US20120087857A1 - Gadolinium expressed lipid nanoparticles for magnetic resonance imaging - Google Patents

Gadolinium expressed lipid nanoparticles for magnetic resonance imaging Download PDF

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US20120087857A1
US20120087857A1 US13/208,100 US201113208100A US2012087857A1 US 20120087857 A1 US20120087857 A1 US 20120087857A1 US 201113208100 A US201113208100 A US 201113208100A US 2012087857 A1 US2012087857 A1 US 2012087857A1
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lipid
nanoparticle
dtpa
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dspe
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Rodney J.Y. Ho
John D. Hoekman
Ken Maravilla
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University of Washington
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Assigned to WASHINGTON, UNIVERSITY OF reassignment WASHINGTON, UNIVERSITY OF ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: HO, RODNEY J.Y., MARAVILLA, KEN, HOEKMAN, JOHN D.
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    • A61K49/06—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/08—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by the carrier
    • A61K49/085—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by the carrier conjugated systems
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    • A61K49/18—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes
    • A61K49/1818—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles
    • A61K49/1821—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles
    • A61K49/1824—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles
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    • A61K49/1818—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles
    • A61K49/1821—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles
    • A61K49/1824—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles
    • A61K49/1878—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles the nanoparticle having a magnetically inert core and a (super)(para)magnetic coating
    • A61K49/1881—Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes particles, e.g. uncoated or non-functionalised microparticles or nanoparticles coated or functionalised microparticles or nanoparticles coated or functionalised nanoparticles the nanoparticle having a magnetically inert core and a (super)(para)magnetic coating wherein the coating consists of chelates, i.e. chelating group complexing a (super)(para)magnetic ion, bound to the surface
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    • A61K51/065—Macromolecular compounds, carriers being organic macromolecular compounds, i.e. organic oligomeric, polymeric, dendrimeric molecules conjugates with carriers being macromolecules
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    • A61K51/1217—Dispersions, suspensions, colloids, emulsions, e.g. perfluorinated emulsion, sols
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    • A61K51/1244—Preparations containing radioactive substances for use in therapy or testing in vivo characterised by a special physical form, e.g. emulsion, microcapsules, liposomes, characterized by a special physical form, e.g. emulsions, dispersions, microcapsules particles, powders, lyophilizates, adsorbates, e.g. polymers or resins for adsorption or ion-exchange resins microparticles or nanoparticles, e.g. polymeric nanoparticles
    • A61K51/1251—Preparations containing radioactive substances for use in therapy or testing in vivo characterised by a special physical form, e.g. emulsion, microcapsules, liposomes, characterized by a special physical form, e.g. emulsions, dispersions, microcapsules particles, powders, lyophilizates, adsorbates, e.g. polymers or resins for adsorption or ion-exchange resins microparticles or nanoparticles, e.g. polymeric nanoparticles micro- or nanospheres, micro- or nanobeads, micro- or nanocapsules
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Definitions

  • MR imaging Magnetic resonance (MR) imaging has become a powerful and non-invasive tool for detecting the spread of cancer to the lymph nodes.
  • Standard MR imaging relies on size and morphology criteria to determine occult lymphoid tissues including lymph node metastasis, which has as low as 60% accuracy.
  • MR contrast enhancing agents are becoming more widely used due to their usefulness in early tumor detection. Contrast enhancing agents diffuse into metastatic lymph nodes and healthy lymph nodes at different rates causing “filling defects.” Predicting lymph node metastasis using filling defects from contrast agents as opposed to size criteria can increase the sensitivity from 29% to 93%.
  • MR contrast enhancing agents there are two types.
  • Superparamagnetic contrast agents have a low r2/r1 ratio and create dark spots in T2- and T2*-weighted images. These are usually based on iron oxide particles and are referred to as negative contrast agents.
  • paramagnetic contrast agents increase the r1 relaxivity and have a high r2/r1 ratio, creating bright spots in T1 weighted MR images.
  • These contrast agents are known as positive contrast agents and are usually complexes of gadolinium (Gd 3+ ).
  • Gd 3+ is a heavy metal toxin, it is commonly delivered as a tightly bound linear or macroscopic chelate. Chelated forms of Gd 3+ reduce toxicity by preventing cellular uptake of free Gd 3+ and by limiting the clearance almost exclusively to renal filtration that resulted in renal toxicities. Despite reducing toxicity, the rapid clearance and small molecular size of gadolinium chelates mean that low levels of Gd 3+ accumulates in the lymph nodes, making these agents a poor choice for MR lymphography. In addition, the FDA posted a warning about the risk of serious nephrogenic systemic fibrosis for all commercially available gadolinium contrast agent to identify well-perfused tissues and organs in subjects with acute or chronic renal insufficiency.
