A METHOD FOR GENE THERAPY USING NUCLEIC ACID LOADED POLYMERIC MICROPARTICLES

Abstract: The invention involves methods and products for oral gene therapy. Genes under the control of promoters are protectively contained in microparticles and delivered to cells in operative form, thereby obtaining noninvasive gene delivery for gene therapy.

Description: A METHOD FOR GENE THERAPY USING NUCLETC ACID LOADED POLYMERIC MICROPARTICLES Background of the Invention This application claims priority under 35 USC § 119 to US application 60/001,365 entitled "Process for Preparing Microspheres Through Phase Inversion Phenomena" filed July 21, 1995 by Edith Mathiowitz, Donald E. Chickering III, Yong S. Jong and Jules S. Jacob. The application of gene therapy for the treatment of human disease has increased steadily since the first human gene therapy trial was conducted in 1989. To date, more than one hundred gene therapy protocols and clinical trials have been approved by the Recombinant DNA Advisory Committee (RAC) for the treatment of inherited and acquired diseases. Despite the reported advances in gene therapy technology and the increase of approvals in gene therapy protocols, obstacles still remain, including the difficulty in efficient delivery of exogenous genes in vivo. Gene therapy generally involves the introduction and expression in an animal of an exogenous gene to supplement or replace a defective or missing gene or to produce a product for treating an acquired disease. While there remains some debate about which vectors are most useful under which circumstances, the evolving challenge is not whether gene therapy will work, but rather determining which vectors are the most effective and which delivery schemes are most effective for carrying out gene therapy. Among the difficulties with delivering exogenous genes to cells for gene therapy is the cell wall itself. Some vectors and naked DNA do not efficiently penetrate mammalian cell walls. This is less of a problem in ex vivo applications where a variety of physio/chemical and mechanical technologies have been developed for introducing genes into cells. Many ofthese techniques, however, cannot be applied in vivo. Another problem with in vivo delivery of genes to cells is that complex structures such as vectors containing genes under the control of promoters do not fare well in certain physiological environments and are destroyed. These larger complex DNA molecules are unlike short antisense oligonucleotides which typically are modified to protect them against physiological degradation. The conditions that can destroy an operable gene in vivo are not the only barriers to delivery of genes for gene therapy. The preparative techniques for formulating delivery systems can be destructive to DNA as well. For example, many procedures for forming microparticles require high temperature and/or high sheer forces and/or sonication. Such conditions typically would destroy a vector containing a gene or would result in breakage of a large piece of DNA. Oral formulations of drugs, although most convenient to the patient, face severe obstacles to delivering the drug molecules to the target cells. This is particularly true for labile drugs such as pieces of DNA or genes. A first obstacle is the stomach. The environment ofthe stomach is extremely destructive to DNA, and most DNA (and especially large pieces of DNA) would not survive the environment ofthe stomach. Even if the DNA did survive the environment ofthe stomach, it then must be taken up by or passed between the cells lining the large and small intestine. Uptake of material across a mucosal epithelial barrier is a selective event, and not all molecules would be expected to be taken up by absoφtive and nonadsorptive epithelial cells and/or taken up into systemic circulation. Even if this obstacle is overcome, then the DNA still must resist destruction when in general circulation. The DNA also must gain access accross the membrane ofthe target cell which is to be transplanted. Finally, the DNA must be presented in a fashion that is nontoxic to the subject. For example, some viral vectors have been shown to induce severe immunological responses in the recipients and some liposomes have been shown to be toxic to recipients. US Patent 5, 075,109, entitled "METHOD OF POTENTIATING AN IMMUNE RESPONSE", issued to Tice, is directed to methods for oral administration of a bioactive agent contained in microparticles to protect the agent from degradation during its passage through the gastrointestinal tract. The patent is particularly directed to a method of oral immunization which will effectively stimulate the mucosal immune system and overcome the problem of degradation ofthe bioactive ingredient during its passage through the gastrointestinal tract to the Peyer's patch. The ' 109 patent involves administering bioactive agents contained in microcapsules that are sized between approximately one and ten microns. The microcapsules apparently survive the environment ofthe stomach and are taken up by the Peyer's patches to stimulate the immune response. The ' 109 patent does include the term "nucleic acids" as a member of a long list of materials regarded as "bioactive agents". The ' 109 patent does not mention the delivery of genes, the delivery of genes under the control of a promoter or the delivery of vectors including genes. This is perhaps because the methodology employed by Tice in making the microparticles is typical of prior art fabrication techniques, that is, aggressive emulsification conditions are applied, such as would destroy large pieces of DNA, in order to form the microparticles. In none ofthe prior art of which applicants are aware is there disclosed the notion of delivery in microparticles of genes under the control of promoters. Certainly, none disclose the notion of oral delivery of genes under the control of promoters. It is an object of the invention to provide a noninvasive method of carrying out gene therapy. Another object ofthe invention is to provide an oral means of carrying out gene therapy. Another object ofthe invention is to provide a method for microencapsulating large pieces of DNA, such as genes under the control of promoters and vectors, in a manner which does not destroy the DNA and that produces a high yield of DNA within the microcapsule. These and other objects are achieved by the present invention. Summary of the Invention The invention involves the discovery of a method for encapsulating oligonucleotides in a nondestructive fashion and in high yield. The invention further involves the discovery that microparticles can be used to deliver these oligonucleotides orally and in f nctional form, not only to intestinal epithelial cells but also to nonepithelial cells within the gastrointestinal system (e.g. Peyer's patches) and even to cells remote from the intestinal epithelium such as spleen or liver cells. The invention further involves the discovery that bioadhesive microspheres. instead of simply increasing residence time upon attachment to a mucosal epithelium, suφrisingly, are: (1) taken up into the epithelial cells, including absoφtive intestinal epithelial cells; (2) taken up into gut associated lymphoid tissue; and (3) even transported to cells remote from the mucosal epithelium. The microparticles containing the oligonucleotides preferably are between 10 nanometers and five microns. In some important embodiments, the microparticles have an average particle size consisting of between 100 nanometers and three microns. Most preferably, the microparticles are prepared by phase inversion nanoencapsulation. The oligonucleotides are in bioactive form when released from the microparticles. Suφrisingly, we have established that genes under the control of promoters can be protectively contained in microparticles and delivered to cells in operative form, thereby obtaining noninvasive gene delivery for gene therapy. The invention overcomes extraordinary obstacles: (1) the genes are not destroyed, disrupted or inactivated by the manufacturing technique for producing the microparticles; (2) the microparticles protect the genes from the destructive environment ofthe stomach; (3) the microparticles enter the target cells; (4) the microparticles cause transfection ofthe cells with the genes; (5) the microparticles can deliver the genes to sites remote from the mucosal epithelium, i.e. can cross the epithelial barrier and enter into general circulation, thereby transfecting cells at other locations. According to one aspect ofthe invention, a method for delivering a gene to a cell of a subject for gene therapy is provided. An effective amount of bioadhesive microparticles containing an isolated gene under the control of a promoter is administered noninvasively to a mucosal epithelial surface of a subject in need of such treatment. Preferably the bioadhesive microparticles consist of microparticles having an average particles size of between ten nanometers and five microns. In one embodiment, the microparticles consist of microparticles having an average particle size of between one hundred nanometers and three microns. The preferred bioadhesive microparticles comprise polyanhydrides, most preferably poly(fumaric-co- sebacic)anhydride. Preferably, they also contain metal oxides or hydroxides. Preferably, they further contain anhydride oligomers. Most preferably the bioadhesive microparticles have bioadhesive properties at least as strong as 20:80 poly(fumaric-co-sebacic)anhydride. The microparticles can be administered non-invasively, such as by oral formulation and by aerosols for the respiratory tract. In some embodiments, the gene is delivered to and transforms an epithelial cell. In other embodiments the gene is delivered to and transforms a nonepithelial cell. According to another aspect of the invention, a method is provided for delivering a gene to a cell of a subject for gene therapy. An effective amount of microparticles containing an isolated gene under the control of a promoter is administered orally to a subject in need of such treatment. The microparticles consist of microparticles having an average particle size of between ten nanometers and five microns. In one embodiment, the microparticles have an average particle size of between one hundred nanometers and three microns. The microparticles may be delivered to and transfect an epithelial cell or may be delivered across such epithelial cells to nonepithelial cells which are transformed by the gene. In one embodiment the cell is a gut associated lymphatic tissue cell. In another embodiment the cell is an adsoφtive epithelial cell. In yet another embodiment, the microparticle is taken up into systemic circulation and the cell transfected is a nonepithelial cell remote from the epithelial barrier, such as, for example, a spleen cell or a liver cell. It is