EXTERNALLY TRIGGERED MICROCAPSULES

Abstract: Disclosed are microcapsules comprising a polymer shell enclosing one or more immiscible liquid phases in which a drug or drug precursor are contained in a liquid phase. The microparticles also contain magnetic particles that can be heated by application of an external magnetic field and thus heated to a predetermined Curie temperature. Heating of the particles melts the polymer shell and releases the drug without causing heating of surrounding tissues.

Description: EXTERNALLY TRIGGERED MICROCAPSULES CROSS-REFERENCE TO RELATED APPLICATIONS This application is a continuation-m-part of U.S. Patent Application No. 08/349,169 filed December 2, 1994 (now U.S. Pat. No. 5,827,531), which is hereby incorporated by reference as though completely set forth herein. This application is further related to the following U.S. Patent Applications which are filed contemporaneously herewith: (1) Application No. 09/079,741 filed May 15, 1998 entitled "In Situ Activation of Microcapsules" invented by Dennis R. Mornson and Benjamin Mosier, NASA Case No. MSC-22866-1 (Attorney Docket No. 1306-01500); (2) Application No. 09/079,833 filed May 15, 1998 entitled "Microencapsulation and Electrostatic Processing Device" invented by Dennis R. Mornson, Benjamin Mosier, and John M. Cassanto, NASA Case No. MSC-22937-1-SB (Attorney Docket No. 1306-01600); (3) Application No. 09/079,758 filed May 15. 1998 entitled "Externally Triggered Microcapsules" invented by Dennis R. Mornson and Benjamin Mosier, NASA Case No. MSC-22939-1- SB (Attorney Docket No. 1306-01700); (4) Application No. 09/079,770 filed May 15, 1998 entitled "Low Shear Microencapsulation and Electrostatic Coating Process" invented by Dennis R. Mornson and Benjamin Mosier, NASA Case No. MSC22938- 1 -SB (Attorney Docket No. 1306-01800); (5) Application No. 09/079,766 filed May 15, 1998 entitled "Microencapsulated Bioactive Agents and Method of Making" invented by Dennis R. Momson and Benjamin Mosier, NASA Case No. MSC-22936-1-SB (Attorney Docket No. 1306-01900). These applications are also hereby incorporated by reference as though completely set forth herein. STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT The invention described herein was made in the performance of work under a NASA contract and is subject to the provisions of Section 305 of the National Aeronautics and Space Act of 1958, Public Law 85-568 (72 Stat. 435; 42 U.S.C.2457). BACKGROUND OF THE INVENTION Field of the Invention The invention relates to microcapsules, methods for making microcapsules, encapsulating pharmaceutical compounds m microcapsules, microcapsule encapsulated pharmaceutical compositions and products, and methods of using these compositions. The invention also relates to controlled delivery of a substance contained in a microcapsule through the use of magnetic particles that are heated upon exposure to an electromagnetic field. Description of the Related Art Although encapsulation of a drug m a microcapsule or other earner addresses several problems of drug delivery, an area of interest m the art of drug delivery is still the specific, controlled release of the drug from the microcapsule when it reaches the target site. Several approaches have been descnbed to solve this problem, including heating liposomes to the melting temperature of the phosphohpid bilayer by inducing local hyperthermia or by heating magnetic powders incorporated into the membranes, and also including physically shaking microcapsules by ultrasound or by oscillating magnetic fields. However, the inventors are aware of no previous method m which a permanent hole is melted in a microcapsule compnsmg a polymer outer shell, so that the contents are released through the pore. In a controlled delivery system descnbed by Supersaxo et al. in U.S Patent No. 5,470582, microparticles are made from polymers such as polyesters, polyamides, polyanhydndes and polyacrylates with pre-formed pores and an active agent is allowed to migrate into the microparticles through the pores. After administration, the active agent is released through the pores by diffusion. A burst of release may be caused by application of ultrasonic radiation Another system, descnbed by Mathiowitz et al. in U.S. Patent No 4,898,734, is also based on passive or facilitated diffusion of an active agent from pore-containing polymer microspheres. Methods of facilitating diffusion include exposure to high temperature, light, or ultrasound. This patent also descπbes degradable microspheres and microspheres immobilized rn a polymer matnx. A controlled release delivery system descnbed by Modi in U.S. Patent No. 5,417,982 is biodegradable copolymer based microspheres in which delayed release of an active agent is controlled by the time required for enzymatic digestion of the polymer matnx. Wheatley et al, in U.S. Patent No. 4,933,185, descnbe microcapsules having an inner core and an outer, ionic skin. An active agent and an enzyme are encapsulated in the inner core, such that the enzyme degrades the inner core and releases the active agent Controlled release of drugs from liposomes has been achieved by usmg temperature sensitive polymers in the formation of the liposomes (Magm et al. 1986). Once the liposomes are localized in the target tissue (or tumor) the drug can be rapidly released if the local tissue temperature can be raised above the transition temperature of the hposome membrane. This requires some method of controlled tissue heating which is difficult to achieve without complicated surgical procedures, implanted interstitial antennas or ultrasonics to produce effective local hyperthermia (Hand, 1991). Thermosensitive liposomes have been prepared from a vanety of natural and synthetic lipids such as dipalmitoyl phosphatidylcholine, distearoyl phosphatidylchohne, and cholesterol to have transition temperatures of 41-43 °C so that the outer phosphohpid membrane melts and releases contained drugs m response to local hyperthermia. Attempts have been made to use these liposomes and local tissue hyperthermia for achieving drug targeting to tumors. Chelvi and Rathan (1995) prepared temperature-sensitive liposomes from natural lipids, egg phosphatidylcholinexholesterol (PC:Ch) in a 7:1 molar ratio and ethanol, 6 % (v/v) having a transition temperature of 43 °C. Fluorescence labeled calcein was encapsulated in the liposomes and administered to mice, a group of whose tumor-beanng legs were immersed in a water bath to achieve a tumor temperature of 43 °C and held there for one hour. Fluorescence microscopy demonstrated the release of calcein from the temperature sensitive liposomes. The in vivo efficacy of temperature-sensitive unilamellar vesicles containing dacarbazine in combination with hyperthermia was detected in murme fibrosarcomas. Kakinuma et al. (1995) also used thermosensitive liposomes containing cis- diammedichloroplatm (CDDP) to deliver cytotoxic doses to bram tumors by dissolving the liposomes with localized bram heating. The investigators studied the anti-tumor effect on rat malignant ghoma. Ten days after tumor inoculation, the rats were assigned to one of six treatment groups: control, free CDDP, hyperthermia, free CDDP + hyperthermia, liposomes containing CDDP (CDDP-hposomes), and CDDP-hposomes + hyperthermia. Liposomes containing CDDP or free CDDP were injected via the tail vem. Bram tumor heating was administered by means of a radiofrequency antenna designed for rat bram. The rats treated with CDDP-hposome + hyperthermia had the longest survival time and the tumor CDDP level of this group was the highest when compared to the other groups. Histophathological examination showed that tumor cells were necrotized but surrounding normal brain tissue remained undamaged. The greater anti-tumor effects suggested that the combination of thermosensitive hposome and localized hyperthermia better focused anti-tumor drugs to the tumor. Thermosensitive liposomes designed for drug release by hyperthermia have been tested at different local tissue temperatures (Kakinuma et al., 1996). Four groups were studied: the first received free Cisplatin (cis-diaminedichloroplatin, CDDP); the second received free CDDP and above 41°C local bram heating for 30 minutes; the third group received liposomes containing CDDP (CDDP-hposomes); and the fourth group received CDDP-hposome and above 41°C local bram heating for 30 minutes. Bram CDDP levels were significantly higher in group 4, while those m the other groups were undetectable. The present inventors have also studied the distnbution of Evans blue dye (Eb) in the artificially heated region of dogs' bram. One group received free Eb and the other group received liposomes containing Eb (Eb-liposome). While the extravasation of free Eb was localized in regions heated to greater than 44°C, that of Eb-hposome was extended up to the regions heated at 41°C. It appears that the use of thermosensitive liposomes and hyperthermia not only contnbutes to the bram tumor killing as direct thermal killing does, but also helps to increase the concentration of chemotherapeutic drugs mto the tumor invaded zones with mild local hyperthermia of only 41°C. A method of localizing a drug earner that has been descnbed is the inclusion of magnetic particles m the earner. The encapsulation of oil-suspended magnetic particles mto microcapsules with hydrophilic, organic colloidal membranes is descnbed m U.S Patent 2,971,916. The magnetic particles were used to direct the microcapsules to a magnetized location on a paper medium, where the capsules were crushed to deliver an ink or stain to the paper. Microspheres for lntravascular administration compnsrng magnetic particles m a biodegradable earner are descnbed in U.S. Patents 4,247,406 and 4,345,588. The microcapsules descnbed in these patents compπse magnetic particles embedded in a polyamino acid matnx, such as albumin, which also acts as a earner for a therapeutic drug. The microcapsules are infused into an artery that feeds a particular capillary bed and are then immobilized by the application of a magnetic field across the capillary bed. The microcapsules are held m the bed by the magnetic field until the polymer matrix is dissolved by proteolytic enzymes, or they may be drawn into the surrounding tissues by application of a stronger field. As descnbed m these patents, when these earners are drawn into tissue in order to directly deliver the drugs, they become immobilized m the tissue where they remain after the field is terminated. Liposomes encapsulating magnetic particles are descnbed by Chang m U.S. Patent 4,652,257. These liposomes are also used to localize a chemotherapeutic drug in a capillary bed by application of a magnetic field After the liposomes are immobilized at the target site, the magnetic particles are vibrated by application of an oscillating magnetic field. The particles are vibrated m order to destabilize, or to rupture the lipid membrane, thus releasing the drug. The liposomes descnbed by Chang are small (on the order of 1-2 micrometers with ferromagnetic particles of about 100 to 1000 angstroms), and are further limited that only hydrophilic drugs can be delivered from the liposomes. The small size of these liposomes limits their utility because the size and shape is a factor m the distribution and drug delivery of the liposomes in the tissues Additionally, m the liposomes descnbed by Chang, it is the mechanical force of the vibrating ferromagnetic particles that destabilizes or ruptures the membrane, rather than any local heating effect It is evident, therefore, that improvements are still needed to address certain drawbacks of conventional hposome or microcapsule delivery systems. Delivery of a vaπety of active drugs to a specific site m the body with a hposome formulation still presents difficulties, for example. There is a need for a system that would address certain disadvantages of thermosensitive liposomes for drug delivery. These delivery systems are pπmanly useful for drugs that diffuse out of the earner across the outer phosphohpid bi-layer membrane, or in liposomes that are phagocytized by a particular cell type. Thermosensitive liposomes may be melted by local hyperthermia, but unfortunately, methods for creating hyperthermia in local tissues are not precise and are largely dependent on the local tissue composition. Heating may also be counteracted by blood flow cooling. Thermosensitive liposomes (or microcapsules) are limited to those having outer membranes that can be melted at temperatures below those that cause permanent damage to healthy tissues, usually a maximum of 41-44°C. In those methods in which heating or mechanical forces are used to disrupt or melt the hposome membrane, or even melt a hole m the membrane, the phosphohpid bilayer will rapidly extend to close off the hole and thereby re-form the lipid bilayer. There is a need, therefore for a method of controlled delivery of a drug at the tumor site without depending on passive diffusion, local hyperthermia of tissues, or temporary phase changes in the outer membrane. BRIEF SUMMARY OF THE INVENTION The present invention addresses these and other drawbacks in the pnor art by providing compositions and methods compnsmg multi-layered liquid microcapsules that are composed of a polymenc outer skin or membrane surrounding immiscible fluid compartments containing drugs m either solid, crystalline or dissolved states. The microcapsules may also contain metal particles such as ferromagnetic particles or other magnetic particles that become heated by induction to a controllable temperature when exposed to an external electromagnetic field or other forms of activating energy. The microcapsules are designed so that the magnetic particles may be heated to their charactenstic Cune temperature (Cune point) by exposure to an electromagnetic field, and will melt holes in the outer skin of the microparticles, designed to have a melting temperature that is less than the Cune temperature, thus releasmg the contents (drugs) without causing widespread damage to the surrounding tissues. These magnetic particles typically have a size range of 0.01 to 50 microns, and preferably not more than 1/10 of the diameter of the microcapsule containing the magnetic particle. The magnetic particles that are contained in the microcapsules have a specific absorption rate (SAR) when exposed to an electromagnetic field, which is different from that of normal cells or tissues, and the particles may be designed to have a charactenstic maximum temperature (Cune point), at which the magnetic matenal loses it thermal conductivity or magnetic permeability and will not heat further upon continued exposure to the magnetic field The microcapsules are also designed so that the melting temperature of the outer polymenc skin or membrane of the microcapsules is less than the Cune point of the magnetic particles withm that microcapsule. The magnetic particles may be composed of a vanety of metals mcludmg ferromagnetic particles, such as Fe 3 0 4 , iron carbonyls and combinations of vaπous transition metal oxides. The inventors have demonstrated the utility of ceramic coated particles compnsmg oxides of iron, nickel and zinc, such as particles compnsmg about 66 wt % Fe 2 0 3 , about 9 wt % NiO, and about 25 wt % ZnO. Additional metals that may be used in the particles descnbed herein mclude, but are not limited to cobalt, copper, gold, silver and combinations thereof, including copper containing gold and silver alloys The magnetic matenal used in microcapsules as descnbed herein is also typically covered by a matenal such as a ceramic that is compatible with the liquids withm the microcapsule and with the drug or active agent. Although the particles descnbed herein are coated with ceramics, other coatings that are compatible with the liquid phases and drugs or solvents to be used in the microcapsules. Ceramics were chosen for the exemplary microcapsules descnbed below because of their low antigemcity, they are not chemically reactive with the solvents or drugs used in the microcapsules, and the protect the metal from oxidation. Alternate coatings would include, but not be limited to methacrylates, algmates, dextran, polyacrylates, polyvmyl pyrrolidone (if the ferrous matenal is fully oxidized). For use in clinical applications, the particles may have a Cune temperature of from about 41°- 44° or even up to as high as about 80 to 95°C. Such high temperatures may be utilized in the microcapsules because the small magnetic particles are a point heat source rather than a tissue hyperthermia technique, which could never be used at such high temperatures without causing extensive tissue damage. With the microcapsules of the present invention, it is contemplated by the inventors that even a Cune point of 95°C would cause collateral damage in only a few neighbonng cells. In the practice of the invention, one may use an electromagnetic field with a frequency of about 85-95, or even about 100 kHz, a strength of about 1500-2000 Amps/m, although frequencies below about 500 KHz are also acceptable. Certain compositions may also contain mixtures of