GENE THERAPY DELIVERY SYSTEM FOR TARGETING TO ENDOTHELIA

Abstract: A composition comprising biodegradable microspheres that act as carriers for the delivery of DNA to the endothelial cells of a vascular bed, wherein the microspheres carry a net negative charge and to which is adsorbed positively charged particles of a smaller size, wherein such positively charged particles comprise a conjugate of DNA and a cationic compacting agent.

Description: GENE THERAPY DELIVERY SYSTEM FOR TARGETING TO ENDOTHEIJA The present invention relates to a novel embolism system for the delivery of gene therapy. Gene therapy offers exciting opportunities for the treatment of various diseases, including those that are inherited and conditions such as cancer and asthma, as well as for immunization (DNA vaccines). An important aspect in the success of gene therapy will be the development of appropriate delivery systems (often termed "vectors") that provide the gene construct with access to the target organ and, more particularly, to the target cells wherein transfection will occur. A good example is the treatment of inherited and acquired diseases in the lung (Curiel et al. (1996) Am. J. Resp. Cell. Mol. Biol. 14, 1-18). Two drug delivery routes are available for lung treatments. The drug can be delivered via the mouth in the form of an aerosol into the lung airways. For example, the preparation of lipid carrier-nucleic acid complexes for delivery to the lung airways by aerosol are described in PCT W093/1275. Such delivery is known to be extremely inefficient using existing powder and aerosol devices. More efficient delivery can be achieved using various nebulizer systems but these devices can cause degradation of the gene construct and also require substantial periods of time for a dose to be administered. Moreover, in many clinical conditions such as cystic fibrosis, the lungs contain mucus that prevents deep penetration of the delivery system into the lung and appropriate presentation of the gene construct to the target epithelial cells. An alternative means of delivery to the lung is to exploit the circulation system and to deliver the gene product to the lung endoώelia. The gene product can be injected into the venous or arterial supply and directed to the endothehal layer using appropriate delivery technologies. The prior art describes how this can be achieved using some form of ligand mediated approach using sugars or monoclonal antibodies or their fragments (see for example the studies of Huang, Holmberg et al, (1990) J. Liposome Res., 1, 393. This approach, while successful in animal models, is complex and does not lend itself easily to scale-up and manufacture under normal pharmaceutical processing. An alternative approach to delivery to the lung is to use particle systems wherein the particles have a size that will result in the temporary blockage or embolism of the capillary beds of the lungs. Particles larger than 4-5 μm in diameter will be filtered out by the lung capillaries, with high extraction and primarily to the alveolar segments (see for example Kanke et al, (1980) J.Pharm. Sci. 69, 755). The human lung is believed to have about 2.8 x 10 8 alveoli and 2.8 x 10 u capillary segments. Previously, a wide variety of colloidal systems has been examined as lung scanning agents including Au adsorbed onto carbon, m Ag and 203 Hg adsorbed onto ceramic materials, """Tc-ferric hydroxide aggregates as well as more recently, macroaggregates and microspheres made from human serum albumin. Metabolisable albumin microspheres labeled with m Tc, In or m In are the systems of choice (see Hagan et al, (1978) J. Nucl. Med., 19, 1055). Davis has indicated that the size range 13.5 ±1.5 μm diameter would be ideal; however, this was too narrow for commercial production and he has proposed a range 10 to 20 μm (15 ± 5 μm). Such systems have a large margin of safety, provided that the administered dose (particle number) is very small in comparison to the number of capillary segments, the toxicity being related to the size; large particles (90 μm in diameter) are more toxic than smaller ones (Davis, in Radiopkarmaceuticals, Ed. Subramanian et al, Soc. Nucl. Med. New York, 1975, p.267 and Davis and Taube (1978) J. Nucl. Med. 19, 1209). The rate of breakdown of albumin (either in the form of microaggregates or microspheres) is dependent on the so-called "hardness" of the system, which is related to the method of preparation and treatment (heating temperature, cross-linking agents, etc.). Total clearance from the lung field is generally seen within 24 hr but the rate of breakup of the microsphere and the loss of the label do not necessarily occur at the same rate. Ilium et al ((1982) Int. J. Pharm. 12, 135 and (1982; J. Pharm. Pharmacol. Suppl. 