CA2068632C - Nanocrystalline magnetic iron oxide particles, processes for their preparation and their use in medical diagnostics and therapy - Google Patents

Nanocrystalline magnetic iron oxide particles, processes for their preparation and their use in medical diagnostics and therapy Download PDF

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CA2068632C
CA2068632C CA002068632A CA2068632A CA2068632C CA 2068632 C CA2068632 C CA 2068632C CA 002068632 A CA002068632 A CA 002068632A CA 2068632 A CA2068632 A CA 2068632A CA 2068632 C CA2068632 C CA 2068632C
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magnetic particles
cross
synthetic
magnetite
proteins
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CA2068632A1 (en
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Mayk Kresse
Rudiger Lawaczeck
Detlef Pfefferer
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Bayer Pharma AG
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Institut fuer Diagnostikforschung GmbH
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    • B82Y5/00—Nanobiotechnology or nanomedicine, e.g. protein engineering or drug delivery
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    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2400/00—Assays, e.g. immunoassays or enzyme assays, involving carbohydrates
    • G01N2400/10—Polysaccharides, i.e. having more than five saccharide radicals attached to each other by glycosidic linkages; Derivatives thereof, e.g. ethers, esters
    • G01N2400/38—Heteroglycans, i.e. polysaccharides having more than one sugar residue in the main chain in either alternating or less regular sequence, e.g. gluco- or galactomannans, e.g. Konjac gum, Locust bean gum, Guar gum
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Abstract

Novel nanocrystalline magnetic particles are provided herein which consist of a magnetic iron oxide core of Fe3 0 4, gamma-Fe2 0 3 or mixtures thereof, and an envelope chemisorbed to the core. The composition of the coating material comprises natural or synthetic glycosaminoglycans and/or their derivatives with molecular weights of 500 Da to 250,000 Da, if necessary, which have been covalently cross-linked with appropriate cross-linking agents and/or modified by specific additives. Processes for preparation of these particles as well as the use thereof in medical diagnostics and/or therapy are also taught.

Description

(a) TITLE OF THE INVENTION
NANOCRYSTALLINE MAGNETIC IRON OXIDE PARTICLES, PROCESSES
FOR THEIR PREPARATION AND THEIR USE IN MEDICAL DIAGNOSTICS
AND THERAPY
(b) TECHNICAL FIELD TO WHICH THE INVENTION RELATES
The invention relates to nanocrystalline magnetic particles, to processes for the preparation of these particles, as well as their use in medical diagnostics and therapy.
(c) BACKGROUND ART
Magnetic substances have found their way into medical use as contrast media for magnetic resonance imaging. It should be noted that the first substance to be approved for use was a Gd-DTPA complex (MAGNEVISTTM). Magnetic iron oxide particles have proven to be especially effective in liver diagnostics. They are now in the pre-clinical and also, to some extent, in the clinical development stage. Such magnetic substances are primarily ferrimagnetic iron oxides (e.g., magnetite), nanoparticles which are surrounded with a coating to form stable aqueous sols.
Besides their use as diagnostic agents, ferrous/ferrimagnetic particles are playing an increasing role in the in vitro separation technique and as "thermoseeds"
in local hyperthermia.
Numerous magnetite preparation processes and uses are described in the scientific and patent law literature.
Hasegawa and Hokkoku (U.S. Patent No. 4,101,435) describe an iron oxide-dextran complex and its preparation.
Rembaum (U.S. Patent No. 4,267,234) refers to magnetic polyglutaraldehyde microparticles which are prepared by suspension n:.~ ~ ~."~ ~ ;~
polymerization in the presence of magnetic particles. Widder and Senyei (US 4,247,406) prepare microparticles from an amino acid-polymer matrix in which magnetic particles are embedded. A similar method with nanoparticles is used by Schroder and Mosbach (WO 83/01738) whereby a crystalline hydrocarbon matrix surrounds the magnetic material. Groman and Josephson (US 4,770,183) use magnetic metal oxide particles which are non-coated and coated with a polysaccharide and/or protein coating. Molday (US 4,452,773) describes the synthesis of ferromagnetic iron oxide cores with a polysaccharide coating. He achieves a Stable sol and can couple proteins to the dextran coating using periodate activation.
Gordon (US 4,731,239) claims the use of ferrous, pare- and diamagnetic particles of iron hydroxide, iron oxide and iron dextran for diagnostic purposes. Additional patents (US
4,767,611: 4,758,429 4,735,796) focus on diagnosis and therapy with the aid of the aforesaid iron dextran or iron transferric dextran particles and alternating electromagnetic fields. The particles can be directed to their targets by antigens, antibodies, enzymes or prosthetic groups. Dries et al. (EP 186616) use magnetic particles of double metal oxide/
hydroxide and a complex agent of proteins or alkaline treated saccharides or polysaccharides.
over the years the complexity of the particles has increased and the target has become more specific. Ranney (EP-361960) uses polyatomic chrome complexes which are bonded to a biocompatible clearable carrier.
The carriers listed are: hydrocarbons, polysaccharides, glycosaminoglycans and structurally analogous synthetic polymers.

