM optima grade hydrochloric acid (HCl; Fisher Scientific, Pittsburgh, PA, USA) along with 0.02 mL of 150 g/L l-ascorbic acid (Sigma-Aldrich) and 0.2 mL of 3 M tetramethylammonium acetate (Fisher Scientific) buffer, pH 5.5, at 60°C for 60 minutes (reaction 1). Purification was accomplished using SEC with a P6 gel stationary phase and a phosphate buffer saline (PBS) mobile phase. Chemicals used in the radiolabeling and purification steps were of American Chemical Society reagent-grade or higher purity. The labeling solutions were prepared and subsequently rendered metal free with Chelex® 100 resin, 200–400 mesh, sodium form (Bio-Rad Laboratories), and sterile filtered through a 0.22 or 0.45 μm filter device. Solutions of 50 mM diethylenetriaminepentaacetic acid (DTPA; Sigma-Aldrich) were sterile filtered and used to quench the labeling reaction prior to SEC. Human serum albumin (HSA; Swiss Red Cross, Bern, Switzerland) and 0.9% NaCl (Abbott Laboratories, North Chicago, IL, USA) were used as received.225Ac activity was measured with a Squibb CRC-17 Radioisotope Calibrator (or equivalent model; E.R. Squibb and Sons, Inc, Princeton, NJ, USA) set at 775 and multiplying the displayed activity value by 5 to report the activity.
Instant thin layer chromatography using silica gel impregnated paper (ITLC-SG; Gelman Science Inc, Ann Arbor, MI, USA) was used to determine the labeling efficiency of the reaction mixture and the purity of the product. Briefly, a 0.001 mL aliquot was spotted onto the paper strips and developed using 2 different mobile phases.13,23,48 Mobile phase 1 was 10 mM EDTA and 2 was 9% NaCl/10 mM sodium hydroxide (NaOH; Sigma- Aldrich). The Rf of the radiolabeled construct was 0 and any free metal species and metal chelates were characterized by Rf of 1.0 in mobile phase 1. In mobile phase 2, the radiolabeled construct and free metal species were characterized by Rf of 0 and the metal chelates by Rf of 1.0. The strips were counted intact using a System 400 Imaging Scanner (Bioscan Inc, Washington, USA).
The next key step (reaction 2) was the conversion of the VE-cad-specific IgG (E4G10; Imclone Systems, New York, NY, USA) or the isotype control anti-keyhole limpet hemocyanin (anti-KLH) IgG (R&D Systems, Minneapolis, MN, USA) to the reactive arylaldehyde modified–IgG precursors. Briefly, immediately before use, 15 mg of succinimidyl 4-formylbenzoate (SFB; Solulink Inc) was dissolved in 0.5 mL DMF. An aliquot of this modification solution was added to 2.5 mg of E4G10 protein (5 g/L; or the isotype control IgG) to achieve a 10–20 fold molar excess of the reagent. The reaction mixture was incubated at 37°C for 2–3 hours. Purification of the arylaldehyde modified–IgG was performed by SEC as described above. The modified proteins were stored at 4°C. The stoichiometry of substitution (moles of formylbenzoate [FB] per mole IgG) was determined first by assaying the protein concentration using the bicinchoninic acid (BCA) protein assay (Pierce, Rockford, IL, USA) and the moles of FB per mole IgG using the 2-HNH-dihydrochloride (2-HP; Solulink) quantification assay. Briefly, the addition of a molar excess 2-HP to the FB moiety on E4G10 at pH 4.7 permitted the measurement of the molar substitution ratio by electronic absorption spectroscopy using the arylhydrazone chromophore (maximum absorption [Absmax] = 350 nm, = 18,000 M−1 cm−1).
The E4G10-FB antibodies were covalently attached to the SWCNT-([225Ac]DOTA)(HNH) by the reaction of 0.05 mg of SWCNT-([225Ac]DOTA)(HNH) with 0.17 mg of E4G10-FB in 1.2 mL of 100 mM sodium phosphate/150 mM NaCl, pH 5.2 buffer (reaction 3). A similar chemical scheme was used to append several of the anti-KLH-FB moieties to the SWCNT-([225Ac]DOTA)(HNH) precursor to yield the control Construct I. The reaction mixture was incubated at 37°C for several hours, and the high and low SA SWCNT-([225Ac] DOTA)(E4G10) (Construct I) and isotype control Construct I products were stored at 4°C. The products were formulated into 1% HSA for injection.
The radioimmunoimaging (RII) drug Construct II (Figure 1B) was designed to specifically target the tumor vessels and deliver the positron-emitting 89Zr radionuclide for PET imaging. The key precursor to Construct II was assembled first by appending multiple copies of the reactive arylaldehyde, SFB. Briefly, the SFB was dissolved in 0.1 mL DMF and a volume of this modification solution was added to 0.5 mg of SWCNT-NH2 (3 g/L) to achieve a ratio of 5 SFB per 100 amines. The reaction mixture was incubated at 37°C for 2–3 hours. Purification of the arylaldehyde modified– SWCNT was performed by SEC as described above. The stoichiometry of substitution was determined (moles of FB per gram SWCNT) using the 2-HP quantification assay as described previously. Then, the remaining amines on the SWCNT-(FB)(NH2) construct were covalently modified by appending the desferrioxamine B (DFO) chelate. The details of preparation of the reactive DFO intermediate reagent are described below.