preferred that the microparticles are bioadhesive microparticles, as described above. According to another aspect ofthe invention. a method is provided for noninvasive delivery of a gene into systemic circulation of a subject for gene therapy. Microparticles containing a gene under the control of a promoter are administered noninvasively to a mucosal epithelial surface of a subject in need of such treatment. The microparticles are in an effective amount and consist of microparticles having an average particle size of between ten nanometers and five microns. In one embodiment the average particles size is between one hundred nanometers and three microns. The modes of delivery and the preferred microparticles are as described above. According to another aspect ofthe invention. an article of manufacture is provided. The article of manufacture is a preparation consisting essentially of microparticles containing an isolated gene under the control of a promoter. The microparticle preferably is bioadhesive. In one embodiment the microparticles consist of microparticles having an average particle size of between ten nanometers and five microns. In other embodiments, the microparticles consist of microparticles having an average particle size of between one hundred nanometers and three microns. The preferred bioadhesive microparticles are as described above. According to another aspect ofthe invention, a phaπnaceutical preparation for gene therapy is provided. The preparation contains an effective amount of microparticles containing a gene under the control of a promoter, wherein the microparticles consist of microparticles having an average particle size of between ten nanometers and five microns. In some embodiments, the microparticles consist of microparticles having an average particle size of between one hundred nanometers and three microns. The preparation also can include a pharmaceutically acceptable carrier suitable, for example, for oral administration to a subject wherein the pharmaceutical preparation is formulated as an oral dosage. The invention also involves the use of any one ofthe foregoing materials for gene therapy. A particularly important embodiment involves a formulation for oral administration or administration by inhalation. These and other aspects ofthe invention are described in greater detail below. Brief Description of the Drawing Fig. 1 is a graph depicting a luminometry assay of bacterial β - galactosidase activity in tissue homogenates resulting from oral delivery of β - galactosidase gene in microparticles. Detailed Description of the Invention The invention involves a gentle process for the microencapsulation of DNA, and in particular, genes under the control of promoters and vectors containing genes under the control of promoters. Microparticles, microcapsules and microspheres (here and after "microparticles") have been used in the pharmaceutical, agricultural, textile and cosmetic industry as delivery vehicles. Microparticles of a very small size have not been used for the encapsulation of genes under the control of promoters. Many microencapsulation techniques exist which can produce a variety of particle types and sizes under various conditions. Those methods that involve aggressive emulsification procedures or other procedures that would tend to break, degrade, or otherwise inactivate genes under the control of promoters are not useful according to the present invention. The present invention, in part, was prompted by the discovery of a novel method of creating microparticles having the size of five microns or less under extremely gentle processing conditions. It has been discovered, suφrisingly, that genes under the control of promoters can be delivered, in operable form, noninvasively to epithelial surfaces for gene therapy: The genes in the microparticles, not only gain access to and transfect eithelial cells, but also pass across epithelial barriers, gaining access to and transfecting cells proximal to the epithelial cells and even cells remote from the epithelial barriers, transported via systemic circulation. Even more suφrising, it has been discovered that genes can be delivered to and can transfect such cells when administered orally. It is believed that the invention represents the first demonstration of oral gene delivery to intestinal epithelial cells, Peyer's patches, spleen cells, liver cells and the like. The fabrication process, dubbed "Phase Inversion Nanoencapsulation" or "PIN", differs from existing methods of encapsulation in that it is essentially a one-step process, is nearly instantaneous, and does not require emulsification ofthe solvent. Under proper conditions, low viscosity polymer solutions can be forced to phase invert into fragmented spherical polymer particles when added to appropriate nonsolvents. Phase inversion phenomenon has been applied to produce macro and microporous polymer membranes and hollow fibers. The basis for the formation of such membranes or fibers, as well as the process ofthe invention, depends upon the mechanism of microphase separation. A prevalent theory of microphase separation is based upon the belief that "primary" particles form of about 50nm diameter, as the initial precipitation event resulting from solvent removal. As the process continues, primary particles are believed to collide and coalesce forming "secondary" particles with dimensions of approximately 200nm, which eventually join with other particles to form the polymer matrix. An alternative theory, "nucleation and growth", is based upon the notion that a polymer precipitates around a core micellar structure (in contrast to coalescence of primary particles). The fact that the present invention results in a very uniform size distribution of small particles forming at lower polymer concentrations without coalescing supports the nucleation and growth theory, while not excluding coalescence at higher polymer concentrations (e.g., greater than 10% weight per volume) where larger particles and even aggregates can be formed. (Solvent would be extracted more slowly from larger particles, so that random collisions ofthe partially-solvated spheres would result in coalescence and, ultimately, formation of fibrous networks.) By adjusting polymer concentration, polymer molecular weight, viscosity, miscibility and solvent:nonsolvent volume ratios, the interfibrillar interconnections characteristic of membranes using phase inversion are avoided, with the result being that microparticles are spontaneously formed. As will be seen from the examples below, as well as the following discussion, the foregoing parameters are interrelated and the adjustment of one will influence the absolute value permitted for another. In the prefeπed processing method, a mixture is formed ofthe agent to be encapsulated, a polymer and a solvent for the polymer. The agent to be encapsulated may be in liquid or solid form. It may be dissolved in the solvent or dispersed in the solvent. The agent thus may be contained in microdroplets dispersed in the solvent or may be dispersed as solid microparticles in the solvent. The phase inversion process thus can be used to encapsulate a wide variety of agents by including them in either micronized solid form or else emulsified liquid form in the polymer solution. The loading range for the agent within the microparticles is between 0.01-80% (agent weight/polymer weight). When working with nanospheres, an optimal range is 0.1-5% (weight/weight). The agent is added to the polymer solvent, preferably after the polymer is dissolved in the solvent. The solvent is any suitable solvent for dissolving the polymer. Typically the solvent will be a common organic solvent such as a halogenated aliphatic hydrocarbon such as methylene chloride, chloroform and the like; an alcohol; an aromatic hydrocarbon such as toluene; a halogenated aromatic hydrocarbon; an ether such as methyl t-butyl; a cyclic ether such as tetrahydrofuran; ethyl acetate; diethylcarbonate; acetone; or cydohexane. The solvents may be used alone or in combination. The solvent chosen must be capable of dissolving the polymer, and it is desirable that the solvent be inert with respect to the agent being encapsulated and with respect to the polymer. The polymer may be any suitable mircoencapsulation material including, but not limited to, nonbioerodable and bioerodable polymers. Such polymers have been described in great detail in the prior art. A list of suitable polymers is provided below. The working molecular weight range for the polymer is on the order of 1 kDa- 150,000 kDa, although the optimal range is 2kDa-50kDa. The working range of polymer concentration for the phase inversion method is 0.01-50% (weight/volume), depending primarily upon the molecular weight ofthe polymer and the resulting viscosity ofthe polymer solution. In general, the low molecular weight polymers permit usage of a higher concentration of polymer. The prefeπed concentration range according to the invention will be on the order of .1%-10% (weight/volume), while the optimal polymer concentration typically will be below 5%. It has been found that polymer concentrations on the order of 1 -5% are particularly useful according to the methods ofthe invention. The viscosity ofthe polymer solution preferably is less than 3.5 centipoise and more preferably less than 2 centipoise, although higher viscosities such as 4 or even 6 centipoise are possible depending upon adjustment of other parameters such as molecular weight ofthe polymer. The molecular weight of the polymer also will affect particle size. It will be appreciated by those of ordinary skill in the art that polymer concentration, polymer molecular weight, and viscosity are inteπelated and that varying one will likely affect the others. The nonsolvent, or extraction medium, is selected based upon its miscibility in the solvent. Thus, the solvent and nonsolvent are thought of as "pairs". We have determined that the solubility parameter (δ (cal/cm 3 )' /: ) is a useful indicator ofthe suitability ofthe solvent/nonsolvent pairs. The solubility parameter is an effective predicter ofthe miscibility of two solvents and, generally, higher values indicate a more hydrophilic liquid while lower values represent a more hydrophobic liquid (e.g., δj water=23.4 (cal/cm 3 ) Vl whereas δ,hexane=7.3 (cal/cm 3 )!