microcapsules m which some capsules contain particles with different Cune temperatures than others, or microcapsules with polymer membranes that have different melting temperatures so that one can effect multiple releases of drug with a single infusion. Of course, one may release different drugs at different temperatures, or one may effect multiple releases of the same drug. This allows a physician to release part of the drug under control of an electromagnetic field, and then later release more drug by using a different field power or time, or to release different drugs separately, still from a single infusion or injection. The invention, therefore, provides a flexibility that is a distinct advantage over pnor methods of controlled delivery. In a method of using the microcapsules. after the microcapsules reach a target site such as a tumor, either by direct in j ection or infusion, the microcapsules are exposed to an external electromagnetic field that is tuned to the maximum SAR of the magnetic particles contained in the microcapsules. This method may include exposure of microcapsules entrapped m tissues of a subject where the exposure is by external administration of the electromagnetic field through the subject's skin and outer tissues. This energy is absorbed by the magnetic particles which are heated to their Cune temperature without heating the surrounding tissue. The heated magnetic particles melt a hole or perforation in the outer skin of the microcapsules, thereby lysmg the microcapsules and providing a conduit for rapid release of the drug by bulk fluid flow out of the microcapsules and or diffusion of the drug out of the hole created in the membrane. The released drug is then m contact with cells at the local site. It is understood that, although the heating of the particles withm the microcapsules does not require heating of the local tissue, that the compositions and methods descnbed herein may be used in conjunction with local hyperthermia therapies where desired. In certain embodiments, the microcapsules may be exposed to an electromagnetic field of up to 500 KHz, and in certain embodiments, around 100 KHz, or alternatively to from about 6.78 to 27.12 MHz radiofrequency, from about 915 to about 2450 MHz microwave radiation, or to ultrasound. In the practice of the invention, virtually any drug may be encapsulated, including both hydrophilic and hpophilic drugs. Certain embodiments include the encapsulation of an anti-cancer drug, such as cis-platin, doxorubicin, daunorubicm, paclitaxel, azindmylbenzoquinone, muramyl- tnpeptide, 5-fluoruracιl, and other types of drugs that would include, but not be limited to anesthetics, systemic antibiotics, antiparasitics, systemic qumolones, anti-mfectives, anti-inflammatoπes, ammoglycosides, cephalosponns, penicillins, antidotes, anti-cholinesterases, metal poisoning antidotes, antineoplastics, cytotoxic agents, hormones, steroids, immunomodulators, cytokines, mterleukms, systemic antivirals, systemic antifungals, biologicals, alpha-antitrypsin, bone metabolism regulators, hypercalcemic agents, cardiovascular agents, beta blockers, cerebral vasodilators, cerebral metabolic enhancers, cholmesterase inhibitors, colony stimulating factors, granulocyte-colony stimulating factors, granulocyte macrophage-colony stimulating factors, vasopressors, local diabetic agents, diagnostics such as CT scan enhancers and angiocardiography agents, adenosme deaminase deficiency agents, gonadotropm inhibitors, adrenal cortical steroid inhibitors, gonadotropm releas g hormone stimulants, vasopressms, urofolhtropins, muscle relaxants such as neuromuscular blocking agents, prostaglandm analogs, prostaglandms, prostaglandin inhibitors, respiratory therapy agents, anticholmergics, beta andrenergic stimulators, sympathomimetics, and thrombolytics In certain embodiments, the drugs may be enzymes, or proenzymes that may be encapsulated and activated by mixing as descnbed in a related application by the same inventors, entitled "In Situ Activation of Microcapsules" incorporated herein by reference. In addition to the methods of mixing immiscible layers descnbed elsewhere, m microcapsules containing magnetic particles, one can facilitate internal mixing by exposing the microcapsules to an oscillating magnetic field. As such, certain embodiments of the present invention may be descnbed as methods of treating a tumor in a sub j ect compnsmg: obtaining a pharmaceutical composition compnsmg a plurality of microcapsules m a pharmaceutically acceptable solution, each microcapsule compnsmg two or more immiscible liquid phases enclosed in a polymer shell having a melting temperature, magnetic particles withm the microcapsules having a Cune temperature higher than the melting temperature of the polymer shell, and contamed a liquid phase in contact with the polymer shell, and an anti-cancer drug contamed in a liquid phase; administering the pharmaceutical composition to the subject in a manner effective to place the microcapsules withm or adjacent to the tumor; and applying a magnetic field to the microcapsules effective to heat the magnetic particles to their Cune temperature and melt at least a portion of the polymer shell In certain embodiments of the invention, the microcapsules may also contain a radiocontrast media, or a medium that becomes radio-opaque through a change of oxidation state when exposed to energy. The radiocontrast media to be used may include, but is not limited to a halogenated oil, such as for example, halogenated poppy seed oil, cotton seed oil, soybean oil, safflower oil, corn oil, olive oil, sunflower seed oil, sesame seed oil, or canola oil. The microcapsules of the invention can be separated by filtration or other means known in the art to obtain a population of microcapsules of a particular size range that is preferred for a particular use. Typically, microcapsules of 1-20 micron diameter are optimum for intravenous administration, whereas, 50-300 micron diameter microcapsules are used for mtraartenal delivery and 300 micron or greater for mtrapentoneal administration. In each size range, highly uniform microspheres are needed for maximum packing densities and maximum drug payload delivery to target organs or tumors. Therefore, one may obtain microcapsules of from about 1 to about 500 microns m diameter, or from about 300 to about 500 microns m diameter, or from about 30 to about 50 microns m diameter, or even from about 1 to about 20 microns m diameter As is known in the art of chemo-embohzation, particles of a certain size will form a part of an embohzation m different areas such as the artenal, lung capillanes, venous, or even pentoneal systems of a body. Microcapsules may be designed, then to be used in a chemo- embolization application, or they may be designed to pass freely through the capillanes or circulation of a subject m order to reach a target site. In the practice of the invention, one may choose microcapsules of a particular size so that the microcapsules will occlude an artenal or venous vessel, for example at the site of a disease. Such a disease site may be a thrombosis, a wound, a site of infection, a lipid deposit or even the vasculature of a tumor. Because the microcapsules contain magnetic particles, they may also be localized by application of an electromagnetic field as is known in the art, except that care must be taken not to heat the particles prematurely The drug precursors of the present invention are m certain cases a proenzyme or a zymogen. A proenzyme is an inactive enzyme precursor that can be activated by cleavage of one or a few specific peptide bonds. In certain embodiments the proenzyme may be a pro-thrombolytic enzyme, or a pro- urokinase, or a pro-tissue plasminogen activator. Certain embodiments of the invention will mclude the use of fluonnated pynmidine or punne analogs such as the prodrug Floxuπdine (Fluorodeoxyundine) which is converted to the inhibitor 5'- monophosphate nucleotide (F-UMP) by thymidme kinase Other embodiments may utilize the oxidation, reduction or hydrolysis of a prodrug that results in activation, change m activity or m conformation. Another example may be the use of the prodrug 6-mercaptopunne, which is activated to 6-mercaptopuπne nbonucleotide. the oxidation of tπmethadone to the active agent, dimethadione, the oxidation of phenacetin to methemoglobin, or the reduction of chloral hydrate to tnchloroethanol. In addition, active agents may be produced in microcapsules by contact with lipid soluble enzymes such as those isolated from the hepatic microsomes, or they may use doxorubicin denvatives activated by lysozyme. As descnbed herein certain inventions of the present disclosure may be compositions compnsmg a microcapsule compnsmg two or more immiscible liquid phases enclosed m a polymer shell, a drug precursor and possibly a drug activator, wherein the drug precursor and drug activator, when present, are contained m separate immiscible liquid phases, a magnetic particle with a Cune point higher than the melting temperature of the polymer shell and further wherein the microcapsule is made by the method compnsmg : formulating a first phase compnsmg a first solvent, a first polymer soluble m the first phase and insoluble m a second phase, a co-solvent, oil, and water; formulating the second phase immiscible with the first phase, the second phase compnsmg a second solvent, a second polymer soluble m the second phase and insoluble m the first phase, a surface active agent, and a salt; the surface active agent having a hydrophihc/lipophilic balance value greater than that of the first polymer, the second polymer having a hydrophihc/lipophilic balance value lower than that of the surface active agent; creating an interface between the first and second phases m a manner that limits fluid shear to between about 1 to 100 dynes/cm 2 , if earned out under conditions of greater than or about equal to 1 gravity, or between about 2 to 30 dynes/cm 2 , if earned out under conditions of less than or about equal to 1 x 10 "2 gravity, and maintains adsorptive surface charactenstics at the interface. It is understood that the magnetic particles are contamed in the liquid layer that lies next to the membrane, which may be an aqueous or hydrocarbon layer depending on the particular application. Processes and compositions are provided by the present invention which overcome certain of the limitations of pnor methodology for forming microcapsules. In particular, methods and compositions are provided which form multilamellar microcapsules having alternating hydrophilic and hydrophobic liquid layers, surrounded by flexible, semi-permeable hydrophobic, outer membranes which can be tailored specifically to control the diffusion rate. In particular, the methods of making microcapsules provided by the present invention do not rely on batch processes such as density-dnven phase separation and stratification into honzontal layers, mechanical mixing or solvent evaporation. Encapsulation of cytotoxic or labile drugs m such microcapsules enables targeted delivery and sustamed release kinetics that are not currently available with intravenous injection. The invention provides, in one aspect, methods of making a multi-layered microcapsule. The term microcapsule as used herein is a general term which can mclude any spheπcal microscopic vesicle including microspheres, micelles, mverted micelles, bilayer vesicles and liposomes. The term microcapsule as used herein is also a more specific term which refers to a microcapsule that compnses at least two layers, one of which is innermost and is substantially completely enclosed withm the other. In a distinct break from traditional methods for making microcapsules, the methods of the invention rely on low fluid shear, mterfacial coacervation and liquid-liquid diffusion process, particularly as developed for forming microcapsules that may contain both aqueous and hydrocarbon soluble drugs. The terms multi-layered and multi-lamellar are used interchangeably throughout the specification and claims and both refer to the fact that the microcapsules of the invention compnse at least two immiscible layers nested around one another. In some instances, the core layer will be hydrophobic m nature and will be completely surrounded by at least one neighbonng hydrophilic layer. In others, the core layer will be hydrophilic m nature and will be completely surrounded by at least one neighbonng hydrophobic layer. The basic method of the invention relies on liquid-liquid interactions. In the basic method, the first step entails formulating a first phase or layer while the second step entails formulating a second phase or layer. The two phases or layers are formulated to be immiscible with one another. For the purposes of this invention, "immiscible" means that due to differences in density, viscosity or surface tension, the two adjoining phases or layers form an interface resembling a meniscus, and furthermore that the solubility of any component one phase is not more than lOgm/lOOml the second, adjoining phase or layer. Formulating the first phase or layer compnses combining a first solvent, a first polymer soluble in the first phase, a co-solvent, an oil, and water. The first solvent will typically compnse about 75-90% by volume of the first phase. The first polymer is selected to be one soluble the first phase and typically will compnse about 1-5% by volume of the first phase. A small amount of a co-solvent is also added to the first phase, which co-solvent may also function as a co-surfactant. Oil compnsmg about 1- 10% by volume is also added to the formulation. The first phase will also contain about 1-5% water by volume. The method next calls for formulating a second phase immiscible with the first phase The second phase compnses a second solvent, a second polymer soluble m the second phase, a surface active agent, and a salt. The relative, approximate volume percentages of these constituents is about 70-98% second solvent, 1-10% second polymer, 1-4% surface active agent, and 0-3% salt. In order to ensure that the liquid-liquid interactions necessary to form the microcapsule will occur, certain of the constituents of each phase are selected relative to one another. Thus, the surface active agent m the second phase is selected such that it will have a hydrophihc lipophilic balance value greater than that of the first polymer constituent of the first phase. Generally, the most useful surface active agents have been found to be those which are nomomc and which have a hydrophihc/lipophilic balance value of 10.0 or greater. Next, the second polymer constituent of the second phase is selected to have a hydrophihc/lipophilic balance value lower than that of the surface active agent constituent of the same phase. While not an exhaustive list, certain hydrophihc/lipophilic balance values of matenals which may be used in the formulations of the invention are provided below HYDROPHILIC/LIPOPHILIC BALANCE (HLB) (McCutcheon 1979) Compound HLB Glycerol trioleate 0.8 Cholesterol 1.0 Triglyceride of coconut oil 1.4 Sorbitan trioleate 1.8 Sorbitan tristearate 2.1 Glycerol monooleate 2.7 Mono and di glycerides of fat burning fatty acids 2.8 Glycerol Monostearate (gms) 2.8-5.0 (3.8 preferred) Propoxylated ethylene diamine plus ethylene oxide 3 -28 Mono/diglyceride 3.2 Glycerol mono coconut 3.4 Mono/diglyceride 3.5 Propylene glycol mono fatty acid ester 3.5 Monoethoxyl lauryl ether 3.6 Stearyl lactyl acid 3.8 Hydrogenated cottonseed oil 3.8 Sodium lauryl sulfate 4.0 Mono and diglycerides with citric acid or 4.2-4.6 Lactylic ester or fatty acid Ethoxylated fatty amine (2 moles ETO) 4.5 Diethylene glycol monostearate 4.7 Sorbitan monopalmitate 4.7 Diethylene glycol monostearate and oleate 4.7 Ethoxylated (2) cetyl ether 5.3 Glycerol Monoricinoleate 6.4 Glycerol monolaurate 6.8 Triglycerol mono stearate 7.0 Polyethylene glycol (400 dioleate) 7.2 Lanolin sterol 8.0 Ethoxylated nonyl phenol (CO-420 & CO 850) 8.0-16.0 Polyethylene glycol (400) distearate 8.2 Sorbitan monolaurate 8.6 Ethoxvlated sorbitan fattv acid esters and alkyl/aryl alcohol 9.0 Compound HLB Anhydrous lanolm 10.0 Polyethylene glycol monostearate 11.0 Polyethylene glycol 400 11.2 Ethoxylated ( 10) cetyl ether 12.9 Ethoxylated glycerol monostearate (gms) 13.1 Sorbitan monostearate 14.9 Sorbitan monooleate with 20 moles ethylene oxide 15.0 Ethoxylated (20) oleyl ether 15.3 Ethoxylated (20) stearyl cetyl ether 15.8 Ethoxylated castor oil 18.0 Nonyl phenol polyethylene glycol ether 18.1 Polyethylene glycol 600 mono laurate 19.6 Sodium lauryl sulfate 40 Propylene glycol monostearate 40 Hydroxylated lanolm sodium oleyl sulfate 42 Blends of GMS and sorbitan monooleate 52 with 20 mols ethylene oxide The basic method next involves creating an interface between the first and second phases. The creation of the interface is achieved m such a way that minimal shear and mixing occurs between the phases. The two immiscible phases are brought together in such a mechanical manner that the fluid shear properties are controlled to low levels, typically below about 12 dynes/cm 2 , and such that the adsorptive