The synthesis of N-succinylDFO (N-succDFO) was performed by the reaction of DFO mesylate (0.508 g, 0.77 mmol; Calbiochem, Spring Valley, CA, USA) dissolved in 7.5 mL of pyridine (Sigma-Aldrich) with excess (1.704 g, 0.017 mol) succinic anhydride (Sigma-Aldrich) at room temperature for 24 hours. The resulting white suspension was then poured into an aqueous NaOH solution (120 mL, 0.015 M) and stirred at room temperature for 16 hours. The colorless solution was adjusted to pH 2 by the addition of 12 M HCl and cooled with stirring at 4°C for 2 hours. The white precipitate was collected by filtration, washed with copious amounts of 0.01 M HCl and then water, and dried in a vacuum to give the N-succDFO as a white microcrystalline solid (0.306 g, 4.75 × 10−4 mol).
The preparation of ferric DFO-2,3,5,6-tetrafluorophenol (Fe[DFO-TFP]) was performed by reacting the activated ester N-succDFO (9.0 mg, 0.014 mmol), suspended in 3 mL of 0.9% sterile saline and the pH adjusted to 6.5, with 0.05–0.075 mL of 0.1 M sodium carbonate (Na2CO3; Sigma-Aldrich). A solution of ferric trichloride hexahydrate (FeCl3 6H2O [4 mg, 0.015 mmol, 0.3 mL of 0.1 M HCl]; Sigma-Aldrich) – was added to this N-succDFO solution. Upon addition of the FeCl3, the reaction mixture changed from colorless to deep orange due to the intense electronic absorption band of Fe(DFO) with a peak at 430 nm (430 = 2,216 ± 49 M−1 cm−1). After stirring the reaction mixture at room temperature for 1 hour, a 1.2 M solution of TFP (0.3 mL, 0.036 mmol; Sigma-Aldrich) in Chelex-purified acetonitrile (MeCN; Sigma-Aldrich) was added to the reaction followed by the addition of solid N-(3-dimethylaminopropyl)-N’-ethylcarbodiimide hydrochloride (0120 mg, 0.63 mmol; Sigma Aldrich). The reaction mixture (pH 6.5) was then stirred at room temperature for 1 hour before purifying the Fe(DFO-TFP) product using a C18 Light Sep-Pak cartridge (Waters). The reaction mixture was loaded onto a preactivated (6 mL MeCN and 10 mL H2O) C18 cartridge, washed with copious amounts of water (>40 mL), and eluted with 1.5 mL MeCN. The final Fe(DFO-TFP) solution had a concentration of ~9.8 mM. The Fe(DFO-TFP) solution was stored at 4ºC.
The Fe(DFO-TFP) reagent was then reacted with the remaining amines on the SWCNT-(FB)(NH2) construct to introduce the DFO chelate onto the SWCNT precursor. The Fe was removed by exposing the metallated precursor to a 10-fold excess of EDTA (0.0674 M, 0.0137 mmol, 0.03 mL) with respect to Fe(N-succDFO-TFP). The reaction was incubated in a water bath at 38°C for 1 hour. The SWCNT-(DFO)(FB) was purified by SEC chromatography to render it Fe free and was ready to be radiolabeled (reaction 4).
89Zr was produced via the 89Y(p,n)89Zr transmutation reaction on an EBCO TR19/9 variable-beam-energy cyclotron (Ebco Industries Inc, Richmond, BC, Canada) in accordance with previously reported methods.30 The 89Zr-oxalate was isolated in high radionuclidic and radiochemical purity (RCP) >99.9%, with an effective SA of 195–497 TBq/g, (5,280–13,430 Ci/g).30 Methods for radiolabeling and purification of a 10 g/L solution of SWCNT-(DFO)(FB) in MFW with 89Zr at pH 5 are similar to those described previously.30 Briefly, 0.1 mg of SWCNT-(DFO)(FB) in 0.02 mL of MFW was reacted with 122.5 MBq (3.31 mCi) of 89Zr in 0.005 mL of 1 M oxalic acid (Sigma-Aldrich), pH 6.5. The pH was adjusted to 8.1 with the addition of 0.17 mL of 1.0 M Na2CO3. The reaction was heated to 60°C for 60 minutes. Purification was accomplished using SEC with a P6 gel stationary phase and a PBS mobile phase.89 Zr activity was measured with a Squibb CRC-17 Radioisotope Calibrator (or equivalent model) set at 465. ITLC-SG was used to determine the labeling efficiency of the reaction mixture and the purity of the product. The strips were counted intact using a System 400 Imaging Scanner (or equivalent).