/2). We have determined that solvent/nonsolvent pairs are useful where 0<δ solvent - δ nonsolvent <6 (cal/cm 3 )' 72 . Although not wishing to be bound by any theory, an inteφretation of this finding is that miscibility ofthe solvent and the nonsolvent is important for formation of precipitation nuclei which ultimately serve as foci for particle growth. If the polymer solution is totally immiscibile in the nonsolvent, then solvent extraction does not occur and nanoparticles are not formed. An intermediate case would involve a solvent/nonsolvent pair with slight miscibility, in which the rate of solvent removal would not be quick enough to form discreet microparticles, resulting in aggregation of coalescence ofthe particles. It, suφrisingly, was discovered that nanoparticles generated using "hydrophilic" solvent/nonsolvent pairs (e.g., a polymer dissolved in methylene chloride with ethanol as the nonsolvent) yielded approximately 100% smaller particles than when "hydrophobic" solvent/nonsolvent pairs were used (e.g., the same polymer dissolved in methylene chloride with hexane as the nonsolvent). Similarly, it was discovered, suφrisingly, that the solventnonsolvent volume ratio was important in determining whether microparticles would be formed without particle aggregation or coalescence. A suitable working range for solvent:nonsolvent volume ratio is believed to be 1 :40-l : 1,000,000. An optimal working range for the volume ratios for solvent:nonsolvent is believed to be 1 :50-l :200 (volume per volume). Ratios of less than approximately 1 :40 resulted in particle coalescence, presumably due to incomplete solvent extraction or else a slower rate of solvent diffusion into the bulk nonsolvent phase. It will be understood by those of ordinary skill in the art that the ranges given above are not absolute, but instead are inteπelated. For example, although it is believed that the solvent:nonsolvent minimum volume ratio is on the order of 1 :40, it is possible that microparticles still might be formed at lower ratios such as 1 :30 if the polymer concentration is extremely low, the viscosity ofthe polymer solution is extremely low and the miscibility of the solvent and nonsolvent is high. Thus, the polymer is dissolved in an effective amount of solvent, and the mixture of agent, polymer and polymer solvent is introduced into an effective amount of a nonsolvent, so as to produce polymer concentrations, viscosities and solvent:nonsolvent volume ratios that cause the spontaneous and virtually instantaneous formation of microparticles. As will be seen from the examples below, a variety of polymers have been tested in the methods of the invention, including polyesters such as poly(lactic acid), poly(lactide-co- glycolide) in molar ratios of 50:50 and 75:25; polycaprolactone; polyanhydrides such as poly(fumaric-co-sabacic) acid or P(FA:SA) in molar ratios of 20:80 and 50:50; poly(carboxyphenoxypropane-co-sebacic) acid or P(CPP:SA) in molar ratio of 20:80; and polystyrenes or PS. Nanospheres and microspheres in the range of lOnm to lOμm have been produced according to the methods ofthe invention. Using initial polymer concentrations in the range of 1-2% (weight/volume) and solution viscosities of 1-2 centipoise, with a "good" solvent such as methylene chloride and a strong non-solvent such as petroleum ether or hexane, in an optimal 1 :100 volume ratio, generates particles with sizes ranging from 100-500nm. Under similar conditions, initial polymer concentrations of 2-5% (weight/volume) and solution viscosities of 2- 3 centipoise typically produce particles with sizes of 500-3,000nm. Using very low molecular weight polymers (less than 5 kDa), the viscosity ofthe initial solution may be low enough to enable the use of higher than 10% (weight/volume) initial polymer concentrations which generally result in microspheres with sizes ranging from 1-1 Oμm. In general, it is likely that concentrations of 15% (weight/volume) and solution viscosities greater than about 3.5 centipoise discreet microspheres will not form but, instead, will iπeversibly coalesce into intricate, interconnecting fibrilar networks with micron thickness dimensions. It is noted that only a limited number of microencapsulation techniques can produce particles smaller than 10 microns, and those techniques are associated with significant losses of polymer, the material to be encapsulated, or both. This is particularly problematic where the active agent is a gene under the control of a promoter, which large DNA molecules are particularly labile to manufacturing processes and are extremely expensive to produce. The present invention provides a method to produce nano to micro-sized particles with minimal losses. The described methods can result in product yields greater than 80%. The methods ofthe invention also can produce microparticles characterized by a homogeneous size distribution. Typical microencapsulation techniques produce heterogeneous size distributions ranging from lOμm to mm sizes. Prior art methodologies attempt to control particle size by parameters such as stiπing rate, temperature, polymer/suspension bath ratio, etc. Such parameters, however, have not resulted in a significant naπowing of size distribution. The present invention can produce, for example, nanometer sized particles which are relatively monodisperse in size. By producing a microparticle that has a well defined and less variable size, the properties ofthe microparticle such as when used for release of a bioactive agent can be better controlled. Thus, the invention permits improvements in the preparation of sustained release formulations for administration to subjects. As mentioned above, the methods ofthe invention can be, in many cases, carried out in less than five minutes in the entirety. It is typical that preparation time may take anywhere from one minute to several hours, depending on the solubility ofthe polymer and the chosen solvent, whether the agent will be dissolved or dispersed in the solvent and so on. Nonetheless, the actual encapsulation time typically is less than thirty seconds. After formation ofthe microcapsules, they are collected by centrifugation, filtration, and the like. Filtering and drying may take several minutes to an hour depending on the quantity of material encapsulated and the methods used for drying the nonsolvent. The process in its entirety may be discontinuous or a continuous process. Because the process does not require forming the solvent into an emulsion, it generally speaking may be regarded as a more gentle process than those that require emulsification. As a result, materials such as whole plasmids including genes under the control of promoters can be encapsulated without destruction ofthe DNA as a result ofthe emulsification process. Thus the invention particularly contemplates encapsulating oligonucleotides such as plasmids, vectors, external guide sequences for RNAase P, ribozymes and other sensitive oligonucleotides, the structure and function of which could be adversely affected by aggressive emulsification conditions and other parameters typical of certain ofthe prior art processes. Delivery of antisense, of course, also is possible according to this invention. Included in Table I below are examples of a variety of polymers, solvents, viscosities, nonsolvents, and concentrations tested in the phase inversion process used for manufacturing microparticles. Table 1 Polymer MW Concen¬ Viscosity Solvent Non- Drug Concen¬ Product tration Solvent tration polystyrene 2K 5% MeCl, pet ether rhodamine 0.1% polystyrene 2K 10% MeCl 2 pet ether rhodamine 0.1% polystyrene 50K 1% MeCl, pet ether none - polystyrene 50K 1% MeCl 2 pet ether rhodamine 0.1% 1-5 μm polystyrene 50K 3% MeCl, pet ether rhodamine 0.1% polystyrene 50K 5% MeCl, pet ether rhodamine 0.1% 500 nm -2 μm polystyrene 50K 10% MeCl, pet ether rhodamine 0.1% 1-4 μm polystyrene 50K 15% MeCl 2 pet ether rhodamine 0.1% 1-10 μm & aggr Table 1 polystyrene 50K 20% MeCl, pet ether rhodamine 0.1% large aggre¬ gate polystyrene 50K 1% MeCl, ethanol rhodamine 0.1% polystyrene 50K 5% MeCl, ethanol rhodamine 0.1% <100 nm polystyrene 50K 10% MeCl, ethanol rhodamine 0.1% <100 nm - 3 μm polycapro- 72K 1% 3.188 MeCl, pet ether rhodamine 0.1% 1-3 μm lactone polycapro- 72K 5% 7.634 MeCl, pet ether rhodamine 0.1% 1-3 μm lactone large aggr polycapro- 1 12 1% 4.344 MeCl, pet ether rhodamine 0.1% 500 nm - lactone K 5μm polycapro- 112 5% MeCl, ethanol rhodamine 0.1% Large lactone K aggre¬ gate polyvinyl- 1.5- 1% acetone pet ether none - 250 nm - phenol 7K 1 μm polyvinyl- 1.5- 5% acetone pet ether none - phenol 7K polyvinyl- 1.5- 10% acetone pet ether none - phenol 7K polyvinyl- 9- 1% acetone pet ether none - 100 nm - phenol 11K 2 μm polyvinyl- 9- 5% acetone pet ether none - 250 nm - phenol 11K 2.5 μm polyvinyl- 9- 10% acetone pet ether none - 500 nm - phenol 1 1K 10 μm polylactic 2K 1% 0.876 MeCl, pet ether rhodamine 0.1% lOO nm acid Table 1 polylactic 2K 5% 1.143 MeCl, pet ether rhodamine 0.1% 500 nm - acid 2 μm polylactic 2K 10% 2.299 MeCl 2 pet ether rhodamine 0.1% 1-10 μm acid brittle polylactic 24K 1% 1.765 MeCl, pet ether rhodamine 0.1% lOO nm acid polylactic 24K 5% 2.654 MeCl, pet ether rhodamine 0.1% 500 nm - acid 1 μm polylactic 24K 10% 3.722 MeCl 2 pet ether rhodamine 0.1% 10 μm acid aggr polylactic 40- 1% 2.299 MeCl, pet ether rhodamine 0.1% acid 100 K polylactic 40- 5% 2.832 MeCl, pet ether rhodamine 0.1% acid 100 K polylactic 40- 10% 6.122 MeCl, pet ether rhodamine 0.1% acid 100 polylactic 100 1% 2.566 MeCl, pet ether rhodamine 0.1% l OO nm acid poly- lactic 100 5% 4.433 MeCl, pet ether rhodamine 0.1% 500 nm - acid K 2 μm aggr poly-lactic 100 10% 8.256 MeCl, pet ether rhodamine 0.1% film/ acid K aggr ethylene- 55K 1% MeCl, pet ether rhodamine 0.1% Globu¬ vinyl acetate lar strands ethylene- 55K 5% MeCl 2 pet ether rhodamine 0.1% co¬ vinyl acetate alesced strands Table 1 ethylene- 55K 10% MeCl, pet ether rhodamine 0.1% con¬ vinyl acetate tinuous sheet PAN PVC 1% 2.566 acetone pet ether none - coarse 1-20 μm PAN/PVC 5% 15.903 acetone pet ether none - 100 μm aggr It will be understood by those of ordinary skill in the art that the microparticles can be formed by other processes such as by certain spray drying technologies. Spray drying is typically a process for preparing 1-10 micron sized microspheres in which the core material to be encapsulated is dispersed or dissolved in the polymer solution (typically aqueous). The solution or dispersion is pumped through a micronizing nozzel driven by a flow of compressed gas, and the resulting aerosol is suspended in a heated cyclone of air, allowing the solvent to evaporate from the microdroplets . The solidified particles pass into a second chamber and are trapped in a collection flask. Numerous polymers can be used to prepare DNA containing microparticles. They include, but are not limited to: polyamides, polycarbonates, polyalkylenes, polyalkylene glycols, polyalkylene oxides, polyalkylene terepthalates, polyvinyl alcohols, polyvinyl ethers, polyvinyl esters, polyvinyl halides, polyvinylpyπolidone, polyglycolides, polysiloxanes. polyurethanes and copolymers thereof, alkyl cellulose, hydroxyalkyi celluloses, cellulose ethers, cellulose esters, nitro celluloses, polymers of acrylic and methacrylic esters, methyl cellulose, ethyl cellulose, hydroxypropyl cellulose, hydroxy-propyl