surface properties at the immiscible interfaces are not significantly altered. Although the exact mechanisms are not fully understood, the inventors believe that the maintenance of certain surface properties, such as the surface tension, Helmholtz charge distnbution (electncal double layer), and partitioning of the surfactant molecules between the immiscible phases must remain substantially intact so that lateral phase separation can occur in a manner which allows simultaneous formation of multiple liquid interfaces (oil water or water/oil) and which results in microcapsules having alternating sphencal shells of hydrophilic and hydrophobic liquid layers. This is believed to be the mechanism for the formation of multi-lamellar vesicles which are formed m a single step. Although this can best be demonstrated under microgravity conditions, wherein buoyant convection is absent and diffusion-dnven convection and surface tension differences predominate, this also can be accomplished m unit gravity conditions by balancing the density differences between the two liquid phases or by any other mechanical means which prevents excess fluid shear from significantly altenng the normal adsorptive surface properties which are determined by the chemical composition of the formulas and the rnterfacial phenomena among the solvents, polymers and surfactants. In a preferred embodiment, the creation of the interface will occur by sliding individually separated compartments containing the two phases mto register with one another m a manner that substantially limits shear and provides gentle mixing. In the final step of the basic method, conditions are established m order to substantially limit all mixing between the interfaced liquid phases. In the most preferred environment, the two phases would be allowed to interact at their interface without agitation, stirπng, shearing or like force. It is preferred to also limit even those quiescent forces such a gravity-controlled sedimenting, phase separation mto stratified layers, shifting, dnft and the like. Thus, in certain preferred embodiments, only chiefly diffusion-dnven convection and lnterfacial coacervation is used to spontaneously form microcapsules, as the chemical formulations of the different phases assist m lowenng the surface free energy across the interface. It is also at this time that formation of the polymenc outer coating is initiated. In one embodiment, the two liquids thus formulated are separated mto distinct compartments or spaces which spaces are each connected to a central diffusion chamber into which each compartment can deliver its resident liquid loading. The compartments are initially closed to access mto the central diffusion chamber so that the first and second liquids are kept apart from one another and not allowed to interact. While it is possible to use any number of devices to achieve this separation, a preferred device is a device like the Matenals Dispersion Apparatus (MEPS) descnbed m more detail elsewhere. Preferred devices are also descnbed in a related US Patent Application by the same inventors and John M. Cassanto filed concurrently with the present application and entitled, "Microencapsulation and Electrostatic Processing Device." The separation of the two liquids is maintained until both liquids and the device containmg them can be placed in an environment in which convective mixing may be minimized, such as m a microgravity environment. The methods of the invention are slightly different depending upon whether the first solvent is selected to be organic or aqueous Where an organic solvent is used to formulate the first phase, that organic solvent is selected from the group of organic solvents consisting of ethyl alcohol, methyl alcohol and isopropyi alcohol. Where an organic first solvent is used to formulate the first phase, the first polymer is selected to be one soluble in the organic solvent selected. Such a first polymer may be selected from the group of polymers consisting of glycerol monosterate, glycerol monooleate, glycerol monolaurate, glycerol dioleate, glycerol disterate, cholesterol, stigmasterol, phytosterol, campesterol, and lecithins such as phosphatidyl chohnes (e.g., Centrolex-F ® ). Where the first solvent is aqueous, a slightly different approach is taken. In those instances, the first polymer is aga requisitely soluble in the first aqueous phase and may be selected from the group of polymers consisting of polyvmyl pyrrolidone, polyvmyl alcohols, gelatm, gum tragacanth, carrageenan, Karaya gum, Guar gum, gum arable, alginates, carboxymethyl cellulose, hydroxypropyl cellulose, carboxypropyl cellulose, and lecithins. Regardless of the formulation with an aqueous or organic first solvent and polymer, the methods of the invention both use a co-solvent which may be selected from the group of co-solvents consisting of C 3 -Cs alcohols, tetrahydrofuran, dioxane, acetonitπle, dimethylformamide, dimethylacetamide, and dimethyl sulfoxide. Similarly regardless of the organic/aqueous nature of the first solvent and polymer used, the methods of the invention add to the formulation of the first phase an oil. These oils may be selected from the group of oils consisting of unsaturated oils such as poppy seed oil, olive oil, peanut oil, sesame oil, cotton seed oil, soybean oil, safflower oil, corn oil, sunflower seed oil and canola oil or saturated oils such as mineral oil, long cham paraffinic oil, and liquid petrolatum. In a preferred embodiment, poppy seed oil will be halogenated, or m certain embodiments, lodrnated to form lodinated poppy seed oil (IPO) and incorporated into a microcapsule as a marker or tracer for tracking the presence of the microcapsule once injected via radiocontrast detection methods known well to those of skill m the art of radiography. Whether the method involves an organic or an aqueous first solvent, the second polymer, the surface active agent and the salt may each be selected from a particular group of such compounds. The second polymer may be selected from the group of polymers consistmg of polyethyleneglycol 400- 20000 daltons, dextran 1000-100,000 daltons, polyvinylpyrrohdone, polyvmyl alcohols, gelatin, gum tragacanth, carrageenan, Karaya gum, Guar gum, gum arable, alginates, carboxymethyl cellulose, hydroxypropyl cellulose, carboxypropyl cellulose, and lecithins. The surface active agent is selected from the group of surface active agents consistmg of sorbitan monooleate treated with ethylene oxide, dextran, polyethylene glycol, Cι 2 -C o fatty acids, 2-amιno-2-methyl-l -propyl ammomethyl propanol amphotenc salts and quaternary ammonium salts. The salt is selected from the group of salts consisting of NaCl, KC1, CaCl 2 , MgCl 2 , quaternary ammonium salts such as cetyl tnmethylammonium bromide and 4-methoxy-4(3-phosphatidyl cholme)spιro(l,2-dιoxetane-3-g,l-adamantane) disodium salt. Multi-layered microcapsules, with both hydrophobic and hydrophilic drug compartments, as produced by the methods of the invention enable diffusion of complimentary drugs from the same microcapsule, e.g. antibiotics and lmmuno-stimulants to treat resistant infections or multiple fϊbπnolytic drugs to dissolve emboh. Co-encapsulation of radio-contrast medium as provided herein enables oncologists to monitor the delivery of anti-tumor microcapsules to target tumors using computerized tomography and radiography that track the distnbution of microcapsules after release from the rntra- artenal catheter. Such microcapsules will have important applications in chemotherapy of certain liver, kidney, bram and other tumors. The diameters of microcapsules possible to attain using the methods of the invention are also of particular usefulness in medical applications Thus, whereas pnor art methods have been able to routinely produce microcapsules over 1-10 micron average sizes, the present invention's methods provide similarly-sized microcapsules of 1-20 micron diameters for mtravenous admmistration. Also provided are 25-300 micron sized microcapsules particularly useful m interartenal chemoembolization of tumors, and microcapsules m the range of 300 micron and greater diameters useful m lnterpeπtoneal or intramuscular administered drugs The pharmaceutical composition encapsulated in the microcapsule may be one soluble in aqueous solutions or may be one soluble in organic solutions This, of course, governs the selection of the phase or layer in which the pharmaceutical composition is formulated The microcapsules of the invention and methods for producmg them are of particular utility when formulating organic-soluble drugs as these types of drugs are otherwise very difficult to administer. The pharmaceuticals may be those selected from the group of such widely diversified pharmaceutical compositions as that consisting of cytotoxms, proteases, cytokmes, anti-nauseants, steroids, anti-fungal agents, fibrmolytic enzymes, and antibiotics The inventors have successfully encapsulated representatives of these classes of pharmaceuticals using the methods of the invention It is also possible to incorporate a pharmaceutical composition which is not initially dissolved in one or another of the phases or layers, but rather which drug is in suspension As noted above, depending upon its solubility and upon where the pharmaceutical chemist wishes to locate the drug, it is possible to formulate a drug in any of the phases or layers, by dissolving or suspending the drug as needed Upon melting of the polymer shell by heating the magnetic particles, any of such layers and their contents will leak out of the microcapsule. The methods of the invention surpnsingly demonstrated the ability to package very high concentrations of drugs in the layers formed It is possible, usmg the methods of the invention, to formulate a pharmaceutical at a concentration sufficient to allow nascent crystal formation within the microcapsule once it is formed These microcapsules, due in one regard to their being constructed with outer polymenc coatings, are also particularly flexible yet rugged (able to withstand shear forces greater than 10 dynes/cm 2 ) As will be related specifically below, microgravity expenments, on sounding rockets (1989-92) and Shuttle missions STS-52 (1992) and STS-56 (1993) usmg an automated Matenals Dispersion Apparatus, produced multi-lamellar microcapsules contammg both Cis-platmum (anti-tumor drug) and lodmated poppy seed oil (a non-radioactive, radiocontrast medium), surrounded by a polymenc skin. Microcapsules formed with amoxicilhn (antibiotic) or urokinase (a clot dissolving enzyme), co-encapsulated with IPO, were still intact after two years after return to 1 x g environments In many instances, microcapsules were formed with the Cis-Platinum or amoxicillin so concentrated that crystals of the drugs formed inside In certain embodiments of the methods of the invention, pharmaceutical compositions will be incorporated into the microcapsule Where such pharmaceuticals are thusly incorporated, they may be introduced initially as a solute or as particulates suspended in one or the other of the liquids used to formulate the layers of the microcapsules In certain embodiments, the pharmaceutical is introduced in one of the phases or layers used to produce the microcapsule at a concentration sufficient to allow nascent crystal formation withm said microcapsule. Crystal formation may occur at or near the time of formation of the microcapsule containing the dissolved pharmaceutical matenal. The aqueous solvent system used to dissolve an aqueous-soluble pharmaceutical is selected to permit water molecules to migrate away from the drug-containing layer mto the alcoholic mixture. The process of crystal formation is likely to be promoted in this manner after formation of the microcapsule. In fact, it is possible to enhance the crystallization process after the microcapsule is formed by controlled transport of the solvent phase or layer in which the pharmaceutical to be crystallized is a solute. In certain embodiments, the crystal thus formed may take up most of the internal capacity of the microcapsule. Surpnsmgly, the methods of the invention have demonstrated a unique ability to encapsulate such saturated drug solutions, and since the overall partitioning charactenstics between immiscible layers facilitates solvent transport out of the aqueous layer, it is possible to concentrate the drug to the pomt that formation of drug crystals occurs within the microcapsules. This ability of the microcapsules and methods of the invention provides the maximum drug payload per microcapsule and the best drug release kinetics for prolonged treatment at maximum drug diffusion rates. Microcapsules contammg a large volume component of crystallme drug provide the most concentrated drug possible when it is released at the target site. Until the crystals are completely dissolved, the drug release rate is independent of time (zero order release kinetics). When the crystals have dissolved, the drug release rates revert to first order kinetics (exponential with time). The encapsulated crystals of the invention are in the range of 1-100 microns along one face. Since these crystals are precipitated in situ, they are quite different from the other commercially-available crystallme drug delivery systems (e.g., Microcrystal®) which use phosphohpids to encapsulate tiny particles or crystals of drugs with an average diameter of only 0.3 - 1.0 micron [Pankl and Stern 1994]. It is also possible to additionally treat the microcapsules thus formed with additional steps. In some instances, the methods of the invention, regardless of whether they initially use an organic or an aqueous first solvent, formulate a third phase compnsmg an oil or C 20 -C 38 paraffin and, contact the formed microcapsule with the third phase. In other instances, the methods of the invention form a two- layered microcapsule, then formulate a third phase compnsmg an aqueous solution and, contact the formed microcapsule with the third phase. The basic method and alternatives are summarized below. Group 1 Group 2 Solution 1 Solvent 1 is a hydrocarbon Solvent 1 is aqueous Polymers are hydrocarbon soluble, selected to Polymers (skin) are water soluble, form the outer coating (typically of lower HLB but can be extended into organic values) phase (includes phosphohpids) Ex. Centrolex F ® Co-solvents alcohols, hydrocarbons (act as co- Co-solvents same, but often less % surfactants) Oils saturated or unsaturated oils Ojls same Prodrug or activator dissolved (or suspended Prodrug or activator dissolved (or paniculate) paniculate) Solution 2 Solvent 2 aqueous Solvent 2 same Polymers water soluble (PEG, Dextran) Polymers same Surfactants (typically higher HLB value) Surfactants same but often less % Salts ionic, quaternary ammonium salts Salts same, but often different % Prodrug or activator aqueous soluble Prodrug or activator aqueous soluble Solution 3 Oils hydrocarbons Oils same Polymers hydrocarbon-soluble Polymers same Drugs can be included Drugs can be included ■ OR - - OR - Alternative aqueous solution Alternative aqueous solution Coating-adjuvants coating same polymer same Immunoglobulins Polymers - aqueous soluble surfactants same Surfactants - Traditional emulsion methods form a O/W/O (oil/water/oil) or W/O/W (water/oil/water) liquid system which is designed to retain the internal phase(s) withm the external solvent unless the emulsion is broken, whereupon the liquid phases separate. In the methods of the invention, the use of surfactants and co-surfactants permits formation of an emulsion of large spheroids (not small microspheroids) of one phase dispersed in the other phase configured m a sphere. The sphere is also surrounded by another immiscible liquid layer (opposite phase to that of the innermost liquid sphere) and then (often) this multi-layered sphere is contamed in another opposite-phase liquid layer and finally the entire multi- layered sphere is contamed in an outer skin. The results of the process of the invention are not to form a traditional O/W/O or W/O/W emulsion (which is a fine dispersion of one phase m another), but rather to form multi-lamellar, alternating immiscible-layer microcapsules contamed withm a thm, semi- permeable outer skin. In the microcapsules of the invention, the immiscible phases are distmct and separated accordmg to the surface tension charactenstics of the liquids at each interface, hence there is no true emulsion maintained by the surfactant which could be broken. Thus, m certain embodiments of the methods and compositions of the invention, the multi- layered microcapsule will be produced which compnses at least three alternating layers or phases. Thus, if the first layer is an aqueous layer or core, the next layer may be an organic layer. This organic layer may then be covered over by a second aqueous layer which forms on its outer surface a polymenc skin. Conversely, the liquid at the core of the microcapsule may be an organic liquid layered over by an aqueous layer followed by another organic layer which forms a polymenc skin over the surface of the microcapsule. Certainly, extension of these basic