EP1680142A2

EP1680142A2 - Thermosensitive, biocompatible polymer carriers with a variable physical structure for treatment, diagnosis and analysis

Info

Publication number: EP1680142A2
Application number: EP04766003A
Authority: EP
Inventors: Detlef Müller-Schulte
Original assignee: MagnaMedics GmbH
Current assignee: MagnaMedics GmbH
Priority date: 2003-10-28
Filing date: 2004-10-22
Publication date: 2006-07-19
Also published as: US20070148437A1; WO2005042142A3; WO2005042142A2; DE10350248A1; WO2005042142A8

Abstract

The invention relates to biocompatible, thermosensitive polymers that can be heated by encapsulating magnetic and/or metallic colloids or magnetic nanoparticles by means of a high-frequency, magnetic alternating field. The inductive heating of the polymer matrix triggers physical structural changes in the polymer matrix, that lead to encapsulated bioactive substances being rapidly released in the polymer matrix. Said stimulus-response principle is used to produce controllable medicament depots, contrast-reinforcing means for NMR diagnosis, and manipulable microtools, as means for blocking blood vessels and as controllable porogens during the production of membranes.

Description

Thermosensitive, biocompatible polymer carrier with changeable physical structure for therapy, diagnostics and analysis

The invention relates to biocompatible and thermosensitive polymer carriers of different particle sizes, which enable in vivo application for therapeutic, diagnostic or analytical purposes. Substances in the form of magnetic and / or metallic colloids are encapsulated in the polymer matrix, which can be heated by supplying energy with the aid of a high-frequency magnetic alternating field, which results in a physical change in the structure of the polymer matrix in the form of a configuration change.

The invention further relates to the production and use of the polymer carrier.

Inductively heatable magnetic polymer particles are known from various publications and patents, for example from publication WO 03/101486 A2, in which inductively heatable thermosensitive polymer supports based on N-isopropylacrylamide and acrylamide derivatives are described, which are based on an inductive one Stimulus to be induced to encapsulated organic substances or Pharma_s_a. release.

The isopropylamides described there are the most related. Polymers with thermosensitive properties. They exhibit phase segregation at temperatures above 27 ° C, which is accompanied by a shrinking process. This shrinkage is reversible, ie when the polymer cools below 30 ° C it practically resumes its original shape. This special property of the poly-N-isopropylacrylamide as well as the interesting applications derived from it as a medication depot, biosensor, cell culture substrate, cell encapsulation matrix, actuator or Ventil has long been known and has found expression in a number of publications and patents.

The disadvantage of the agents described there is the use of acrylamide derivatives. This class of compounds is not physiologically unobjectionable, since it cannot be ruled out during the polymerization that incompletely reacted monomers or oligomers are still present in the polymer. These monomers are considered highly toxic and can diffuse out of the polymer in the event of a possible in vivo application. In this respect, active ingredient carriers made from these polymers can only be used to a very limited extent for in vivo applications.

The application WO 03/101486 A2 simultaneously represents the closest prior art and offers a good overview of the same.

The other means and processes cited there have in common that magnetic induction serves exclusively to heat the particles in order to destroy cells or biological organisms by overheating, or that their function derives exclusively from the complementary interaction of a bioligand bound to the matrix or receptor with the substance to be analyzed. Their areas of application are thus limited to the known fields of tumor treatment and the separation and analysis of biomolecules or the labeling of certain cells using the classic principle of affinity. They differ from the agents according to the invention in that, owing to their chemical structure, they are not thermosensitive, ie they are not able to change their physical structure or geometric shape due to an internal heat stimulus caused by external induction. However, this property is the basic prerequisite for being able to use polymer carriers as manipulable or controllable micro or nanocarriers or tools.

Edelmann et al., J. Bio ed. Mat. Res., Vol. 21, 339, 1987, describe an ethylene-vinyl acetate copolymer in which millimeter-sized magnets are embedded. Encapsulated serum albumin is released by an oscillating magnetic field. Since the polymer and the encapsulated magnet are relatively large macroscopic structures that can only be applied by implantation and then cannot be excreted from the body by themselves, broad in vivo applications are excluded from this process.

In summary, it can be said that the agents or products described in the prior art have in common that they are either not physiologically harmless, or, in the case of non-magnetic polymer carriers, only by means of heat supplied directly from the outside to change the physical structure or shape can be induced or, if they are magnetic carriers, can be structurally altered in any way neither by an external stimulus nor by energy supplied from outside. Furthermore, the ^w stimulus-response "carriers known from the prior art are either irregular nanoparticles or larger-volume bulk polymers which are not carriers of active substances (phar aka), as contrast agents in NMR diagnostics (magnetic resonance tomograph), suitable as media for molecular separation or as controllable micro tools for in vivo applications. task

The object of the present invention is to produce thermosensitive and biocompatible polymer supports which are distinguished by high biocompatibility or biodegradability and which can be stimulated in a targeted manner by supplying energy in the form of magnetic induction in such a way that a change in the physical structure due to the resulting heating the polymer matrix is brought about. The polymers are preferably spherical nano- or microparticulate particles or fibers, tubes or threads. Since the configuration change of the polymers according to the invention is in the range of 27-50 ° C., ie also in the range of the body temperature (37 ° C.), these carriers can be used in vivo.

Using inductive heating, dosing systems for the administration or application of active substances for the medical field or analytics are created, which are characterized in particular by their contact-free controllability. An active substance / an active substance is understood to mean a substance which triggers a chemical, biochemical or physiological reaction in some way and can thereby produce a therapeutic, diagnostic and / or prophylactic effect or fulfill an analytical function. Examples include biologically active proteins or peptides, enzymes, antibodies, antigens, nucleic acids, glycoproteins, lectins, oligosaccharides, hormones, lipids, growth factors, interleukins, cytokines, steroids, vaccines, anticoagulants, cytostatic agents, immunomodulatory agents or antibiotics , For this purpose, the active substances are encapsulated in the polymer particles, which is usually done by directly admixing the active substance in question to the soluble polymer phase. The carriers obtained in this way and loaded with the relevant active substances can then be applied to the desired physiological or bio-analytical active sites using known administration methods such as injection, implantation, infiltration, diffusion, flow or puncture. The location-specific application of the magnetic particles can be further strengthened in that the particles can be placed at the desired locations with the aid of electro-magnets or strong permanent magnets which are applied from the outside to the target or effective location. After the polymer particles have reached their point of action, they can be heated to above body temperature by applying a high-frequency magnetic alternating field, which results in a change in the physical structure of the polymer matrix. According to the invention, “change in the physical structure” defines the change in the original molecular configuration including the conformation due to a swelling or swelling process which leads to a change in the geometric shape, the volume or the particle size of the polymer carrier. The change in volume can change manifest in a shrinking or swelling process with a parallel change in the pore size or in a change in the external shape (geometry) of the polymer. The change in the physical structure can also mean the return of the molecular configuration to its original shape, caused by a heating and cooling process (Freezing process) was changed in the meantime (shape-memory-polymer, "shape-memory-polymer"). The change in the physical structure thus triggers a concentrated and rapid release of the encapsulated active ingredients from the matrix.