  • Liposomes and lipid nanoparticles containing Gd 3+ have several advantages for MR contrast imaging of lymph nodes. Liposomes as well as lipid nanoparticles can lower the toxicity by encapsulating or binding to their surfaces a large amount of Gd 3+ . However, the rapid clearance mechanism of intravenously (IV) administered liposomes does not significantly improve liposome-associated Gd 3+ accumulation in the lymph nodes. Only a fraction of the lipid nanoparticles in blood are phagocytosed by reticuloendothelial cells, and only a fraction of those cells traverse to lymphatic system. Thus, IV administered liposomes provide indirect targeting of the lymphatic system and lymph nodes.
  • gadolinium chelated with diethylenentriaminepentaacetyl provides contrast in magnetic resonance imaging to identify pathogenic tissues.
  • DTPA diethylenentriaminepentaacetyl
  • the soluble Gd-DTPA complexes approved for clinical use such as OMNISCAN, are cleared within a few minutes and do not provide sufficient concentrations or time in lymphoid tissues.
  • the residual fraction of gadolinium can lead to fibrosis in patients with renal insufficiency.
  • contrast agents Despite the advances in the development of contrast agents, a need exists for improved contrast agents having longer in vivo life, provide sufficient concentration in tissues to be analyzed, and low residual gadolinium concentrations to avoid side effects.
  • the present invention seeks to fulfill this need and provide further related advantages.
  • the present inventions provides compositions expressing metal ions and methods for using the compositions.
  • the invention provides a composition, comprising a lipid, a polyalkylene-containing lipid, and a lipid-containing metal chelator.
  • Representative lipids include phospholipids, sphingolipids, cholesterol and steroid derivatives, bile acids and derivatives, cardilipin, acyl-glycerides and derivatives, glycolipids, acyl-peptides, fatty acids, carbohydrate-based polymers, functionalized silica, polyanhydride polymers, polylactate-glycolate polymers, and bioploymers.
  • the lipid is a phospholipid.
  • Representative phospholipids include 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC); dipalmitoyl phosphatidylcholine;
  • dimysristoyl phosphatidyl choline dimysristoyl phosphatidyl choline; dioleoyl phosphatidyl choline; trans-esterified phospholipids derived from eggs, soybean, flaxseed, and the like; and phosphatidylcholine substituted with phosphatidyl ethanolamine, phosphatidylglycerol, phosphatidyl serine, and phosphatidic acids.
  • polyalkylene-containing lipids include polyoxyethylene-containing lipids or polyoxypropylene-containing lipids.
  • the polyalkylene-containing lipid is a phospholipid functionalized with polyethylene glycol such as N-(carbonyl-methoxypolyethyleneglycol-2000)-1,2-distearoyl-sn-glycero-3-phosphoethanol-amine (mPEG-2000-DSPE).
  • lipid-containing metal chelators include 1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-diethylenetriaminepentaacetyl (DSPE-DTPA), tetraazacyclododecane, tetraacety(gadodiamide)-PE, and lipid-functionalized-[N,N-bis[2-[bis(carboxymethyl)amino]-ethyl]-glycinato-(5′′)].
  • the lipid-containing metal chelator comprises a PEGylated lipid moiety.
  • the lipid-containing metal chelator is a PEGylated DTPA.
  • the lipid-containing metal chelator is a DSPE-BOPTA, a DSPE-DO3A, and a DSPE-DOTA.
  • the composition further includes a targeting moiety.
  • targeting moieties include proteins, polypeptides, peptides, antibodies or fragments thereof, small molecules, sugars or polysaccharides or derivatives thereof, and nucleic acids.
  • the composition of the invention has the form of a nanoparticle.
  • the nanoparticle has a diameter of from about 5 nm to about 2 ⁇ m. In one embodiment, the nanoparticle has a diameter of from about 50 nm to about 100 ⁇ m.
  • the composition of the invention can further include a metal ion.
  • Suitable metal ions include paramagnetic metal ions and ions of radio-isotopes.
  • Representative paramagnetic metal ions include Gd 3+ , Cu 2+ , Fe 3+ , Fe 2+ , and Mn 2+ ions.
  • Representative ions of radio-isotopes include 68 Ga, 55 Co, 86 Y, 90 Y, 177 Lu, and 111 In ions.
  • the invention provides administrable compositions including a carrier and a plurality of the nanoparticles of the invention.
  • Suitable carriers include pharmaceutically acceptable carriers such as saline for injection or dextrose for injection.
  • the invention provides a method for imaging of tissues, comprising administering to a subject to be imaged an effective amount of the composition of the invention.
  • Representative tissues that can be imaged by the method include lymphoid, cardiovascular, liver, kidney, brain, heart, muscle, and gastrointestinal tract tissues, and other tissues accessible by the lymphatic or vascular (blood) systems.