formulations may be envisioned where four or more layers are possible or where multiple skins or coatings are utilized. Whether used in conjunction with a two-layer microcapsule or with microcapsules with more than two layers, the coatings of the present invention are of substantial utility, particularly when the methods are earned out at Earth-normal gravity The coatings can be either substantially of a hydrophobic nature or of a hydrophilic nature as descnbed below and are denved from addition of certain polymers in the initial formulations of the liquids used to make the microcapsules. Where hydrophobic coatings are used in conjunction with drug-delivery systems, the coatings are selected for then- complementary permeability to the drug to be delivered. The polymers are also selected for their flexible charactenstics after formation and cunng which is of particular utility during lntravascular transport and allows higher packing densities for forming emboh such as m chemoembohzation therapy. Thus, for example where a water-soluble drug is to be delivered, the drug is contamed in an inner aqueous layer over which is placed a coating permeable to the dissolved drug. In alternate embodiments, the drug may be more hydrophobic and will be contained m a hydrocarbon layer withm the microcapsule. In either embodiment the drug may actually be a prodrug, and an activator may be contamed m a layer immiscible with the layer containing the prodrug. Preferably, the coating matenal should be impermeable to solvents or oils. The coatings which have been observed to be deposited on the surfaces of the microcapsules of the invention are about 0.01-2.0 microns thick where the coating is a hydrophobic coating, and about 0.1-5.0 microns thick where hydrophilic coatmgs are deposited. The additional steps and third formulated phases may also be used advantageously to provide the microcapsule with specific charactenstics. Thus, the third phase may further compnse a pharmaceutical composition which is added to the formed surface of the microcapsule. The third phase may also be used to add a pharmaceutical composition such as an adjuvant. The adjuvant may further compnse an immunoglobulin, other protein, hydrocolloid or polysacchande. This is of particular utility in designing microcapsules with unique lmmunologic, proteinaceous, surface charged, or other surface charactenstics which makes them selectively adhere to certain target tissues (cells) or renders the microcapsules attractive to certain phagocytic cells (when the cells are the actual target for the therapeutic drug). Where the adjuvant is a hydrocolloid, it may be selected from the group of such hydrocolloids consisting of collagen, isoelectnc gelatin, agar, gum arable, gum tragacanth, alginates, cellulose denvatives, guar gum, cyclodextnns, and carrageenans. The third phase may also further compnse a surface active agent. The third aqueous phase can also contain a chemical activator which acts upon the inactive form of the pharmaceutical agent (drug) as it diffuses out of the inner layers of the microcapsule. The function of the activator is to chemically convert the inactive drug to its active form just before it is released from the microcapsule. This is illustrated when the pharmaceutical is a pro-enzyme and where the activator is another proteolytic enzyme which cleaves the pro-enzyme at active site to render the molecule biologically active. This embodiment can be used to deliver very labile drugs which have very limited shelf-lives or short biological half-lives whereupon the activator (third phase) can be added just pnor to mtravascular administration such that the inactive drug becomes activated after the microcapsules have reached the target site Upon activation, the microcapsules are exposed to an electromagnetic field effective to heat the magnetic particles, thus melting the polymer shell and releasing the activated drug. This can maximize the therapeutic effectiveness of the short-lived drug at the target site of action. One or more of the phases of the microcapsule of the invention may further compnse fluorescent molecules selected from the group of fluorescent molecules consisting of fluoresceins, cyamns, naturally fluorescent molecules, and rhodamines, and others excited between 260 and 700 nanometers. This is particularly useful where radiocontrast media are not desirable or where an additional tracking method is useful or where it is of value to monitor the presence or absence of a layer in the microcapsule, fluorescent molecules may be incorporated into the microcapsule of the invention. Thus, for instance, as descnbed more fully below, it may be useful to incorporate a hydrophilic fluorescent molecule in the aqueous liquid in order to determine the relative location and number of aqueous liquid layers in a certain production batch of microcapsules produced by the methods of the invention. Cntical to the success of the methods of the invention is the substantial limitation of mixing between said phases to diffusion-dπven convection and low fluid shear (preferably less than 50 dynes/cm 2 ). One manner in which to so limit other types of mixing is to carry out the methods under rmcrogravity. Microgravity is defined as a gravity force of less than 1 x 10 "3 x g. Such gravitational environments may be achieved in a vaπety of ways, at least some of which are detailed herein. For instance, microgravity may be achieved m certain trajectones of sounding rockets. Even longer penods of microgravity may be obtained with temporary orbiters such as the space shuttle. Relatively indefinite penods of microgravity may be obtained m permanent or semipermanent orbital space craft such as the orbital space station and other geosynchronous orbital satellites. The exposure of the first and second liquids to microgravity has been found to be effective in forming the microcapsules of the invention where the exposure is at least 6.5 minutes in duration, and later studies have shown that a few seconds is sufficient. Certainly, as descnbed more fully below, greater exposure penods have also been proven successful. The inventors have shown that penods of exposure as short as a few seconds will also produce adequate numbers of microcapsules. In formation of microcapsules, however, the methods of the invention will not necessanly use microgravity in order to limit mixing between the phases. Of course, such limitations of mixing can be promoted by carrying out the methods below ambient temperature. Limitation of interactions between the phases is best promoted by substantially balancing the specific gravity between said phases as is descnbed below. The formulations and methods necessary to achieve Earth-normal microcapsule formation are descnbed in greater detail herein. In either case, or m combinations of these techniques, mixing between the two phases may be chiefly the result of diffusion-dπven convection. The inventors have found that there is a greater size distribution which results from microencapsulation at Earth-normal gravity At least a partial reason for this wider size distπbution is apparently the inability under Earth-normal gravity to avoid certain sedimentation phenomena alone and sedimentation effects combined with weight-related contact of sedimented microcapsules. These facts require some additional manipulation under Earth-normal environments not required m the 0 - g environments - namely, sieving of the resulting microcapsules m order to generate more uniform fractions. Therefore, at Earth-normal gravity, the utility of the outer coating of the microcapsules of the present invention become even more important. Enhancmg the ruggedness of the Earth-normal microcapsules by cunng and other steps as related herein may also be used. A preferred method of making a multi-layered microcapsule compnses: formulating a first phase compnsmg an organic solvent selected from the group of organic solvents consisting of ethyl alcohol, methyl alcohol and isopropyi alcohol, a first polymer soluble m the first phase selected from the group of polymers consisting of glycerol monosterate, glycerol monooleate, glycerol monolaurate, glycerol dioleate, glycerol disterate, cholesterol, stigmasterol, phytosterol, campesterol, lecithins such as phosphatidyl cholmes (e.g., Centrolex-F ® ), a co-solvent selected from the group of co-solvents consisting of C 3 -C 8 alcohols, tetrahydrofuran, dioxane, acetomtπle, dimethylformamide, dimethylacetamide, and dimethyl sulfoxide, an oil selected from the group of oils consisting of poppy seed oil, olive oil, peanut oil, sesame oil, cotton seed oil, soybean oil, safflower oil, corn oil, sunflower seed oil, canola oil (unsaturated oils), or mineral oil, long chain paraffinic oil, and liquid petrolatum (saturated oils), and water; formulating a second phase immiscible with the first phase, the second phase compnsmg water, a second polymer soluble in the second phase selected from the group of polymers consisting of polyethyleneglycol 1000-8000 daltons, dextran 1000-10000 daltons, polyvmylpyrrolidone, polyvmyl alcohols, gelatin, gum tragacanth, carrageenan, Karaya gum, Guar gum, gum arable, alginates, carboxymethyl cellulose, hydroxypropyl cellulose, hydroxyethyl cellulose, carboxypropyl cellulose, lecithins, a surface active agent selected from the group consisting of sorbitan monooleate treated with ethylene oxide, dextran, polyethylene glycol, C 12 -C 20 fatty acids, cyclodextπns, PEG dextran copolymer, PEG acrylates, lactides, galactides, chitosan, Zem®, carbapol, polyoxamers, quaternary ammonium salts, and a salt selected from the group of salts consisting of NaCl, KC1, CaCl 2 , MgCl 2 , quaternary ammonium salts, such as cetyl tnmethylammomum bromide, 2-amιno-2-methyl-l -propyl ammomethyl propanol, and 4-methoxy-4(3-phosphatidyl cholιne)spιro(l,2-dιoxetane-3-g,l-adamantane) disodium salt; the surface active agent having a hydrophihc/lipophilic balance value greater than that of the first polymer; the second polymer having a hydrophihc/lipophilic balance value lower than that of the surface active agent; creating an mterface between the first and second phases m a manner that substantially limits fluid shear; and, substantially maintaining adsorptive surface charactenstics of said interface. Microcapsule products produced by any of the methods of the invention are also claimed. The methods of the invention are used to form unique multi-lamellar, microcapsules, having alternating hydrophilic and hydrophobic liquid layers surrounded by a flexible, semi-permeable, polymenc outer "skin". The outer skin which can be either hydrophilic or hydrophobic, is designed to allow controlled drug diffusion out of the microcapsule. The outer skin is also designed to have a melting temperature below the Cune point of the encapsulated magnetic particles, so that exposure to an electromagnetic field will cause the melting of a hole or pore m the skin, thus aiding m release or diffusion of dissolved chemicals out of the microcapsule. Unlike any natural phosphohpid or other component of cell membranes, the outer skin of the microcapsules of the invention will not reform an intact membrane, and is designed to avoid recognition and phagocytosis by immune cells, thereby increasing the amount of drug delivered to the tissues. The multi-layered microcapsules of the invention can entrap multiple drugs in different solvent compartments and saturated solutions of drugs which may then form crystals side the microcapsule Radiocontrast medium can be co-encapsulated with drugs in the same microcapsule A magnetic resonance contrast agent can also be encapsulated such as vanous metallo-orgamc compounds including aqueous soluble ferrous gluconate, Gadolinium diethylene tnamine pentaacetic acid and hydrocarbon- soluble, iron pentacarbonyl. The microcapsules of the invention have been found to provide a surpnsingly uniform distnbution of diameters. This uniformity is particularly important in its medical applications. The microcapsules thus produced can be used to deliver several drugs which can be released sequentially to the target tissues through choosing magnetic particles with vanous Cune points, for example. The deformable, liquid-filled microcapsules also have advantages over solid matnx microcapsules in achieving maximum packing density m blood vessels, thereby decreasing blood flow to target tissues This enhances the therapeutic effect of combined drug delivery and reducmg the blood supply to vascular tumors (chemoembohzation). The methods of the invention result m more sphencal, uniform size distπbutions of microcapsules. When companng certam prior art equipment and methods for forming microcapsules (Microfluidics, Inc.), the inventors found that even the preferred formulations disclosed herein were mcapable of providing such uniformity with the pnor art equipment. In certam instances, hardly any microcapsules formed at all where mixing and vortexmg were used to distπbute one phase mto the next. In others, poorly formed and non-sphencal microcapsules resulted. In contrast to the failures of the pnor art methods, the methods of the mvention were successfully used to generate uniform, spherical microcapsules both under unit gravity and under microgravity conditions. Such uniformity enables supenor drug delivery. Enhanced uniformity also enables better dose distnbution calculations for establishing the therapeutic dose in the treatment of specific diseases, especially treatment of certam types of tumors. Importantly, the methods of the invention allow the formation of larger-sized, multilamellar microcapsules (1-350 micron) than heretofore possible. Such a capability allows multilamellar microcapsules to be made specifically for inhalation and deposition in the lungs. This uniformity allows facile sieving or filtenng of the microcapsule products in order to obtain highly uniform diameter fractions. Most liposomes have a very small hydrophobic compartment and therefore can only carry small amounts of hydrophobic drugs. Contrastingly, the microcapsules of the invention have a relatively large hydrophobic liquid compartment which enables delivery of more hydrophobic drug per microcapsule. Moreover, the microcapsules of the invention have relatively large hydrophilic and hydrophobic compartments which permits tandem delivery of both water soluble and non-water soluble drugs in the same microcapsule. As previously noted, the microcapsules of the invention may contain polysacchandes. Inclusion of such polysacchandes is one of several aspects of the methods of the invention that enhance the formation of the microcapsules. The inclusion of injectable polysacchandes m the formulations of the mvention contnbutes to the dnving forces that control phase separation and phase partitionmg of the entrapped drugs. The polysacchandes also provide increased shelf-life and stability of the parenteral suspensions. Use of the neutral salt solutions m the aqueous phase enhances micelle formation, lateral phase separation, and increases the dispersion of microcapsules and then- stability as they are formed. In certam embodiments, phosphate buffered salme containmg dextran may be used. The methods of the invention, in certam embodiments, utilize a non-phosphohpid outer coating. The microcapsules formed by this method are contamed in a thm, semi-permeable, outer membrane compnsed of hydrophobic (e.g. mono- or polyglycendes or waxy-polymers) or hydrophilic polymers (e.g., PVA or PVP), depending on the desired diffusion release rate of the encapsulated drug. Thus, the coating has the advantage of allowing design of the appropnate drug diffusion and release charactenstics while avoidmg certam of the disadvantages of conventional liposomes (and hpid bilayers). In particular, the coating produced by the methods of the invention around the outer surface of the microcapsule avoids bemg readily detected and largely eliminated by the reticuloendothelial system (RES) The outer skin protects the microcapsules against shear forces encountered duπng manufacturing processes and dunng transport withm the vascular system en route to the target tissues. The hydrophobic outer membrane also can be designed to retard oxygen transport, thereby reducmg oxidative degradation of the entrapped drug and improving the shelf-life of the parenteral suspensions. The flexible/deformable outer skm on the microcapsules of the invention results m mcreased packing densities withm vascular beds. This results in microcapsules supeπor to solid microspheres (e.g. gelatin, albumin or starch) commonly used for chemoembolization therapy against tumors. The formulations used to produce the microcapsules of the invention are summanzed below. Table 1 Formulas for Pnmary, Secondary and Tertiary Solutions for Microencapsulation Group 1 Table 1 (cont'd) Group 2 Where the microcapsules of the invention compnse a pharmaceutical composition, certam medically related advantages may be obtained Thus, due to the uniformity and ease with which the methods of the invention allow formation of multilamellar microcapsules, co-encapsulation of multiple drugs is made possible. Thus, for