Patent Application
20190336619
Foreign priority benefits are claimed under 35 U.S.C. § 119(a)-(d) or 35 U.S.C. § 365(b) of Australian application number 2018901483, filed May 2, 2018. The entire contents of this application is incorporated herein by reference in its entirety.
The present invention relates to multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agents for image enhancement, and more particularly to a multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agent that does not require a chelator or complexing agent to bind the radionuclide responsible for providing the PET signal.
The invention has been developed primarily for use as a multimodal contrast agent in PET (positron emission tomography)/MRI (magnetic resonance imaging) imaging, and will be described hereinafter with reference to this application.
The following discussion of the background to the invention is intended to facilitate an understanding of the invention. However, it should be appreciated that the discussion is not an acknowledgement or admission that any of the material referred to was published, known or part of the common general knowledge in Australia or any other country as at the priority date of any one of the claims of this specification.
To date, a number of techniques have been employed as a means of non-invasively providing medical images. There is no one ultimate method of imaging that is capable of providing a detailed image of all fractions of the body (blood, bone, organ, tissue, cells). Therefore, each technique fills a particular niche and cohesively along with other imaging techniques, provides new and complementary information in order to understand the big picture. In recent years there has been a push for non-invasive methods and multimodal methods of imaging that may be capable of providing a more detailed image as a result. Despite this constant evolution of technology, the ability to produce images of internal structures of the body still remains limited.
Magnetic resonance imaging (MRI) is an imaging modality that is used to construct images of the nuclear magnetic resonance (NMR) signal, primarily from the hydrogen atoms in an object. The image contrast is achieved by the differences in the NMR signal intensity in different areas within the object, and the NMR signal intensity largely depends on the nuclear density (proton spins), the relaxation times (T1, T2, and T2*), and the magnetic environment of the tissues.
Contrast agents are a group of contrast media used to improve the visibility of internal body structures in magnetic resonance imaging (MRI).
MRI contrast agents are not directly visible. The modification in contrast is due to their effect of shortening the relaxation time T1 and/or T2 of the hydrogen nuclei located in their vicinity. If the contrast agent reduces time T1 (paramagnetic contrast agents), we observe a T1 hypersignal. On the other hand, if it shortens T2 (superparamagnetic contrast agents), there will be a reduction in the T2 and T2* signal. The effectiveness of the contrast agent depends on its relaxivity (that is, its capacity to modify relaxation times).
The most commonly used compounds for contrast enhancement are gadolinium-based. Such MRI contrast agents shorten the relaxation times of nuclei within body tissues following oral or intravenous administration. In MRI scanners, sections of the body are exposed to a very strong magnetic field causing primarily the hydrogen nuclei (“spins”) of water in tissues to be polarized in the direction of the magnetic field. An intense radiofrequency pulse is applied that tips the magnetization generated by the hydrogen nuclei in the direction of the receiver coil where the spin polarization can be detected. Random molecular rotational oscillations matching the resonance frequency of the nuclear spins provide the “relaxation” mechanisms that bring the net magnetization back to its equilibrium position in alignment with the applied magnetic field. The magnitude of the spin polarization detected by the receiver is used to form the MR image but decays with a characteristic time constant known as the T1 relaxation time. Water protons in different tissues have different T1 values, which is one of the main sources of contrast in MR images. A contrast agent usually shortens, but in some instances increases, the value of T1 of nearby water protons thereby altering the contrast in the image.
Positron emission tomography (PET) is another imaging modality in nuclear medicine that is used to observe metabolic processes in the body. The system detects pairs of gamma rays emitted indirectly by a positron-emitting radionuclide (tracer), which is introduced into the body on a biologically active molecule. Three-dimensional images of tracer concentration within the body are then constructed by computer analysis.
Radionuclides used in PET scanning are typically isotopes with short half-lives such as carbon-11 (˜20 min), nitrogen-13 (∞10 min), oxygen-15 (˜2 min), fluorine-18 (∞110 min), gallium-68 (∞67 min), zirconium-89 (˜78.41 hours), copper-64 (˜12.70 hours) or rubidium-82 (˜1.27 min). These radionuclides are incorporated either into compounds normally used by the body such as glucose (or glucose analogues), water, or ammonia, or into molecules that bind to receptors or other sites of drug action.
The current use of radionuclides for certain applications is limited by the requirement for the use of chelators or complexing agents to bind these radionuclides to pharmaceuticals, proteins, peptides, targeting agents or directly to biological structures such as cells. Complexing agents and/or chelators operate by providing specific binding sites for the target surface such as a nanoparticle, as well as a specific binding site for the radionuclide. One end of the complexing agent or chelator binds to the core, while the other binds to the radionuclide, thereby providing a mechanism to attach one to the other. As this is a reaction that requires one binding site for each radionuclide, the complexing agent or chelator acts as a significant limiting factor of the reaction. An added complication in the use of chelators is the risk of “poisoning”; this occurs when chelators are exposed to metals unintentionally. This can occur as the result of metals being extracted out of reaction and storage vessels. Once present, these metals can bind to the chelators taking up binding sites and sometimes binding irreversibly. In the case of cell based applications, the current chelator-based radionuclide formulations often suffer from a common lack of efficiency in cell retention and upon in vivo administration can lead to significant non-specific uptake.
Magnetic nanomaterials have been commonly used as MRI contrast agents; both T1- and T2-weighted MRI agents have been clinically approved and are commercially available. However, the majority of the T1 contrast agents used at present are gadolinium-based, of which there are several reported side effects, most notably associated with the kidneys including for example, nephrogenic systemic fibrosis (NSF), which are due largely in part to the inherent toxicity of this particular element. For instance, gadolinium(III) is somewhat toxic as a free solubilized aqueous ion, but it is generally regarded as safe when administered as a chelated compound.
Currently, there are no T2-based MRI iron oxide contrast agents being utilised for MRI imaging. Those products that had previously gained marketing approval for use including, Feridex I.V.™ (Endorem™; ferumoxides injectable solution), Resovist™ (Cliavist™), Sinerem™ (Combidex™), Guerbet™, Lumirem™ (Gastromark™) and Feraheme™ (Ferumoxytol) have since been withdrawn for one reason or another. As the market is dominated by T1 agents for clinical use and common MRI imaging purposes, T2 agents have to date received little market demand. This lack of demand for T2 contrast agents is the primary reason for their withdrawal from the market.
Iron oxide nanoparticles (IONPs) are nanocrystals made from magnetite or hematite. Despite spin surface disorders and the observed spin canting effect, IONPs typically possess substantial saturation magnetization (Ms) values at room temperature, especially for those made from pyrolysis protocols with good crystallinity. Unlike the bulk materials, IONPs that less than 20 nm in size are superparamagnetic—a state where particles show zero magnetism in the absence of an external magnetic field, but can become magnetized when there is one. The underlying mechanism is that at such small scale, the thermal energy is sufficient to overcome the anisotropy energy of each small magnet (nanoparticle), and this leads to random fluctuation of the magnetizations that, macroscopically, result in zero net coercivity and magnetic moment.
The superior magnetic properties of IONPs, along with their inherent biocompatibility and inexpensiveness, have made IONPs a material of choice in many bioapplications, such as contrast probes for magnetic resonance imaging (MRI). The high magnetic moments of IONPs make them effective in reducing T2 relaxation times, leading to signal attenuation on a T2- or T2*-weighted map. When the particles are engineered with targeting specificity, such signal alterations can be harnessed to report abnormal biological activity.
Superparamagnetic iron oxide nanoparticles (SPIONs) comprise a class of novel MRI contrast agents that are composed of a ferric iron (Fe3+) and ferrous iron (Fe2+) core coated with a layer of polysaccharide such as dextran, or another chemical species. The iron nanoparticles at the core have a very large magnetic moment, which leads to local magnetic field inhomogeneity. Consequently, the intensity of the NMR signal produced in respect of these SPIONs is significantly decreased, appearing dark on T2- and T2*-weighted images. On the basis of size (namely, diameter), SPIONs are commonly classified as oral SPIO (300 nm-3.5 μm), polydispersed SPIO (PSPIO, 50 nm-150 nm), or ultrasmall SPIO (USPIO, <50 nm). In addition, USPIO nanoparticles with an iron oxide core that is monocrystalline in nature are referred to as monocrystalline iron oxide nanoparticles (MION), and MION with a chemically cross-linked and aminated polysaccharide shell are called cross-linked iron oxide nanoparticles (CLIO).