methyl cellulose, hydroxybutyl methyl cellulose, cellulose acetate, cellulose propionate, cellulose acetate butyrate, cellulose acetate phthalate, carboxylethyl cellulose, cellulose triacetate, cellulose sulphate sodium salt, poly (methyl methacrylate), poly(ethylmethacrylate), poly(butylmethacrylate), poly(isobutylmethacrylate), poly(hexlmethacrylate), poly(isodecylmethacrylate), poly(lauryl methacrylate), poly (phenyl methacrylate), poly(methyl acrylate), poly(isopropyl acrylate), poly(isobutyl acrylate), poly(octadecyl acrylate), polyethylene, polypropylene polyethylene glycol), poly(ethylene oxide), poly(ethylene terephthalate), poly(vinyl alcohols), poly(vinyl acetate, poly vinyl chloride polystyrene and polyvinylpryπolidone. Examples of prefeπed non-biodegradable polymers include ethylene vinyl acetate, poly(meth) acrylic acid, polyamides, copolymers and mixtures thereof. Examples of prefeπed biodegradable polymers include synthetic polymers such as polymers of lactic acid and glycolic acid, polyanhydrides, poly(ortho)esters, polyurethanes, poly(butic acid), poly(valeric acid), poly(caprolactone), poly(hydroxybutyrate), poly(lactide-co- glycolide) and poly(lactide-co-caprolactone), and natural polymers such as algninate and other polysaccharides including dextran and cellulose, collagen, chemical derivatives thereof (substitutions, additions of chemical groups, for example, alkyl, alkylene, hydroxylations, oxidations, and other modifications routinely made by those skilled in the art), albumin and other hydrophilic proteins, zein and other prolamines and hydrophobic proteins, copolymers and mixtures thereof. In general, these materials degrade either by enzymatic hydrolysis or exposure to water in vivo, by surface or bulk erosion. The foregoing materials may be used alone, as physical mixtures (blends), or as a co-polymer. The most prefeπed polymers are polyesters, polyanhydrides, polystyrenes and blends thereof. Particularly prefeπed are bioadhesive polymers. A bioadhesive polymer is one that binds to mucosal epithelium under normal physiological conditions. Bioadhesion in the gastrointestinal tract proceeds in two stages: (1) viscoelastic deformation at the point of contact ofthe synthetic material into the mucus substrate, and (2) formation of bonds between the adhesive synthetic material and the mucus or the epithelial cells. In general, adhesion of polymers to tissues may be achieved by (i) physical or mechanical bonds, (ii) primary or covalent chemical bonds, and/or (iii) secondary chemical bonds (i.e., ionic). Physical or mechanical bonds can result from deposition and inclusion ofthe adhesive material in the crevices ofthe mucus or the folds ofthe mucosa. Secondary chemical bonds, contributing to bioadhesive properties, consist of dispersive interactions (i.e., Van der Waals interactions) and stronger specific interactions, which include hydrogen bonds. The hydrophilic functional groups primarily responsible for forming hydrogen bonds are the hydroxyl and the carboxylic groups. Numerous bioadhesive polymers are discussed in that application. Representative bioadhesive polymers of particular interest include bioerodible hydrogels described by H.S. Sawhney, CP. Pathak and J.A. Hubell in Macromolecules. 1993, 26:581-587, the teachings of which are incoφorated herein, polyhyaluronic acids, casein, gelatin, glutin, polyanhydrides, polyacrylic acid, alginate, chitosan, poly(methyl methacrylates), poly(ethyl methacrylates), poly(butyl methacrylate), poly(isobutyl methacrylate), poly(hexl methacrylate), poly(isodecl methacrylate), poly(lauryl methacrylate), poly(phenyl methacrylate), poly (methyl acrylate), poly(isopropyl acrylate), poly(isobutyl acrylate), and poly(octadecl acrylate). Most prefeπed is poly(fumaric- co-sebacic) acid. Polymers with enhanced bioadhesive properties can be provided wherein anhydride monomers or oligomers are incoφorated into the polymer. The oligomer excipients can be blended or incoφorated into a wide range of hydrophilic and hydrophobic polymers including proteins, polysaccharides and synthetic biocompatible polymers. Anhydride oligomers may be combined with metal oxide particles to improve bioadhesion even more than with the organic additives alone. Organic dyes because of their electronic charge and hydrophobicity/hydrophilicity can either increase or decrease the bioadhesive properties of polymers when incoφorated into the polymers. The incoφoration of oligomer compounds into a wide range of different polymers which are not normally bioadhesive dramatically increases their adherence to tissue surfaces such as mucosal membranes. As used herein. the term "anhydride oligomer" refers to a diacid or polydiacids linked by anhydride bonds, and having carboxy end groups linked to a monoacid such as acetic acid by anhydride bonds. The anhydride oligomers have a molecular weight less than about 5000, typically between about 100 and 5000 daltons, or are defined as including between one to about 20 diacid units linked by anhydride bonds. In one embodiment, the diacids are those normally found in the Krebs glycolysis cycle. The anhydride oligomer compounds have high chemical reactivity. The oligomers can be formed in a reflux reaction ofthe diacid with excess acetic anhydride. The excess acetic anhydride is evaporated under vacuum, and the resulting oligomer, which is a mixture of species which include between about one to twenty diacid units linked by anhydride bonds, is purified by recrystallizing, for example from toluene or other organic solvents. The oligomer is collected by filtration, and washed, for example, in ethers. The reaction produces anhydride oligomers of mono and poly acids with terminal carboxylic acid groups linked to each other by anhydride linkages. The anhydride oligomer is hydrolytically labile. As analyzed by gel permeation chromatography, the molecular weight may be, for example, on the order of 200-400 for fumaric acid oligomer (FAPP) and 2000-4000 for sebacic acid oligomer (SAPP). The anhydride bonds can be detected by Fourier transform infrared spectroscopy by the characteristic double peak at 1750 cm "1 and 1820 cm "1 , with a coπesponding disappearance ofthe carboxylic acid peak normally at 1700 cm "1 . In one embodiment, the oligomers may be made from diacids described for example in U.S. Patent No. 4,757,128 to Domb et al., U.S. Patent No. 4,997,904 to Domb, and U.S. Patent No. 5,175,235 to Domb et al., the disclosures of which are incoφorated herein by reference. For example, monomers such as sebacic acid, bis(p-carboxy-phenoxy)propane, isophathalic acid, fumaric acid, maleic acid, adipic acid or dodecanedioic acid may be used. Organic dyes, because of their electronic charge and hydrophilicity/hydrophobicity, may alter the bioadhesive properties of a variety of polymers when incoφorated into the polymer matrix or bound to the surface ofthe polymer. A partial listing of dyes that affect bioadhesive properties include, but are not limited to: acid fuchsin, alcian blue, alizarin red s, auramine o, azure a and b, Bismarck brown y, brilliant cresyl blue aid, brilliant green, carmine, cibacron blue 3GA, congo red, cresyl violet acetate, crystal violet, eosin b, eosin y, erythrosin b, fast green fcf, giemsa, hematoylin, indigo carmine, Janus green b, Jenner ' s stain, malachite green oxalate, methyl blue, methylene blue, methyl green, methyl violet 2b, neutral red, Nile blue a, orange II, orange G, orcein, paraosaniline chloride, phloxine b, pyronin b and y, reactive blue 4 and 72, reactive brown 10, reactive green 5 and 19, reactive red 120, reactive yellow 2,3, 13 and 86, rose bengal, safranin o, Sudan III and IV, Sudan black B and toluidine blue. The bioadhesive properties of a polymer are enhanced by incoφorating a metal compound into the polymer to enhance the ability of the polymer to adhere to a tissue surface such as a mucosal membrane. Metal compounds which enhance the bioadhesive properties of a polymer preferably are water-insoluble metal compounds, such as water-insoluble metal oxides and hydroxides. The metal compounds can be incoφorated within a wide range of hydrophilic and hydrophobic polymers including proteins, polysaccharides and synthetic biocompatible polymers. As defined herein, a water-insoluble metal compound is defined as a metal compound with little or no solubility in water, for example, less than about 0.0-0.9 mg/ml. The water-insoluble metal compounds, such as metal oxides, can be incoφorated by one of the following mechanisms: (a) physical mixtures which result in entrapment of the metal compound; (b) ionic interaction between metal compound and polymer; (c) surface modification of the polymers which would result in exposed metal compound on the surface; and (d) coating techniques such as fluidized bead, pan coating or any similar methods known to those skilled in the art, which produce a metal compound enriched layer on the surface of the device. Preferred properties defining the metal compound include: (a) substantial insolubility in aqueous environments, such as acidic or basic aqueous environments (such as those present in the gastric lumen); and (b) ionizable surface charge at the pH of the aqueous environment. The water-insoluble metal compounds can be derived from metals including calcium, iron, copper, zinc, cadmium, zirconium and titanium. For example, a variety of water- insoluble metal oxide powders may be used to improve the bioadhesive properties of polymers such as ferric oxide, zinc oxide, titanium oxide, copper oxide, barium hydroxide, stannic oxide, aluminum oxide, nickel oxide, zirconium oxide and cadmium oxide. The incoφoration of water-insoluble metal compounds such as ferric oxide, copper oxide and zinc oxide can tremendously improve adhesion of the polymer to tissue surfaces such as mucosal membranes, for example in the gastrointestinal system. The polymers incoφorating a metal compound thus can be used to form or coat drug delivery devices to improve their bioadhesive properties. In one embodiment, the metal compound is provided as a fine particulate dispersion of a water-insoluble metal oxide which is incoφorated throughout the polymer or at least on the surface of the polymer which is to be adhered to a tissue surface. For example, in one embodiment, water-insoluble metal oxide particles are incoφorated into a polymer defining or coating a microparticle. In a preferred embodiment, the metal oxide is present as a fine particulate dispersion on the surface of the microparticle. The fme metal oxide particles can be produced for example by micronizing a metal oxide by mortar and pestle treatment to produce particles ranging in size, for example from 10.0 - 300 nm. The metal oxide particles can be incoφorated into the polymer, for example, by dissolving or dispersing the particles into a solution or dispersion of the