These Cr4 S clusters have the disadvantage that the number of unpaired electrons is limited to 12.
Application in diagnostics is complemented by therapeutic aspects (hyperthermia, chemotherapy).
Menz et al. (WO 9001295) aim at a special cellular uptake mechanism (receptor-mediated endocytosis) with their superparamagnetic contrast media. They use magnetic iron oxide particles which are surrounded by an arabinose galactan coating of vegetable extraction the toxicological safety of which has not as yet been confirmed.
Yudelson (WO 8911154) deposits a coating of gelatin and a polymeric acid (preferably gum arabic) on the superparamagnetic particles using coacervation and cross-linking preferably with glutaraldehyde. Pilgrim (European patent application publication number 0284549) uses a different approach by forming a chemical bond between the magnetite surface and synthetic polymer stabilizer substances. The reactive stabilizer substance is chemically bonded to the superparamagnetic particles using phosphate, phosphonate or carboxylate groups. Tissue specific bonding substances can be added to the polyethylene skeleton of the stabilizer substance.
In both cases, preparation and magnetic properties of the superparamagnetic particles are described without furnishing proof of the medical suitability and tolerance of the particles.
Magnetic materials are classified as die-, pare-, or ferromagnetic according to their properties in a magnetic field. Dia- and paramagnetism are atomic/ molecular properties which are based on the magnetic moment of the / v H W
prA ~ e~' ~ i~1 ~n..Y LV
electron. The diamagnetism is based on orbital motion of the electrons and is induced by the applied magnetic field. The magnetization is aligned inversely to the external magnetic field. Paramagnetic substances are characterized by one or more unpaired electrons, magnetization is aligned parallel to the external field. Hence paramagnetic atoms/molecules have a permanent magnetic moment and without an external field these magnetic,moments are not oriented. The susceptibility is ,.
independent of the applied field and is inversely proportional to temperature (Curie°s law).
In solid bodies, strong interaction may develop between adjacent atoms/ions so that spontaneous magnetization results. One generally refers to ferromagnetism with more accurate classification in ferrous, ferric and antiferromagnetism. Examples of ferromagnetic materials are the metals iron, cobalt, nickel, many rare earth elements as well as their alloys. The magnetic moment of adjacent atoms/ions can be aligned anti°parallel in combinations of different types of atoms, of ions with different oxidation numbers or of ions that are constructed on a different lattice position. Complete suspension of spontaneous magnetization is referred to as antiferromagnetism. Partial suspension is referred to as ferrimagnetism. Ferrite with a spinal structure demonstrates ferrimagnetic properties. In all three cases domains are formed in solid bodies with different alignments of spontaneous magnetization. Without an external field the magnetic moments of the domains are randomly distributed and there is no externally directed total magnetic moment. Magnetic moments of the domain are aligned in the external magnetic field. A condition preserved in the permanent magnet even after disconnection of the external magnetic field. This is referred 'to as remanence.
The thermal energy counteracts a spontaneous parallel/antiparallel alignment of the individual magnetic ~a~'s~'~,)e~y, a n P~ ~ i of ._d id ' ~s moments in particles which are smaller than the domain.
Suspensions of such ferrous/ferrimagnetic particles with dimensions smaller than 10 - 50 nm have properties similar to paramagnetic materials. They show no remanence or hysteresis 5 but they show susceptibility values which approach. the corresponding values for the solid body. Therefore, they are often referred to as superparamagnetic particles. Ferrites which have been used as parenteral MR contrast media are included in this category (e. g. Wolf et al., Magnetic Resonance Annual, Neia York, Raven Press 1985, 231-266; Saini et al., Radiology 1987, 162, 217-222).
The MR image and signals of MR spectroscopy are produced due to interaction of three physical parameters: density of the sort of core involved (e. g. protons, 13 carbon, 3lphosphorous) spin-lattice-relaxation time, T1, and spin-spin-relaxation time, T2. T1 and T2 affecting signal intensity in a complicated manner. They are functions of strength of the magnetic field, temperature, reorientation and th:~ type of rhysical interaction among individual molecules. Signal intensity increases proportionally to the density of the observed core. For protons the observed cores can be roughly subdivided between fat and water protons.
Proton density in a physiological environment can only be slightly influenced, e.g. by deuterium oxide substitution.
Relaxation time, on the other hand, can be relatively easily influenced by additional paramagnetic molecules/ions (molecules with unpaired electrons, e.g. spin probes or ions of rare earth elements). The underlying relaxation mechanisms, e.g. by paramagnetic ions, are fairly well understood and are found in relevant monographs and text books (Solomon-Bloembergen equation).
Physical description of the relaxation effect is more difficult in the case of particular aotive substances, da~~~i~:~~~ a s especially when these are not homogeneously distributed.
Influence on T2 time is predominant with ferric/ferromagnetic iron oxide particles. This may result in signal boosting up to complete signal extinction, depending on the given concentration of iron oxide particles and the chosen pulse sequence. Normally, relaxation-time-shortening properties of MR contrast media are expressed by relaxivity. Good -molecularly dissolved - paramagnetic substances have values of apex. 4 1/mmol ~ s (Gd-DTPA) for T2 and T2 relaxivity at 20 0.47 T in water and 40 °C. The dispersions of superparamagnetic magnetite or maghemite are appx. 20 - 40 for the T2 and apex. 200 for the T2 relaxivity. Size, coating, the amount of gamma-Fe2 03 and the degree of the recuperation of crystalline fault sites contribute to the 25 individual value.
Pure magnetic iron oxide particles which could possibly be used as diagnostic agents in nuclear magnetic resonance imaging aggregate in aqueous solution with neutral pH and do 20 not form a stable and parenterally injectable sol. The balance of forces among the particles can be so shifted by coating the magnet core with appropriate substance that the thermal energy (Brownian motion) counteracts the aggregation and sedimentation and a stable gel can be obtained. A number 25 of substances which can be used in this manner are known from the literature and patents.
The coating must provide for a stable suspension. Heat sterilization and/or sterile preparation should be possible 30 in the context of a galenic formulation. In addition, the particles must be of medical diagnostic and/or therapeutic value. Moreover, they must be pharmacologically and toxicologically safe. Most of the coating substances fail to fulfill these criteria.

'; ~_:'~.>,~' °~ °,~
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So far dextran encapsulated iron oxides are the furthest developed of all the ferrimagnetic nanoparticles mentioned.
Clinical development has been cancelled in the US due to side effects (e. g. drop in blood pressure) (G. L. Wolf "Current status of I~R imaging contrast agents: special report", Radiology 172, 709-710 (1989)). These dextran magnetites are currently being thoroughly tested by the FDA (Food and Drug Administration) (Diagnostic Imaging, October 1990). Dextran magnetites are instable against mixtures with common solvents. Galenic stability in physialogical NaCl solution cannot be maintained either aver extended periods of time.
Derivatization is limited or only possible under drastic conditions. Physiologically, dextran has an adverse allergic potential: the same being true for protein coated magnetites.
The medical diagnostic usefulness of coated ferric/
ferromagnetic (superparamagnetic) iron oxide particles (parent substance) is based on the fact that, following intravenous injection, they are taken up by phagocytizing monocytes and macrophages of the reticuloendothelial system (RES) of the clinically intact splenic and hepatic tissue but are not taken up by tumors and metastases. With normal spin-echo sequences such locally differentiated uptake leads to signal extinction in the magnetic resonance image of the clinically intact splenic and hepatic tissue shortly after parenteral application. Whereas tumors and metastases in liver and spleen appear bright against dark background. A
similar effect is also found in tumors and metastases in the lymphatic system.
Presently, efforts are being made to avoid singular uptake of liposomes and other particular drug carriers via mononuclear phagocytizing cells (RES). This is important for selective enrichment of tumors/tissues in diagnostics and therapy.

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<. - ' ~_J .. b a..D ,a~
The therapeutic benefit of the aforesaid iron oxide particles is based on the applicability of iron preparations as anti-anemic drugs as well as in magnetic targeting, a possibility of targeted transport of iron oxide particles and adhering substances to the site of action by means of external magnetic fields. Recoil-free sensitization by gamma rays and intracellular H-field coupled hyperthermia are additional applications of the iron oxide particles. Resonant nuclear absorption of gamma quanta with subsequent re-emission or emission of Auger electrons is referred to as the M~ssbauer effect after its discoverer. Utilization of this effect in radiotherapy was described by Mills et a1. (Nature 335, 787 -789, 1988).
In contrast to the iron oxide sots described herein, Mills uses molecularly dissolved substances which in solution show only a negligible recoil-free M~ssbauer effect and consequently a resonance strengthened radiotherapeutic benefit. The advantages of resonant nuclear absorption of gamma-quanta with subsequent re-emission or emission of Auger electrons are obvious. The primary radioactive source is outside of the body and the non-radioactive sensor is introduced to the tumor tissue. Absorption of gamma quanta by the non-radioactive radiation sensors without significant stress on the surrounding tissue is the primary result which is attributable to the large capture cross section of the resonant core absorption. These radiation sensors (antennae) can be placed in the tumor tissue (preferably intracellularly). The radioactive source (transmitter) and the receiver are tuned to each other and must satisfy physical and radiobiological criteria. On the receiving end 57Fe, 99Ru, 119Sn, 121Sb, 127I, 151Eu, and 157Gd are preferred possible substances, all of which are not radioactive. Ferrites and magnetites can be doped with the ~,' ~:: J?~ a.a ,a aforesaid Mossbauer isotopes without significant impact on physical properties.
Further use of ferromagnetic materials is based on the assumption that magnetic materials can be introduced into the tumor in the farm of small particles and externally heated by coupling of electromagnetic alternating fields through eddy current, hysteresis losses in the course of magnetic reorientation. Controllable energy uptake is possible through choice of the Curie point (Curie temperature) based on the composition of the magnetic particles (cf. Lilly et al., Radiology 154, 243-244 (1985)). In either case, particles with dimensions larger than each of the single domains should be used for energy uptake. Here, a compromise will have to be made between the physically necessary and pharmacologically tolerable particle dimension, depending on the mode of application. However, based on electron microscopic images of tissue sections the conclusion may be drawn that nanocrystalline particles also tend to aggregate into larger complexes following intracellular uptake so that these nanocrystalline particles may also be considered for this application. Moreover, initial measurements on phantoms indicate that there are also physical mechanisms which can lead to heating of single domain particles.
Another possible approach to therapy can be taken by insertion of 157Gd into ferrites and accomplishing neutron activation for thermal and epithermal neutrons taking advantage of the large capture cross section of 157Gd. As in resonant nuclear absorption through photons (Mossbauer) described above, tissue containing no 157Gd will scarcely take up neutrons and consequently will not be detrimentally affected. Neutron uptake is primarily concentrated on the areas containing 157Gd. Hence, sufficient enrichment of the tumor provided, radiation damage is inflicted only an the 1~
tumour by secondary radiation (Auger electrons and photons). The particles must be doped with the appropriate isotopes for application of ferrite/magnetite in therapy. The degree of doping of ferrite/magnetite as well as size, charge, hydrophobicity and possibly targeting should be adjusted to the purpose of the therapy. Macrophages are known to take up iron oxide particles and other foreign substances and to undergo concentration on the periphery of tumours. It is also possible to concentrate substances in specific tumours by attaching them to monoclonal antibodies. This enables targeting of radiation in order to inhibit the tumour growth and/or perform therapeutic hyperthermia.
In addition, a positive contribution can be made to synovectomy through extracorporeal and/or intracorporeal radiation sensitization. Moreover, even slight accumulation of macrophages containing iron oxide in the vicinity of a tumour can be used for tumour detection by means of highly sensitive magnetic field probes (SQUIDs).
(d) DESCRIPTION OF THE INVENTION
It is the aim of this invention to minimize or even to overcome the above described disadvantages of the known state of the art. Specifically, it is an object of a main aspect of this invention to provide, with an acceptable input in terms of synthesis technique, multiply modifiable and thus variably applicable, pharmacologically and toxicologically safe magnetic particles which can be prepared under thermally sterilized and aseptic conditions.
Surprisingly, the attempt to meet the catalogue of pharmaceutical demands for medical use has been successful owing to glycosaminoglycan coated magnetites.
The present invention in one broad aspect, now provides nanocrystalline magnetic particles consisting of a magnetic iron oxide core of Fe304, gamma-Fe203 or mixtures thereof and a chemisorbed coating on this core, the composition of such coating material comprising natural or synthetic glycosaminoglycans and/or derivatives thereof with molecular weights of 500 Da to 250,000 Da combined.
By one variant of this broad aspect of the invention, the coating material is covalently cross-linked by appropriate cross-linking agents and/or is modified by specific additives.