34, 89P) have used polystyrene particles surface labelled witii 131 I and ion exchange (DEAE) cellulose microspheres labelled with 131 I-rose bengal to investigate effects of particle size and particle shape on lung deposition. Polystyrene microspheres of 15.7 μm mean diameter and DEAE-cellulose microspheres 40 to 160 μm diameter at a dose of about 10 8 particles were rapidly taken up by the lungs and the particles were lodged in the lung capillaries. The lung entrapment and fate of albumin microspheres loaded with the drug adriamycin have been studied by Wilmott et al using the rat as an animal model (Wilmott et al in Microspheres and Drug Therapy. Pharmaceutical, Immunological and Medical Aspects edited by S S Davis, L Ilium, J G McVie and E Tomlinson 1984, Elsevier Science Publishers B.V., Amsterdam, p.205). The idea was that the particle would reside in the blocked capillary and thereby allow the retained drug to be released from the particle and diffuse into the tissues and reach the site of action. A similar embolism concept has been developed by the Swedish company, Pharmacia, with its Spherex (registered trade mark) system. This system is based upon degradable starch microspheres that are administered intravenously or intra arterially so as to reach organ sites in order to create a local embolism before the administration of a pharmacological agent, usually a drag used in the chemotherapy of cancer. The temporary embolism, once again, is intended to hold the drug at the target site for a prolonged period of time in order to maximize absorption of the drug into the surrounding tissues (see Lindberg et al in Microspheres and Drug Therapy. Pharmaceutical, Immunological and Medical Aspects edited by S S Davis, L Ilium, J McVie and E Tomlinson 1984, Elsevier Science Publishers, Amsterdam, p. 153). This embolism system is described for the lung and the liver. The encapsulation of synthetic ohgonucleotides and PCR generated DNA fragments into gelatin microspheres has been described by Cortesi et al, (1994) Int. J. Pharmaceut. 105, 181. Neither the attachment of DNA to the surface of preformed microspheres nor the use of such systems for delivery to the endothelial cells in the lung vasculature were described. We have devised a novel embolism system intended for the delivery of genes. Unlike the previously described drug delivery systems for lung targeting, we have deliberately arranged for the gene material to reside on the surface of the biodegradable microsphere that occludes the vascular bed on a temporary basis. In this manner, we have found that the gene product is presented to the endothelial surface in an extremely efficient manner, leading to improved cellular uptake and expression of e gene product. It will be understood that the embolism system may be used for organs other than the lung. For other organs the embolism system may be administered by injecting into the relevant artery. We have further discovered that it is important that the gene product is itself appropriately formulated, not only to provide good attachment to the surface of the carrier microsphere, but in a form that allows appropriate cell presentation and uptake. We have found that the simple adsorption of uncondensed DNA or plasmid DNA to a microsphere through a process of physical adsorption wherein the microsphere carries a positive charge that allows the strong binding of the negatively charged DNA, does not lead to beneficial expression within a cell culture model. Moreover, it is unlikely that a positively charged microsphere for use as a carrier would be approved for human use since such positively charged microspheres and other particles can be associated with toxic effects upon injection. In contrast, we have discovered that, if the DNA itself is first condensed into small particles of a size less than 1 μm, then good expression of the polypeptide encoded by the DNA can be achieved. Such condensation can be brought about by the use of cationic compacting agents such as cationic lipids or, preferably, by cationic polymers. A first aspect of the invention is a composition comprising biodegradable microspheres wherein the microspheres carry a net negative charge and to which is adsorbed positively charged particles of a smaller size, wherein such positively charged particles comprise a conjugate of DNA and a cationic compacting agent. It will be clear to the skilled person that the final composition will carry a net negative charge, will be neutral or will carry a small positive charge, depending on the net charge and size of the microsphere and the surface density and net charge of the adsorbed particles. A second aspect of the invention is a method of preparing said composition, the method comprising 1) preparation of positively charged particles comprising a conjugate of DNA and a cationic compacting agent, and 2) adsorbing said positively charged particles on to biodegradable microspheres carrying a net negative charge. By "adsorbing" is meant any form of non-covalent binding. The term "microsphere" is used herein to include both solid matrix microspheres and microcapsules. Biodegradable microspheres that are of the appropriate size and surface charge density can be formulated from a number of different materials, such as soluble starch, carrying carboxyl groups covalently linked to the starch, and polymers that contain groups that ionise to allow electrostatic interaction between positively charged DNA conjugates and the biodegradable microspheres. Such groups are preferably carboxyl or sulphate groups. Such polymeric materials include the alginates, heparin and other sulphated polysaccharides (carboxymethyl dextran, carboxydextran and dextran sulphate) and biodegradable synthetic polymers such as polylactide coglyceride and polylactic acid. Likewise, a physical mixture of polymers that is then converted into microspheres may be used. For example, heparin albumin microspheres have previously been described for the purposes of drug delivery (Kwon et al, (1991) J. Colloid Interface Sci. 143, 501 and Cremers et al, (1990) J. Controlled Release 11, 167. Such materials have not been described for use in gene therapy nor for the carriage of DNA conjugates. Hence, the biodegradable microspheres may be