Over the past few decades, significant technological advances have taken place in an attempt to improve radiologic imaging techniques. One example is the development of the bimodal PET/MRI scanner, which is now finding its way into clinical settings. As the name suggests, the bimodal PET/MRI scanner combines both imaging techniques into a single device. The benefit of this bimodal imaging technique is in its ability to maintain the benefits of each imaging tool individually, thereby producing images of a complementary nature. The bimodal PET/MRI scanner retains excellent sensitivity, high temporal resolution and biological functional imaging through the PET functionalities, whilst high spatial and temporal resolution, details in soft tissue contrast and anatomical information is provided through the MRI imaging modality.
However, despite the fact that a bimodal PET/MRI scanner is commercially available, there are no bimodal or indeed multimodal PET/MRI contrast agents currently available that have received approval from the FDA for use in bimodal PET/MRI imaging in a clinical setting. The access to efficient contrast agents for multimodal PET/MRI imaging would allow appropriate enhancement of the images and potentially improve the utilisation of this technique in the clinic, with the potential to enhance diagnostic accuracy.
The use and development of a number of bimodal or multimodal PET/MRI imaging agents is currently being explored. However, to the best of our knowledge, all of the systems employed to date are still heavily reliant on the use of complexing agents to combine the radionuclides with the nanoparticle core.
Importantly, in regards to current clinical practice, before administration in the patients, radionuclides that have a limited half-life (which means that its efficiency will reduce to half within a certain time, and further exponential decay of activity as time passes), are directly delivered from the source (e.g. a reactor or cyclotron) to the clinic. Technologists or radiochemists then have a very limited time and infrastructure to radiolabel carriers (either particles or chelators) with commercial radionuclides, before administration.
In essence, the majority of the radiometals with physical properties suitable for imaging and/or therapy applications, for example, 64Cu, 89Zr, 99mTc, 111In, 177Lu, 90Y, require the coordination of certain chelators to form stable complexes. Due to the uniqueness of each radionuclide, knowing the particular coordination chemistry and selecting the best chelator with sufficient in vivo stability are a vital, however, highly challenging task. Therefore, the development of a stable radiopharmaceutical that contains both diagnostic and therapeutic radioisotopes, labeled via a simple but effective chelator-free strategy, is highly desirable.
The present invention seeks to provide a multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agent and a process for the synthesis thereof, which will overcome or substantially ameliorate at least some of the deficiencies of the prior art, or to at least provide an alternative.
According to a first aspect of the present invention there is provided a multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agent comprising: a magnetic signal generating core; and a coating portion formed at least partially over a surface of said magnetic signal generating core, wherein the coating portion comprises a plurality of layers, including an inner layer having a functionalized surface, and an outer layer in the form of a radionuclide electrolessly plated layer formed on said functionalized surface.
Suitably, the magnetic signal generating core is a ferromagnetic, paramagnetic or superparamagnetic signal generating core.
In one embodiment, the magnetic signal generating core comprises an oxide, a mixed oxide and/or a hydroxide of at least one metal selected from the group consisting of iron (Fe), cobalt (Co), nickel (Ni), neodymium (Nd), gadolinium (Gd) and manganese (Mn).
In one embodiment, the magnetic signal generating core comprises a support material loaded with at least one metal ion selected from the group consisting of iron (Fe), cobalt (Co), nickel (Ni), neodymium (Nd), gadolinium (Gd) and manganese (Mn).
In one embodiment, the magnetic signal generating core comprises an iron-based material selected from the group consisting of iron (Fe), magnetite (Fe3O4), maghemite (γ-Fe2O3), hematite (α-Fe2O3), an iron alloy and a ferrite material.
In one embodiment, the magnetic signal generating core comprises an alloy of at least one metal selected from the group consisting of iron (Fe), cobalt (Co), nickel (Ni), neodymium (Nd), gadolinium (Gd) and manganese (Mn).
In one embodiment, the alloy is an iron alloy selected from the group consisting of gold-iron oxide (Au—Fe3O4), iron-cobalt (Fe—Co) and iron-platinum (FePt) nanoparticles.
Suitably, the radionuclide is a positron emitter.
In one embodiment, the positron emitter is selected from the group consisting of copper (60Cu, 61Cu, 64Cu), scandium (44Sc), titanium (45Ti), iron (52Fe), manganese (51Mn, 52Mn), cobalt (55Co), gallium (66Ga, 68Ga), arsenic (72As), rubidium (82mRb), strontium (83Sr), technetium (94mTc), yttrium (86Y), zirconium (89Zr) and indium (110In, 111In).
Preferably, the positron emitter is 64Cu.
In one embodiment, the inner layer is formed from a species selected from the group consisting of a metal, a metal oxide, a metal chalcogenide, a metal pnictogenide, a metalloid, a metalloid oxide, a metalloid chalcogenide, a metalloid pnictogenide, a self-assembled monolayer, a polymer, a protein, a carbohydrate and a biopolymer.
Preferably, the inner layer is formed from silica (SiO2).
Preferably, the multimodal PET/MRI contrast agent further comprises at least one fluorophore.
In one embodiment, the at least one fluorophore is coupled to a surface of the second layer.
In one embodiment, the at least one fluorophore is embedded substantially within the inner layer.
Preferably, the multimodal PET/MRI contrast agent further comprises at least one quantum dot.
In one embodiment, the at least one quantum dot is associated with at least one magnetic material to form said magnetic signal generating core.
In one embodiment, the at least one quantum dot is coupled to a surface of the outer layer.
In one embodiment, the at least one quantum dot is embedded substantially within the inner layer.
According to a second aspect of the present invention there is provided a process of synthesizing a multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agent comprising:
contacting a surface of a magnetic signal generating core with a functionalizing solution to form an inner layer at least partially over said magnetic signal generating core to define a functionalized surface;
contacting said functionalized surface with a sensitizing solution containing at least a source of bivalent tin ions to form a tin-sensitized surface;
contacting said tin-sensitized surface with an activator solution containing at least a source of precious metal-ions to form a precious metal-activated surface; and
contacting said precious metal-activated surface with an electroless plating solution containing at least a source of radionuclide ions and a reducing and/or hydrolyzing agent for treating said radionuclide ions to form an electrolessly plated layer of said radionuclide on the precious metal-activated surface.
In one embodiment, the reducing agent is formaldehyde.
In one embodiment, the hydrolyzing agent is an alkali selected from the group consisting of ammonia, lithium hydroxide, sodium hydroxide, potassium hydroxide and ammonium hydroxide.
In one embodiment, the functionalizing solution comprises a tetraethyl orthosilicate (TEOS) precursor, the process further comprising:
polymerizing the TEOS precursor to form the inner layer as a silica (SiO2) shell that at least partially encapsulates the magnetic signal generating core.
Suitably, the step of forming the inner layer to define the functionalizing surface occurs at a pH value that falls within a range of 6 to 14.
In one embodiment, the sensitizing solution comprises tin (II) chloride (SnCl2) as a source of bivalent tin ions.
Suitably, the step of forming the tin-sensitized surface occurs at a pH value that falls within a range of 1 to 8.
In one embodiment, the activator solution comprises palladium nitrate as a source of palladium ions.
Suitably the step of forming the precious metal-activated surface occurs at a pH value that falls within a range of 1 to 13.
Suitably, the radionuclide is a positron emitter.
In a preferred embodiment, the positron emitter is 64Cu.
In one embodiment, the step of forming electroless plating layer occurs at a pH value that falls within a range of 1 to 13.
In one embodiment, the electroless plating solution additionally comprises at least one additive selected from the group consisting of stabilizers, complexing agents and surfactants.
According to a third aspect of the present invention there is provided a multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agent synthesized by a process according to the second aspect.