The time it takes for the active substance to diffuse out of the gel basically depends on the size of the polymer carrier (micro or nanoscale) as well as its molar mass, the molar mass of the active substance and that in the polymer. temperature generated by the capsule. As a rule, nanoscale polymer particles under otherwise analogous conditions (same active substance, temperature, polymer) have a release time that is 0.1 to 0.5 times shorter than corresponding microgels (> 20 μm).

It is therefore an object of the invention to make the polymers usable as carriers for therapeutic, analytical or diagnostic applications and to encapsulate active substances or pharmaceuticals in the polymer carriers in order to apply them in a targeted and controllable manner after corresponding in vivo administration with the aid of magnetic induction or to bring it to the site of action by means of a magnet. The task of specifically releasing the encapsulated active substances or pharmaceuticals is achieved by heating the thermally sensitive polymers by means of magnetic induction, ie solved by an externally applied high-frequency alternating magnetic field, the magnetic and / or metallic substances encapsulated in the polymer matrix absorbing energy from the magnetic field and thereby being able to heat the polymer carrier above body temperature.

Another object of the invention is the production of polymers which shrink at temperatures above body temperature, so that the polymer carriers are applied in a dewaxed (shrunk) state at temperatures above body temperature and return to a swollen state after cooling to body temperature. This phenomenon can be used in the context of therapeutic anti-tumor measures. One of the fatal pathological developments in tumor development is angiogenesis. This is generally understood to mean the widespread formation of blood vessels in the tumor tissue. This pathological process, which was previously mainly treated with medication (or surgery), can now are surprisingly suppressed or greatly delayed with the aid of the agents according to the invention. For this purpose, particles, preferably with a particle size of 0.3 p to 5 μm, which have previously been heated to temperatures> 45 ° C. and thus have reached their maximum degree of shrinkage, are applied to the tumor tissue. As a result of the subsequent adaptation to body temperature, the particles begin to swell again in order to finally reach their equilibrium swelling state after a few minutes. In this swollen state, the polymer carriers exert an embolization function, ie they are able to block the blood vessels and thereby counteract tumor formation. This special property is primarily possessed by polymers such as, for example, hydroxyalkyl cellulose, isopropyl cellulose, polyoxyethylene and poly (ethylene glycol lactide glycolide) copolymers. In practice, particles with a wide size distribution (0.3 to 10 μm) are suitable for combating angiogenesis, since this enables all blood vessel widths to be recorded integrally.

Accordingly, due to the special combination of products and processes, the polymer carriers according to the invention can in particular be used as a matrix for encapsulating active substances and as a means for blocking blood vessels.

The combination of the magnetic field-induced heating of biocompatible, thermosensitive polymer carriers with a parallel change in the physical structure or carrier geometry thus opens up a spectrum of properties that goes far beyond the previous polymer carrier systems.

With the targeted application of the polymer carrier according to the invention in connection with an externally controllable structural change, the possibility is surprisingly also opened up the possibility of using new integral combinations of effects.

A further object of the invention is therefore to produce polymer particles which can be used as novel contrast-enhancing agents in the context of NMR diagnostics and in parallel as the basis for a controllable active substance application. As is known from the state of the art already discussed, superparamagnetic, ferromagnetic or paramagnetic substances can lead to substantial contrast enhancement during imaging in the context of NMR diagnostics (e.g. magnetic resonance imaging, MRI). Due to the receptor-specific bioligand coupling to the agents according to the invention, more precise diagnoses can be made through better localization and assignment of pathological processes, e.g. Detection of tumors in the early stages and micrometastases can be made possible.

In order to be able to heat the aforementioned magnetic and metallic substances or compounds to the temperatures relevant for the analytical, therapeutic and diagnostic applications, a special design of the magnetic field is required with regard to field strength and frequency. As a rule, commercially available systems consisting of coils through which current flows and which are fed by a high-frequency generator are used. The dimensions of the coils depend on the respective sample sizes and the area to be irradiated; they generally have a diameter of 5 to 30 cm and a length of 5-30 cm. The required output power of the HF generators is normally between 1.5 and 4.5 kW. Basically two generator settings can be selected to heat up the magnetic samples: a) high frequency in the range of 5-20 MHz with low magnetic field strength of 100-500 A / m or b) low frequency of 0.2-0.8 MHz in connection with one high field strength of 1 to 45 kA / m. Both field parameter combinations guarantee sufficient heating output within a short application period (<1 min.). Also for the irradiation of larger voluminous areas, as is the case, for example, with the application of medicinal substances in certain areas of the body, larger coil geometries (30-40 cm diameter) can be used to increase the field strength to> 15kA / m by heating enough Carriers are made available.

The starting point for the synthesis of the thermosensitive polymer carriers are magnetic colloids in the form of ferromagnetic, ferrimagnetic or superparamagnetic nano- or microparticles, which have a high magnetization and can be inductively heated in an alternating magnetic field and preferably a Curie temperature of 30 ° C to 100 ° C. The substance preferably used for this purpose is magnetite (Fe ₃ 0 ₄ ) or γ-Fe ₂ 0 ₃ . The production of such colloids has been adequately described in the literature. For the production of magnetite or γ-Fe ₂ 0 ₃ , iron (III) and iron (II) salt solutions with varying molar ratios (0.5: 1, 2: 1 to 4: 1) are used as the starting point, which then by adding bases or by applying heat to corresponding colloidal magnetic dispersions (“magnetic colloids”). In order to prevent agglomeration of the fine magnetic particles, which is particularly caused by the van der Waals ^λ , surface-active substances (surfactants, emulsifiers, stabilizers) added, which practically prevent settling of the colloid in an aqueous dispersion. These stabilized colloidal dispersions are also known under the name “ferrofluids” and are commercially available (Ferrofluidics Corp., USA; Advanced Magnetiσs, USA; Taibo Co, Japan; Liquids Research Ltd., Wales; Schering AG, Germany). The surface-active substances used are cationic, anionic or non-ionic in nature, such as: oleic acid, lauryl sulfonate, phosphate ester, alcohol ether sulfates, alkylaryl polyether sulfates, alkylaryl polyether sulfonates, citrates, alkyl naphtalenesulfonates, polystyrene sulfonic acid, polyacrylic acid or petrolium sulfonium ethyl (anionic deionic sulfonate) (anionic ammonium sulfonate) (anionic ammonium sulfonate) (anionic ammonium sulfonate) (anionic ) and nonylphenoxypolyglycidol, polyvinyl alcohol, kerosene, alkylaryloxypolyethoxyethanols, nonylphenol or polyethylene glycols (non-ionic surfactants).

The particle sizes of the magnetic colloids depend, as is generally known, on various experimental parameters such as the iron salt ratio, the base concentration, the pH and the temperature.