prepared from crosslinked soluble starch, albumin, gelatin, heparin, carboxydextran, dextran, dextran sulphate, alginate, polylactide, or their admixtures. The biodegradable microspheres, in order to provide embolism, should be preferably have an average size (mean number diameter, as determined by light microscopy) larger than 5 μm, more preferably between 6 and 200 μm, most preferably between 10 and 100 μm and still more preferably between 12-50 μm. The size of the biodegradable microsphere described herein refers to the size of the swollen particle in the vehicle chosen for intravenous administration. The properties of the carrier system can be so designed as to provide different rates of degradation and thereby control the period of contact between the carrier microsphere and, for example, the lung endothelial cells. The different rates of degradation can be achieved by methods known to those skilled in the art such as regulating the degree of crosslinking of the microspheres; the less crosslinked microspheres degrade faster than the microspheres which are crosslinked to a higher degree. Likewise for some polymers it is possible to control the rate of degradation by selection of lower molecular weight polymer chains for faster degradation and higher molecular weight polymer chains for slower degradation. For systems that are crosslinked by heating, the degree of crosslinking and therefore the rate of degradation can be controlled by the period of heating and the temperature. In order for the positively charged particles to be adsorbed onto the surface of biodegradable carrier microspheres, the carrier microsphere itself should have a net negative charge (zeta potential) of at least -1 mV, preferably at least -5 mV and more preferably at least -20 mV when measured using microelectrophoresis. Suitable microparticles for use the compositions of the invention are commercially available and include starch microspheres (such as Cadoxamer (Perstorp) and Spherex (Pharmacia Upjohn)), dextran microspheres (CM Sephadex (Pharmacia Upjohn) and SP Sephadex (Pharmacia Upjohn)) and agarose microspheres (CM Sepharose (Pharmacia Upjohn) and S Sepharose (Pharmacia Upjohn)). Albumin and gelatin microspheres may be prepared according to methods which are well known to those skilled in the art. Examples of cationic compacting agents include chitosan. By the term "chitosan" we mean polyglucosamine and oligomers of glucosamine materials of different molecular weights and degrees of acetylation. Modified chitosans, particularly those conjugated to polyethylene glycol, are included in this definition. Further examples of cationic compacting agents include, but are not limited to, polyamidoamines (including dendritic derivatives thereof), stearylamine, DOTMA (N-[l-(2,3- dioleoyloxy)propyl]-N,N,N-lτimethylammonium chloride), BISHOP (N- [(2,3-dihexadecyloxy)prop-l-yl]-N,N,N-trimethylammonium chloride), DODAC(B) (N,N-dimethyl-N-octadecyl-l-octadeca ammonium chloride (or bromide)), polylysine, lipofectin, lipofectamine, DMRIE (dimyristoyl Rosenthal Inhibitor ether), DC-cholesterol (dimethylaminoethyl carbamyl cholesterol). These compacting agents can be mixed with neutral zwitter ionic lipids such as DOPE (dioleoyl phosphatidyl ethanolamine) in order to elicit optimal effects. Other compacting agents include CTAB (cetyldimethylethyl ammonium bromide), DDAB (dimethyl dioctadecyl ammonium bromide), lipopolyamines such as dioctadecylamido glycylsperaύne and dipalmitoyl phosphatidyl ethanol amido speπnine, cationic derivatives of cholesterol, DOSP A (dioleoyl-N-(2-(speπninecarboxamido)ethyl-N , N-dimethyl- 1 - propanaminium trifluoroacetate). Such cationic compacting agents can either be used separately or in any combination. Such condensation processes have been described previously in the prior art with particular emphasis on the cationic polymer, polylysine. For example, polyelectrolyte complexes formed between DNA and polylysine have been described by Wolfert and Seymour (1996) Gene Therapy 3, 269. A preferred aspect of the invention is that the cationic compactmg agent is chitosan. In the present invention, compacted complexes of DNA are produced so that they carry a net positive charge. These are termed "conjugates". This can be accomplished using a cationic compacting agent as described above by titrating the cationic compacting agent into a solution of DNA and then measuring both the size of the resultant particle, but more importantly the surface charge using appropriate techniques such as Laser Doppler Anemometry that provides a measure of the zeta potential. The following example describes a method of preparing chitosan-DNA complexes. The method comprises mixing the two components together, the rate of mixing, the relative concentrations of the starting solution, the ratios of the two components, pH, ionic strength and temperature being such as to achieve the required particle size and charge. The rate of mixing, the relative concentrations of the starting solution, pH, ionic strength and temperature can be altered as part of a standard experimental design to control particle size. The ratios of the two components can also be used to control size and surface charge. The weight to weight ratio between nucleic acid and chitosan can be between 1:1 and 1:25, preferably between 1:2 and 1:20 and most preferably between 1:5 and 1:6. The size and size distribution of the complexes may be determined by Photon Correlation Spectroscopy (PCS) using a Malvern 4700 submicron