The next key step was the conversion of the E4G10 or the isotype control anti-KLH IgGs to the reactive arylhydrazine modified–IgG precursors (reaction 5). Briefly, 1 mg of IgG was dissolved in 0.2 mL of 100 mM sodium phosphate/150 mM NaCl, pH 7.6 buffer. Immediately before use, 2–4 mg of SANH was dissolve in 0.1 mL of dry DMF. A volume of SANH/DMF solution was added to the IgG to achieve a 10–20 fold molar excess of the SANH to antibody. The reaction proceeded at ambient temperature for 2–3 hours at pH 7.6. The product, IgGHNH, was purified using SEC with a 10 DG gel column as the stationary phase and 100 mM 2-(N-morpholino) ethanesulfonic acid (MES; Sigma-Aldrich)/150 mM NaCl conjugation buffer at pH 5.4 as the mobile phase. The amount of HNH substituent per IgG was determined first by assaying the protein concentration using the BCA protein assay and the moles of arylhydrazine (HNH) per mole IgG using the 4-nitrobenzaldehyde (4-NBA; Solulink) quantification assay. Addition of a molar excess 4-NBA to the HNH moiety on IgG at pH 4.7 permitted the measurement of the molar substitution ratio of the chromophore (Absmax = 390 nm, = 24,000 M−1 cm−1).
The E4G10-HNH antibodies (or anti-KLH-HNH) were covalently attached to the SWCNT-([89Zr]DFO)(FB) by the reaction of 0.1 mg of SWCNT-([89Zr]DFO)(FB) with 0.3 mg of E4G10-HNH in 0.25 mL of 100 mM MES/150 mM NaCl conjugation buffer at pH 4.7 (reaction 6). The reaction mixture was incubated at 37°C for several hours. The SWCNT-([89Zr] DFO)(E4G10) (Construct II) and isotype control Construct II products were stored at 4°C and were formulated into 1% HSA for injection.
A fixed mass of SWCNT-(DOTA)(HNH) precursor was radiolabeled with varying amounts of 225Ac activity to determine the reaction yields and specific activities. In each of 5 radiolabeling reactions, the volume, pH, time, temperature, and reagent concentrations were held constant (see specific conditions described above), while only the amount of radionuclide was varied. Briefly, 0.18 mg of SWCNT-(DOTA)(HNH) was 225Ac-radiolabeled in 0.4 mL, at pH 5.5, at 60°C for 60 minutes in 5 different reactions. In amplification reaction 1, the SWCNT-(DOTA) (HNH) was labeled with 0.444 MBq (0.012 mCi); 2, 1.48 MBq (0.04 mCi) was used; 3, 2.26 MBq (0.061 mCi) was used; 4, 21.1 MBq (0.57 mCi) was used; and 5, 193 MBq (5.21 mCi) was used. An aliquot of each reaction was assayed using ITLC-SG (see above), and then, the reaction was quenched with the addition of DTPA. The reaction mixture was then purified by SEC (see above) and the purified product assayed by ITLC-SG and the recovered activity measured.
Data for numerous preclinical radiolabeling preparations of 225Ac-E4G10 were also compiled for comparison. The radiolabeling data using our published methods48 from 11-dose preparations that used 0.75 ± 0.13 mg (mean ± standard deviation) of E4G10 and 93.6 ± 51.1 MBq (2.53 ± 1.38 mCi) of 225Ac per dose were used as comparison to the results from the SWCNT-(DOTA)(HNH) labeling study.
As a further demonstration of the consistency of our published 2-step IgG radiolabeling methodology, lintuzumab (Protein Design Labs, Inc, Mountain View, CA, USA), a monoclonal IgG that targets CD33 on leukemia cells, was routinely radiolabeled with 225Ac for a Phase I clinical trial to produce 225Ac-lintuzumab. The radiolabeling data from 17 clinical dose preparations that used 1.4 ± 0.5 mg (mean ± standard deviation) of lintuzumab and 91 ± 55.1 MBq (2.46 ± 1.49 mCi) of 225Ac were also included as comparison to the results from the SWCNT-(DOTA)(HNH) labeling study.
Three-dimensional fluorescent-mediated tomography (FMT) experiments were performed by using the FMT-2500 (VisEn Medical, Boston, MA, USA) to determine the PK profile of the of E4G10 (and anti-KLH isotype control) IgGs and the number of binding sites per newly formed vascular endothelial cell in the LS174T xenograft model.