  • the invention provides a method for delivering a radio-cancer therapeutic agent to a cancer cell, comprising administering to a cancer cell an effective amount of the composition of the invention that includes anion of a radio-isotope.
  • FIG. 1 is a graph illustrating reduction of calcein fluorescence as a function of Gd 3+ : DTPA-PE (m/m) ratio for a representative formulation of the invention.
  • the formulation was incubated with calcein and its fluorescence measured. Free Gd 3+ binds to calcein and reduces its fluorescence.
  • FIGS. 2A and 2B compare relaxivity as a function of Gd 3+ concentration.
  • FIG. 2A compares Gd 3+ dose effect on T1 relaxation rate; R 1 (1/T1) values of Gd 3+ concentrations ( ⁇ mol/mL) measured in a 1.5T magnetic resonance (MR) scanner using a standard spin-echo sequence for a representative formulation of the invention (Gd-DPTA-PE: mPEG-PE: DSPC) compared to other formulations.
  • MR magnetic resonance
  • FIG. 3 illustrates time-course coronal images of ventral cavity of M. Nemestrina up to 24 hours after injection of a representative formulation of the invention (Gd-DPTA-PE: mPEG-PE: DSPC).
  • FIGS. 3A-3D are time sequence images of the liver before (3A) and after 20 min (3B), 6 hr (3C), and 24 hr (3D) administration.
  • the top panel illustrates time sequence images of lymph nodes. The lymph nodes and liver show high contrast compared to background tissues.
  • FIG. 4A is a graph comparing MR dynamic contrast enhanced image intensity of the lymph nodes (LN 1, LN 2, and LN3) and liver (Liver) in M. Nemestrina up to 24 hr after subcutaneous injection of 24.4 ⁇ mol/kg of a representative formulation of the invention (Gd-DPTA-PE: mPEG-PE: DSPC). Results are for images shown in FIGS. 3A-3D .
  • FIG. 4B is a graph comparing the time course of tissue specific MR signal (lymph node) compared to adjacent control tissue.
  • FIGS. 5A-5D are time course MR images of a rat after intravenous injection of a representative formulation of the invention (0.01 mmol/kg Gd-DPTA-PE: mPEG-PE:
  • DSPC DSPC: pre-dose (5A); 5 min (5B); 14 min (5C); and 24 hr (5D). Contrast enhancement is localized mainly in vasculature and vascularized tissues in lymph nodes at 5 min and 14 min.
  • the arrow in 5C indicates the beginning of gadolinium elimination into the gastrointestinal tract through the biliary route.
  • 24 hr (5D) most of the contrast agent is eliminated and the residual fraction appears in the intestine.
  • FIGS. 6A-6C are time course MR images of a rat after intravenous injection of a commercially available gadolinium-based contrast agent (0.05 mmol/kg Gd-DPTA, OMNISCAN): pre-dose (6A); 5 min (6B); and 15 min (6C). Contrast enhancement is diffused throughout and does not localize in the vasculature, well-perfused tissues, or the lymph nodes at either 5 min or 15 min. Distribution of contrast media to periphery and extremities is apparent.
  • a commercially available gadolinium-based contrast agent 0.05 mmol/kg Gd-DPTA, OMNISCAN
  • FIGS. 7A-7D compare time course MR images of a rat after intravenous injection of a commercially available gadolinium-based contrast agent (0.05 mmol/kg Gd-DPTA, OMNISCAN, pre-dose (7A), 5 min (7B), and 15 min (7C)) an MR image of a rat 15 min after administration of a representative formulation of the invention (0.01 mmol/kg Gd-DPTA-PE: mPEG-PE: DSPC).
  • a commercially available gadolinium-based contrast agent 0.05 mmol/kg Gd-DPTA, OMNISCAN, pre-dose (7A), 5 min (7B), and 15 min (7C)
  • FIGS. 8A-8F compare dose response MR images of a rat after intravenous injection of a representative formulation of the invention (Gd-DPTA-PE: mPEG-PE: DSPC): 0.0 mmol/kg (8A); 0.00125 mmol/kg (8B); 0.0025 mmol/kg (8C); 0.005 mmol/kg (8D); and 0.010 mmol/kg (8E and 8F). Lymph nodes are clearly apparent in FIG. 8F .
  • FIGS. 9A-9C compare MR images of rats after intravenous injection of two commercially available gadolinium-based contrast agents (0.05 mmol/kg MS-325, 9A; 0.05 mmol/kg MAGNEVIST Gd-DPTA, 9B) and a representative formulation of the invention (0.01 mmol/kg Gd-DPTA-PE: mPEG-PE: DSPC, 9C). Images were acquired near peak enhancement, about 1 to 2 min after administration.