polymer prior to microparticle formation, and then can be incoφorated into the polymer during microparticle formation using a procedure for forming microparticle such as one of those described herein. The incoφoration of metal oxide particles on the surface of the microparticle advantageously enhances the ability of the of the microsphere to bind to mucosal membranes or other tissue surfaces and improves the drug delivery properties of the microparticle. While not being limited to any theory, it is possible that the enhanced binding of the polymers incoφorating a metal compound is due to the presence of partially ionized metal compounds, such as divalent or trivalent cations, on the surface of the polymer which interact, for example, via an ionic binding attraction with negatively charged glycosubstances such as sialic acid and L-fucose groups on the mucosal membrane surface. Multivalent ions such as divalent or trivalent cations in the metal compounds generally have the strongest affinity for the negatively-charged mucin chains. As used herein, a "gene" is an isolated nucleic acid molecule of greater than thirty nucleotides, more typically one hundred nucleotides or more, in length. It generally will be under the control of an appropriate promoter, which may be inducible, repressible, or constitutive. Any genes that would be useful in replacing or supplementing a desired function, or achieving a desired effect such as the inhibition of tumor growth, could be introduced using the microparticles described herein. Promoters can be general promoters, yielding expression in a variety of mammalian cells, or cell specific, or even nuclear versus cytoplasmic specific. These are known to those skilled in the art and can be constructed using standard molecular biology protocols. A list of genes that have been approved for gene therapy by RAC between the years of 1990 and 1994 is provided in Table 2. Table 2 Human Gene Therapy Protocols Approved by RAC: 1990-1994 Severe combined Autologous lymphocytes transduced with human 7/31/90 immune deficiency ADA gene (SCID) due to adenosine deaminase (ADA) deficiency Advanced cancer Tumor-infiltrating lymphocytes transduced with tumor 7/31/90 necrosis factor gene Advanced cancer Immunization with autologous cancer cells transduced 10/07/91 with tumor necrosis factor gene Advanced cancer Immunization with autologous cancer cells transduced 10/07/91 with interleukin-2 gene Familial Ex vivo gene therapy 10/08/91 hypercholesterolemia Malignancy In vivo gene transfer into tumors 2/10/92 Cancer Gene transfer 2/10/92 Relapsed/refractory Cytokine-gene modified autologous neuroblastoma cells 6/01/92 neuroblastoma (Phase I study) Brain tumors Intratumoral transduction with thymidine kinase gene and 6/01/92 intravenous ganciclovir Metastatic melanoma Immunization with HLA-A2 matched allogeneic 6/02/92 melanoma cells that secrete interleukin-2 Advanced renal cell Immunization with interleukin-2 secreting allogeneic 6/02/92 carcinoma HLA-A2 matched renal-cell carcinoma cells Cancer Interleukin-4-gene modified antitumor vaccine 9/15/92 (pilot study) Cystic fibrosis Replication deficient recombinant adenovirus carrying 12/03/92 cDNA of normal human cystic fibrosis transmembrane conductance regulator (CFRT) gene; single administration to the lung (Phase I study) Cystic fibrosis El-deleted adenovirus vector for delivering CFTR gene 12/03/92 (Phase I study) Cystic fibrosis Adenovirus vector used for delivering CFTR gene to 12/04/92 nasal epithelium Recurrent glioblastoma In vivo tumor transduction using heφes simplex thymidine kinase 3/01/93 (brain tumor) gene/ganciclovir system Metastatic renal cell Injection of non-replicating autologous tumor cells 3/01/93 carcinoma prepared +/- granulocyte-macrophage colony stimulating factor transduction (Phase I study) Cystic fibrosis Use of replication deficient recombinant adenovirus 3/02/93 vector to deliver human CFTR cDNA to the lungs (Phase I study) Cystic fibrosis Use of El-deleted adenovirus for delivery of CFTR gene 3/02/93 to nasal cavity (Phase I study) Disseminated malignant Human gamma-interferon transduced autologous tumor 6/07/93 melanoma cells (Phase I study) Ovarian cancer Use of modified retro viruses to introduce chemotherapy 6/07/93 resistance sequences into normal hematopoietic cells for chemoprotection (pilot study) Cancer Immunotherapy by direct gene transfer into tumors 6/07/93 Gaucher's disease Ex vivo gene transfer and autologous transplantation of 6/07/93 CD34 + cells Gaucher's disease Retro viral-mediated transfer of cDN A for human 6/07/93 glucocerebrosidase into hematopoietic stem cells Asymptomatic patients Murine Retro viral vector encoding HIV-l genes 6/07/93 infected with HIV-l [HIV-IT(V)] AIDS Effects of a transdominant form of rev gene on AIDS 6/07/93 intervention Recurrent pediatric In vivo tumor transduction with heφes simplex 6/08/93 malignant astrocytomas thymidine kinase gene Advanced cancer Human multiple-drug resistance (MDR) gene transfer 6/08/93 Brain tumors Episome-based antisense cDNA transcription of 6/08/93 insulin-like growth factor I Small-cell lung cancer Cancer cells transfected with and expressing interleukin-2 9/09/93 gene (Phase I study) Breast cancer Retro viral mediated transfer ofthe human MDR gene into 9/09/93 (post-chemotherapy) hematopoietic stem cells (autologous transplantation) Recurrent pediatric Intra-tumoral transduction with thymidine kinase gene 9/09/93 brain tumors and intravenous administration of ganciclovir Malignant melanoma Immunization with interleukin-2 secreting allogeneic 9/10/93 human melanoma cells HIV infection Autologous lymphocytes transduced with catalytic 9/10/93 ribozyme that cleaves HIV- 1 RNA (Phase I study) Metastatic melanoma Genetically engineered autologous tumor vaccines 9/10/93 producing interleukin-2 Leptomeningeal Intrathecal gene therapy 12/02/93 carcinomatosis Colon carcinoma Injection with autologous irradiated tumor cells and 12/2/93 fibroblasts genetically modified to secrete interleukin-2 Gaucher's disease Retro virus-mediated transfer of cDNA for human 12/3/93 glucocerebrosidase into peripheral blood repopulating patients' cells HIV infection Murine Retro viral vector encoding HIV-IT(V) genes 12/03/93 (open label Phase I/II trial) Advanced (stage IV) Induction of cell-mediated immunity against tumor- 12/03/93 melanoma associated antigens by B7-transfected lethally irradiated allogeneic melanoma cell lines (Phase I smdy) Advanced colorectal Immunotherapy by direct gene transfer into hepatic 12/03/93 carcinoma metastases (Phase I study) Melanoma Adoptive immunotherapy with activated lymph node 12/03/93 cells primed in vivo with autologous mmor cells transduced with interleukin-4 gene Cystic fibrosis Cationic liposome-mediated transfer of CFTR gene into 12/03/93 nasal airway (Phase I study) Cystic fibrosis Adenovirus-mediated transfer of CFTR gene to the nasal 12/03/93 epithelium and maxillary sinus Pediatric neuroblastoma Immunization with gamma-interferon transduced neuro 3/03/94 blastoma cells (ex vivo) (Phase I) HIV infection Adoptive transfer of syngeneic cytotoxic T lymphocytes 3/03/94 (identical twins) (Phase I/II pilot study) Emphysema Expression of an exogenously administered human 3/03/94 alpha-I-antitrypsin gene in respiratory tract Metastatic renal cell Immunotherapy by direct gene transfer into metastatic 3/04/94 carcinoma lesions (Phase I study) Malignant melanoma Immunotherapy by direct gene transfer (Phase I study) 3/04/94 Non-small cell lung Modification of oncogene and tumor suppressor gene 3/04/94 cancer expression (first antisense therapy; original protocol (resubmitted approved by RAC 9/15/92, but then approval withdrawn protocol) 12/03/93) Metastatic colorectal Polynucleotide augmented anti-tumor immunization to 6/09/94 cancer human carcinoembryonic antigen (Phase I) Rheumatoid arthritis Transduction interleukin- 1 receptor antagonist gene 6/09/94 to human joints Breast cancer (chemo- Use of modified Retro virus to introduce chemotherapy 6/09/94 protection during resistance sequences into normal hematopoietic cells therapy) (pilot study) Fanconi's anemia Retro viral mediated gene transfer ofthe Fanconi anemia 6/09/94 complementation group C gene to hematopoietic progenitors Non-small cell lung Modification of tumor suppressor gene expression 6/10/94 cancer and induction of apoptosis with adenovirus vector expressing wild type p53 and cisplatin Glioblastoma Injection of tumor cells genetically modified to secrete 6/10/94 interleukin-2 (Phase I study) Cancer Direct injection of tumors with autologous fibroblasts 6/10/94 engineered to contain interleukin- 12 gene Metastatic prostate Autologous human granulocyte macrophage-colony ORDA/NIH carcinoma stimulating factor gene transduced prostate cancer vaccine 8/03/94* * (first protocol to be approved under the accelerated review process; ORDA=Office of Recombinate DNA Activities) Cystic fibrosis (adults Adeno-associated virus vector to deliver CFTR gene to 9/12/94 with mild disease) cells in nose and lung (Phase I study) Metastatic breast cancer ln vivo infection with breast-targeted Retro viral vector 9/12/94 expressing antisense c-fox or antisense c-myc RNA Cystic fibrosis Repeat administration of replication deficient 9/12/94 recombinant adenovirus containing normal CFTR cDNA to patient's airways Metastatic breast cancer Non-viral system (liposome-based) for delivering human 9/12/94 (refractory or recurrent) interleukin-2 gene into autologous mmor cells (pilot smdy) Mild Hunter syndrome Retro viral-mediated transfer ofthe iduronate-2-sulfatase 9/13/94 (muco-polysaccharidosis gene into lymphocytes type II) Peripheral artery disease Arterial gene transfer for therapeutic angiogenesis 9/13/94 Advanced CNS Use of recombinant adenovirus (Phase 1 study) 9/13/94 malignancy Advanced mesothelioma Use of recombinant adenovirus (Phase I smdy) 9/13/94 The foregoing represent only examples of genes that can be delivered according to the methods ofthe invention. Suitable promoters, enhancers, vectors, etc.. for such genes are published in the literature associated with the foregoing trials. In general, useful genes replace or supplement function, including genes encoding missing enzymes such as adenosine deaminase (ADA) which has been used in clinical trials to treat ADA deficiency and cofactors such as insulin and coagulation factor VIII. Genes which affect regulation can also be administered, alone or in combination with a gene supplementing or replacing a specific function. For example, a gene encoding a protein which suppresses expression of a particular protein-encoding gene can be administered by the microparticles ofthe invention. Because the mucosal epithelium is rich in immune-system cells, the invention is particularly useful in delivering genes which stimulate the immune response, including genes encoding