The E4G10 and anti-KLH antibodies were reacted with the succinimidyl ester of Alexa Fluor® 680 carboxylic acid (AF680; Invitrogen, Carlsbad, CA, USA) per the manufacturer’s instructions to prepare 2 antibody constructs for an in vivo near-infrared (NIR) FMT imaging study. Briefly, the constructs were prepared by the reaction of a 10–20 fold mole excess of the succinimidyl ester of the AF680 dye per milligram of IgG at pH 8 for 2 hours at ambient temperature. The dye-labeled constructs were purified by SEC chromatography as described above and characterized by UV-visible spectroscopy (measured the absorbance at 280 and 679 nm per the manufacturer’s instructions) and SEC HPLC. The HPLC system used a Beckman Coulter System Gold Bioessential 125/168 diode array detection system (Beckman Coulter, Fullerton, CA, USA) equipped with an in-line Jasco FP-2020 fluorescence detector (Tokyo, Japan). The stationary phase was a Tosoh Science G3000SWXL column (300 mm × 7.8 mm, 5 μm; Fisher Scientific) and a 20 mM sodium acetate (Sigma-Aldrich), 150 mM NaCl, pH 6.4, mobile phase at 1 mL/min at ambient temperature.
Two groups of 5 nude mice with the LS174T tumor were randomly assembled, and each mouse received 0.03 mg of the construct in 0.1 mL in 1% HSA via intravenous (IV) retro-orbital sinus injection. NIR FMT imaging was performed every 24–48 hours over a 7-day time period by using the specific 680 channel (excitation/emission [Ex/Em]: 680 nm/700 nm). The volume of interest (VOI) was drawn over the whole tumor (as visualized by the 3-dimensional photographic image acquisition), and fluorescence uptake was quantified. Mice were maintained on a diet of low-fluorescence chow (AIN76A; Harlan Teklad, Wisconsin) to minimize background noise. The FMT device was calibrated for use with sample standards of the E4G10-AF680 and anti-KLH-AF680 constructs in accordance with the manufacturer’s guidelines. The values obtained from the measurements of these standards of the injected dose were entered into the TrueQuant software (VisEn Medical) to allow for quantification.
To determine the number of VE-cad epitopes in these tumors, we employed the data obtained from Hilmas and Gillette49 that reported a morphometric analyses of tumor microvasculature during growth. Their data described changes in the tumor vascular volume, vessel diameter, mean vessel length, and surface area per unit volume of tumor tissue. Further, it was assumed that a VE cell has an area50 of 1E-3 mm2 (0.141 mm × 0.007 mm) and that there were 1E9 cells per gram of tumor. The data of Hilmas and Gillette49 reported that a 500 mm3 tumor had a vascular surface area per tumor volume of 13 mm2/mm3 and as the tumor volume increased (up to 1,500 mm3), the ratio of vascular surface area per tumor volume decreased and leveled at 12 mm2/mm3.
A RIT study was performed in the LS174T xenograft tumor model with SWCNT-([225Ac]DOTA)(E4G10) vs appropriate controls. Briefly, tumor cells were xenografted 13 days before treatment (the mean ± standard deviation tumor volumes for the animals in this study were 179 ± 112 mm3 at the time RIT commenced). Mice were randomly separated into 4 groups before treatment, and all mice received a single IV dose of drug (or vehicle control) via the retro-orbital sinus except one mouse in group 1 that received a single intraperitoneal injection to investigate tumor targeting by that administration route. Group 1 mice (n = 6) each received a single dose of the high SA = 851 GBq/g SWCNT (23 Ci/g) Construct I containing 16.1 kBq (435 nCi) 225Ac, 19 ng SWCNT, and 29 ng E4G10. Group 2 mice (n = 5) each received a single dose of the high SA = 851 GBq/g SWCNT (23 Ci/g) isotype control Construct I containing 15.2 kBq (410 nCi) 225Ac, 18 ng SWCNT, and 27 ng anti-KLH. Group 3 mice (n = 5) each received a single dose of the low SA = 1.9 GBq/g SWCNT (0.05 Ci/g) Construct I containing 0.037 kBq (1 nCi) 225Ac, 19 ng SWCNT, and 29 ng E4G10. Group 4 mice (n = 4) each received a single dose of normal saline and served as a growth control. Mice were observed daily and tumor volumes measured and recorded. The tumor volumes were assessed using calipers to measure the diameters and the volume was calculated as V = a × b2 × 0.52, where a is the longest diameter and b is the shortest diameter. When tumor volumes reached 1,000 mm3 or greater, mice were euthanized. Survival was analyzed as a function of time from treatment using Kaplan–Meier analysis.
A RII study was performed in the LS174T xenograft tumor model with SWCNT-([89Zr]DFO)(E4G10) vs appropriate controls. Briefly, tumor cells were xenografted 13 days before treatment (the mean ± standard deviation tumor volumes for the animals in this study were 558 ± 413 mm3 at the time RII commenced). Mice were randomly separated into 3 groups before treatment, and all mice received a single IV dose of drug via the lateral tail vein. All the SWCNT-([89Zr]DFO)(IgG) constructs were labeled to high SA (592 GBq/g SWCNT [16 Ci/g]). Group 1 mice (n = 4) received a single dose of Construct II containing 4.18 MBq (0.113 mCi) 89Zr, 7,000 ng SWCNT, and 15,700 ng E4G10. Group 2 mice (n = 3) received a single IV 0.8 mg dose of unlabeled E4G10 (50-fold excess relative to the construct-associated E4G10) 30 minutes before the single dose of Construct II containing 4.18 MBq 89Zr, 7,000 ng SWCNT, and 15,700 ng E4G10. This group served as a blocking control. Group 3 mice (n = 3) received a single dose of the isotype control Construct II containing 3.08 MBq (0.083 mCi) 89Zr, 5,200 ng SWCNT, and 12,100 ng anti-KLH.
