Patent Application
20070009436
This invention relates generally to detection and treatment of cancer, and more particularly to radioimmunotherapy and imaging using radionuclide nanoparticles encased by an inorganic shell.
Radioimmunotherapy (RIT) is a therapeutic regimen used to treat diseases such as non-Hodgkins lymphoma (NHL). In RIT, a radioimmunoconjugate comprising a monoclonal antibody (mAb) that is specific to the target tissue of interest is bound to a radionuclide particle. The mAb attaches to a binding site on the target cell, and the radionuclide administers a lethal dose of radiation. RIT is used alone or can be combined with chemotherapy and other therapeutic strategies. The basic strategy of RIT is that coupling of a radionuclide to the mAb causes enhanced accumulation of the radionuclide at the targeted site. Accumulation of the radionuclide at the targeted site causes radiation therapy to be delivered near the targeted site with a radius approximating the mean path length of the emitted particle, about ˜5 mm for 2 MeV β particles from yttrium-90 (90Y), and ˜100 μm for 8 MeV α particles from 213Bi.
Effective treatment of cancer patients by using RIT and diagnostics of malignant tumors by radioimmunodetection (RAID) requires improvements of tumor-to-background (T/B) distribution of a radiolabel. The T/B ratio is the principal parameter that determines tumoricidal action, sensitivity of tumor detection and, most importantly, systemic toxicity of the compound. Radioactive isotopes of metals are used very often in various modalities of RIT and RAID in the form of conjugates with monoclonal antibodies.
Several different radionuclides have been considered for RIT therapies. The choice of radionuclide takes into account the physical and chemical characteristics of the radionuclide, including half-life, radiation emission properties, radiolabeling properties, availability, in vivo distribution and stability. Radionuclides considered suitable for RIT possess a half-life long enough for target localization, little or no gamma radiation, intermediate beta particle energy, stable daughter products, and stable fixation with an antibody system. Many β particle-emitting radionuclides are available for RIT. These include yttrium-90 (90Y), iodine-131 (131I), copper-67 (67Cu) and rhenium-186 (186Re). Alpha (α) particle-emitting radionuclides include astatine-211 (211At), and bismuth-212 (212Bi). Alpha and beta emitters are preferred because the mean path links are limited to dozens of mm, thereby limiting treatment to the immediate vicinity of the target. Beta particles may be more suitable for larger tumors due to the longer mean path length of the beta emission. Alpha particles generally have extremely high energies (greater than 5 MeV) and high linear energy transfer rates, which are useful for delivering high doses to a limited area.
The selection of the optimal target for RIT is one that expresses homogenously at high levels on the surface of the target cell, is absolutely or relatively specific to the cell in order to minimize toxicity to normal cells, and is not shed into the vascular compartment. Monoclonal antibodies have been developed against a number of B-cell antigens. CD20 is a particularly attractive target for RIT in the case of NHL. CD20 is expressed among 90% of B-cell NHL's, but is not expressed on stem cells, progenitor cells or fully differentiated plasma cells. This allows serum immunoglobulin levels to be maintained despite eradication of mature B cells, thus minimizing the potential for serious infection. CD20 is not shed from the cell surface, and is minimally internalized on antibody binding. Other RIT targets investigated for NHL includes CD19, CD22, and CD37, and HLA Class II variant antigens, which are selectively expressed on malignant B-cells.
Traditionally, the radionuclide is delivered as an atom bound directly to the mAb, such as 131I-mAb, or in a chelating complex bound to the antibody, such as 90Y-DPTA-mAb. This approach, while effective, presents risk to the patient through unintentional release of the radionuclide as considerable leaching of the radionuclide metal ions is possible, which diminishes the practical applications of the RIT system.
Ideally, the mAb-radionuclide conjugate would be rapidly excreted via the urinary tract without intracellular retention, with intact conjugate accumulating and being retained selectively at the tumor site. This is however not always the case, and in several instances, persistent and unwanted retention of metallic nuclides has been reported.
The tumor uptake and overall biodistribution of the radiolabeled compound depends on the metabolism of the mAb and the strength of the radionuclide-antibody link. Although there is substantial room for improving targeting properties of mAbs, studies indicate that the thermodynamic and kinetic stability of the conjugate in vivo is of primary importance for the design of clinically successful radiochemicals.