particle analyser system (Malvern Instruments, UK) with a PCS 100 spectrometer. The samples are diluted with distilled water and measured at 25°C at a scattering angle of 90°. The size distribution is characterised by a polydispersity index (PI). We have found that die molecular weight of the chitosan influences the size of the compacted DNA complex, and indeed can be chosen so as to influence the size of the complex. To this end studies can be conducted using ethidium bromide fluorescence as described by Wolfert and Seymour (1996) Gene Therapy 3, 269-273. Ethidium bromide interacts with DNA to provide strong fluorescence. When a complexing cationic polymer is added the ethidium bromide is squeezed out of the complex and the fluorescence reduced. A plot of fluorescence against quantity of added polymer can be used to assess the compaction process (loss of fluorescence is indicative of degree of compaction) and thereby the selection of the appropriate molecular weight of the complexing chitosan species. Fluorescence may be measured using Perkin-Elmer 3000 Fluorescence Spectrometer, for example. The optical emission wavelength is set at 591 nm and optical excitation wavelength is set at 366 nm. Ethidium bromide (EtBr) is added to water in a cuvette (reference) and DNA solution and ethidium bromide to are added to water in a second cuvette (test). The fluorescence of the reference cuvette is set to zero. The fluorescence obtained for the test cuvette is measured. Chitosan samples are then introduced in very small portions to the test cuvette with constant stirring, and the fluorescence reading is taken three times, re rning to the zero cell in between each reading. The average of the three is then recorded. The molecular weight of the chitosan is preferably between 500 Dalton and 500,000 Dalton, more preferably 700 Dalton to 250,000 Dalton and most preferably 1,000 Dalton to 150,000 Dalton. Chitosans of different low molecular weight can be prepared by enzymatic degradation of chitosan using chitosanase or by the addition of nitrous acid. Both procedures are well known to those skilled in the art and are described in recent publications (Li et al, (1995) Plant Physiol. Biochem. 33, 599-603; Allan and Peyron, (1995) Carbohydrate Research 111, 257-272; Damard and Cartier, (1989) Int. J. Biol. Macromol. 11, 297-302). The positive charge of the DNA conjugate (the zeta potential) should be at least +5mV, preferably at least +10 mV and most preferably at least +20 mV, but preferably less than + 100 mV. The surface charge of the conjugates is expressed as a zeta potential. This is determined at pH 7.4 and 0.001 M ionic strength. The zeta potential is measured by Laser Doppler Anemometry (LDA) using for example a Malvern Zeta Sizer IV (Malvern, UK). Laser Doppler Anemometry involves the detection of scattered laser light from particles which are moving in an applied electric field. The equipment used can for example be a Malvern Zetasiser II (Malvern Instruments). Electrophoretic mobility measurements are carried out by dispersing the conjugates in 10 ml buffer solution such as phosphate or Mcllvaine buffer, from 100 μg - 1 mg, with a constant ionic strength 0.001M. Four readings are taken using a PC4 wide capillary cell at a voltage of 100 volt, electrode spacing of 50 mm and a dielectric constant of 78.54. Such positively charged conjugates with a size between 10-1000 nm can be separated from the excess complexing agent using procedures familiar to those skilled in the art. It is known that column separation methods are less than ideal for investigations with chitosan and similar cationic polymers. Instead, methods such as field flow fractionation using a cross-flow process (FF Fractionation, Salt Lake City, Utah; Ratanathanawongs and Giddings, (1993) ACT Symp. Ser. 521, 13) or continuous split-flow thin (SPLITT) cell can be employed as described by Levin and Giddings, (1991) J. Chem. Biotechnol. 50, 43; Williams et al (1992) Ind. Eng. Chem. Res. 31, 2172. At the research level, filter centrifugation tube systems can be used. In order for the DNA conjugate to provide good expression of me polypeptide encoded by the DNA, we have found that the conjugate should preferably be of a size below 1 μm, more preferably below 500 nm and most preferably below 200 nm. The conjugate preferably has a size of at least 10 nm (hydrodynamic diameter, as measured by photon correlation spectroscopy). By DNA we mean nucleic acids (including RNA) and ohgonucleotides greater than 100 base pairs in length or plasmids or cosmids, coiled or uncoiled. The DNA may be any DNA that expresses polypeptides and protein drugs that are useful in the treatment of diseases bo inherited and acquired that are localised in the lung. These include cystic fibrosis (cystic fibrosis transmembrane regulator), alpha 1-antitrypsin deficiency and lung cancer (genes to induce immunity or those that are directly tumoricidal). Immunity inducing genes include those encoding for MHC (major histocompatibility complex) molecules, co-stimulatory molecules and cytokines. Toxic systems include tumor expressed genes (p53) or enzymes that convert non toxic prodrags to toxic ones. Herpes thymidine kinase is an example. Pulmonary inflammation, surfactant deficiency, pulmonary hypertension and malignant mesothelioma are other conditions in which the compositions of the invention may be applied. However, the compositions may also be used for delivery of DNA to me lung where the lung is used as a bioreactor for polypeptides