The PET study was performed with a microPET FocusTM 120 (CTI Molecular Imaging, Knoxville, TN, USA). Mice were maintained under 2% isoflurane/oxygen anesthesia during the scanning. Images were recorded at various time points between 0–96 hours after injection. The list-mode data were acquired for between 10 and 30 minutes using a γ-ray energy window of 350–750 keV and a coincidence timing window of 6 ns. For all static images, scan time was adjusted to ensure a minimum of 20-million coincident events recorded. Data were sorted into 2-dimensional histograms by Fourier rebinning, and transverse images were reconstructed by filtered back-projection into a 128 × 128 × 63 (0.72 × 0.72 × 1.3 mm) matrix. The reconstructed spatial resolution for 89Zr was 1.9 mm full width at half maximum at the center of the field of view. The image data were normalized to correct for nonuniformity of response of the PET, dead-time count losses, positron-branching ratio, and physical decay at the time of injection but no attenuation, scatter, or partial volume-averaging correction was applied. An empirically determined system calibration factor (in units of [mCi/mL]/[cps/voxel]) for mice was used to convert voxel count rates to activity concentrations. The resulting image data were then normalized to the administered activity to parameterize images in terms of %ID/g. Manually drawn 2-dimensional region of interest (ROI) or 3-dimensional VOI were used to determined the maximum and mean % ID/g (decay corrected to the time of injection) in various tissues.6 Images were analyzed by using ASIPro VM 5.0 software (Concorde Microsystems, Knoxville, TN, USA).
LS174T, Chinese hamster ovary (CHO), and CHO cells that stably expressed human VE-cad were assessed for VE-cad expression by flow cytometry. Cells were stained with E4G10 plus a secondary goat anti-rat phycoerythrin IgG-conjugated antibody (R&D Systems) and then analyzed by flow cytometry (FACSAria; Beckman Coulter). In addition, lysates from these cell lines were tested for VE-cad expression by Western blot analysis. The lysates were resolved on a 4%–12% NuPAGE Bis–Tris gel (Invitrogen) and transferred to a polyvinylidene difluoride membrane, and VE-cad was detected using E4G10 plus a goat anti-rat horseradish peroxidase IgG–conjugated antibody (R&D Systems). In addition, glyceraldehyde 3-phosphate dehydrogenase (GAPDH) was included as a loading control and was measured to evaluate protein loading using an anti-GAPDH pAb (R&D Systems).
Three-dimensional VOI analysis on PET images was accomplished with ASIPro VM 5.0 software (Concorde Microsystems). Statistical data were evaluated using Graphpad Prism 5.0 (Graphpad Software Inc, La Jolla, CA, USA). Analysis of NIR images used the VisEn FMT- 2500 instrument’s TrueQuant software (VisEn Medical). Statistical comparison between 2 experimental groups was performed using a t test (unpaired comparison); comparison of multiple groups was performed with the one-way analysis of variance using Bonferroni’s multiple comparison post hoc analysis. All statistical comparisons were 2-sided, and the level of statistical significance was set at P < 0.05.
The SWCNT-(DOTA)(HNH) precursor to Construct I was assayed and found to contain 1 mmol DOTA and 0.06 mmol HNH per gram of SWCNT. This precursor was radiolabeled (reaction 1) with 5 different amounts of 225Ac activity, which after SEC purification yielded 96% radiochemically pure SWCNT-([225Ac]DOTA)(HNH). The SA for the 5 reaction products was 2.15, 4.07, 12.1, 108, and 914 GBq/g (0.058, 0.11, 0.326, 2.91, and 24.7 Ci/g, respectively). The 2 antibody components, E4G10-FB and the isotype control anti-KLH-FB, had 5–7 FB reactive groups appended per IgG (reaction 2). These IgG precursors were in turn reacted (reaction 3) in 5-fold excess (per 100 nm of SWCNT) with the SWCNT-([225Ac]DOTA)(HNH) (0.058 and 24.7 Ci/g) precursors to yield the RIT Construct I at two different SA and the nontargeting high-SA isotype control Construct I. Approximately 3 IgG per construct were appended per SWCNT. The starting amount of radioactivity used in the reaction is plotted vs the resultant SA (Figure 2).
The preclinical radiolabeling data for 225Ac-E4G10 yielded SA of 6.7 ± 4.4 GBq/g (0.18 ± 0.12 Ci/g) with RCP of 96.7% ± 2.6%. The radiolabeled clinical IgG, 225Aclintuzumab, yielded SA of 6.7 ± 1.9 GBq/g (0.18 ± 0.05 Ci/g) with RCP of 97.2% ± 2.5%. A comparison of the SWCNT-(DOTA)(HNH) precursor and the IgG construct labeling results demonstrates that the increased amount of DOTA per SWCNT yields almost a 2-log amplification of SA vs the IgG-DOTA constructs (Figure 2).