  • FIG. 10 is a schematic illustration of the preparation of a representative lipid-containing gadolinium chelate: DSPE-DOTA-Gd.
  • FIG. 11 illustrates three metal chelators useful for preparing representative lipid-containing chelates: p-SCN-Bn-DOTA; CHX-A′′-DTPA; and p-SCN-Bn-DTPA.
  • FIG. 12 is a schematic illustration of the preparation of representative lipid-containing gadolinium chelates.
  • compositions expressing metal ions and methods for using the compositions are lipid nanoparticles that include paramagnetic metal ions and are useful for magnetic resonance imaging. In another embodiment, the compositions are lipid nanoparticles that include ions of radio-isotopes and are useful for delivery of radio-cancer therapeutic agents.
  • the invention provides compositions and methods for magnetic resonance imaging.
  • the compositions and methods enhance gadolinium distribution and accumulation in lymphatics.
  • the invention provides a gadolinium composition (referred to herein as “Gd-DTPA-lipid nanoparticle”) that is suitable for both intravenous and subcutaneous administration.
  • Subcutaneous administration allows direct access to lymphatic system.
  • the composition enhances T1 weighted MR signal in the lymph nodes as well as increases the residence time of the contrast agent in the lymphatics.
  • the composition Upon intravenous administration, the composition exhibits at least 100-fold enhancement over soluble Gd-DTPA as a vascular imaging agent and eliminates predominantly through biliary, rather than renal clearance.
  • the composition was shown to significantly increase signal-to-noise ratio by more than 300-fold for MR visualization of lymph nodes in macaques.
  • the composition of the invention includes a lipid, a polyalkylene-containing lipid, and a lipid-containing metal chelator. In one embodiment, the composition further includes a chelated metal ion.
  • the composition of the invention is a chelator- (or metal chelate-) expressing particle.
  • the term “expressing” refers to the particle presenting or having available the chelator or chelated metal for activity.
  • the composition of the invention is a lipid nanoparticle having chelated gadolinium ion (Gd +3 ) (e.g., Gd-DTPA-lipid nanoparticle). In the lipid nanoparticle, chelated gadolinium ion is expressed.
  • the lipid nanoparticles of the invention are biocompatible and are readily administered.
  • the nanoparticles have a diameter of from about 5 nm to about 2 ⁇ m. In one embodiment, the nanoparticles have a diameter of from about 10 nm to about 100 ⁇ m. In one embodiment, the nanoparticles have a diameter of about 70 nm.
  • composition of the invention (e.g., lipid nanoparticles) includes a lipid, a polyalkylene-containing lipid, and a lipid-containing metal chelator.
  • the lipid component of the nanoparticles of the invention comprise the nanoparticle core.
  • lipids useful in the compositions include phospholipids, sphingolipids, cholesterol and steroid derivatives, bile acids and derivatives, cardilipin, acyl-glycerides and derivatives, glycolipids, acyl-peptides, fatty acids, carbohydrate-based polymers (e.g., cellulose polymers), suitably functionalized silica, lipophilic polymers (e.g., polyanhydrides, polylactate-glycolate), and lipophilic bioploymers (e.g., proteins, sugar polymers).
  • carbohydrate-based polymers e.g., cellulose polymers
  • suitably functionalized silica e.g., lipophilic polymers (e.g., polyanhydrides, polylactate-glycolate), and lipophilic bioploymers (e.g., proteins, sugar polymers).
  • the lipid is disteroylamidomethylamine.
  • the lipid is a phospholipid.
  • Representative phospholipids include 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC); dipalmitoyl phosphatidylcholine; dimysristoyl phosphatidyl choline; dioleoyl phosphatidyl choline; trans-esterified phospholipids derived from eggs, soybean, flaxseed, and the like; and phosphatidylcholine substituted with phosphatidyl ethanolamine, phosphatidylglycerol, phosphatidyl serine, and phosphatidic acids.
  • the phospholipid is 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC).
  • Polyalkylene-containing lipids The polyalkylene-containing lipid component of the nanoparticles of the invention serve as surface hydrating agents.
  • polyalkylene-containing lipids include polyoxyethylene-containing lipids and polyoxypropylene-containing lipids.
  • the polyalkylene-containing lipid is a phospholipid functionalized with polyethylene glycol (e.g., PEGylated phospholipid).
  • PEGylated phospholipids include a polyethylene glycol having a number average molecular weight of from about 500 to about 20,000.
  • the PEGylated phospholipid is N-(carbonyl-methoxypolyethyleneglycol-2000)-1,2-distearoyl-sn-glycero-3-phosphoethanolamine (mPEG-2000-DSPE) (also referred to herein as “mPEG-DSPE” and “mPEG-PE”).