instance, as will be descnbed more fully below, co-encapsulation of drugs and radiocontrast medium in the same microcapsules is made possible by the methods of the invention. Such co-encapsulation allows radiological monitoπng of the tissue distπbution duπng mtravascular delivery. Additionally, incorporation of fluorescent-labels for entrapped drugs enables accurate measure of the drug compartment volumes (usmg fluorescent imaging techniques) and convenient determinations of the drug loadmg efficiencies, particle size distnbutions and measurement of shelf-life stability of the final parenteral suspensions. In some applications made possible by the methods and compositions of the mvention, the organic phase can include a tracer compound or radiocontrast medium to provide the additional advantage of real-time imaging of the microcapsules with computenzed tomography (CT) scanning as they are released from the catheter en route to the target tissue Other examples include aqueous soluble metallo-orgamc compounds used for diagnostic imaging such as ferrous gluconate or Gadolinium diethylene tnamme pentaacefic acid (Gd-DTPA) used for nuclear magnetic resonance imagmg and hydrocarbon soluble agents such as iron pentacarbonyl which also may be used for NMR imagmg. Production of multi-layered microcapsules via the methods of the mvention which possess alternating hydrophobic and hydrophilic drug compartments allows for design of multiple-therapy microcapsules. Spontaneous formation of microcapsules with one or more large hydrophobic solvent compartments increases the potential application for delivery of more aqueous-insoluble drug at target sites with adequate vascular networks. By usmg the microcapsules made possible by the methods of the mvention, sequential diffusion of two or more drugs out of the same microcapsule may be achieved at the target tissues. The incorporation of aqueous-soluble cyclodextnn which can act as an internal hydrophobic drug earner is also made practical usmg the smgle step methods and formulations provided m this disclosure. This extends the capability of the mvention in dehvenng otherwise aqueous-insoluble drugs. For instance, the use of multiple drugs withm the same microcapsule provides microcapsules specifically designed for chemoembohzation treatments. Multiple-drug microcapsules also may be used to deliver first a chemotherapeutic drug which kills tumor cells, and then an immuno-adjuvant (tumor necrosis factor) or lmmunological stimulant (e.g. mterferon-g) that would enhance the patient's immune response to the tumor. Multiple-drug microcapsules can also be used to deliver combinations of chemotherapeutic drugs to tumors that are located in pnvileged sites, such as bram tumors. For example, and as descnbed more fully in the examples to follow, simultaneous delivery of different types of drugs in the same microcapsule is made possible with the methods and compositions of the mvention, e.g. diaziquone and cis-platinum to bram tumors via the carotid artery [K mier et al. 1993]. Multi- layered microcapsules may also be used to treat deep infections that are resistant to systemic antibiotics. In these applications, one or more antibiotics may be sequentially delivered to the site of the infection. Multi-layered microcapsules can be designed to protect active forms of urokmase and other thrombolytic enzymes until they are delivered and entrapped at the local site of a blood clot, where therapeutic doses of the enzyme may then be released by lysmg the outer membrane to dissolve the unwanted embolism. The multilamellar microcapsules can also be used to deliver lmmunostimulants; cytokmes such as Interferons, Interleukins, and growth factors; antmauseants such as metocloprarmde and tetrahydrocannabinol; multiple fibnnolytic enzymes such as urokmase (uPA), tissue plasminogen activator (tPA) and streptokmase; steroids such as hydrocortisone, dexamethasone, etc.; anti-fungals such as nystatm and gnseofulv , anti-virals such as amantidme, lododeoxundme, nboviran; and multiple antibiotics such as amoxicilhn, ampicilhn, etc. In one embodiment, as related to the space-based research that lead to the Earth-normal embodiments of the invention, exposure to microgravity for at least 20 seconds in duration produced microcapsules If the microcapsules of the invention are to be used m 1-g environments, as is generally anticipated, an additional step compnsmg recovenng the multi-layer microcapsules will be necessanly accomplished at Earth-normal gravity Generally, this step will be accomplished by reentry and recovery of the orbital device by which exposure to 0-g was accomplished. While it is preferred to accomplish the recovery without exposure of the formed microcapsules to physical extremes (pressure, temperature, sheanng, mixing, etc.), recovery of the microcapsules of the invention have been accomplished via a transition from microgravity to Earth-normal gravity at accelerations of at least 15-g without substantial loss of integrity. As used herein the term contain or contained in a microcapsule or in a liquid phase or layer is construed to have its normal meaning, and may include suspended or dissolved as in a liquid layer, or mterface, and also includes the meaning associated with a polymer shell mcludmg on its inner or outer surfaces. As used herein, the term "prodrug" or "proenzyme" mcludes the meaning of a precursor, such as lntraglandular prohormones, or the meaning of an agent whose drug or enzymatic activity, or pharmacological action, results from a conversion or transformation mto an active or more active form. Such conversion may be the result of a metabolic process or biotransformation, or it may be the result of an artificial reaction. BRIEF DESCRIPTION OF THE DRAWINGS For a detailed descnption of a preferred embodiment of the invention, reference will now be made to the accompanying drawings wherein: FIG. 1A Schematic of microcapsules contammg magnetic particle that is heated by exposure to an electromagnetic field. FIG. IB Schematic of microcapsules after magnetic particle has melted a pore in the outer membrane and ntenor contents are diffusing from microcapsule FIG. 2 Graph showing the permeability vs temperature of the ceramic ferromagnetic particles encapsulated m the microcapsules demonstrating a Cune temperature of about 48°C. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS The present disclosure is drawn to multi-layered microcapsules and methods of making microcapsules having a polymenc outer membrane that may enclose immiscible liquid phases that contain drugs or bioactive chemicals and magnetic solid particles that can absorb electromagnetic energy and thereby heat up to a predetermined temperature (Cune point or Cune temperature), which is sufficient to melt a hole in, or to melt at least a portion of, or otherwise lyse the polymenc shell and release the liquid contents of the microcapsule mcludmg the drug or bioactive chemical. The microcapsules descnbed herein may, m certam embodiments be injected mto artenes leading to thrombi, vasculaπzed tumors, or other capillary beds, or they may be injected directly mto tumors or other tissues m order to reach a target site. When the microcapsules are at the target site, the patient or subject may be exposed to an external, or internal electromagnetic field, typically for a peπod of a few minutes, thereby causing the magnetic particles to reach their Cune temperature and melt the polymenc shell and release the drug at the target site. In certain embodiments, multiple releases of drug may be achieved by mcludmg microcapsules contammg magnetic particles with diffenng Cune points. In addition, these microcapsules may also contain different drugs so that sequential administrations of a combination of drugs may be achieved by manipulating the frequency of the external field and the length of exposure. The use of magnetic particles for controlled drug delivery may be used with any of the microcapsules and delivery methods as descnbed herein and in related applications. The microcapsules descnbed herein provide advantages over pnor compositions and methods in that the microcapsules may be designed to that the Cune temperature is from about 41°C to any temperature, even as high as 95°C without causing widespread thermal damage to local tissues. Based on the small size relative to a cell and the small number of particles, collateral damage will be minimal. In addition, the microcapsules may be used to deliver multiple drugs from a smgle administration, or to release several pulses of drug as the case may be. Another advantage is that the drug releases are tnggered by external electromagnetic fields that are non-mvasive, can be applied for a shorter time than is necessary for tissue hyperthermia, and do not rely on local hyperthermia, which is hard to control and may cause collateral damage. In addition, induction heating of the magnetic particles is not restπcted to frequencies and power densities normally needed to mduce hyperthermia. The microcapsules are also useful for storing unstable drugs for extended penods, possibly in an inactive form, and for carrying drugs or bioactive agents to the target site in a protected environment until they are released, thus avoidmg unwanted drug activity at non-specific sites, as well as avoidmg potential problems with an immune response to the agent. Finally, the microcapsules containing magnetic particles can be separated and purified usmg DC magnetic fields and routine separation techniques, and they can be concentrated in a chosen tissue location by application of an external magnetic field. For those embodiments descnbed herein m which an electromagnetic field is used to heat microparticles, field strength may be descnbed alternatively as typically on the order of 85-95 KHz or 1500-2400 A/m, or as approximately 3-5 KW. It is known that microparticles and microcapsules may be made to absorb other types of energy than an electromagnetic field. In certam embodiments the microcapsules may contain microparticles or internal components that specifically absorb radiofrequency (6.7-27.1 MHz) or 915-2450 MHz microwave radiation, or ultrasonic waves at greater than 18 KHz, such that the microparticles or internal components are heated to a temperature above the melting temperature of the outer membrane. More specifically, the microcapsules are designed so that, for a particular type of energy to be used (e.g., electromagnetic, radiofrequency, microwave or ultrasound), the specific absorption rate (SAR) of a microparticle or internal component is much greater than the SAR of the outer membrane, which is much greater than the SAR of the surrounding tissue. The design of such microcapsules is descnbed in more detail m the Examples below The present disclosure provides methods of encapsulating multiple drugs or biological therapeutics mto liquid microcapsules or liposomes that are designed for delivery to selected tissues or organs where, upon activation, a short-lived drug can be released directly to the target area by diffusion out of the microcapsules. A method of the present disclosure may be used to form multi-lamellar microcapsules having alternating hydrophilic and hydrophobic liquid layers surrounded by a flexible, semi-permeable, polymenc outer "skm." In this embodiment, the outer skm is designed to allow sustamed diffusion of the bioactive drug from the microcapsule. The methods and compositions of the present invention may use special formulations of solubihzed drugs, surfactants, polymenc co-surfactants, and energy absorbing components within a specific immiscible liquid phase. The energy absorbing medium (e.g. photo activator, thermoabsorber, etc.) absorbs electromagnetic, ultraviolet (UV), infrared (JR.), ultrasonic, radiofrequency (RF), or microwave radiation and thereby causes chemical activation of a chemical substrate or drug precursor mto a bioactive drug molecule which can readily diffuse out of the microcapsule. The absorbed energy also can be used to create thermal convection, Maragom flows or other high velocity flows that can cause interfacial mixing, redistnbution of partitioning compartments withm immiscible phases, and mcreased radiocontrast of selected components within certam liquid compartments. This is exemplified by UV (220-390 nanometers) photoactivation of microcapsules contammg drugs, fluorescent compounds and radiocontrast media in the same microcapsule. The in situ activated microcapsules are characteπzed by: outer polymenc membranes that are both transparent to the activating radiations and are permeable to the bioactive drug thereby allowing sustamed time-release of the active drug; immiscible fluid compartments inside the microcapsules or internal spheroids surrounded by thermosensitive or a shear sensitive interfacial boundary or membrane, containmg chemical components that absorb the activating energy; chemical reactions or convective mixing that convert the prodrug or proenzyme to the bioactive form or change the molecular form of a drug (which is already bioactive) to increase its diffusion rate out of the microcapsule or its bioavailabihty once it has been released; and a longer shelf-life than that of the bioactive drug dissolved or suspended in the earner solution. In the practice of the invention, one may expose the microcapsules to a first form of energy or wavelength m order to cause mixing of immiscible layers or to otherwise activate a prodrug or chemical agent, and subsequently expose the microcapsules to an electromagnetic field designed to heat the microparticles and release the contents of the microcapsules. Included within the present disclosure are multi-layered liquid microcapsules and methods of forming the multi-layered liquid microcapsules compnsmg a drug permeable outer skin or membrane surroundmg a sphere of immiscible fluid compartments. The immiscible compartments may contam a drug precursor in one phase and an activating agent m another phase. The activating agent may be activated by exposure to external electromagnetic radiation or other forms of activating energy causing it to react with the drug precursor to produce an active drug or agent Embodiments of the present invention include methods of exposing the microcapsules to activating radiation or other forms of activating energy. These methods include, but are not limited to the following: (a) Direct exposure of the microcapsules in dry or liquid dispersion just pnor to dispensing. This method may be accomplished, for example, by exposure to radiation from a band pass filter system, laser light, infrared light, radio waves or microwaves, or a combination of same, all of which are transmitted through the outer membrane of the microcapsules to be absorbed by the activating agent which has been co-encapsulated with the precursor drug. (b) Entrapment of the microcapsules tissue followed by external administration of the activating energy through the skm and outer tissues of a subject without physiological damage and absorption of the energy by the activating agent with the microcapsules, or by magnetic particles resulting m heating and melting of the polymer outer membrane. (c) Entrapment of microcapsules m arteπoles, venules, or tissues, followed by exposure of the microcapsules via lntravascular catheters, or other internal devices contammg a fiber optic probe, electromagnetic transducer, or other miniature energy transducer that can transmit the activating energy locally to the entrapped microcapsules, again followed by heating of the magnetic particles to release the activated contents. In the practice of certam embodiments of the inventions, the absorption of the activating energy may result in a chemical reaction between an activator and a prodrug or enzyme precursor that produces a bioactive molecular moiety, or such absorption may dnve fluid mixing and turbulent fluid flows wherein the internal mixing of the immiscible internal phase contammg the prodrug and the internal phase contammg the activator results in production of the bioactive form of the drug Alternatively, absorption of activating energy may occur mside inner spheroids surrounded by a thermosensitive membrane contammg a solution of the activating agent where energy deposition increases the temperature in the spheroid causing the thermosensitive membrane to rupture or dissolve, allowing the activating solution to mix with the next outer solution contammg the prodrug or substrate to produce the active agent. Such mixing may also be caused by ultrasonic radiation, which would be effective to lyse the inner spheroids. The activating energy may also be absorbed by the outer membrane of the microcapsules, to produce an agent such as free radicals, superoxides, oxidizing or reducing agents to activate a prodrug. An embodiment of the present mvention is also microcapsules in which activating energy is absorbed by radiocontrast media contamed in the microcapsules, thus increasing the radio-opacity of the media while the microcapsules are trapped m tissue. Examples of such radiocontrast media include, but are not limited to halogenated oils