WO1988000060A1 - Biodegradable superparamagnetic materials used in clinical applications - Google Patents

Biodegradable superparamagnetic materials used in clinical applications Download PDF

Info

Publication number
WO1988000060A1
WO1988000060A1 PCT/US1987/001588 US8701588W WO8800060A1 WO 1988000060 A1 WO1988000060 A1 WO 1988000060A1 US 8701588 W US8701588 W US 8701588W WO 8800060 A1 WO8800060 A1 WO 8800060A1
Authority
WO
WIPO (PCT)
Prior art keywords
superparamagnetic
tissue
organ
iron
magnetic
Prior art date
Application number
PCT/US1987/001588
Other languages
French (fr)
Inventor
Ernest V. Groman
Lee Josephson
Jerome M. Lewis
Original Assignee
Advanced Magnetics, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation
First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=26748043&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=WO1988000060(A1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Priority claimed from US06/882,044 external-priority patent/US4770183A/en
Application filed by Advanced Magnetics, Inc. filed Critical Advanced Magnetics, Inc.
Priority to EP87904772A priority Critical patent/EP0275285B1/en
Priority to DE3751918T priority patent/DE3751918T2/en
Publication of WO1988000060A1 publication Critical patent/WO1988000060A1/en
Priority to NO880931A priority patent/NO880931D0/en

Links

Classifications

    • BPERFORMING OPERATIONS; TRANSPORTING
    • B82NANOTECHNOLOGY
    • B82YSPECIFIC USES OR APPLICATIONS OF NANOSTRUCTURES; MEASUREMENT OR ANALYSIS OF NANOSTRUCTURES; MANUFACTURE OR TREATMENT OF NANOSTRUCTURES
    • B82Y5/00Nanobiotechnology or nanomedicine, e.g. protein engineering or drug delivery
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00Preparations for testing in vivo
    • A61K49/06Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/18Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00Preparations for testing in vivo
    • A61K49/06Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/18Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes
    • A61K49/1806Suspensions, emulsions, colloids, dispersions
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00Preparations for testing in vivo
    • A61K49/06Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/18Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes
    • A61K49/1818Nuclear 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
    • A61K49/1821Nuclear 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
    • A61K49/1824Nuclear 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
    • A61K49/1827Nuclear 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 having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle
    • A61K49/1851Nuclear 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 having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle having a (super)(para)magnetic core coated or functionalised with an organic macromolecular compound, i.e. oligomeric, polymeric, dendrimeric organic molecule
    • A61K49/1863Nuclear 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 having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle having a (super)(para)magnetic core coated or functionalised with an organic macromolecular compound, i.e. oligomeric, polymeric, dendrimeric organic molecule the organic macromolecular compound being a polysaccharide or derivative thereof, e.g. chitosan, chitin, cellulose, pectin, starch
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K49/00Preparations for testing in vivo
    • A61K49/06Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations
    • A61K49/18Nuclear magnetic resonance [NMR] contrast preparations; Magnetic resonance imaging [MRI] contrast preparations characterised by a special physical form, e.g. emulsions, microcapsules, liposomes
    • A61K49/1818Nuclear 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
    • A61K49/1821Nuclear 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
    • A61K49/1824Nuclear 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
    • A61K49/1827Nuclear 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 having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle
    • A61K49/1866Nuclear 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 having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle the nanoparticle having a (super)(para)magnetic core coated or functionalised with a peptide, e.g. protein, polyamino acid
    • A61K49/1869Nuclear 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 having a (super)(para)magnetic core, being a solid MRI-active material, e.g. magnetite, or composed of a plurality of MRI-active, organic agents, e.g. Gd-chelates, or nuclei, e.g. Eu3+, encapsulated or entrapped in the core of the coated or functionalised nanoparticle the nanoparticle having a (super)(para)magnetic core coated or functionalised with a peptide, e.g. protein, polyamino acid coated or functionalised with a protein being an albumin, e.g. HSA, BSA, ovalbumin
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61PSPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P7/00Drugs for disorders of the blood or the extracellular fluid
    • A61P7/06Antianaemics
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08GMACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G18/00Polymeric products of isocyanates or isothiocyanates
    • C08G18/06Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
    • C08G18/08Processes
    • C08G18/16Catalysts
    • C08G18/18Catalysts containing secondary or tertiary amines or salts thereof
    • C08G18/1808Catalysts containing secondary or tertiary amines or salts thereof having alkylene polyamine groups
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08GMACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G18/00Polymeric products of isocyanates or isothiocyanates
    • C08G18/06Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
    • C08G18/08Processes
    • C08G18/16Catalysts
    • C08G18/18Catalysts containing secondary or tertiary amines or salts thereof
    • C08G18/1816Catalysts containing secondary or tertiary amines or salts thereof having carbocyclic groups
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08GMACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G18/00Polymeric products of isocyanates or isothiocyanates
    • C08G18/06Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
    • C08G18/08Processes
    • C08G18/16Catalysts
    • C08G18/18Catalysts containing secondary or tertiary amines or salts thereof
    • C08G18/1825Catalysts containing secondary or tertiary amines or salts thereof having hydroxy or primary amino groups
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08GMACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G18/00Polymeric products of isocyanates or isothiocyanates
    • C08G18/06Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
    • C08G18/08Processes
    • C08G18/16Catalysts
    • C08G18/18Catalysts containing secondary or tertiary amines or salts thereof
    • C08G18/20Heterocyclic amines; Salts thereof
    • C08G18/2009Heterocyclic amines; Salts thereof containing one heterocyclic ring
    • C08G18/2036Heterocyclic amines; Salts thereof containing one heterocyclic ring having at least three nitrogen atoms in the ring
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08GMACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G18/00Polymeric products of isocyanates or isothiocyanates
    • C08G18/06Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
    • C08G18/08Processes
    • C08G18/16Catalysts
    • C08G18/22Catalysts containing metal compounds
    • C08G18/24Catalysts containing metal compounds of tin
    • C08G18/244Catalysts containing metal compounds of tin tin salts of carboxylic acids
    • C08G18/246Catalysts containing metal compounds of tin tin salts of carboxylic acids containing also tin-carbon bonds
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08GMACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G18/00Polymeric products of isocyanates or isothiocyanates
    • C08G18/06Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
    • C08G18/08Processes
    • C08G18/16Catalysts
    • C08G18/22Catalysts containing metal compounds
    • C08G18/26Catalysts containing metal compounds of lead
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08JWORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J9/00Working-up of macromolecular substances to porous or cellular articles or materials; After-treatment thereof
    • C08J9/04Working-up of macromolecular substances to porous or cellular articles or materials; After-treatment thereof using blowing gases generated by a previously added blowing agent
    • C08J9/12Working-up of macromolecular substances to porous or cellular articles or materials; After-treatment thereof using blowing gases generated by a previously added blowing agent by a physical blowing agent
    • C08J9/14Working-up of macromolecular substances to porous or cellular articles or materials; After-treatment thereof using blowing gases generated by a previously added blowing agent by a physical blowing agent organic
    • C08J9/143Halogen containing compounds
    • C08J9/144Halogen containing compounds containing carbon, halogen and hydrogen only
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01RMEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00Arrangements or instruments for measuring magnetic variables
    • G01R33/20Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48NMR imaging systems
    • G01R33/54Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/5601Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution involving use of a contrast agent for contrast manipulation, e.g. a paramagnetic, super-paramagnetic, ferromagnetic or hyperpolarised contrast agent
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08GMACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
    • C08G2101/00Manufacture of cellular products
    • CCHEMISTRY; METALLURGY
    • C08ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08JWORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J2375/00Characterised by the use of polyureas or polyurethanes; Derivatives of such polymers
    • C08J2375/04Polyurethanes