  • the surface hydrating agent is hydrophilic biomaterials such as a carbohydrate polymer, a polyamine, a polyvinyl pyrrolidone, a poly(aspartate), or a poly(L-amino acid).
  • Other useful surface hydrating agents include covalent conjugates of polyethoxyl, polymethylene glycol, or propylene glycol and a lipid or other hydrophobic moiety (e.g., long chain hydrocarbon).
  • the surface hydrating agent is preferably present from about 5 to about 50 mole percent of the composition (i.e., lipid, polyalkylene-containing lipid (surface hydrating agent), and lipid-containing metal chelator).
  • Lipid-containing metal chelator The lipid-containing metal chelator component of the nanoparticles of the invention are expressed on the surface of the nanoparticle and serve to chelate metal ions.
  • Suitable lipid-containing metal chelators include two moieties: (1) a lipid moiety and (2) a metal chelator moiety.
  • lipid-containing metal chelators include 1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-diethylenetriaminepentaacetyl (DSPE-DTPA), tetraazacyclododecane, tetraacety(gadodiamide or OMNISCAN)-PE, and lipid-functionalized-[N,N-bis [24bis(carboxymethyl)amino]ethyl]-glycinato-(5′′)] (MAGNEVIST).
  • DSPE-DTPA 1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-diethylenetriaminepentaacetyl
  • MAGNEVIST lipid-functionalized-[N,N-bis [24bis(carboxymethyl)amino]ethyl]-glycinato-(5′′)]
  • Representative metal chelators include BOPTA, DO3A, and DOTA chelators.
  • the metal chelator includes a PEGylated lipid moiety.
  • Representative PEGylated metal chelators include DSPE-BOPTA, a DSPE-DO3A, and a DSPE-DOTA.
  • the metal chelator is a PEGylated DTPA (DPTA-PE).
  • the metal chelator is preferably present from about 5 to about 50 mole percent of the lipid, polyalkylene-containing lipid (surface hydrating agent), and metal chelator.
  • compositions of the invention are effective carriers of metal ions.
  • the composition e.g., lipid nanoparticles
  • the composition further includes a chelated metal ion.
  • useful metal ions include paramagnetic metal ions.
  • paramagnetic metal ions include Gd 3+ , Cu 2+ , Fe 3+ , Fe 2+ , and Mn 2+ ions.
  • useful metal ions include ions of radio-isotopes.
  • Representative radio-isotopes include ions of 68 Ga, 55 CO, 86 Y, 90 Y, 177 Lu, and 111 In.
  • the ratio of metal ion: metal chelator is 0.1-1.0:1.0 (less than or equal to 1:1).
  • compositions of the invention can be used to target specific tissues.
  • the composition e.g., lipid nanoparticles
  • the composition further includes a targeting moiety.
  • targeting moieties include proteins, polypeptide, and peptides; antibodies and derivatives (fragments); small molecules; sugars, polysaccharides, and derivatives; and nucleic acids, such as nucleotide polymers (e.g., aptamers), DNAs; and RNAs.
  • Representative targeting moiety targets include cancer cells and virus infected cells.
  • compositions for administration can be formulated into compositions for administration.
  • suitable compositions for administration include a carrier and a plurality of the lipid nanoparticles.
  • Representative carriers include pharmaceutically acceptable carriers, such as saline for injection or dextrose for injection.
  • the lipid nanoparticle of the invention is not a liposome and does not form liposomes when formulated.
  • the invention provides methods for imaging tissues (e.g., occluded tissues).
  • the method includes administering to a subject to be imaged a diagnostically effective amount of a composition of the invention.
  • the composition can be administered by a variety of techniques including subcutaneously and intravenously.
  • the method is effective for imaging tissues such as lymphoid, cardiovascular, liver, kidney, brain, heart, muscle, and gastrointestinal tract tissues, and other tissues accessible by the lymphatic or vascular (blood) systems.
  • the method is effective for imaging the tissues above to determine whether the tissues are occluded.
  • the composition includes a paramagnetic metal ion (e.g., Gd 3+ ).
  • the effective amount is from about 0.001 to about 5 mmol metal/kg subject. In one embodiment, the effective amount is from about 0.005 to about 0.050 mmol metal/kg subject. In one embodiment, the effective amount is about 0.010 mmol metal/kg subject.
  • the invention provides methods for delivering a radio-cancer therapeutic agent to a cancer cell.
  • the method includes administering to a subject in need thereof a therapeutically effective amount of a composition of the invention in which the chelated metal ion is a radio-isotope (e.g., 68 Ga, 55 Co, 86 Y, 90 Y, 177 Lu, and 111 In).
  • the composition can be administered by a variety of techniques including subcutaneously and intravenously.