The N-succDFO product was obtained in 62% yield. High resolution mass spectrometry confirmed the product identity (HRMS-ES+ Calculated for [C29H52 N6O11 + H+] = 661.3772; found 661.3760 ([M + H+] = 100%).
The SWCNT-(DFO)(FB) precursor to Construct II was assayed and found to contain 0.4 mmol DFO and 0.3 mmol FB per gram of SWCNT. This precursor was radiolabeled with 89Zr activity, which after SEC purification yielded 97% radiochemically pure SWCNT-([89Zr]DFO)(FB) (reaction 4). The SA was 592 GBq/g (16 Ci/g). To assemble Construct II, ~11 HNH reactive groups were appended per IgG to yield E4G10- HNH and the isotype control anti-KLH-HNH (reaction 5). These antibody precursors were in turn reacted with the SWCNT-([89Zr]DFO)(FB) precursor in 10-fold excess (to SWCNT) to yield the RII Construct II and the nontargeting isotype control Construct II (reaction 6). Approximately 3 IgG per construct were appended per SWCNT.
The E4G10-AF680 and anti-KLH-AF680 constructs prepared for the FMT tumor NIR imaging and PK studies were prepared in 75% and 51% yield, respectively. Spectrophotometric analysis revealed that there were 5.5 AF680 appended per E4G10 and 10.2 AF680 per anti-KLH isotype control. Both constructs were 99% pure as determined by HPLC analysis. The amount of dye that accumulated in each tumor was imaged and measured on days 1, 2, 3, 5, 6, and 7 by FMT imaging. NIR FMT images of 2 representative mice demonstrate the differential targeting of the VE-cad epitope in the LS174T tumor vessels with E4G10-AF680 vs a similarly prepared isotype anti-KLH-AF680 nontargeting control construct 7 days after injection (Figure 3). There was 1.2 ± 1 pmol E4G10-AF680 (mean ± standard deviation) vs 0.04 ± 0.06 pmol anti-KLH-AF680 per group (n = 5 mice per group) on day 7 representing a 30-fold excess of signal-to-noise at this time.
A kinetic analysis of this data yielded the concentration of IgG-AF680 per tumor per day (Figure 4), which demonstrated a blood compartment clearance time of ~3 days. The tumor volumes (mean ± standard deviation) of the E4G10- AF680 group were 1,208 ± 444 mm3 (n = 5), and the anti- KLH-AF680 group had tumor volumes of 1,022 ± 667 mm3 (n = 5) on the second day of NIR FMT imaging study. This PK data were also used to calculate an estimate of the number of VE-cad per VE cell. In the E4G10-AF680 group, the mean tumor volume was 1,208 mm3, and 3.2 ± 0.08 pmol of E4G10 was accumulated after the blood compartment clearance. Using data from Hilmas and Gillette49 along with the aforementioned assumptions, there were 1.44E7 VE cells in the tumor with 1.33E5 VE-cad epitopes per VE cell. (The isotype control group that received the anti-KLH-AF680 had 0.27 ± 0.25 pmol of antibody in the tumor.)
A single administration of the high SA Construct I to the RIT group 1 mice significantly improved the median survival relative to the RIT group 4 mice (the growth controls; 26 days vs 12.5 days; P = 0.0334). RIT group 2 mice received the high SA isotype control Construct I and RIT group 3 mice received the low SA Construct I and had median survival times of 13 and 14 days, respectively. The Kaplan–Meier survival plot and the plot of the change in tumor volumes from time of treatment showed the benefit of a single dose, high SA Construct I relative to controls (Figure 5). It was observed that on day 10 after treatment, there was a noticeable transient decrease in tumor volume in RIT group 1 mice compared with other groups. Photographic images (Figure 6) of a representative mouse from RIT groups 1 and 3 are shown at day 10 from treatment to illustrate the therapeutic effect of the high SA drug construct control vs the low SA drug construct control. The tumor volume was significantly less in the RIT group 1 mouse with a lesion scar in the center of the tumor area.
A single IV administration of Construct II to the RII group 1 mice via the lateral tail vein showed rapid accumulation by PET ROI analysis of signal in the tumor (~0.36% ID/g at 24 hours after injection) (Figure 7A). RII group 2 mice (n = 3) received a single IV 0.8 mg dose of unlabeled E4G10 (50-fold excess relative to the construct-associated E4G10) 30 minutes prior to a single dose of Construct II and did not show accumulation of signal in the tumor (~0.24% ID/g at 24 hours after injection) (Figure 7B). RII group 3 mice (n = 3) received a single dose of the isotype control Construct II and did not show accumulation of signal in the tumor (~0.18% ID/g at 24 hours after injection) (Figure 7C). Other imaging data (Figure 8A) was taken from dynamic PET measurements in the first hour after administration which showed clearly the rapid blood compartment clearance (t1/2 = 15 minutes). The tumor accumulation in a representative RII group 1 mouse showed rapid and persistent accumulation of drug, whereas a representative RII group 3 control mouse demonstrated decrease of tumor-associated activity in the first 5 minutes that leveled off and appeared as noise. Further PET ROI data (Figure 8B) from a representative mouse from RII group 1 was plotted as a function of time at 1, 4, 24, and 96 hours and showed a tumor-to-muscle ratio of 1.61, 1.98, 2.95, and 5.08, respectively. The tumor-to-muscle ratios were highest at 96 hours, but reasonable contrast was apparent between 4 and 24 hours. This demonstrated a significant improvement over the E4G10-alone imaging agent that required ~3–4 days for the blood compartment activity to clear.