Definitions

  • This invention relates to materials exhibiting certain magnetic and biological properties which make them uniquely suitable for use as magnetic resonance imaging (MRI agents to enhance MR images of animal organs and tissues. More particularly, the invention relates to the .in vivo use biologically degradable and etabolizable superparamagnetic metal oxides as MR contrast agents. Depending on their preparation, these metal oxides are in the form of superparamagnetic particle dispersoids or superparamagnetic fluids where the suspending medium is a physiologically- acceptable carrier. These dispersoids and fluids are administered to animals, including humans, by a variety of routes and the metal oxides therein collect in specific targ organs to be imaged.
  • MRI agents magnetic resonance imaging
  • the biodistribution of the metal oxide in target organs or tissues results in a more detailed image of such organs or tissues because the metal oxides, due to their superparamagnetic properties, exert profound effects o the hydrogen nuclei responsible for the MR image.
  • the dispersoids and fluids are quite stable and, i the case of the fluids, can even be subjected to autoclavin without impairing their utility.
  • the materials are well-suited for in vivo use.
  • the combination of superparamagnetism and biodegradability makes the materials described herein particularly advantageous for use as MR contrast agents.
  • Superparamagnetism which results in profound capabilities alter MR images, makes it possible to use these materials i concentrations lower than those required for MRI with other types of magnetic materials.
  • Biodegradability results in optimum retention times within the organs and tissues to be imaged, i.e., the materials remain within the organ or tiss sufficiently long to permit an image to be obtained, yet ar eventually cleared from or metabolized within the organ or tissue.
  • iron-based agents when administere the iron thereon is eventually metabolized and incorporated into the subject's hemoglobin.
  • These materials can, therefore, be used for a variety of clinical diagnostic purposes including, but not limited to, detection of cancerous lesions in liver and oth reticuloendothelial tissue, detection of cancerous or other lesions in the intestine, detection of liver diseases, such cirrhosis and hepatitis, and assessment of liver regenerati Those that are iron-based are also clinically useful as ant anemia agents.
  • NMR Nuclear magnetic resonance
  • the magnetic fields utilized in a clinical NMR scan are not considered to possess any deleterious effects to human health (see Budinge supra. , at 296) .
  • MR images are a composite of the effects of a number of parameters which are analyzed and combined by computer.
  • Choice of the appropriate instrument parameters such as radio frequency (Rf) , pulsing and timing can be utilized to enhance (or, conversely, attenuate) the signals of any of the image-producing parameters thereby improving image quality and providing better anatomical and functiona information.
  • Rf radio frequency
  • pulsing and timing can be utilized to enhance (or, conversely, attenuate) the signals of any of the image-producing parameters thereby improving image quality and providing better anatomical and functiona information.
  • the use of such imaging has, in some cases, proven to be a valuable diagnostic tool as normal a diseased tissue, by virtue of their possessing different parameter values, can be differentiated in the image.
  • T. and T are of primary importance.
  • T. also called the spi lattice or longitudinal relaxation time
  • T 2 also called the spin-spin or transverse relaxation time
  • T and/ T_ of the tissue to be imaged must be distinct from that of the background tissue.
  • the magnitude of thes differences is small, limiting diagnostic effectiveness.
  • One approach is the use of contrast agents.
  • any material suitable for use as a contrast age must affect the magnetic properties of the surrounding tissu MRI contrast agents can be categorized by their magnetic properties.
  • Paramagnetic materials have been used as MRI contrast agents because of their long recognized ability to decrease T.. [ einmann et al.. Am. J. Rad. 142, 619 (1984), Greif et al. Radiology 157, 461 (1985), Runge, et al. Radiology 147, 789 (1983), Brasch, Radiology 147, 781 (1983) Paramagnetic materials are characterized by a weak, positive magnetic susceptibility and by their inability to remain magnetic in the absence of an applied magnetic filed.
  • Paramagnetic MRI contrast agents are usually transition metal ions of iron, manganese or gadolinium. The may be bound with ⁇ helators to reduce the toxicity of the metal ion (see Weinman reference above) .
  • Paramagnetic materials for use as MRI contrast agents are the subject of number of patents and patent applications. (See EPA 0 160 552; UK Application 2 137 612A; EPA 0 184 899; EPA 0 186 947 US Patent 4,615,879; PCT WO 85/05554; and EPA 0 210 043). Ferromagnetic materials have also been used as contrast agents because of their ability to decrease T- [Medonca-Dias and Lauterbur, Magn. Res. Med.
  • Ferromagnetic materials have high, positive magnetic susceptibilities and maintain their magnetism in the absence of an applied field. Ferromagnetic materials for use as MRI contrast agents are the subject of recent patent applications [PCT WO 86/01112; PCT WO 85/043301].
  • superparamagnetic materials have been used as contrast agents [Saini et al Radiology, 167, 211 (1987); Hahn et al., Soc. Ma Res. Med. 4(22) 1537 (1986)]. Like paramagnetic materials, superparamagnetic materials are characterized by an inability to remain magnetic in the absence of an applied magnetic field. Superparamagnetic materials can have magnetic susceptibilities nearly as high as ferromagnetic materials an far higher than paramagnetic materials [Bean and Livingston J Appl. Phys. suppl to vol. 3_0_, 1205, (1959)].
  • Ferromagnetism and superparamagnetism are propertie of lattices rather than ions or gases.
  • Iron oxides such as magnetite and gamma ferric oxide exhibit ferromagnetism or superparamagnetism depending on the size of the crystals comprising the material, with larger crystals being ferromagnetic [G. Bate in Ferromagnetic Materials. vol. 2, Wohlfarth (ed.) p.439].
  • superparamagnetic and ferromagnetic materials alter the MR image by decreasing 2 resulting in image darkening.
  • crystals of these magnetic materials accumulate in the targeted organs o tissues and darken the organs or tissues where they have accumulated.
  • Abnormal volumes of liver, such as tumors, are deficient in their ability to take up the magnetic materials and appear lighter against normal background tissue than the would without contrast agent.
  • superparamagnetic materials posse some characteristics of paramagnetic and some characteristic of ferromagnetic materials. Like paramagnetic materials, superparamagnetic materials rapidly lose their magnetic properties in the absence of an applied magnetic field; they also possess the high magnetic susceptibility and crystallin structure found in ferromagnetic materials. Iron oxides suc as magnetite or gamma ferric oxide exhibit superparamagnetis when the crystal diameter falls significantly'below that of purely ferromagnetic materials.
  • FO ⁇ cubic magnetite (Fe O ) this cut-off is a crystal diameter of about 300 angstroms [Dunlop, J. Geophys. Rev. 7_8_ 1780 (1972)].
  • a similar cut-off applies for gamma ferric oxide [Bare in Ferromagnetic Materials, vol. 2, Wohfarth (ed.) (1980) p. 439]. Since iron oxide crystals a generally not of a single uniform size, the average size of purely ferromagnetic iron oxides is substantially larger th the cut-off of 300 angstroms (.03 microns).
  • w gamma ferric oxide is used as a ferromagnetic material in magnetic recording, (e.g., Pfizer Corp.
  • particles are needle-like and about 0.35 microns long and .06 microns thick.
  • Other ferromagnetic particles for data recording ar between 0.1 and 10 microns in length [Jorgensen, The Comple Handbook of Magnetic Recording, p. 35 (1980)].
  • preparations of purely ferromagnetic particles have average dimensions many times larger than preparations of superparamagnetic particles.
  • ferrofluids are a solution of very fine magnetic particles kept from settling by Brownian motion To prevent particle agglomeration through Van der Waals attractive forces, the particles are coated in some fashion. When a magnetic field is applied, the magnetic force is transmitted to the entire volume of liquid and the ferroflui responds as a fluid, i.e. the magnetic particles do not separate from solvent.
  • Solution stability is defined as the retention of the size of the magnetic material in solution; in an unstable solution the _ g _
  • Autoclaving solutions of superparamagnetic materials after bottling is preferable, since sterilization is achieved after final bottling, and there is little opportunity for contamination of the final product. Autoclaving involves heating sealed solutions to 121 * C for 30 minutes.
  • Paramagnetic iron oxides or ferric oxides are currently used in the treatment of anemia under many trade names such as Imferon. When dissolved in aqueous solution, such materials can be represented as FeO.OH and are termed
  • 35 ferric oxyhydroxides are paramagnetic and exert small if any, effects of proton relaxivity. They are stable, undergo the manipulations discussed supra for pharmaceutical manufacture, and are commercially available as drugs used in the treatment of anemia.
  • biodegradable in reference to the materials of this invention is defined as being metabolized and/or excreted by the subject within 30 days or less; for superparamagnetic iron oxides, the term is further defined a being incorporated into the hemoglobin of a subject within 3 days or less after administration.
  • blocking agent is defined as any materi which when administered parenternally to a subject, will competitively bind to the receptors of the cells of the reticuloendothelial system which recognize and bind MRI contrast agents.
  • This invention provides a novel MR imaging method using biodegradable superparamagnetic metal oxides as con ⁇ trast agents which fulfill the foregoing objectives.
  • Such materials it has been discovered, combine an optimal balanc of features and are particularly well-suited for use as MR contrast agents. Remarkably, it has been found that these superparamagnetic materials exert a greater effect on T ? tha ferromagnetic or paramagnetic materials, thereby producing a well-resolved, negative contrast image of an in vivo target organ or tissue. It has also been surprisingly found that the materials used in the methods of this invention exhibit highly desirable in vivo retention times, i.e., they remain intact for a sufficient time to permit the image to be taken yet are ultimately biodegradable.
  • degraded iron-based materials serve as a source of nutritional iron. Additionally, they are sufficiently small to permit free circulation through the subject's vascular system and rapid absorption by the organ/ tissue being imaged, allowing for maximum latitude in the choice of administration routes and ultimate targets.
  • the materials used as MR imagin agents comprise superparamagnetic metal oxide particles whic comprise superparamagnetic crystalline cores.
  • Each core is composed of magnetically active metal oxides and can range from about 50 to about 500 angstroms in diameter.
  • the cores may be uncoated or, alternatively, coated with a polysac- charide, a protein, a polypeptide or any composite thereof.
  • the polysaccharide coating may comprise dextran of varying molecular weights and the prote coating may comprise bovine or human serum albumin.
  • the overall particle diameter ranges upward to about 5,000 angstroms.
  • th coatings can serve as a base to which various biological molecules can be attached.
  • the biological molecules can be used to direct the particles to the desired target and are preferentially recognized and bound by the target organ or tissue.
  • Such molecules include proteins, polysaccharrides, hormones, antibodies, etc.
  • Preferred superparamagnetic particles comprise ir oxides with crystal sizes ranging from about 50 to about 50 angstroms. These iron oxide particles have surface areas
  • these iron oxide particles have a size range between about 50 and abou 5,000 angstroms, including coatings, if any.
  • the superpara magnetic iron oxides have magnetic saturations between abou 5 and about 90 electromagnetic units (EMU) per gram of oxid at room temperature (approximately 25 ⁇ C) and possess a magnetic squareness of less than 0.10, i.e., lose greater than 90% of their magnetism when an applied magnetic field removed.
  • EMU electromagnetic units
  • Superparamagnetic particles with these general dimensions overcome problems associated with the use of ferromagnetic and paramagnetic materials as MR contrast agents. Specifically, superparamagnetic particles, because they are smaller than ferromagnetic particles, are more abl to avoid uptake by the subject's reticuloendothelial cells and may be more effectively targeted to other organ and tissue sites within the body. Also, because the superparamagnetic particles are smaller than ferromagnetic particles, they have higher surface area per unit mass and are more easily and rapidly digested by chemical or metaboli processes. However, the superparamagnetic particles used herein, because they are larger than paramagnetic ions, are not so rapidly metabolized in the target organ or tissue as to prevent convenient imaging.
  • Uncoated or coated particles may be suspended in a appropriate medium (e.g., saline) to form a particle disper- soid that has the properties of a solution.
  • a appropriate medium e.g., saline
  • Solvent can be added (decreasing) or removed (increasing) particle concentration.
  • This dispersoid of particles may be administered t the subject being studied.
  • the particles are distributed to various target organs, where absorption occurs.
  • the superparamagnetic particles are administered intravascularly (e.g., intravenously or intra-arterially)
  • they are selectively distributed to reticuloendothelial organs, including liver, spleen, lymph nodes and bone marrow and, to a lesser extent, lung.
  • the superparamagnetic particles are administered via the gastrointestinal tract, e.g., orally, by intubation or by enema, they can be used as imaging agents for the organs and tissues of the gastrointestinal tract.
  • sub-micron sized particles is particu ⁇ larly important when the route of administration is intra- vascular, as such particles can freely circulate in the subject's vascular system, since they are small enough to pass through the capillary network.
  • contrast agents can be carried to targeted organs or tissue after being intravascularly administered with a minimum of trouble or delay.
  • a dextran- ⁇ oated iron oxide particle dispersoid is injected into a subject's bloodstream and the particles localize in the liver.
  • the particles are absorbed by the reticuloendothelial cells of the liver by phagocytic uptake; a particular benefit of this mode of uptake is that phagocytized iron is metabolized and cleared from the liver much more slowly (but not so slowly as to lea to undesirably long retention times) than prior art paramag ⁇ netic ions.
  • the dextran-coated particles can be preferentially absorbed by healthy cells, with less uptak into cancerous (tumor) cells. This preferential uptake enhances the contrast between healthy and cancerous tissue and allows for better definition of the tumor location on t image.
  • the mate als comprise stable, biodegradable superparamagnetic metal oxides, preferably ferric oxides, in the form of superparamagnetic fluids.
  • superparamagnetic fluids exhibit some of the magnetic properties of superparamagneti ferrofluids (e.g., the metal oxides in them cannot be remov from solution by magnetic mani ulation) , yet the metal oxid in them can be easily be reclaimed from the bulk fluid by physical means (e.g. centrifugation) and, ultimately redispersed in the bulk fluid.
  • the metal oxides will not scatter visible light, indicating the individual metal oxide "particles" are quite small (general between 50 and 4000 angstroms in diameter.) .
  • the metal oxides of the invention exist in the bul fluid as ionic crystals, having both ionic and crystalline characteristics.
  • magnetite Fe_0.
  • gamma ferric oxide gamma Fe ? 0_ they have high magnetic susceptibility.
  • ferric oxyhydroxides they cause retention of anions.
  • the counterion to the crystals can be any one of a number of organic anions.
  • the metal oxide is a superparamagnetic ferric oxyhydroxide and the counterion is citrate.
  • citrate counterions also confers a distinct advantage to the fluids as it renders them highly stable. In fact, the citrated fluids can withstand autoclaving greatly facilitating sterile administration.
  • the metal oxides in the superparamagnetic fluids m also be surrounded by a coating comprising a polysaccharide, protein, a polypeptide, an organosilane, or any composite thereof.
  • a coating comprising a polysaccharide, protein, a polypeptide, an organosilane, or any composite thereof.
  • These polymeric coatings serve a dual purpose, helping to stabilize the superparamagnetic fluids as well as serving as a base to which biological molecules can be attached.
  • These biological molecules can be used to direct particles to the desired target and are preferentially recog nized and bound by the target organ or tissue.
  • These mole ⁇ cules include proteins, polysaccharides, hormones, antibodie etc.
  • the superparamagnetic fluids can be administered to a subject by any of the means described supra for the metal oxide dispersoids. Furthermore, in general the fluids are quite stable and can be prepared well in advance of use and stored.
  • the superparamagnetic fluids, containing both coated an uncoated metal oxides are produced by a unique three step process from a mixture of Fe 2+ and Fe3+ salts. In addition, this process permits incorporation of other metals similar t iron (such as cobalt (Co) and manganese (Mn) into the fluids by replacing some of the divalent iron salts with divalent salts of these metals. In the process, the salts are precipitated in base to form the corresponding oxides.
  • oxides are then dispersed and oxidized by sonication of the mixture; the result, remarkably, is a superparamagnetic ferr oxyhydroxide. Insoluble oxides can then be removed by centrifugation and the final fluid is dialyzed against a neutral or alkaline buffer suitable for in vivo use.
  • the salt mixture is
  • both the metal oxides of the superparamagnetic particle dispersoids and the superpara ⁇ magnetic fluids collect in the target organ or tissue and exert a profound contrast effect to permit an image to be taken.
  • the superparamagnetic metal oxides act primarily to enhance T_ relaxation, but T. is also affected (although to lesser extent) .
  • Another embodiment of this invention presents a method for extending the lifetime of the superparamagnetic metal oxides in the subject's serum.
  • the method comprises administering a dose of paramagnetic metal oxide in the same form as the superparamagnetic imaging agent (i.e. approprate particle size and, if applicable, the same coating) as a blocking agent prior to the administration of the imaging agent.
  • This blocking agent- will compete with the imaging agent for binding to the reticuloendothelial system (RES) receptors. Since the RES is responsible for removing impurities from the blood, the binding of the blocking agent greatly increases the serum lifetime of the imaging agent. Potential applications of this procedure include, but are no limited to, use of MRI to"diagnose blood circulation disorde and strokes.
  • FIG. 1 is a graphical representation comparing the effect of ferromagnetic and superparamagnetic contrast agent on T 2 ;
  • FIG. 2 is a composite of five in vivo MR images of cancerous rat liver obtained on a Technicare MR Imager;
  • FIGS. 2A and 2B were obtained without the use of contrast agents and were taken at different settings of instrument
  • FIGS. 2C and 2D were obtained after the intravenou administration of the dextran-coated particle produced in Example 6.1. at a dosage of 0.5mg/kg; the tumor can clearly seen;
  • FIG. 2E is the image reproduced in FIG. 2C showing the tumor highlighted by crosshairs
  • FIG. 3 is a graphical representation of the % T_ reduction in liver and spleen tissue for three different dosages of an uncoated superparamagnetic particle as a function of time after administration;
  • FIG. 4 presents hysteresis curves for paramagnetic, ferromagnetic and superparamagnetic iron oxides
  • FIG. 5 shows the effect of autoclaving on superparamagnetic fluids having varying concentrations of citrate
  • FIG. 6 presents a schematic diagram of the apparatu used in example 7.10.
  • FIG. 7 is a graphical representation of the T_ of rat blood as a function of time after the injection of a dextran-coated superparamagnetic iron oxide particle with and without the use of a blocking agent.
  • the synthesis of superparamagnetic iron oxide particles for use as MRI contrast agents is accomplished by mixing ferrous and ferric salts with base to form a black, magnetic oxide of iron. Crystals result from such precipita tions, for when the material is subjected to X-ray diffrac ⁇ tion analyses long range order is apparent. A diameter of between about 50 and about 300 angstroms for such crystals has been calculated although crystals may range in diameter from about 50 to about 500 angstroms.
  • the iron oxides have correspondingly high surface areas, greater than about 75 m /gm.
  • This approach to the synthesis of an albumin coated magnetic particle is a practical one for an imaging agent.
  • the HSA coated particle (plus HSA in solution) can be injected into patient and the HSA in solution mixes with HSA in serum.
  • the loosely associated HSA can be removed by treatments such as moderate temperature (50"C) or high salt (1M NaCl) .
  • the coating methods are general and can be performed with a variety of physiologically acceptable pro ⁇ teins and carbohydrates, particularly those with molecular weights from about 5,000 to about 250,000 daltons.
  • other polymeric coatings include, but are not limited to, albumin/dextran composites, ficoll, dextrin, starch, glycoge and polyethylene glycol.
  • Polysaccharide-coated superparamagnetic iron oxide particles (about 50 to about 5000 angstroms in diameter) useful as MR contrast agents are prepared by a single-step process according to the procedure of Molday [U.S. Patent No.
  • the ratio of Fe to Fe is preferentially main ⁇ tained at about 2:1, but can be varied from about 0.5:1 to about 4.0:1 without substantial changes in product quality and efficiency as contrast agents.
  • bases other than ammonium hydroxide can be used, but NH.OH is preferred because the ammonium ion has a slight dispersing effect on iron oxides which increases the yield.
  • various magnetically active metals notably Co, and Mn, may be substituted for Fe without any deleterious effect on the efficiency of the particles as contrast agents.
  • Use of other polysaccharides such as stare- hes, glycogen or dextrins is also contemplated.
  • Protein-coated superparamagnetic iron oxide parti ⁇ cles are prepared by a single-step process similar to that of Molday [U.S. Patent 4,452,733].
  • base NH.OH
  • the protein can be dissolved in the base and an aqueous solution of the iron salts can be added dropwise to form a coated particle.
  • the oversized particles are subsequently collected by centrifugation at 1500 x g and the remaining particles are subjected to dialysis against distilled water followed by ultrafiltration. Any unbound protein can be removed by gel filtration chromatography in a chloride/acetate buffer.
  • both the coating composition and the Fe 3+/Fe2+ ratio (about 2/1) can be varied from about 0.5:1 to about 4:1 without any deleterious effect on the efficiency of these particles as contrast agents.
  • various magnetically active metals notably Co, and Mn, may be substituted for Fe without any deleterious effect on the efficiency of the particles as contrast agents.
  • Uncoated FeO and Fe 2 ° 3 superparamagnetic particles are prepared by mixing an aqueous solution of ferric chlorid (FeCl_) with ferrous chloride (FeCl_) in HC1 and precipitat ⁇ ing in 0.7 molar aqueous ammonia.
  • the base precipitation offers a dual advantage in that the base reacts with the iro chlorides to form uncoated superparamagnetic iron oxide particles.
  • the precipitate (a gelatinous substance) is then collected by centrifugation or application of a magnetic field followed by decantation of the liquid phase.
  • the gel is then peptized to form a dispersoid by mixing with either 1 molar aqueous tetramethylammonium hydroxide (to form an alkaline dispersoid) or 2 molar aqueou perchloric acid (to form an acidic dispersoid) followed by centrifugation and redispersion- in water. Both of these dispersoids show remarkable stability and, being colloidal i nature, will not possess large jsolid particles.
  • the counter ions either tetramethlylammonium hydroxide or perchlorate, are charged in basic or acidic media, respectively and, thus prevent complex coagulation in solution; the particles (com ⁇ plexes of iron oxide/counterions) can be repeatedly precipi ⁇ tated and re-dispersed in solution and will retain this property.
  • the particles can be collected by the application of an external magnetic field rather than centrifugation. The resultant magnetic cake is then peptized by the appropriate counterion.
  • the ratio of Fe 3+/Fe2+ i.s preferably maintai.ned a about 2/1, but can be varied between about 0.5/1 and about
  • the average particle size produc is about 1200 angstroms as measured by light scattering.
  • the magnetic materials described above can be use as contrast-enhancing agents for _in vivo MR imaging.
  • the particles are dispersed in a suitable injection medium, such as distilled water or normal saline, or any other physiologically acceptable carrier known in th art, to form a dispersoid which is introduced into the subject's vascular system by intravenous injection. The particles are then carried through the vascular system to t target organ where they are taken up.
  • a suitable injection medium such as distilled water or normal saline, or any other physiologically acceptable carrier known in th art
  • the particles When intravascularly administered, the particles will be preferentially taken up by organs which ordinarily function to cleanse the blood of impurities, notably the liver, spleen, and lymph nodes, and the other organs which tend to accumulate such impurities, notably bone and neural tissue and to some extent, lung.
  • organs which ordinarily function to cleanse the blood of impurities
  • the uptake into the reticuloendothelial cells will occur by phagocytosis, wherein the particles enter the indi vidual cells in membrane-bound vesicles; this permits a longer half-life in the cells, as such membrane-bound parti cles will not tend to clump or aggregate (aggregates are rapidly metabolized and cleared from the organ/tissue) .
  • Other uptake mechanisms are possible, e.g., pinocytosis.
  • the other cells of the liver may absorb the magnetic particles.
  • cancerous tumor cells can lack the ability of phagocytic uptake
  • the- intravascularly administered particles can serve as valuable tools in the diagnosis of cancer in the above-mentioned organs, as tumors will be immediately distinguishable on any image obtained.
  • the particles are adminis tered as dispersoids in a physiologically acceptable carrier such as distilled water, into the gastrointestinal tract, which includes the esophagus, stomach, large and small intestine, either orally, by intubation, or by enema, in a suitable medium.
  • a physiologically acceptable carrier such as distilled water
  • the particles are preferentially absorbed by the cells of the tract, especially those of the intestine and, like the intravascularly introduced particles, will exert an effect on T 2 of the organ or tissue. In this manner, cancers and other debilitating diseases of the digestive system such as ulcers can be diagnosed and affecte areas pinpointed.
  • the particles distribute to and collect rapidly in the target organs, generally in 30-minutes to an hour.
  • these superparamagnetic particles will alter the magnetic fields produced by the MR i ager. These altered fields will exert an effect on the magnetic properties of the hydrogen nuclei (protons) in neighboring molecules; notably affected is the spin-spin relaxation time T_,. This parameter is shortened which can result in image darkening. Thus, the contrast is enhanced between areas which absorb the particles rapidly and those which absorb them slowly or not at all.
  • the particles are, however, ultimately biodegrade- able and the iron can be utilized by the body for physio ⁇ logical requirements.
  • the contrast effect will vary with th dose, being longer at higher doses, and also with the organ imaged. Particularly in the liver and spleen (which store iron for physiological use) the effect can be observed for 1 days or more, (see Section 7.6), and, often, as long as 30 days.
  • the superparamagnetic fluids useful as imaging agents in this invention are preferably prepared in a three step process which comprises the steps of: formation of a superparamagnetic metal oxide; oxidation and dispersion of this oxide by sonication; and dialysis in buffer. This process yields stable biodegradable superparamagnetic metal oxides that owe their stability primarily to their anion retaining properties.
  • the metal oxides may be uncoated or attached to organic coatings. Each of these steps is discussed separately below.
  • Formation of the superparamagnetic metal oxide is accomplished by mixing the appropriate metal salts with a base. In a preferred embodiment, this is accomplished by mixing an aqueous solution or suspension of divalent and trivalent iron salts (FeCl 2 /FeCl_) with a base such as sodiu hydroxide (NaOH) .
  • metals similar in structure t iron, such as Co and Mn can be incorporated into the horrenda, with a divalent salt of that metal. The result is then a mixed metal oxide precipta containing both ferrous and ferric oxides, as well as oxides of the divalent metal.
  • the ratio of Fe3+/Fe2+ ca be varied from 1/4 to 4/1 and still produce usable product.
  • a superparamagnetic metal oxide precipitate is formed.
  • the us of a high concentration of reactants and an abrupt change in pH favors the formation of small superparamagnetic metal oxides. Such oxides are preferred for use in the subsequent steps of this process.
  • the superparamagnetic metal oxide prepared in 6.3.1. is dispersed and oxidized further by sonication.
  • the sonication which can be conduct at ambient or elevated temperatures (up to 100 * C) serves a dual purpose: it serves to disperse any clusters of superparamagnetic particles (which increases the ultimate effects of the material on proton relaxation and, hence, enhances their effectiveness as MR contract agents) and, additionally, it serves to oxidize most, if not all, of fer- rous oxide (Fe 2+) to ferri.c oxi.de (Fe3+) .
  • the resultant material remarkably, is a soluble superparamagnetic iron oxyhydroxide which forms a superparamagnetic fluid.
  • the sonication can be accomplished in any commerci apparatus including in a continuous flow sonicator or by a sonic probe.
  • the former is especially useful when large Q volumes of materials are being handled and, for a continuous process, can be coupled with a heating and cooling apparatus to permit heating of the iron oxide prior to or after
  • the final step in the process is the transfer of t solution to an aqueous polycarboxylic buffer suitable for in vivo use.
  • This transfer is accomplished by dialyzing the fluid against the buffer at neutral pH, generally at a pH of 6-9, preferably 6-8.3. These conditions result in a stable superparamagnetic fluid; under acidic conditions (below a pH of about 6) a significant amount of a chelate of the iron begins to form rather than the superparamagnetic iron oxide.
  • the fluid from 6.3.2. is centri- fuged, to remove larger oxide aggregates, and the supernatan is dialyzed against the buffer.
  • the preferred buffer contai a citrate salt because of its suitability for _in vivo use a its long history as an injectable agent, but in general buffers containing salts of any polycarboxylic acid, (such a tartrate, succinate) or maleate, allow for the formation of stable superparamagnetic fluids.
  • the resultant fluids can then be autoclaved and stored until needed.
  • Superparamagnetic fluids containing metal oxides t which organic coatings are attached can be prepared by modifications of the above procedure.
  • Such organic coatings can be selected from a wide array of polymeric materials including, but not limited to, carbohydrates such as dextran (preferably having a molecular weight between 5,000 and 250,000 daltons), proteins (preferably having a molecular weight between 5,000 and 250,000 daltons) such as bovine or human serum albumen, polypeptides (preferably having molecul weights between 5,000 and 250,000 daltons) such as polylysin and polyglutamates and organosilanes (preferably having a molecular weight between 5,000 and 250,000 daltons) such as N-2-aminoethyl-3-aminopropyltrimethoxysilane.
  • the attachment can be accomplished during either the first or th second steps.
  • the coating material When attachment is accomplished during the first step, the coating material is mixed with the salt solution prior to the supermagnetic metal oxide precipitation. The coating material is attached to the resultant precipitate, a remains attached during the subsequent steps. Any unbound coating agent is removed during dialysis (step 3). In a preferred embodiment, superparamagnetic fluids containing dextran-coated iron oxides can be formed in this manner.
  • the attachment can also occur during the dispersio and oxidation second step by adding the coating agent prior the sonication and subsequently sonicating the mixture to fo the corresponding oxyhydroxide. Again, the unbound coating agents are removed by dialysis.
  • Superparamagnetic fluids containing silanized iron oxides are prepared in a similar manner. Initially, the iro oxides are subjected to sonication to form the oxyhydroxides The organosilane is then added and the mixture is sonicated disperse the materials. Finally, the silane is attached to the surface via a dehydration reaction. The polymerization the silane may occur before or after the deposition on the oxyhydroxide surface. In one embodiment, the silanization reaction occurs in two steps. First, a trimethoxysilane is placed in the sonicated mixture which condenses to form silane polymers:
  • An important aspect of this procedure is the metho of dehydration used to effect the adsorptive or covalent binding of the silane polymer to the metal oxide.
  • This association is accomplished by heating the silane polymer an metal oxide in the presence of a wetting agent miscible in both the organic solvent and water.
  • Glycerol with a boilin point of about 290°C, is a suitable wetting agent. Heating to about 105°C in the presence of glycerol serves two purpo- ses. It insures the evaporation of water, the organic solve (which may be e.g., methanol, ethanol, dioxane, acetone or other moderately polar solvents) and any excess silane mono ⁇ mer.
  • glycerol prevents the aggreg tion or clumping and potential cross linking, of particles that is an inherent problem of other silanization techniques known in the art wherein dehydration is brought about by heating to dryness. Thus, few aggregates are formed. Any formed aggregates are removed by centrifugation and the unbound silane is removed by hydrolysis.
  • the process used to prepare the superparamagnetic fluids of this invention is uniquely suited for preparing magnetic fluids suitable for ⁇ n vivo use. Specifically, the following advantages are noted:
  • the fluids produced by the methods described in section 6.3. are characterized by a high magnetic moment in high magnetic field (generally, about 5 to about 90 ⁇ MU/gm metal oxide) and a negligible magnetic moment in the absence of an applied field (i.e., a magnetic squareness of less than 0.1). Such behavior is characteristic of superparamagnetic particles.
  • FIG. 4 shows magnetic hysteresis loops for typica paramagnetic, superparamagnetic and ferromagnetic iron oxid Magnetization was measured in a vibrating sample magnetomet with fields up to 6,000 Gauss, 25"C.
  • the superparamagnetic fluid of the invention is nearly as magnetic as ferromagnetic iron oxide and far more magnetic than the paramagnetic ferric oxyhydroxide.
  • the solutions of the invention are superparamagnetic rather tha ferromagnetic, losing virtually all of their magnetic momen in the absence of an applied magnetic field.
  • the superparamagnetic solutions of this invention are characterized by a saturation magnetization of 30 EMU/gm or greater, with the loss of more than 90% of this magnetism i the absence of a magnetic field.
  • citrate from aqueous sodium, potassium, or ammonium citrate buffer
  • the retention of citrate can be used to distinguish the superparamagnetic fluids of this invention from other iron oxides.
  • Studies of citrate binding capacit of commercially available forms of iron oxides and ferric oxyhydroxides reveals that the iron oxides in the superparamagnetic fluids of this invention are capable of retaining nearly as much citrate as the paramagnetic (ionic ferric oxyhydroxide, while gamma ferric oxide and magnetite cannot retain significant amounts of citrate.
  • FIG. 5 The stability of fluids of the invention is shown i FIG. 5, where a superparamagnetic fluid made according to the procedure described in section 6.3. was subjected to autoclaving with and without citrate. Addition of 50 mM citrate stabilized a solution of 1.26 M iron oxide, preventin the gellation of the material.
  • the stability of the oxyhydroxide solutions of iron is related to the exchange of hydroxide for citrate ion. Both paramagnetic and superparamagnetic oxides retain citrate in a similar fashion:
  • the invention's superparamagnetic fluids are stabilized due to the ionic character of the iron oxide and the choice of appropriate anions.
  • the stable solutions ' of this invention comprise a metal concentration ranging from 0.05 to 5 molar and a citra ion concentration of 0.001 to 0.1 moles of citrate/mole preferably 0.01 to 0.1 moles of citrate/mole of iron at a pH ranging from about 6 to about 10.
  • a metal concentration ranging from 0.05 to 5 molar and a citra ion concentration of 0.001 to 0.1 moles of citrate/mole preferably 0.01 to 0.1 moles of citrate/mole of iron at a pH ranging from about 6 to about 10.
  • the ratio of citrate/iro must also increase to yield the stability.
  • they are compatible with physiological conditions.
  • the superparamagnetic fluids of the invention owe their stability in solution, not to their coating with polymers or surfactants, but to the existence of a cationic character of the iron oxide and its stabilization with anio such as citrate.
  • polymeric coatings though th help stabilize iron oxides, are not sufficient to protect t against the rigors of autoclaving.
  • superparamagnetic fluids made according to the invention ca be made omitting the polymer altogether and are highly stab
  • MR contrast agents work by shortening proton relaxation time and, thus, increases the contrast and overall image quality.
  • Two relaxation paramet termed spin-spin relaxation time (T.) and spin-lattice relaxation time (T 2 ) are used in the generation of the MR image.
  • the material of the invention is remarkable in its ability to shorten proton relaxation.
  • the materials prepared according to the invention are more poten enhancers of proton relaxation than either ferromagnetic materials or paramagnetic .ferric oxyhydroxide.
  • the highly dispersed state of the materials of the invention produces higher relaxivities than those characteristic of clustered materials (See 7.12 and Table III). The process, thus, yields superparamagnetic solutions optimized for their effects on proton relaxation time.
  • the high relaxivity (see Table III) of the materia of the invention is important to their pharmaceutical use as MR contrast agents, because it results in large effects on t MR image with small doses of iron.
  • superparamag netic iron oxides made according to the invention can pro- foundly improve liver imaging at doses of 1 mg of iron per kilogram of rat, while the LD50 for the rat is greater that 250 mg of iron per kilogram.
  • both the superparamagnetic particles in the dispersoids and the metal oxides in the superparamagnetic fluids of the invention have been found to be biodegradable when administered in vivo (see Examples 7.6 and 7.15).
  • iron the predominant species in the dispersoids and fluids accumulate in the liver, where it is eventually catabolized and incorporated into the subject's hemoglobin.
  • the dispersoids and fluids can be used in the treatmen of anemia, and indeed, the fluids have been shown to be as effective as Imferon (a commercially used preparation for treatment of anemia in humans) in the restoration of normal hematocrit levels in anemic rats.
  • Both the superparamagnetic particles in the dispersoids and the metal-oxides in the superparamagnetic fluids of the invention can be coated with various coating agents as described supra.
  • the use of such coatings permits the attachment of various biological molecules to the imagin agents to permit targeting of various organs.
  • antibodies can be bound by a variety of methods including diazotization and attachment through a glutaraldehyde or carbodiimide coupling moiety (Examples of these coupling methods can be found in U.S. Patent No. 4,628,037, which is incorporated herein by reference) .
  • Use of methods such as these permits maximum flexibility, as an antibody-directed superparamagnetic metal oxide can bind to a specific type of cell or tissue. This can permit an image to be generated which differentiates between the target and the surrounding tissue.
  • RES reticuloendothelial system
  • the subject is given a dose of paramagnetic iron oxide either prior to or along with the administration of the imaging agent.
  • the paramagnetic iron oxide should be as simlar to the agent as practical especially in particle size and coating.
  • the imaging agent is administere
  • An excellent blocking agent for a superparmagneti MR agent is a paramagnetic form of the same material. This because the effectiveness of a blocking agent depends on whether a competition for receptors results; cell surface receptors bind materials in circulation prior to internalization. This internalization is termed pinocytosi -4 , ,1-
  • dextran-coated paramagnetic iron oxide is used as a blocking agent for dextran coated superparamagnetic iron oxide.
  • This material ideal as a blocking agent for dextran-coated superparmagneti iron oxide contrast agents for the reasons below:
  • the extension of serum lifetime is of particular importance when MR measurements are used to confirm blood circulation (or lack thereof) .
  • the contrast agent is introduced parenterally and permitted to circulate.
  • T and T_ presence or absence of blood circulation can be determined.
  • Such a procedure ca be a valuable tool in the diagnosis of blood circulation disorders, and can be used to detect the flow of blood into areas where it is normally excluded, such as in strokes.
  • the resultant p_articles exhibit a diameter of abou 1400 angstroms as measured by light scattering. 7.2. Preparation of Particles Coated with Bovine Serum Albumin
  • BSA bovine serum albumi
  • 0.27M FeCl 3 0.27M FeCl 3
  • 0.16M eCl 2 80 mis of 7.5% NH.OH.
  • a black, magnetic solid forms comprised of particles.
  • the mixture is allowed to stand for 5 minutes and then centrifuged at 1,500 x g for 15 minutes to remove larger particles. The pellet is discarded and the supernatant place in a dialysis bag and dialyzed against 3 changes of 10 gallon of distilled water. Larger particles are again removed by centrifugation as above and discarded. Particles are then concentrated by ultrafiltration using an XM-50 membrane and a stirred cell filtration device from Amicon Corporation, Lexington, MA.
  • the resultant particles exhibit a diameter of about 1730 angstroms as measured by light scattering.
  • One hundred milliliters of solution of 0.8M FeCl_, 0.4M FeCl 2 and 0.4M HCl is added dropwise to 1000 ml of 2.4% NH OH and mixed for 5 minutes.
  • a black, magnetic solid forms comprised of easily visible particles. For particles to be visible, they must be larger than the wavelength of scattered light which is about 500 nm (0.5 microns).
  • the particles are isolated by attracting them to a permanent magnet on the outside of the reaction vessel and the solution decanted.
  • To the magnetic cake is added 55 mis of 50% triethylamine in water. Smaller particles are created.
  • the mixture is dialyzed overnight against water which causes the large particles to reappear. Just enough triethylamine is then added to again create the smaller particles resulting from t addition of triethylamine.
  • the particles are then filtered through a 0.2 micron filter indicating the final material is below this size.
  • FIG. 2 presents reproductions of five images obtained on a Technicare MR imager.
  • the images in FIGS. 2A and 2B were obtained prior to the introduction of the imagin agent using different imager settings, in neither case can t tumor be clearly seen;
  • FIGS. 2C and 2D are images of the sam rat liver and were obtained after a single 0.5mg/kg dose of the Section 6.1. dextran-coated particle by intravenous injection through the tail vein, the tumor is easily seen a the overall size and shape can be gauged; in FIG..2E the tu is marked by cross-hairs to aid in visualization.
  • FIG. 1 compares the T- of agar gel in the presenc of dextran-coated particles (produced in Example 7.1.) and ferromagnetic particle Pf-2228 (Pfizer) .
  • the relaxation ti in the presence of varying concentrations of each particle were determined on an IBM PC-20 NMR spectrometer at 0.47 Te (4700 Gauss) . It can clearly be seen that the superparamagnetic particle produces a much greater effect o T 2 than the ferromagnetic particle. Given the fact that superparamagnetic materials are much less magnetic than ferromagnetic materials, this result is quite surprising. 7.6. BIODEGRADABILITY OF DEXTRAN-COATED PARTICLES
  • a dispersion of uncoated superparamagnetic iron oxide particles in water was intravenously injected into Sprague-Dawley rats at a dosages 20, 37 and 243 micromoles
  • N is the number of rats examined.
  • the biodistribution of three uncoated and four dextran-coated particles was examined The uncoated agents were produced according to the procedure Section 7.3., the dextran-coated particles were produced according to the procedure of Section 7.1. except that the molecular weight of the dextran used for the coating was vari (see TABLE II) .
  • the contrast agent Prior to each experiment, the contrast agent were dialyzed against distilled water and subsequently inject into separate groups of Sprague-Dawley rats in a distilled wa carrier. The rats were periodically sacrificed and the relaxation times of the liver, spleen, and lung were determi on an IBM PC-20 NMR Spectrometer. Preprogrammed inversion recovery and Carr, Purcell, Meiboom, Gill pulse sequences we used to determine T. and T 2 , respectively.
  • the data suggest that the contrast agen are rapidly cleared from the lung, and are longer lived in t spleen and the liver. Additionally, it can be seen that the dextran-coated particles are cleared less rapidly than the uncoated ones, exerting a significant effect on the T value of the liver and spleen for about one week.
  • a solution of 0.25 M ferrous chloride and 0.5M ferric chloride (600 ml) was poured into a solution of 5 M NaOH (600 ml) .
  • the ammonium citrate buffer is 10 mM citrate, adjusted to pH 8.2 with NH OH.
  • the result is an autoclavable, homogeneous supermagnetic fluid.
  • a black magnetic slurry was formed.
  • the supernatant (from Section 7.10.3) was diluted t a total volume of 20 liters with deionized, sterile water and the resultant solution was dialyzed as in Example 7.9, except that a larger dialyzer concentrator, the DC 10, was used.
  • Th dialyzer cartridge had a 100,000 dalton molecular weight cutoff, permitting removal of dextran. Ultrafiltration was accomplished in a noncontinuous fashion, reducing the volume from 20 to 5 liters and adding 16 liter volumes of solution. Five volumes of 16 liters of deionized, distilled water were added.
  • Example 7 Sodium citrate was then added as 1M citrate buffer stock and the solution was dialyzed as in Example 7.9. The resultant citrate was adjusted to pH 6.5 with NaOH before autoclaving. The citrate to iron ratio was between 0.01 and 0.1 citrate/Fe in the final solution. (For example, for an iron concentration of 1.26M, 0.04 M citrate was present. The magnetic fluid was bottled and autoclaved (121"C, 30 minutes) The result is a sterile homogenous magnetic fluid as shown i FIG. 5.
  • Example 3 Due to the use of sonication, the material made in Example 3 is far smaller than that described in United State 15 Patent No. 4,554,088. Due to its small size, it cannot be manipulated with hand held magnets.
  • the glycerol dehydrati step is from US Patent 4,554,088 herein incorporated by reference..
  • the glycerol slurry from Section 7.11.2, was add to about 800 ml of water. Large aggregates of magnetic particles were removed by centrifuging the slurry at 1,000
  • Superparamagnetic fluid of the invention A dispersed fluid containing single superparamagnetic crystals of iron oxide prepared as described in Example 7.10. The magnetization curve of this material is presented in FIG. 4.
  • Fe 0. A ferromagnetic gamma ferric oxide used for data recording. This material was obtained from Pfizer Corp. Minerals, Pigments and Metals Division, catalogue #2228.
  • FeO:OH a paramagnetic, ferric oxyhydroxide used the treatment of anemia. It was obtained from Fisons Corporation and is sold under the trade names of Proferdex (Fisons corporation) or Imferon (Merrill Dow Inc.)
  • Fe 3+/DTPA a soluble complex of ferric ion and diethylenetriaminepentaa ⁇ etic acid (DTPA) .
  • DTPA diethylenetriaminepentaa ⁇ etic acid
  • the material of the invention is remarkable in its ability shorten proton relaxation times.
  • the value +4 —1 R2 for ferromagnetic dextran magnetite is 1.7 X 10 M sec
  • the materials prepared according to the invention ar more potent enhancers of proton relaxation time than either ferromagnetic materials or paramagnetic ferric oxyhydroxides.
  • well dispersed materials such as those of the invention, have higher relaxivities than clustered materials.
  • the process of the invention yields superparamagnetic solutions optimized for their effec on proton relaxation.
  • Magnetic hysteresis loops were obtained for the samples of the invention superparamagnetic fluid, gamma Fe_0 (ferromagnetic) , and FeO:OH (paramagnetic) examined in Examp 7.12, using a commercial vibrating sample magnetometer with fields up to 6000 Gauss, 25"C. The results are presented in FIG. 4.
  • the superparamagnetic fluid of the invention is nearly as magnet as ferromagnetic iron oxide and far more magnetic than the paramagnetic ferric oxyhydroxide, showing a high magnetic saturation.
  • the fluids of the invention are superparamagnet rather than ferromagnetic, losing virtually all of their magnetic moment in the absence of an applied magnetic field.
  • the superparamagnetic fluids of the invention retain amounts of citrate similar to commercially available ferric oxyhydroxides indicating that the iron in both preparations is in a similar chemical form.
  • Commercially available forms of iron oxide, such as gamma Fe 0. or Fe O do not retain significant amounts of citrate (the gamma Fe 0 was the same as that used in Examples 7.12 and 7.13 while th Fe_0. was purchased from Fisher Scientific Ine) .
  • Superparamagnetic fluids made according to example 7.9 were subjected to autoclaving with various concentration of citrate. At iron concentration of 1.26M, various concentrations of ammonium citrate, pH8 were added, and the resulting solutions heated 1 hour at 121°C. The results are presented in FIG. 5.
  • the 6 vials of Fig. 5B contained, as shown, citrate concentrations of 100, 50, 25, 15, 10 and 5 m citrate, respectively.
  • the vials were upright during autoclaving but were placed horizontally for the photograph. With the-vials lying horizontally, the presence of gelled material is evident when the upper portion of the vial is translucent.
  • the fully blackenend vials (citrate concentrations between 15 and 100 mM) indicate a solution of superparamagnetic materials was maintained.
  • the two vials o the right (citrate concentration of 5 and lOmM) show the formation of a gel.
  • FIG. 5A further shows the characterist gel obtained without citrate, or with inadequate citrate (5 and 10 mM citrate) .
  • Paramagnetic ferric oxyhydroxides are biodegradab and have long been used for the treatment of anemia. Therefore, the biodegradability of the invention's superparamagnetic fluids was compared with the paramagnetic ferric oxyhydroxides. The ability of both iron preparation to reverse anemia in rats was utilized as a model. The paramagnetic ferric oxyhydroxide was Imferon, and has dextr attached. The supermagnetic fluid also had dextran attache and was produced as described in Example 7.10.
  • Rats in group 1 received a chow containing iron and were sacrificed at weeks 5, 6, 7 and 8 to allow establishment of normal iron (hematocrit) levels in rat tissues.
  • Rats in groups 2, 3 and 4 received an iron defici diet.
  • Rats in group 2 were also sacrificed at weeks 5, 6, and 8 to allow establishment of normal iron levels in rat tissues.
  • Rats in groups 2, 3 and 4 received an iron defici diet.
  • rats groups 3 and 4 received intravenous (tail vein) injections iron to reverse their anemia and restore normal levels.
  • R in group 3 received Proferdex, while those in group 4 recei the dextranized superparamagnetic fluid.
  • Rats receiving i were injected with a single dose of 30 mg of iron per kilogram, a sufficient dose to reverse their anemia. The results are presented in Table V. TABLE V
  • the invention's super ⁇ paramagnetic iron oxide restores normal hematocrits levels i rats as well as the paramagnetic preparation, Imferon.
  • the superparamagnetic fluids of this invent posess a unique combination of magnetic, biological and ani retaining properties.
  • a rat of about 300 g was injected with 1 mg Fe/kg body weight of dextran-coated superpara ⁇ magnetic metal oxide produced as described in Example 7.1.
  • the rat was also injected with 2.5 m Fe/kg dextran-coated paramagnetic iron oxide (produced following the procedure described in example 7.1 except tha no divalent salt was used) 15 minutes prior to receiving th superparamagnetic material.
  • the T_ of the subject's blood measured periodically over the subsequent 3 hours. The results are present in Figure 7. Briefly, in both trials, the blood 2 dropped dramatically within 5 minutes after the superparamagnetic material was added.