The magnetic colloids suitable for the use according to the invention have a particle size of 5-800 μm, preferably that of 10-200 nm, which ensures that the magnetic colloids are present in colloidally dispersed form during the subsequent encapsulation in the polymer matrix. The magnetic properties and, consequently, the heating properties of the polymer carrier can be controlled in a targeted manner by adding appropriate amounts of the colloid in question.

The concentrations of the magnetic colloids in the monomer or polymer batch are generally 10 to 40% by volume, the solids content of the magnetic substance, based on the polymer phase, generally being 5 to 40% by weight, preferably 10 to 30%.

In addition to the magnetic colloids, metallic colloids can alternatively also be encapsulated in the polymer matrix. Basically, all metallic materials in colloidal or finely dispersive form are suitable for this, which can be inductively heated in a high-frequency alternating field. Since the physiological applications in the invented Agents according to the invention represent an essential aspect, preference is given to using inductively heatable metal colloids which are physiologically harmless and / or chemically / physically inert. These include the metals from group 8 to 11 (IUPAC name 1986, ie Fe, Co, Ni, Cu and higher homologues), gold, silver, palladium and platinum colloids or corresponding powders preferably being used because of their biocompatibility , The metal colloids used for the agents according to the invention generally have a particle size between 5 and 200 μm. The production of such colloids, which have long been used in bioanalytics for the determination of proteins and nucleic acids due to their special absorption properties in the visible range, here especially the gold colloids, are well known from the prior art and the metal colloids or powders are also known also offered commercially in a variety of ways. As is known to those skilled in the art, they are obtained consistently by reducing the corresponding metal salts or by metal spraying processes.

Both the metal colloids and the corresponding powders, which are mixed into the polymer batch in the desired concentration, can be used for the agents and processes according to the invention. The proportion of metal in the polymer or in the particles is generally between 5 and 40% by weight.

After adding the colloids, it is often advantageous to briefly sonicate the magnetic colloid-polymer mixture with the aid of an ultrasound finger or in an ultrasound bath in order to achieve a fine dispersion of the colloid. Due to the finely dispersed distribution of the colloid, a correspondingly homogeneous heat distribution in the polymer matrix is later possible, which in turn ensures a continuous release of the encapsulated active substance. Polyethylene oxides, polylactides, polyglycolides, polysaccharides, polysaccharide derivatives, polyamino acids, polyethers, chitosan, polyvinyl alcohol, alginate, gelatin or copolymers or block copolymers of these substances are used as thermosensitive substances with high biocompatibility. Depending on the type of polymer, the following processes are used to produce the thermosensitive polymers:

a) Ring-opening polymerization b) suspension precipitation c) suspension crosslinking process d) ionic crosslinking in suspension e) salt-out emulsion process f) solvent evaporation process

These methods according to the prior art are generally known and are briefly explained below in the context of the polymers according to the invention.

Microparticulate pharmaceutical carriers based on poly (lactide) and poly (lactide-co-glycolide) can be produced by the known processes, such as, for example, solvent evaporation, phase separation or spraying processes or the salting-out technique. The basic principle of this procedure is the use of water-soluble organic solvents, for example acetone, which are emulsified in an aqueous phase saturated with a salt. The solvent evaporation process is preferably based on an aqueous solution of the active ingredient to be encapsulated, which is then dispersed in the polymer phase. Alternatively, the active ingredients can also be dispersed directly in the polymer phase. Subsequent addition of non-solvents - preferably vegetable or mineral oils - precipitates the polymer carrier at the border phase. Preferred solvents for the polymers are acetone, benzene and methylene chloride or chloroform for the poly (lactide-co-glycolide) copolymers used. For better stabilization of the colloids, 0.1 to 1 mol% (based on the polymer) of proteins such as serum albumin or synthetic polymers, polyvinyl alcohol or polyvinyl pyrrolidone can be added.

For the synthesis of the magnetic carriers according to the invention, 5 to 40% by volume, preferably 20-40%, of an organic-based ferrofluid are generally added to the polymer phase. A further advantage of the polymers based on poly (lactide) is their biodegradability over months, the polymer being hydrolyzed within months and the hydrolyzate being subsequently metabolized.

Another group of thermosensitive, biocompatible polymer supports is derived from poly (ethylene glycol-lactide-ethylene glycol) block copolymers. Their special properties consist in changing from a liquid state to a solid gel-like state above approx. 35 ° C. This phase transition can surprisingly be used to produce thermosensitive, magnetic nanoparticles by dispersing magnetic nanoparticles or magnetic colloids, preferably with a particle size between 5 and 100 nm, in a 10 to 30% aqueous solution of the polymer and then with an ultrasound finger Treated for 10 to 120 seconds at temperatures <15 ° C. This creates magnetic particles which are coated with the poly (ethylene glycol lactide ethylene glycol) block copolymers and form stable colloids. Due to their special gelling properties, these colloids can be used for the treatment of tumors and metastases by injecting the colloids, which are low-viscosity at room temperature, directly into the tumor tissue. The subsequent inductive heating of the colloid to above body temperature (> 37 ° C) causes the colloid to solidify into a gel. As a result of the heat-induced gelation, the blood supplying vascular systems can be blocked and further tumor growth can be suppressed. With the aid of the suspension precipitation, further polymers can be produced which meet the criteria of biocompatibility and thermosensitivity according to the invention. This group includes those polymers that are only heat-soluble in a particular solvent, but fail when the solvent cools down. Polymer-solvent systems for the preparation of the corresponding polymers which are suitable for this synthetic engineering are the following examples which in no way limit the invention: polyvinyl alcohol-dimethylfoamamide, polyvinyl alcohol-ethylene glycol, gelatin-water, agarose water, cellulose tributyrate. Ethanol, cellulose acetate butyrate methanol, cellulose acetate butyrate toluene, starch water, cellulose ZnCl ₂ solution, collagen water.

In order to obtain spherical particles, the polymers dissolved at higher temperatures are dispersed in an organic phase which is not miscible with the polymer phase. Vegetable oils or mineral oils, which generally have a viscosity between 40 and 400 cp, are preferably suitable for this. In the subsequent cooling process to room temperature or temperatures <40 ° C, these polymers precipitate out as spherical particles.

By adding magnetic colloids or ferrofluids, which form stable dispersions with the polymer phase, as well as active substances, e.g. in the form of cytostatics, magnetic drug carriers are obtained.

The magnetic field-induced heating of these polymer carriers leads to a pronounced swelling process, which results in a concentrated release of the encapsulated pharmaceuticals. The kinetics of release are dependent both on the molar mass of the polymer and on the magnetic colloid content, which has a direct influence on the heating which can be achieved. As a rule, the swellability decreases with decreasing molar mass and consequently the release rates of the incorporated active substances also increase.