By another variant of this broad aspect of the invention, or of the above-described variant thereof, the particles have core diameters which are smaller than the dimensions of the magnetic singular domains.
By yet another variant of this broad aspect of the invention, or of the above-described variants thereof, the particles are also provided with common pharmaceutical adjuvants for injectable solutions and/or enteral agents as stable aqueous colloid dispersive solutions which are 0.2 ~cm filterable. By one specific variation thereof, the magnetic particles can be heat sterilized.
By yet a further variant of this broad aspect of the invention, or of the above-described variants thereof, the iron oxide core is doped with 6Li, 5'Fe, 6'Ni, Ni, 6'Zn, Zn, Mn, ~Ru, ioiRu m3Cd~ n9sn~ izisb~ iz~I~ isiEu~ issGd~ is6Gd, or ls'Gd.
By yet still another variant of this broad aspect of the invention, or of the above-described variants thereof, the natural or synthetic glycosaminoglycans are chondroitin sulphate, dermatan sulphate, or heparin or synthetic analogues thereof, or other heparinoids.
By a still further variant of this broad aspect of the invention, or of the above-described variants thereof, the coating material, after preparation of enveloped magnetic iron oxide particles, is additionally cross-linked by cross-linkers which are common in biochemistry and chemistry of natural products.
By another variant of this broad aspect of the invention, or of the above-described variants thereof, the glycosaminoglycan is heparan sulphate or a synthetic analog thereof;
or the glycosaminoglycan is hyaluronic acid, or a synthetic analog thereof.
By a further variant of this broad aspect of the invention, or of the above-described variants thereof, the mono-, di-, tri-, and oligoamines and/or synthetic and biological oligopeptides/proteins are bonded to the coating material.
By yet a further variant of this broad aspect of the invention, or of the above-described variants thereof, the reduced or oxidized glutathione is bonded, as well as intraparticularly reversibly cross-linked to, the coating material.