Kotov, U.S. Pat. No. 6,689,338, discloses a bioconjugate including a radionuclide comprising nanoparticle covalently linked to a biological vector biomolecule. The particle core that contains the radionuclide is an inorganic crystal, such as a transition metal sulfide (e.g. ZnS) or oxide (e.g. TiO2) that is doped throughout with the radionuclide. For example, the radionuclide ions can replace some of the parent metal (Zn) within the ZnS crystal structure. The radionuclide comprising core is then surrounded by a monolayer of an organic molecule which is covalently bound to the surface of the nanoparticle. The organic shell disclosed in Kotov tends to help passivate the surface of the nanoparticle and prevent reactivity and dissolution to some degree. However, the organic shell is not impermeable. Thus, although the organic shell disclosed by Kotov may reduce the unintentional release of the radionuclide due to leaching as compared to the conventional arrangements where no shell is used, the significant solubility of organic shell materials in biological fluids results in considerable leaching of the radionuclide metal ions, which diminishes the practical applications of the Kotov approach.
A nanoparticle radionuclide delivery system based on a core-shell approach comprises a radionuclide core, a non-radioactive inorganic shell layer encasing the radionuclide core to form an encased radionuclide, at least one coupling moiety, and at least one vector biomolecule specific to a target tissue. The shell layer prevents radionuclide that may be at or near the surface of the radionuclide comprising core from dissolving away. The coupling moiety includes a first reactive group bound to the non-radioactive layer of the encased radionuclide and a second reactive group bound to the vector biomolecule. The vector biomolecule is generally a monoclonal antibody or fragment thereof or a peptide having an affinity for the target tissue.
The non-radioactive inorganic layer and the radionuclide core can share at least one chemical specie. In a preferred embodiment of the invention, the radionuclide core and the non-radioactive inorganic layer are part of a continuous crystal. For example, the non-radioactive inorganic layer can be Y2O3 and the radionuclide core can include 90Y, such as in the form of 90Y2O3. Oxide nanoparticles can be also synthesized with a percentage of 62Zn—62Cu (ZnO, CuO, or Cu2O), 68Ge—68Ga (GeO2 or Ga2O3), 61Cu/64Cu, (CuO or Cu2O), 177Lu (Lu2O3), 153Sm (Sm2O3), or 111In (In2O3). The nanoparticle delivery systems can also be amorphous silica/alumina and TiO2.
The coupling moiety can include at least one group bound to a protein provided by the vector biomolecule, such as 1-ethyl-3-[3-dimethylaminopropyl]carbodiimide hydrochloride. The nanoparticle radionuclide delivery system can further comprise an organic amine bound to the non-radioactive inorganic layer, wherein the 1-ethyl-3-[3-dimethylaminopropyl]carbodiimide hydrochloride is bound to the organic amine and the vector biomolecule. The organic amine can be 4-aminobenzoic acid or trimethoxysilylpropylamine. In this embodiment, the non-radioactive inorganic layer can comprise a metal oxide, such as yttrium oxide, or a metal phosphate, such as lanthanum phosphate (LaPO4). The radionuclide core can comprise LaPO4 and at least one radionuclide. The non-radioactive inorganic layer is preferably a continuous coating.
A method for treating or imaging tissue, comprises the steps of providing a plurality of encased radionuclide nanoparticles having vector biomolecules attached thereto comprising a radionuclide core, a non-radioactive inorganic layer encasing the radionuclide core to form an encased radionuclide, at least one coupling moiety, and at least one vector biomolecule specific to a target tissue, wherein the coupling moiety includes a first reactive group bound to the non-radioactive layer of the encased radionuclide and a second reactive group bound to the vector biomolecule. The plurality of encased radionuclide nanoparticles are infused into a patient in a dose selected to provide at least one of radioimmunotherapy and imaging of the tissue. The said vector biomolecule can be a monoclonal antibody or fragment thereof or a peptide having an affinity for the target tissue.
The invention provides a nanoparticle radionuclide delivery system including a radionuclide core, a non-radioactive inorganic layer encasing the radionuclide core to form an encased radionuclide, at least one coupling moiety, and at least one vector biomolecule specific to a target tissue. The coupling moiety includes a first reactive group bound to the non-radioactive layer of the encased radionuclide and a second reactive group bound to the vector biomolecule. The vector biomolecule is a monoclonal antibody or fragment thereof or a peptide having an affinity for the target tissue. As known in the art, monoclonal antibodies (mAb) are antibodies that are identical because they were produced by one type of immune cell, all being clones of a single parent cell. Given any substance, it is possible to create monoclonal antibodies that specifically bind to that substance.
The encasing layer is preferably a continuous coating. As used herein, the term “continuous coating” refers to a coating such that the radionuclide core is isolated from a physiological environment by the coating, such that the radionuclide core remains undissolved when the encased radionuclide is under physiological conditions for at least the length of time of a conventional radiotherapy session.