Landscapes

  • Chemical & Material Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Nanotechnology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medicinal Chemistry (AREA)
  • Organic Chemistry (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Polymers & Plastics (AREA)
  • General Health & Medical Sciences (AREA)
  • Radiology & Medical Imaging (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Animal Behavior & Ethology (AREA)
  • Epidemiology (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Pharmacology & Pharmacy (AREA)
  • Bioinformatics & Cheminformatics (AREA)
  • Biotechnology (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Materials Engineering (AREA)
  • Proteomics, Peptides & Aminoacids (AREA)
  • Crystallography & Structural Chemistry (AREA)
  • Medical Informatics (AREA)
  • General Engineering & Computer Science (AREA)
  • Dispersion Chemistry (AREA)
  • Immunology (AREA)
  • Signal Processing (AREA)
  • Biophysics (AREA)
  • General Physics & Mathematics (AREA)
  • Condensed Matter Physics & Semiconductors (AREA)
  • General Chemical & Material Sciences (AREA)
  • Diabetes (AREA)
  • Hematology (AREA)
  • Medicines Containing Antibodies Or Antigens For Use As Internal Diagnostic Agents (AREA)
  • Materials For Medical Uses (AREA)
  • Magnetic Resonance Imaging Apparatus (AREA)
  • Investigating Or Analysing Biological Materials (AREA)

Abstract

The in vivo use of biologically degradable and metabolizable superparamagnetic metal oxides as MR contrast agents. Depending on their preparation, these metal oxides are in the form of superparamagnetic particle dispersoids or superparamagnetic fluids where the suspending medium is a physiologically-acceptable carrier, and may be uncoated or surrounded by a polymeric coating to which biological molecules can be attached. In the case of coated particles, the biological molecules can be chosen to target specific organs or tissues. The biodistribution of the metal oxides in target organs or tissues results in a more detailed image of such organs or tissues because the metal oxides, due to their superparamagnetic properties, exert profound effects on the hydrogen nuclei responsible for the MR image.