For the synthesis of the polymer supports by means of the suspension precipitation process, 1 to 15% polymer solutions are preferably used. The concentration of added magnetic colloid is usually 10 to 40% by volume, based on the polymer phase. Suitable substances which can be incorporated are substances which, with the polymer phases, are stable, homogeneous, i.e. form non-agglomerating colloidal dispersions. For this, e.g. Plasmids, peptides, nucleic acids, oligosaccharides or cytostatics such as Ifosfamide, melphalan, cyclophosphamide, chlorambucil, cisplatin or methotrexate are suitable.

To improve the quality of the suspensions and particle geometries (spherical shape), it has been found to be advantageous for all polymer supports according to the invention to add at least one, but generally not more than three, surface-active substances to the oil phases. Examples of such, the invention is not limiting additives include polyoxyethylene adducts, Alkylsulfosucσinate, polyoxyethylene sorbitol esters, polyethylene oxide-propylene oxide block copolymers, alkylphenoxypolyethoxyethanols, Fettalkoholglycolether- organophosphate, sorbitan fatty acid ester, Sucrosestea- rat-palmitate, Fettalkoholpolyethylenglykolether, poly glycerinester, polyoxyethylene alcohols, Polyoxyethylensorbi - Tan fatty acid esters and / or polyoxyethylene acids. Substances of this type are also commercially available, for example, under the trade name Hoostat, Isofol, Synperonic, Span, Tween, Brij, Aerosol OT, Hypermer, Myrj, Triton, Arlacel, Dehymuls, Eumulgin, Renex, Lameform, Pluronic or Tetronic. To control the size of the polymer droplet size formed during the suspension process, which should be below (<1 μm), 0.05-15% by weight, preferably 0.5-5% by weight, of one or more surfactants are added to the oil phase. The particle sizes of (<1 µm) are particularly suitable for biomedical in vivo applications, since they sustainably support tissue mobility for these applications. Particles with a size of 20-200 μm are preferably used as contrast agents in NMR diagnostics and as porogens for producing adjustable pore sizes in membranes. In contrast, particles with a size of 200-800 nm are used particularly as a medicament depot for the targeted application of active substances, for example in the form of therapeutic, diagnostic or prophylactic agents.

The suspension process is usually carried out with the aid of a conventional stirrer or a dispersing tool. Particle sizes in the range of 10-500 μm can be achieved with propeller stirrers with stirring speeds between 600 and 1500 rpm, particle sizes of <10 μm can generally be achieved with stirring speeds of> 1500 rpm. In contrast, for particle sizes <1 μm only dispersing tools with stirring speeds of> 5000 rpm are used. in question. Mixing tools that work according to the rotor-stator principle are used for this purpose. At these high stirring speeds, the dispersions should preferably be prepared under an argon or nitrogen atmosphere or in vacuo in order to largely eliminate the introduction of air which adversely affects the suspension quality.

The use of oils as a suspension medium can be dispensed with entirely in a further process approach according to the invention, in which (meth) acrylate-substituted dextrans are used, which are then suspended in a polyethylene glycol phase. By varying the ratio of dextran to polyethylene glycol, it is possible, as is known from the prior art (Stenekes et al. Pharm. Res., Vol. 15, 557, 1998), to vary the size of the polymer parts which form. As a rule, the particle large in the case of polyethylene glycol / dextran volume ratios of <40 to larger particles (> 10 μm). A wide range of different polymer carriers can be obtained through further variations, including the degree of substitution, the acrylate substituents (eg hydroxyethyl methacrylate, glycidyl methacrlylate) and the molecular weights of the phases used (polyethylene glycol, dextran). After encapsulation of the corresponding magnetic colloids, as described above, and encapsulation of certain active ingredients (peptides, plasmids, for example), the carriers can be stimulated with the help of magnetic field-induced heating within 5 minutes to give targeted and concentrated active ingredient releases.

Another group of biocompatible and thermosensitive carrier media in the sense of the invention is derived from the liposomes. Liposomes are synthetically produced spherical hollow bodies (vesicles) that are encased in a membrane consisting of a lipid layer or lipid bilayer. The biocompatibility is given by the fact that the lipids constituting the membrane mainly consist of constituents of natural cell membranes. Because of the vesicle structure, the liposomes are particularly well suited to act as active substance carriers by encapsulating pharmaceuticals or other bioactive substances such as peptides or nucleic acids. By encapsulating magnetic colloids or ferrofluids in the vesicles and by combining certain lipids, it has surprisingly been possible to show that thermosensitive magnetic liposomes are formed which can be heated to temperatures above 37 ° C. using the magnetic field induction explained above. In principle, all natural lipids such as phosphatidylcholine, phosphatidyl acid, cholesterol, phosphatidylethanolamine, monosialogangliosides, phosphatidylinositol, phosphatidylserine and sphingomyelin can be used as lipids. As is well known, the lipid Compositions vary both in relation to one another and in terms of concentration within certain limits. Examples of such compositions are: phosphatidylcholine: cholesterol: monosialoganglioside: 2: 1: 0.14; Sphingomyelin: monosialoganglioside 1: 0.07; Sphingomyelin: cholesterol: monosialoganglioside 2: 1: 0.13; Sphingomyelin: phosphatidylcholine: cholesterol: 1: 1: 1; Phosphatidylcholine: Cholesterol: Phosphatidylethanolamine: 1: 1: 0.2. Substitution with lipids that stabilize the membrane conformation, such as sphingomyelin, can reduce phagocytosis by 90%. An analogous effect can also be achieved with polyethylene glycol (PEG) -substituted (pegylated) lipids, PEG-phosphatidylethanolamine, for example. The molar ratios of the biocompatibility-increasing substituents to the other lipids are preferably between 0.1 and 0.4.

A dialysis method known from the prior art (M. De Cuyper et al. Prog. Coll. Poly. Sei. Vol. 82, 353, 1990) is used to produce magnetic liposomes. For this, a ferrofluid stabilized by lauric acid is dialyzed in the presence of a unilamellar lipid vesicle. It has now surprisingly been possible to show that inductive heating of the magnetic liposomes to temperatures> 45 ° C. changes the lamellar lipid conformation in such a way that encapsulated active ingredients are released to> 60% within 1 to 6 minutes. By further heating to> 50 ° C, the vesicle structure breaks down completely, so that the encapsulated active ingredients are fully released within one minute.

The thermosensitive and biocompatible agents according to the invention also include the group of polyoxyethylenes and polyoxypropylenes and copolymers of these substances with the general formula HO- (CH -CH_0) - (CH (CH -CH.O) - (CH -CH.0) -H , These polymers, also known as poloxamers or Pluronic, have a high degree of biocompatibility on the one hand, and on the other hand they have a pronounced thermosensitivity due to their strong tendency to form hydrogen bonds. By means of targeted copolymerization or block copolymerization from polyoxyethylene and polyoxypropylene, the critical phase transition temperatures can be set in the range from 20 to 70 ° C so that the phase transition to temperatures> 40 ° C increases with increasing hydrophilic polyoxyethylene content (usually> 50 mol%) can be moved. An alternative to influencing the phase transition temperature is to add polyhydroxy compounds such as sorbitol, sucrose or glycerin. These compounds shift the gelation point to lower temperatures (<40 ° C), whereas acids or salts such as NaCl, Na ₂ S0 ₃ , Na ₂ S0 ₄ , KC1 shift the phase transition to higher temperatures (> 45 ° C).