The radionuclide material is an atom or molecule that includes an atom with an unstable nucleus which undergoes radioactive decay by emitting a gamma ray(s) and/or subatomic particles. The radionuclide material can be any such material suitable for use in RIT or RAID. The radionuclide can be formed as a substantially homogeneous particle, or can be combined with one or more compounds. Such materials should emit radiation in sufficient amounts to be lethal to the target cell or provide a sufficient signal for imaging. It is preferable that the radiation from the radionuclide has a mean path length that is sufficiently limited (Betas are limited to ˜10-12 mm and Alphas are limited to ˜<1 mm) so as to minimize exposure of healthy cells to the emitted radiation. Suitable radionuclides can include a variety of alpha and beta emitters. Beta emitters may be better treatments for larger tumors due to the longer mean path link of the beta emitters. Alpha particles have extremely high energies and high linear transfer rates which may be useful for delivering high doses to a small area. Beta-emitting radionuclides include yttrium-90 (90Y), iodine-131 (131I, indium-111, samarium-133, copper-67 (67Cu) and rhenium-186 (186Re). Alpha-emitting radionuclides include astatine-211 (211At), and bismuth-212 (212Bi).
There is shown in
A biological vector biomolecule being a monoclonal antibody 18 is coupled to the encasing layer 14 by a coupling moiety 20. The coupling moiety 20 is generally covalent bound to the encasing layer 14. Although a single coupling moiety 20 is shown, the encased nanoparticle surface generally includes a plurality of covalently bound coupling moiety molecules 20. Similarly, although a single monoclonal antibody 18 is shown in
The material for inorganic encasing layer 14 is selected so as to be substantially impermeable to radionuclide particles, such that daughter particles will not escape the encasing layer. In a preferred embodiment, as noted above, the inorganic encasing layer is a continuous layer.
The encasing layer 14 is preferably a non-radioactive continuation of the core. For example, the core 12 may be Y2O3 isotopically enriched with Y-90. The encasing layer 14 would then be a layer of Y2O3 devoid of Y-90. Being a continuous crystal in this arrangement, the Y-90 would not be capable of migration. Yttrium oxide is easily doped with several useful radioactive elements other than Y-90. In another embodiment, a continuous crystal provides a lanthanum phosphate (LaPO4) core 12 including the radionuclide, and an encasing layer 14 thereon of LaPO4 that contains no radionuclide. LaPO4 may be doped with any of the heavy lanthanide (III) ions, including actinium.
The encasing layer should be substantially stable in biological systems under human physiological conditions and when subjected to the radionuclide core material, should not be subject to leaching of the radionuclide, and should be capable of containing nuclear reaction products from the radionuclide. The encasing layer should be capable of facile attachment to various antibodies or selective ligands, without the need for expensive organic synthesis.
Oxide materials, such as metal oxides, are suitable for the inorganic encasing layer 14. Oxide materials are stable, especially under physiological conditions, and will not generally release free nuclides into the body. In addition, the protocol for the attachment of antibodies to oxide surfaces is well established. An atom encased in an oxide nanoparticle generally loses its atomic chemical nature. As noted above, in one embodiment, the non-radioactive inorganic encasing layer 14 and the core 12 share at least one chemical specie, such as Y2O3 and Y, respectively.
The non-radionuclide comprising nanoparticle encasement material can be of a variety of materials. Methods have been developed described in the Examples below for synthesizing oxide and phosphate encased nanoparticles with diameters of 50 nanometers or less. Yttrium, which in the ionic form (e.g. ZEVALIN® (ibritumomab tiuxetan) can accrete into bone, is instead utilized as yttrium oxide (Y2O3), which is a refractory and very insoluble ceramic material. Other oxide nanoparticles that can be employed as hosts for entrapment of targeted radionuclides include indium oxide, amorphous silica/alumina, zeolite, germanium oxide, gallium oxide, titanium oxide, iron oxide, rare-earth oxide, boron oxide, cupper oxide, cuprous oxide, zinc oxide, nickel oxide, and rhenium oxide. In another inventive aspect, the nanoparticles are rare-earth phosphate (e.g. lanthanum phosphate: LaPO4) and aluminum phosphate (AlPO4). Both yttrium oxide and lanthanum phosphate are highly insoluble under physiological conditions, and will contain both the radionuclide core 12 and any daughter products.
Yttrium oxide may be synthesized with a percentage or all of the yttrium as 90Y. The above oxide nanoparticles can be also synthesized with a percentage of 62Zn—62Cu (ZnO, CuO, or Cu2O), 68Ge—68Ga (GeO2 or Ga2O3), 61Cu/64Cu, (CuO or Cu2O), 177Lu (Lu2O3), 153Sm (Sm2O3), or 111In (In2O3). Lanthanum phosphate may be loaded with any rare earth nuclide and most trivalent transition metals. This includes alpha emitting radionuclides such as 225Ac that have not previously been considered because of the radiotoxicity of daughter products. For example, La1-xAcxPO4 will become La1-xAcx-yBiyPO4 as it decays, but the bismuth, the decay daughter of actinium, will remain in the nanoparticle and will not present a threat to other tissue.