According to a fourth aspect of the present invention there is provided a pharmaceutical formulation comprising a multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agent as claimed in any one of claims 1 to 16, and a pharmaceutically acceptable excipient, wherein the formulation is suitable for administration to a patient as a multimodal PET/MRI contrast agent, and wherein the multimodal PET/MRI contrast agent is present in the formulation in an amount sufficient to enhance one or more of the following images: a magnetic resonance imaging (MRI) image, a positron emission tomography (PET) image, a single photon emission computed tomography (SPECT) image and a computed tomography (CT) image.
In one embodiment, the pharmaceutically acceptable excipient is a buffered saline.
In one embodiment, the multimodal PET/MRI contrast agent is present in the formulation in an amount ranging from about 0.0001% to about 25% by weight based on the total weight of the formulation.
According to a fifth aspect of the present invention there is provided a method of imaging a region of interest in a patient using multimodal PET/MRI imaging, the method comprising:
administering to a patient a pharmaceutical formulation according to the fourth aspect;
detecting arrival of the multimodal PET/MRI contrast agent present in the formulation in the region of interest by comparing the PET and/or MRI signals in said region of interest during or after administering said formulation;
collecting PET and MRI image data of the region of interest; and
constructing a multimodal PET/MRI image of said region of interest using the PET and MRI image data, wherein the region of interest appears distinct from the background tissue.
In one embodiment, the formulation is administered to the patient by intramuscular or intravenous injection.
Suitably, the patient is one of a human or non-human subject.
According to a sixth aspect of the present invention there is provided a use of a multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agent according to the first aspect in the preparation of a pharmaceutical formulation for imaging a region of interest in a patient using multimodal PET/MRI imaging.
Other aspects of the invention are also disclosed.
Notwithstanding any other forms which may fall within the scope of the present invention, preferred embodiments of the invention will now be described, by way of example only, with reference to the accompanying drawings in which:
It is to be understood that the following description is for the purpose of describing particular embodiments only and is not intended to be limiting with respect to the above description.
The present invention is predicated on the finding of a process for synthesizing multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agents suitable for enhancing the contrast of images obtained during PET/MRI imaging that does away with the need for a chelator or complexing agent to bind the radionuclide responsible for providing the PET signal.
Moreover, the process and the multimodal PET/MRI contrast agents synthesized according to this presently claimed process, represent a significant departure from the chelator-free contrast agents that have previously been developed for the purpose of medical imaging. For instance, the radiolabeled ferrite particles described in US Patent Application No. 2004/0081617 A1 (in the name of Browitt et al.)[1] are obtained via the co-precipitation method, which is notably limited by the fact that the particles resulting from this method are polydispersed with sizes ranging from 5 nm to 200 nm. This limitation not only impacts upon the magnetic properties of the obtained particles (batch to batch variation), but also raises doubts as to the stability, biocompatibility, surface modification and overall suitability of these particles for applications in vivo.
Process
A process of synthesizing a multimodal PET (positron emission tomography)/MRI (magnetic resonance imaging) contrast agent according to a preferred embodiment of the present invention will now be described.
In its simplest form, the process comprises steps to modify a magnetic signal generating core by applying a coating portion in the form of a plurality of layers, in which an inner layer presents a plurality of suitably functionalised surface groups that can be activated to promote the formation of a second layer of an electrolessly plated radionuclide metal around the magnetic signal generating core.
Magnetic Signal Generating Core
As will be appreciated by those skilled in the relevant art, the core of a contrast agent to be used for MRI imaging purposes can be either a ferromagnetic, paramagnetic or superparamagnetic signal generating core. Ferromagnetic materials generally contain iron (Fe), cobalt (Co) or nickel (Ni). Such materials have a large positive magnetic susceptibility when placed in an external magnet field, and have the ability to remain magnetized when the external magnetic field is removed, which is a distinguishing factor when compared to paramagnetic, superparamagnetic, and diamagnetic materials. Paramagnetic materials include oxygen and ions of various metals like iron (Fe) and gadolinium (Gd) for example. These ions have unpaired electrons, resulting in a positive magnetic susceptibility. The magnitude of this susceptibility is significantly less than that of ferromagnetic materials. Superparamagnetic materials on the other hand, consist of individual domains of elements that have ferromagnetic properties in bulk. Their magnetic susceptibility is between that of ferromagnetic and paramagnetic materials.
Thus, for the purposes of the present invention, the magnetic signal generating core of the multimodal PET/MRI contrast agent comprises at least one metal selected from the group consisting of iron (Fe), cobalt (Co), nickel (Ni), neodymium (Nd), gadolinium (Gd) and manganese (Mn).
In one embodiment, the magnetic signal generating core may take the form of an oxide, a mixed oxide and/or a hydroxide of at least one of Fe, Co, Ni, Nd, Gd and Mn. For example, in the case of iron (Fe), the magnetic signal generating core may be produced from an iron oxide selected from the group consisting of magnetite (Fe3O4), maghemite (γ-Fe2O3) and hematite (α-Fe2O3), or a mixture thereof. In the case of gadolinium (Gd), the magnetic signal generating core may take the form of gadolinium hydroxide (Gd(OH)3) nanoparticles. While the case of manganese (Mn), the magnetic signal generating core may take the form of magnesium-based layered double hydroxide (Mn-LDH) nanoparticles.
In another embodiment, the magnetic signal generating core may take the form of an alloy of one or more of these metals (Fe, Co, Ni, Nd, Gd and Mn), potentially in combination with another metal. Alloy-based nanomaterials are described as good candidates for developing T2 contrast agents with higher relaxivities.
In one embodiment, the magnetic signal generating core may take the form of iron-based alloy nanoparticles, such as iron-cobalt (FeCo) and iron-platinum (FePt) nanoparticles. FePt nanoparticles are chemically more stable than Fe and FeCo nanoparticles, and have been shown to have great potential as contrast agents for MRI and computed tomography (CT) imaging. Other iron-based alloy nanoparticles that may find application as a magnetic signal generating core include gold-iron oxide (Au—Fe3O4) nanoparticles.
The substitution of one of the Fe ions in an iron oxide for a different magnetic atom (Mn, Zn, Co, Ni) produces compounds known as ferrites. Such ferrite materials are characterized by their high saturation magnetization, which increases the relaxation rate.
In another embodiment, the magnetic signal generating core of the multimodal PET/MRI contrast agent may take the form of a ferrite material with a spinel-, garnet-, magnetoplumbite-, or other hexagonal structure, such as those disclosed in US Patent Application No. 2007/0258888 A1 (in the name of Feldmann et al.)[3], and which are incorporated herein by reference.
In another embodiment, the magnetic signal generating core may take the form of a support material loaded with at least one metal ion selected from the group consisting of iron (Fe), cobalt (Co), nickel (Ni), neodymium (Nd), gadolinium (Gd) and manganese (Mn).
The magnetic signal generating core of the multimodal PET/MRI contrast agent is not simply limited to just including a magnetic material. Indeed, it is possible to integrate other materials within the core, without impacting negatively on the magnetic properties of the magnetic material.
In one embodiment, the magnetic signal generating core further includes one or more quantum dots to introduce fluorescence imaging as a further mode of imaging, which is complementary to both PET and MRI imaging.
In a preferred embodiment, the inventors have obtained good results when the magnetic signal generating core is formed from iron oxide nanoparticles.
Coating Portion
As indicated above, the coating portion used to coat the magnetic signal generating core includes an inner layer that presents a plurality of suitably functionalised surface groups that can be activated to promote the formation of a second layer of an electrolessly plated radionuclide metal around the magnetic signal generating core.
An inner layer suitable for coating the magnetic signal generating core of the multimodal PET/MRI contrast agent and provide the surface groups necessary for further activation may take one of several forms.