such as halogenated poppy seed oil, cotton seed oil, soybean oil, safflower oil, corn oil, sesame seed oil, canola oil, and others that can be readily lodmated to produce a radio-opaque contrast medium for radiographic imagmg. For the purposes of this disclosure, the terms "a", "an" and "one" encompass the conventional meaning, and includes the meaning "one or more " Hence, a descnption of a microcapsule, or a pro- drug, for example, would include the meaning one, or one or more, as a particular context requires. Thermoparticle Temperature Regulation At high frequencies, the heating of ferromagnetic metal rods or particles by electromagnetic induction is mainly due to eddy currents that are known to circulate almost exclusively in a thin surface layer. Under such conditions, the power mto the thermoparticles per unit length m an alternating magnetic field, which is applied parallel to the long axis, is. P e = π(μoμp ) 1/2 αH 2 where P e is the power input due to eddy currents, W/m; μo is the permeability of free space, 4 π x 10 ' 7 Wb/A ■ m; μ is the relative permeability of the thermoparticle, dimensionless; p is the electncal resistivity, ohm • m; α is the radius of the thermoparticle, m; H is the amplitude of the smusoidally, varying magnetic field, A m; and / is the frequency, s "1 (Chen et al., 1988). From this equation, the only matenal properties that affect the power input to a heating thermoparticle are μ and p; H and / are charactenstics of the induction heating equipment and its operating conditions. Resistivity does not change appreciably at the Cune temperature, and the vanation of resistivity in the temperature range just below the Cune temperature is small compared to the correspondmg change m permeability More importantly there is a drastic reduction in the relative permeability as the temperature closely approaches the Cune temperature and this results in a correspondmg reduction m the power absorption, current flow, and subsequent heating. FIG. 1A is a schematic drawing of a drug or enzyme contamed in a microcapsule that also contains a metal particle or sphere, such as a ferromagnetic ceramic particle, for example. The microcapsule 120 has an outer polymer membrane 122 that encloses one or more internal liquid phases 124, 128. In the embodiment shown in the figure, two internal liquid phases are shown. In the embodiment shown, a first internal phase 128 contains a drug or enzyme 130 for which the membrane 122 is impermeable. A second internal phase 124 may, in certam embodiments, contam an activating agent. A metal particle 136 contamed m the microcapsule 120, has a Cune temperature higher than the melting pomt of the outer membrane 122. An activating electromagnetic field 132 is shown passing through the outer membrane 122 and causing the metal particle 136 to heat and to melt a hole or pore in the outer membrane 122. In vanous embodiments of the mvention, the internal liquid layer adjacent the outer membrane 122 and that contains the magnetic particle 136 may be an aqueous layer or a hydrocarbon layer depending on the solubility of the active drug. FIG. IB is a schematic drawing of a portion of a microcapsule shown m FIG. 1 A after the metal particle 136 has melted a permanent hole or pore 138 in the outer membrane 122. The pore 138 allows the contents of the microcapsule 120 to leak out, including any drug 130 that is contamed m an internal liquid phase 128 next to the outer membrane 122. FIG. 2 is a graph showing the permeability vs temperature of the ceramic ferromagnetic particles encapsulated in the microcapsules descnbed m Example XI The Cune temperature is shown to be about48°C. A senes of more than 38 separate expenments on four space flights has led to the development of aspects of this invention These expenments along with their ground-based counterparts are descnbed below for the purpose of pointing out the invention specifically and providing details useful m carrying out the invention. These specific examples, however, do not limit the scope of the claimed invention. The following examples are offered by way of illustration and are not intended to limit the scope of the mvention in any manner. All of the matenals used in these examples were obtained from well known commercial sources, or as specifically stated in the examples. Essentially conventional methods were employed in each instance where no specific procedure is stated. Example I MICROGRAVITY EXPERIMENTS SUMMARY The basic formulations and simplified liquid-liquid, dispersion methods were developed m 1988 and 1989. The basic concept is the formation of a multi-lamellar microcapsule with an aqueous drug/oil dispersion at its center, a hydrocarbon/oil drug#2 and/or radiocontrast medium (e.g. IPO) as a next layer, an aqueous layer/drug (e.g., cis-platinum) as a next layer, and a polymenc outer coating or skm. Microencapsulation-related expenments designed to overcome the limitations of the first methods were conducted on six space missions beginning in Apnl 1989 with the Consort-I sounding rocket usmg the Matenals Dispersion Apparatus (MDA) mini-lab developed by Instrumentation Technology Associates, Inc. The sounding rocket flights produced only 6.5 minutes of microgravity conditions, but this was adequate to form the unique microcapsules in a smgle step. Expenments on the Space Shuttle permitted 10 minute dispersion times followed by curing of the outer polyglycende skm for eight days under microgravity conditions. A summary of these expenments is shown m Table 2. New formulations were tested on Shuttle STS-52, usmg only aqueous-soluble drugs, polymers and surfactants, and on STS-56 usmg alcohols as co-surfactants. The specific expenments and results are descnbed in detail m the examples to follow. Table 2. MED Flight Expenments Summary Example π GRAVTTY-DEPENDENT RESTRICTIONS RECOGNIZED Gravity-dependent restπctions in the basic liquid-liquid spontaneous microencapsulation process led to the design of several microgravity expenments to explore the utility of this process when density-dπven phenomena were eliminated. In particular, density-dnven, gravity-dependent restnctions of the liquid-liquid microencapsulation process were: early phase separation producing fragile microcapsules; interfacial dynamic flow causing coalescence of microcapsules. Failure of ground-based expenments to denve uniform microcapsules lead to a desire to attempt microcapsule formation in space. The microgravity flight expenments led to the development of a new liquid-liquid microencapsulation process that involves use of surfactants and co-surfactants m the aqueous phase and co-surfactant alcohols m the organic phase, which also contamed, in one embodiment, high molecular weight polymers that formed a tough outer "skm" on the final microcapsules. In microgravity, a smgle step dispersion produced unique multi-lamellar microcapsules contammg vanous aqueous drugs co- encapsulated with iodinated poppy seed oil (a radiocontrast medium with a sp. gravity =1.35). Subsequent ground control expenments also produced some of these unique microcapsules and illustrated that the 1 - g process could be improved to yield useable microcapsules by usmg different formulations. In particular, it became clear that the outer coatings substantially improved the ruggedness of the microcapsules formed. Example m: SOUNDING ROCKET EXPERIMENTS Initial expenments on Consort- 1 and -3 were used to determine the effective mixing and diffusion kinetics m the MDAs (see below for apparatus descnption). This showed that sufficient volume was mixed at the interface via diffusion to allow formation of microcapsules. These expenments also provided the diffusion constants for each of the components of the liquid phases. The first successful microencapsulation of drugs m microgravity was conducted on the Consort- 4 mission in November 1991. The microcapsules were recovered and analyzed by microscopic image analysis. Mono-dispersed fluorescent beads were included as internal size standards and fluorescent labels were used to determine the distnbution of drug m the vanous fluid compartments. Additional expenments, conducted on Consort-5 m September 1992, confirmed the capabilities of the new method for forming multi-lamellar microcapsules with alternating layers of hydrophilic and hydrophobic drugs. Microcapsules formed in 38 microgravity mim-expenments used liquid-liquid dispersion of aqueous drug solutions, surfactant and polyethylene glycol dispersed in alcoholic co-surfactant solutions contammg soluble polyglyceπdes. Microcapsules of both oil/water and polymer/water/oil were recovered from the Consort flights. These expenments produced multi-lamellar liquid microcapsules (concentπc spheres withm spheres) compnsed of three or more, alternating immiscible layers. Image analysis of the microcapsules was made possible by co-encapsulation of standard size fluorescent beads. Microcapsules were formed m the ranges of 1-15 microns, 40-50 microns, 110-130 microns and 160-230 microns in diameters. This was a substantial improvement over the pnor art approaches which had initially been attempted by the inventors to denve microcapsules only in the 10 micron and less range. The size distnbution covered a range of from about as low as 5 microns m diameter up to about 300 microns in diameter and greater The average size of the microcapsules formed m these expenments was about 150 microns, greatly m excess of the average 10 micron or less diameters obtained with pnor art approaches. The ruggedness of the microcapsules formed under these conditions allowed for size segregation by filtration or other separation methods. Digital image analysis (National Institutes of Health image analysis program) of phase contrast and fluorescent images taken with a fluorescent microscope also confirmed that the aqueous-soluble drugs were routinely encapsulated withm the mner aqueous core and the outermost aqueous shell of the microcapsules. Multi-lamellar microcapsules were, also formed which contained relatively large amounts of IPO (Guerbet Laboratoπes - France, Savage Laboratones - U.S.A.) in discrete lamella, mcludmg microcapsules heavily loaded with IPO, which often compnses up to 38% of the total volume Often small hemispheres of IPO were also found clinging to the outer surface of the large inner (aqueous) sphere or adhered to the outer polymer skm of the microcapsule. Microcapsules formed by almost all of the formulations survived 15-g accelerations, severe vibrations and turbulent mixing, dunng the reentry of the expeπment capsule, and have remamed intact for two years after recovery from space. These multi-layered microcapsules are similar to liquid-filled, thm-skinned, micro-balloons which are flexible enough to be manipulated on a microscope slide without collapse. The microcapsules formed in just 6 5 minutes of microgravity retain their sphencal shape and appear tough enough to survive the extensive physical manipulations required for sizing, final preparation and storage of parenteral suspensions, and the fluid shear encountered after lntravascular injection. The inventors have also discovered that such capsules may form withm a penod of a few seconds. Also formed were very unusual structures (multiple small spheres of aqueous-soluble drug) distπbuted withm multi-lamellar o/w/o microcapsules, wherein the aqueous spheroids are arranged m an annular nng that appears fixed in a plane withm the innermost sphere. These nng structures remain intact when the microcapsules are "rolled around" on the microscope slide without ruptunng These structures demonstrate the ability of the methods of the invention to form small spheroids that do not coalesce inside the larger microcapsule. Such structures may be advantageously used to control the specific volume to surface area ratio m order to control the rate of diffusion of a solute in such spheroids. In particular, sustamed release of pharmaceuticals contained in such spheroids withm microcapsules may find utility, as will applications in which the contents of such spheroids may be released into the microcapsule by ultrasonic irradiation. Example IV SPACE SHUTTLE EXPERIMENTS In expenments conducted on STS-52, the inventors co-encapsulated cis-platmum (diammodichlor-cis-platinum; Bnstol Laboratones) with IPO by forming microcapsules from water- soluble polymers using special formulations of aqueous, non-alcoholic solvents. Such formulations will find particular utility m co-encapsulations of anti-tumor compounds along with radiocontrast medium for tracking drugs m the body. Polyvmyl pyrohdone (PVP), polyvmyl alcohol, and a commercial lecithin (Centrolex-F ® ; a phosophohpid compound denved from soya and produced by U.S. Soya, Inc.) were used to form multilamellar microcapsules at 20°C. Fluorescent beads and fluorescent label were co-encapsulated with the drugs to permit drug-distnbution measurements within the vanous lamellae, usmg fluorescence microscopy and digital image analysis. The final microcapsules were recovered and resuspended in either aqueous solutions, IPO or mineral oil. The microcapsules formed by these formulations were similar to those made usmg alcohol-soluble polyglycendes. However, without the hydrocarbon-soluble polymer membrane these microcapsules were more fragile and friable. Another unique type of microcapsule was formed dunng these expenments that was charactenzed by drug crystals formed withm the inner aqueous core of the multi-lamellar microcapsules. Microcapsules were formed which were packed (approximately 65% of the aqueous compartment) with crystals of Cis-platmum, an anti-tumor drug. Microcapsules contammg crystals of amoxicillin were also formed in the STS-52 expenments. These illustrate that aqueous-soluble drugs can be encapsulated at very high concentrations near the solubility limit of the drug. After the microcapsules are formed the drug can become further concentrated (perhaps via the alcohol absorbing the water from the aqueous phase m which the pharmaceutical solute is dissolved) to form large crystals which are more stable than the dissolved drug dunng prolonged storage. Microcapsules formed from first organic solvent polymer methods appeared to be more rugged (by visual compaπson under the microscope) than those formed on STS-52 formed from first solvent aqueous/polymer methods The STS-56 expenments again produced multi-lamellar liquid microcapsules (multiple concentπc spheres withm spheres) compnsed of alternating immiscible layers Using fluorescent 64 micron beads and image analysis, it was found that the most interesting microcapsules were formed in the range of 10-15 micron, 40-50 micron, 50-100 micron, and 160-230 micron diameters. These diameter distnbutions were of particular interest since it is known that mtraartenal uses can accommodate 50-300 micron diameter microcapsules while mtravenous applications can only tolerate 1-10 micron microcapsules Thus, by segregating the microcapsules mto sized fractions (sieving), it is possible to address particular mtravascular limitations. As noted above, microcapsules were formed contammg crystals of cis-Platinum or amoxicillin. The crystals apparently were formed after encapsulation. Several microcapsules were formed that contained a smgle, large cubic crystal of Cis-Platinum which so completely filled the inner sphere that only about 15% of the inner volume remamed as a liquid. One encapsulated, cubic Cis-Platinum crystal was measured at 48 microns across withm a 57 micron diameter microcapsule After formation, some of the microcapsules were dispersed m an external oil phase (either IPO or mmeral oil) and allowed to cure for eight days before return to Earth. These microgravity expenments have shown that formation of multi-lamellar, alternating-phase microcapsules can be controlled by proper timed-sequence exposures of the immiscible phases usmg special solvent formulations and surfactants. Once formed, these microcapsules remain sphencal due to the predommant surface tension of the internal phases and polymer/solvent phase partitionmg at the interfaces. These expenments clearly demonstrated the capability to use liquid-liquid diffusion mixing to form unique microcapsules contammg hydrophilic and hydrophobic drugs under microgravity conditions. Thus, ground-based expenments were conducted to compliment and replicate the space expenments. These ground-based expenments were able to replicate the size range (5-250 microns in diameter) to a limited degree, but the average size microcapsule obtained was about 10-40 microns m diameter. Still, this was a substantial improvement over the pnor art approaches which rarely formed microcapsules over 10 microns in diameter. It was also observed that the ground-based expenments resulted in less rugged microcapsules. This is likely a result of the gravity-dependent deformations of the sphencal microcapsules as they form giving nse to areas of thinner polymer deposition. Thus, the flexible microcapsules, formed under microgravity conditions, were of more uniform size distnbutions than those formed in 1 - g, were more rugged, and had a higher average diameter