The vector biomolecule 18 is preferably a monoclonal antibody (mAb). The monoclonal antibody can be any suitable monoclonal antibody which is capable of binding to the target. In one aspect, the monoclonal antibody is anti-CD20, such as mAb 2B8.
The nanoparticle may be bound to the vector biomolecule 18 using any suitable coupling moiety. In one example, the coupling moiety 20 is a protein coupler molecule such as EDC (1-ethyl-3-[3-dimethylaminopropyl]carbodiimide hydrochloride). EDC may couple an organic amine, such as 3-aminopropyltrimethoxysilane, that is bound to the surface of the oxide nanoparticle, to a carboxolate functionality within a protein provided by the vector biomolecule 18, such as glutamate or aspartate. The methoxysilane groups hydrolyze and react with hydroxyls on the surface of the yttria. The majority of the EDC molecule cleaves to leave an amide bridge between the amine and the protein. In this way, a nanoparticle mAb conjugate is formed.
It is also possible to add an imaging compound to the nanoparticles. Radioactive chemical tracers which emit radiation such as gamma rays can be included in nanoparticles according to the invention to provide diagnostic information about a person's anatomy and the functioning of specific organs. In the case of yttrium oxide encasing layers, a positron emitter such as 87Y can be added to the particle to allow imaging. In the case of lanthanum phosphate, there are a variety of gamma emitters that may be used to add an imaging component to the treatment component.
A method for treating or imaging tissue according to the invention comprises the steps of providing a plurality of encased radionuclide nanoparticles having vector biomolecules attached thereto comprising a radionuclide core, a non-radioactive inorganic layer encasing the radionuclide core to form an encased radionuclide, at least one coupling moiety, and at least one vector biomolecule specific to a target tissue, wherein the coupling moiety includes a first reactive group bound to the non-radioactive layer of the encased radionuclide and a second reactive group bound to the vector biomolecule. A plurality of encased radionuclide nanoparticles are then infused into a patient in a dose selected to provide at least one of radioimmunotherapy and imaging.
It should be understood that the Examples described below are provided for illustrative purposes only and do not in any way define the scope of the invention.
Various methods may be used to form encased radionuclide nanoparticles having vector biomolecules attached thereto. Exemplary methods are described below for forming Y2O3 encased 90Y and lanthanum phosphate encased trivalent lanthanide or actinide series species including 225Ac, a potent alpha emitting radionuclide.
In one method, yttrium oxide nanoparticles are synthesized using a polymer-complex method. Yttrium nitrate is mixed with malic acid in ethylene glycol to form a polymer complex. 90Y may be introduced at this point as either the chloride or the nitrate salt. The 90Y salt is incorporated into the polymer complex with the natural 89Y. The polymer complex is thermally decomposed within a micelle to produce an amorphous Y2O3 nanoparticle, which is then heat-treated to produce the final particle. See Saengkerdsub, S; Im, H J; Willis, C; et al. Pechini-type in-situ polymerizable complex (IPC) method applied to the synthesis of Y2O3:Ln (Ln=Ce or Eu) nanocrystallites, Journal of Materials Chemistry, 14 (7): 1207-1211 2004) for exemplary process specifics.
The lanthanum phosphate nanoparticles can be synthesized through a direct reaction of lanthanum chloride within anhydrous phosphoric acid:
RCl3+LaCl3+H3PO4→3HCl+LaPO4:R (R=225Ac or other radionuclide)
The reaction is performed at approximately 200° C. in order to promote crystallization and off gassing of the hydrogen chloride. The reactants are contained within a micelle in a manner identical to the yttrium oxide, in order to restrict the volume of the particles and prevent aggregation. Lanthanide or Actinide radioisotopes may be introduced into the micelles as chloride salts, and will be incorporated into the nanoparticles during the condensation with phosphoric acid. The nanoparticles may then be reacted with a coordinating organophosphate such as 2-aminoethylphosphonic acid. The organophosphate is reacted with ECD in the same manner as yttrium oxide to produce the LaPO4 nanoparticle-mAb conjugate.
This invention can be embodied in other specific forms without departing from the spirit or essential attributes thereof. Accordingly, reference should be had to the following claims, rather than to the foregoing specification, as indicating the scope of the invention.
The United States Government has rights in this invention pursuant to Contract No. DE-AC05-000R22725 between the United States Department of Energy and UT-Battelle, LLC.