and proteins whose main site of action is elsewhere in the body (for example blood factors Xiπ, IX). By mis is meant that the DNA is expressed in the lung tissue, and the expressed polypeptides are secreted from the cells and enter the circulation, with the effect that the polypeptides are distributed to other parts of the body. It will be appreciated that the invention may also be used to deliver gene therapy into other body compartments such as joints, nasal cavity, vagina, rectum, eye, gastrointestinal tract, ear or buccal membrane. The compositions may comprise any DNA diat expresses polypeptides and protein drugs that are useful in the treatment of disease in mese compartments. Examples include antiinfective agents, antimflammatory agents, prophylactic agents and antigens that will lead to humoral and cell mediated responses i.e. antigenic material intended as a vaccine. The DNA may encode a viral, bacterial or parasite protein and thus be useful in vaccination against diseases such as tetanus, diphtheria, whooping cough and influenza. Gene products include but are not limited to alpha 1-antitrypsin, growth hormone synthase, factor VIH, factor IX, TNF, cytokines, antigen genes (hepatitis B, influenza, cholera), the cystic fibrosis transmembrane conductance regulator CTFR, cancer genes (p53, K-ras, HS-Ek), sucrose-isomaltase, lactase- phlorizin hydrolase and maltase-glucoamylase. The physical attachment of the conjugate to the larger biodegradable carrier microspheres can be undertaken using conventional formulation methods. The adsorption of the DNA conjugate on the microspheres can be carried out by methods known to those skilled in the art. For example, the microspheres may be suspended in a solvent such as water or a buffer of low ionic strength. The DNA conjugate is added to the suspension and the mixture left at room temperature with gentle shaking for a period of time sufficient to allow adsorption to take place, typically 1 - 3 hours. The excess DNA conjugate is separated from the microspheres by centrifuging at low speed (about 6000 rpm) for about 3 - 5 mins. The process by which one large microsphere carries many small particles on the surface has been described in the colloid science area and is known as "heterocoagulation" (see for example, Buscall et al, Polymer Colloids, Elsevier, London, 1985, p. 167). In such coagulation processes, it is important to ensure that the carrier microspheres are uniformly coated with the small nanoparticles radier than resulting in a gel interlinked or bridged system (Figure 1). This may be checked by standard techniques (e.g. microscopy or rheological techniques). A further aspect of the present invention is the use of the composition of the invention in medicine. It will be important that the dose of me microspheres administered to man or to a mammal is chosen such that only a small percentage of the available organ, for example lung, capillaries are blocked at any one time. The literature in the field of diagnostic imaging provides details of the doses that can be safely administered for such a purpose in diagnostic imaging (see Davis and Taube (1978) J. Nucl. Med. 19, 1209). In practice, not more than 10% of the lung capillaries should be so blocked. A suitable range of microspheres would be less than 10 x 10 10 in number, preferably 10 - 10 8 and more preferably 10 7 . Doses of microspheres of less than 500 mg and preferably 1 - 100 mg are suitable. Harding et al ((1973) J. Nucl. Med. 14, 579) have calculated that a 1 mg dose of albumin microspheres of 15 μm in diameter (equivalent to 5.7 x 10 5 particles) will block only 0.14% of the pulmonary arterial circulation. A photomicrograph showing how such microspheres can block the capillary beds to provide excellent contact between the particle surface and the endothelial cells of the lung capillary is shown in Figure 2. The long term residence of low doses of such microspheres in the pulmonary capillaries would appear to be without pathological effect (Davis and King, (1974) J. Nucl. Med. 15, 436). The degraded microsphere, once it is too small to block the capillary, will continue within the circulatory system and be removed by the liver through the normal process of particle recognition and subsequent phagocytosis. Here, die microsphere and its contents will be taken up by the Kupffer cells of the liver into a lysosomal compartment leading to the further degradation of the microsphere and more particularly to the degradation of the surface attached DNA material. Thus, me new delivery system for the lung should be able to provide site specific expression of a gene in the lung since any DNA material finding its way to the liver is likely to be effectively degraded and unable to provide expression. A composition of the invention may be administered intravenously or intra-arterially to a mammal. It may be delivered intravenously or intra-arterially to the lung endodielium of a mammal. It may also be delivered intra-arterially to a body compartment such as the joints, nasal cavity, vagina, rectum, eye, gastrointestinal tract, ear or buccal membrane. It may be administered such mat the DNA is delivered to the joints, nasal cavity, vagina, rectum, eye, gastrointestinal tract, ear or buccal membrane. For example, the composition may be administered into a blood vessel that supplies blood to the desired compartment. A further aspect of the invention is the use of a composition of the invention in a method of gene therapy. A further aspect of the