than ground-made microcapsules, largely due to the absence of thermal convection, buoyancy forces, and instabilities that occur at the immiscible interfaces. These problems have been largely overcome by new manufacturing apparatus as descnbed m a related application, "Microencapsulation and Electrostatic Processmg Device" invented by Dennis R. Mornson, Benjamin Mosier and John M. Cassanto, incorporated herein by reference. The microgravity expenments illustrate the feasibility of co-encapsulating aqueous-soluble drugs, hydrocarbon-soluble drugs and oil-based contrast media within a hpid-soluble, polyglycende outer film which cures rapidly enough to be impervious to oil or hydrocarbon resolubilization. They also allow the formation and harvesting of unique microcapsules which are durable enough to be removed from the external solvent without disruption or destruction of the internal phases. It is anticipated that these microcapsules will have several advantages over conventional liposomes that are designed for mtravascular injection. Example V FLIGHT HARDWARE DESCRIPTION The microencapsulation expenments descnbed herein were conducted using the Matenals Dispersion Apparatus (MDA, ITA, Inc., Exton, PA). The MDA's consist of an upper and a lower block that contam chambers for each sample fluid. The blocks are misaligned at launch so that the chambers are not m contact with each other Upon activation m microgravity, the blocks are moved to align the chambers so that the fluids can mix by liquid-liquid diffusion. Some of the expenments were conducted with a smgle-step fluid mixmg, and some were done with a two-step fluid mixing technique which allows diffusion of a third fluid or sample into the mixture of the first two fluids while still in the microgravity environment. In these expenments, the shear forces are minimal while moving the fluids mto contact with each other. Example VT DISCUSSION AND ALTERNATIVE EMBODIMENTS Spontaneous formation of multi-lamellar, microcapsules containmg alternating layers of aqueous and hydrophobic solvent compartments is strongly dependent on the interfacial tension and the amount of mixing between immiscible liquid phases. On Earth this process is limited by gravity- dependent, density-dπven separation of the immiscible liquids mto stratified horizontal layers. In microgravity, this process is largely dependent on the surface-free energies of the different liquids, but independent of density-dπven convection or buoyant phase separation. Hydrocarbon soluble, high molecular weight polymers have been included m the formulations to form flexible, permeable "skins" or outer coatings around the liquid microcapsules as they are created by phase partitioning mechanisms. It is also possible to form such polymer barπers between internal layers. The microcapsules can be formed and cured without deformation by contact with container walls. More specifically, co-encapsulation of an aqueous-soluble, anti-tumor drug (Cis-platmum) and a radio-contrast medium (TPO), in microgravity, has produced a unique drug delivery system that can be visualized by radiologic or computenzed tomography scanning to insure that the cytotoxic drug is delivered directly to the target tumor Multi-layered microcapsules have been developed which can provide a new mtravascular delivery system for targeted tissues and sequential, sustamed and controlled release of multiple anti-tumor drugs. This method has resulted in formation of flexible sphencal microcapsules of more uniform sizes, which can provide maximum packing densities and maximum drug delivery to target organs or tumors. Multi-layered microcapsules can be designed to protect active forms of urokmase and other thrombolytic enzymes until they are delivered and entrapped at the local site of a blood clot, where therapeutic doses of the enzyme can diffuse out to dissolve the unwanted embolism. These lmmiscible- liquid diffusion methods also could be used for encapsulating certam labile drugs to make microcapsules for special purpose drug delivery systems, especially those designed to deliver drugs via the nasal or buccal mucosa or via inhalation directly to the lungs. Examples include protected delivery of mucolytic DNAse for sustamed release treatment of cystic fibrosis and I anti-trypsm for patients with deficiencies m the lung epithelium. Example Vπ REDISPERSION OF MICROCAPSULES IN AQUEOUS OR OIL VEHICLES A frequently used second step includes dispersion of the microcapsules (after they have formed) m different aqueous/polymer solvents or in a pure oil phase. A unique attribute of microcapsules formed by these methods is that they do not re-dissolve m an oily external phase, even though the semi- permeable outer skin is hydrophobic This produces a suspension in the liquid earners that are commonly used for mtravascular admmistration Examples of suitable aqueous solutions for redispersion would include, but not be limited to dextran, PEG, phosphate buffered saline (PBS), Ringer's solution, or any solution known in the art that is selected so the membrane has little or no solubility m that medium. The solutions are stenhzed pnor to redispersion and are selected for the particular application, such as injection into a human. It is a further advantage, that redispersion m these solutions inhibits coalescence. Example VTTT: EXEMPLARY FIRST ORGANIC SOLVENT MICROCAPSULE FORMULATIONS The following formulations have been used with particular success by the inventors m both Earth-normal and microgravity methods of making microcapsules Fluid 1 - (hydrocarbon). The first solvent is a hydrocarbon fluid (ethyl alcohol, methyl alcohol, or isopropyi alcohol) with a low or medium HLB (HLB=5-10) One or more co-solvents are used (which also can act as co-surfactants). Small concentrations of oil and water are added. Into this mixture, the mono- or polyglycende is dissolved up to 5% w/v. An example is: 88% ΓPA 2.5% m-Hexanol 2.5% n-Heptanol 5% IPO 2% H 2 0 5% GMS Fluid 2 (aqueous). The second solvent is water plus surfactants (ex. polyethoxylated sorbitan esters; polyethylene glycol). A polysacchande (Dextran) and normal saline (0.9%) are added which helps achieve the desired cntical micelle concentration A pharmaceutical soluble m water is added. An example is. 1% PEG 4000 5% Dextran-40 (MW=40,000) 0.9% Sodium chlonde 2% Sorbitan Monooleate/20 moles Ethylene oxide Water (up to 100% volume) dissolved drug at specified concentration (accordmg to required dose and release rate) Fluid 3 (oil). An oil, immiscible with the first two fluids m which the microcapsule's "outer skm" is insoluble so that the suspended microcapsules can be delivered by injection when non-aqueous admmistration is required. Submersion of microcapsules in the oil also can aid the curing or polymenzation of the "outer skm." A preferred example of the oil vehicle is halogenated poppy seed oil which also serves as a radiocontrast medium Alternate compositions for Fluid 1 Mam solvent - ethyl alcohol Co-solvents - (co-surfactants) are normal alcohols - C4 to C8 high dielectnc constant solvents - tetrahydrofuran dioxane acetonitπle dimethylformamide dimethylacetamide dimethylsulfoxide il dense radiocontrast liquids s.a. halogenated unsaturated oils e.g. halogenated poppy seed oil, cotton seed oil, safflower oil, olive oil, canola oil, peanut oil, sesame oil, corn oil. also saturated oils can be used, s.a. heavy mineral oil, liquid petrolatum Polymers - used to form the "outer skin" on the microcapsules Monoglycerides, polyglycerides, - esp. glycerol esters ranging from C12 - C22, e.g. monostearate, distearates, monooleates, monolaurates and olive oil polyglycerides - cholesterol, waxy plant sterols (stigmasterol, phytosterol, campesterol) phosphohpids - lecithins (phosphatydyl choline) and/or combinations with mono/polyglycerides polyvinylpyrolidone polyacrylates, PEG-hydroxypropyl methacrylate (HPMA) PEG 4,000 - 12,000 polyethylene glycol/acrylate copolymers polyethylene glycol/dextran copolymers Alternate concentrations: Elui l; Main solvent 75-95% Co-solvents 1-10% Oil 1-10% Polymer 1-5% Water 1-20% Alternate composition for Fluid 2 PEG 400-20000 Dextran (MW = 40,000-100,000) 0.9% Sodium chloride Sorbitan Monolaurate/20 moles Ethylene oxide balance is water Drug dissolved at saturated or specified concentration (according to required dose and release rate) Alternate concentrations: PEG 1-5% Dextran (MW=40,000- 100,000) 5-10% Sodium chloride 0.9% Sorbitan Monolaurate/20ETO 1-5% Water (balance of volume) Drug concentration saturated or specified Alternate composition for Fluid 3 (Oils) Dense radiocontrast liquids s.a. iodinated unsaturated oils e.g. poppy seed oil, cotton seed oil, safflower oil, olive oil, canola oil, peanut oil, sesame oil, corn oil. Also saturated oils can be used, s.a. heavy mineral oil and petrolatum. One hundred percent oil or a mixture may be used as a earner vehicle for the suspended microcapsules Example IX: EXEMPLARY FIRST AQUEOUS SOLVENT MICROCAPSULE FORMULAΗONS ALTERNATE METHOD - Hydrophilic Outer Skin Fluid 1 - (aqueous); the mam solvent is a water, one or more co-solvents (which also can act as co- surfactants), and a lecithins are dissolved up to 5% w/v to form the outer skm on the microcapsules. An example is: 3% polyvmyl alcohol dissolved in a mixture of 20% isopropyi alcohol and 80% water Fluid 2 (aqueous); the mam solvent is water plus surfactants (ex. polyethoxylated sorbitan esters; polyethylene glycol) and plus a polysacchande (Dextran) and normal sal e (0.9%) which helps achieve the desired cntical micelle concentration. An example is: 1 % PEG 4000 5% Dextran-70 (MW=~70,000) 0.9% Sodium chlonde 2% Sorbitan Monooleate/20 moles Ethylene oxide Water (up to 100% volume) dissolved drug at saturated or specified concentration (according to required dose and release rate) Fluid 3 (aqueous) - a PEG and PVP solution which can aid the curing or polymenzation of the "outer skm." 1% Polyvmyl pyrolhdone 4% PEG 4000 5% Dextran-70 (MW=~70,000) balance is 0.9% Sodium chlonde Example X: EXTERNALLY TRIGGERED MICROCAPSULES Multilayered microcapsules were formed m microgravity conditions, contammg cis-plat and ferromagnetic particles obtained from Ceramic Magnetics, Inc. (Fairfield, NJ). These ferromagnetic particles (<1 μ) are composed of 66 wt % Fe 2 0 3 , 9 wt % NiO and 25 wt % ZnO. These ceramic (magnetic) particles have a Cune temperature of about 48° C (FIG. 2). The microcapsules ranged from 10 to 100 μ m diameter. Microcapsules of this size are suitable for chemoembohzation of sohd vascular tumors such as those in the spleen, liver, kidney or pancreas, whereby the anti-tumor drug, cis-platin m the case, can be released by exposure to an externally tnggered electromagnetic field. For use m pancreatic or liver cancer, for example, the microcapsules descnbed m this example would be infused mto a designated artery or directly injected mto the tumor dunng a surgical procedure. The patient is subjected to an electromagnetic field of about 85-100 KHz, or a magnetic field strength of about 0.1 Tesla for a penod of about 10 minutes in order to release the drug. In alternate embodiments, one could use an electromagnetic field of from about 20 to about 500 KHz. For embodiments usmg a magnetic field such as descnbed m this example, the microcapsules are designed so that the SAR of the microparticle is much greater than that of the microcapsule membrane and the tissue. Typically the SAR of the microcapsule is 2 to 4 times greater than the SAR of the outer membrane, which is 4-10 times greater than the SAR of the surrounding tissue. Example XI : Alternative Forms of Energy for Externally Tnggenng Microcapsules The microcapsules descnbed herein may also be designed to tngger a drug release by application of radiofrequency (RF). In this case, the microcapsule is designed to have a SAR for the RF of at least 20 times greater than that of the surrounding tissues. In such applications, the microcapsules may contam internal components of high dielectnc paiticulates, such as amorphous carbon, graphite, aluminum powder, acetylene black, a combination of TWEEN, sodium amyl alcohol, and paraffin oil, or other metallic particles dispersed throughout or surrounded by a th n layer of a lower dielectnc medium that is a solid or dense gel, such as polyacrylate, nylon, or polyethyl methacrylate, for example. The use of such matenals as amorphous carbon, graphite, aluminum powder, or other metallic particles as absorbers of both radiofrequency and microwave energy are descnbed m the literature, m particular in Gauthene, 1990, pages 9-16, Chou, et al., 1984, and Guy et al., (incorporated herein in pertinent part by reference). The overall conductivity of the microparticles contained m the microspheres are at least 5 times greater than that of surrounding tissues at the wavelength used. A table of minimum conductivities follows: Table 3. Minimum conductivity of microparticles mside therapeutic capsules. mS is milhSiemens (amps/vol) Because the microparticles are more dense than the liquid contents of the microcapsules, the microparticles sediment to the membrane. When the radiofrequency is applied, the microparticles heat much more rapidly than the membrane, thus melting a hole in the outer membrane. Often two electrodes or two planes of electrodes are used, however, individual voltage control for each set of electrodes is normally required. In those embodiments in which microwave heating is used, the typical microwave range is from about 300 MHz to about 300 GHz Frequencies above 2450 MHz require a shielded room to avoid interference. The same heating principles apply as descnbed for radiofrequency, i.e. the SAR of the microparticle is much greater than the SAR of the outer membrane, which is much greater than the SAR of the surroundmg tissue. Sphencal microparticles may be used, however, the preferred shape of the microparticles is a tmy rod or miniature helical coil to maximize local microwave absorption and punctuate heating. The pnmary energy absorber in the microparticles can be made of carbon fibers, amorphous carbon, graphite particles, aluminum, acetylene black, a combination of TWEEN, sodium amyl alcohol, and paraffin oil, or other metallic particles surrounded by a ceramic, a polymer, or a dense gel that has a thermal conductivity at least 5 times greater than that of the polymer compnsmg the outer membrane of the microcapsule. The preferred mode is to use frequencies up to 250 GHz or greater where the quarter wavelength node is on the order of 10 microns, which is the size of the energy absorbing microparticles In those embodiments in which ultrasound is used to tπgger the microcapsules, microspheroids contammg oils or alcohols and surfactants may be made m the same manner as the pnmary microcapsules except that these spheroids are then coated with a layer of charged polymer that has a conductivity on the order of 5000 mS/meter or greater. Several of these microspheroids are then dispersed inside the drug carrying larger microcapsule, the outer membrane of which has a melting point at least 20°C less than that of the outer wall of the ultrasound absorbmg microspheroid. As the ultrasound is transmitted through the tissues (and the outer membrane of the microcapsules), it is absorbed by the different density phases mside the spheroids. For example, ultrasound is reflected by the more dense, conductive outer wall and thus the microspheroid heats up to a temperature above the melting temperature of the outer membrane and thus melts a hole in the microcapsule outer membrane. Typical components mside the microspheroid are amyl alcohol, sorbitan monooleate, SMO-20, oils, and other mediums that have a density significantly different from that of water (aqueous phases mside the microcapsule) and the surrounding tissues The use of oil/graphite and other oil layers for absorption of ultrasound is descnbed m Gauthene, 1990, pages 92-93, Madsen et al., 1982, and Lele et al., 1982, (all incorporated m pertinent part herein by reference.) Thus the system represents an ultrasound absorbmg microcapsule (microspheroid) made m the same fashion as the larger microcapsules descnbed herein, but the microspheroids are then placed inside a therapeutic microcapsule with an outer membrane that melts at a temperature at least 20°C below that of the microspheroid. It is also understood that the present methods may be used in conjunction with other forms of therapy including, but not limited to hyperthermia therapy The use of the combination of hyperthermia and chemotherapeutic drugs is discussed in Urano et al, Local Hyperthermia in Combination with Chemotherapeutic Agents, in Interstitial Hyperthermia. L. Handl-Zeller (ed.) Springer- Verlag, New York, 1992, incorporated in pertinent part herein by reference. The present mvention has been descnbed in terms of particular embodiments found or proposed to compnse preferred modes for the practice of the invention. It will be appreciated by those of skill in the art that, m light of the present disclosure, numerous modifications and changes can be made m the particular embodiments exemplified without departing