By combining the polyoxyethylenes and polyoxypropylenes with di- or triamines, e.g. Ethylenediamine, there is a further group of thermosensitive, biocompatible polymers of the general formula: [(R1R2) (R1R2)] = X = [(R1R2) (R1R2)], which are also known under the name poloxamines. R1 and R2 mean a polyoxyethylene or polyoxypropylene radical and X is a polyfunctional amine. The syntheses of such copolymers are generally known from the prior art.

The production of magnetic micro- or nanoparticles could surprisingly be achieved by adding up to 40 vol.% Of a water-based ferrofluid to the aqueous solutions of these polymers or copolymers. The mixtures are then in an organic phase immiscible with the polymer phase - preferably oils with a viscosity of 40 to 120 cp - with the addition of 0.1 to 2 mol% of a bi- or trifunctional crosslinker. suspended, which is able to cross-link the terminal hydroxyl groups. Examples of these are: cyanuric chloride, diisocyanates, epichlorohydrin, dihalides, carbonyldiimidazole. The mechanical suspension of these mixtures can optionally be carried out using a conventional stirrer or, to obtain nanoparticles, advantageously using a dispersing tool (eg T25 Ultraturrax, IKA, FRG) using a stirring speed > 10,000 rpm. The volume ratio of polymer to suspension phase is usually 0.03 to 0.1.

Surprisingly, thermosensitive and biocompatible polymer supports can also be produced by suspending positively or negatively charged polymers dissolved in aqueous phases in the organic phase and solidifying them by subsequent addition of oppositely charged substances to form discrete spherical polymer parts. Examples of this which in no way limit the invention are alginates, chitosan, nucleic acids, proteins, polyamino acids. For this purpose, the polymers are first transferred to a 1 to 10% by weight aqueous solution. During the subsequent suspension in a water-immiscible phase (e.g. vegetable or silicone oils or chlorinated hydrocarbons, ratio polymer phase / continuous phase: 0.025-0.15), the dissolved polymers are crosslinked into spherical particles by adding oppositely charged substances. Examples of such crosslinking substances are divalent salts such as Calcium chloride for alginates, nucleic acids and polyamino acids or polyphosphates for chitosan.

For the synthesis of magnetic carriers, water-based ferrofluids are added to the polymer solutions, which are able to form stable, colloidally disperse solutions with the polymer phase. Surprisingly, positively charged amines such as spermine, spermidine and protamine, which occur in the cells and envelop the DNA, can also be used to produce spherical magnetic particles. A preferred synthetic route for these particles is based on a 0.5 to 10% nucleic acid buffer solution (pH> 8.4). 10 to 40% by volume of a water-based ferrofluid and, optionally, a water-soluble pharmaceutical or bioactive substance are added to the solution. This approach is suspended in a water-immiscible phase, preferably consisting of oils with a viscosity of 60 to 100 cp, with stirring. During the suspension process, with the addition of 0.1 to 3 mol%, based on the nucleic acid content, the corresponding amines are added, which solidify the nucleic acid suspension into spherical particles. Depending on the stirring conditions and nucleic acid concentrations, particles with a size between 0.3 and 20 μm are obtained, with the particle sizes generally increasing with increasing stirring speed (> 3000 rpm) and falling nucleic acid concentration (<5%) be shifted into the nanometer range. By adding 0.1-5% by weight & s (based on the nucleic acid content) of a bioactive, preferably neutral active substance to the nucleic acid solutions, pharmaceutical carriers can be produced which can be treated with an induction coil (15 kA / m, 0.3 MHz, 4.4 kW) are heated within 1 to 5 minutes so that the encapsulated active substance is released up to 70% due to the partial swelling effect of the nucleic acid carrier within the heating period.

In addition to the magnetic field-induced release of encapsulated pharmaceuticals or bioactive substances, the agents according to the invention offer the possibility of coupling bioaffine ligands such as antibodies, cell receptors, anti-cell receptor antibodies, nucleic acids, oligosaccharides, lectins and antigens to the polymer carriers with which the thermosensitive ven carriers can be bound to certain target substances such as cells, biomolecules, viruses, bacteria or tissue compartments or selectively attach to these target organs according to the known affinity principle. Thus, the polymer carriers can be specifically coupled to T cells by coupling those antibodies which are directed against the cell surface structures such as, for example, CD2, CD3, CD4, CD8, CD19, CD14, CD15, CD34 and CD45 (“cluster of differentiation”) , B-lymphocytes, monocytes, granulocytes, stem cells and leukocytes The agents according to the invention which have functional groups in the form of carboxyl, hydroxyl or amino groups are particularly suitable for targeted application by means of ligand-coupled polymer carriers. Examples of these are the polysaccharides, polyvinyl alcohol, gelatin, alginates and polylactides.

By coupling such antibodies or antibody fragments that are directed against a tumor cell antigen, the prerequisite is first created to concentrate the polymer supports in the tumor tissue or to attach them to the tumor cells. Examples of such tumor markers or antigens, which do not restrict the invention, are: tumor-associated transplantation antigen (TATA), oncofetal antigen, tumor-specific transplantation antigen (TSTA), p53 protein, carcinoembryonic antigen (CEA), melanoma antigens (MAGE-1 , MAGE-B2, DAM-6, DAM-10), mucin (MUCl), human epidermis receptor (HER-2), alpha-fetoprotein (AFP), helicose antigen (HAGE), human papilloma virus (HPV- E7), Caspase-8 (CASP-8), CD3, CD10, CD20, CD28, CD30, CD25, CD64, Interleukin-2, Interleukin-9, Mamma-CA antigen, prostate-specific antigen (PSA), GD2 antigen, melanocortin receptor (MCIR), 138H11 antigen. The corresponding antibodies can be selected either as monoclonal or polyclonal antibodies, as antibody fragments (Fab, F (from ₂ ), as single chain molecules (scFv), as "diabodies", "triabodies", "minibodies" or bispecific antibodies.