For instance, in one embodiment, the inner layer may take the form of a self-assembled monolayer (SAM) of a plurality of long chain ligands suitably functionalised with groups capable of undergoing reaction with the groups on the surface of the magnetic core. For example, where the magnetic core comprises iron oxide (Fe3O4) nanoparticles, it is possible to modify the surface of the iron oxide particles by silanisation with ligands having a trialkoxy(alkyl)silyl moiety at one end. It will be appreciated that once the SAM has been formed on the surface of the iron oxide particles, the other end of the long chain ligands presents a new surface group that is itself suitably functionalised to be activated to promote the formation of the electrolessly plated radionuclide metal layer, or can be further modified so that it becomes suitably functionalised.
In one embodiment, the inner layer may take the form of a polymer that is suitably functionalised with groups capable of undergoing reaction with the groups on the surface of the magnetic core. For example, where the magnetic core comprises iron oxide (Fe3O4) nanoparticles, it is possible to modify the surface of the iron oxide particles by grafting with suitably terminated polymer chains. Again, it will be appreciated that once the polymer chains have been grafted on the surface of the iron oxide particles, the other end of the polymer chains presents a new surface group that is itself suitably functionalised to be activated to promote the formation of the electrolessly plated radionuclide metal layer, or can be further modified so that it becomes suitably functionalised.
In one embodiment the inner layer may take the form of a shell layer that partially or wholly encapsulates the magnetic signal generating core to realise a core-shell type arrangement. Suitable shells may include metal or metalloid oxide shells such as the oxides, chalcogenides or pnictogenides formed from silicon, titanium, zinc, tin or aluminium.
In the case of silica (SiO2), it will be appreciated by those skilled in the relevant art, that the formation of a silica shell around a central core can be implemented by a number of methods including, but not limited to the Stöber method, reverse emulsion, and the like.
In other embodiments, the inner layer may be formed from another species entirely, such as those selected from the group consisting of a polyelectrolyte, protein, a carbohydrate or biopolymer. Examples may include poly(allylamine hydrochloride), poly(glutamic acid), poly-lysine, poly-styrene and chitosan.
In a preferred embodiment, the inventors have obtained good results when the inner layer takes the form of a silica (SiO2) shell layer to encapsulate the iron oxide nanoparticles to realise a core-shell type arrangement. Specifically, the silica (SiO2) shell layer is formed using the reverse emulsion method by polymerizing a solution (pH in the range of about 6 to about 14) of tetraethyl orthosilicate (TEOS) as precursor to define a functionalized surface suitable for promoting electroless deposition.
Electroless Plating
In general terms, the process of electroless plating requires the use a redox reaction to deposit metal onto a surface of the substrate to be plated without the passage of an electric current. The reaction typically involves the use of a suitable catalyst to facilitate the reduction process of the reaction. The most commonly used catalyst system employs the use of palladium chloride (PdCl2)/tin (II) chloride (SnCl2) catalyst composition in acidic (HCl) solution. Specifically, the substrate surface is first sensitized by immersion in the tin (II) chloride solution, followed by activation in the palladium chloride solution. The activated surface is then exposed to a solution of the metal to be plated.
The inventors have obtained good results when the electroless plating step of the process is conducted by contacting said functionalized surface of the silica (SiO2) shell layer encapsulating the iron oxide nanoparticle core with a sensitizing solution (pH in the range of about 1 to about 8) containing Sn2+ ions using tin (II) chloride (SnCl2) as a source of said bivalent tin ions to form a tin-sensitized surface, contacting the tin-sensitized surface with an activator solution (pH in the range of about 1 to about 13) containing Pd2+ ions using a palladium nitrate solution as a source of said palladium ions, which are subsequently reduced, thereby realising a palladium-activated surface consisting of metallic Pd0 nuclei. The palladium-activated surface is then contacted by an electroless plating solution (pH in the range of about 1 to about 13) containing ions of the radionuclide metal to be plated and a reducing agent to reduce the radionuclide metal ions to form an electrolessly plated layer of the radionuclide metal on the palladium-activated surface of the silica (SiO2) shell layer.
In other embodiments, rather than using a reducing agent, the radionuclide metal may be hydrolyzed to generate the radionuclide metal ions. For instance, the hydrolyzing agent may be an alkali selected from the group consisting of ammonia, lithium hydroxide, sodium hydroxide, potassium hydroxide and ammonium hydroxide.
It will be appreciated by those skilled in the relevant art that the electroless plating solution may additionally comprise one or more additives selected from the group consisting of stabilizers, complexing agents and surfactants.
Radionuclide
For the purposes of the present invention, it will be understood that the radionuclide metal used for realising PET imaging must be a positron emitter with a half-life that is sufficiently long enough to enable a reasonable PET image to be produced. As such, suitable positron emitters may be selected from the group consisting of copper (60Cu, 61Cu, 64Cu), scandium (44Sc), titanium (45Ti), iron (52Fe), manganese (51Mn, 52Mn), cobalt (55Co), gallium (66Ga, 68Ga), arsenic (72As), rubidium (82mRb), strontium (83Sr), technetium (94mTc), yttrium (86Y), zirconium (89Zr) and indium (110In).
In a preferred embodiment, the inventors have obtained good results when the positron emitter is 64Cu with a concentration in the electroless plating solution in the range of between about femtomolar to several tens of Molar. The reducing agent used in this instance is formaldehyde having an equivalent concentration in the range of between about femtomolar to several tens of Molar.
By virtue of the above process, it is possible to bind such radionuclides directly to the surface of the silica (SiO2) shell layer encapsulating the iron oxide nanoparticle core, thereby removing the need for a complexing agent or chelator.
In other embodiments, the hydrolyzing agent is an alkali selected from the group consisting of ammonia, lithium hydroxide, sodium hydroxide, potassium hydroxide and ammonium hydroxide.
Multimodal PET/MRI Contrast Agent
For the purpose of demonstrating one particular preferred embodiment of the present invention, the process for synthesizing multimodal PET/MRI contrast agents will be described in terms of a core-shell nanoparticle arrangement using iron oxide nanoparticles as the magnetic signal generating core, with a coating portion that includes a silica shell inner layer that presents a plurality of silanol groups on the surface of the shell for use in facilitating the formation of an electrolessly plated radionuclide metal outer layer.
Iron Oxide Nanoparticles
According to a first step (A) of the process, nanoparticles having a superparamagnetic iron oxide core were synthesized via a two-stage process. In the first stage, iron oxide nanoparticles were produced by thermal decomposition according to a literature method (Park et al., 2004)[2], which is incorporated herein by reference. In the second stage, the iron oxide nanoparticles obtained via the thermal decomposition method were then purified using a cleaning protocol developed by the present inventors and which forms the subject of International PCT patent application no. PCT/AU2017/050981 (Gammilonghi et al.)[4], which is also incorporated herein by reference. In this respect, the magnetic nanoparticles were purified by washing in a first solvent composition comprising a 1:1 (vol/vol) ratio of diethyl ether and methanol, followed by washing in a second solvent composition comprising a 1:1 (vol/vol) ratio of hexane and ethanol, before finally being dispersed in a third solvent composition comprised of cyclohexane.
Silica-Coated Iron Oxide Nanoparticles
According to a second step (B), a silica (SiO2) shell is grown around the purified iron oxide nanoparticles in order to render the nanoparticles dispersible in polar solvents such as water. The formation of the SiO2 shell on the surface of the purified iron oxide nanoparticles was performed through the formation of a water in-cyclohexane reverse microemulsion according to a literature method (Han et al., 2008)[5], which is incorporated herein by reference, but which has been modified according to a protocol which will now be described. Specifically, the purified iron oxide nanoparticles were first well-dispersed in a cyclohexane solution comprising a suitable surfactant to improve conditions for hydrophilicity. The solution of well-dispersed nanoparticles was then subsequently mixed with tetraethyl orthosilicate (TEOS) in a 1:1 (vol/vol) ratio for a few minutes, followed by the addition of ammonia solution (28 wt. % in water) to form a reverse microemulsion. Silica-coated iron oxide nanoparticles with an overall particle size of about 15 nm (±1 nm) were obtained after 6 hours of reaction under stirring at room temperature. Once the reaction was completed, methanol was added to disrupt the reverse microemulsion, and the silica-coated iron oxide nanoparticles were extracted from the methanol phase using magnetic separation or centrifugation at room temperature.