  • the method is effective for delivery to tissues such as lymphoid, cardiovascular, liver, kidney, brain, heart, muscle, and gastrointestinal tract tissues, and other tissues accessible by the lymphatic or vascular (blood) systems.
  • Lipid nanoparticles were prepared composed of 10 mole percent of surface-bound DTPA. These lipid nanoparticles contained distearoyl-phosphatidylcholine and PEGylated lipid, mPEG-2000-DSPE. They were allowed to complex with Gd 3+ (presented as Gd 3+ —Cl ⁇ ) at varying Gd 3+ -to-DTPA-PE mole ratios. The presence of free Gd 3+ in the admixture was determined by the ability of free Gd 3+ to quench the fluorescence of calcein. With up to a Gd 3+ -to-DTPA-PE mole ratio of 4, no free Gd 3+ could be detected by the calcein quenching assay.
  • the apparent diameter of Gd 3+ -DTPA lipid nanoparticle increases by about 2- to 3-fold, while there is no apparent decrease in the degree of Gd associated with DTPA-lipid nanoparticles (see Table 1). These lipid nanoparticles appeared to be stable as no significant change in diameter was detected over 24 hr at room temperature.
  • the ratio of Gd 3+ -to-DTPA influence the degree of Gd 3+ incorporation into Gd-DTPA lipid nanoparticles and their apparent diameters.
  • substantially all Gd 3+ was associated with lipid nanoparticles.
  • the Gd 3+ -to-DTPA mole ratio in the composition of the invention is about 1.
  • the contrast properties of the Gd 3+ -expressed lipid nanoparticles was determined by comparing the effects of the various Gd 3+ formulations on the R1 (1/T1) relaxivity of Gd 3+ .
  • Lipid nanoparticles composed of distearoyl-phosphatidylcholine (DSPC) with or without PEGylated lipid (mPEG-2000-DSPE, referred to herein as “mPEG-DSPE” or “mPEG-PE”) and fixed Gd 3+ -to-DTPA mole ratio at 1.
  • DSPC distearoyl-phosphatidylcholine
  • mPEG-2000-DSPE PEGylated lipid
  • mPEG-PE fixed Gd 3+ -to-DTPA mole ratio
  • Gd-DTPA-PE mPEG-PE
  • DSPC lipid nanoparticle containing mPEG-PE
  • FIG. 2B the representative composition of the invention, Gd-DTPA lipid nanoparticle containing mPEG-PE (Gd-DTPA-PE: mPEG-PE: DSPC), exhibited significantly higher R1 value than other preparations, including OMNISCAN and lipid nanoparticles that did not contain mPEG.
  • the effects of mPEG on Gd-DTPA lipid nanoparticles are less for T2 measurement (see FIG. 2B ).
  • the R1 and R2 values for both Gd-DTPA lipid nanoparticle compositions were significantly higher than that of the soluble Gd-DTPA commercial preparation (OMNISCAN) or free Gd 3+ in solution (Gd w/o DTPA).
  • Gd-DTPA-PE DSPC
  • mPEG-PE DSPC
  • FIG. 2B demonstrates the effects of the various Gd 3+ formulations on the R2 (1/T2) relaxivity measurements.
  • the mPEGylated Gd-DTPA-lipid nanoparticles (Gd-DTPA-PE: mPEG-PE: DSPC) showed about eight-fold increase in R2, compared to OMNISCAN.
  • the Gd-DTPA in DSPC (without mPEG) nanoparticle formulation (Gd-DTPA-PE: DSPC) showed a greater increase in R2 than R1, which may limit its effectiveness as a positive contrast agent formulation.
  • the DSPC and DSPC plus mPEG-2000-PE control formulations without Gd 3+ (DTPA-PE: mPEG-PE: DSPC and DTPA-PE: DSPC) again showed no effect on relaxivity.
  • Gd-DTPA-PE mPEG-PE: DSPC or “Gd-DTPA lipid nanoparticles”
  • FIGS. 3A-3D shows several coronal MR images of ventral cavity of M. Nemestrina both pre-contrast and up to 24 hours following subcutaneous injection of Gd 3+ -DTPA-lipid nanoparticles.
  • the auxiliary lymph nodes are clearly visible with a high degree of intensity enhancement compared to the surrounding tissue ( FIG. 3 top panel). The enhancement of the lymph nodes can be seen as early as twenty minutes while lasting up to twenty four hours.
  • FIG. 4 shows the time course of dynamic contrast enhanced MRI, showing relative intensities of various organs vs. time. This data shows that the Gd 3+ -DTPA-lipid nanoparticles quickly reach the lymph nodes tissue within twenty minutes after injection, and maintain the contrast enhancement for at least twenty four hours.
  • a single subcutaneous Gd-DTPA lipid nanoparticles dose provided greatly enhanced signal for extended time.