For parallel treatment of the tumors, the antitumor agents or cytostatics known from cancer therapy are encapsulated in the polymer particles. Examples include: methotrexate, cis-platinum, cyclophosphamide, chlorambucil, busulfan, fluorouracil, doxorubicin, ftorafur or conjugates of these substances with proteins, peptides, antibodies or antibody fragments. Conjugates of this type are known from the prior art: "Monoclonal Antibodies and Cancer Therapy", UCLA Symposia on Molecular and Cellular Biology, Reisfeld und Seil, ed., Alan R. Riss, Inc., New York, 1985 ,

The known methods for coupling bioactive substances such as proteins, peptides, oligosaccharides or nucleic acids to solid supports are used for the covalent attachment of the bio- or affinity ligands or receptors to the polymer supports. Coupling agents which are used here are, for example: tresyl chloride, tosyl chloride, cyanogen bromide, carbodiimide, epichlorohydrin, diisocyanate, diisothiocyanate, 2-fluoro-1-methyl-pyridinium-toluene-4-sulfonate, 1,4-butanediol diglycidyl ether , N-hydroxysuccinimide, chlorocarbonate, isonitrile, hydrazide, glutaraldehyde, 1,1 ', carbonyldiidazole. In addition, the bioligands can also be coupled via reactive heterobifunctional compounds which can form a chemical bond both with the functional groups of the matrix (carboxyl, hydroxyl, sulfhydryl, amino groups) and with the bioligand. Examples in the sense of the invention are: succinimidyl-4- (N-maleiimido-methyl) -cyclohexane-1-carboxylate, 4-succinimidyl-oxycarbonyl- - (2-pyridyldithio) toluene, succinimidyl-4- (p-maleimidophenyl) butyrate, N-γ-maleimidobutyryloxysuccinimide ester, 3- (2-pyridyldithio) propionylhydrazide, sulfosuccin imidyl-2- (p-azidosalicylamido) ethyl-l, 3 '-dithiopropionate. One skilled in the art can use these coupling agents at any time as described in "GT Hermanson," Bioconjugate Techniques, "Academic Press, San Diego, 1996.

The invention is explained in more detail in the following descriptive but not restrictive examples. The particle sizes were determined by scattered light / laser diffraction using a Malvern MasterSizer 2000 (Malvern Instruments, FRG).

example 1

2.8 g of polyvinyl alcohol, molecular weight 204 kDa, are dissolved in 18 ml of ethylene glycol at 120 ° C. After the solution has cooled down to 80 ° C., 5 ml of a ferrofluid stabilized with lauric acid are added to the solution. This is followed by a five-minute treatment in an ultrasound bath. The dispersion is then allowed to cool down to 65 ° C. After 50 mg of melphalan have been dissolved in the polymer phase, the mixture is dissolved in 100 ml of vegetable oil preheated to 70 ° C (viscosity 84 cp), in which 1.5% by volume Pluronic 6200, 0.8% by volume Dehymuls HRE and 2% by volume Tween 85 are dissolved, suspended with stirring (2000 rpm). During the suspension process, the mixing vessel is cooled down with ice. After about 3 minutes, the polymers precipitate out as pearl-shaped particles. Stirring is continued for 15 minutes. Then 100 ml of petroleum ether are added and the magnetic fraction is separated using a hand magnet. It is washed ten times alternately with petroleum ether and methanol. After drying in a vacuum to constant weight, magnetic particles with an average particle size of 12 μm are obtained.

The pharmaceutical carriers can be used, among other things, for the treatment of breast cancer. Example 2

500 mg of a triblock copolymer prepared analogously to the instructions by B. Jeong et al., Colloid Surfaces B Biointerfaces Vol. 16, 185, 1999, consisting of poly (ethylene glycol lactide ethylene glycol) (Mw: 11.8 KDa), are added in 4 ml 0.1 M Na phosphate buffer, pH 7.4, dissolved and then sonicated in an ultrasonic bath at 15 ° C. for 5 minutes. 100 mg of cobalt ferrite powder (CoFe ₂ 0 ₄ , average particle size 259 nm), which was produced from CoCl ₂ and FeCl ₃ , are added to this solution. The dispersion is then sonicated under ice cooling using a high-performance ultrasound finger (from Dr. Hielscher, 80% amplitude) three times for 50 seconds under ice cooling and a nitrogen atmosphere. A stable colloid with an average particle size of 645 nm is formed.

Example 3

Magnetic chitosan nanoparticles are produced by ionic gelation of chitosan with sodium tripolyphosphate. 3.5 ml of a 0.6% chitosan-glutamate solution (MW: 205 kDa) are dissolved in double-distilled and degassed water, the pH of which has been adjusted to 5.5, with 1.5 ml of one according to Shinkai et al., Biocatalysis, Vol. 5, 61, 1991, prepared aqueous magnetic colloid solution (average particle size 26 nm). 2.8 ml of a 0.084% Na tripolyphosphate solution in which 3 mg / ml gonodropin are dissolved are added dropwise to this dispersion with vigorous stirring (4500 rpm). After stirring for two minutes, the magnetic particles are placed on a glass column densely packed with steel wool (filling volume: approx. 4 ml; inner diameter: 0.5 cm), which is surrounded by a 3 cm long ring-shaped neodymium-boron-iron magnet. The mixture is slowly dripped through (0.5 ml / min.). After the run, it is washed ten times with about 20 ml of 30 t of ethanol. This is followed by five washings with 0.1 M Na phosphate buffer, pH 7.2, followed by ten washings. see with bidest. Water. The magnetic polymer fraction on the column is then redistilled with 10 ml after removal of the magnet. Water eluted. The eluate obtained is then freeze-dried.

Particles with an average size of 672 nm are obtained. After appropriate dispersion in physiological saline, the pharmaceutical carriers can be used for hormone treatment.

Example 4

A 2.8% by weight gelatin solution is prepared by heating to 90 ° C. in 1.5 ml of 0.05 M Na phosphate buffer, pH 7.4. The solution is then brought to 40 ° C. and first 0.5 ml of ferrofluid EMG 507 (from FerroTec, USA) are added. The dispersion is then treated in an ultrasound bath at 40 ° C. for 2 minutes. 1 ml of a 0.05 M Na phosphate buffer solution, pH 7.4, heated to 40 ° C., in which 0.25% human insulin (Sigma) and 0.5% polyvinyl alcohol (Mw: 22 kDa) were dissolved are added to the gelatin ferrofluid dispersion. The resulting mixture is poured into 80 ml vegetable oil preheated to 40 ° C (viscosity 84 cp), in which 0.8 vol% Pluronic L61, 0.8 vol% Tetroniσ 1101 and 2.5 vol% Dehymuls FCE are dissolved, and at 12,000 rpm with Homogenized using a dispersing tool (T25 Ultraturrax, IKA, FRG) under a nitrogen atmosphere for 2 minutes. The dispersion is then cooled to <10 ° C. by means of ice cooling, the gelatin particles precipitating. After adding 50 ml of petroleum ether, the magnetic fraction is separated using a neodymium-boron-iron hand magnet and washed ten times alternately with petroleum ether and ethanol. This is followed by five washes with Ξis water. Polymer particles with an average size of 1.4 μm are obtained. Example 5

80 mg of one according to a specification by Zweers et al. (J. Biomed. Mater. Res. Part B, Vol. 66B, 559, 2002) and vacuum-dried poly (lactide-co-glycolide) s (Mw 110 kDa) are dissolved in 4 ml of acetone. 1.5 ml of the ferrofluid DKS1S21 (from Liquids Research Ltd., Wales) and 8 mg of cyclophosphamide are added to the solution. The mixture is then dispersed using a dispersing tool (T25 Ultraturrax, IKA, FRG) at 20,000 rpm. dispersed in 8 ml of water in which 60% by weight of MgCl ₂ and 2% by weight of polyvinyl alcohol (Mw 22 kDa) as a stabilizer are dispersed for one minute at room temperature. 7.5 ml of water are added during the emulsification process and the stirring process is continued for 20 seconds. The high-gradient magnetic field separation is then carried out analogously to Example 3. After the run (0.5 ml / min.), The mixture is distilled ten times with about 20 ml. Washed water. The magnetic polymer support retained on the column is then eluted three times with 1.5 ml of physiological saline after removal of the magnet. Nanoparticles with an average particle size of 483 nm are obtained. The encapsulated pharmaceuticals that can be used for tumor therapy can be released to> 50% within 5 minutes using a high-frequency magnetic field (10 kA / m, 0.8 MHz, 4.8 kW).