viral antigens, tumor antigens, cytokines (e.g. tumor necrosis factor) and inducers of cytokines (e.g. endotoxin). Because the mucosal epithelium is a route to systemic circulation, the invention can be used to deliver genes encoding various pharmacological agents. These genes may transfect cells locally within the mucosal epithelium for release ofthe gene product to systemic circulation, or the genes may transfect cells remote from the mucosal epithelium, being delivered to the remote location, for example, via systemic circulation ofthe microparticles. Genes can be obtained or derived from a variety of sources, including literature references, Genbank, or commercial suppliers. They can be synthesized using solid phase synthesis if relatively small, obtained from deposited samples such as those deposited with the American Type Culture Collection, Rockville, MD or isolated de novo using published sequence information. The genes described herein are distinguished from short oligonucleotides such as antisense and ribozymes by their length and function. Unlike such short oligonucleotides, genes encode protein and therefore will typically be a minimum of greater than 100 base pairs in length, more typically in the hundreds of base pairs. It was not predictable that these long nucleic acid sequences, highly susceptible to breakage and distortion of secondary and tertiary sequence, could be incoφorated into microparticles without damage, and not predictable that the encapsulated DNA would survive the environment ofthe stomach and be delivered and released intracellularly in active form for transfection cells. As used herein, vectors are agents that transport the gene into a cell without degradation and include a promoter yielding expression ofthe gene in the cells into which it is delivered. Vectors are divided into two classes: A) Biological agents derived from viral, bacterial or other sources. B) Chemical/physical methods that increase the potential for gene uptake, directly introduce the gene into the nucleus or target the gene to a cell receptor. Biological Vectors Viral vectors have higher transaction (ability to introduce genes) abilities than do most chemical or physical methods to introduce genes into cells. Retroviral vectors are the vectors most commonly used in clinical trials, since they carry a larger genetic payload than other viral vectors. However, they are not useful in non- proliferating cells. Adenovirus vectors are relatively stable and easy to work with, have high titers, and can be delivered in aerosol formulation. However, many people may have pre-existing antibodies negating effectiveness and they are difficult to produce in quantity. Pox viral vectors are large and have several sites for inserting genes, they are thermostable and can be stored at room temperature. However, they cannot be transmitted from host to host and there are some safety issues since they can enter other cells. Plasmids are double stranded DNA which may exist in supercoiled, linear, open circular or denatured conformation. Plasmids used for gene transfer typically contain the gene of interest, a promoter/enhancer, a poly (A) termination sequence, an origin of replacation, intron and/or a reporter gene. Plasmids are not integrated into the genome and the vast majority of them are present only from a few weeks to several months, so they are typically very safe. However, they have lower expression levels than retroviruses and since cells have the ability to identify and eventually shut down foreign gene expression, the continuous release of DNA from the polymer to the target cells may substantially increase the duration of functional expression while maintaining the benefit ofthe safety associated with non-viral transfections. Chemical/Phvsical Vectors Other methods to directly introduce genes into cells or exploit receptors on the surface of cells include the use of liposomes and lipids, ligands for specific cell surface receptors, cell receptors, and calcium phosphate and other chemical mediators, microinjections directly to single cells, electroporation and homologous recombination. The chemical/physical methods have a number of problems, however, and will typically not be used with the microparticles described herein. For example, chemicals mediators are impractical for in vivo use: when calcium phosphate is used there appears to be very low transduction rate, when sodium butyrate is used the inserted gene is highly unstable and when glycerol is used inserted gene is rapidly lost. It is possible to incoφorate nucleic acid molecules into liposomes or complexed to liposomes which are then incoφorated into the microparticles for delivery to cells. The ratio of liposome to polymer solution is important in determining whether the liposomes will remain as separate entities during the process for incoφoration into the microparticles. If the ratio of solvent is too high, the phospholipid will dissolve into the polymer solvent, rather than remaining as part ofthe liposome bilayer. This is a function ofthe liposome composition, polymer concentration, and solvent composition. The liposomes can increase the efficiency of the transfer ofthe DNA into the cells when the liposomes are released from the microparticles. Liposomes are commercially available from Gibco BRL, for example, as LIPOFECTIN® and LIPOFECTACE®, which are formed of cationic lipids such as N-[l-(2,3 dioleyloxy)-propyl]- n,n,n-trimethylammonium chloride (DOTMA) and dimethyl dioctadecylammonium bromide (DDAB). Numerous methods are also published for making liposomes, known to those skilled in the art. Table 2 provides a summary ofthe functions of some vectors cunently used in gene therapy. Table 2 Summary of various the Vectors Cunently Used in Gene Therapy Size Specificity Immunogenicity/ Sustained/High/Low/ Constraints of Targeting Toxicity Controlled Expression Retrovirus 7Kb none none low, uncontrolled transient transfection Adenovirus 7Kb none high low, uncontrolled immunogenicity transient transfection Liposome none none toxic at high doses low, uncontrolled transient transfection The methods ofthe invention are applied to subjects. As used herein, subjects means humans, nonhuman primates, horses, goats, cows, sheep, pigs, dogs, cats and rodents. When used therapeutically, the compounds ofthe invention are administered in therapeutically effective amounts. In general, a therapeutically effective amount means that amount necessary to delay the onset of, inhibit the progression of, ameliorate the symptoms of or halt altogether the particular condition being treated. It is less than that amount that produces medically unacceptable side-effects. Generally, a therapeutically effective amount will vary with the subject's age, condition, and sex, as well as the nature and extent ofthe disease in the subject, all of which can be determined by one of ordinary skill in the art. The dosage may be adjusted by the individual physician or veterinarian, particularly in the event of any complication. A therapeutically effective amount typically varies from 0.0001 mg/kg (active agent/body weight) to about 1000 mg/kg, preferably from about 0.1 mg/kg to about 20 mg/kg in one or more dose administrations daily, for one or more days. The therapeutics ofthe invention can be administered by any conventional route. The prefeπed route is to the mucosal epithelium, such as with an oral formulation, aerosol for respiratory tract delivery, vaginal formulation, rectal formulation, nasal formulation, buccal formulation or occular formulation. The administration can, however, be, via any conventional route, including intramuscular, intracavity, subcutaneous, or transdermal administration. Techniques for preparing aerosol delivery systems are well known to those of skill in the art. Generally, such systems should utilize components which will not significantly impair the biological properties ofthe therapeutic (see, for example, Sciarra and Cutie, "Aerosols," in Remington's Pharmaceutical Sciences. 18th edition, 1990, pp 1694-1712; incoφorated by reference). The PIN process for making the microparticles ofthe invention is particularly suited to making aerosols. Those of skill in the art can readily determine the various parameters and conditions for producing aerosols or other formulations without resort to undue experimentation. Oral formulations are well known to those skilled in the art, and include tablets, capsules, or liquids with flavorants, stabilizers and the like. Preparations for parenteral administration include sterile aqueous or non-aqueous solutions, suspensions, and emulsions. Examples of non¬ aqueous solvents are propylene glycol, polyethylene glycol, vegetable oils such as olive oil, and injectable organic esters such as ethyl oleate. Aqueous carriers include water, alcoholic/aqueous solutions, emulsions or suspensions, including saline and buffered media. Parenteral vehicles include sodium chloride solution, Ringer's dextrose, dextrose and sodium chloride, lactated Ringer's or fixed oils. Intravenous vehicles include fluid and nutrient replenishers, electrolyte replenishers (such as those based on Ringer's dextrose), and the like. Preservatives and other additives may also be present such as, for example, antimicrobials, anti-oxidants, chelating agents, and inert gases and the like. The pharmaceutical preparation of microparticles may be used alone or in combination with a therapeutic agent for treating the disease or condition for which the microparticles are being administered. Known therapeutics are described in medical textbooks such as Haπisons, Principles of Internal Medicine (McGraw Hill, Inc., New York). The particular therapeutic used depends on the nature ofthe disease or condition being treated. In some embodiments, a common administration vehicle (e.g., pill, tablet, implant, injectable solution, etc.) would contain both the microparticles useful in this invention and the therapeutic agent for treating the disease or condition. Thus, the present invention also provides pharmaceutical compositions, for medical use, which comprise the microparticles ofthe invention together with one or more pharmaceutically acceptable carriers thereof and optionally other therapeutic ingredients. The pharmaceutical compositions should contain a therapeutically effective amount ofthe microparticles in a unit of weight or volume suitable for administration to a patient. The term "pharmaceutically acceptable" means a non-toxic material that does not interfere with the effectiveness ofthe biological activity ofthe active ingredients. The characteristics ofthe carrier will depend on the route of administration. Pharmaceutically acceptable carriers include diluents, fillers, salts, buffers, stabilizers, solubilizers, and other materials which are well known in the art. The methods and products