Description

Biodegradable Superparamagnetic Materials Used In Clinical Applications
This application is a continuation-in-part of the applicants' prior co-pending U.S. Application Serial No. 882,044 filed July 3, 1986, which is incorporated herein by reference.
1. INTRODUCTION
This invention relates to materials exhibiting certain magnetic and biological properties which make them uniquely suitable for use as magnetic resonance imaging (MRI agents to enhance MR images of animal organs and tissues. More particularly, the invention relates to the .in vivo use biologically degradable and etabolizable superparamagnetic metal oxides as MR contrast agents. Depending on their preparation, these metal oxides are in the form of superparamagnetic particle dispersoids or superparamagnetic fluids where the suspending medium is a physiologically- acceptable carrier. These dispersoids and fluids are administered to animals, including humans, by a variety of routes and the metal oxides therein collect in specific targ organs to be imaged. The biodistribution of the metal oxide in target organs or tissues results in a more detailed image of such organs or tissues because the metal oxides, due to their superparamagnetic properties, exert profound effects o the hydrogen nuclei responsible for the MR image. In addition, the dispersoids and fluids are quite stable and, i the case of the fluids, can even be subjected to autoclavin without impairing their utility. Thus, the materials are well-suited for in vivo use. The combination of superparamagnetism and biodegradability makes the materials described herein particularly advantageous for use as MR contrast agents. Superparamagnetism, which results in profound capabilities alter MR images, makes it possible to use these materials i concentrations lower than those required for MRI with other types of magnetic materials. Biodegradability results in optimum retention times within the organs and tissues to be imaged, i.e., the materials remain within the organ or tiss sufficiently long to permit an image to be obtained, yet ar eventually cleared from or metabolized within the organ or tissue. Remarkably, when iron-based agents are administere the iron thereon is eventually metabolized and incorporated into the subject's hemoglobin.
These materials can, therefore, be used for a variety of clinical diagnostic purposes including, but not limited to, detection of cancerous lesions in liver and oth reticuloendothelial tissue, detection of cancerous or other lesions in the intestine, detection of liver diseases, such cirrhosis and hepatitis, and assessment of liver regenerati Those that are iron-based are also clinically useful as ant anemia agents.
2. BACKGROUND OF THE INVENTION
2.1 IN VIVO NMR IMAGING; GENERAL CONSIDERATIONS
Nuclear magnetic resonance (NMR) is now widely us for obtaining spatial images of human subjects for clinical diagnosis. Clinical usage of NMR imaging, also called magnetic resonance imaging or, simply, MRI, for diagnostic purposes has been reviewed [see e.g., Pykett, et al., Nucle Magnetic Resonance, pgs. 157-167 (April, 1982) and T.F. Budinger, et al.. Science, pgs. 288-298, (October, 1984)]. Several advantages of using such a procedure over currently used diagnostic methods, e.g., x-ray computer-aided tomograp (CT) , are generally recognized. For instance, the magnetic fields utilized in a clinical NMR scan are not considered to possess any deleterious effects to human health (see Budinge supra. , at 296) . Additionally, while x-ray CT images are formed from the observation of a single parameter, x-ray attenuation, MR images are a composite of the effects of a number of parameters which are analyzed and combined by computer. Choice of the appropriate instrument parameters such as radio frequency (Rf) , pulsing and timing can be utilized to enhance (or, conversely, attenuate) the signals of any of the image-producing parameters thereby improving image quality and providing better anatomical and functiona information. Finally, the use of such imaging has, in some cases, proven to be a valuable diagnostic tool as normal a diseased tissue, by virtue of their possessing different parameter values, can be differentiated in the image.
In MRI, the image of an organ or tissue is obtain by placing a subject .in a strong external magnetic field an observing the effect of this field on the magnetic properti of the protons (hydrogen nuclei) contained in and surroundi the organ or tissue. The proton relaxation times, termed T. and T,, are of primary importance. T. (also called the spi lattice or longitudinal relaxation time) and T2 (also calle the spin-spin or transverse relaxation time) depend on the chemical and physical environment of organ or tissue proton and are measured using the Rf pulsing technique; this information is analyzed as a function of distance by comput which then uses it to generate an image. The image produced, however, often lacks definitio and clarity due to the similarity of the signal from other tissues. To generate an image with good definition, T and/ T_ of the tissue to be imaged must be distinct from that of the background tissue. In some cases, the magnitude of thes differences is small, limiting diagnostic effectiveness. Thus, there exists a real need for methods which increase or magnify these differences One approach is the use of contrast agents.
2.2. MRI CONTRAST AGENTS
As any material suitable for use as a contrast age must affect the magnetic properties of the surrounding tissu MRI contrast agents can be categorized by their magnetic properties.
Paramagnetic materials have been used as MRI contrast agents because of their long recognized ability to decrease T.. [ einmann et al.. Am. J. Rad. 142, 619 (1984), Greif et al. Radiology 157, 461 (1985), Runge, et al. Radiology 147, 789 (1983), Brasch, Radiology 147, 781 (1983) Paramagnetic materials are characterized by a weak, positive magnetic susceptibility and by their inability to remain magnetic in the absence of an applied magnetic filed.
Paramagnetic MRI contrast agents are usually transition metal ions of iron, manganese or gadolinium. The may be bound with σhelators to reduce the toxicity of the metal ion (see Weinman reference above) . Paramagnetic materials for use as MRI contrast agents are the subject of number of patents and patent applications. (See EPA 0 160 552; UK Application 2 137 612A; EPA 0 184 899; EPA 0 186 947 US Patent 4,615,879; PCT WO 85/05554; and EPA 0 210 043). Ferromagnetic materials have also been used as contrast agents because of their ability to decrease T- [Medonca-Dias and Lauterbur, Magn. Res. Med. 3_, 328, (1986); Olsson et al., Mag Res. Imaging , 437 (1986); Renshaw et al. Mag Res. Imaging 4, 351 (1986) and 3_, 217 (1986)]. Ferromagnetic materials have high, positive magnetic susceptibilities and maintain their magnetism in the absence of an applied field. Ferromagnetic materials for use as MRI contrast agents are the subject of recent patent applications [PCT WO 86/01112; PCT WO 85/043301].
A third class of magnetic materials termed superparamagnetic materials have been used as contrast agents [Saini et al Radiology, 167, 211 (1987); Hahn et al., Soc. Ma Res. Med. 4(22) 1537 (1986)]. Like paramagnetic materials, superparamagnetic materials are characterized by an inability to remain magnetic in the absence of an applied magnetic field. Superparamagnetic materials can have magnetic susceptibilities nearly as high as ferromagnetic materials an far higher than paramagnetic materials [Bean and Livingston J Appl. Phys. suppl to vol. 3_0_, 1205, (1959)].
Ferromagnetism and superparamagnetism are propertie of lattices rather than ions or gases. Iron oxides such as magnetite and gamma ferric oxide exhibit ferromagnetism or superparamagnetism depending on the size of the crystals comprising the material, with larger crystals being ferromagnetic [G. Bate in Ferromagnetic Materials. vol. 2, Wohlfarth (ed.) p.439].
As generally used, superparamagnetic and ferromagnetic materials alter the MR image by decreasing 2 resulting in image darkening. When injected, crystals of these magnetic materials accumulate in the targeted organs o tissues and darken the organs or tissues where they have accumulated. Abnormal volumes of liver, such as tumors, are deficient in their ability to take up the magnetic materials and appear lighter against normal background tissue than the would without contrast agent.
2.3 SUPERPARAMAGNETIC MATERIALS
As stated supra, superparamagnetic materials posse some characteristics of paramagnetic and some characteristic of ferromagnetic materials. Like paramagnetic materials, superparamagnetic materials rapidly lose their magnetic properties in the absence of an applied magnetic field; they also possess the high magnetic susceptibility and crystallin structure found in ferromagnetic materials. Iron oxides suc as magnetite or gamma ferric oxide exhibit superparamagnetis when the crystal diameter falls significantly'below that of purely ferromagnetic materials.
FOΪ: cubic magnetite (Fe O ) this cut-off is a crystal diameter of about 300 angstroms [Dunlop, J. Geophys. Rev. 7_8_ 1780 (1972)]. A similar cut-off applies for gamma ferric oxide [Bare in Ferromagnetic Materials, vol. 2, Wohfarth (ed.) (1980) p. 439]. Since iron oxide crystals a generally not of a single uniform size, the average size of purely ferromagnetic iron oxides is substantially larger th the cut-off of 300 angstroms (.03 microns). For example, w gamma ferric oxide is used as a ferromagnetic material in magnetic recording, (e.g., Pfizer Corp. Pf 2228), particles are needle-like and about 0.35 microns long and .06 microns thick. Other ferromagnetic particles for data recording ar between 0.1 and 10 microns in length [Jorgensen, The Comple Handbook of Magnetic Recording, p. 35 (1980)]. For a given - ,7_-
type of crystal, preparations of purely ferromagnetic particles have average dimensions many times larger than preparations of superparamagnetic particles.
The theoretical basis of superparamagnetism has bee described in detail by Bean and Livington [J. Applied Physics Supplement to volume 30, 1205 (1959)]. Fundamental to the theory of superparamagnetic materials is the destabilizing effect of temperature on their magnetism. Thermal energy prevents the alignment of the magnetic moments present in superparamagnetic materials. After the removal of an applied magnetic field, the magnetic moments of superparamagnetic materials still exist, but are in rapid motion, causing a randomly oriented or disordered magnetic moment and, thus, no net magnetic field. At the temperatures of biological system and in the applied magnetic fields of MR i agers, superparamagnetic materials 'are less magnetic than their ferromagnetic counterparts. For example, Berkowitz et al. [ (J. App. Phys. 3_9, 1261 (1968)] have noted decreased magnetism of small superparamagnetic iron oxides at elevated temperatures. This may in part explain why workers in the field of MR imaging have looked to ferromagnetic materials as contrast agents on the theory that the more magnetic a material is per gram, the more effective that material should be in depressing T_ [Drain, Proc. Phys. Soc. _80, 1380 (1962) ; Medonca-Dias and Lauterur, Mag. Res. Med. 3_, 328 (1986)].
2.4. WATER-BASED SUPERPARAMAGNETIC SOLUTIONS
It has been recognized for some time that superparamagnetic particles can be fashioned into magnetic fluids termed ferrofluids [see Kaiser and Miskolczy, J. Appl. Phys. 4JL 3_ 1064 (1970)]. A ferrofluid is a solution of very fine magnetic particles kept from settling by Brownian motion To prevent particle agglomeration through Van der Waals attractive forces, the particles are coated in some fashion. When a magnetic field is applied, the magnetic force is transmitted to the entire volume of liquid and the ferroflui responds as a fluid, i.e. the magnetic particles do not separate from solvent.
Another approach to synthesizing water-based magnetic compounds is disclosed by Gable et al (U.S. Patent No. 4,001,288). Here, the patent discloses that magnetite c be reacted with a hydroxycarboxylic acid to form a water soluble complex that exhibits ferromagnetic behavior both in the solid form and in solution.
- 2.4.1. PROBLEMS MANIPULATING AQUEOUS SOLUTIONS
OF SUPERPARAMAGNETIC MATERIALS
Approaches to the synthesis of aqueous fluids of superparamagnetic iron oxides often involve surrounding iron oxide crystals with polymer or surfactants in an effort to block the attractive forces between the crystals that promot aggregation. In many cases however, the polymer does not completely coat the oxide and the resultant material maintai much of the sensitivity to clumping or aggregation characteristic of the uncoated iron oxide. The tendency to clump, and other peculiar properties of iron oxide solutions hamper the manipulations of these solutions needed in pharmaceutical manufacture.
The manufacture of a magnetic pharmaceutical solution such as an MRI contrast agent requires an extremely stable solution so certain manipulations, common in pharmaceutical manufacture, can be carried out. Solution stability is defined as the retention of the size of the magnetic material in solution; in an unstable solution the _g_
material will clump or aggregate. Such changes in the size o magnetic material alter its biodistribution after injection, an intolerable situation for an MRI contrast agent. A high degree of stability is required to perform common operations 5 associated with pharmaceutical manufacture such as dialysis, concentration, filtration, centrifugation, storage of concentrates prior to bottling, and long term storage after bottling. Particular problems are posed by the need to sterilize aqueous solutions of metal oxide, e.g. iron oxide, 10 for pharmaceutical use.
Additionally, concentrated solutions of aqueous superparamagnetic materials cannot be sterilized by filtratio even when the solution is comprised of materials smaller than
1 the pore of the filter. This phenomena is related to the concentration of the solution, for dilute solutions can be filter sterilized. Filter-sterilized, dilute material can be reconcentrated and dispensed into sterile bottles, but such operations offer many chances to recontaminate the produάt.
20 Autoclaving solutions of superparamagnetic materials after bottling is preferable, since sterilization is achieved after final bottling, and there is little opportunity for contamination of the final product. Autoclaving involves heating sealed solutions to 121*C for 30 minutes. Such
25 extreme temperatures induce aggregation or clumping of the superparamagnetic oxides, making them unusable as an injectable material.
2.5. PARAMAGNETIC FERRIC OXIDES
^ '30
Paramagnetic iron oxides or ferric oxides are currently used in the treatment of anemia under many trade names such as Imferon. When dissolved in aqueous solution, such materials can be represented as FeO.OH and are termed
35 ferric oxyhydroxides. They are paramagnetic and exert small if any, effects of proton relaxivity. They are stable, undergo the manipulations discussed supra for pharmaceutical manufacture, and are commercially available as drugs used in the treatment of anemia.
3. NOMENCLATURE
The term "biodegradable" in reference to the materials of this invention is defined as being metabolized and/or excreted by the subject within 30 days or less; for superparamagnetic iron oxides, the term is further defined a being incorporated into the hemoglobin of a subject within 3 days or less after administration.
The term "blocking agent" is defined as any materi which when administered parenternally to a subject, will competitively bind to the receptors of the cells of the reticuloendothelial system which recognize and bind MRI contrast agents.
The term "superparamagnetic fluid" defines any met oxide fluid produced by the methods described in section 6.3 herein, which has the characteristics described in section 6 herein.
4. SUMMARY OF THE INVENTION
It is an object of this invention to provide an i vivo MR imaging technique for diagnostic purposes which wil produce a clear, well-defined image of a target organ or tissue. Specifically, it is an object of this invention to provide an imaging method using MR contrast agents which are easily administered, exert a significant effect on the image produced and which distribute jln vivo to specific orga or tissues. These contrast agents are stable in vivo, can b easily processed for in vivo use, and overcome problems of toxicity and excessively long retention in the subject (i.e. are biodegradable) . It is further an object of this inventi to provide a means whereby these contrasts agents can be directed, in vivo, to a specific target organ or tissue.
This invention provides a novel MR imaging method using biodegradable superparamagnetic metal oxides as con¬ trast agents which fulfill the foregoing objectives. Such materials, it has been discovered, combine an optimal balanc of features and are particularly well-suited for use as MR contrast agents. Remarkably, it has been found that these superparamagnetic materials exert a greater effect on T? tha ferromagnetic or paramagnetic materials, thereby producing a well-resolved, negative contrast image of an in vivo target organ or tissue. It has also been surprisingly found that the materials used in the methods of this invention exhibit highly desirable in vivo retention times, i.e., they remain intact for a sufficient time to permit the image to be taken yet are ultimately biodegradable. Remarkably, once degraded iron-based materials serve as a source of nutritional iron. Additionally, they are sufficiently small to permit free circulation through the subject's vascular system and rapid absorption by the organ/ tissue being imaged, allowing for maximum latitude in the choice of administration routes and ultimate targets.
In one embodiment, the materials used as MR imagin agents comprise superparamagnetic metal oxide particles whic comprise superparamagnetic crystalline cores. Each core is composed of magnetically active metal oxides and can range from about 50 to about 500 angstroms in diameter. The cores may be uncoated or, alternatively, coated with a polysac- charide, a protein, a polypeptide or any composite thereof. By way of illustration, the polysaccharide coating may comprise dextran of varying molecular weights and the prote coating may comprise bovine or human serum albumin. With coatings, the overall particle diameter ranges upward to about 5,000 angstroms. In the case of coated particles, th coatings can serve as a base to which various biological molecules can be attached. The biological molecules can be used to direct the particles to the desired target and are preferentially recognized and bound by the target organ or tissue. Such molecules include proteins, polysaccharrides, hormones, antibodies, etc.
Preferred superparamagnetic particles comprise ir oxides with crystal sizes ranging from about 50 to about 50 angstroms. These iron oxide particles have surface areas
2 greater than 75 m /gram. In aqueous solution, these iron oxide particles have a size range between about 50 and abou 5,000 angstroms, including coatings, if any. The superpara magnetic iron oxides have magnetic saturations between abou 5 and about 90 electromagnetic units (EMU) per gram of oxid at room temperature (approximately 25βC) and possess a magnetic squareness of less than 0.10, i.e., lose greater than 90% of their magnetism when an applied magnetic field removed.
Superparamagnetic particles with these general dimensions overcome problems associated with the use of ferromagnetic and paramagnetic materials as MR contrast agents. Specifically, superparamagnetic particles, because they are smaller than ferromagnetic particles, are more abl to avoid uptake by the subject's reticuloendothelial cells and may be more effectively targeted to other organ and tissue sites within the body. Also, because the superparamagnetic particles are smaller than ferromagnetic particles, they have higher surface area per unit mass and are more easily and rapidly digested by chemical or metaboli processes. However, the superparamagnetic particles used herein, because they are larger than paramagnetic ions, are not so rapidly metabolized in the target organ or tissue as to prevent convenient imaging.
Uncoated or coated particles may be suspended in a appropriate medium (e.g., saline) to form a particle disper- soid that has the properties of a solution. The particles d not settle upon standing and do not scatter visible light (i.e., the solution appears translucent). Solvent can be added (decreasing) or removed (increasing) particle concentration.
This dispersoid of particles may be administered t the subject being studied. Depending on the route of administration, the particles are distributed to various target organs, where absorption occurs. For example, when the superparamagnetic particles are administered intravascularly (e.g., intravenously or intra-arterially) , they are selectively distributed to reticuloendothelial organs, including liver, spleen, lymph nodes and bone marrow and, to a lesser extent, lung. However, when the superparamagnetic particles are administered via the gastrointestinal tract, e.g., orally, by intubation or by enema, they can be used as imaging agents for the organs and tissues of the gastrointestinal tract.
The use of sub-micron sized particles is particu¬ larly important when the route of administration is intra- vascular, as such particles can freely circulate in the subject's vascular system, since they are small enough to pass through the capillary network. Thus, such contrast agents can be carried to targeted organs or tissue after being intravascularly administered with a minimum of trouble or delay.
In one embodiment, a dextran-σoated iron oxide particle dispersoid is injected into a subject's bloodstream and the particles localize in the liver. The particles are absorbed by the reticuloendothelial cells of the liver by phagocytic uptake; a particular benefit of this mode of uptake is that phagocytized iron is metabolized and cleared from the liver much more slowly (but not so slowly as to lea to undesirably long retention times) than prior art paramag¬ netic ions. Additionally, the dextran-coated particles can be preferentially absorbed by healthy cells, with less uptak into cancerous (tumor) cells. This preferential uptake enhances the contrast between healthy and cancerous tissue and allows for better definition of the tumor location on t image.
In another embodiment of this invention, the mate als comprise stable, biodegradable superparamagnetic metal oxides, preferably ferric oxides, in the form of superparamagnetic fluids. These superparamagnetic fluids exhibit some of the magnetic properties of superparamagneti ferrofluids (e.g., the metal oxides in them cannot be remov from solution by magnetic mani ulation) , yet the metal oxid in them can be easily be reclaimed from the bulk fluid by physical means (e.g. centrifugation) and, ultimately redispersed in the bulk fluid. When dispersed, the metal oxides will not scatter visible light, indicating the individual metal oxide "particles" are quite small (general between 50 and 4000 angstroms in diameter.) .
- -
The metal oxides of the invention exist in the bul fluid as ionic crystals, having both ionic and crystalline characteristics. In common with magnetite (Fe_0.) and gamma ferric oxide (gamma Fe?0_ they have high magnetic susceptibility. In common with ionic forms of ferric oxide the so-called ferric oxyhydroxides, they cause retention of anions. The counterion to the crystals can be any one of a number of organic anions."
In a preferred embodiment, the metal oxide is a superparamagnetic ferric oxyhydroxide and the counterion is citrate. The use of citrate counterions also confers a distinct advantage to the fluids as it renders them highly stable. In fact, the citrated fluids can withstand autoclaving greatly facilitating sterile administration.
The metal oxides in the superparamagnetic fluids m also be surrounded by a coating comprising a polysaccharide, protein, a polypeptide, an organosilane, or any composite thereof. These polymeric coatings serve a dual purpose, helping to stabilize the superparamagnetic fluids as well as serving as a base to which biological molecules can be attached. These biological molecules can be used to direct particles to the desired target and are preferentially recog nized and bound by the target organ or tissue. These mole¬ cules include proteins, polysaccharides, hormones, antibodie etc.
The superparamagnetic fluids, whether comprised of coated or uncoated metal oxides, can be administered to a subject by any of the means described supra for the metal oxide dispersoids. Furthermore, in general the fluids are quite stable and can be prepared well in advance of use and stored. The superparamagnetic fluids, containing both coated an uncoated metal oxides, are produced by a unique three step process from a mixture of Fe 2+ and Fe3+ salts. In addition, this process permits incorporation of other metals similar t iron (such as cobalt (Co) and manganese (Mn) into the fluids by replacing some of the divalent iron salts with divalent salts of these metals. In the process, the salts are precipitated in base to form the corresponding oxides. These oxides are then dispersed and oxidized by sonication of the mixture; the result, remarkably, is a superparamagnetic ferr oxyhydroxide. Insoluble oxides can then be removed by centrifugation and the final fluid is dialyzed against a neutral or alkaline buffer suitable for in vivo use.
In a preferred embodiment, the salt mixture is
FeCl2/FeCl in a 1:2 ratio and the buffer is lOmM ammonium citrate at pH 8.2. The result is a superparamagnetic fluid unusual stability, characterized by its capacity to withstan autoclaving. »
Once administered, both the metal oxides of the superparamagnetic particle dispersoids and the superpara¬ magnetic fluids collect in the target organ or tissue and exert a profound contrast effect to permit an image to be taken. The superparamagnetic metal oxides act primarily to enhance T_ relaxation, but T. is also affected (although to lesser extent) .
Another embodiment of this invention presents a method for extending the lifetime of the superparamagnetic metal oxides in the subject's serum. The method comprises administering a dose of paramagnetic metal oxide in the same form as the superparamagnetic imaging agent (i.e. approprate particle size and, if applicable, the same coating) as a blocking agent prior to the administration of the imaging agent. This blocking agent- will compete with the imaging agent for binding to the reticuloendothelial system (RES) receptors. Since the RES is responsible for removing impurities from the blood, the binding of the blocking agent greatly increases the serum lifetime of the imaging agent. Potential applications of this procedure include, but are no limited to, use of MRI to"diagnose blood circulation disorde and strokes.
5. BRIEF DESCRIPTION OF THE FIGURES
FIG. 1 is a graphical representation comparing the effect of ferromagnetic and superparamagnetic contrast agent on T2;
FIG. 2 is a composite of five in vivo MR images of cancerous rat liver obtained on a Technicare MR Imager;
FIGS. 2A and 2B were obtained without the use of contrast agents and were taken at different settings of instrument;
FIGS. 2C and 2D were obtained after the intravenou administration of the dextran-coated particle produced in Example 6.1. at a dosage of 0.5mg/kg; the tumor can clearly seen;
FIG. 2E is the image reproduced in FIG. 2C showing the tumor highlighted by crosshairs; FIG. 3 is a graphical representation of the % T_ reduction in liver and spleen tissue for three different dosages of an uncoated superparamagnetic particle as a function of time after administration;
FIG. 4 presents hysteresis curves for paramagnetic, ferromagnetic and superparamagnetic iron oxides;
FIG. 5 shows the effect of autoclaving on superparamagnetic fluids having varying concentrations of citrate;
FIG. 6 presents a schematic diagram of the apparatu used in example 7.10; and
FIG. 7 is a graphical representation of the T_ of rat blood as a function of time after the injection of a dextran-coated superparamagnetic iron oxide particle with and without the use of a blocking agent.
6. DETAILED DESCRIPTION OF THE INVENTION
6.1. PREPARATION OF COATED SUPERPARAMAGNETIC IRON OXIDE PARTICLES
The synthesis of superparamagnetic iron oxide particles for use as MRI contrast agents is accomplished by mixing ferrous and ferric salts with base to form a black, magnetic oxide of iron. Crystals result from such precipita tions, for when the material is subjected to X-ray diffrac¬ tion analyses long range order is apparent. A diameter of between about 50 and about 300 angstroms for such crystals has been calculated although crystals may range in diameter from about 50 to about 500 angstroms. The iron oxides have correspondingly high surface areas, greater than about 75 m /gm.
The presence of ferrous salts prior to base addi¬ tion insures the formation of a black, crystalline magnetic iron oxide. Without the ferrous ion, paramagnetic ferric oxide gels (noncrystalline materials) result (as described e.g., in U.S. Patent No. 2,885,393). The presence of divalent iron, so essential to the formation of the superparamagnetic material, can then be removed by exposure of the material to oxidizing conditions. Oxidation of the iron to produce a ferric oxide after formation of the crysta does not alter the usefulness of the material as a contrast agent in MRI or the superparamagnetism.
It is to be understood throughout this detailed description, that the use of superparamagnetic iron oxides a MR contrast agents is but one embodiment of the invention an that superparamagnetic oxides of other magnetic metals, e.g. cobalt or gadolinium, may be substituted for iron oxides.
There are two general strategies for the formation of the coated superparamagnetic iron oxide particles suitabl for MRI.
1. Synthesis of iron oxide by precipitation in th presence of polymers like dextran, or polyglutaraldehyde or other material. Such syntheses include those described by London et al. , U.S. Patent No. 2,870,740, Molday, U.S. Paten No. 4,452,773, Cox et al. , Nature, 208, 237 (1965) and Rembaum, U.S. Patent No. 4,267,234; all of which are incor¬ porated herein by reference. 2. Synthesis of the iron oxide by precipitation followed by coating with a polymer like dextran or other material. This type of synthetic route is utilized by Elϊttore, Phys. Rev. 54, 309 (1938) and Ohgushi et al. , J. Mag Res. , 29, 599 (1978) ; both of which are incorporated herein by reference.
With proteins and dextrans, synthesis of the oxide in the presence of the polymer seems to effect a tight association between the polymer and the oxide. The synthesi of oxide first, followed by exposure to a protein or dextran yields a coated particle with the coating being held to the particle surface by relatively weak adsorption phenomena. However, if the oxide and adsorbed polymer can be manipulated, stored and injected in the presence of nonadsorbed polymer, the weakness of the association between oxide and polymer is not a problem. For example, when the particles of Section 6.1.3. (uncoated) are diluted 1:1 into neutral buffer containing 1% w/v human serum albumin (HSA) , considerable protein will adsorb to the oxide surface." This approach to the synthesis of an albumin coated magnetic particle is a practical one for an imaging agent. The HSA coated particle (plus HSA in solution) can be injected into patient and the HSA in solution mixes with HSA in serum. When particles are made by this approach the loosely associated HSA can be removed by treatments such as moderate temperature (50"C) or high salt (1M NaCl) .
The coating methods are general and can be performed with a variety of physiologically acceptable pro¬ teins and carbohydrates, particularly those with molecular weights from about 5,000 to about 250,000 daltons. other polymeric coatings include, but are not limited to, albumin/dextran composites, ficoll, dextrin, starch, glycoge and polyethylene glycol.
6.1.1. PREPARATION OF POLYSACCHARIDE- COATED PARTICLES
Polysaccharide-coated superparamagnetic iron oxide particles (about 50 to about 5000 angstroms in diameter) useful as MR contrast agents are prepared by a single-step process according to the procedure of Molday [U.S. Patent No.
4,452,773] incorporated herein by reference above. In a preferred embodiment, dextramzed divalent (Fe 2+) and trival ent (Fe 3+) iron salts, e.g., FeCl_ and FeCl , are precipita¬ ted from an aqueous solution containing a mixture of the iro salts and dextran (molecular weight of dextran can vary from 5,000 to 250,000 daltons) by the dropwise addition (to pH=lθ) of base ammonium hydroxide at 60-65*C, followed by centrifugation at 1500 x g for 15 minutes to remove the oversized particles which are subsequently discarded. The remaining particles are dialyzed against distilled water and can be concentrated by ultrafiltration. Any unbound dextran can be removed by gel filtration chromatography in a chloride/acetate buffer. 3+ 2+
The ratio of Fe to Fe is preferentially main¬ tained at about 2:1, but can be varied from about 0.5:1 to about 4.0:1 without substantial changes in product quality and efficiency as contrast agents.
Likewise, bases other than ammonium hydroxide (NH.OH) can be used, but NH.OH is preferred because the ammonium ion has a slight dispersing effect on iron oxides which increases the yield. As mentioned above, various magnetically active metals notably Co, and Mn, may be substituted for Fe without any deleterious effect on the efficiency of the particles as contrast agents. Use of other polysaccharides such as stare- hes, glycogen or dextrins is also contemplated.
6.1.2. PREPARATION OF PROTEIN-COATED PARTICLES
Protein-coated superparamagnetic iron oxide parti¬ cles are prepared by a single-step process similar to that of Molday [U.S. Patent 4,452,733]. The protein-coated particles can be prepared like the dextran coated wherein the iron salts (e.g., ecl2 and FeCl3) and the protein are dissolved in water and the coated iron oxide particles are precipitated by the dropwise addition of base (NH.OH) to pH=10. In an alternative embodiment the protein can be dissolved in the base and an aqueous solution of the iron salts can be added dropwise to form a coated particle.
In either method, the oversized particles are subsequently collected by centrifugation at 1500 x g and the remaining particles are subjected to dialysis against distilled water followed by ultrafiltration. Any unbound protein can be removed by gel filtration chromatography in a chloride/acetate buffer.
As with the polysaccharide coated particles, both the coating composition and the Fe 3+/Fe2+ ratio (about 2/1) can be varied from about 0.5:1 to about 4:1 without any deleterious effect on the efficiency of these particles as contrast agents. - _ _
-23-
As mentioned above, various magnetically active metals notably Co, and Mn, may be substituted for Fe without any deleterious effect on the efficiency of the particles as contrast agents.
6.1.3. PREPARATION OF UNCOATED PARTICLES
Uncoated FeO and Fe2°3 superparamagnetic particles are prepared by mixing an aqueous solution of ferric chlorid (FeCl_) with ferrous chloride (FeCl_) in HC1 and precipitat¬ ing in 0.7 molar aqueous ammonia. The base precipitation offers a dual advantage in that the base reacts with the iro chlorides to form uncoated superparamagnetic iron oxide particles. The precipitate (a gelatinous substance) is then collected by centrifugation or application of a magnetic field followed by decantation of the liquid phase.
The gel is then peptized to form a dispersoid by mixing with either 1 molar aqueous tetramethylammonium hydroxide (to form an alkaline dispersoid) or 2 molar aqueou perchloric acid (to form an acidic dispersoid) followed by centrifugation and redispersion- in water. Both of these dispersoids show remarkable stability and, being colloidal i nature, will not possess large jsolid particles. The counter ions, either tetramethlylammonium hydroxide or perchlorate, are charged in basic or acidic media, respectively and, thus prevent complex coagulation in solution; the particles (com¬ plexes of iron oxide/counterions) can be repeatedly precipi¬ tated and re-dispersed in solution and will retain this property. In an alternative embodiment the particles can be collected by the application of an external magnetic field rather than centrifugation. The resultant magnetic cake is then peptized by the appropriate counterion.
The ratio of Fe 3+/Fe2+ i.s preferably maintai.ned a about 2/1, but can be varied between about 0.5/1 and about
4/1. Decreasing the ratio will produce larger and increasi the ratio will produce smaller sized particles. Using the 2/1 ratio and 0.7M NH.OH, the average particle size produc is about 1200 angstroms as measured by light scattering.
6.2. USE OF THE PARTICLES AS MR IMAGING AGENTS
The magnetic materials described above can be use as contrast-enhancing agents for _in vivo MR imaging. In on embodiment, the particles are dispersed in a suitable injection medium, such as distilled water or normal saline, or any other physiologically acceptable carrier known in th art, to form a dispersoid which is introduced into the subject's vascular system by intravenous injection. The particles are then carried through the vascular system to t target organ where they are taken up.
When intravascularly administered, the particles will be preferentially taken up by organs which ordinarily function to cleanse the blood of impurities, notably the liver, spleen, and lymph nodes, and the other organs which tend to accumulate such impurities, notably bone and neural tissue and to some extent, lung. In each of these organs a tissues, the uptake into the reticuloendothelial cells will occur by phagocytosis, wherein the particles enter the indi vidual cells in membrane-bound vesicles; this permits a longer half-life in the cells, as such membrane-bound parti cles will not tend to clump or aggregate (aggregates are rapidly metabolized and cleared from the organ/tissue) . Other uptake mechanisms are possible, e.g., pinocytosis. Also, it is possible that the other cells of the liver (hepa tocytes) may absorb the magnetic particles.
Because cancerous tumor cells can lack the ability of phagocytic uptake, the- intravascularly administered particles can serve as valuable tools in the diagnosis of cancer in the above-mentioned organs, as tumors will be immediately distinguishable on any image obtained.
In a another embodiment, the particles are adminis tered as dispersoids in a physiologically acceptable carrier such as distilled water, into the gastrointestinal tract, which includes the esophagus, stomach, large and small intestine, either orally, by intubation, or by enema, in a suitable medium. . The particles are preferentially absorbed by the cells of the tract, especially those of the intestine and, like the intravascularly introduced particles, will exert an effect on T2 of the organ or tissue. In this manner, cancers and other debilitating diseases of the digestive system such as ulcers can be diagnosed and affecte areas pinpointed.
Regardless of the route, once administered, the particles distribute to and collect rapidly in the target organs, generally in 30-minutes to an hour.
In the organ, these superparamagnetic particles will alter the magnetic fields produced by the MR i ager. These altered fields will exert an effect on the magnetic properties of the hydrogen nuclei (protons) in neighboring molecules; notably affected is the spin-spin relaxation time T_,. This parameter is shortened which can result in image darkening. Thus, the contrast is enhanced between areas which absorb the particles rapidly and those which absorb them slowly or not at all.
The particles are, however, ultimately biodegrade- able and the iron can be utilized by the body for physio¬ logical requirements. The contrast effect will vary with th dose, being longer at higher doses, and also with the organ imaged. Particularly in the liver and spleen (which store iron for physiological use) the effect can be observed for 1 days or more, (see Section 7.6), and, often, as long as 30 days.
The localization in these organs, which store iron for ultimate incorporation into hemoglobin, reveals that the iron oxide particles will ultimately serve as a source of metabolizable iron and, in fact, will be incorporated in the subjects hemoglobin. Thus, these materials can also be useful in the treatment of anemia.
The differences in parameter values are interprete by computer and used to generate an image of the organ in question. In the cases, as mentioned above, where uptake occurs by phagocytic processes (notably the liver, spleen, lymph nodes, and bone and neural tissue and to some extent, lung) such an image will clearly and distinctly differentiat between cancerous and healthy tissue, allowing for tumor location. In other organs and/or in the diagnosis of other diseases, modifications of the coating of these particles b the attachment of various functional groups will stimulate uptake by the organ or cell of choice. For example antibod ies to a particular tumor cell (e.g. lung carcinoma) can be attached to the surface of a coated particle, stimulating uptake by that organ if such a cell is present. In this way the method can serve a diagnostic tool for many diseases.
6.3. PREPARATION OF SUPERPARAMAGNETIC FLUIDS
The superparamagnetic fluids useful as imaging agents in this invention are preferably prepared in a three step process which comprises the steps of: formation of a superparamagnetic metal oxide; oxidation and dispersion of this oxide by sonication; and dialysis in buffer. This process yields stable biodegradable superparamagnetic metal oxides that owe their stability primarily to their anion retaining properties. The metal oxides may be uncoated or attached to organic coatings. Each of these steps is discussed separately below.
6.3.1. FORMATION OF SUPERPARAMAGNETC METAL OXIDE
Formation of the superparamagnetic metal oxide is accomplished by mixing the appropriate metal salts with a base. In a preferred embodiment, this is accomplished by mixing an aqueous solution or suspension of divalent and trivalent iron salts (FeCl2/FeCl_) with a base such as sodiu hydroxide (NaOH) . In addition, metals similar in structure t iron, such as Co and Mn, can be incorporated into the ultima superparamagnetic fluid by replacing a portion, preferably 1 or less, of the divalent iron salt with a divalent salt of that metal. The result is then a mixed metal oxide precipta containing both ferrous and ferric oxides, as well as oxides of the divalent metal. When iron salts are used the ratio of Fe3+/Fe2+ ca be varied from 1/4 to 4/1 and still produce usable product.
Thus, a wide range of salt mixtures can be utilized.