Example 6

1.5 ml of magnetic colloid (2.2 mM Fe / l, average particle size 26 nm), which was produced according to a specification by Shinkai et al., Bio-catalysis, Vol. 5, 61, 1991, are mixed with 5 ml of a 0.05 M Na carbonate buffer solution, pH 9.5, in which 10% of the polyoxyethylene-polyoxypropylene copolymer (Pluro are dissolved, mixed and sonicated for 5 minutes in an ultrasonic bath (500 W) with ice cooling. Nitrogen is then passed into the mixture at 20 ° C. for 15 minutes. The dispersion is then 0.5 ml of 0.05 M Na carbonate buffer solution, pH 9.5, in which 1 wt .-% Somatotro- pin, 0.5% by weight of inositol and 0.05% by weight of human serum albumin are added. The mixture is treated with ultrasound for a further two minutes and then in 50 ml of sesame oil (viscosity 153 cp) in which 2.5% by volume of Span 60 and 1.5% by volume of Dehymuls HRE7 are dissolved, with stirring (1200 rpm) and nitrogen injection Dispersed at 20 ° C. 100 μl of divinyl sulfone are pipetted in during the dispersing process. The mixture is further stirred over a period of 2 hours. Separation and washing processes take place analogously to Example 3. After freeze-drying and dispersion in physiological saline solution, polymer carriers with an average particle size of 0.767 μm are obtained. When the particles are treated in an alternating magnetic field (magnetic field: 10 kA / m; 0.6 MHz, coil diameter: 5.5 cm, 8 turns), a swelling process is triggered which releases more than 45% of the incorporated hormone within 5 minutes.

Example 7

Magnetic liposomes are produced according to the known methods. For this purpose, magnetite magnetic colloids (diameter approx. 15 nm) are first produced and stabilized with lauric acid at 90 ° C. 0.18 ml of this colloid (61 mg Fe ₃ 0 ₄ / ml) are mixed with 9 ml of a vesicle dispersion, which is treated by ultrasound treatment with an ultrasound finger (150 W) of a phospholipid-lidocaine mixture of dimyristoylphosphatidylglycerol sodium salt / phosphate idylethanolamine. Polyethylene glycol biotin / lidocaine (concentration: 8.4μM / ml molar; ratio 9/1 / 0.5) was obtained, dialyzed for 72 h at 37 ° C (Spectra / Por dialysis tube, Speσtrum edical Industries, Los Angeles, CA, molecular weight exclusion limit2, 000-14, 000). The dialysis buffer (5 mM N-tris [hydroxymethyl] methyl-2-aminoethanesulfonic acid, TES, pH 7.0) is replaced every 5 hours. Excess vesicles are separated by means of the column filled with steel wool (see Example 3). After the separation, the magnetic fraction is washed several times with 4 ml of TES buffer. The magnetic liposomes are then obtained after removal of the magnet by elution three times with 2 ml of buffer solution each. The molar ratio of phospholipid / Fe ₃ 0 ₄ is 0.69. In the subsequent treatment of the particles in an alternating magnetic field (magnetic field: 10 kA / m; 0.6 MHz, coil diameter: 5.5 cm, 8 turns), the vesicular structure of the liposomes is dissolved within 5 minutes and the encapsulated lidocaine is released completely , The pharmaceutical carrier can be used as a local anesthetic.

Example 8

A cobalt ferrite magnetic colloid (CoFe ₂ 0 ₄ ) is produced from CoCl ₂ and FeCl ₃ and in water with the help of a high-performance ultrasound finger (Dr. Hielscher, 80% amplitude) in the presence of 0.75% polyacrylic acid (M _w : 5,500) dispersed for 30 seconds. 2 ml of the colloid containing 1.9 mM Fe / ml (particle size 21 nm) are mixed with 5 ml of twice-distilled and degassed water in which 5% by weight of isopropyl cellulose are dissolved. The mixture is sonicated for 10 minutes in an ultrasonic bath at 20 ° C. The mixture is then dissolved in 70 ml vegetable oil preheated to 70 ° C (viscosity 134 cp), in which 1.5% Tween 80, 2.5% Pluronic PE 3100 and 2.5% Span 85 are dissolved, using a stirrer ( 1200 rpm.) Dispersed. Stirring is continued for 10 minutes at this temperature. Solid polymer particles are formed during this process. After adding 100 ml of butanol, the magnetic fraction is separated using a hand magnet and washed several times alternately with petroleum ether and methanol. Magnetic particles with an average particle size of 16 μm are obtained.

200 mg of the polymer particles produced in this way are mixed with 3 ml of 3.5 M NaOH and 5 ml of epichlorydrine and reacted for 2 hours at 55 ° C. with vigorous stirring. The magnetic particles are then removed using a neodymium-iron-boron magnet. Cut. The product is suspended in approx. 10 ml of water and magnetically separated again. This washing / separating process is repeated 10 times, followed by washing once with acetone. The activated magnetic particle fraction is then reacted with 2 ml of 0.1 M borate buffer, pH 11.4, which contains 10% hexamethylene diamine, at 50 ° C. for 2 hours. After magnetic separation, it is washed ten times with water. The product obtained is then reacted with 2 ml of 0.1 M K-phosphate buffer, pH 7.0, in which 12.5% of glutaraldehyde are dissolved, for 2 h at 30 ° C. It is then washed 20 times with water and then five times with 0.1 M Na phosphate buffer, pH 7.5, over a period of 30 minutes. By incubating 1.5 ml of 0.1 M Na phosphate buffer, pH 7.5, in which 0.2 mg of CD4 are dissolved, for three hours, polymer particles are obtained which can be used to bind the HIV (human immunodeficiency virus). By inductive heating of the virus-magnetic particle complex (4.8 kW, 0.5 MHz) temperatures (> 60 ° C) are reached within 10 minutes, which can kill the viruses.