  • the MR image enhancing property of the Gd-DTPA-lipid nanoparticles can be used to minimize the IV dose need to produce vascular image enhancement and also reduce renal burden.
  • Administration of 0.01 mmole/kg Gd-DTPA nanoparticles (about 1 ⁇ 5 of current dose for human) in rats produced a high quality MR image with clearly discernable central and peripheral vasculature of rat within 5 min ( FIG. 5B ). It begins to clear through the bile and gut within 15 min ( FIG. 5C ), and by the clearance process appeared to complete by 24 hr ( FIG. 5D ).
  • 0.05 mmole soluble Gd-DTPA produce diffuse contrast localization with no vascular definition; it also appeared to distribute to periphery an extremities ( FIG. 6A ).
  • OMSCAN 0.05 mmole soluble Gd-DTPA
  • the 0.0025 mmole/kg Gd in DTPA-lipid nanoparticles produce equivalent image quality of 0.05 mmole/kg Gd-DTPA (OMNISCAN) preparation. Therefore, the Gd-DTPA-lipid nanoparticles may overcome challenges in the clinical use with currently approve Gd contrast agents due to renal insufficiency and neurotoxicity.
  • the PEGylated lipid nanoparticles of the invention having surface-bound gadolinium ion exhibited a great improvement over other preparations in contrast enhanced MR lymphography and vascular imaging. These lipid nanoparticles showed high degree of accumulation in the lymph nodes after subcutaneous injection.
  • the contrast enhancement in lymphoid tissue begins within 20 minutes of injection and is maintained for 24 hours. When given intravenously this agent produced high quality images of vasculature in much higher sensitivity than the current agents.
  • Intravenously administered lipid nanoparticles are cleared almost exclusively through biliary route and appeared to complete within 24 hr. Surface modification by adding mPEG in lipid nanoparticles increased the MR signal of Gd 3+ through coordination of water molecules.
  • the lipid nanoparticle formulation may allow using a low dose to achieve a high signal-to-noise MR contrast ratio for increasing the metastatic nodal discrimination and allowing for a much wider time frame for imaging.
  • the potentially lower dose and more favorable elimination route of Gd 3+ needed for MR contrast could provide higher safety margin.
  • FIGS. 8A-8F compare dose response MR images of a rat after intravenous injection of a representative formulation of the invention (Gd-DPTA-PE: mPEG-PE: DSPC): 0.0 mmol/kg (8A); 0.00125 mmol/kg (8B); 0.0025 mmol/kg (8C); 0.005 mmol/kg (8D); and 0.010 mmol/kg (8E and 8F). Lymph nodes are clearly apparent in FIG. 8F .
  • FIGS. 9A-9C compare MR images of rats after intravenous injection of two commercially available gadolinium-based contrast agents (0.05 mmol/kg MS-325, EPIX Pharmaceuticals, Inc., Cambridge, Mass., FIG. 9A ; and 0.05 mmol/kg MAGNEVIST Gd-DPTA, Bayer HealthCare Pharmaceuticals, FIG. 9B ) and a representative formulation of the invention (0.01 mmol/kg Gd-DPTA-PE: mPEG-PE: DSPC, FIG. 9C ). Images were acquired near peak enhancement, about 1 to 2 min after administration. As can be seen from the images, the representative formulation of the invention demonstrates significantly greater contrast than the currently available agents.
  • FIG. 10 is a synthetic scheme for preparing a representative Gd complexes useful in the invention (DSPE-DOTA-Gd) by reacting DSPE with p-SCN-Bn-DOTA followed by Gd metallation.
  • FIG. 11 illustrates three representative chelating agents (isothiocyanates, —N ⁇ C ⁇ S or —NCS) (p-SCN-Bn-DOTA, CHX-A′′-DTPA, and p-SCN-Bn-DTPA) that are reactive toward phospholipids and useful in the invention.
  • FIG. 10 is a synthetic scheme for preparing a representative Gd complexes useful in the invention (DSPE-DOTA-Gd) by reacting DSPE with p-SCN-Bn-DOTA followed by Gd metallation.
  • FIG. 11 illustrates three representative chelating agents (isothiocyanates, —N ⁇ C ⁇ S or —NCS) (p-SCN-Bn-DOTA, CHX-A′′-DTPA
  • FIG. 12 illustrates four representative lipophilic compounds (DSA, Diether PE, DSPE-PEG(2000) Amine, and DSPE) and a synthetic scheme for preparing a representative Gd complex useful in the invention (DSPE-DOTA-Gd) by reacting DSPE with p-SCN-Bn-DOTA followed by Gd metallation.
  • Lipid-containing metal chelators useful in the invention are readily prepared as shown in FIGS. 10 and 12 .