By a still further variant of this broad aspect of the invention, or of the above-described variants thereof, the surface-active substances are bonded to the coating material.
By another variant of this broad aspect of the invention, or of the above-described variants thereof, the targetable structure substances are bonded to the coating material.
By one specific variation thereof, the targetable structure substances comprise hormones, cholesterol, lipids, ether lipids, proteins, monoclonal antibodies, lectins, tumour lectins, adhesion proteins, fusion proteins, transport proteins and transport units, alkaline proteins, e.g., histones, interleukins, lipoproteins, for example, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, residual glycosyl or general sugar residues which play a role in complement and immune recognition as well as ribonucleic or deoxyribonucleic acids or their fragments or structural elements or mixtures thereof. By another specific variation thereof, the magnetic particles include additional chemotherapeutic agents, e.g., cytostatic agents.
By a still further variant of this broad aspect of the invention, or of the above-described variants thereof, the cross-linking or bonding of targetable structures and/or surface-active substances are combined.
By yet a still further variant of this broad aspect of the invention, or of the above-described variants thereof, the magnetic particles are surrounded by cage molecules. By a specific variation thereof, the cage molecules comprise subunits of clathrin and/or synthetic analogues.
As described above, the chondroitin magnetites, according to aspects of the present invention, can be classified as physiologically safe. Chondroitin is considered a glycosaminoglycan and is of animal or human origin. It is of ubiquitous presence in the body and has numerous medical applications. The iron oxide core presents no difficulties, as long as it is properly shielded by coating material. After intracellular dissolution of the iron oxide core, the liberated iron is incorporated in the endogenous iron pool. Chondroitin magnetites exhibit extremely good tolerance following heat sterilization with LDso values of 20 mmol/kg (rat and mouse). Well-defined imaging of tumours/metastases has been obtained even from doses as low as 10 ~,mol/kg.
This has provided an almost unprecedented safety margin of 2000. Furthermore, glycosaminoglycans are characterized by high hydrolytic stability of the glycosidic bond.
The entire range of demands can be met by these glycosaminoglycan-coated magnetic iron oxide particles: homogeneous iron oxide core; chemical stability of the coating material with well-known positive activity spectrum; preparation of nanocrysalline magnetic particles under non-invasive conditions; expansion of synthesis according to the modular principle (starting from a basic body, specific task oriented modifications can be added), high efficiency of diagnostic and therapeutic action; good tolerance, no significant side effects, no necessary additives to avoid possible side effects;
higher margin of safety (factor 2000 as MR tumour/metastases diagnostic agent);
continued galenic stability even after adjustment of the isotonic value with salt and after heat sterilization in the final receptacle; and low number of decomposition products after extended storage. On the other hand, dextran magnetite, protein magnetite, gum arabic gelatin magnetite or magnetite with synthetic coating materials can only partially satisfy such catalogue of demands. According to aspects of this invention, if the particles are used in therapy, the magnetic core can be doped with 6Li, s'Fe, 6lNi, Ni, 6'Zn, Zn, Mn, 99Ru~ ioiRu u3Cd~ u9sn~ iaisb~ ia~I~ ~siEu~ issGd~ is6Gd~ or ls~Gd.
Especially preferred variants of the magnetic particles are, according to various aspects of this invention, characterized by the following features:
a) the core consists of magnetic iron oxide with core diameters which are smaller than the dimension of the individual magnetic domains; and/or b) they are available with the common pharmaceutical adjuvants for injectable solutions and/or enteral agents as stable aqueous colloid dispersion solutions which are 0.2 ~,m filterable and can be thermally sterilized; and/or c) the core, if doped, is preferably doped with 6Li, s'Fe, 6'Ni, 'SIEu, 'S'Gd;
and/or d) the natural or synthetic glycosaminoglycans are chondroitin sulphates, dermatan sulphates, heparan sulphates, heparin or their synthetic analogues, or other heparinoids; and/or e) the coating material, after the preparation of the coated magnetic iron oxide particles, is additionally cross-linked by cross-linking agents which are common in biochemistry and the chemistry of natural substances; and/or f) mono- di-, tri-, and oligoamines and/or synthetic and biological oligopeptides and proteins are bonded to the coating material; and/or g) reduced or oxidized glutathione is bonded to the coating material and is cross-linked with intraparticular reversibility; and/or h) surface-active substances are bonded to the coating material; and/or i) targetable structure substances, preferably hormones, cholesterol, lipids, ether lipids, proteins, monoclonal antibodies, lectins, tumour lectins, adhesion proteins, fusion proteins, transport proteins and transport units, alkaline proteins, e.
g. , histones, interleukins, lipoproteins, for example, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, residual glycosyl or general sugar residues which play a role in complement and immune recognition as well as ribonucleic or deoxyribonucleic acid or their fragments or structural elements or mixtures thereof, if necessary with the addition of chemotherapeutic agents, preferably cytostatic agents, are bonded to the coating material;
and/or j) cross-linking, or bonding of targetable structures and/or surface-active substances can be combined as desired; and/or k) they are surrounded by cage molecules, preferably consisting of subunits of clathrins and/or synthetic analogues.
By another aspect of this invention, a process is provided for the preparation of nanocrystalline magnetic particles consisting of a magnetic iron oxide core of Fe304, gamma-Fez03 or mixtures thereof and an envelope chemisorbed to the core, the process comprising the steps of synthesizing iron oxide cores, and enveloping the iron oxide cores, under biometric conditions, with a composition comprising natural or synthetic glycosaminoglycans and/or derivatives thereof with molecular weights of 500 Da to 250,000 Da combined.
By one variant of this broad process aspect of this invention, free functional groups of the coating material are activated and intraparticularly cross-linked by adding a cross-linking agent, and modifying the cross-linked coating by the addition of surface-active substances, or targetable structure substances.
By another variant of this broad process aspect of this invention, or of the above variant thereof, the process includes the step of adding chemotherapeutic agents and/or 5 residual low-molecular weight residues.
By another variant of this broad process aspect of this invention, or of the above variants thereof, natural or synthetic glycosaminoglycans or their derivatives which are used as a coating substance, comprises chondroitin sulphate, dermatan sulphate, heparin sulphate or synthetic analogues thereof, hyaluronic acid or synthetic analogues thereof, 10 or heparin or synthetic analogues.
By yet another variant of this broad process aspect of this invention, or of the above variants thereof, the process includes the step of activating functional groups of the coating material of the magnetite stock solution by means of water-soluble carbodiimide derivatives, or in a two-phase system by lipophilic carbodiimides, and 15 subsequently purifying and isolating the activated magnetite. By one specific variation thereof, the process includes the step of adding bifunctional cross-linking agents which are common in biochemistry and chemistry of natural products and/or adding mono-, di-, tri-, and oligoamines, synthetic or biological oligopeptides, or reduced or oxidized glutathione to the activated magnetite solution, then non-invasively separating non-reacted educt by dialysis and finally adjusting magnetite with its hydrophilia altered and/or cross-linked to the desired final concentration. By another specific variation thereof, the process includes the step of adding and admixing surface-active substances to the activated magnetite solution. By a further specific variation thereof, the process includes the step of adding targetable structure substances to the activated magnetite solution. By a variation of that further specific variation, the targetable structure substances comprise hormones, cholesterol, lipids, tumour lectins, adhesion proteins, fusion proteins, transport proteins and transport units, alkaline proteins, e.g., histones, interleukins, lipoproteins, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, residual glycosyl or general sugar residues which play a role in complement and immune recognition as well as ribonucleic or deoxyribonucleic acids or their fragments or structural elements as well as mixtures thereof. By still another variation of that further specific variation, the process includes the step of admixing chemotherapeutic agents to the magnetite solution or to the magnetite. By yet a further variation thereof, the process includes the step of admixing and adding lower molecular weight residues which influence the physiological distribution pattern of the particles to the activated magnetite solution. By a specific further variation thereof, the process includes the step of adding clathrin to the activated magnetite solution.
Especially preferred variants of the process of this aspect of this invention are characterized by the following features:
a) natural or synthetic glycosaminoglycans or derivatives thereof, preferably chondroitin sulphates, dermatan sulphates, heparan sulphates, heparin or synthetic analogues thereof which are used as coating substances; and/or b) the functional groups of the coating material of the magnetite stock solution are activated with water-soluble carbodiimide derivatives or in a two-phase system with lipophilic carbodiimides, and thereafter the activated magnetite is purified and isolated; and/or c) bifunctional cross-linking agents which are common in biochemistry and in the chemistry of natural products and/or mono-, di-, tri-, and oligoamines, synthetic or biological oligopeptides, or reduced or oxidized glutathione are added to the activated magnetite solution, with non-reacted educts being non-invasively separated by dialysis and the magnetite cross-linked and/or with its hydrophilia altered is then adjusted to its desired final concentration; and/or d) surface-active substances are admixed and added to the activated magnetite solution; and/or e) the activated magnetite solution which are added thereto are targetable structure substances, preferably hormones, cholesterol, lipids, tumour lectins, adhesion proteins, fusion proteins, transport proteins, or transport units, alkaline proteins, e.g., histones, interleukins, lipoproteins, for example, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, compounds which contain residual sugar, which plays a role in complement and immune recognition, as well as ribonucleic or deoxyribonucleic acids, as well as fragments or structural elements thereof, or a mixture thereof; and/or f) chemotherapeutic agents are admixed to the activated magnetite solution, or are added to the magnetite; and/or g) lower molecular weight substances affecting the physiological distribution pattern of the particles are admixed and added to the activated magnetite solution, and/or h) clathrin is admixed to the activated magnetite solution.
Furthermore, by another broad aspect, the invention also provides diagnostic and/or therapeutic agents comprising isotope-doped iron oxide cores of Fe304, gamma Fe203 or their mixtures, which are surrounded by a biodegradable coating of natural or synthetic glycosaminoglycans and/or derivatives thereof with molecular weights between 500 - 250,000 Da.
By one variant of this broad aspect of the invention, the coating material is covalently cross-linked by appropriate cross-linking agents and/or is modified by specific additives.
By another variant of this broad aspect of the invention, or of the above-described variant thereof, the particles have core diameters which are smaller than the dimensions of the magnetic singular domains.
By yet another variant of this broad aspect of the invention, or of the above described variants thereof, the particles are also provided with common pharmaceutical adjuvants for injectable solutions and/or enteral agents as stable aqueous colloid dispersive solutions which are 0.2 ~.m filterable. By one specific variation thereof, the magnetic particles can be heat sterilized.
By yet a further variant of this broad aspect of the invention, or of the above described variants thereof, the iron oxide core is doped with 6Li, 5'Fe, 6'Ni, Ni, 6'Zn, Zn, Mn, ~Ru, ioiRu nsCd~ u9sn~ izisb~ i2~I~ isiEu~ issGd~ is6Gd, or ls'Gd.
By yet still another variant of this broad aspect of the invention, or of the above-described variants thereof, the natural or synthetic glycosaminoglycans are chondroitin sulphate, dermatan sulphate, or heparin or synthetic analogues thereof, or other heparinoids.

Ig By a still further variant of this broad aspect of the invention, or of the above-described variants thereof, the coating material after preparation of enveloped magnetic iron oxide particles, is additionally cross-linked by cross-linkers common in biochemistry and chemistry of natural products.
By another variant of this broad aspect of the invention, or of the above-described variants thereof, the glycosaminoglycan is heparan sulphate or a synthetic analog thereof, or the glycosaminoglycan is hyaluronic acid or a synthetic analog thereof.
By a further variant of this broad aspect of the invention, or of the above-described variants thereof, the mono-, di-, tri-, and oligoamines and/or synthetic or biological oligopeptides/proteins are bonded to the coating material.
By yet a further variant of this broad aspect of the invention, or of the above-described variants thereof, the reduced or oxidized glutathione is bonded, as well as intraparticularly reversibly cross-linked to, the coating material.
By a still further variant of this broad aspect of the invention, or of the above-described variants thereof, the surface-active substances are bonded to the coating material.
By another variant of this broad aspect of the invention, or of the above-described variants thereof, the targetable structure substances are bonded to the coating material.
By one specific variation thereof, the targetable structure substances comprise of hormones, cholesterol, lipids, ether lipids, proteins, monoclonal antibodies, lectins, tumour lectins, adhesion proteins, fusion proteins, transport proteins or transport units, alkaline proteins, e.g., histones, interleukins, lipoproteins, for example, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, residual glycosyl or general sugar residues which play a role in complement and immune recognition as well as ribonucleic or deoxyribonucleic acids or their fragments or structural elements or mixtures thereof. By another specific variation thereof, the magnetic particles include additional chemotherapeutic agents, e.g., cytostatic agents.
By a still further variant of this broad aspect of the invention, or of the above-described variants thereof, the cross-linking or bonding of targetable structures and/or surface-active substances are combined.