Once the salts are mixed with the base, a superparamagnetic metal oxide precipitate is formed. The us of a high concentration of reactants and an abrupt change in pH favors the formation of small superparamagnetic metal oxides. Such oxides are preferred for use in the subsequent steps of this process.
6.3.2. DISPERSION AND OXIDATION
In the second process step, the superparamagnetic metal oxide prepared in 6.3.1. is dispersed and oxidized further by sonication. The sonication, which can be conduct at ambient or elevated temperatures (up to 100 * C) serves a dual purpose: it serves to disperse any clusters of superparamagnetic particles (which increases the ultimate effects of the material on proton relaxation and, hence, enhances their effectiveness as MR contract agents) and, additionally, it serves to oxidize most, if not all, of fer- rous oxide (Fe 2+) to ferri.c oxi.de (Fe3+) . The resultant material, remarkably, is a soluble superparamagnetic iron oxyhydroxide which forms a superparamagnetic fluid.
The sonication can be accomplished in any commerci apparatus including in a continuous flow sonicator or by a sonic probe. The former is especially useful when large Q volumes of materials are being handled and, for a continuous process, can be coupled with a heating and cooling apparatus to permit heating of the iron oxide prior to or after
3 sonication (to increase the dispersion and oxidation of the oxides) and subsequent cooling of the sonicated mixture to facilitate collection.
6.3.3. DIALYSIS
The final step in the process is the transfer of t solution to an aqueous polycarboxylic buffer suitable for in vivo use. This transfer is accomplished by dialyzing the fluid against the buffer at neutral pH, generally at a pH of 6-9, preferably 6-8.3. These conditions result in a stable superparamagnetic fluid; under acidic conditions (below a pH of about 6) a significant amount of a chelate of the iron begins to form rather than the superparamagnetic iron oxide.
In the process, the fluid from 6.3.2. is centri- fuged, to remove larger oxide aggregates, and the supernatan is dialyzed against the buffer. The preferred buffer contai a citrate salt, because of its suitability for _in vivo use a its long history as an injectable agent, but in general buffers containing salts of any polycarboxylic acid, (such a tartrate, succinate) or maleate, allow for the formation of stable superparamagnetic fluids. The resultant fluids can then be autoclaved and stored until needed.
6.3.4. PREPARATION OF STABLE SUPERPARAMAGNET FLUIDS CONTAINING METAL OXIDES WITH ORGANIC COATINGS
Superparamagnetic fluids containing metal oxides t which organic coatings are attached can be prepared by modifications of the above procedure. Such organic coatings can be selected from a wide array of polymeric materials including, but not limited to, carbohydrates such as dextran (preferably having a molecular weight between 5,000 and 250,000 daltons), proteins (preferably having a molecular weight between 5,000 and 250,000 daltons) such as bovine or human serum albumen, polypeptides (preferably having molecul weights between 5,000 and 250,000 daltons) such as polylysin and polyglutamates and organosilanes (preferably having a molecular weight between 5,000 and 250,000 daltons) such as N-2-aminoethyl-3-aminopropyltrimethoxysilane. Briefly, the attachment can be accomplished during either the first or th second steps.
When attachment is accomplished during the first step, the coating material is mixed with the salt solution prior to the supermagnetic metal oxide precipitation. The coating material is attached to the resultant precipitate, a remains attached during the subsequent steps. Any unbound coating agent is removed during dialysis (step 3). In a preferred embodiment, superparamagnetic fluids containing dextran-coated iron oxides can be formed in this manner.
The attachment can also occur during the dispersio and oxidation second step by adding the coating agent prior the sonication and subsequently sonicating the mixture to fo the corresponding oxyhydroxide. Again, the unbound coating agents are removed by dialysis.
Superparamagnetic fluids containing silanized iron oxides are prepared in a similar manner. Initially, the iro oxides are subjected to sonication to form the oxyhydroxides The organosilane is then added and the mixture is sonicated disperse the materials. Finally, the silane is attached to the surface via a dehydration reaction. The polymerization the silane may occur before or after the deposition on the oxyhydroxide surface. In one embodiment, the silanization reaction occurs in two steps. First, a trimethoxysilane is placed in the sonicated mixture which condenses to form silane polymers:
Figure imgf000033_0001
The mixture is then sonicated, after which these polymers associate with the metal oxide, presumably by formin a covalent bond with surface OH groups through dehydration:
Figure imgf000033_0002
Adsorption of silane polymers to the metal oxide is also possible.
An important aspect of this procedure is the metho of dehydration used to effect the adsorptive or covalent binding of the silane polymer to the metal oxide. This association is accomplished by heating the silane polymer an metal oxide in the presence of a wetting agent miscible in both the organic solvent and water. Glycerol, with a boilin point of about 290°C, is a suitable wetting agent. Heating to about 105°C in the presence of glycerol serves two purpo- ses. It insures the evaporation of water, the organic solve (which may be e.g., methanol, ethanol, dioxane, acetone or other moderately polar solvents) and any excess silane mono¬ mer. Moreover, the presence of glycerol prevents the aggreg tion or clumping and potential cross linking, of particles that is an inherent problem of other silanization techniques known in the art wherein dehydration is brought about by heating to dryness. Thus, few aggregates are formed. Any formed aggregates are removed by centrifugation and the unbound silane is removed by hydrolysis.
6.3.5. ADVANTAGES OF THE SUPERPARAMAGNETIC FLUID PREPARATION PROCESS
The process used to prepare the superparamagnetic fluids of this invention is uniquely suited for preparing magnetic fluids suitable for ±n vivo use. Specifically, the following advantages are noted:
1. At no time is the material dried, nor is it precipitated after the intial formation of the superpara- magentic oxides. Such operations bring particles into close proximity with each other resulting in clustering and aggreg tion, which adversely affects their utility as MR contrast agents. Further, at no time are the metal oxides removed fr superparamagnetic fluid by precipitation or filtration; in fact, they cannot be so removed. In dilute concentrations, the metal oxides will pass through a 0.22 micron filter. 2. Because the material is never precipitated (after the initial formation of the iron oxide) , acids or bases are not needed to (resolubilize the iron oxide. Use o acids tends to dissolve iron oxides, yielding ferric ion whi is toxic and must be removed prior to _in vivo use. Strong bases are also poorly suited for use in the preparation of pharmaceutical solutions of superparamagnetic fluids. Stro bases can hydrolyze biological molecules attached to iron oxides such as proteins or polysaccharides. Amine-containi strong bases can react with polysaccharides in the well kno Malliard reaction.
3. Changes in solvents, such as to citrate buffe are accomplished by dialysis. Many other methods (such as that described in U.S. Patent 4,001,288) of iron oxide preparation require removal of iron oxides from solution to accomplish changes in solvent, often using acid or base to resolubilize the precipitate. * 4. The attachment of coating materials to the particles during the preparation permits a wide array of biologically active molecules such as antibodies, antigens, serum proteins or other materials to be attached. The attached biologically active molecule can serve to direct t superparamagnetic agent in vivo, as described in section 6.5
6.4. CHARACTERSTICS OF
SUPERPARAMAGNETIC FLUIDS
6.4.1. MAGNETIC PROPERTIES
The fluids produced by the methods described in section 6.3. are characterized by a high magnetic moment in high magnetic field (generally, about 5 to about 90 ΞMU/gm metal oxide) and a negligible magnetic moment in the absence of an applied field (i.e., a magnetic squareness of less than 0.1). Such behavior is characteristic of superparamagnetic particles.
FIG. 4 shows magnetic hysteresis loops for typica paramagnetic, superparamagnetic and ferromagnetic iron oxid Magnetization was measured in a vibrating sample magnetomet with fields up to 6,000 Gauss, 25"C. At high magnetic fiel the superparamagnetic fluid of the invention is nearly as magnetic as ferromagnetic iron oxide and far more magnetic than the paramagnetic ferric oxyhydroxide. Also, the solutions of the invention are superparamagnetic rather tha ferromagnetic, losing virtually all of their magnetic momen in the absence of an applied magnetic field. In fact, the superparamagnetic solutions of this invention are characterized by a saturation magnetization of 30 EMU/gm or greater, with the loss of more than 90% of this magnetism i the absence of a magnetic field.
6.4.2. RETENTION OF CITRATE AND
STABILITY OF SUPERPARAMAGNETIC FLUID
The retention of citrate (from aqueous sodium, potassium, or ammonium citrate buffer) can be used to distinguish the superparamagnetic fluids of this invention from other iron oxides. Studies of citrate binding capacit of commercially available forms of iron oxides and ferric oxyhydroxides reveals that the iron oxides in the superparamagnetic fluids of this invention are capable of retaining nearly as much citrate as the paramagnetic (ionic ferric oxyhydroxide, while gamma ferric oxide and magnetite cannot retain significant amounts of citrate. The inabilit of iron oxides to retain citrate, coupled with the ability ferric oxyhydroxide to do so, strongly suggest that citrate does not adsorb to the surfaces of iron oxides prepared according to the method of this invention (see Section 6.3) _ .
through the usual chemical adsorption mechanism. The retention of anions like citrate by the superparamagnetic iro oxides of the invention indicates these materials have an ionic character similar to the ferric oxyhydroxides.
The stability of fluids of the invention is shown i FIG. 5, where a superparamagnetic fluid made according to the procedure described in section 6.3. was subjected to autoclaving with and without citrate. Addition of 50 mM citrate stabilized a solution of 1.26 M iron oxide, preventin the gellation of the material.
The stability of the oxyhydroxide solutions of iron (i.e., the superparamagnetic fluids) is related to the exchange of hydroxide for citrate ion. Both paramagnetic and superparamagnetic oxides retain citrate in a similar fashion:
3 FeO:OH + Citrate3^—> (FeO) —Citrate + 3 OH~
Instead of trying to block the Van der Waals forces between neutral crystals with polymers, by attaching surfactants, or forming complexes, the general approach used by others in forming ferrofluids, the invention's superparamagnetic fluids are stabilized due to the ionic character of the iron oxide and the choice of appropriate anions.
The stable solutions' of this invention comprise a metal concentration ranging from 0.05 to 5 molar and a citra ion concentration of 0.001 to 0.1 moles of citrate/mole preferably 0.01 to 0.1 moles of citrate/mole of iron at a pH ranging from about 6 to about 10. As the concentration of iron in the solution is increased, the ratio of citrate/iro must also increase to yield the stability. Thus, they are compatible with physiological conditions.
The superparamagnetic fluids of the invention owe their stability in solution, not to their coating with polymers or surfactants, but to the existence of a cationic character of the iron oxide and its stabilization with anio such as citrate. In general, polymeric coatings, though th help stabilize iron oxides, are not sufficient to protect t against the rigors of autoclaving. In contrast, superparamagnetic fluids made according to the invention ca be made omitting the polymer altogether and are highly stab
6.4.3. EFFECTIVENESS AS MR CONTRAST AGENTS
In evaluating magnetic materials as MR contrast agents, the ability of materials to shorten proton relaxati time can be more important than bulk magnetic properties su as magnetization. Since MR imaging works by determining th •rates of two types of proton relaxations in various tissues and, by using variations in those relaxation rates, develop an image, the differences in proton relaxation times betwee the tissues must be sufficiently great to obtain a good quality image. As stated supra, MR contrast agents work by shortening proton relaxation time and, thus, increases the contrast and overall image quality. Two relaxation paramet termed spin-spin relaxation time (T.) and spin-lattice relaxation time (T2) are used in the generation of the MR image.
In experiments evaluating the effect of these materials as contrast agents, it was found that the superpa magnetic fluids have a much greater effect on both T. and T - -
than any commercially available iron compounds including chelated ferric ion, paramagnetic ferric oxyhydroxides, gamm ferric oxides, and superparamagnetic iron oxide clusters (Example 7.15). In fact, the material of the invention is remarkable in its ability to shorten proton relaxation. The materials prepared according to the invention are more poten enhancers of proton relaxation than either ferromagnetic materials or paramagnetic .ferric oxyhydroxide. In addition, the highly dispersed state of the materials of the invention produces higher relaxivities than those characteristic of clustered materials (See 7.12 and Table III). The process, thus, yields superparamagnetic solutions optimized for their effects on proton relaxation time.
The high relaxivity (see Table III) of the materia of the invention is important to their pharmaceutical use as MR contrast agents, because it results in large effects on t MR image with small doses of iron. For example, superparamag netic iron oxides made according to the invention can pro- foundly improve liver imaging at doses of 1 mg of iron per kilogram of rat, while the LD50 for the rat is greater that 250 mg of iron per kilogram.
6.5. BIODEGRADABILITY
Both the superparamagnetic particles in the dispersoids and the metal oxides in the superparamagnetic fluids of the invention have been found to be biodegradable when administered in vivo (see Examples 7.6 and 7.15). In fact, iron, the predominant species in the dispersoids and fluids accumulate in the liver, where it is eventually catabolized and incorporated into the subject's hemoglobin. Thus, the dispersoids and fluids can be used in the treatmen of anemia, and indeed, the fluids have been shown to be as effective as Imferon (a commercially used preparation for treatment of anemia in humans) in the restoration of normal hematocrit levels in anemic rats.
6.6. DIRECTABILTY
Both the superparamagnetic particles in the dispersoids and the metal-oxides in the superparamagnetic fluids of the invention can be coated with various coating agents as described supra. The use of such coatings permits the attachment of various biological molecules to the imagin agents to permit targeting of various organs. For example, antibodies can be bound by a variety of methods including diazotization and attachment through a glutaraldehyde or carbodiimide coupling moiety (Examples of these coupling methods can be found in U.S. Patent No. 4,628,037, which is incorporated herein by reference) . Use of methods such as these permits maximum flexibility, as an antibody-directed superparamagnetic metal oxide can bind to a specific type of cell or tissue. This can permit an image to be generated which differentiates between the target and the surrounding tissue.
In addition to antibodies, other biological molecules which affect directability can also be attached to the particles as the particular application dictates. Some possible applications are listed below:
Antibodies Application
1. Anti-heart myosin Imaging infarcted ar of heart
2. Anti-fibrin Image clot
3. Anti-T-cells Lymphoma
4. Anti-CEA Colonic tumor imagin 5. Anti-melanoma Melanoma imaging antibodies
6. Anti-ovarian Ovarian cancer imag cancer antibodies
7. IgG Fc receptor delineation
Carbohydrates
1. Bacterial lipopolysaccharides
10 2. Cellulose
3. Mucopolysaccharides . Starch
5. Modification of carbohydrate after synthesis, e.g., dextran coating made positively or
15 negatively charged, diethylamino (DEAE) cellulose or carboxymethyl (CM) dextran.
Hormones Application 1. Insulin Insulin receptor
20 status as in maturi onset diabetes
2. Thyroid stimulating Thyroid disease hormone
3. Acetylcholine Delineation of
25 (or analogs) neural receptors
4. Serum low density Delineation of ■lipoprotein familial hyper cholesterolemia
5. Hormone analogs Delineation of
30 including drugs endocrine system an receptors
6. Serum transferrin Transferrin recepto delineation
35 6.7 METHOD FOR EXTENDING THE SERUM
LIFETIME OF AN MR IMAGE CONTRAST AGENT
To extend the lifetime of an MR imaging agent in t serum of a subject, if desired, it is neccessary to prevent its absorption by the reticuloendothelial system (RES) . It has been found that this can be accomplished by introducing the subject a blocking agent which effectively competes with the imaging agent for binding the RES receptors responsible for removing the MR contrast agent from the bloodstream. There are a number of phagocytic receptors which function independently of each other. As a result, no single materia is equally effective at blocking all the RES receptors and a blocking agent must be specific for the imaging agent. (See Davis et al. in "Polymeric Nanoparticles and Microspheres", Gurot, P. and Covreur, P., eds, (CRC Press, 1986) p. 180).
In the procedure, the subject is given a dose of paramagnetic iron oxide either prior to or along with the administration of the imaging agent. For the best results, the paramagnetic iron oxide should be as simlar to the agent as practical especially in particle size and coating. After short time interval, generally 15-20 minutes during which ti the paramagnetic material circulates in the bloodstream and binds to the RES receptors, the imaging agent is administere By proper choice of the paramagnetic dosage, the lifetime of the imaging agent in the serum is greatly enhanced.
An excellent blocking agent for a superparmagneti MR agent is a paramagnetic form of the same material. This because the effectiveness of a blocking agent depends on whether a competition for receptors results; cell surface receptors bind materials in circulation prior to internalization. This internalization is termed pinocytosi -4 , ,1-
(removal of liquids) or phagocytosis (removal of particles) . If competition is created, which blocks removal of the superparamagnetic MR contrast agent, the removal of the contrast agent will be hindered. Because the RES receptors are specific and will bind substances of only one particular size or shape, this competition is best observed among materials which are physically similar. Since a paramagneti particle can differ from a superparamagnetic particle only i its core magnetic properties and rather than its surface chemistry, a high degree of competition is inevitable and, thus, the paramagnetic material is a highly efficient blocki agent.
In a preferred embodiment, dextran-coated paramagnetic iron oxide is used as a blocking agent for dextran coated superparamagnetic iron oxide. This material ideal as a blocking agent for dextran-coated superparmagneti iron oxide contrast agents for the reasons below:
1. It is virtually undectectable by MR.
2. It can be made by the process used for super¬ paramagnetic materials, but without the use of divalent iron (which is required for the superparamagnetic product) . The contrast agent and blocking agent are identical except for t fine structure of the iron oxide which determines magnetism and detectability by MR. From the point of view of the cell surface receptor governing removal from circulation the superparmagnetic imaging agent and blocking agent are identical. 3. It is non-toxic in humans and has an established therapeutic use in the treatment of anemia. In fact, therapeutically approved paramagnetic dextran (Imferon) can used as a blocking agent for the superparmagnetic MR contras agents of the invention.
The extension of serum lifetime is of particular importance when MR measurements are used to confirm blood circulation (or lack thereof) . In such measurements, the contrast agent is introduced parenterally and permitted to circulate. By measurement of T and T_, presence or absence of blood circulation can be determined. Such a procedure ca be a valuable tool in the diagnosis of blood circulation disorders, and can be used to detect the flow of blood into areas where it is normally excluded, such as in strokes.
7. EXAMPLES
7-1. PREPARATION OF DEXTRAN-COATED PARTICLES
To a solution of 500 mis of 0.28M FeC13, 0.16M FeC and 12.5% w/v dextran, (molecular weight 71,000 daltons from Sigma Chemical Company, Cat. #D1390) is added 500 mis 7.5% NH40H over a 2 minute period. A black, magnetic solid forms comprised of large and small particles. The material is stirred for 5 minutes and then heated for 30 minutes at 70"C. The solution is centrifuged for 1500 x g for 15 minut to remove large particles, and the small particles are dialyzed against 10 gallons of H20 for three days, changing the water each day.
The resultant p_articles exhibit a diameter of abou 1400 angstroms as measured by light scattering. 7.2. Preparation of Particles Coated with Bovine Serum Albumin
To a solution of 80 mis of 0.5% bovine serum albumi (BSA) , 0.27M FeCl3, and 0.16M eCl2, is added 80 mis of 7.5% NH.OH. A black, magnetic solid forms comprised of particles. The mixture is allowed to stand for 5 minutes and then centrifuged at 1,500 x g for 15 minutes to remove larger particles. The pellet is discarded and the supernatant place in a dialysis bag and dialyzed against 3 changes of 10 gallon of distilled water. Larger particles are again removed by centrifugation as above and discarded. Particles are then concentrated by ultrafiltration using an XM-50 membrane and a stirred cell filtration device from Amicon Corporation, Lexington, MA.
The resultant particles exhibit a diameter of about 1730 angstroms as measured by light scattering.
7.3. PREPARATION OF UNCOATED PARTICLES
One hundred milliliters of solution of 0.8M FeCl_, 0.4M FeCl2 and 0.4M HCl is added dropwise to 1000 ml of 2.4% NH OH and mixed for 5 minutes. A black, magnetic solid forms comprised of easily visible particles. For particles to be visible, they must be larger than the wavelength of scattered light which is about 500 nm (0.5 microns). The particles are isolated by attracting them to a permanent magnet on the outside of the reaction vessel and the solution decanted. To the magnetic cake is added 55 mis of 50% triethylamine in water. Smaller particles are created. The mixture is dialyzed overnight against water which causes the large particles to reappear. Just enough triethylamine is then added to again create the smaller particles resulting from t addition of triethylamine. The particles are then filtered through a 0.2 micron filter indicating the final material is below this size.
7.4. USE OF PARTICLES
IN LIVER TUMOR VISUALIZATION
The effect of the dextran-coated particles of Section 7.1. on the image of a rat liver tumor is demonstrat in FIG. 2, which presents reproductions of five images obtained on a Technicare MR imager. The images in FIGS. 2A and 2B were obtained prior to the introduction of the imagin agent using different imager settings, in neither case can t tumor be clearly seen; FIGS. 2C and 2D are images of the sam rat liver and were obtained after a single 0.5mg/kg dose of the Section 6.1. dextran-coated particle by intravenous injection through the tail vein, the tumor is easily seen a the overall size and shape can be gauged; in FIG..2E the tu is marked by cross-hairs to aid in visualization.
7.5. COMPARATIVE EFFECT OF SUPERPARAMAGNETIC
PARTICLES AND FERROMAGNETIC PARTICLES ON T2
FIG. 1 compares the T- of agar gel in the presenc of dextran-coated particles (produced in Example 7.1.) and ferromagnetic particle Pf-2228 (Pfizer) . The relaxation ti in the presence of varying concentrations of each particle were determined on an IBM PC-20 NMR spectrometer at 0.47 Te (4700 Gauss) . It can clearly be seen that the superparamagnetic particle produces a much greater effect o T2 than the ferromagnetic particle. Given the fact that superparamagnetic materials are much less magnetic than ferromagnetic materials, this result is quite surprising. 7.6. BIODEGRADABILITY OF DEXTRAN-COATED PARTICLES
A dispersion of uncoated superparamagnetic iron oxide particles in water was intravenously injected into Sprague-Dawley rats at a dosages 20, 37 and 243 micromoles
Fe/kg of body weight. Periodically, the rats were sacrificed, and T2 of the liver tissue was measured on an IBM PC-20 NMR Spectrometer. The results are presented in FIG. 3.
The data demonstrate that T_ undergoes a marked drop rapidly after the injection, and then begins to recover slowly, presumably as the iron is metabolized. However, the effects are still detectable even two weeks after administration. Also, the effects are more marked with the higher dosages. Thus the particles have an extended lifetime in these organs. Since the liver and spleen are the major organs which store iron for incorporation into hemoglobin, it is postulated that these materials are incorporated into the hemoglobin of the rat.
7.7. BIODISTRIBUTION OF BSA-COATED PARTICLES
Six Sprague-Dawley rats of about 200 gm each were injected intravenously with 0.4 mg of the BSA-coated particle (produced in Section 7.2.) in distilled water. Two rats each were sacrificed at 90 minutes, 24 hours, and 7 days after injection and the relaxation times (T- and T_ of various organs were measured on an IBM PC-20 NMR Spectrometer. The following results were obtained: TABLE I
DISTRIBUTION OF BSA-COATED PARTICLE IN RAT ORGANS AND TISSUE
Time After Relaxation Times (msec) Injection Liver Spleen Lung Blood
Control 0.279 0.544 0.688 0.786 N1 ^ 6 32 48.3 57 158
0.232 0.396 20 22
0.279 0.494 22 44
0.268 0.572
Figure imgf000048_0001
31 49
Figure imgf000048_0002
N is the number of rats examined.
The data suggest that both the blood and the lung rapidly clear the magnetic material exhibiting nearly no ef on the relaxation times 90 minutes after the injection. Th spleen demonstrates a moderately rapid recovery, exhibiting substantial reduction in both T. and T 90 minutes after th injection, but nearly no residual effect after 24 hours. T liver exhibits two different recovery rates. T- attains it original value after 24 hours, while T2 remains substantial reduced after 24 hours and exhibits recovery after 7 days. 7 . 8 . COMPARATIVE BIODISTRIBUTION OF
UNCOATED AND DEXTRANIZED PARTICLES
In this experimental series, the biodistribution of three uncoated and four dextran-coated particles was examined The uncoated agents were produced according to the procedure Section 7.3., the dextran-coated particles were produced according to the procedure of Section 7.1. except that the molecular weight of the dextran used for the coating was vari (see TABLE II) . Prior to each experiment, the contrast agent were dialyzed against distilled water and subsequently inject into separate groups of Sprague-Dawley rats in a distilled wa carrier. The rats were periodically sacrificed and the relaxation times of the liver, spleen, and lung were determi on an IBM PC-20 NMR Spectrometer. Preprogrammed inversion recovery and Carr, Purcell, Meiboom, Gill pulse sequences we used to determine T. and T2, respectively.
The results were as follows:
Complex Coating Dose
Control None
AMI-12 None 24.2 jx.moles/
Figure imgf000049_0001
kg Relaxation Times
Figure imgf000050_0001
Relaxation Times
Figure imgf000051_0001
Relaxation Times
Figure imgf000052_0001
As before, the data suggest that the contrast agen are rapidly cleared from the lung, and are longer lived in t spleen and the liver. Additionally, it can be seen that the dextran-coated particles are cleared less rapidly than the uncoated ones, exerting a significant effect on the T value of the liver and spleen for about one week.
7.9. PREPARATION OF SUPERPARAMAGNETIC FLUIDS CONTAINING UNCOATED METAL OXIDE
7.9.1 PREPARATION OF SUPERPARAMAGNETIC IRON OXIDE
A solution of 0.25 M ferrous chloride and 0.5M ferric chloride (600 ml) was poured into a solution of 5 M NaOH (600 ml) . A black magnetic oxide precipatate was forme This precipitate was washed repeatedly by base and decanted until a pH of about 9 was achieved.
7.9.2 DISPERSON AND OXIDATION
In a beaker, 400 ml of magnetic oxide (about 15 grams) from Section 7.9.1 and 25 ml of glacial acetic acid were mixed. A sonic probe was placed in the beaker and the solution was sonicated at high intensity for 2 minutes. The sonic probe was then remove and the solution centrifuged at 1,000 X g for 20 minutes. The pellet was discarded and the supernatant liquid was retained.
7.9.3 TRANSFER TO CITRATE BUFFER
The supernatant, from Section 7.9.2, was dialyzed against ammonium citrate buffer by use of a hollow fiber dialyzer/concentrator, model DC 2 (AMICON Corp. Danvers, MA) The ammonium citrate buffer is 10 mM citrate, adjusted to pH 8.2 with NH OH. The result is an autoclavable, homogeneous supermagnetic fluid.
7.10. PREPARATION OF AN AQUEOUS, STABLE SUPERPARAMAGNETIC FLUID CONTAINING METAL OXIDE WITH DEXTRAN ATTACHED
7.10.1 SYNTHESIS OF IRON OXIDE
Five liters of a solution containing 755 g FeCl3 6H20 and 320 g eCl2 4H20 was added slowly to liters of 16% NH.OH containing 2500 gm dextran (MW=10-15,00 The iron salt solution was added over 5 minutes during whic time the base was vigorously stirred during addition.
A black magnetic slurry was formed.
7.10.2. DISPERSION, OXIDATION AND HEATING
The 10 liters of slurry (from Section 7.10.1) was pumped through a continuous flow sonicator connected to a 100'C heating coil and cooling coil apparatus as indicated FIG. 6. The pumping rate was about 0.4 liters per minute a pumping was continued for about 30 minutes. The resultant solution was subsequently centrifuged and the precipitated pellet was discarded. 7.10.3. REMOVAL OF UNREACTED DEXTRAN, TRANSFER TO CITRATE BUFFER AND STERILIZATION
The supernatant (from Section 7.10.3) was diluted t a total volume of 20 liters with deionized, sterile water and the resultant solution was dialyzed as in Example 7.9, except that a larger dialyzer concentrator, the DC 10, was used. Th dialyzer cartridge had a 100,000 dalton molecular weight cutoff, permitting removal of dextran. Ultrafiltration was accomplished in a noncontinuous fashion, reducing the volume from 20 to 5 liters and adding 16 liter volumes of solution. Five volumes of 16 liters of deionized, distilled water were added.
Sodium citrate was then added as 1M citrate buffer stock and the solution was dialyzed as in Example 7.9. The resultant citrate was adjusted to pH 6.5 with NaOH before autoclaving. The citrate to iron ratio was between 0.01 and 0.1 citrate/Fe in the final solution. (For example, for an iron concentration of 1.26M, 0.04 M citrate was present. The magnetic fluid was bottled and autoclaved (121"C, 30 minutes) The result is a sterile homogenous magnetic fluid as shown i FIG. 5.
7.11. PREPARATION OF AN AQUEOUS STABLE SUPERPARAMAGNETIC FLUID CONTAINING METAL
OXIDE WITH SILANE ATTACHED
7.11.1. PREPARATION OF IRON OXIDE
A solution of 0.25 M ferrous chloride and 0.5M ferric chloride (600 ml) was poured into a solution of 5 M NaOH (600 ml) . A black magnetic oxide precipitate formed which was repeatedly washed by base and decanted until a pH about 9 was achieved. 7.11.2. DISPERSION, OXIDATION AND SILANIZATION
In a beaker 400 ml of magnetic oxide (from Section 7.11.1., about 15 grams) and 25 ml of glacial acetic acid we 5 mixed. A sonic probe was placed in the beaker and the solu¬ tion was sonicated at high intensity for 2 minutes. The son probe was then removed and 30 ml of N-2-aminoethyl-3-amino- propyltri ethoxysilane was added. The resultant mixture was then sonicated as before. The magnetic solution was *~ subsequently added to 200 ml of glycerol at 50"C. The temperature was raised to 105°C and the water was evaporated
Due to the use of sonication, the material made in Example 3 is far smaller than that described in United State 15 Patent No. 4,554,088. Due to its small size, it cannot be manipulated with hand held magnets. The glycerol dehydrati step is from US Patent 4,554,088 herein incorporated by reference..
20 7.11.3. REMOVAL OF UNREACTED SILANE AND TRANSFER CITRATE BUFFER
The glycerol slurry, from Section 7.11.2, was add to about 800 ml of water. Large aggregates of magnetic particles were removed by centrifuging the slurry at 1,000
25 for 20 minutes. The supernatant was then dialyzed against citrate buffer in a hollow fiber dialysis device as in Exam 6.9.
35 7.12. EFFECT OF THE SUPERPARAMAGNETIC FLUID ON PROTON RELAXATION TIME
The effects of materials on an n vivo MR image can be evaluated through the use of a magnetic resonance spectrometer. In this study, an IBM-PC 20 instrument which measures T. and T2 at 25βC, 0.47 Tesla and 20 MHz was used. Enhancement of proton relaxation can be quantified by taking the slope of a plot of 1/T, the reciprocal of the relaxation time, versus the concentration of contrast agent. The plot i generally linear, with the slope being termed the relaxivity and denoted Rl or R2. Relaxivity has units of M —1 sec—1
Higher relaxivity values indicate that material is more poten per mole of iron at decreasing relaxation times of protons and, thus, is a more potent contrast again. Relaxivities for a number of different forms of magnetic materials were determined. The following materials were examined:
Superparamagnetic fluid of the invention: A dispersed fluid containing single superparamagnetic crystals of iron oxide prepared as described in Example 7.10. The magnetization curve of this material is presented in FIG. 4.
Fe 0.: A ferromagnetic gamma ferric oxide used for data recording. This material was obtained from Pfizer Corp. Minerals, Pigments and Metals Division, catalogue #2228.
Cluster: A silanized cluster of superparamagnetic iron oxide with tens to hundreds of crystals packed into micron-sized particles. This material was made according to U.S. Patent No. 4,554,088. FeO:OH: a paramagnetic, ferric oxyhydroxide used the treatment of anemia. It was obtained from Fisons Corporation and is sold under the trade names of Proferdex (Fisons corporation) or Imferon (Merrill Dow Inc.)
Fe 3+/DTPA: a soluble complex of ferric ion and diethylenetriaminepentaaσetic acid (DTPA) . (The data for th material is from Lauffer ύt al, J. Comp. Assist. Tomog. 9(3) 431 (1985)).
The results were as follows:
TABLE III
EFFECT OF DIFFERENT FORMS OF IRON ON PROTON RELAXATION TIM
Material Rl R2
(M_1 X sec"1) (M"1 X sec"1)
superparamagnetic fluid 4 X 10+4
gamma e203 100
Fe0:0H
Cluster 2 X 10+3
Fe3+/DTPA 0.73 X 10+3
Figure imgf000058_0001
Briefly, as the high values of Rl and R2 indicate, the material of the invention is remarkable in its ability shorten proton relaxation times. For comparison, the value +4 —1 R2 for ferromagnetic dextran magnetite is 1.7 X 10 M sec
[Ohgushi et al., J. Mag Res. 2_9, 599 (1978)]. This is the highest literature value for R2 of which the authors are aware. The materials prepared according to the invention ar more potent enhancers of proton relaxation time than either ferromagnetic materials or paramagnetic ferric oxyhydroxides.
Additionally, well dispersed materials, such as those of the invention, have higher relaxivities than clustered materials. Thus, the process of the invention yields superparamagnetic solutions optimized for their effec on proton relaxation.
7.13. BULK MAGNETIC PROPERTIES OF SUPERPARAMAGNETIC FLUIDS
Magnetic hysteresis loops were obtained for the samples of the invention superparamagnetic fluid, gamma Fe_0 (ferromagnetic) , and FeO:OH (paramagnetic) examined in Examp 7.12, using a commercial vibrating sample magnetometer with fields up to 6000 Gauss, 25"C. The results are presented in FIG. 4.
Briefly, at high magnetic fields, the superparamagnetic fluid of the invention is nearly as magnet as ferromagnetic iron oxide and far more magnetic than the paramagnetic ferric oxyhydroxide, showing a high magnetic saturation. The fluids of the invention are superparamagnet rather than ferromagnetic, losing virtually all of their magnetic moment in the absence of an applied magnetic field.
7.14. RETENTION OF CITRATE
The retention of 14C citrate upon dialysis can be used to distinguish various forms of iron oxide as shown in
Table IV. All iron oxides were initially dialyzed against a
s-.. buffer of 1 mM Tris-Cl, pH 8 before use. Equilibrium dialys was then performed to determine fraction of citrate retained. The concentrations of iron and citrate were 17.8 and 2.6 mM, respectively. The superparamagnetic fluids of the invention retain amounts of citrate similar to commercially available ferric oxyhydroxides indicating that the iron in both preparations is in a similar chemical form. Commercially available forms of iron oxide, such as gamma Fe 0. or Fe O , do not retain significant amounts of citrate (the gamma Fe 0 was the same as that used in Examples 7.12 and 7.13 while th Fe_0. was purchased from Fisher Scientific Ine) . The inability of these commercially available iron oxides to retain citrate, coupled with the ability of ferric oxyhydroxide to do so, strongly suggests that citrate does n absorb to iron oxide surfaces through the usual chemical adsorption mechanism. The retention of citrate by the superparamagnetic iron oxides of the invention indicates the materials have an ionic character similar to the ferric oxyhydroxides.
' TABLE IV
RETENTION OF CITRATE BY SOLUTIONS WITH DIFFERENT IRON OXIDES
Material Citrate Retained per Iron
(mole/mole) FeO:OH " 0.026
Invention 0.019
gamma Fe O. 0.0028
Fe3°4 0.0018
7.15. STABILITY OF SUPERPARAMAGNETIC FLUIDS
Superparamagnetic fluids made according to example 7.9 were subjected to autoclaving with various concentration of citrate. At iron concentration of 1.26M, various concentrations of ammonium citrate, pH8 were added, and the resulting solutions heated 1 hour at 121°C. The results are presented in FIG. 5. The 6 vials of Fig. 5B contained, as shown, citrate concentrations of 100, 50, 25, 15, 10 and 5 m citrate, respectively. The vials were upright during autoclaving but were placed horizontally for the photograph. With the-vials lying horizontally, the presence of gelled material is evident when the upper portion of the vial is translucent. The fully blackenend vials (citrate concentrations between 15 and 100 mM) indicate a solution of superparamagnetic materials was maintained. The two vials o the right (citrate concentration of 5 and lOmM) show the formation of a gel. FIG. 5A further shows the characterist gel obtained without citrate, or with inadequate citrate (5 and 10 mM citrate) .
7.16. BIODEGRADABILITY OF SUPERPARAMAGNETIC FLUI
Paramagnetic ferric oxyhydroxides are biodegradab and have long been used for the treatment of anemia. Therefore, the biodegradability of the invention's superparamagnetic fluids was compared with the paramagnetic ferric oxyhydroxides. The ability of both iron preparation to reverse anemia in rats was utilized as a model. The paramagnetic ferric oxyhydroxide was Imferon, and has dextr attached. The supermagnetic fluid also had dextran attache and was produced as described in Example 7.10.
Weanling rats were divided into four groups of fi rats each. Rats in group 1 received a chow containing iron and were sacrificed at weeks 5, 6, 7 and 8 to allow establishment of normal iron (hematocrit) levels in rat tissues. Rats in groups 2, 3 and 4 received an iron defici diet. Rats in group 2 were also sacrificed at weeks 5, 6, and 8 to allow establishment of normal iron levels in rat tissues. Rats in groups 2, 3 and 4 received an iron defici diet. After receiving the low iron diet for 5 weeks, rats groups 3 and 4 received intravenous (tail vein) injections iron to reverse their anemia and restore normal levels. R in group 3 received Proferdex, while those in group 4 recei the dextranized superparamagnetic fluid. Rats receiving i were injected with a single dose of 30 mg of iron per kilogram, a sufficient dose to reverse their anemia. The results are presented in Table V. TABLE V
REVERSAL OF ANEMIA WITH SUPERPARAMAGNETIC IRON OXIDE PARTICL
Hematocrit (1% red cells in whole blood) week 5 week 6 week 7 week 8 avg sd avg sd avq sd avg sd
Chow 45.1 1.4 45.2 0.5 46.7 0.9 47.0 0.8 low Fe 28.5 2.6 29.5 2.1 32.7 1.2 34.8 2.3
Imferon 43.1 1.9 42.8 1.3 46.3 1.2
Invention 44.3 2.3 42.7 1.1 47.6 1.6
It can be seen that the invention's super¬ paramagnetic iron oxide restores normal hematocrits levels i rats as well as the paramagnetic preparation, Imferon.
. 7.17. SUMMARY OF SUPERPARAMAGNETIC FLUID PROPERTIES
The properties of the superparamagnetic fluids of the invention compared with solutions made with other types ferric oxide are summarized TABLE VI:
TABLE VI
SUMMARY OF PROPERTIES OF AQUEOUS SOLUTIONS OF VARIOUS FERRIC OXIDES
Figure imgf000064_0001
Thus, the superparamagnetic fluids of this invent posess a unique combination of magnetic, biological and ani retaining properties.
7.18. EXTENSION OF THE SERUM LIFETIME OF DEXTRAN
COATED SUPERPARAMAGNETIC IRON OXIDE PARTIC
To assess the effectiveness of dextran-coated paramagnetic iron oxide as a serum lifetime extender for dextran-coated superparamagnetic iron oxide particles, a comparative study was conducted.
In both trials, a rat of about 300 g was injected with 1 mg Fe/kg body weight of dextran-coated superpara¬ magnetic metal oxide produced as described in Example 7.1. However, in one trial, the rat was also injected with 2.5 m Fe/kg dextran-coated paramagnetic iron oxide (produced following the procedure described in example 7.1 except tha no divalent salt was used) 15 minutes prior to receiving th superparamagnetic material. The T_ of the subject's blood measured periodically over the subsequent 3 hours. The results are present in Figure 7. Briefly, in both trials, the blood 2 dropped dramatically within 5 minutes after the superparamagnetic material was added. However, the value rapidly returned to normal in the rat which did not receive the superparamagneti material, presumably due to absorption of the agent by the reliculoendothelial system (RES) . In contrast, when the paramagnetic agent was used the T2 depression is dramaticall extended. This is due to-a competition between the superparamagnetic and the paramagnetic material for RES receptors, greatly expanding the lifetime of the superparamagnetic agent.
It is apparent that many modifications and variations of this invention as hereinabove set forth may b made without departing from the spirit and scope thereof. specific embodiments described are given by way of example only and the invention is limited only by the terms of the appended claims.