  • Reitably reactive metal chelators e.g., isothiocyanate-functionalized metal chelators, see FIG.
  • lipid compounds containing suitably reactive groups e.g., amino groups in DSPE, DSPE-PEG(2000) Amine, Diether PE, DSA, see FIGS. 10 and 12
  • lipid-containing metal chelators in which the lipid moiety is covalently coupled to the metal chelator.
  • the product lipid-containing metal chelator includes a thiourea (—NH—C( ⁇ S)—NH—) linkage coupling the lipid to the chelator.
  • suitably reactive metal chelators e.g., isocyanate
  • lipid compounds containing suitably reactive groups e.g., alcohol
  • Metallation of the chelators provides the metal ion-containing compounds.
  • Lipid nanoparticle preparation 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC, Avanti Polar Lipids, Ala.), N-(carbonyl-methoxypolethyleneglycol-2000)-1,2-distearoyl-sn-glycero-3-phospoethanolamine (mPEG-2000-DSPE, Genzyme, Mass.), and 1,2-distearoyl-sn-glycero-3-phophoethanolamine-N-DTPA (DSPE-DTPA, Avanti Polar Lipids, AL) were combined in chloroform (DSPC: mPEG-DSPE: DSPE-DTPA) in a ratio of 8:2:1 and dried into a thin film under nitrogen and then under high vacuum overnight.
  • DSPC 1,2-distearoyl-sn-glycero-3-phosphocholine
  • mPEG-2000-DSPE N-(carbonyl-methoxypolethyleneglycol-2000)-1,2-d
  • the mPEG-DSPE containing PEG polymers of various molecular weights (or chain lengths) are also purchased from Genzyme, Mass. At this point phosphate buffered saline (PBS, pH 7.4) was added to the film and sonicated in a bath-type sonicator (Laboratory Supplies Company, New York). The vesicle diameter, as measured by dynamic light scattering using a Malvern Zetasizer 5000 photon correlation spectroscopy (Malvern Instruments, PA), was 50 nm.
  • the nanoparticles in suspension were mixed with gadolinium (III) chloride hexahydrate (Aldrich, St Louis, Mo.) for 20 minutes at indicated mole ratio to form Gd-DTPA-lipid nanoparticles.
  • gadolinium (III) chloride hexahydrate Aldrich, St Louis, Mo.
  • the nanoparticles were incubated with calcein (0.5 ⁇ M) (Sigma, St Louis, Mo.) in PBS, pH 7.4, and the fluorescence was measured at 485/535 nm using a Victor3V 1420 multilabel counter (PerkinElmer, Waltham, Mass.). Free ionic Gd 3+ quenches calcein fluorescence in [Gd 3+ ] dependent manner.
  • elemental Gd mass was determined using the inductively coupled plasma atomic emission spectrometry. The particles along with control particles without Gd 3+ were used in the studies described herein.
  • Relaxivity studies Dilutions of Gd-DTPA-lipid nanoparticles were prepared with Gd 3+ concentrations between 0-5 ⁇ mol/ml. For comparison several samples were prepared from commercial agents such as OMNISCAN (Gd-DTPA-BMA) with Gd 3+ concentrations from 0-5 ⁇ mol/ml.
  • the relaxation time T1 was measured using the standard spin-echo sequence on a 1.5T MR scanner with a volume head coil as RF receiver.
  • TE was fixed to 9 ms and seven TR were 133, 200, 300, 500, 750, 1000 and 2000 ms, respectively.
  • T2 measurements TR was fixed to 2000 ms and four TE were 15, 30, 45, and 60 ms, respectively.
  • the imaging intensities were fitted to obtain the corresponding T1 and T2 values, which were plotted versus Gd 3+ concentration.
  • the total dose of Gd is estimated to be 24.4 ⁇ mol/kg for the primate studies.
  • the images were recorded on a Signa 1.5T Scanner using a surface coil 12 ⁇ 12 inch.
  • Rat vascular MRI study In vivo imaging of the rat using Gd-DTPA-lipid nanoparticles for dynamic contrast enhanced (DCE) MRI was performed in a 3.0T MR scanner.
  • the rats (SD) was anesthetized with inhaled isofluorane (1-2%) and closely monitored during the experiments.
  • a pre-contrast image of the rat was recorded to determine proper location, orientation and fine-tune the imaging parameters.
  • the animal was removed from the MR scanner and injected with 400 ⁇ L of indicated Gd contrast media through femoral vein. The images were recorded on a Signa 1.5T Scanner using a surface coil 12 ⁇ 12 inch.

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Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:HO, RODNEY J.Y.;HOEKMAN, JOHN D.;MARAVILLA, KEN;SIGNING DATES FROM 20110930 TO 20111216;REEL/FRAME:027440/0313

STCB Information on status: application discontinuation

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