By yet a still further variant of this broad aspect of the invention, or of the above-described variants thereof, the magnetic particles are surrounded by cage molecules. By a specific variation thereof, the cage molecules comprise subunits of clathrin and/or synthetic analogues.
Especially preferred variants of the diagnostic and/or therapeutic agents, according to aspects of this invention, are characterized by the following features:
a) the core, if doped, is preferably doped with 6Li, 5'Fe, 6'Ni, 'S'Eu, 'S'Gd;
and/or b) the natural or synthetic glycosaminoglycans are chondroitin sulphates, dermatan sulphates, heparan sulphates, heparin or their synthetic analogues which are cross linked with bifunctional cross-linking agents which are common in biochemistry and the chemistry of natural products and/or are cross-linked with mono-, di-, tri-, and oligoamines, synthetic and biological oligopeptides, reduced or oxidized glutathione; and/or c) surface-active substances are bonded to the cross-linked coating; and/or d) the cross-linked coating which are bonded thereto are targetable structure substances, preferably hormones, cholesterol, lipids, ether lipids, proteins, monoclonal antibodies, lectins, tumour lectins, adhesion proteins, fusion proteins, transport proteins, transport units, alkaline proteins, e.g., histones, interleukins, lipoproteins, for example, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, compounds which contain residual sugar which plays a role in complement and immune recognition as well as ribonucleic or deoxyribonucleic acids as well as fragments or structural elements thereof or mixtures thereof, if necessary, with addition of chemotherapeutic agents, preferably cytostatics; and/or e) subunits of clathrin surround the enveloped particles in cage form; and/or f) the magnetic particles are incorporated in liposomes, chylomicrons, cells, cell organelles bacterial, virus shells and are surrounded by lipids in the form of a double layer.
The invention in another aspect provides the use of the diagnostics and/or therapeutic agents as described generically, sub-generically and specifically hereinabove in the preparation of diagnostic and/or therapeutic agents for radiotherapy, hyperthermia, chemotherapy and MR diagnosis as well as biomagnetic probes.
In contrast to the particles of the present state of the art, the nanocrystalline particles according to aspects of this invention described herein are constructed according 5 to the modular principle. Based on a parent substance which consists of a magnetic iron oxide core and an envelope of, for example, glycosaminoglycan, they can be modified in solution according to the purpose of application.
Such modifications can be achieved by covalent or non-covalent adding, activation and/or cross-linking as well as by combinations thereof. It has proven helpful first to 10 cross-link the coating material in vitro before coupling the targetable structures.
Coupling of targetable structures without prior cross-linkage might cause destabilization of the magnetic particles. The parent substance can thus be supplemented with targetable structures and the addition of chemotherapeutic agents for application to selective tumour diagnostics/therapy. In addition, there are many possibilities to modify the parent 15 substance itself. This diversity is associated with a wide spectrum of applications. One can differentiate between the parent substance which is identified and taken up by the reticuloendothelial system (RES) due to its particular nature, and serves, for example, MRI contrasting of liver and spleen tumours (metastases). Targeting of other organs/tissues can be achieved after parenteral administration by extending retention in 20 the blood stream, acceleration of the extravasation and organ or tissue selection by attachment of targetable structures. Uptake by the RES is perceived as a reaction parallel to the reaction with the target organ and can be influenced by size, charge, surface, hydrophobia and pre-saturation of the RES.
The chemisorbed coating substances used are biodegradable substances of animal/human origin which are capable of stabilizing the iron oxohydroxy complex and of ensuring a synthesis of the coated iron oxide under biomimetic conditions.
Precipitation of the iron oxide at alkaline level can thus be avoided. The stock sots can be prepared from blood isotones, for example, by the addition of mannitol and stable NaCI. The size of the emerging particles can be controlled during synthesis, for example, by proper choice of the chondroitin/iron ratio, and must not be adjusted to a fixed value by fractionation procedures.
No organic solvents are used in the preparation process according to aspects of this invention. In contrast to dextran magnetites, particle stability is guaranteed in several organic solvents. The substances are useful in many diagnostic and therapeutic areas. Chemical bonding of coating molecules to the iron oxide core, as described in the European patent application (publication number 0284549), is avoided in order to guarantee the biological degradability. The animal/human origin of the coating material is reflected in good tolerance. "Pro drug" forms and coating substances with pH
dependent fracture sites can also be produced.
The envelope of glycosaminoglycan with carboxylic acid groups ensures solid chemisorption to the iron oxide core (and with the sulphuric acid and the residual N-acetyl also provides for the sufficient stability of the sol). The iron oxide core in this context is sufficiently shielded so that, in contrast to the majority of the conventional formulations, physiological incompatibilities with parenteral application are adequately compensated.
Possible coating materials are water-soluble glycosaminoglycans, e. g. , chondroitin sulphates, keratin sulphates, dermatan sulphates, heparin, hyaluronic acid, heparan sulphates or synthetic analogues. (Hyaluronic acid is often considered as one of the four primary representatives of glycosaminoglycans [mucopolysaccharide polysulphuric acid esters] as mentioned before). Hyaluronic acid differs from chondroitin sulphate, keratin sulphate, dermatan sulphate and heparan (heparin) sulphate in that it does not contain any residual sulphuric acid and is itself not protein conjugated, but it promotes the proteoglycan aggregation. Glycosaminoglycans together with connecting tissue proteins form the ubiquitously present proteoglycans.
In the context of conventional wet chemical procedures of magnetite preparation, acid Fe(II) : Fe(III) solutions are adjusted at increased temperature to a pH
value at an alkaline level by adding lye (e.g. NaOH,) or NH40H. The forming magnetite precipitates in the presence of the coating agent and entrains it, or the coating agent is added after formation of the magnetites. In some cases, ultrasound is applied during magnetite synthesis and leads to reduction in size of the forming particles (see, Menz et al. WO 90/295). The subsequent steps include peptization, neutralization, purification, addition of stabilizers as well as filling and heat sterilization, if possible, in the final receptacle.
While these processes which differ slightly from each other by initial concentrations, reaction temperatures, rates of adding, choice of the coating agent and the processing steps, the processes described here result in formation of glycosaminoglycan-coated magnetites in a neutral medium (pH7) and in ambient temperatures. Also, ultrasonic treatment is unnecessary. The pH value can be held constantly neutral in a chemostat. The alkaline range in which many coating agents and biological materials are hydrolytically instable can be avoided. This proves to be a significant advantage, since the number of possible decomposition products can thus be kept low.
According to broad aspects of this invention, the glycosaminoglycans of the magnetites provide for almost complete shielding of the surface, so that specific interactions are minimized or avoided. Extensive hydrate coating is under discussion for erythrocytes as a result of the poly-N-acetyl-lactosamines (J. Vitala and J.
Jarnefelt, TIBS, October 1985, 392-395). It appears to be important for macrophage uptake of the parent substance that the coating surrounding the core does not cause any specific reactions, yet can still be activated by the immune system so that the opsonized particles are taken up by the macrophages. Choice and derivation of the coating (charge and hydrophobia) in addition to size, offer a possibility, for other purposes, passively to influence extracelluar interaction of the magnetites. Moreover, direct drug targeting is possible by attachment of specific recognition tags (e.g., monoclonal antibodies, hormones, guide proteins). Similar to the wide range of liposome applications, the interactions of parenterally applied particles so far have only been phenomenologically understood and are a current field of biochemical, pharmacological and medical research.
According to broad aspects of this invention, the described magnetic iron oxide particles which (with or without additional doping) together with a coating of glycosaminoglycan and the derivatives thereof or the synthetic analogous substances provide the advantage that the coating materials are biodegradable products.
Iron is liberated from the iron oxide following the intracellular uptake and is incorporated into the iron pool (haemoglobin, iron storage proteins). The normal iron pool of an adult is increased only insignificantly by one single application of 10-30 ,u mol/kg body weight, a dose which is normally sufficient for diagnostic MR tomography. Extreme pH
values can be avoided with the underlying synthesis, except for dissolution of the salts of iron so that the susceptibility to hydrolysis and/or pH induced chemical modification of the coating material is of minor importance.
Iron oxide particles which are dissolved in water with a coating of glycosaminoglycan represent the stock solution. The physical and pharmacological parameters of the particles can be influenced in situ by attaching lower and higher molecular substances/ligands/guide structures and by cross-linking as well as inclusion in and addition to cells or cell components, as described in the following examples. This actually enables adaptation to specific diagnostic and/or therapeutic problems. The approach has been so chosen that the pre made magnetites (made according to Example 1 or 2 hereinafter), are transformed by activation of reactive groups into a form which allows coupling in a physiologically acceptable form to the appropriate ligands/spacers/substrates/targetable structures.
(e) DESCRIPTION OF THE FIGURES
In the accompanying drawings:
FIG. 1 is an MR image, namely an axial slice of a mouse liver before (baseline) and 1, 10, and 30 minutes after application of 10 ~. mol/kg of chondroitin magnetite (chondroitin-4-sulphate) prepared according to Example 1;
FIG. 2 is a graph of the relative intensity (MRI liver signal/MRI reference signal) in percent of the baseline value following intravenous administration of 20 ~, mol/kg chondroitin magnetite as ordinate as a function of time as abscissa;
FIG. 3 is a graph of the relative intensity (MRI liver signal/MRI reference signal) 24 h after intravenous administration of chondroitin magnetite (prepared according to Example 1) with Sl (liver/reference) as ordinate;