Claims

WHAT IS CLAIMED IS:
1. An improved method for obtaining an in vivo M image of an organ or tissue of an animal or human subject,
5 wherein the improvement comprises administering to such a subject as a contrast agent to enhance such MR image an effective amount of a dispersoid which comprises uncoated biodegradable superparamagnetic metal oxide particles dispersed in a physiologically acceptable carrier, an 0 individual particle (i) comprising metal oxide crystals of about 50 to about 500 angstroms in diameter; (ii) having an overall mean diameter of about 50 angstroms to about 5000 angstroms as measured by light scattering; and (iii) further characterized as having a retention time in said organ or
5 tissue sufficiently long to permit an image to be obtained a being biodegradable.
2. An improved method for obtaining an in vivo M image of an organ or tissue of an animal or human subject, 0 wherein the improvement comprises administering to such a subject as a contrast agent to enhance such MR image an effective amount of a dispersoid which comprises coated biodegradable superparamagnetic metal oxide particles dispersed in a physiologically acceptable carrier, said particles consisting of superparamagnetic metal oxide cores, each core generally surrounded by a polymeric coat, an individual particle (i) comprising metal oxide crystals of about 50 to about 500 angstroms in diameter; (ii) having an overall mean diameter of about 50 angstroms to about 5000
30 angstroms as measured by light scattering; and (iii) further characterized as having a retention time in said organ or tissue sufficiently long to permit an image to be obtained a being biodegradable.
35
3. The method of claim 1 or 2 wherein the superparamagetic metal oxide particle is an iron oxide particle (i) comprising crystals of about 50 to about 500 angstroms in diameter; (ii) having a surface area greater tha 2 about 75m /gram; (iii) having a magnetic saturation between about 5 and about 90 EMU/gram of iron oxide; and (iv) possessing a magnetic squareness of less than 0.1.
4. The method of claim 2 wherein the polymeric coat is selected from the group consisting of carbohydrates, proteins, and composites thereof.
5. The method of claim 2 wherein the polymeric coat consists of albumin.
6. The method of claim 5 wherein the albumin is selected from the group consisting of human serum albumin an bovine serum albumin.
7. The method of claim 2 wherein the polymeric coat consists of dextran having a molecular weight between 5,000 and 250,000 daltons.
8. The method of claim 7 wherein the dextran is selected from the group consisting of dextran of 9,000 MW, dextran of 17,900 MW, dextran of 35,600 MW, dextran of 71,00 MW and dextran of 249,000 MW.
9. The method of claim 1 or 2 wherein said dispersoid is administered to the subject by intravascular injection.
10. The method of claim 1 or 2 wherein said dispersoid is administered to the subject by a method selecte from the group consisting of oral administration, intubation, and by enema.
11. The method of claim 9 wherein the physiologically acceptable carrier is selected from the group consisting of normal saline and distilled water.
12. The method of claim 10 wherein said physiologically acceptable carrier is distilled water.
13. The method of claim 1 or 2 wherein the superparamagnetic metal oxide particles are administered at dosage of up to about 250 mg per Kilogram of body weight of the subject.
14. The method of claim 1' or 2 wherein the organ tissue imaged is part of. the reticuloendothelial system.
15. The method of claim 14 wherein the organ imag is a liver.
16. The method of claim 14 wherein the organ imag 5 is a spleen.
17. The method of claim 14 wherein the tissue imaged is bone marrow.
Q 18. The method of claim 14 wherein the organ or tissue imaged is lymph or lymph nodes.
19. The method of claim 1 or 2 wherein the tissue imaged is neural tissue. 5
20. The method of claim 1 or 2 wherein the organ imaged is a lung.
21. The method of claim 1 or 2 wherein the organ o 5 tissue imaged is part of the gastrointestinal tract.
22. The method of claim 21 wherein the organ image is an esophagus.
"0 23. The method of claim 21 wherein the organ image is a stomach.
24. The method of claim 21 wherein the organ image is a small intestine.
15
25. The method of claim 21 wherein the organ image is a large intestine.
26. An improved method for obtaining an in vivo MR 20 image of an organ or tissue of an animal or human subject, wherein the improvement comprises administering to such a subject as a contrast agent to enhance such MR image an effective amount of a superparamagnetic fluid comprising superparamagnetic metal oxides in aqueous solution, said meta
25 oxides (i) having a magnetic saturation between about 5 and about 90 EMU/gm of metal oxide at approximately 300"K and a magnetic squareness of less than 0.1, characteristic of a superparamagnetic metal oxide crystal; (ii) being capable of retaining anions, in solution in a.manner characteristic of
30 paramagnetic metal oxides; (iii) having an overall mean diameter of about 50 to about 4000 angstroms as measured by light scattering; and (iv) further characterized as having a retention time in said organ or tissue sufficiently long to permit an image to be obtained and being biodegradable.
35 — 6S — 88/00060 PCT/ S87/01588
27. An improved method for obtaining an in vivo MR image of an organ or tissue of an animal or human subject, wherein the improvement comprises administering to such a subject as a contrast agent to enhance such MR image an effective amount of a superparamagnetic fluid comprising smal superparamagnetic metal oxides attached to a polymeric coati in aqueous solution, said metal oxides (i) having a magnetic saturation between about 5 and about 90 EMU/gm of metal oxid at approximately 300'K and a magnetic squareness of less tha 0.1 characteristic of super paramagnetic metal oxide crystal (ii) being capable of retaining anions in solution in a mann characteristic of paramagnetic metal oxides; (iii) having an overall mean diameter of about 50 to about 4000 angstroms as measured by light scattering; and (iv) further characterized as having a retention time in said organ or tissue sufficiently long to permit an image to be obtained and bein biodegradable.
28. The method of claims 26 or 27 wherein the superparamagnetic fluid comprises a superparamagnetic iron oxide in an aqueous polycarboxylic acid buffer further characterized by:
(i) an iron concentration ranging from 0.05 5 molar;
(ii) a polycarboxylate counterion concen¬ tration ranging from 0.001 to 0.1 moles of tricarboxylate pe mole of iron; and
(iii) a pH between about 6 and about 8.3 wherein the fluid is characterized by a saturation magnetization of between about 30 and about 90 EMU/g of iron oxide and a magnetic squareness of less than 0.1.
29. The method of claim 28 wherein the aqueous polycarboxylic acid buffer is selected from the group consisting of aqueous citrate buffer, aqueous tartrate buffe aqueous succinate buffer, and aqueous maleate buffer.
30. The method of claim 28 wherein the iron concentration is about 1.26 molar, the citrate concentration is about 0.04 molar, and -the pH is about 6.5.
31. The method of claim 27 wherein the polymeric coating is selected from the group consisting of carbohydrates, polypeptides, organosilanes, proteins, and composites thereof.
32. The method of claim 27 wherein the polymeric coating consists of dextran having a molecular weight betwee 5,000 and 250,000 daltons.
33. The method of claim 27 wherein the protein is
BSA.
34. The method of claim 27 wherein the polymeric coating is N-2-aminoethyl-3-arainopropyltrimethoxysilane.
35. The method of claim 26 or 27 wherein said superparamagnetic fluid is administered to the subject by intravascular injection.
36. The method of claim 26 or 27 wherein said superparamagnetic fluid is administered to the subject by a method selected from the group consisting of oral administration, intubation, and by enema.
37. The method of claim 26 or 27 wherein the or or tissue imaged is part of the reticuloendothelial system.
38. The method of claim 37 wherein the organ im 5 is a liver.
39. The method of claim 37 wherein the organ im is a spleen.
"0 40. The method of claim 37 wherein the tissue imaged is bone marrow.
41. The method of claim 37 wherein the organ or tissue imaged is lymph or lymph nodes.
15
42. The method of claim 26 or 27 wherein the ti imaged is neural tissue.
43. The method of claim 26 or 27 wherein the or 20 imaged is a lung.
44. The method of claim 26 or 27 wherein the or or tissue imaged is part of the gastrointestinal tract.
25 45. The method of claim 44 wherein the organ im is an esophagus.
46. The method of claim 44 wherein the organ im is a stomach.
30
47. The method of claim 44 wherein the organ im is a small intestine.
35
48. The method of claim 44 wherein the organ image is a large intestine.
49. The method of claim 2 or 27 in which the magnetic metal oxides further comprise an effective amount of biological molecules covalently coupled to said coating, said biological molecules possessing functional groups which are recognized by receptors in various organs and tissues of the subject, such that the particles are directed _in vivo to the organ or tissue which recognizes the attached biological molecule.
50. The method of claim 49 wherein the biological molecule is an antibody.
51. The method of claim 50 wherein the antibody i an anti-melanoma antibody and the tissue being imaged is melanoma tissue.
• 52. The method of claim 50 wherein the antibody i an anti-heart myosin antibody and the tissue being imaged is infarcted heart tissue.
53. The method of claim 50 wherein the antibody i an anti-T-cell antibody and the tissue being imaged is lymphoma tissue.
- 54. The method of claim 50 wherein the antibody i anti-carcinomic embryonic antigens and the tissue being imag is colonic tumor tissue.
..' 55. The method of claim 50 wherein the antibody i an anti-ovarian cancer cell antibody and the tissue being imaged is ovarian cancer tissue.
56. The method of claim 49 wherein the biological molecule is a carbohydrate.
57. The method of claim 49 wherein the biological 5 molecule is a hormone.
58. An autoclavable superparamagnetic fluid comprising a superparamagnetic iron oxide in an aqueous tricarboxyliσ acid buffer, further characterized by: 0 (i) an iron concentration ranging from 0.05 to 5 molar;
(ii) a polycarboxylate counterion concen¬ tration ranging from 0.001 to 0.1 moles of tricarboxylate per mole of iron? and
'5 (iii) a pH between about 6 and about 9 wherein the fluid is characterized by a saturation magnetization of between about 30 and about 90 EMU/g of iron oxide at approximately 300°K and a magnetic squareness of les than 0.1. 0
59. The superparamagnetic fluid of claim 58 wherei the aqueous polycarboxylic acid buffer is selected from the group consisting of aqueous citrate buffer, aqueous tartrate buffer, aqueous suσcinate buffer, and aqueous aleate buffer.
25
60. The superparamagnetic fluid of claim 59 wherei the aqueous citrate buffer is selected from the group consisting of sodium citrate buffer, potassium citrate buffer and ammonium citrate buffer.
30
61. The superparamagnetic fluid of claim 58 wherei the iron concentration is about 1.26 molar, the citrate concentration is about 0.04 molar, and the pH is about 8.0
35 W
62. The superparamagnetic fluid of claim 58 whic further comprises a polymeric coating attached to said iron oxide.
5 63. The superparamagnetic fluid of claim 62 wher the coating is a dextran having a molecular weight between and 250,000 daltons.
64. The superparamagnetic fluid of claim 62 wher 0 the coating is a protein having a molecular weight between
5,000 and 250,000 daltons.
65. The superparamagnetic fluid of claim 64 wher the protein is selected from the group consisting of bovine
15 serum albumin and human serum albumin.
66. The superparamagnetic fluid of claim 62 wher the coating is a polypeptide having a molecular weight betw 5,000 and 250,000 "daltons.
?0
67. The superparamagnetic fluid of claim 66 wher the polypeptide is polyglutamate.
68. The superparamagnetic fluid of claim 60 wher 25 the polypeptide is polylysine.
69. The superparamagnetic fluid of claim 63 wher the coating is a organosilane having a molecular weight between 5,000 and 250,000 daltons."
30
... ._ 70._ -The superparamagnetic fluid bf claim 69 wher the organosilane is N-2-aminoethyl-3-aminopropyltrimethoxy- silane.
35
71. A method for preparing stable superparamagne fluids comprising:
(i) forming a superparamagnetic metal oxide base precipitation of divalent and trivalent iron salts; (ii) dispersing and oxidizing said superpar magnetic metal oxide by sonication at a temperature between ambient or 100"C; and
(iii) transferring the soluble superpara¬ magnetic metal oxide to a tricarboxylic acid buffer by dialysis.
72. The method of claim 71 wherein the divalent trivalent iron salts are present in a ratio ranging from 1: to 4:1.
73. The method of claim 71 wherein the divalent trivalent iron salts are FeCl, and FeCl .
74. The m,ethod of claim 71 which further compris replacing a portion of the divalent iron salt with a divale salt of cobalt or manganese.
75. The method of claim 74 wherein the portion o divalent iron salt replaced is half or less.
76. The method of claim 71 wherein the sonicatio is accomplished by sonic probe.
77. The method of clam 71 wherein the sonication accomplished in a continuous flow sonicator.
78. The method of claim 71 wheren the tricarboxy acid buffer is a citrate buffer.
79. The method of clam 71 wherein the tricarboxyli acid buffer is a tartrate buffer.
80. A superparamagnetic metal oxyhydroxide comprising water soluble superparamagnetic metal oxides, said metal oxides (i) having a magnetic saturation between about 5 and about 90 EMU/g of metal oxide at approximately 300"K and a magnetic squareness of less thn 0.1, characteristic of a superparamagnetic metal oxide crystal; (ii) being capable of retaining anions wherein solution, characteristic of paramagnetic metal oxides in solution; (iii) having an overal mean diameter of about 50 to about 4000 angstroms as measured by light scattering; and (iv) and further characterized by being capable of forming solution in water at concentrations up to about 5 molar.
81. A superparamagnetic ferric oxyhydroxide comprising small water soluble superparamagnetic ferric oxides, said ferric oxides (i) having a magnetic saturation between about 5 and about 90 EMU/gm of ferric oxide at approximately .300" and a magnetic squareness of less than 0.1, characteristic of a superparamagnetic ferric oxide crystal; (ii) being capable of retaining anions solution, characteristic of paramagnetic ferric oxides in solution; (iii) having an overall mean diameter of about 50 to about 4000 angstroms as measured by light scattering; and (iv) and further characterized by being capable of forming solution in water at concentrations up to about 5 molar.
82: A method for extending the serum lifetime of superparamagnetic MR contrast agent in an animal or human subject comprising administering to said subject prior to, o simultaneously with, administering said contrast agent, an effective amount of a blocking agent in a physiologically acceptable carrier, said blocking agent being capable of competitively binding to reticuloendothelial system receptor which can remove the contrast agent from circulation.
83. The method of claim 82 wherein the blocking agent is a paramagnetic form of the contrast agent.
84. The method 'of claim 82 wherein the contrast agent is a superparamagnetic iron oxide and the blocking age is a paramagnetic form of the superparamagnetic iron oxide.
85. A method for detecting in vivo blood flow in animal or human subject comprising:
(i) administering to said subject an effecti amount of a dispersoid of a blocking agent in a physiolog¬ ically acceptable carrier said blocking agent being recogniz by RES receptors;
(ii) subsequently administering to said subject a dispersoid or solution of a superparamagnetic MR contrast agent in a physiologically-acceptable carrier said NMR contrast-agent competing for the same RES receptors as i
(i)
(iii) obtaining an MR image of the blood in a section of the sub~=ct; and
(iv) detecting the presence or absence of blood flow in the section.
86. The method of claim 85 wherein the blocking agent is a paramagnetic form of the superparamagnetic MR contrast agent.
87. The method of claim 85 wherein the superparamagentic MR contrast agent is a superparamagnetic iron oxide and the blocking agent is a paramagnetic form of the superparamagnetic iron oxide.
88. A method for reducing anemia in an animal or human subject comprising parenterally administering to said subject an effective amount of a dispersoid of the superparamagnetic iron oxides of claim 3.
89. A method for reducing anemia in an animal or human subject comprising parenterally administering to said subject an effective amount of the superparamagnetic fluid of claim 56.
PCT/US1987/001588 1986-07-03 1987-07-01 Biodegradable superparamagnetic materials used in clinical applications WO1988000060A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP87904772A EP0275285B1 (en) 1986-07-03 1987-07-01 Biodegradable superparamagnetic materials used in clinical applications
DE3751918T DE3751918T2 (en) 1986-07-03 1987-07-01 BIODEGRADABLE SUPER-PARAMAGNETIC MATERIAL FOR USE IN CLINICAL APPLICATIONS
NO880931A NO880931D0 (en) 1986-07-03 1988-03-02 BIODEGRADABLE SUPERPARAMAGNETIC MATERIALS FOR USE FOR CLINICAL APPLICATIONS.