invention is the use of a composition of the invention in the manufacmre of a medicament for the treatment of a mammal in need of gene therapy. A further aspect of me invention is a kit of parts for delivery of the compositions of the invention to a mammal, comprising compositions of the invention and sterile carrier components. For example, the pulmonary delivery system of this invention can be produced just prior to administration using sterile components or a preformed heterocoagulated particulate system can be produced using sterile components and then freeze dried for subsequent resuspension and administration. The present invention will now be described, by way of example, in more detail with reference to the following figures and examples. Figure 1: DNA-chitosan nanoparticle conjugates adsorbed to biodegradable microparticle Figure 2: photomicrograph showing microspheres in the lung capillary bed Figure 3: adsorption of DNA-chitosan complexes on negative charged starch microspheres. Approximately 50 μg DNA in 1.5 ml distilled water. Figure 4: microspheres wititi and without adsorbed complex. Example 1: Preparation of DNA-chitosan conjugates, and their adsorption on negatively charged starch microspheres. The following example describes the preparation of a starch microsphere particle carrying a CMV-CAT plasmid complexed with chitosan. A. Preparation of DNA-CTS (chitosan) complexes 26.4 mg of chitosan hydrochloride was dissolved in 18 ml of water. The solution was passed d-rough a 0.2 μm membrane filter (CTS solution). 15 ml of CTS solution was added drop wise into 50 ml of DNA solution (containing 2.2 mg pCAT-DNA) under magnetic stirring until the solution just started to be turbid (about 2 ml). The remaining CTS solution was then added quickly into the suspension (ml by ml). The resulting suspension (containing 33.8 μg/ml of DNA and 338 μg/ml of CTS) was stored at 4°C until use. The particles had a size of about 200 nm and a surface charge (zeta potential) of +35 mV. B. Purification of DNA-CTS complexes 0.4 ml of DNA/CTS complex suspension was added to a filter- centrifugation tube (100 nm cutoff) (Amicon) and centrifuged at 6500 m for 10 min. The complexes were resuspended in 0.3 ml of water and collected. 15 ml of sample was treated and me resulting cleaned complexes were contained in about 10 ml of water. C. Quantitative methods for assay of DNA-CTS complexes (spectrophotometry method) The turbidity of the complex suspension at the range 350-600 nm is too low to use for quantitative measurement. However, maximum absorbance at 259 nm (λ- nax of DNA) can be used as an alternative parameter for measurement of the complex. A good linear relation between tiie UV absorbance at 260 nm and me concentration of DNA- CTS complexes in the suspension fraction range of 0.2 B 1.0 (approx. 10-50 μg/ml DNA) was obtained. D. Adsoφtion of me complexes onto starch microspheres 0.1 ml of formulation B and 0.5 ml of 4% (w/v) starch microsphere suspension comprising carboxylated microspheres of an approximate size 50 μm (Cadoxamer from Perstoφ, Sweden) were added into 1.0 ml of DNA/CTS complex suspension. 0.5 ml of me starch microsphere suspension without the DNA-CTS complex was used as blank control and die 1.0 ml of DNA-CTS complex suspension without starch microspheres as standard control. The final volume of the samples was adjusted to 1.5 ml by adding a suitable amount of water. The samples were shaken on a vibratory shaker at room temperamre for 2 hours followed by centrifuging at 6500 m for 3 min. Only slight influence of the supernatant from starch microspheres on DNA measurement at 260 nm was found. The supernatant was taken and measured at 260 nm. The adsoφtion of the complexes was calculated by comparing the reduction of UV absorbance of me samples with that of DNA-CTS complex standard control (Figure 3). A linear increase in the surface adsoφtion of die DNA-CTS complex was found. The addition of 20 mg of starch microspheres gave rise to greater tiian 80% adsoφtion of the complex. Electronmicrographs showing adsorbed DNA-CTS complex on starch microspheres are shown in Figure 4. Example 2: Administration of the composition prepared as described in Example 1 to rabbits. The composition described in Example 1 was prepared and me microspheres carrying the DNA-conjugate separated by centrifugation and dispersed in sterile water for injection. New Zealand White female rabbits in a group of 3 were injected intravenously via the marginal ear vein with 10 6 particles in 0.5 ml. The animals were sacrificed 3 hours later and me lungs removed togemer with liver and spleen. Histological examination showed that me microspheres were largely sequestered by me lungs. The microspheres were found to deposit deeply into me capillary beds of die lungs. Example 3: Assay of gene expression - CAT analysis Materials The reporter gene pCAT-DNA driven by a CMV promoter was supplied by GeneMedicine, Houston, USA. ApCAT-DOTMA (N[l-(2,3- dioleoyloxy)-propyl]-NNN-trimethylammonium chloride) complex was used as a control material. This was prepared as outiined by Feigner et al, (1987), Proc. Natl. Acad. Sci. (UA) 84, 7415-7417. Methods A control pCAT DNA solution was prepared by die dilution of me pCAT-DNA stock solution (0.811 mg/ml) in autoclaved PBS. To 0.863 ml of the pCAT-DNA stock solution was added 13.137 ml of autoclaved PBS. This provided 14.0 ml of control pCAT-DNA solution (0.05 mg/ml), sufficient to dose six rabbits with 100 μg of pCAT-DNA in a volume of 2 ml. The solution