FIG. 4 is an X-ray diffractogram of a lyphophilized transferrin magnetite conjugate prepared by periodate activation of chondroitin-4-sulphate-magnetite and subsequent coupling to transferrin; and FIG. 5 is an electron microscopic representation of the transferrin magnetite conjugate.
(f7 AT LEAST ONE MODE FOR CARRYING OUT THE INVENTION
Example 1: (Conventional Synthesis) 18.24 gm chondroitin-4-sulphate (Sigma Type A) is dissolved under heat in 400 ml of distilled water and gassed with nitrogen. 20.6 gm of Fe(II) chloride are dissolved under nitrogen in 210 ml of 1 M Fe(III) chloride solution. The freshly prepared Fe (II)/Fe(III) solution is slowly added drop-wise ( .: 0.5 ml/min) under nitrogen rinse to the 75°C chondroitin sulphate solution so that the precipitate formed at the point of dripping is immediately dissolved. Then, previously degassed 3N NaOH solution is slowly added. The solution is then titrated to pH 10. Immediately thereafter, it is neutralized and boiled for 3 h on the reflux side and is continuously regulated in the process to pH 7. After cooling to room temperature and centrifuging (10 min., RPM) the supernatant solution is diafiltered with 10 1 distilled water over a 3 kDa hollow fibre cartridge and is then reduced in a rotary evaporator to a volume of 250 ma.
The pH value is adjusted to 7. After 0.2 ~,m filtration the ready-to-use solution is autoclaved at 121°C. The yield amounts to 100% relative to the employed iron.
The data of the chondroitin-4-sulphate prepared according to this example is shown hereinbelow in Table 1:
Table 1: Data of chondroitin magnetite (chondroitin-4-sulphate) prepared according to Example 1.
Size: 52 nm (with laser light diffraction) Relaxivity: Tl 401/mmolOs TZ 1201/mmolOs Fe concentration: 0.33 M

Acute tolerance LDSO (mouse) 25 mmol/kg Half life in blood 4.4 min.
(with a dosage of 100 ~, mol/kg in rat) Example 2: (Biomimetic Synthesis) 5.0 gm chondroitin-4-sulphate are dissolved in 200 ma iron III hydroxide sol, corresponding to 6.6 mM Fe (see Jander/Blasius, Lehrbuch dr analytischen and praparativen anorganischen Chemie, S. Hirzel Verlag, Stuttgart). Possible cloudiness is 10 filtered off. A nearly neutralized solution of 1.282 gm ammonium iron(II) sulphate hexahydrate is added dropwise to the solution heated to 37°C, with the pH slowly drifting towards acidic being readjusted with diluted lye to physiological pH
values. The completed magnetite is purified and autoclaved, which provides for accelerated recuperation of possible fault positions of the magnetite crystals.
Example 3: (Doping The procedure was the same as in Example I, except that 5 % of the employed Fe(II) is replaced by 6'Ni as a Mossbauer active isotope for use in the resonant nuclear absorption therapy. 19.57 gm FeCl2 and 1.05 gm 6lNiClZ are to be used instead of the 20.6 gm FeCl2.
Example 4: (Desulphatizingyto Chan a tg he Hydrophilic) 10 ml chondroitin sulphate magnetite according to Example 2 are eluted over a DOWEXTM cation exchanger and are neutralized with appx. 7.5 ml pyridine. The pyridinium salt of chondroitin sulphate magnetite is obtained following lyophilization.
The salt is dissolved in DMSO/ethanol or DMSO/H20 and is maintained at 80 °C for 5 h. After cooling the solution is diluted with water and is adjusted with NaOH
to pH 9-9.5. This adjusted dispersion of desulphated chondroitin magnetite is dialysed against water, ultrafiltered ( 10 kDa) and filtrated under sterile conditions.

Example 5: (Activation of Free Carboxylic Acids) 1 ml chondroitin-4-sulphate magnetite according to Example 2 is diluted 1:10 in distilled water and the pH value is adjusted to 4.5 with HCI. Water-soluble carbodiimide [1-ethyl-3(3-dimethylaminopropyl)-carbodiimide-HCl (EDC.Pierce)] is added under agitation in 1.5-fold surplus quantity (compared to the functional groups to be activated) and the pH value is held constant at 4.5 (1h at 4°C). On completion of reaction, the non-reacted educt is carefully separated by dialysis from the activated magnetite and the substance retained is lyophilized.
The EDC reaction will have to be modified if consequent reactions are to be initiated with the EDC-activated magnetite (e.g. coupling to biogenic ligands) which are not stable at pH 4-5 or would lose biological activity. N-hydroxysulphosuccinimide (Sulfo-NHS, Pierce) must be added to the chondroitin magnetite or the reaction mixture of chondroitin magnetite and ligand and/or cross-linker for the coupling-cross-linking under physiological conditions or in the course of a biomimetic synthesis in order to enhance the stability of the intermediate product at physiological pH values and thus to increase yield and ensure biological activity. A stable intermediate product is obtained by adding sulfo-NHS (see Staros et al., Analytical Biochemistry 156, 220-222, 1986) in contrast to EDC reaction without sulfo-NHS additive where an O-acyl-urea derivative is intermediately formed which requires acidic reaction conditions and is sensitive to hydrolysis. The additional reagent has no influence on the final product. An amide bond is also produced in response to addition of an aminic ligand, and the lower molecular weight reagent is removed from the colloidal solution by dialysis of the ultrafiltration, following mediated condensation between acid and amine components.
Example 6: (Desulphatized EDC) 10 ml desulphatized chondroitin magnetite, prepared according to Example 4, are converted with EDC according to Example 5. This results in activated magnetites which, due to reaction with the acid group of the coating material, is negatively charged or neutral depending on EDC content.