The concurrent processes of angiogenesis and tumor cell proliferation are keys to tumor growth and dissemination and are interrelated by a paracrine effect.51 Endothelial cells will expand to produce a tortuous network of vessels that supplies required nutrients, oxygen, cytokines, and chemokines to tumor cells. Disrupting and damaging the vascular endothelial architecture associated with tumor tissue have been recognized as a viable therapeutic strategy.51–57 Furthermore, imaging modalities that can specifically target the tumor vessels would be of value in diagnosing disease and following the progression or regression as a function of treatment.58,59
We hypothesized that novel synthetic structures based on hybrid molecules consisting of targeting biologics, radionuclides, and CNTs will have emergent anticancer properties. These molecular hybrids were designed to amplify the intrinsic targeting, binding, imaging, and therapeutic attributes of a drug construct and should, therefore, improve potency, specificity, and efficacy relative to current drugs. Irradiation of the vessels associated with tumor tissue was effected by specifically targeting the high LET alpha particle-emitting 225Ac in high SA to the VE-cad epitope; however, imaging the tumor vessels was effected by specifically targeting the same epitope with the positron-emitting 89Zr in high SA.
We previously demonstrated that an alpha particle-emitting, vascular-targeting antibody construct, 225Ac-E4G10, could specifically irradiate prostate carcinoma vascular endothelial cells27 and also their bone marrow-derived endothelial progenitors,28 delaying tumor growth and improving survival. We have also examined 225Ac-E4G10 in vascular-targeting strategies to treat animal models of glioblastoma mutiforme25,26 and the colon carcinoma (LS174T) model of tumor vasculature.60 Others have also used vascular-targeting, alpha particle-emitting RIT approaches to treat animal models of disease61–64 or vascular/tumor epitope-targeting RII approaches to PET image tumor.65–67
Two particular SWCNT properties, the high aspect ratio and the periodic structure, have rendered this nano-material amenable to being simultaneously appended with multiple copies of reactive primary amines, radiometal-ion chelates (DOTA or DFO), and IgGs. By amplifying the number of chelates per SWCNT, we have demonstrated a 2-log increase of SA of radiolabeling of SWCNT-(DOTA) relative to IgG constructs. Each of these SWCNT molecules had ~100 DOTA or DFO chelates appended per SWCNT. In contrast, an IgG might only accommodate 5–10 DOTA moieties per molecule before losing the ability to target and bind efficiently.68
The radiotherapeutic SWCNT constructs, labeled with 225Ac, were also functionalized with multiple copies of E4G10 antibody and used to treat LS174T tumors vs low SA control, nontargeting high SA isotype IgG control, and growth control. Survival of animals treated with high SA Construct I was doubled after only one treatment relative to the control groups and was significantly better than the growth controls. Tumor growth was also arrested and regressed in the high SA RIT group 1. The mice treated with the high SA, tumor vascular-targeting Construct I showed significant tumor regression while the low SA targeting analog did not control tumor growth. The image of the regressed tumor lesion was similar to the images obtained by Nilsson and Neri69 who targeted the delivery of tissue factor to the ED-B domain of fibronectin, a marker of angiogenesis, and mediated the infarction of solid tumors in mice.
The increased SA was also key to achieving a high signal-to-noise ratio for imaging purposes. We have utilized this increased sensitivity with indium-111 (111In) and 86Y labeled SWCNT-(DOTA) constructs for PK studies.3–6 In addition, covalently SWCNT-appended IgG and peptides have conferred biological targeting and binding capabilities to this scaffold and bind to the specific antigen epitope in vitro and in vivo.3,5 We were able to improve the SA of the 89Zr-labeled RII Construct II ~5-fold relative to 89Zr-labeled IgG-only labeled constructs.30
Another key SWCNT property that was utilized extensively was the favorable PK profile that featured rapid blood compartment clearance. The RII Construct II targeted and bounded and then rapidly cleared the blood compartment and the muscle yielding excellent contrast for imaging. The targeting system also favored this profile as the murine VE-cad epitope is expressed in the vessel lumen and, therefore, is readily accessible to the CNT construct. The binding occurred rapidly, precluding any need to diffuse into the solid tumor to target and bind. All of these studies demonstrated that the administered constructs were safe and well tolerated.