was stored at 4°C and warmed to room temperamre 15 min prior to dosing me rabbits. A pCAT-DNA DOTMA formulation supplied in the form of lyophilised powder was reconstituted on me appropriate study day using sterile water. The resultant liquid formulations contained a sufficient concentration of plasmid DNA to administer a dose of 100 μg of pCAT- DNA in a volume of 2 ml. The formulation was stored at 4°C and warmed to room temperamre 15 min prior to dosing me rabbits. CAT ELISA The CAT ELISA procedure for the analysis of CAT in the animal tissues was set up following me protocol supplied by me manufacturer of the kit (Boerhinger Mannheim). The assay is based on me sandwich ELISA principle, where the anti-CAT antibody is prebound to me surface of the microtitre plate modules, me CAT enzyme in the extracts of the tissues, binds specifically to the immobilised anti-CAT antibody and digoxogenin-labeled antibody to CAT (anti-CAT-DIG) binds to CAT enzyme. The detection antibody, peroxidase conjugated anti-digoxigenin antibody (anti-DIG-POD) binds to digoxigenin. In die final step me peroxidase substrate (ABTS; 2,2'-azinobis[3-ethylbenzthiazoline sulphonic acid]) is catalysed by peroxidase yielding a colour reaction product which is enhanced by the use of a substrate enhancer. The absorbance of tiiis colour is then directly correlated to me amount of CAT enzyme present in the standards and the extracts. Validation of CAT ELISA Prior to analysing the test samples, the CAT ELISA procedure was validated. Since the appropriate quality control tissue samples containmg CAT were not available, both the intra-day and inter-day variations were determined using me standard curves. These curves were prepared using the CAT standards supplied in me CAT ELISA kit at CAT concentrations of 0.0, 15.6, 31.25, 62.5, 125, 250 and 500 pg/ml. The intra-day variation was determined by preparing the standard curve in triplicate. Both for the intra-day and inter-day variation me coefficient of variation (%CV) at each standard concentration was calculated. Validation of the tissue extraction procedures The tissue extraction procedure was initially established by taking the various tissue samples from two control rabbits dosed wifli "naked" plasmid DNA and storing separately at -80°C. 0.5 ml of ice-cold tissue extraction buffer (10 mM Tris pH 7 - 8; 150 mM NaCl, 1 mM EDTA, 0.5% Triton X- 100, 100 μM Leupeptin, 1.0 μM pepstatin and 0.25 mM PMSF) was added to die tube containing the tissue sample and homogenised four different times (0.6, 1.2 or 2.4 min) using a Mini- Bead Beater at 4°C. The homogenate was transferred to a sterilised microfuge tobe (1.5 ml) and centrifuged in an MSE Microfuge at 13,000 φm for 20 min at 4°C. The supernatant (ie. tissue extract) was transferred to a sterilised, microfuge tube (1.5 ml) and placed on ice. An aliquot of me tissue extract was diluted (1 in 20) with PBS and assayed for protein concentration using the BCA protein assay. Each sample was analysed in duplicate and corrected for dilution in order to obtain the total protein concentration (mg/ml) in the tissue extract. The CAT ELISA procedure was validated for the analysis of CAT in tiie gastrointestinal tissue extracts. Firsdy, the effect of protein concentration on the determination of CAT concentration in the various tissue extracts using the CAT ELISA procedure was assessed. Tissue samples from the control rabbits were extracted in ice-cold tissue extraction buffer (0.5 ml) as described above but were homogenised for 1.5 min (3 cycles of 30 sec. homogenisation and 30 sec. rest). After determining me protein concentration, the tissue extracts were diluted witfi Sample Buffer (CAT ELISA kit) to produce extract solutions with protein concentrations of approximately 0.5, 1.0 and 2.0 mg/ml). Each of these diluted extracts were spiked widi CAT standard (CAT ELISA kit) to given final CAT concentrations of 25 and 100 pg/ml. The spiked samples were then analysed in duplicate for CAT concentration and the percentage recovery of CAT in each sample was calculated. Secondly, the effect of extraction procedure on e stability of CAT in me various tissues was established. This was carried out by extracting the tissue samples from the above control rabbits with extraction buffer containing CAT concentrations of 50 or 200 pg/ml. After deteraiining die protein concentrations each sample extract was diluted (1 in 2 or 1 in 4) with me Sample Buffer. Each diluted sample was analysed in duplicate for CAT concentration. After correcting for dilution the percentage recovery of CAT in each tissue extract was calculated. Example 4: Administration to a patient A DNA: chitosan complex is prepared according to me method oudined in Example 1 above, with me exception that me DNA plasmid is a DNA plasmid expressing cystic fibrosis transmembrane conductance regulator. The complex preparation is controlled to obtain particles in the range 100 to 300 nm. The particles are freeze dried after me addition of 2.5 to 5% mannitol. Immediately prior to administration to a patient, an amount of DNA: chitosan complex equivalent to 100 μg DNA is dispersed in 1.0 ml water for injection (USP) together widi 20 mg of starch microspheres (Cadoxomer, Perstoφ, Sweden). The suspesnsion is injection into a vein of a patient. The material is also available as a kit consisting of a mixture of the required amount of freeze dried starch microspheres and DNA: chitosan complex, a vial containing 1 ml water for injection and a syringe for injection.