Example 7: (Condensation with Glucosamine) Magnetite solutions, according to Example 5 are mixed with a 1.5-fold surplus quantity of glucosamine. An amide bond results from the condensation reaction between EDC activated carboxylic acid and glucosamine. The resulting magnetite, which has undergone change in hydrophilia, is dialysed against distilled water and adjusted to the desired concentration.
Example 8: (Cross-linking with Ethylenediamine) The procedure was as in Example 7, but bifunctional ethylenediamine is added instead of glucosamine. In order to avoid interparticular cross-linking, the latter is done at lower magnetite concentrations with these concentrations being increased on completion of cross-linkage.
Example 9: (Transferrin Coupling, 10 ml magnetite solution, according to Example 5, with pH adjusted to 7.4, are mixed with 10 ma (10-20 mg/ml) human transferrin which had been transformed into biologically active Fe(III) transferrin using an appx. 10-fold molar surplus of iron (II) in a phosphate citrate buffer. The mixture is agitated for 6 h at 4°C, with the pH value being maintained at the physiological level. This is followed by ultrafiltration at 4°C in order to separate the unbonded transferrin. The chondroitin magnetite which is not cross-linked or bonded with Fe transferrin and the chondroitin magnetite that is bonded with biologically non-active transferrin are separated by CNBr SEPHAROSETM 4 B
(Pharmacia) which had been previously bonded with anti-H-transferrin (see van Ejik and van Noort, J. Clin. Chem. Clin. Biochem., Vol. 14, 475-478, 1976).
This is followed by an assay of content and after adjustment of desired final concentration, by sterile filtration. Yield of iron: transferrin + 1.1 to 5.1 (w/w).
Storage is at 4 °C, with the stability relative to native transferrin being significantly improved, as is known for immobilized proteins. Other targetable structures, e.g., monoclonal antibodies and/or cytostatic agents, can be coupled to the EDC
activated magnetite (Example 5), according to the same reaction pattern.

Example 10: (Hydrophobic Ma ng etite) 1 gm chondroitin magnetite lyophilized according to Example 1 is mixed with ma DMSO/acetone and acidified. Dicyclohexylcarbodiimide (a 5-fold surplus quantity relative to carboxylic acid) is subsequently added to the solution and is mixed with the lipophilic amine benzylamine in a 2-fold surplus quantity relative to carboxylic acids.
The result is hydrophobic magnetite. The magnetites are 50 nm in size in ethanol (70nm in water) .
Example 11: (Lipid Double Layer Magnetite) The procedure is the same as in Example 7; however phosphatidylethanolamine (cephalin from egg yolk) is stoichiometrically (relative to EDC group) added as the amine component under N2 and maintained at 4°C for 2 h. The cephalin displaces the EDC
with the ethanolamine head group and bonds to the chondroitin magnetite. A
complete double layer is formed by addition of phosphatidylcholine (lecithin) in a 1.5-fold surplus quantity, relative to the cephalin or by a mixture of lecithin and cholesterol. Change of the solvent (EtOH water mixture) proves to be advantageous during the cephalin formation. The ethanol must be removed to enable formation of the double layer.
Example 12: (Clathrin Ca,.
Clathrin is isolated in monomeric form by well known procedures [see Review B. M. F. Pearse & R. A. Crother, "Structure and Assembly of Coated Vesicles", An.
Rev. Biophys. Biophys. Chem. 16, 49-68 (1987)]. Addition of pre-made magnetites (see Examples 1, 2) in Fe : protein = 1:l to 5:1 ratio (w/w) is followed by condensation of the clathrin monomers to typical clathrin cages by reduction of pH to 6.2 and addition to MgCl2. Magnetites which were not incorporated in the process of condensation and empty clathrin cages are chromatographically separated from bonded cages.
Example 13: (Small Ma neg tites) Preparation of chondroitin magnetite according to Example 2 is so modified that the reaction solution is repumped through a filter cartridge with some of the magnetite particles appearing in the filtrate. In this manner, especially small magnetites are produced which are highly suitable for intravenous lymphography and have a longer half life in blood.
Example 14: (Erythrocyte Inclusion) Erythrocytes are separated from the other blood components in the customary fashion and are mixed with physiological NaCI solution. The premade magnetites are added (0.56 mg/ma Fe to 1 mg/ma protein). The solution is subsequently pressurized with 50 bar nitrous oxide at 37 °C according to Disclosure DE 3812816 Al. Following pressure relief, non-included magnetite is separated by centrifugation. The result is envelopes which have taken up magnetite in a non-erythrocyte process.
As indicated hereinbefore, FIG. 1 is an MR image of an axial slice of a mouse liver before (baseline) and 1, 10, and 30 minutes after application of 10 ~, mol/kg of chondroitin magnetite (chondroitin-4-sulphate), prepared according to Example 1. CSI
GE 2T. Magnetites are taken up by the RES in clinically-intact liver tissue which takes up the magnetites so that the signal is extinguished. Tumour or tumour metastases have no RES and consequently cannot take up magnetite and do not exhibit any variation in signal intensity. The metastases are not visible in the baseline image, but are clearly distinguishable from the intact liver tissue in response to a dosage of as little as 10 ~, mol/kg.
FIG. 2, shows the time dependence in the form of a graph of the kinetics of magnetite degradation in rat liver for chondroitin magnetite prepared according to Example 1 (chondroitin-4-sulphate). Represented is the relative intensity (MRI
liver signal/MRI reference signal) in percent of the baseline value following intravenous administration of 20 ~c mol/kg chondroitin magnetite as a function of time.
FIG. 3, shows the dosage dependence after application in the form of a graph.
Represented is the relative intensity (MRI liver signal/MRI reference signal) 24 h after intravenous administration of chondroitin magnetite (prepared according to Example 1) as a function of the applied dosage.

FIG. 4 shows a powder diffraction system in the form of an X-ray diffractogram of a lyphophilized transferrin magnetite conjugate prepared by periodate activation of chondroitin-4-sulphate-magnetite and subsequent coupling to transferrin. The lines can be labelled cuboid in the manner of a spinet structure. The X-ray diffractogram shows 5 the magnetite structure remains intact even after periodate activation.
FIG. 5 is an electron microscopic representation of the transferrin magnetite conjugate as described for FIG. 4. The magnification is 1 : 300,000. The electron edited magnetite core is clearly visible. No aggregates appear.

Claims (45)