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US06/882,044 US4770183A (en) 1986-07-03 1986-07-03 Biologically degradable superparamagnetic particles for use as nuclear magnetic resonance imaging agents
US882,044 1986-07-03
US067,586 1987-06-26
US07/067,586 US4827945A (en) 1986-07-03 1987-06-26 Biologically degradable superparamagnetic materials for use in clinical applications

Publications (1)

Publication Number Publication Date
WO1988000060A1 true WO1988000060A1 (en) 1988-01-14

Family

ID=26748043

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US1987/001588 WO1988000060A1 (en) 1986-07-03 1987-07-01 Biodegradable superparamagnetic materials used in clinical applications

Country Status (7)

Country Link
US (1) US4827945A (en)
EP (1) EP0275285B1 (en)
JP (1) JPH01500196A (en)
AT (1) ATE143604T1 (en)
CA (1) CA1301063C (en)
DE (1) DE3751918T2 (en)
WO (1) WO1988000060A1 (en)

Cited By (48)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1989003675A1 (en) * 1987-10-26 1989-05-05 Carbomatrix Ab Superparamagnetic particles, a way of producing said particles and their use
WO1989009625A1 (en) * 1988-04-08 1989-10-19 Cockbain, Julian, Roderick, Michaelson Contrast agents for magnetic resonance imaging
WO1989011873A1 (en) * 1988-06-03 1989-12-14 Nycomed As Magnetic particle-containing compositions
WO1989011874A1 (en) * 1988-06-07 1989-12-14 Laurence David Hall Magnetic resonance imaging
EP0361960A2 (en) * 1988-09-29 1990-04-04 RANNEY, David F. Methods and compositions for magnetic resonance imaging
EP0381742A1 (en) * 1988-08-04 1990-08-16 Advanced Magnetics Inc Receptor mediated endocytosis type mri contrast agents.
EP0441797A1 (en) * 1988-08-16 1991-08-21 Advanced Magnetics Inc Vascular magnetic imaging method and agent.
WO1991014457A1 (en) * 1990-03-24 1991-10-03 The Victoria University Of Manchester Method for the study of internal body tissues
WO1991015243A1 (en) * 1990-04-02 1991-10-17 Cockbain, Julian, Roderick, Michaelson Diagnostic agents
EP0474785A1 (en) * 1989-05-30 1992-03-18 Alliance Pharmaceutical Corporation Percutaneous lymphography
WO1992004916A2 (en) * 1990-09-14 1992-04-02 St. George's Enterprises Limited Particulate agents
EP0489119A1 (en) 1989-08-22 1992-06-10 Immunicon Corp Resuspendable coated magnetic particles and stable magnetic particle suspensions.
EP0502814A2 (en) * 1991-02-15 1992-09-09 BRACCO International B.V. Compositions for increasing the image contrast in imaging of the digestive tract of patients
WO1992022586A1 (en) 1991-06-11 1992-12-23 Meito Sangyo Kabushiki Kaisha Oxidized composite comprising water-soluble carboxypolysaccharide and magnetic iron oxide
US5190744A (en) * 1990-03-09 1993-03-02 Salutar Methods for detecting blood perfusion variations by magnetic resonance imaging
WO1993012717A2 (en) * 1992-01-03 1993-07-08 Cockbain, Julian, Roderick, Michaelson Contrast media
US5260050A (en) * 1988-09-29 1993-11-09 Ranney David F Methods and compositions for magnetic resonance imaging comprising superparamagnetic ferromagnetically coupled chromium complexes
US5314681A (en) * 1988-12-23 1994-05-24 Nycomed Innovation Ab Composition of positive and negative contrast agents for electron spin resonance enhanced magnetic resonance imaging
EP0600529A2 (en) * 1992-12-02 1994-06-08 NanoSystems L.L.C. Preparation and magnetic properties of very small magnetite-dextran particles
US5342607A (en) * 1986-07-03 1994-08-30 Advanced Magnetics, Inc. Receptor mediated endocytosis type magnetic resonance imaging contrast agents
WO1994021240A2 (en) * 1993-03-17 1994-09-29 Silica Gel Ges.M.B.H Superparamagnetic particles, process for producing the same and their use
US5352432A (en) * 1986-07-03 1994-10-04 Advanced Magnetics, Inc. Hepatocyte specific composition and their use as diagnostic imaging agents
EP0656368A1 (en) * 1992-08-05 1995-06-07 Meito Sangyo Kabushiki Kaisha Small-diameter composite composed of water-soluble carboxypolysaccharide and magnetic iron oxide
WO1996004017A1 (en) * 1994-08-04 1996-02-15 Institut für Diagnostikforschung GmbH an der Freien Universität Berlin Iron-containing nanoparticles with double coating and their use in diagnosis and therapy
US5494655A (en) * 1990-03-09 1996-02-27 The Regents Of The University Of California Methods for detecting blood perfusion variations by magnetic resonance imaging
US5496534A (en) * 1991-09-26 1996-03-05 Nycomed Imaging As Squid magnetometry using ferri-and ferromagnetic particles
US5582654A (en) * 1994-05-20 1996-12-10 The University Of Southern California Method for creating a corrosion-resistant surface on aluminum alloys having a high copper content
WO1997014443A1 (en) * 1995-10-19 1997-04-24 Bracco International B.V. Magnetically labeled chemoattractants as targeted contrast agents in the nmr imaging of living tissues
WO1997016474A1 (en) * 1995-11-01 1997-05-09 Bracco Research S.A. Targeted magnetically labeled molecular marker systems for the nmr imaging
US5679323A (en) * 1986-07-03 1997-10-21 Advanced Magnetics, Inc. Hepatocyte-specific receptor-mediated endocytosis-type compositions
EP0861667A2 (en) * 1990-09-14 1998-09-02 Syngenix Limited Particulate agents
WO1998058673A1 (en) * 1997-06-20 1998-12-30 Institut Für Neue Materialien Gem. Gmbh Nanoscale particles having an iron oxide-containing core enveloped by at least two shells
US5948384A (en) * 1990-09-14 1999-09-07 Syngenix Limited Particulate agents
US6342396B1 (en) 1997-01-30 2002-01-29 Bio Merieux Method for isolating, in particular for detecting or quantifying an analyte in a medium
WO2003066644A1 (en) * 2002-02-04 2003-08-14 The Circle For The Promotion Of Science And Engineering Organic substance having ferrite bonded thereto and process for producing the same
US6713173B2 (en) 1996-11-16 2004-03-30 Nanomagnetics Limited Magnetizable device
US6815063B1 (en) 1996-11-16 2004-11-09 Nanomagnetics, Ltd. Magnetic fluid
US6896957B1 (en) 1996-11-16 2005-05-24 Nanomagnetics, Ltd. Magnetizable device
US6919067B2 (en) 1991-09-13 2005-07-19 Syngenix Limited Compositions comprising a tissue glue and therapeutic agents
US6986942B1 (en) 1996-11-16 2006-01-17 Nanomagnetics Limited Microwave absorbing structure
US7082326B2 (en) 2000-03-31 2006-07-25 Amersham Health As Method of magnetic resonance imaging
WO2008089738A2 (en) * 2007-01-23 2008-07-31 Bayer Schering Pharma Aktiengesellschaft Ferrous oxide-binding peptides
RU2497546C1 (en) * 2012-04-23 2013-11-10 Общество с ограниченной ответственностью "Ланда Фармасьютикалз" Magnetic resonant and x-ray contrast agent, and method for preparing it
US8669236B2 (en) 2005-05-12 2014-03-11 The General Hospital Corporation Biotinylated compositions
US8771699B2 (en) 2008-01-09 2014-07-08 Magforce Ag Magnetic transducers
US9408912B2 (en) 2011-08-10 2016-08-09 Magforce Ag Agglomerating magnetic alkoxysilane-coated nanoparticles
US9530928B2 (en) 1997-11-25 2016-12-27 The Regents Of The University Of California Semiconductor nanocrystal probes for biological applications and process for making and using such probes
US10532104B2 (en) 2012-08-31 2020-01-14 The General Hospital Corporation Biotin complexes for treatment and diagnosis of Alzheimer'S disease

Families Citing this family (107)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5618514A (en) 1983-12-21 1997-04-08 Nycomed Imaging As Diagnostic and contrast agent
PT81498B (en) * 1984-11-23 1987-12-30 Schering Ag METHOD FOR PREPARING COMPOSITIONS FOR DIAGNOSTICS CONTAINING MAGNETIC PARTICLES
US5186922A (en) * 1985-03-15 1993-02-16 See/Shell Biotechnology, Inc. Use of biodegradable microspheres labeled with imaging energy constrast materials
US5554386A (en) * 1986-07-03 1996-09-10 Advanced Magnetics, Inc. Delivery of therapeutic agents to receptors using polysaccharides
US5248492A (en) * 1986-07-03 1993-09-28 Advanced Magnetics, Inc. Low molecular weight carbohydrates as additives to stabilize metal oxide compositions
US5284646A (en) * 1986-07-03 1994-02-08 Advanced Magnetics Inc. Hepatocyte specific receptor mediated endocytosis type magnetic resonance imaging contrast agents
US5141739A (en) * 1986-07-03 1992-08-25 Advanced Magnetics, Inc. Delivery of x-ray contrast agents using receptor mediated endocytosis
US5160726A (en) * 1990-02-15 1992-11-03 Advanced Magnetics Inc. Filter sterilization for production of colloidal, superparamagnetic MR contrast agents
US5102652A (en) * 1986-07-03 1992-04-07 Advanced Magnetics Inc. Low molecular weight carbohydrates as additives to stabilize metal oxide compositions
US5219554A (en) 1986-07-03 1993-06-15 Advanced Magnetics, Inc. Hydrated biodegradable superparamagnetic metal oxides
US5069216A (en) 1986-07-03 1991-12-03 Advanced Magnetics Inc. Silanized biodegradable super paramagnetic metal oxides as contrast agents for imaging the gastrointestinal tract
US5314679A (en) * 1986-07-03 1994-05-24 Advanced Magnetics Inc. Vascular magnetic resonance imaging agent comprising nanoparticles
US5336506A (en) * 1986-07-03 1994-08-09 Advanced Magnetics Inc. Targeting of therapeutic agents using polysaccharides
US5129877A (en) * 1988-04-29 1992-07-14 University Of Georgia Research Foundation, Inc. Receptor-mediated delivery system
JPH0226551A (en) * 1988-07-15 1990-01-29 Olympus Optical Co Ltd Ultrasonic remedying device
US5190635A (en) * 1989-04-03 1993-03-02 Ashland Oil, Inc. Superparamagnetic formation of FCC catalyst provides means of separation of old equilibrium fluid cracking catalyst
US5064636A (en) * 1989-10-19 1991-11-12 Li King C P Paramagnetic oil emulsions as enteric MRI contrast agents
US5120527A (en) * 1989-10-19 1992-06-09 King Chuen Peter Li Paramagnetic oil emulsions as mri contrast agents
JPH05503538A (en) 1990-02-15 1993-06-10 アドバンスド・マグネティクス・インク Filter sterilization method for colloidal superparamagnetic MR contrast agent production
IL98744A0 (en) * 1990-07-06 1992-07-15 Gen Hospital Corp Method of studying biological tissue using monocrystalline particles
US5198098A (en) * 1990-10-19 1993-03-30 Ashland Oil, Inc. Magnetic separation of old from new equilibrium particles by means of manganese addition
US5171424A (en) * 1990-10-22 1992-12-15 Ashland Oil, Inc. Magnetic separation of old from new cracking catalyst by means of heavy rare earth "magnetic hooks"
ES2131067T5 (en) * 1991-01-19 2004-10-16 Meito Sangyo Kabushiki Kaisha COMPOSITION CONTAINING ULTRAFIN PARTICLES OF MAGNETIC METAL OXIDE.
GB9106686D0 (en) * 1991-03-28 1991-05-15 Hafslund Nycomed As Improvements in or relating to contrast agents
GB9200388D0 (en) * 1992-01-09 1992-02-26 Nycomed As Improvements in or relating to contrast agents
ATE132758T1 (en) * 1992-06-01 1996-01-15 Basf Ag APPLICATION OF DISPERSIONS OF MAGNETO-IONIC PARTICLES IN MRI CONTRAST AGENTS
WO1994002068A1 (en) * 1992-07-21 1994-02-03 The General Hospital Corporation System of drug delivery to the lymphatic tissues
US5323780A (en) * 1992-08-07 1994-06-28 University Of Florida Research Foundation, Inc. Artifact-free imaging contrast agent
DE4239442C2 (en) * 1992-11-24 2001-09-13 Sebo Gmbh Use of an adsorbent material modified with polynuclear metal oxide hydroxides for the selective elimination of inorganic phosphate from protein-containing liquids
US5411730A (en) * 1993-07-20 1995-05-02 Research Corporation Technologies, Inc. Magnetic microparticles
JP3854631B2 (en) * 1993-08-12 2006-12-06 アドバンスド・マグネティクス・インク Synthesis of superparamagnetic oxide colloids coated with polysaccharides
WO1995031220A1 (en) * 1994-05-12 1995-11-23 Otsuka Pharmaceutical Co., Ltd. Contrast medium for magnetic resonance imaging
KR970705154A (en) * 1994-07-07 1997-09-06 아서 에스. 모겐스턴 HIGHLY DISPERSIVE MAGNETIC METAL OXIDE PARTICLES, PROCESSES FOR THEIR PREPARATION AND THEIR USE
WO1996009840A1 (en) 1994-09-27 1996-04-04 Nycomed Imaging A/S Contrast agent
US5643246A (en) * 1995-02-24 1997-07-01 Gel Sciences, Inc. Electromagnetically triggered, responsive gel based drug delivery device
US6107102A (en) * 1995-06-07 2000-08-22 Regents Of The University Of California Therapeutic microdevices and methods of making and using same
AU6104896A (en) * 1995-06-07 1996-12-30 Regents Of The University Of California, The Therapeutic microdevices and methods of making and using sam e
DE19528029B4 (en) 1995-07-31 2008-01-10 Chemagen Biopolymer-Technologie Aktiengesellschaft Magnetic polymer particles based on polyvinyl alcohol, process for their preparation and use
US20030119724A1 (en) * 1995-11-22 2003-06-26 Ts`O Paul O.P. Ligands to enhance cellular uptake of biomolecules
GB9600427D0 (en) * 1996-01-10 1996-03-13 Nycomed Imaging As Contrast media
NZ325403A (en) 1996-01-10 2000-02-28 Nycomed Imaging As Contrast media comprising superparamagnetic particles in an organic coating
US5855868A (en) * 1996-04-01 1999-01-05 Nycomed Imaging As Method of T1 -weighted resonance imaging of RES organs
DK172860B1 (en) 1998-03-25 1999-08-16 Pharmacosmos Holding As Iron dextran compound for use as a component of a therapeutic agent for the prevention or treatment of iron man
DK173138B1 (en) 1998-11-20 2000-02-07 Pharmacosmos Holding As Process for Preparing an Iron Dextran Compound, Iron Dextran Compound Prepared by the Process, Pharmaceutical
US7871597B2 (en) 1999-04-09 2011-01-18 Amag Pharmaceuticals, Inc. Polyol and polyether iron oxide complexes as pharmacological and/or MRI contrast agents
EP1522318A3 (en) * 1999-04-09 2005-07-06 Advanced Magnetics Incorporated Heat stable coated colloidal iron oxides
JP5064612B2 (en) 1999-04-09 2012-10-31 エーエムエージー ファーマシューティカルズ,インコーポレイテッド Thermally stable colloidal iron oxide coated with reduced carbohydrates and carbohydrate derivatives
US6140001A (en) * 1999-05-04 2000-10-31 Mitsui Mining & Smelting Co., Ltd. Iron oxide microparticles and a process for producing them
GB9921579D0 (en) * 1999-09-13 1999-11-17 Nycomed Imaging As
DE10016559A1 (en) * 2000-04-03 2001-10-18 Eucro Europe Contract Res Gmbh System for the transport of active substances in a biological system
US6676686B2 (en) 2000-04-25 2004-01-13 Harumi Naganuma Noninvasive detection and activation of the lymphatic system in treating disease and alleviating pain
US7169618B2 (en) 2000-06-28 2007-01-30 Skold Technology Magnetic particles and methods of producing coated magnetic particles
CN100406065C (en) 2000-12-01 2008-07-30 细胞工厂治疗公司 Conjugates of glycosylated/galactosylated peptide, bifunctional linker and nucleotidic monomers/polymers, and related compositions and method of use
US20020177769A1 (en) * 2001-04-23 2002-11-28 The Regents Of The University Of California Method and apparatus for locating cells in the body by measuring magnetic moments
WO2002100269A1 (en) * 2001-06-13 2002-12-19 The Government Of The United States Of America, As Represented By The Secretary Of The Department Of Health & Human Services Compositions and methods for magnetically labeling cells
JP4090722B2 (en) * 2001-10-23 2008-05-28 純一 小川 Magnetic fluid detection device
US7162302B2 (en) 2002-03-04 2007-01-09 Nanoset Llc Magnetically shielded assembly
US20050260331A1 (en) * 2002-01-22 2005-11-24 Xingwu Wang Process for coating a substrate
US20040225213A1 (en) * 2002-01-22 2004-11-11 Xingwu Wang Magnetic resonance imaging coated assembly
US20030191090A1 (en) * 2002-04-09 2003-10-09 Pharmacosmos Holding A/S Iron dextrin compounds for the treatment of iron deficiency anaemia
DE10224352A1 (en) * 2002-06-01 2003-12-11 Mueller Schulte Detlef Thermosensitive polymer carrier with changeable physical structure for biochemical analysis, diagnostics and therapy
EP1386927B1 (en) 2002-08-02 2005-03-30 Institut Curie Shiga toxin B-subunit as a vector for tumor diagnosis and drug delivery to GB3 expressing tumors
SE0202725D0 (en) * 2002-09-12 2002-09-12 Genovis Ab Device for magnetically inducible membrane transport
DE10331439B3 (en) * 2003-07-10 2005-02-03 Micromod Partikeltechnologie Gmbh Magnetic nanoparticles with improved magnetic properties
US20060116349A1 (en) * 2003-03-14 2006-06-01 Luitpold Pharmaceuticals, Inc. Methods and compositions for administration of iron for the treatment of restless leg syndrome
US6960571B2 (en) * 2003-03-14 2005-11-01 Luitpold Pharmaceuticals, Inc. Methods and compositions for administration of iron for the treatment of restless leg syndrome
WO2004091395A2 (en) 2003-04-15 2004-10-28 Philips Intellectual Property & Standards Gmbh Method for spatially resolved determination of magnetic particle distribution in an area of examination
US20060210986A1 (en) 2003-04-15 2006-09-21 Koninklijke Philips Electronics N.V. Method of determining state variables and changes in state variables
US20060248945A1 (en) * 2003-04-15 2006-11-09 Koninklijke Philips Electronics N.V. Method and apparatus for improved determination of spatial non-agglomerated magnetic particle distribution in an area of examination
WO2004091394A2 (en) * 2003-04-15 2004-10-28 Philips Intellectual Property & Standards Gmbh Method to determine the spatial distribution of magnetic particles and magnetic particle administering compositions
FR2855315B1 (en) * 2003-05-23 2005-08-19 Centre Nat Rech Scient NEUTRAL-STABLE FERROFLUIDS AND MODIFIED FERROFLUIDS OBTAINED BY MODIFICATION OF THE PARTICLE SURFACE OF THESE FERROFLUIDS
EP1635878B1 (en) * 2003-06-25 2010-12-29 Guerbet Peptide conjugate for magnetic resonance imaging of matrix metalloproteinases
AR047692A1 (en) * 2003-07-10 2006-02-08 Epix Medical Inc IMAGES OF STATIONARY WHITE
AU2004264038B2 (en) * 2003-07-17 2010-09-23 Life Technologies As Process for preparing coated magnetic particles
EP1693387B1 (en) * 2003-07-17 2012-06-20 Invitrogen Dynal AS Process for preparing coated magnetic particles
DE10350248A1 (en) * 2003-10-28 2005-06-16 Magnamedics Gmbh Thermosensitive, biocompatible polymer carriers with variable physical structure for therapy, diagnostics and analytics
DE10355409A1 (en) * 2003-11-25 2005-06-30 Magnamedics Gmbh Spherical, magnetic silica gel carriers with increased surface area for the purification of nucleic acids
US20070100457A1 (en) * 2004-03-04 2007-05-03 Hyde Edward R Jr Paramagnetic liquid interface
US20060014938A1 (en) * 2004-07-14 2006-01-19 Groman Ernest V Stable aqueous colloidal lanthanide oxides
US20060024229A1 (en) * 2004-07-29 2006-02-02 Seth Karp Method and product for locating an internal bleeding site
US20080118440A1 (en) * 2004-08-23 2008-05-22 The General Hospital Corporation Imaging Cellular Nucleic Acids
JP2008510829A (en) * 2004-08-25 2008-04-10 ザ リージェンツ オブ ザ ユニバーシティ オブ ミシガン Compositions based on dendrimers and their use
DE102004052533A1 (en) * 2004-10-15 2006-05-04 Mykhaylyk, Olga, Dr. Particles for use in diagnosis and therapy, especially for binding therapeutic agent for treating e.g. tumors and bacterial, rheumatic, neurologic and thrombotic diseases, have nanocrystalline magnetic core and envelope enclosing core
KR100746312B1 (en) * 2005-03-14 2007-08-03 한국화학연구원 Water soluble iron oxide nanoparticles and preparation
US20100166669A1 (en) * 2005-06-28 2010-07-01 Joslin Diabetes Center, Inc. Methods of imaging inflammation in pancreatic islets
US20070041934A1 (en) * 2005-08-12 2007-02-22 Regents Of The University Of Michigan Dendrimer based compositions and methods of using the same
US9149545B2 (en) * 2005-11-02 2015-10-06 General Electric Company Nanoparticle-based imaging agents for X-ray/computed tomography and methods for making same
CZ301067B6 (en) * 2006-02-24 2009-10-29 Ústav makromolekulární chemie AV CR Iron oxide-based superparamagnetic nanoparticles with modified surface, process of their preparation and use
WO2008008483A2 (en) * 2006-07-12 2008-01-17 The Regents Of The University Of Michigan Dendrimer based compositions and methods of using the same
US7892520B2 (en) * 2006-07-31 2011-02-22 The Hong Kong University Of Science And Technology Solid-state synthesis of iron oxide nanoparticles
US20080097606A1 (en) * 2006-10-19 2008-04-24 Cragg Andrew H Knee joint prosthesis and hyaluronate compositions for treatment of osteoarthritis
US20080167544A1 (en) * 2006-12-01 2008-07-10 Cold Spring Diagnostics, Inc. Compositions And Methods For Locating An Internal Bleeding Site
PT2319804E (en) * 2006-12-14 2014-11-24 Novartis Ag Iron(iii)-carbohydrate based phosphate adsorbent
JP5607368B2 (en) * 2006-12-18 2014-10-15 コロロッビア イタリア ソシエタ ペル アチオニ Magnetic nanoparticles applied in hyperthermia, their preparation and use in structures with pharmacological applications
CA2684725A1 (en) * 2007-04-19 2009-01-15 The Regents Of The University Of Michigan Dendrimer based compositions and methods of using the same
US8252834B2 (en) 2008-03-12 2012-08-28 The Regents Of The University Of Michigan Dendrimer conjugates
US8889635B2 (en) 2008-09-30 2014-11-18 The Regents Of The University Of Michigan Dendrimer conjugates
US9017644B2 (en) 2008-11-07 2015-04-28 The Regents Of The University Of Michigan Methods of treating autoimmune disorders and/or inflammatory disorders
DE102008060708A1 (en) 2008-12-05 2010-06-17 Dianogen Gmbh Improving contrast properties of medical polymer substrates in framework of imaging processes using magnetic nanoparticles, noble metal colloids or paramagnetic salts, by introducing magnetic nanoparticles or noble metals on the substrate
JP2009175161A (en) * 2009-05-11 2009-08-06 Regents Of The Univ Of California Organo luminescent semiconductor nanocrystal probe for biological applications, and process for making and using such probe
WO2010149150A2 (en) 2009-06-22 2010-12-29 Deklatec Gmbh Colorless, magnetic polymer particles for highly sensitive detection of biological substances and pathogens within the context of bioanalytics and diagnostics
US8945508B2 (en) 2009-10-13 2015-02-03 The Regents Of The University Of Michigan Dendrimer compositions and methods of synthesis
US8912323B2 (en) 2009-10-30 2014-12-16 The Regents Of The University Of Michigan Multifunctional small molecules
WO2012136813A2 (en) 2011-04-07 2012-10-11 Universitetet I Oslo Agents for medical radar diagnosis
WO2013085718A1 (en) 2011-12-08 2013-06-13 The Regents Of The University Of Michigan Multifunctional small molecules
AU2019242190B2 (en) 2018-03-27 2024-06-13 Exact Sciences Corporation Method for stabilizing hemoglobin and reagents for performing the same
CN108653732B (en) * 2018-04-24 2020-06-26 江苏大学 PH-responsive ferroferric oxide nanoparticle and preparation method and application thereof

Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2820740A (en) 1953-02-27 1958-01-21 Benger Lab Ltd Therapeutic preparations of iron
US2885393A (en) 1956-02-24 1959-05-05 R K Laros Company Dextran-iron complex and process for making same
US4001288A (en) 1965-09-15 1977-01-04 Howard S. Gable Magnetic organo-iron compounds
US4267234A (en) 1978-03-17 1981-05-12 California Institute Of Technology Polyglutaraldehyde synthesis and protein bonding substrates
US4329241A (en) 1979-07-20 1982-05-11 Agence Nationale De Valorisation De La Recherche (Anvar) Magnetic fluids and process for obtaining them
US4452773A (en) 1982-04-05 1984-06-05 Canadian Patents And Development Limited Magnetic iron-dextran microspheres
WO1985004330A1 (en) * 1984-03-29 1985-10-10 Nyegaard & Co A/S Use of ferromagnetic particles in contrast agents for nmr imaging and contrast agents
US4554088A (en) 1983-05-12 1985-11-19 Advanced Magnetics Inc. Magnetic particles for use in separations
US4615879A (en) * 1983-11-14 1986-10-07 Vanderbilt University Particulate NMR contrast agents for gastrointestinal application
US4628037A (en) 1983-05-12 1986-12-09 Advanced Magnetics, Inc. Binding assays employing magnetic particles
US4637929A (en) * 1985-01-04 1987-01-20 Salutar, Inc. Ferrioxamine-paramagnetic contrast agents for MR imaging, composition, apparatus and use
US4656026A (en) * 1984-12-10 1987-04-07 University Of Iowa Research Foundation Magnetic resonance (MR) image enhancement compounds for specific areas of the brain
US4675173A (en) * 1985-05-08 1987-06-23 Molecular Biosystems, Inc. Method of magnetic resonance imaging of the liver and spleen

Family Cites Families (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4303636A (en) * 1974-08-20 1981-12-01 Gordon Robert T Cancer treatment
US4106488A (en) * 1974-08-20 1978-08-15 Robert Thomas Gordon Cancer treatment method
US3980076A (en) * 1974-10-02 1976-09-14 The Board Of Trustees Of Leland Stanford Junior University Method for measuring externally of the human body magnetic susceptibility changes
US4136683A (en) * 1976-03-25 1979-01-30 Gordon Robert T Intracellular temperature measurement
US4647447A (en) * 1981-07-24 1987-03-03 Schering Aktiengesellschaft Diagnostic media
US4731239A (en) * 1983-01-10 1988-03-15 Gordon Robert T Method for enhancing NMR imaging; and diagnostic use
DE3316703A1 (en) * 1983-05-04 1984-11-08 Schering AG, 1000 Berlin und 4709 Bergkamen ORAL CONTRAST AGENT FOR MRI MRI AND THE PRODUCTION THEREOF
DE3422249A1 (en) * 1984-06-15 1985-12-19 Pfeifer & Langen, 5000 Köln WATER-SOLUBLE IRON DEXTRANE AND METHOD FOR THE PRODUCTION THEREOF
PT81498B (en) * 1984-11-23 1987-12-30 Schering Ag METHOD FOR PREPARING COMPOSITIONS FOR DIAGNOSTICS CONTAINING MAGNETIC PARTICLES
GB8504330D0 (en) 1985-02-20 1985-03-20 Rolls Royce Brush seal manufacture

Patent Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2820740A (en) 1953-02-27 1958-01-21 Benger Lab Ltd Therapeutic preparations of iron
US2885393A (en) 1956-02-24 1959-05-05 R K Laros Company Dextran-iron complex and process for making same
US4001288A (en) 1965-09-15 1977-01-04 Howard S. Gable Magnetic organo-iron compounds
US4267234A (en) 1978-03-17 1981-05-12 California Institute Of Technology Polyglutaraldehyde synthesis and protein bonding substrates
US4329241A (en) 1979-07-20 1982-05-11 Agence Nationale De Valorisation De La Recherche (Anvar) Magnetic fluids and process for obtaining them
US4452773A (en) 1982-04-05 1984-06-05 Canadian Patents And Development Limited Magnetic iron-dextran microspheres
US4628037A (en) 1983-05-12 1986-12-09 Advanced Magnetics, Inc. Binding assays employing magnetic particles
US4554088A (en) 1983-05-12 1985-11-19 Advanced Magnetics Inc. Magnetic particles for use in separations
US4615879A (en) * 1983-11-14 1986-10-07 Vanderbilt University Particulate NMR contrast agents for gastrointestinal application
WO1985004330A1 (en) * 1984-03-29 1985-10-10 Nyegaard & Co A/S Use of ferromagnetic particles in contrast agents for nmr imaging and contrast agents
US4656026A (en) * 1984-12-10 1987-04-07 University Of Iowa Research Foundation Magnetic resonance (MR) image enhancement compounds for specific areas of the brain
US4637929A (en) * 1985-01-04 1987-01-20 Salutar, Inc. Ferrioxamine-paramagnetic contrast agents for MR imaging, composition, apparatus and use
US4675173A (en) * 1985-05-08 1987-06-23 Molecular Biosystems, Inc. Method of magnetic resonance imaging of the liver and spleen

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
OHGUSHI ET AL., J. MAG RES., vol. 29, 1978, pages 599

Cited By (84)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5352432A (en) * 1986-07-03 1994-10-04 Advanced Magnetics, Inc. Hepatocyte specific composition and their use as diagnostic imaging agents
US5679323A (en) * 1986-07-03 1997-10-21 Advanced Magnetics, Inc. Hepatocyte-specific receptor-mediated endocytosis-type compositions
US5342607A (en) * 1986-07-03 1994-08-30 Advanced Magnetics, Inc. Receptor mediated endocytosis type magnetic resonance imaging contrast agents
WO1989003675A1 (en) * 1987-10-26 1989-05-05 Carbomatrix Ab Superparamagnetic particles, a way of producing said particles and their use
WO1989009625A1 (en) * 1988-04-08 1989-10-19 Cockbain, Julian, Roderick, Michaelson Contrast agents for magnetic resonance imaging
WO1989011873A1 (en) * 1988-06-03 1989-12-14 Nycomed As Magnetic particle-containing compositions
WO1989011874A1 (en) * 1988-06-07 1989-12-14 Laurence David Hall Magnetic resonance imaging
EP0381742A4 (en) * 1988-08-04 1991-04-24 Advanced Magnetics Incorporated Receptor mediated endocytosis type mri contrast agents
EP0670167A1 (en) * 1988-08-04 1995-09-06 Advanced Magnetics Incorporated Receptor mediated endocytosis type diagnostic agents
EP0381742A1 (en) * 1988-08-04 1990-08-16 Advanced Magnetics Inc Receptor mediated endocytosis type mri contrast agents.
EP0441797A4 (en) * 1988-08-16 1992-01-15 Advanced Magnetics Incorporated Vascular magnetic imaging method and agent
EP0441797A1 (en) * 1988-08-16 1991-08-21 Advanced Magnetics Inc Vascular magnetic imaging method and agent.
EP0361960A2 (en) * 1988-09-29 1990-04-04 RANNEY, David F. Methods and compositions for magnetic resonance imaging
EP0361960A3 (en) * 1988-09-29 1992-01-02 RANNEY, David F. Methods and compositions for magnetic resonance imaging
US5260050A (en) * 1988-09-29 1993-11-09 Ranney David F Methods and compositions for magnetic resonance imaging comprising superparamagnetic ferromagnetically coupled chromium complexes
US5314681A (en) * 1988-12-23 1994-05-24 Nycomed Innovation Ab Composition of positive and negative contrast agents for electron spin resonance enhanced magnetic resonance imaging
EP0474785A1 (en) * 1989-05-30 1992-03-18 Alliance Pharmaceutical Corporation Percutaneous lymphography
EP0474785A4 (en) * 1989-05-30 1992-11-04 Alliance Pharmaceutical Corporation Percutaneous lymphography
US5496536A (en) * 1989-05-30 1996-03-05 Wolf; Gerald Percutaneous lymphography
EP0489119A1 (en) 1989-08-22 1992-06-10 Immunicon Corp Resuspendable coated magnetic particles and stable magnetic particle suspensions.
EP0489119B2 (en) 1989-08-22 2003-01-02 Immunicon Corporation Resuspendable coated magnetic particles and stable magnetic particle suspensions
US5494655A (en) * 1990-03-09 1996-02-27 The Regents Of The University Of California Methods for detecting blood perfusion variations by magnetic resonance imaging
US5190744A (en) * 1990-03-09 1993-03-02 Salutar Methods for detecting blood perfusion variations by magnetic resonance imaging
US5833947A (en) * 1990-03-09 1998-11-10 The Regents Of The University Of California Magnetic resonance imaging
WO1991014457A1 (en) * 1990-03-24 1991-10-03 The Victoria University Of Manchester Method for the study of internal body tissues
US5380514A (en) * 1990-03-24 1995-01-10 The Victoria University Of Manchester Method for magnetic resonance imaging of internal body tissues using polysiloxanes
US5384109A (en) * 1990-04-02 1995-01-24 Nycomed Imaging As Diagnostic magnetometry using superparamagnetic particles
US5628983A (en) * 1990-04-02 1997-05-13 Nycomed Imaging Squid magnetometry using paramagnetic metal chelates
US5738837A (en) * 1990-04-02 1998-04-14 Nycomed Imaging As Lanthanide paramagnetic agents for magnetometric imaging
EP0727224A2 (en) * 1990-04-02 1996-08-21 Nycomed Imaging A/S Diagnostic agents
EP0727224A3 (en) * 1990-04-02 1997-07-09 Nycomed Imaging As Diagnostic agents
WO1991015243A1 (en) * 1990-04-02 1991-10-17 Cockbain, Julian, Roderick, Michaelson Diagnostic agents
AU655175B2 (en) * 1990-04-02 1994-12-08 Nycomed Imaging As Diagnostic agents
US5948384A (en) * 1990-09-14 1999-09-07 Syngenix Limited Particulate agents
US6562318B1 (en) 1990-09-14 2003-05-13 Syngenix Limited Particular agents
WO1992004916A3 (en) * 1990-09-14 1992-08-20 St George S Enterprises Ltd Particulate agents
EP0861667A3 (en) * 1990-09-14 2001-08-08 Syngenix Limited Particulate agents
EP0861667A2 (en) * 1990-09-14 1998-09-02 Syngenix Limited Particulate agents
WO1992004916A2 (en) * 1990-09-14 1992-04-02 St. George's Enterprises Limited Particulate agents
US5792445A (en) * 1991-02-15 1998-08-11 Bracco International B.V. Polymers and copolymers of acrylic acid MRI of the digestive tract of patients
EP0502814A3 (en) * 1991-02-15 1992-10-07 Sintetica S.A. Compositions for increasing the image contrast in diagnostic investigations of the digestive tract of patients
US5688490A (en) * 1991-02-15 1997-11-18 Bracco International B.V. Mucoadhesive compositions for increasing the ultrasonic image contrast of the digestive tract
EP0502814A2 (en) * 1991-02-15 1992-09-09 BRACCO International B.V. Compositions for increasing the image contrast in imaging of the digestive tract of patients
US5370901A (en) * 1991-02-15 1994-12-06 Bracco International B.V. Compositions for increasing the image contrast in diagnostic investigations of the digestive tract of patients
US5653959A (en) * 1991-02-15 1997-08-05 Sintetica Sa Compositions for increasing the image contrast in diagnostic investigations of the digestive tract of patients
WO1992022586A1 (en) 1991-06-11 1992-12-23 Meito Sangyo Kabushiki Kaisha Oxidized composite comprising water-soluble carboxypolysaccharide and magnetic iron oxide
US6919067B2 (en) 1991-09-13 2005-07-19 Syngenix Limited Compositions comprising a tissue glue and therapeutic agents
US5496534A (en) * 1991-09-26 1996-03-05 Nycomed Imaging As Squid magnetometry using ferri-and ferromagnetic particles
WO1993012717A2 (en) * 1992-01-03 1993-07-08 Cockbain, Julian, Roderick, Michaelson Contrast media
WO1993012717A3 (en) * 1992-01-03 1993-08-05 Cockbain Julian R M Contrast media
US5639444A (en) * 1992-01-03 1997-06-17 Nycomed Imaging As Method of electrical impedance imaging using a triiodophenyl compound or gas encapsulated microbubbles
EP0656368A1 (en) * 1992-08-05 1995-06-07 Meito Sangyo Kabushiki Kaisha Small-diameter composite composed of water-soluble carboxypolysaccharide and magnetic iron oxide
US5766572A (en) * 1992-08-05 1998-06-16 Meito Sangyo Kabushiki Kaisha Water-soluble carboxypolysaccharide-magnetic iron oxide complex having a small particle diameter
EP0656368A4 (en) * 1992-08-05 1996-05-08 Meito Sangyo Kk Small-diameter composite composed of water-soluble carboxypolysaccharide and magnetic iron oxide.
EP0600529A3 (en) * 1992-12-02 1995-10-25 Sterling Winthrop Inc Preparation and magnetic properties of very small magnetite-dextran particles.
EP0600529A2 (en) * 1992-12-02 1994-06-08 NanoSystems L.L.C. Preparation and magnetic properties of very small magnetite-dextran particles
US5916539A (en) * 1993-03-02 1999-06-29 Silica Gel Ges. M.B.H. Superparamagnetic particles, process for producing the same and their use
WO1994021240A3 (en) * 1993-03-17 1994-10-13 Silica Gel Gmbh Superparamagnetic particles, process for producing the same and their use
WO1994021240A2 (en) * 1993-03-17 1994-09-29 Silica Gel Ges.M.B.H Superparamagnetic particles, process for producing the same and their use
US5582654A (en) * 1994-05-20 1996-12-10 The University Of Southern California Method for creating a corrosion-resistant surface on aluminum alloys having a high copper content
US6048515A (en) * 1994-08-04 2000-04-11 Institut Fur Diagnostikforschung Gmbh Iron-containing nanoparticles with double coating and their use in diagnosis and therapy
WO1996004017A1 (en) * 1994-08-04 1996-02-15 Institut für Diagnostikforschung GmbH an der Freien Universität Berlin Iron-containing nanoparticles with double coating and their use in diagnosis and therapy
WO1997014443A1 (en) * 1995-10-19 1997-04-24 Bracco International B.V. Magnetically labeled chemoattractants as targeted contrast agents in the nmr imaging of living tissues
WO1997016474A1 (en) * 1995-11-01 1997-05-09 Bracco Research S.A. Targeted magnetically labeled molecular marker systems for the nmr imaging
US5910300A (en) * 1995-11-01 1999-06-08 Bracco Research S.A. Amphiphilic linkers for coupling administrable diagnostically or physiologically active agents and bioselective targeting compounds
US6986942B1 (en) 1996-11-16 2006-01-17 Nanomagnetics Limited Microwave absorbing structure
US6713173B2 (en) 1996-11-16 2004-03-30 Nanomagnetics Limited Magnetizable device
US6815063B1 (en) 1996-11-16 2004-11-09 Nanomagnetics, Ltd. Magnetic fluid
US6896957B1 (en) 1996-11-16 2005-05-24 Nanomagnetics, Ltd. Magnetizable device
US6342396B1 (en) 1997-01-30 2002-01-29 Bio Merieux Method for isolating, in particular for detecting or quantifying an analyte in a medium
WO1998058673A1 (en) * 1997-06-20 1998-12-30 Institut Für Neue Materialien Gem. Gmbh Nanoscale particles having an iron oxide-containing core enveloped by at least two shells
US6979466B2 (en) 1997-06-20 2005-12-27 Leibniz-Institut Fuer Neue Materialien Gemeinnuetzige Gmbh Nanoscale particles having an iron oxide-containing core enveloped by at least two shells
US9530928B2 (en) 1997-11-25 2016-12-27 The Regents Of The University Of California Semiconductor nanocrystal probes for biological applications and process for making and using such probes
US7082326B2 (en) 2000-03-31 2006-07-25 Amersham Health As Method of magnetic resonance imaging
WO2003066644A1 (en) * 2002-02-04 2003-08-14 The Circle For The Promotion Of Science And Engineering Organic substance having ferrite bonded thereto and process for producing the same
US8669236B2 (en) 2005-05-12 2014-03-11 The General Hospital Corporation Biotinylated compositions
WO2008089738A3 (en) * 2007-01-23 2009-01-08 Bayer Schering Pharma Ag Ferrous oxide-binding peptides
WO2008089738A2 (en) * 2007-01-23 2008-07-31 Bayer Schering Pharma Aktiengesellschaft Ferrous oxide-binding peptides
US8771699B2 (en) 2008-01-09 2014-07-08 Magforce Ag Magnetic transducers
US9814677B2 (en) 2008-01-09 2017-11-14 Magforce Ag Magnetic transducers
US9408912B2 (en) 2011-08-10 2016-08-09 Magforce Ag Agglomerating magnetic alkoxysilane-coated nanoparticles
US9962442B2 (en) 2011-08-10 2018-05-08 Magforce Ag Agglomerating magnetic alkoxysilane-coated nanoparticles
RU2497546C1 (en) * 2012-04-23 2013-11-10 Общество с ограниченной ответственностью "Ланда Фармасьютикалз" Magnetic resonant and x-ray contrast agent, and method for preparing it
US10532104B2 (en) 2012-08-31 2020-01-14 The General Hospital Corporation Biotin complexes for treatment and diagnosis of Alzheimer'S disease

Also Published As

Publication number Publication date
CA1301063C (en) 1992-05-19
EP0275285A4 (en) 1990-01-08
DE3751918T2 (en) 1997-03-20
US4827945A (en) 1989-05-09
EP0275285B1 (en) 1996-10-02
JPH01500196A (en) 1989-01-26
EP0275285A1 (en) 1988-07-27
ATE143604T1 (en) 1996-10-15
DE3751918D1 (en) 1996-11-07

Similar Documents

Publication Publication Date Title
EP0275285B1 (en) Biodegradable superparamagnetic materials used in clinical applications
US4951675A (en) Biodegradable superparamagnetic metal oxides as contrast agents for MR imaging
US5069216A (en) Silanized biodegradable super paramagnetic metal oxides as contrast agents for imaging the gastrointestinal tract
US5219554A (en) Hydrated biodegradable superparamagnetic metal oxides
US4770183A (en) Biologically degradable superparamagnetic particles for use as nuclear magnetic resonance imaging agents
AU653220B2 (en) Nanocrystalline magnetic iron oxide particles - methods for preparation and use in medical diagnostics and therapy
US4863715A (en) Method of NMK imaging using a contrast agent comprising particles of a ferromagnetic material
US6576221B1 (en) Iron-containing nanoparticles with double coating and their use in diagnosis and therapy
US5547682A (en) Preparation and use of novel injectable RES avoiding inorganic particles for medical application
Renshaw et al. Immunospecific NMR contrast agents
US20050260137A1 (en) Contrast agents for magnetic resonance imaging
JPH07500823A (en) Processed apatite particles for medical diagnostic imaging
EP0414700A1 (en) Contrast agents for magnetic resonance imaging.
KR20090119867A (en) Mri t1 contrasting agent comprising manganese oxide nanoparticle
US20030185757A1 (en) Iron-containing nanoparticles with double coating and their use in diagnosis and therapy
Bai et al. Modular design of Bi-specific nanoplatform engaged in malignant lymphoma immunotherapy
WO2005112758A1 (en) Contrast agents for magnetic resonance imaging
KR101080581B1 (en) Iron oxide/Manganese oxide hybrid nanocrystals for simultaneous T1 and T2 contrast enhancements in MRI and preparation thereof
WO2001074406A2 (en) Dendrimer composition for magnetic resonance analysis
Schweiger Magnetic iron oxide nanoparticles as potential contrast agents for magnetic resonance imaging
Hultman Development of targeted phospholipid coated gamma-iron oxide nanoparticles as MR contrast agents

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): JP NO

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): AT BE CH DE FR GB IT LU NL SE

WWE Wipo information: entry into national phase

Ref document number: 1987904772

Country of ref document: EP

WWP Wipo information: published in national office

Ref document number: 1987904772

Country of ref document: EP

WWG Wipo information: grant in national office

Ref document number: 1987904772

Country of ref document: EP