The inventors have found that the silica-coated purified iron oxide nanoparticles obtained according to the above protocol are readily dispersible in polar solvents such as water, methanol, or ethanol, and the like.
Referring specifically to
As shown in the TEM image in
Tin-Sensitized Silica-Coated Iron Oxide Nanoparticles
To coat the water-dispersible, silica-coated nanoparticle core with a radionuclide requires a three-step ‘sensitization-seeding-deposition’ process adapted from the Applicant's own work (Anderson et al., 2016)[6], which is incorporated herein by reference.
Thus, according to a third step (C), the silica-coated iron oxide nanoparticles obtained from (B) are first dispersed in water. A solution containing 5 mg equivalent of iron is subsequently withdrawn and centrifuged at 10,000 RPM for around 5 minutes to pelletize the nanoparticles. Following removal of the supernatant, the resulting pellet is added to an acidic solution of tin chloride (SnCl2), where it is then mixed and allowed to react for approximately 10 minutes to allow the positive Sn2+ ions to bind to the negatively-charged silica surface. The resulting tin-sensitized silica-coated iron oxide nanoparticles are centrifuged at 10,000 RPM for 5 minutes, followed by rinsing and centrifuging with deionised water to remove any unbound Sn2+ ions.
Palladium-activated silica-coated iron oxide nanoparticles
According to a fourth step (D), the tin-sensitized particles are subsequently exposed to a palladium nitrate solution (Pd(NO3)2.2H2O) for 5 minutes, leading to deposition of metallic Pd0 nuclei on the tin-sensitised silica surface while simultaneously displacing the previously bound Sn2+ ions. During this seeding reaction, the spontaneous formation of Pd0 nuclei or seeds proceeds via the formation of Sn4+ ions during the reduction of Pd2+ to Pd0. The favourable difference in the standard reduction potentials of Pd2+/0 (+0.99 V vs. standard hydrogen electrode—SHE) and Sn4+/2+ (+0.15 V vs. SHE) allows the reaction to proceed spontaneously (Anderson et al., 2016)[6]. The Pd0 layer formed on the silica surface of the iron oxide nanoparticles through the spontaneous reaction between the Sn4+ and Pd2+ ions acts as a catalyst, that is, the silica surface is activated for subsequent radiolabeling.
An ICP-MS analysis (not shown) of the palladium-activated silica-coated iron oxide nanoparticles (5 minutes reaction) post-digestion in concentrated nitric acid reveals that the nanoparticles have the following composition: 114,411:12:1 molar equivalents of Fe, Sn and Pd, respectively. This result confirms the presence of palladium in the sample. Furthermore, the ICP-MS results indicate that with the introduction of palladium into the system, the amount of tin compared to iron in the sample is notably reduced. The inventors believe this to be the result of the replacement of tin on the nanoparticle surface with palladium.
Conveniently, once the silica-coated iron oxide nanoparticles undergo sensitization and seeding as elaborated in steps (C) and (D), the obtained palladium-activated nanoparticles can either be radiolabelled immediately for use in clinical administration or may be stored for radiolabeling at a later stage just prior to clinical administration.
In either case, the palladium-activated silica surface of the iron oxide nanoparticles is radiolabelled with a suitable radionuclide via the technique of electroless deposition as will now be described.
Cold copper plating of palladium-activated silica-coated iron oxide nanoparticles
In order to optimise the copper plating process while minimising cost and radioactive (hot) waste generation, the copper plating bath was developed using non-radioactive (cold) copper as a model system. To minimise variation between this cold system and the radioactive 64Cu, an acidified copper chloride [pH 1.0, 10-12 M] was initially used, as discussed in the current examples. This is because 64Cu is produced in copper chloride form and is delivered in a hydrochloric acid solution of pH 1.0.
More specifically, and according to a fifth step (E), a solution of the palladium-activated silica-coated iron oxide nanoparticles from step (D) in water is subjected to magnetic separation to isolate a wet pellet containing the palladium-activated silica-coated iron oxide nanoparticles from the supernatant. Sodium hydroxide (or any other alkali such as potassium hydroxide) is added to the wet pellet, followed immediately by sodium potassium tartrate. In the subsequent step, a solution of the desired cold copper source is introduced. This is followed by the addition of the formaldehyde reducing agent. The order in which the reactants are added is significant. Furthermore, the rate of reaction can be controlled through temperature.
Since the reaction is performed in water, the optimisation was restricted to the sub-boiling point of the solvent, (specifically 80° C. in the current case). However,
Once the reaction is complete, the resulting particles are rinsed twice with deionised water using magnetic separation or centrifugation to remove any remaining reactants or by-products. The resulting pellet is then dispersed in a suitable solvent (typically water, saline, buffer or biological growth media) through 2 minutes of sonication (other forms of mixings such as agitation, pipetting, vortexing for varying amounts of time are also possible) to obtain the electrolessly deposited copper plated iron oxide nanoparticles.
As shown in
Elemental mapping of these non-radioactive electrolessly deposited copper plated iron oxide nanoparticles using EDX in
When compared to the T2 value (196.9 mol−1) calculated for the purified iron oxide nanoparticles (see
Radioactive 64Cu Plating of Palladium-Activated Silica-Coated Iron Oxide Nanoparticles
Once the copper bath protocol had been optimised for cold copper, the electroless plating process was carried out using 64Cu as the ‘hot’ copper source. This was achieved by following the same protocol as detailed above with the minor variation of using 64Cu instead of cold copper. It is known that the concentration of copper ions in commercially obtained 64Cu is of the order of femtomolars. However, this copper concentration varies from batch-to-batch. Typically, the known concentration of received commercial radioactive agents is defined as MegaBecquerels (MBq). Therefore, in the current example, a fixed MBq concentration of 64Cu was employed. The commercially obtained 64Cu was diluted to 80 MBq/mL.
The fifth step (E) of the presently claimed process was repeated this time using the radioactive (64Cu) from the stock solution, and the reaction was carried out at 80° C. for 45 minutes to afford radioactive electrolessly deposited copper plated silica-coated iron oxide nanoparticles.
It is known that 64Cu has a half-life of 12.7 hours, typically decaying into nickel. Thus, these radioactive electrolessly deposited copper plated iron oxide nanoparticles were analysed after a week to allow the 64Cu radioactivity to decay to safe handling levels.
There is a noticeable correlation between increasing reaction rate and increasing temperature, as reflected from the temperature-dependent loading data obtained for non-radioactive copper (
Since the concentration of 64Cu in the radioactive electrolessly copper plated iron oxide nanoparticles is very low (on the femtomolar level), and thus approaching the detection limit of the elemental mapping equipment, the inventors employed Radio—instant thin layer chromatography (Radio-ITLC) as a more sensitive technique to measure the 64Cu concentration. Radio-ITLC employs a chelating agent such as ethylenediaminetetraacetic acid (EDTA), which has high affinity towards metal ions, and is capable of stripping off loosely-bound 64Cu from the surface of the silica-coated iron oxide nanoparticle assembly, thus providing an assessment of the binding efficacy of 64Cu to the nanoparticle.
For the Radio-ITLC analysis, 2 μl L of a solution of the radioactive electrolessly copper plated iron oxide nanoparticles is spotted onto one end of a piece of TLC paper. The spotted end of the TLC paper was then placed in 1 mL of 10 mM phosphate buffer containing 10% wt/vol EDTA. The poorly-bound 64Cu and free 64Cu ions will bind to the EDTA and migrate with the solvent front. Conversely, any 64Cu that is rigidly bound to the nanoparticles is expected not to migrate (or show inhibited migration) due to large size of particles. The sample was allowed to migrate on TLC paper for 2 minutes or until the solvent front reached 1 cm from the top end of the TLC paper, followed by drying for 2 minutes, before being run on a Radio-ITLC reader (
As shown in
In contrast,
Formulation
Specifically, the multimodal PET/MRI contrast agent as described above is combined with a suitable pharmaceutically acceptable excipient to provide a formulation suitable for administration to a human or non-human subject by oral, intramuscular or intravenous injection. Once formed, the formulation can then be used for imaging a region of interest in the subject using multimodal PET/MRI imaging.