Claims: CLAIMS 1. A composition comprising biodegradable microspheres wherein the microspheres carry a net negative charge and to which is adsorbed positively charged particles of a smaller size, wherein such positively charged particles comprise a conjugate of DNA and a cationic compacting agent. 2. A composition accordmg to Claim 1 wherein the biodegradable microspheres are prepared from crosslinked soluble starch, albumin, gelatin, heparin, carboxydextran, dextran, dextran sulphate, alginate, polylactide or their admixtures. 3. A composition according to Claim 1 or Claim 2 wherein the catiomc compacting agent is chitosan. 4. A composition according to any one of Claims 1-3 wherein the biodegradable microspheres have an average size larger than 5 μm. 5. A composition according to any one of Claims 1-4 wherein the biodegradable microspheres carry a zeta potential of at least -5 mV before adsoφtion of me DNA conjugate. 6. A composition according to any one of Claims 1-5 wherein me DNA conjugate particles have an average size between 10 and 500 nm. 7. A composition according to any one of Claims 1-6 wherem me DNA conjugate has a positive surface charge (zeta potential) from 5 to 100 mV. 8. A method of preparing a composition which comprises 1) preparing positively charged particles comprising a conjugate of DNA and a cationic compacting agent, and 2) adsorbing of said positively charged particles on to biodegradable microspheres carrying a net negative charge. 9. A composition obtainable by a method according to Claim 8. 10. A composition according to any one of Claims 1-7 or 9, wherein the microspheres act as carriers for the delivery of DNA to me endomelial cells of a vascular bed. 11. A composition accordmg to any one of Claims 1-7, 9 or 10 for use in medicine. 12. A composition according to Claim 11 wherein the dose of administered microspheres is less than 10 x 10 10 in number or of a quantity less than 500 mg. 13. A method of delivery of DNA to a mammal wherein a composition according to any one of Claims 1-7, 9 or 10 is administered intravenously or intra-arterially to a mammal. 14. A memod according to Claim 13 in which e composition is delivered intravenously or intra-arterially to me lung endomelium of a mammal. 15. A method of treatment wherein a composition according to any one of Claims 1-7, 9 or 10 is delivered to me joints, nasal cavity, vagina, rectum, eye, gastrointestinal tract, ear or buccal membrane. 16. A method of treatment wherein a composition according to any one of Claims 1-7, 9 or 10 is administered such that the DNA is delivered to the joints, nasal cavity, vagina, rectum, eye, gastrointestinal tract, ear or buccal membrane. 17. A method according to Claim 13 in which the DNA is delivered to die lung endofhelium of a mammal. 18. Use of a composition according to any one of Claims 1-7, 9 or 10 in the manufacture of a medicament for me treatment of a niammal in need of gene therapy. 19. Use of a composition accordmg to any one of Claims 1-7, 9 or 10 in a method of gene dierapy. 20. A kit of parts for delivery of a composition according to any one of Claims 1-7, 9 or 10 to a mammal, comprising said composition and sterile carrier components. 21. A kit of parts for delivery of a composition according to any one of Claims 1-7, 9 or 10 to a mammal, comprising biodegradable microspheres carrying a net negative charge; positively charged particles of a smaller size, wherein such positively charged particles comprise a conjugate of DNA and a cationic compactmg agent; and sterile carrier components.

Inventors: ILLUM LISBETH, ILLUM, LISBETH
Applicants: DANBIOSYST UK, ILLUM LISBETH, DANBIOSYST UK LIMITED, ILLUM, LISBETH
Application year: 1997
Main classification: A61K47
IPC codes: A61K9, A61K47, A61K48, B82B1, C12N15