The SWCNT-E4G10 construct was tumor vessel specific and targeted the murine VE-cad. E4G10 did not cross-react with the LS174T tumor cells in flow cytometric or Western blot analyses (Figure 9). Furthermore, the normal, resting vasculature no longer exposes this epitope to the E4G10 IgG for binding,9 thus sparing normal vessels. An illustration of this VE-cad targeting concept using IV delivered soluble, targeting, radiolabeled (for imaging or therapy) constructs in patients with tumor is presented in Figure 10. The construct rapidly accesses the tumor vasculature and then can specifically bind to the monomeric VE-cad that is expressed in the neovasculature but cannot bind to resting vasculature with tight cell–cell contacts at the adherens junctions.
This E4G10/VE-cad targeting system is unlike the arginine-glycine-aspartic acid (RGD)-based agents that target the αvβ3 integrin, which is often expressed by both the tumor and the vascular network. The RGD/αvβ3 integrin system lacks the vascular specificity that we designed into our constructs. Targeting studies of vascular endothelial growth factor (VEGF)-A that is expressed in the LS174T human xenograft model with bevacizumab were complicated not only by the relatively small numbers of copies of epitope per tumor cell (12E3) but also by the imaging artifact that was created by the lack of expression of human VEGF-A in a mouse model.66
The NIR FMT imaging data in vivo yielded an estimate of the number of VE-cad expressed per vascular endothelial cell. Using the measured values of the moles of E4G10 (3.2 pmol) per tumor (1,208 mm3) and published vessel area values per tumor volume49 and VE cell area (1E-3 mm2),50 there were 1.4E7 VE cells in the tumor with 1.3E5 VE-cad epitopes per VE cell. The VE-cad epitope was not expressed by the LS174T tumor and is a murine protein in the vessels of a mouse model. Baumgartner and Drenckhahn70 reported 6E6 VE-cad dimers (12E6 VEcad monomers) for immortalized mouse microvascular endothelial cells (MyEND) as determined in vitro using affinity chromatography and trypsinization. Our value was 90-fold lower than their value; however, it might be safely assumed that most of the vascular endothelial cells in our tumor were not newly formed angiogenic cells, and thus, the epitope was hidden. Since our value was based on total vascular endothelial cells, then if only 10% of the vascular endothelial cells in the tumor were newly formed or had irregularly or poorly connected adherens junctions, then our estimate of the number of epitopes per cell would increase 10-fold (1.3E6 VE-cad epitopes per VE cell). If the number of newly formed VE cells was only 1% of the total VE cell population in the tumor, then the value would increase 100-fold (1.3E7 VE-cad epitopes per VE cell). The latter assumption yielded a better correlation with the Baumgartner data.
SWCNT constructs were designed, constructed, and used to deliver therapeutic and imaging radionuclide cargoes specifically to the vessels of a solid tumor using a target on VE-cad found only on new vascular endothelium. The goal was to target the neovessels and irregular vessels in a tumor with these novel nanoconstructs and image accumulation and evaluate the therapeutic anti-angiogenic effects. The construct design incorporated 100-fold amplified cargo delivery (relative to the gold standard for targeted therapy – IgG) and was built to be multifunctional and thus had therapeutic or imaging cargo, as well as targeting capability conferred by the appended IgG. This proof of concept design resulted in a construct with therapeutic efficacy, good image contrast, and specificity for the target. This amplified SA may prove important in delivering potent enough therapy and sensitive enough diagnostic signals simultaneously to the tumor. Our data also provided support of the use of nanomaterials in vascular-targeting strategies. These SWCNT construct doses were well tolerated and safe in these animal models. The number of VE-cad epitopes per tumor was measured and extrapolated to estimate a number of bound VE-cad epitopes per cell. These latter results along with the PK profile will be of use in designing more optimized therapeutic and imaging studies with these constructs. Moving forward, it is anticipated that a single construct could be designed to incorporate both the imaging and therapeutic cargoes onto the same platform. Furthermore, because the construct targets an epitope expressed by the tumor vascular network, a single agent could be employed to image or treat a variety of different tumors.
Funded in part by the National Institutes of Health grants R21 CA128406, R01 CA55349, R25T CA096945, R24 CA83084, P30 CA08748, P01 CA33049; the Memorial Sloan-Kettering Brain Tumor Center; the Memorial Sloan- Kettering Experimental Therapeutics Center; the Geoffrey Beene Cancer Research Center of Memorial Sloan-Kettering Cancer Center; and the Office of Science (BER), US Department of Energy (Award DE-SC0002456). We would also like to thank Medactinium, Inc for the 225Ac; ImClone Systems (a wholly-owned subsidiary of Eli Lilly and Company) for the E4G10 antibody; and Amy Carol McDevitt for the graphic illustration and figure. Conflict of interest statement: David A Scheinberg is a consultant for Enscyce; Michael R McDevitt was a consultant for Medactinium; and Chad May was employed by ImClone Systems at the time of this study.