In one embodiment, the pharmaceutically acceptable excipient is a buffered saline.
The multimodal PET/MRI contrast agent is present in the formulation in an amount sufficient to enhance one or more of the following images: a magnetic resonance imaging (MRI) image, a positron emission tomography (PET) image, a single photon emission computed tomography (SPECT) image and a computed tomography (CT) image.
As will be described in more detail below, the inventors have obtained good results when the multimodal PET/MRI contrast agent is present in the formulation in an amount ranging from about 0.0001% to about 25% by weight based on the total weight of the formulation.
PET/MRI Imaging Method
To investigate the imaging capability of the as-prepared formulation, the inventors have conducted a study on a live mouse subject, the method of which will now be described.
Specifically, the formulation as described above was administered to a six week old female mouse (C57BL/6) by intravenous tail vein injection. The arrival of the multimodal PET/MRI contrast agent in the region of interest in the subject was detected by comparing the PET and/or MRI signals in the region of interest during or after administering the formulation. The PET and MRI image data of the region of interest was then collected using a multimodal PET/MRI scanner, and multimodal PET/MRI images of the region of interest were then constructed using the PET and MRI image data and visualized using suitable software. Specifically, for PET/MRI imaging of animals, the instrument used was a Bruker ClinScan PET-MR scanner comprising of a 300 mm bore 7 Tesla ClinScan, running Siemens VB17, and removable PET insert containing 3 rings of 16 detector blocks with 15×15 LSO crystals (1.6×1.6×10 mm) per block, at the centre of the magnet bore operating under Siemens Inveon Acquisition Workplace (IAW) software. A 72 mm ID rat body MRI rf coil inside the PET ring was used to acquire whole mouse images simultaneously with the PET acquisition.
As shown in the
The MRI part of the image of
The three images in each of these two figures show the mouse observed at different angles. The images on the left looks at the transverse view of the mouse, wherein a significant darkening is observed in the MRI signal (
A typical biodistribution pathway for iron-based nanoparticles intravenously administered in a live subject involves the route of travel through the heart, lungs and liver/spleen, followed subsequently by clearing or purging through the gastro-intestinal (GI) tract of the subject. However, it is often observed that coating of different materials including silica, polymers, surface functionalising agents, etc., of iron-based materials results in uncontrolled lodgement of nanomaterials, particularly in the lungs and heart, which is a major issue for in vivo biomedical imaging.
The observations from the multimodal PET/MRI contrast agent according to the preferred embodiment of the present invention are particularly exciting, as most of the multimodal PET/MRI contrast agent has been cleared from the lungs within 18 hours post administration. This is even more exciting as the multimodal PET/MRI contrast agent does not employ any specific strategy such as PEGylation or targeting agents to circumvent lodgement of particles in organs and tissues.
To fully understand the biodistribution profile of the multimodal PET/MRI contrast agent, the inventors intravenously administered a two day old post-synthesized multimodal PET/MRI contrast agent [2 MBq equivalent of 64Cu along with 200 μg equivalent of Fe] into a second six week old C57BL/6 female mouse via tail vein injection, followed by PET imaging 15 minutes post-administration (see
When the second mouse was dissected, it was determined that the bulk of the observed radiation was located in the liver (1.36 MBq) and kidneys (0.11 MBq), with minor levels being detected in the heart (0.04 MBq), lungs (0.03 MBq), spleen (0.08 MBq) and blood (0.04 MBq). The observed biodistribution results support the theory that within the 15 minutes post-intravenous injection, the multimodal PET/MRI contrast agent had travelled via the bloodstream through the heart and lungs with minimal lodgement in these organs, before reaching the liver and kidneys, where the immediate process of purging the multimodal PET/MRI contrast agent from the body of the second mouse began.
Interestingly, no radiation was detected in the muscles of the second mouse. The inventors consider this to be a promising result, as it indicates that the multimodal PET/MRI contrast agent did not leach out of the gastrointestinal (GI) tract into the organs of the mouse during the procedure. Indeed, any unintended accumulation of the electrolessly deposited copper plated silica-coated iron oxide nanoparticles in the non-target organs of a live subject may result in toxicity.
A comparison of the images in
The multimodal PET/MRI contrast agent based on 64Cu described above demonstrates that the palladium-activated silica-coated iron oxide nanoparticles may act as a template to bind a variety of potential radionuclides to create multimodal imaging and therapeutic agents.
Indium Plating of Palladium-Activated Silica-Coated Iron Oxide Nanoparticles
To test this theory, the inventors employed the same process to electrolessly plate the palladium-activated silica-coated iron oxide nanoparticles with indium ions (In3+) as an example of metal ions in the +3 oxidation state. The electroless plating process in this example was carried out using a cold indium source. To minimise any variation between this cold system and the radioactive 111In, a stock solution of acidified indium chloride (InCl3) [pH 1.0, 10−6 M] was used as the source of metal ions. This is because 111In is produced in indium chloride form and delivered in a hydrochloric acid solution pH 1.0 from the commercial source.
For cold indium deposition, the palladium-activated silica-coated iron oxide nanoparticles in wet pellet form are exposed to an “indium metal bath” comprising: aqueous sodium hydroxide, followed immediately by aqueous sodium potassium tartrate, subsequently followed by acidified indium chloride, immediately followed by addition of aqueous formaldehyde as the reducing agent. The reaction is then heated to 80° C. for 45 minutes. Once the reaction is complete, the product is obtained, in the same manner as detailed above with respect to the non-radioactive and radioactive electrolessly deposited copper plated silica-coated iron oxide nanoparticles.
As shown in
As shown in
Further, while not discussed above, the inventors expect that silica shells with different thicknesses may play an influential role in controlling the amount of metal loading. Further, as shown for copper loading with respect to the non-radioactive and radioactive electrolessly deposited copper plated silica-coated iron oxide nanoparticles, indium loading may also be controlled by varying the reaction time and temperature as well as the metal salt concentration.
An ICP-MS analysis (not shown) of these electrolessly deposited indium plated silica-coated iron oxide nanoparticles, post-digestion in concentrated nitric acid reveals that the electrolessly deposited indium plated silica-coated iron oxide nanoparticles observed in
Yttrium Plating of Palladium-Activated Silica-Coated Iron Oxide Nanoparticles
To further test this theory, the inventors employed the same process to electrolessly plate the palladium-activated silica-coated iron oxide nanoparticles with yttrium ions (Y3+) as another example of metal ions in the +3 oxidation state. The electroless plating process in this example was carried out using a cold yttrium source in the form of yttrium nitrate hexahydrate (Y(NO3)3.6H2O) as the metal ion source.
As shown in
An ICP-MS analysis (not shown) of the electrolessly deposited yttrium plated silica-coated iron oxide nanoparticles dissolved in nitric acid, reveals the following composition: 7.7 molar equivalents of yttrium per molar equivalent of Fe, which confirms that a large amount of yttrium is loaded onto the surface of the silica-coated iron oxide nanoparticles.
Zirconium Plating of Palladium-Activated Silica-Coated Iron Oxide Nanoparticles
To test this theory still further, the inventors employed the same process to electrolessly plate the palladium-activated silica-coated iron oxide nanoparticles with zirconium ions (Zr4+) as an example of metal ions in the +4 oxidation state. The electroless deposition process in this example was carried out using a cold zirconium source in the form of zirconium oxychloride ([Zr4(OH)8(H2O)16]Cl8(H2O)12) as the metal ion source.
Again, the inventors consider that since no effort was made to optimise the metal ion concentration needed to obtain monodispersed nanoparticles, wherein the metal ion concentration was again 6 to 9 orders of magnitude lower than that employed for copper deposition as described above, those persons skilled in the relevant art may appreciate that a uniform zirconium coating may be achieved by controlling the reaction temperature, time and concentration of the employed zirconium source, as was seen for the other examples described above.
As shown in
An ICP-MS analysis (not shown) of the electrolessly deposited zirconium plated silica-coated iron oxide nanoparticles dissolved in nitric acid, reveals the following composition: 0.31 molar equivalents of zirconium per molar equivalent of Fe, which confirms that zirconium can also be loaded onto the surface of the silica-coated iron oxide nanoparticles.