Claims

claims

1. Thermosensitive and biocompatible, magnetic and / or metallic colloids containing polymer particles, which can be heated with the aid of a high-frequency magnetic alternating field and thereby experience a change in their physical polymer structure, characterized in that the polymers used to produce the polymer particles according to the invention are selected from the group the biocompatible polymers, the polyorthoesters, polyalkyl cyanoacrylates, polyglycolic acid, polyether esters, polycarbonates, polyhydroxyalkanoates, polyhydroxy acids, poly (ε-caprolactone), polyamino acids, polysaccharides, polysaccharide (meth) acrylate derivatives, liposomes, isopropyl cellulose , Cellulose acetate butyrate. Starch, starch alkyl ether, collagen, alginate, chitosan, polyvinyl alcohol, gelatin, ionically cross-linked multifunctional amines or linear copolymers, graft copolymers or block copolymers of these polymers or dendrimers formed from the polymers.

2. Thermosensitive and biocompatible polymer particles according to claim 1, characterized in that the polymers consist of one or more copoly er (s) or block copolymer (s).

3. Thermosensitive and biocompatible, containing magnetic and / or metallic colloids Polymerteilσhen, according to claim 1 or 2, characterized in that the change in the physical structure in a swelling, de-swelling, solution or gelation process or in a change in the geometric shape of the Polymers.

4. Thermosensitive and biocompatible polymer particles according to one of claims 1 to 3, characterized in that it is spherical nano- or microparticulate particles or fibers, tubes or threads.

5. Thermosensitive and biocompatible polymer particles according to claim 3, characterized in that the change in the geometric shape consists in a return to an original shape which the polymers held before a heat-related change in shape (“shape-memory polymer”).

6. Thermosensitive and biocompatible polymer particles according to claim 1, characterized in that the magnetic colloids are ferromagnetic, superparamagnetic or ferrimagnetic particles or ferrites or a ferrofluid with a particle size <1 μm and a Curie temperature in the range from 30 ° C to 100 ° C ,

7. Thermosensitive and biocompatible polymer particles according to claim 1, characterized in that the metallic colloids consist of elements from group 8, 9, 10 or 11 (grouping: new proposal IUPAC 1986).

8. Thermosensitive and biocompatible polymer particles according to claims 1, 6 and 7, characterized in that the magnetic and / or metallic colloids are stabilized with at least one surface-active substance which prevent agglomeration of the colloids.

9. Thermosensitive and biocompatible polymer particles according to claim 8, characterized in that the surface-active substance (s) are alkyl and / or aryl group-bearing sulfonic acid, sulfonate or carboxylate derivatives or polyethylene glycol derivatives.

10. Thermosensitive and biocompatible polymer particles according to one of the preceding claims, characterized in that the polymers are crosslinked with a polyfunctional crosslinker selected from the group containing the dihalides, diisoσyanates, diisothiocyanates, dioxiranes, dialdehydes, divinyl derivatives.

11. Thermosensitive and biocompatible polymer particles according to claim 10, characterized in that the crosslinker has a concentration of 0.05 to 10 mol%, based on the polymer.

12. Thermosensitive and biocompatible polymer particles according to one of the preceding claims, characterized in that the polymers have reactive groups coupling to biomolecules.

13. Thermosensitive and biocompatible polymer particles according to claim 11, characterized in that the coupling groups with peptides, proteins, antibodies, antigens, enzymes, cell receptor antibodies, antibodies against tumor markers, antibody fragments, artificially produced antibodies, modified antibodies, antibody conjugates, oligosaccharides, glycoproteins , Lectins, nucleic acids, streptavidin or biotin are implemented.

14. Thermosensitive and biocompatible polymer particles according to one of the preceding claims, characterized in that active substances or pharmaceuticals are encapsulated in the polymers.

15. Thermosensitive and biocompatible polymer particles according to claim 14, characterized in that the encapsulated active substances or pharmaceuticals from the group Hormones, cytostatics, antibodies, antibody derivatives, antibody fragments, cytokines, immunomodulators, antigens, proteins, peptides, lectins, glycoproteins, nucleic acids, antisense nucleic acids, oligosaccharides, antibiotics or generics are selected.

16. A method for producing thermosensitive and biocompatible, by means of magnetic induction heatable polymer particles according to any one of the preceding claims.

17. The method according to claim 16, characterized in that the polymers are prepared by means of ring-opening polymerization, polycondensation, radical polymerization or ionic crosslinking.

18. The method according to claim 16, characterized in that the soluble polymer phase is dispersed in an organic phase which is not miscible with the polymer phase with stirring and by means of the suspension precipitation, the suspension crosslinking, the salting-out emulsion or the solvent evaporation process to give micro- or nanoparticulate Particle is solidified.

19. The method according to claims 16 to 18, characterized in that the magnetic and / or metallic colloids are added to the soluble polymer phase and these are present in the polymer matrix after the solidification of the polymer in colloidally dispersed form.

20. The method according to claim 19, characterized in that ferromagnetic, super-paramagnetic or ferrimagnetic substances or ferrites or ferrofluids with a particle size <1 μm are used as the magnetic colloids.

21. The method according to claim 20, characterized in that the concentration of the added magnetic and / or metallic colloid is 5 to 40 wt .-%, based on the polymer phase.

22. The method according to claim 18, characterized in that mineral oils or vegetable oils with a viscosity of 40 to 400 cp, organic, water-immiscible solvents or polyethylene glycols are used as the organic phase.

23. The method according to claim 22, characterized in that in the organic phase 0.1 to 10 vol% of one or more surface-active substance (s) is / are dissolved, which are selected from the group consisting of alkyl sulfosuccinates, polyoxyethylene aryl ethers, polyoxyethylenes, polyoxyethylene - Lensorbitan esters, polyoxyethylene adducts, polyethylene propylene oxide block copolymers, alkylphenoxypolyethoxyethanols, fatty alcohol polyethylene glycol ethers, polyglycerol esters, polyoxyethylene alcohols, polyoxyethylene sorbitan fatty acid esters, polyoxyethylene acids or mixtures thereof.

24. The method according to any one of claims 16 to 23, characterized in that the polymers peptides, proteins, antibodies, antigens, enzymes, cell receptor antibodies, antibodies against tumor markers, antibodies against tumor antigens, antibody fragments, artificially produced antibodies, modified antibodies, antibody conjugates , Oligosaccharides, glycoproteins, lectins, nucleic acids, streptavidin or biotin can be coupled.

25. The method according to any one of claims 16 to 24, characterized in that active substances or pharmaceuticals are encapsulated in the polymer particles.

26. The method according to claim 25, characterized in that hormones, cytostatics, antibodies, cytokines, immunomodulators, antigens, proteins, peptides, lectins, glycoproteins, nucleic acids, antisense nucleic acids, oligosaccharides, antibiotics or generics are used as the active substance.

27. Use of the thermosensitive and biocompatible polymer particles according to one of claims 1 to 15 as contrast-enhancing agents in NMR diagnostics, as carriers for active substances in medical therapy and diagnostics, as controllable carriers for reactants, as agents for controlling microfluidic processes , as a separation medium in column chromatography, as a means for adjusting and regulating pore sizes in membranes, as a means for blocking blood vessels in tumor treatment, as an artificial cell carrier, as a separation medium for nucleic acids, cells, proteins, steroids, viruses or bacteria.