1. Nanocrystalline magnetic particles consisting of a magnetic iron oxide core of Fe3 0 4, gamma-Fe2 0 3 or mixtures thereof, and a chemisorbed coating on said core, wherein the composition of said coating material comprises natural or synthetic glycosaminoglycans and/or derivatives thereof with molecular weights of 500 Da to 250,000 Da combined.
2. The nanocrystalline magnetic particles according to claim 1, wherein said coating material is covalently cross-linked by cross-linking agents and/or is modified by specific additives.
3. Magnetic particles according to claim 1 or claim 2, wherein said particles have core diameters which are smaller than the dimensions of the magnetic singular domains.
4. Magnetic particles according to claims 1 to 3, wherein said particles are provided with common pharmaceutical adjuvants for injectable solutions and/or enteral agents as stable aqueous colloid dispersive solutions which are 0.2 µm filterable.
5. Magnetic particles according to claim 4, which can be heat sterilized.
6. Magnetic particles according to claims 1 to 5, wherein said iron oxide core is doped with 6Li, 57Fe, 61Ni, Ni, 67Zn, Zn, Mn, 99Ru, 101Ru 113Cd, 119Sn, 121Sb, 127I, 151Eu, 155Gd, 156Gd, or 157Gd.
7. Magnetic particles according to claims 1 to 6, wherein said natural or synthetic glycosaminoglycans are chondroitin sulphate, dermatan sulphate, heparin or synthetic analogues thereof, or other heparinoids.
8. Magnetic particles according to claims 1 to 7, wherein said coating material, after preparation of enveloped magnetic iron oxide particles, is additionally cross-linked by cross-linkers which are common in biochemistry and chemistry of natural products.
9. Magnetic particles according to claims 1 to 7, wherein said glycosaminoglycan is heparan sulphate or a synthetic analog thereof.
10. Magnetic particles according to claims 1 to 7, wherein said glycosaminoglycan is hyaluronic acid, or a synthetic analog thereof.
11. Magnetic particles according to claims 1 to 10, wherein mono-, di-, tri-, and oligoamines and/or synthetic and biological oligopeptides/proteins are bonded to said coating material.
12. Magnetic particles according to claims 1 to 11, wherein reduced or oxidized glutathione is bonded, as well as intraparticularly reversibly cross-linked to, said coating material.
13. Magnetic particles according to claims 1 to 12, wherein surface-active substances are bonded to said coating material.
14. Magnetic particles according to claims 1 to 13, wherein targetable structure substances are bonded to said coating material.
15. Magnetic particles according to claim 14, wherein said targetable structure substances comprise hormones, cholesterol, lipids, ether lipids, proteins, monoclonal antibodies, lectins, tumour lectins, adhesion proteins, fusion proteins, transport proteins and transport units, alkaline proteins, histones, interleukins, lipoproteins, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, residual glycosyl or general sugar residues which play a role in complement and immune recognition as well as ribonucleic or deoxyribonucleic acids or their fragments or structural elements, or mixtures thereof.
16. Magnetic particles according to claim 15, including the addition of chemotherapeutic agents.
17. Magnetic particles according to claim 16, wherein said chemotherapeutic agents comprise cytostatic agents.
18. Magnetic particles according to claims 1 to 17, wherein said cross-linking or bonding of targetable structures and/or surface-active substances are combined.
19. Magnetic particles according to claims 1 to 18, wherein said magnetic particles are surrounded by cage molecules.
20. Magnetic particles according to claim 19, wherein said cage molecules comprise subunits of clathrin and/or synthetic analogues.
21. Diagnostic and/or therapeutic agents comprising isotope-doped iron oxide cores of Fe3 0 4, gamma-Fe2 0 3 or their mixtures, which are surrounded by a biodegradable coating of natural or synthetic glycosaminoglycans and/or derivatives thereof with molecular weights between 500 - 250,000 Da.
22. Diagnostic and/or therapeutic agents according to claim 21, wherein said coating molecules are cross-linked by cross-linking agents, and are modified by surface-active substances, targetable structure substances or lower molecular weight residues.
23. Diagnostic and/or therapeutic agents according to claim 21 or claim 22, wherein said iron oxide core is doped with 6Li, 57Fe, 61Ni, Ni, 67Zn, Zn, Mn, 99Ru, 101Ru, 113Cd, 119Sn, 121Sb, 127I, 151Eu, 155Gd, 156Gd, or 157Gd.
24. Diagnostic and/or therapeutic agents according to claims 21 to 23, wherein said natural or synthetic glycosaminoglycans are chondroitin sulphate, dermatan sulphate, heparan sulphate, heparin or its synthetic analogues which are cross-linked by bifunctional cross-linking agents which are common in biochemistry and chemistry of natural products and/or are cross-linked with mono-, di-, tri-, and oligoamines, synthetic or biological oligopeptides, or reduced or oxidized glutathione.
25. Diagnostic and/or therapeutic agents according to claims 24, including surface-active substances which are bonded to said cross-linked coating.
26. Diagnostic and/or therapeutic agents according to claims 24, including targetable structure substances which are bonded to said cross-linked coating material.
27. Diagnostic and/or therapeutic agents according to claim 26, wherein said targetable structure substances comprise hormones, cholesterol, lipids, ether lipids, proteins, monoclonal antibodies, lectins, tumour lectins, adhesion proteins, fusion proteins, transport proteins and transport units, alkaline proteins, histones, interleukins, lipoproteins, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, residual glycosyl or general sugar residues which play a role in complement and immune recognition as well as ribonucleic or deoxyribonucleic acids or their fragments or structural elements or mixtures thereof.
28. Diagnostic and/or therapeutic agents according to claim 27, including the addition of chemotherapeutic agents.
29. Diagnostic and/or therapeutic agents according to claim 28, wherein said chemotherapeutic agents comprise cytostatic agents.
30. Diagnostic and/or therapeutic agents according to claims 21 to 29, including chronologically-variable combination of cross-linking substances, bonding of targetable structures, surface-active substances and chemotherapeutic agents.
31. Diagnostic and/or therapeutic agents according to claims 21 to 30, wherein said coated particles are surrounded in cage form by subunits of clathrin and/or analogues thereof.
32. Diagnostic and/or therapeutic agents according to claims 21 to 31, wherein said magnetic particles are incorporated in liposomes, chylomicrons, cells, cell organelles, bacteria and virus coatings and are surrounded by lipids in the form of a double layer.
33. Process for the preparation of nanocrystalline magnetic particles consisting of a magnetic iron oxide core of Fe3 0 4, gamma-Fe2 0 3 or mixtures thereof and an envelope chemisorbed to the core, comprising the steps of: (a) synthesizing iron oxide cores; and (b) enveloping said iron oxide cores under biometric conditions with a composition comprising natural or synthetic glycosaminoglycans and/or derivatives thereof with molecular weights of 500 Da to 250,000 Da combined.
34. Process according to claim 33, wherein said free functional groups of said coating material are activated and intraparticularly cross-linked by adding a cross-linking agent, and modifying said cross-linked coating by the addition of surface-active substances, or targetable structure substances.
35. Process according to claim 33 or claim 34, including the steps of adding chemotherapeutic agents and/or residual low-molecular weight residues.
36. Process according to claims 33 to 35, wherein said natural or synthetic glycosaminoglycans or their derivatives, comprise chondroitin sulphate, dermatan sulphate, heparin sulphate or a synthetic analogue thereof, hyaluronic acid or a synthetic analogue thereof, or heparin or synthetic analogues thereof as coating substance.
37. Process according to claims 33 to 36, including the step of activating functional groups of said coating material of said magnetite stock solution by means of water-soluble carbodiimide derivatives, or in a two-phase system by lipophilic carbodiimides, and subsequently purifying and isolating the activated magnetite.
38. Process according to claim 37, including the steps of: adding bifunctional cross-linking agents which are common in biochemistry and chemistry of natural products and/or mono-, di-, tri-, and oligoamines, synthetic or biological oligopeptides, or reduced or oxidized glutathione to said activated magnetite solution; non-invasively separating non-reacted educt by dialysis; and adjusting magnetite with its hydrophilic altered and/or cross-linked to the desired final concentration.
39. Process according to claim 37 or claim 38, including the step of adding and admixing surface-active substances to said activated magnetite solution.
40. Process according to claims 37, claim 38 or claim 39, including the step of adding targetable structure substances to said activated magnetite solution.
41. Process according to claim 40, wherein said targetable structure substances comprise hormones, cholesterol, lipids, tumour lectins, adhesion proteins, fusion proteins, transport proteins and transport units, alkaline proteins, histones, interleukins, lipoproteins, LDL, glycolipids, interferons, tumour-necrosis factors, protein A or adjuvants, residual glycosyl or general sugar residues which play a role in complement and immune recognition as well as ribonucleic or deoxyribonucleic acids or their fragments or structural elements or mixtures thereof.
42. Process according to claim 41, including the step of admixing chemotherapeutic agents to said magnetite solution or to said magnetite.
43. Process according to claims 37 to 42, including the step of admixing and adding lower molecular weight residues which influence the physiological distribution pattern of said particles to said activated magnetite solution.
44. Process according to claims 37 to 43, including the step of adding clathrin to the activated magnetite solution.
45. Use of the diagnostic and/or therapeutic agents according to claims 21 to 30, for the preparation of diagnostic and/or therapeutic materials for radiotherapy, hyperthermia, chemotherapy and MR diagnostics and as biomagnetic probes.
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