The embodiments of the present invention described herein provide a process for the synthesis of multimodal PET/MRI contrast agents (commonly referred to as imaging agents). These multimodal PET/MRI contrast agents can either be used independently for diagnostic imaging with gamma emitters for nuclear scintigraphy, positron emission tomography (PET) imaging, magnetic resonance imaging (MRI), or independently for radionuclide therapy applications, or simultaneously for multimodal imaging applications such as PET/MRI or alternatively for simultaneous imaging and radionuclide therapy applications or theranostic applications.
The demonstrated methodology for synthesizing these multimodal PET/MRI contrast agents shows the ability to convert (reduce or hydrolyse or deposit) a number of radionuclides (or radioactive elements) from each respective oxidation group (2+, 3+and 4+) including but not limited to: 64Cu, 89Y, 111In and 89Zr, onto the surface of a carrier particle (the demonstrated carrier being oxide, more specifically being iron oxide core containing a thin silica shell) by electroless deposition or plating.
While the demonstrated systems have focused on both PET imaging and MRI base applications as target; those persons skilled in the relevant art will be able to apply the same methodology for any radionuclide (for example, for diagnostic applications, radionuclide therapy applications and/or imaging or theranostic applications) using any carrier particle, particularly those that show a surface chemistry similar to those revealed by oxides, in general. More specifically, in the current methodology, the direct loading of radionuclides onto the surface of a silica shell within which is encapsulated a magnetic nanoparticle will also mean that those persons skilled in the relevant art will readily understand that this same proposed process can be applied to any silica/silicate surface, irrespective of the size, shape and composition of the underlying core particle that is encapsulated by the silica shell. It will also be apparent to those same persons that the proposed process of radionuclide loading can also be readily applied on materials other than silica that have a similar chemical structure to that of the silica surface, such as rich in hydroxyl groups.
The current use of radionuclides for certain applications is limited by the requirement of chelators. These complexing agents are used in order to bind radionuclides to pharmaceuticals, proteins, peptides, targeting agents or directly to biological structures such as cells. The dependence of chelators for conjugating radionuclides causes limitations such as, but not limited to, specific chelator to radionuclide binding, specific chelator to targeting agent binding, limited binding sites for radionuclides on targeting agent, limitation of further surface modification due to surface area of the targeting agent core structure taken up by complexing agent, resulting in a bulky final formulation, lengthy synthesis process and complex size and charge separation processing post-synthesis. In addition to this, for a cell based application the current chelator-based radionuclide formulations often suffer from a common lack of efficiency in cell retention and upon in vivo administration can lead to significant non-specific uptake. Therefore, converting a radionuclide into an inorganic particle should address each of these above mentioned limitations and in particular allow cells to retain these radionuclides. It should be appreciated that those experts in the field may like to employ the methodology presented here to further modify the invention and prepare an imaging agent with alternate capabilities (CT, ultrasound, X-ray, etc.). Further the invention may act as a carrier with or without modification. The proposed systems are also possible for tissue targeted applications, including binding of targeting agents (nucleotides, aptamers, proteins, antibodies, carbohydrate, lectins, etc.) on the nanoparticle surface using a number of methodologies available in the open literature.
The various embodiments of the invention as described herein demonstrate just one potential application of the synthesised systems (iron oxide core particle/thin silica shell/Cu64 radionuclide and extended for 89Zr, 89Y, 111In) as a multimodal PET/MRI contrast agent. This nanoparticle-based multimodal PET/MRI contrast agent system also provides scope for other applications including but not limited to: multimodal PET/MRI imaging of proteins, peptides, and pharmaceuticals, together with the possibility of in vivo cell tracking and the like.
This multimodal PET/MRI contrast agent is not limited to T2 materials; in fact the described embodiments of the present invention provide a platform for further modification and use. With the design of the material in the present invention, simple substitution of the core from a T2 SPIO to a T1 agent such as gadolinium provides the possibility to further explore and exploit the virtues of the commercially available multimodal PET/MRI scanner.
Materials and Methods
All chemicals were used as received. All chemicals and solvents were obtained from Sigma-Aldrich Australia and used without further purification.
All aqueous solutions and reagents used in the synthesis were prepared using deionized water purified using a Milli-Q™ reverse osmosis system unless otherwise stated.
Preparation of Iron Oxide Nanoparticles
Nanoparticles having a superparamagnetic iron oxide core were synthesized via a two-stage process.
In the first stage, iron oxide nanoparticles were produced by thermal decomposition according to a literature method (Park J. et al., 2004)[2] , which is incorporated herein by reference. Specifically, the first stage process was carried out by synthesising an iron oleate complex by dissolving 3.24 g of iron chloride and 18.25 g of sodium oleate in a solution comprised of 40 mL ethanol, 30 mL distilled water and 70 mL hexane. Once homogenized, the solution was refluxed at 70° C. for 4 hours. Separation of the upper organic layer was carried out using a separatory funnel. Once separated, the iron oleate layer was washed twice with deionised water and separated again using a separatory funnel. Finally, the hexane was evaporated off leaving a waxy iron oleate complex. The iron oxide nanoparticles were formed by dissolving 10 g of the iron oleate complex in 1.77 g of oleic acid and 60.3 mL of 1-octadecene, followed by refluxing at 320° C. under nitrogen for 30 minutes. The resulting mixture was then allowed to cool to room temperature.
In the second stage, the iron oxide nanoparticles obtained via the thermal decomposition method were then purified using a cleaning protocol developed by the present inventors and which forms the subject of International PCT Application No. PCT/AU2017/050981 (Gammilonghi et al.)[4], which is incorporated herein by reference. In this respect, the magnetic nanoparticles were purified by washing 1 mL of impure iron oxide nanoparticles with 49 mL of a first solvent composition comprising a 1:1 (vol/vol) ratio of diethyl ether and methanol, followed by magnetic separation of particles, and subsequent washing with 20 mL of a second solvent composition comprising a 1:1 (vol/vol) ratio of hexane and ethanol, before finally dispersing the purified iron oxide nanoparticles in a third solvent composition comprised of cyclohexane.
Preparation of Silica-Coated Iron Oxide Nanoparticles
Typically, 0.5 mL of polyoxyethylene (5) nonylphenyl ether (Igepal CO-520) was added to 11 mL of cyclohexane, followed by addition of 20 μL of a 2.5 mg/mL (Fe equivalent concentration) cyclohexane solution of the above-prepared and well-dispersed nanoparticles. This solution was mixed at 300 RPM of 10 minutes before 20 μL of tetraethyl orthosilicate (TEOS) was added. The solution was then allowed to mix for a further 5 minutes before 100 μL of ammonia solution (28 wt. % in water) was added under stirring at 300 RPM to form a reverse microemulsion. Silica coated iron oxide nanoparticles with an overall particle size of 15 nm (±1 nm) were obtained after 6 hours of reaction under stirring at room temperature. Once the reaction was completed, 10 mL of methanol was added to disrupt the reverse microemulsion, and the silica-coated iron oxide nanoparticles were extracted from the methanol phase using magnetic separation or centrifugation (10,000 RPM 10 minutes at room temperature).
Preparation of tin-sensitized silica-coated iron oxide nanoparticles
The surface of the SiO2 shell around the iron oxide nanoparticles is sensitized with tin using an acidic solution of tin chloride (SnCl2). To achieve this, iron oxide nanoparticles containing 5 mg equivalent of iron in water are magnetically precipitated, and in the wet pellet, acidic tin chloride solution [5 mL, 3 mM, pH 1.0] is added and allowed to react for 10 minutes. This results in the binding of Sn2+ ions to the negatively charged silica surface. After 10 minutes, the particles are rinsed twice with 5 mL of deionised water to remove any unbound Sn2+ ions using magnetic separation. This particle separation can also be achieved through centrifugation 10,000 RPM for 5 minutes. The resulting nanoparticles were then characterised using TEM and electron-dispersive X-ray spectroscopy (EDX).