ofthe invention permit the noninvasive delivery of genes under the control of promoters for transfection of cells in vivo. The materials ofthe invention can be applied to epithelial surfaces, including mucosal epithelium. As will be seen from the examples below, both epithelial and nonepithelial cells can be transformed. In the oral delivery methods ofthe invention, for example, adsoφtive and nonadsoφtive intestinal epithelial cells can be transfected, as well as gut associated lymphoid tissue and liver cells. EXAMPLES Example 1: Microspheres Produced by Phase Inversion Encapsulation Exhibit Enhanced Bioavailability of Encapsulated Drugs In Vivo: 1. Oral Delivery of Microparticles: Studies were conducted to deteπnine the fate of orally administered P(FA:SA)20:80 microparticles. The microparticles contained rhodamine and had a particle size range of between 0.1 and 1.0 micrometers. Rats were fed a single dose of 3 mg of such microparticles. As early as one hour posted-feeding of a single dose, microparticles were observed to traverse the mucosal epithelium by passing between absoφtive cells (paracellular route). In addition, microparticles were seen crossing through follicle associated epithelium (FAE) and into the Peyer's patches. After three and six hours, an even greater number of microparticles were seen between epithelial cells and in the Peyer's patches. Focal areas demonstrated massive amounts of nonselective uptake, by both absoφtive cells and Peyer's patches. Liver samples showed large numbers of nanospheres with apparently normal looking hepatocytes. Spleen sections also showed nanospheres, but fewer than in the liver. At twelve hours, large numbers spheres were still observed in between villous epithelial cells and in the Peyer's patches. Similar sections were observed even at twenty-four hours post-feeding. This experiment showed extensive uptake of microparticles extending over at least twenty-four hours, following a single oral dose. Microparticles apparently crossed the epithelial boundary by passing in between cells. The observed uptake did not seem to be limited to the FAE overlying the Peyer's patches; uptake occuπed diffusely by absoφtive epithelium as well as FAE. Transmission electron microscopy experiments using electron-opaque tracers such as micronized feπic oxide or 5nm colloidal gold that had been microencapsulated with bioadhesive P(FASA) 20:80 were also conducted. The findings demonstrated that nanospheres in great number were indeed being taken up by absoφtive epithelial cells lining the small intestine. In a typical thin section of an absoφtive cell, up to one hundred nanospheres could be counted. While the results of light microscopy indicated a paracellular means of entry, these electron micrographs showed many microparticles within cells. The mechanism of entry is not known although several particles were occasionally observed in clear "endocytotic" vesicles located directly beneath the terminal web region in proximity to the apical microvillous border. The range of particle sizes observed in the cytoplasm of cells was 40-120nm, well below the resolution of normal light optics and therefore undetectable by light microscopy. Nanoparticles were visualized in the cytoplasm, inside membranous profiles ofthe endoplasmic reticulum and Golgi apparatus and generally in the supranuclear (apical) portion ofthe absoφtive cell. Occasionally, nanoparticles were seen near the basal aspects ofthe cell. Spheres were often found near the lateral borders ofthe cell, in the intracellular spaces and in close apposition to the tight junctions. These findings suggest that translocation of nanospheres via the transcellular route occuπed in addition to paracellular movement. 2. Oral delivery of insulin: Insulin was encapsulated in P(FA)-PLGA(50:50) polymer blends using the phase inversion nanoencapsulation methods. After measuring fasting blood glucose levels, fasted rats were injected subcutaneously with an initial glucose load and then fed either a suspension of nanospheres containing 20 IU zinc-insulin (micronized FeO was included an electron dense tracer) in saline or else sham fed saline only. Blood glucose levels (BGL) were assayed at intervals after feeding. The controls showed the expected response to the glucose load. BGL rose by 40 mg/dL after three hours and then slowly started to retum towards baseline. In contrast, animals fed the encapsulated insulin formulation had consistently lower blood glucose levels than the control animals at three ofthe four time points that were sampled. After 1.5 hours, the BGL was 20 mg/dL below baseline compared to 30 mg/dL above baseline for control animals. At three hours the BGL ofthe nanoparticle treated animals rose to 20mg/dL above baseline compared to a 40mg/dL rise for the control animals (not statically different). At four hours, the BGL ofthe nanoparticle-fed animals was nearly 30 mg/dL below baseline, compared to a BGL of 20mg/dL above base line for the control animals. After five hours, the glucose levels ofthe test group were lower than at four hours, while the levels ofthe control animals were still 35mg/dL above baseline. Because the animals fed the encapsulated insulin preparation were better able to regulate the glucose load, it is clear that the insulin was not harmed by the encapsulation method, that the insulin survived the environment ofthe stomach, the insulin crossed the intestinal barrier and the insulin was released from the nanoparticles in a bioactive form. A widespread distribution of insulin-loaded nanospheres also was observed. The spheres were observed in great numbers, traversing the mucosal epithelium in the small intestine, in the Peyer's patches, in the lamina propria, in the lacteals and in the blood vessels ofthe gut wall. Nanoparticles also were observed in spleen and other tissue samples. Thus, systemic delivery of both insulin and nanoparticles was demonstrated. 3. Encapsulation and oral delivery of icumarol: Dicumarol containing microspheres were produced as described above in Example 2, subsection 1. Equal doses of dicumarol, spray dried dicumarol and polyanhydride (FA:SA) 20:80 encapsulated dicumarol (25 mg drug/kg body weight) suspended in 1.5 ml maple syrup were fed to catheterized rats (250-350 g). Blood samples were taken at regular intervals and serum was assayed for dicumarol concentrations using a UV spectrophotometric method. The results ofthe in vivo studies indicate that the polyanhydride (FA:SA) microcapsule formulation had significantly increased bioavailability compared to the unencapsulated formulations, including the micronized drug. At 12 hours post-feeding, the serum concentrations for the polyanhydride (FA:SA) formulations were significantly higher than for the controls. At 48 hours post-feeding, the serum levels ofdicumarol in the controls had returned to baseline, while those animals fed the bioadhesive polyanhydride formulation had detectable drug concentrations for at least 72 hours. ORAL BIOAVAILABILITY OF DICUMAROL Table 1 STOCK SPRAY P(FA:SA) 20:80 DICUMAROL DICUMAROL "PIN'ΕNCAPSULATED CONTROL CONTROL DICUMAROL C MAX (ug/ml 11.53 ± 1.10 * 17.94 ± 1.22 18.63 ± 1.76* T MAX (hrs) 9.87 ± 1.76 9.42 ± 1.36 10.61 ± 0.02 t ' (half life) (hrs) 18.25 ± 3.30 16.21 ± 0.87 17.92 ± 0.41 AUC (area under curve) 171.48 ± 33.16 232.10 ± 19.20≠ 363.59 ± 70.95* (ug/ml - hrs) * = Significantly different at p < .03 ≠ = Significantly different at p < .005 (means ± std error) These results indicate that phase inversion encapsulation of drugs in bioadhesive formulations, such as the polyanhydride (FA:SA) can increase bioavailability. Example 2: Incorporation of DNA into polymeric nanospheres by phase inversion This example provides a description ofthe incoφoration of plasmid DNA into poly(fumaric acid:sebacic acid) 20:80 (P(FA:SA)) using a phase inversion technique. Materials. P(FA:SA) 20:80 (synthesized by a method of A. Domb & R. Langer, Journal of Polymer Science, 1987, v. 25, p. 3373-3386), a reporter plasmid pCMV/βgal (Clonetech), methylene chloride (Fisher) and petroleum ether (Fisher) were used to construct the nanospheres. Methods. 200 mg of P(FA:SA) in methylene chloride (1% wt vol) is vortexed (30 sec) with 2 mg of pCMV/βgal in distilled water (1 mg/ml), frozen in liquid nitrogen and lyophilized overnight to disperse the DNA in the polymer. The puφose of this step was to reduce the particulate size and prevent aggregation ofthe DNA. DNA present in the disperse phase ofthe emulsion would not be able to aggregate due to the physical separation induced by the continuous polymer phase. The resulting mixture was redissolved in 2 ml of methylene chloride, poured into 200 ml of petroleum ether and filtered to recover microspheres encapsulating the DNA. Results. Polymer nanoparticles produced using this technique were analyzed to determine whether DNA was encapsulated within the nanoparticles. Plasmid DNA was extracted from the nanoparticles and subjected to agarose gel electrophoresis. The results indicate that DNA was encapsulated without degradation. Thus, the phase inversion technique can be used to incoφorate very large intact molecular weight plasmid DNA (7.2 x IO 6 Daltons) in biodegradable nanoparticles. Example 3: Release of pCMV/βgal from P(FA:SA) nanoparticles This in vitro example demonstrates that plasmid DNA can be released from P(FA:SA) nanoparticles. Materials. P(FA:SA)-pCMV/βgal nanoparticles were fabricated as indicated in Example 1 and the release buffer was Tris-EDTA 10 mM, pH 7.4, 0.02% sodium azide. Methods. Release of plasmid DNA from these nanoparticles was determined using a standard drug release assay. Briefly, 10 mg ofthe P(FA:SA)-pCMV/βgal nanoparticles were incubated in 0.5 ml ofthe release buffer at room temperature. The 0.25 ml ofthe supernatant was collected and replaced with fresh release buffer periodically and analyzed for the presence of plasmid DNA. The collected supernatant was analyzed at 24 hrs, 72 hrs, 1 week and 2 weeks using agarose gel electrophoresis. Results. The following samples were analyzed by Agarose gel electrophoresis 1) λ Hind III ladder; 2) stock unencapsulated pCMV/βgal; 3) 24 hours; 4) 72 hours; 5) 1 week; 6) 2 weeks. The banding pattern of released plasmid DNA indicated that the plasmids were structurally intact and not degraded. It was observed that the encapsulated pCMV/βgal was released without degradation and was present in the release buffer in open circular and supercoiled conformation. These results indicate that plasmid DNA can be released from the degradable P(FA:SA) nanoparticle formulations. Example 4: Efficacy of orally administered P(FA:SA) - pCMV/βgal nanoparticles for in vivo gene transfer This study was conducted to demonstrate the feasibility of in vivo gene transfer through oral administration of genes incoφorated into polymer nanoparticle formulations. Materials. P(FA:SA)-pCMV/βgal nanoparticles were fabricated as indicated in Example 1 and male Sprague-Dawley rats - 400 grams were used for the in vivo evaluation. Methods. 