Preparation of palladium-activated silica-coated iron oxide nanoparticles
Seeding of palladium onto the tin-sensitised iron oxide nanoparticles is achieved by exposing the magnetically-separated particles to an aqueous palladium nitrate solution (Pd(NO3)2.2H2O) [5 mL, 3 mM] for 5 minutes, leading to deposition of metallic Pd0 nuclei on the surface of the silica shell, while simultaneously displacing the previously bound Sn2+ ions. During this reaction, the spontaneous formation of Pd0 nuclei proceeds via the formation of Sn4+ ions during the reduction of Pd2+ to Pd0.
Preparation of Electrolessly Deposited Metal Plated Silica-Coated Iron Oxide Nanoparticles
For metal deposition, the palladium-activated silica-coated iron oxide nanoparticles from step (D) are subjected to magnetic separation to isolate a wet pellet containing the palladium-activated silica-coated iron oxide nanoparticles [200 μg equivalent of Fe in the wet pellet] from the supernatant. The resulting wet pellet is exposed to a metal bath comprising: aqueous sodium hydroxide [125 μL, 1 M], followed immediately by aqueous sodium potassium tartrate [125 μL, 0.3 M], subsequently followed by an acidified metal ion source [250 μL, 10-6 M, pH 1.0], immediately followed by addition of aqueous formaldehyde [500 μL, 1 M] as the reducing agent. Once the reaction is complete, the resulting particles are rinsed twice with (1 ml) deionised water using magnetic separation or centrifugation (10,000 RPM for 5 minutes) to remove any remaining reactants or by-products. The resulting pellet is then dispersed in (0.1 ml) of a suitable solvent (typically water, saline, buffer or biological growth media) through 2 minutes of sonication to obtain the electrolessly metal plated silica-coated iron oxide nanoparticles.
Measurement of PET/MRI
Multimodal PET/MRI images were collected using a Bruker ClinScan PET-MR scanner comprising of a 300 mm bore 7 Tesla ClinScan, running Siemens VB17, and removable PET insert containing 3 rings of 16 detector blocks with 15×15 LSO crystals (1.6×1.6×10 mm) per block, at the centre of the magnet bore operating under Siemens Inveon Acquisition Workplace (IAW) software. A 72 mm ID rat body MRI rf coil inside the PET ring was used to acquire whole mouse images simultaneously with the PET acquisition. (Bruker, Germany).
Multimodal PET/MRI contrast agents with a fixed radioactivity dose (3.17 MBq equivalent of 64Cu along with 80 μg equivalent of Fe in the first mouse and 2 MBq equivalent of 64Cu along with 200 μg equivalent of Fe in the second mouse) were injected into a six week old female mouse (C57BL/6) by intravenous tail vein injection and the intensity of the multimodal PET/MRI contrast agent both pre- and post-injection were observed at several timepoints. Multimodal PET/MRI images were visualized by Siemens Inveon Acquisition Workplace (IAW) software.
Advantages
The multimodal PET/MRI contrast agents described in the preferred embodiments of the present invention have the potential to be used in several applications, including but not limited to:
1. Cell therapy applications
2. Diagnostic imaging
3. Therapy
4. Theranostic applications.
Importantly, the radionuclide employed in the multimodal PET/MRI contrast agent of the present invention is present without the need of a chelator or linker to link the radionuclide to the nanoparticle. This offers two of the biggest advantages from the perspective of application in vivo: (i) a chelator-free approach allows the radionuclide [PET agent] to bind robustly to the surface of the MRI contrast agent and therefore avoid non-specific leaching during imaging, and (ii) the multimodal PET/MRI contrast agent obtained by this approach can be easily surface modified for conjugation of targeting agents such as nucleotides, aptamers, proteins, antibodies, carbohydrate, lectins, and the like.), or other labelling agents such as fluorophores, if desired.
The inventors have demonstrated that it is possible to electrolessly deposit a range of radionuclide metals from the +2, +3 and +4 oxidation states onto the surface of the as-prepared silica-coated iron oxide nanoparticles, thereby offering a generalised approach to prepare many types of imaging and therapeutic agents.
Moreover, by virtue of the synthesis being a two-step process, it is possible to prepare the silica-coated iron oxide nanoparticles beforehand, and then electrolessly deposit the radionuclide on to the surface of the silica-coated iron oxide nanoparticles at a later stage (if necessary) within standard clinical settings prior to the resulting multimodal PET/MRI contrast agent being administered to a live subject. In this respect, there is minimal loss of radioactivity.
In other embodiments, it will be appreciated by those skilled in the relevant art that the multimodal PET/MRI contrast agent is not limited to that described above. For instance, the fluorophore described above is not simply limited to being quantum dots loaded within the magnetic core. For example, the fluorophore may be a dye impregnated within the silica (SiO2) shell layer or a dye or indeed quantum dots coupled to the radionuclide metal layer. It will be appreciated that the binding of the fluorophore to the surface of the PET/MRI contrast agent may be achieved by any one of a number of coupling technologies.
[1] US Patent Application No. 2004/0081617 A1 (Browitt et al.).
[2] Park, J., et al., Nature Materials, 2004, vol. 3, 891-895.
[3] US Patent Application No. 2007/0258888 A1 (Feldmann et al.).
[4] International PCT Patent Application No. PCT/AU2017/050981 (Gammilonghi et al.).
[5] Han, Y., et al., 2008, Langmuir, 24, 5842-5848.
[6] Anderson et al., 2016, Advanced Materials Interfaces, 2016, 3, 1500632-1-8.
Whenever a range is given in the specification, for example, a temperature range, a time range, or concentration range, all intermediate ranges and subranges, as well as all individual values included in the ranges given are intended to be included in the disclosure. It will be understood that any subranges or individual values in a range or subrange that are included in the description herein can be excluded from the claims herein.
All definitions, as defined and used herein, should be understood to control over dictionary definitions, definitions in documents incorporated by reference, and/or ordinary meanings of the defined terms.
Throughout this application, the term “about” is used to indicate that a value includes the inherent variation of error for the device, the method being employed to determine the value, or the variation that exists among the study subjects.
The indefinite articles “a” and “an,” as used herein in the specification, unless clearly indicated to the contrary, should be understood to mean “at least one.”
The phrase “and/or,” as used herein in the specification, should be understood to mean “either or both” of the elements so conjoined, i.e., elements that are conjunctively present in some cases and disjunctively present in other cases. Multiple elements listed with “and/or” should be construed in the same fashion, i.e., “one or more” of the elements so conjoined. Other elements may optionally be present other than the elements specifically identified by the “and/or” clause, whether related or unrelated to those elements specifically identified. Thus, as a non-limiting example, a reference to “A and/or B”, when used in conjunction with open-ended language such as “comprising” can refer, in one embodiment, to A only (optionally including elements other than B); in another embodiment, to B only (optionally including elements other than A); in yet another embodiment, to both A and B (optionally including other elements); etc.
Spatially relative terms, such as “internal,” “outer,” “beneath,” “below,” “lower,” “above,” “upper,” and the like, may be used herein for ease of description to describe one element or feature's relationship to another element(s) or feature(s) as illustrated in the Figures. Spatially relative terms may be intended to encompass different orientations of the device in use or operation in addition to the orientation depicted in the Figures.
While the invention has been described in conjunction with a limited number of embodiments, it will be appreciated by those skilled in the art that many alternatives, modifications and variations in light of the foregoing description are possible. Accordingly, the present invention is intended to embrace all such alternatives, modifications and variations as may fall within the spirit and scope of the invention as disclosed.
Where the terms “comprise”, “comprises”, “comprised” or “comprising” are used in this specification (including the claims) they are to be interpreted as specifying the presence of the stated features, integers, steps or components, but not precluding the presence of one or more other features, integers, steps or components, or group thereof.
The present application may be used as a basis or priority in respect of one or more future applications and the claims of any such future application may be directed to any one feature or combination of features that are described in the present application. Any such future application may include one or more of the following claims, which are given by way of example and are non-limiting in regard to what may be claimed in any future application.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2018901483 | May 2018 | AU | national |