500 μg of unencapsulated pCMV/βgal encapsulated in P(FA:SA) nanoparticles were administered by stomach tube as a single dose to fasted rats. The encapsulated plasmid dosing was given at one-tenth ofthe control plasmid dose to test the efficacy ofthe bioadhesive delivery system and demonstrate the protective benefits of encapsulation. The animals were sacrificed after 5 days and the stomach, small intestine and liver were excised and tested for β- galactosidase expression. The small intestine and stomach were carefully rinsed with physiological saline to remove residual food contents and adherent mucus that might falsely elevate background enzyme levels. An additional sample of untreated animals were included as a control to estimate background galactosidase activity. The minimum sample size was 3 animals. Expression ofthe reporter gene product was assayed by: 1) quantification of β- galactosidase activity and 2) histological identification of transfected cell types using a standard histochemical substrate (X-gal) for β-galactosidase. Results. A Luminomentry assay of bacterial β-galactosidase activity in tissue homogenates was performed to determine the amount of reporter gene activity detected in the various tissue types following administration of unencapsulated and P(FA:SA) encapsulated pCMV/βgal. Stomach, small intestine and liver were excised from animals fed either pCMV/βgal encapsulated in P(FA:SA) 20:80 "PIN" nanospheres or else the unencapsulated plasmid (control). The tissues were homogenized in lysis buffer containing 0.1 % Triton (w/v), PMSF and leupeptin to inhibit proteolysis and incubated at 48 °C for 1 hr to deactivate endogenous β-galactosidase activity. Tissue homogenates were incubated in Galacto-Light substrate and luminescence was measured using a Berthold luminometer. Five days following a single oral dose of plasmid-loaded PIN nanospheres and unencapsulated pCMV/β-gal, β-galactosidase activity was quantified in the stomach, small intestine and the liver. (Fig.l) Animals which were fed encapuslated pCMV/β-gal showed significant levels of β-galactosidase activity in both the small intestine and the liver compared to unencapsulated pCMV/β-gal as well as unfed animals. The reporter gene activity measured in animals which received the encapsulated pCMV/β-gal was highest in intestinal tissue (greater than 54 mU compared to 24 mU for the unencapsulated plasmid and 18 mU for the background levels of activity found in untreated control animals). These same animals averaged 11 mU of activity in the liver compared to less than 1 mU for plain CMV-fed or untreated control animals. Reporter gene expression in stomach homogenates was not different and generally low in all groups. The levels in encapsulated and naked plasmid-fed groups were identical at lmU and actually lower than the untreated control levels of 11 mU. The reporter gene expression detected in animals following oral administration of encapsulated pCMV/βgal indicate that the "PIN" system can be utilized to deliver plasmid DNA into intestinal and liver tissues. Visual localization of transfected cells following oral administration was performed using X-gal histochemical techniques on both whole tissue or frozen sections. Whole tissue staining of intestinal segments from animals receiving encapsulated pCMV/β-gal showed occasional β-galactosidase positive staining of intestinal villous epithelium as well as the outer serosal surface of Peyer's patches. However, it has been shown that some populations of rat intestinal tissue, primarily the epithelial cells on the villous apical tip, contain endogenous lactose which makes differentiation between transfected bacterial β-galactosidase and background activity difficult. Because ofthe difficulties associated with conclusive identification of transfected cells within intestinal villi, we focused on other cell populations which do not contain background activities, the Peyer's patch. Whole tissue X-gal staining showed that the serosal surface of small intestine from encapsulated β-galactosidase fed rats stained intensely in localized areas coπesponding to areas containing Peyer's patches. Similar histochemical X-gal staining of frozen sections coπesponding to the Peyer's patch area revealed that although there were a few β-galactosidase positive cells within the central lymphoid tissue mass, the majority of transfected cells were located in the muscularis mucosae and advertitia below the Peyer's patch. This distribution of staining was consistent with previous studies which showed retention of nanospheres in the Peyer's patch. Neither groups of control animals (unencapsulated pCMV/β-gal or unfed normal rats) showed any false-positive β-galactosidase staining in the Peyer's patches region. Histological examination of the tissue revealed near normal histology in all experimental groups with no evidence of mucosal damage or inflammation. CONCLUSION: Encapsulation of plasmid DNA in the "PIN" system offers two primary benefits: 1) protection from rapid degradation when administered orally and 2) targeting of transfection to certain cell types. The results ofthe in vivo study confirmed that plasmid DNA can be delivered by the oral route using the bioadhesive "PIN" nanoparticle formulations. The encapsulated DNA is incoφorated into cells in the small intestine and hepatocytes and can express functional gene products at levels that are easily detectable using common histological and luminometric techniques. Certain ofthe various objects and advantages ofthe invention are illustrated in the following examples. Numerous equivalents and embodiments will be apparent to those of ordinary skill in the art and are intended to be embraced by the appended claims. What we claim is:

Claims: CLAIMS 1. A method for delivery of a gene to a cell of a subject for gene therapy gene therapy comprising; administering to a mucosal epithelial surface of a subject in need of such treatment an effective amount of bioadhesive microparticles containing an isolated gene under the control of a promoter. 2. The method of Claim 1 wherein the bioadhesive microparticles consist of microparticles having an average particle size of between ten nanometers and five microns. 3. The method of Claim 1 wherein the bioadheisve microparticles consist of microparticles having an average particle size of between one hundred nanometers and three microns 4. The method of Claim 1 wherein the bioadhesive microparticles comprise a polyanhydride. 5. The method of Claim 1 wherein the bioadhesive microparticles comprise poly(fumaric-co- sebacic)anhydride. 6. The method of Claim 1 wherein the bioadhesive microparticles are prepared by phase inversion nanoencapsulation. 7. The method of Claim 1 wherein the cell is an epithelial cell. 8. The method of Claim 1 wherein the cell is a non-epithelial cell. 9. The methods of Claims 1-8 wherein the bioadhesive microparticles are administered orally to the subject. 10. A method for delivery of a gene to a cell of a subject for gene therapy comprising: administering orally to a subject in need of such treatment an effective amount of microparticles containing an isolated gene under the control of a promoter, wherein the microparticles consist of microparticles having an average particle size of between ten nanometers and five microns. 11. The method of Claim 10 wherein the microparticles consist of microparticles having an average particle size of between one hundred nanometers and three microns. 12. The method of Claim 10 wherein the microparticles are prepared by phase inversion nanoencapsulation. 13. The method of Claim 10 wherein the cell is an intestinal epithelial cell. 14. The method of Claim 10 wherein the cell is an intestinal non-epithelial cell. 15. The method of Claim 10 wherein the cell is a gut associated lymphatic tissue cell. 16. The method of Claim 10 wherein the cell is a liver cell. 17. The method of Claims 13-16 wherein the microparticles comprise bioadhesive microparticles. 18. The method of Claim 17 wherein the microparticles comprise a polyanhydride. 19. The method of Claim 18 wherein the microparticles comprise a poly)fumaric-co- sebacic)anhydride. 5 20. A method of noninvasive delivery of a gene into systemic circulation of a subject for gene therapy comprising: administering noninvasively to a mucosal epithelial surface of a subject in need of such treatment an effective amount of bioadhesive microparticles containing the gene l o under the control of a promoter, wherein the microparticles consist of microparticles having an average particle size of between ten nanometers and five microns. 21. The method of Claim 20 wherein the bioadhesive microparticles are administered orally to the subject. 15 22. The method of Claim 20 wherein the bioadhesive microparticles are administered in an aerosol to the respiratory epithelium ofthe subject. 23. The method of Claim 20-22 wherein the bioadhesive microparticles comprise a 20 polyanhydride. 24. The method of Claim 23 wherein the polyanhydride is poly(fumaric-co-sabacic)anhydride. 25. A pharmaceutical preparation for gene therapy comprising: 25 an effective amount of microparticles containing a gene under the control of a promoter, wherein the microparticles consist of microparticles having an average particle size of between ten nanometers and five microns; and a pharmaceutically acceptable carrier sutiable for oral administration to a subject, wherein the pharmaceutical prepartion is formulated as an oral dosage. 26. The pharmaceutical preparation of Claim 25 wherein the microparticles comprise bioadhesive microparticles. 27. An article of manufacture comprising : a preparation consisting essentially of bioadhesive microparticles containing an isolated gene under the control of a promoter. 28. The article of manufacture of Claim 27 wherein the bioadhesive microparticles consist of microparticles having an average particle size of between ten nanometers and five microns. 29. The bioadhesive article of manufacture of Claim 27-29 wherein the microparticles consist of microparticles having an average particle size of between ten nanometers and three microns. 30. The article of manufacture of Claims 27-29 wherein the bioadhesive microparticles comprise a polyanhydride. 31. The article of manufacture of Claims 27-29 wherein the bioadhesive microparticles comprise poly(fumaric-co-sebacic)anhydride.

Inventors: CARINO GERARDO, JACOB JULES S, JONG YONG, MATHIOWITZ EDITH, CARINO, GERARDO, JACOB, JULES, S., JONG, YONG, MATHIOWITZ, EDITH
Applicants: UNIV BROWN RES FOUND, BROWN UNIVERSITY RESEARCH FOUNDATION
Application year: 1996
Main classification: A61K48
IPC codes: A61K9, A61K47, A61K48, B01J13