from the intended scope of the invention. For example, one alternate embodiment includes use of aqueous-soluble cyclodextπn (m the hydrophilic phase) which has a hydrophobic center that can itself entrap hydrophobic drugs thereby actmg as a earner for hydrophobic drugs withm the aqueous phase. Another alternate embodiment allows after microcapsules are formed, for ancillary polymenc outer coats to be applied by conventional methods (electrostatic coating, aerosohzation and drying, etc ). This is made possible by designing the precise chemical makeup of the initial polymenc outer skin such that it will be compatible with both drug diffusion and the ancillary coating to be applied When surfactants are used to facilitate adhesion of the third solution or ancillary coating the HLB must be selected to be compatible with the HLB of the existing outer coating which has already been formed, such that the solution contammg the ancillary coating will wet the surface of the existing outer coating, to enable deposition of the ancillary coating. This is in contrast to conventional liposomes whose outer membrane composition is a vanable, depending on the phase separation of the phosphohpids and cholesterol adduct when each hposome forms. Another alternative embodiment incorporates an energy absorbing medium ( e.g. photoactivator) which can absorb electromagnetic, ultraviolet, infrared, ultrasonic, radiofrequency and microwave radiation and thereby cause activation of a short-lived drug component just pnor to administration or after the microcapsules have reached the target site. Another embodiment incorporates magnetic particles and magnetic fields or free-fluid electrophoretic mechanisms, etc. to facilitate dispersion or transport of one phase across the immiscible interface mto the other phase. This has been demonstrated as a single pass, unidirectional form of mixing that is best exploited m microgravity Another embodiment includes attachment of certam (hydrophobic) antibodies to the polymenc skm which gives the microcapsules site specificity by bemg able to bmd to target cells (e.g. tumor) while entrapped drugs diffuse out to provide maximum doses to those cells with that antigenic site. Another embodiment makes use of polyethylene glycol (PEG) complexed to peptide or protein drugs and a customized polymenc outer skm which permits the drug-PEG complex to diffuse out of the microcapsule as an intact entity. This permits the drug to resist antibody attachment and remain m the blood stream longer as found in the Pegnology 4 type of drug complexes developed by Enzon, Inc. The improvement bemg delivery of this complex m the tailored microcapsules and controlled release of the complex through the specially designed polymenc outer skm. Another embodiment is microcapsules containmg magnetic particles that can be heated by exposure to an electromagnetic field so that the particles are able to melt the polymer shell and release the contents without causing widespread hyperthermic damage to the surroundmg tissues. Other embodiments include the use of the microcapsules of the mvention for the production of crystals withm an internal aqueous phase. All such modifications are intended to be mcluded withm the scope of the appended claims. While the preferred embodiments of the mvention have been shown and descnbed, modifications thereof can be made by one skilled in the art without departing from the spint and teachings of the inventions. The embodiments descnbed herein are exemplary only, and are not limiting. Many vanations and modifications of the invention and apparatus disclosed herein are possible and are withm the scope of the inventions. Accordingly, the scope of protection is not limited by the descnption set out above, but is only limited by the claims which follow, that scope mcludmg all equivalents of the subject matter of the claims. ******** All patents and publications mentioned m this specification are indicative of the level of skill of those of knowledge in the art to which the invention pertains. All patents and publications referred to in this application are incorporated herein by reference to the same extent as if each was specifically mdicated as bemg incorporated by reference and to the extent that they provide matenals and methods not specifically shown. REFERENCES CITED The following references to the extent that they provide procedural details supplementary to those set forth herein, are specifically incorporated herein by reference. Allen, T. M.. Interactions of Drug Carπers with the Mononuclear Phagocytic System, in G. Gregoπadis (Ed.) Liposomes as Drug Camers. John Wiley & Sons Ltd., New York, pp.37-50, 1988. Allen, T. M., Mehra, T., Hansen, C. and Chin, Y.C., Stealth Liposomes: An Improved Sustamed Release System for 1-b-D-Arabmofuranosylcytosιne, Cancer Res. 52:2431-39, 1992. Bhargava, H. N., Narurkar, A., and Lieb, L. M., Using Microemulsions for Drug Delivery, Pharmaceutical Technology, pp. 46-54, March 1987 Chang, T.M.S., The m vivo effect of semi-permeable microcapsules contammg L-asparaginase on 6C3HED lymphosarcoma, Nature, 229:117-178, 1971. Chelvi, T.P. and Ralhan, R., Int. J. Hyperthermia, 11(5):685-695, 1995. Chen, J.S. et al., Development of Nι-4 wt % Si Thermoseeds for Hyperthermia Cancer Treatment, J. Biomedical Matenals Research 22:303-319, 1988. Chou C.K. et al., Bioelectromagnetics 5:435-441, 1984. Gabizon, A., et al., Liposome-Associated Doxorubicin: Preclinical Pharmacology and Exploratory Clmical Phase, m G. Lopez-Berestein and I.J. Fidler (Eds.) Therapy of Infectious Diseases and Cancer Alan R. Liss, Inc., New York, pp. 189-203, 1992. Gauthene M. (ed.) Methods of External Hyperthermic Heating, Spnnger-Verlag, New York, 1990. Guy, A.W., IEEE Trans. Microwave Theory and Tech. 32:1182-1200. Halbert, G.W. , Stuart, J.B., Florence, A.T., The Incorporation of Lipid Soluble Antineoplastic Agents mto Microemulsions-Prote -free Analogues of Low Density Lipoprotein, Int. J. Pharm. 21: 219-232, 1984. Hand, J.W., Biophysics and Technology of Electromagnetic Hyperthermia, m Gauthereie, M., (Ed.) Methods of External Hyperthermic Heating. Springer- Verlag, New York, pp. 16-24, 1991. Kakmuma, K. et al., Targeting chemotherapy for malignant bram tumors usmg thermosensitive liposomes and localized hyperthermia, J. Neurosurgery 84:180-184, 1996. Kakmuma, K. et al., Drug delivery to the brain usmg thermosensitive liposomes and local hyperthermia, Int. J. Hyperthermia, 12:157-165, 1996. Kimler, B. F, et al., Combmation of Azindmylbenzoqumone and Cis-platmum with Radiation Therapy m the 9L Rat Bram Tumor Model, Int. J. Radiation Oncology Biol. Phys, 26: 445 - 450, 1993. Lele P.P. et al., Bnt. J. Cancer 45 (Suppl V) 108:121, 1982. Magm, R.L., Hunter, J.M., Meisman, M.R., and Bark, G.A., Effect of vesicle size on clearance, distnbution and tumor uptake of temperature sensitive liposomes, Cancer Drug Delivery 3.223-237, 1986. Madsen E.L. et al., Ultrasound Med. Biol. 8.277-287, 1982. McCutcheon's Detergents and Emulsifiers, 1979, North Amencan Edition, McCutcheon Division, MC Publishing Co., 175 Rock Road, Glen Rock, NJ 07452. Mitchell, J.B., Cook, J.A., and Russo, A., Biological Basis for Phototherapy, in Morstyn, G. and Kaye, AH. (Eds.), Phototherapy of Cancer. Harwood Academic Pub., New York, pp.1 -22, 1990. Mornson, D., Mosier, B., and Cassanto, J.M., Immiscible phase microencapsulation of drugs m microgravity, 6 th International Symposium on Expenmental Methods for Microgravity Matenals Sciences, published by Minerals, Metals and Matenals Society, Warrendale, PA, RA. Schiffman & J.B. Andrews, Eds., pp 199-207, 1994 Pankl, 1. and Stern, W Microcrystal ® Drug Delivery System, in Harvey S Pnce (Ed) ϋs Biotechnology Report 1 93/94. Bookbuilders, Ltd., Hong Kong, pp. 219-220, 1994. Talsma, H. and Cromrnelm, D. J. A., Liposomes as Drug Delivery Systems, Part 1- Preparation. Pharmaceutical Technology, pp. 96-106, October 1992. Wπght, K.C., Wallace, S., Mosier, B. and Mosier, D., Microcapsules for Artenal Chemoembolization- Appearance and In Vitro Drug Release Charactenstics, J. Microencapsulation 5: 13-20, 1988.

Claims: CLAIMS What is claimed is: 1. A microcapsule compnsmg one or more internal, immiscible liquid phases enclosed withm a polymer outer membrane havmg a melting temperature, and further compnsmg one or more energy absorbing components m an internal liquid phase m contact with the outer membrane, wherem the energy absorbing component has a higher specific absorption rate for magnetic, radiofrequency, microwave, or ultrasound than the specific absorption rate of the polymer membrane. 2. The microcapsule of claim 1, wherem the energy absorbing component is a magnetic particle and the energy is a magnetic field. 3. The microcapsule of claim 1, wherein the energy absorbmg medium compnses amorphous carbon, graphite, aluminum powder, acetylene black, TWEEN, sodium amyl alcohol, or paraffin oil, and the energy is radiofrequency or microwave. 4 The microcapsule of claim 1, where the energy absorbing medium compnses a spheroid withm the microcapsule, and wherem the spheroid contains amyl alcohol, sorbitan monooleate, SMO- 20, graphite/oil, or an oil, and wherem the energy is ultrasound. 5. The microcapsule of claim 1, wherem the microcapsule compnses at least one internal aqueous phase and at least internal hydrocarbon phase. 6. The microcapsule of claim 1, wherem said outer polymer shell compnses glycerol monosterate, glycerol monooleate, glycerol monolaurate, glycerol dioleate, glycerol distearate, cholesterol, stigmasterol, phytosterol, campesterol, lecithins, polyvmyl pyrrolidone, polyvmyl alcohols, hydrocolloids, polyethylene glycol 400-20000 daltons, dextran 1000-100000 daltons, polyvmylpyrrolidone, polyvmyl alcohols or combinations thereof. 7. The microcapsule of claim 1, wherein one of the internal liquid phases contains a drug or drug precursor. 8. The microcapsule of claim 1 , wherem a first internal liquid phase contains a drug precursor, and a second internal liquid phase immiscible with the first internal liquid phase contains an activator of the drug precursor. 9. The microcapsule of claim 7, wherem said drug or drug precursor is an anti-cancer drug or anti- cancer drug precursor. 10. The microcapsule of claim 9, wherem said anti-cancer drug is cis-platin, doxorubicin, daunorubicin, diaziquone, paclitaxel, azindmylbenzoqumone, muramyltπpeptide, 5-fluorouracil, cyclophosphamide, melphalan, dacarbazine, methotrexate, cytarabme, azaπbme, mercaptopunne, thioguanine, vinblastine, vincπstine, bleomycm, predmsone, ethinyl estradiol, diethylstilbestrol, tamoxifen, testosterone propionate, or fluoxymesterone. 11. The microcapsule of claim 7, wherem said drug or drug precursor is an anesthetic. 12. The microcapsule of claim 11 , wherem said anesthetic is cocaine, procame, or hdocaine. 13. The microcapsule of claim 7, wherein said drug or drug precursor is a systemic antibiotic. 14. The microcapsule of claim 13, wherein said antibiotic is a penicillin, vancomycin, a cephalosporin, erythromycin, ampicillin, amoxicillin, chloramphenicol, rifampicin, gentarnicin, sulfanilamide, sulfadiazine, sulfamethoxazole, sulfisoxazole, sulfacetamide, para-aminobenzoic acid, streptomycin, or isoniazid. 15. The microcapsule of claim 7, wherem said drug or drug precursor is a systemic antifungal. 16. The microcapsule of claim 15, wherein said antifungal is nystatin, or amphotericin B, or griseofulvin. 17. The microcapsule of claim 7, wherein said drug or drug precursor is a systemic antiviral. 18. The microcapsule of claim 17, wherein said antiviral is idoxuridine, iododeoxuridine, riboviran, or amantidine. 19. The microcapsule of claim 7, wherein said drug or drug precursor is an anti-parasitic. 20. The microcapsule of claim 7, wherein said drug or drug precursor is an anti-inflammatory. 21. The microcapsule of claim 7, wherein the drug or drug precursor is a hormone, a steroid, hydrocortisone, dexamethasone, a systemic quinolone, an aminoglycoside, an antidote, an anti- cholinesterase, a metal poisoning antidote, a cytotoxic agent, an immunomodulator, a cytokine, an interleukin, an alpha-antitrypsin, a bone metabolism regulator, a hypercalcemic agent, a cardiovascular agent, a beta blocker, a cerebral vasodilator, a cerebral metabolic enhancer, a colony stimulating factor, a granulocyte-colony stimulating factor, a granulocyte macrophage-colony stimulating factor, a vasopressor, a local diabetic agent, a CT scan enhancer, an angiocardiography agent, an adenosine deaminase deficiency agent, a gonadotropin inhibitor, an adrenal cortical steroid inhibitor, a gonadotropin releasing hormone stimulant, a urofollitropin, a muscle relaxant, a neuromuscular blocking agent, a prostaglandin analog, a prostaglandin, a prostaglandin inhibitor, a respiratory therapy agent, an anticholinergic, a beta andrenergic stimulator, metoclopramide, tetrahydrocannabinol or a sympathomimetic. 22. The microcapsule of claim 7, wherein said drug or drug precursor is a thrombolytic agent. 23. The microcapsule of claim 22, wherein said thrombolytic agent is urokinase (uPA), tissue plasrninogen activator (tPA) or streptokmase. 24. The microcapsule of claim 2, wherein the magnetic particles comprise oxides of iron, nickel and zinc. 25. The microcapsule of claim 2, wherein the magnetic particles comprise about 66 wt % Fe 2 0 3 , about 9 wt % NiO, and about 25 wt % ZnO. 26. The microcapsule of claim 2, wherein the magnetic particles comprise Fe 3 0 4 , oxides of copper, gold, silver or combinations thereof. 27. The microcapsule of claim 2, wherein the magnetic particles comprise a ceramic coating. 28. The microcapsule of claim 2, wherein the magnetic particles comprise a methacrylate, alginate, dextran, polyacrylate, or polyvmyl pyrrolidone coating. 29. The microcapsule of claim 2, wherein the magnetic particles have a Curie temperature of from about 41°C to about 95°C. 30. The microcapsule of claim 1, wherein the microcapsule has a diameter of from about 1 to about 500 microns. 31. The microcapsule of claim 1, wherein the microcapsule has a diameter of from about 300 to about 500 microns. 32. The microcapsule of claim 1, wherein the microcapsule has a diameter of from about 50 to about 300 microns. 33. The microcapsule of claim 1, wherein the microcapsule has a diameter of from about 30 to about 50 microns. 34. The microcapsule of claim 1, wherein the microcapsule has a diameter of from about 20 to about 30 microns. 35. The microcapsule of claim 1 , wherein the microcapsule has a diameter of from about 1 to about 20 microns. 36. The microcapsule of claim 1, wherein the microcapsule is further defined as containing a radiocontrast media. 37. The microcapsule of claim 34, wherein the radiocontrast media is a halogenated oil. 38. The microcapsule of claim 37 wherein the radiocontrast media is halogenated poppy seed oil, cotton seed oil, soybean oil, safflower oil, com oil, sunflower seed oil, sesame seed oil, or canola oil. 39. The microcapsule of claim 37, wherein the radiocontrast media is iodinated poppy seed oil. 40. The microcapsule of claim 1 , contained in a pharmaceutically acceptable solution. 41. A composition comprising microcapsules, and wherein said microcapsules comprise two or more internal, immiscible liquid phases enclosed within a polymer outer membrane having a melting temperature, and further comprising one or more magnetic particles in an internal liquid phase in contact with the outer membrane, wherein the magnetic particles have a Curie point higher than the melting temperature of the polymer membrane; and further wherein a first portion of said microcapsules contain magnetic particles with a first Curie point, and a second portion of said microcapsules contam magnetic particles with a second Curie point, and further wherein the first Curie point is different than said second Curie point. 42. The composition of claim 41 , wherein the microcapsules contain a drug. 43. The composition of claim 42, wherem said first portion contains a different drag than said second portion. 44. A method of controlling the release of a drug comprising: providing a dmg delivery solution comprising microcapsules comprising one or more internal, immiscible liquid phases enclosed within a polymer outer membrane having a melting temperature, and further comprising one or more energy absorbing components in an internal liquid phase in contact with the outer membrane, wherein the energy absorbing component has a higher specific absorption rate for magnetic, radiofrequency, microwave, or ultrasound than the specific absoφtion rate of the polymer membrane, and a drug contained in at least one of the internal liquid phases; administering the drug delivery solution to a subject and exposing the microcapsule to an energy source, effective to heat the internal component and to melt at least a portion of the polymer outer membrane and to release the drug. 45. The method of claim 44, wherein the energy absorbing component is a magnetic particle and the energy is a magnetic field. 46. The method of claim 44, wherein the energy absorbing medium comprises amoφhous carbon, graphite, aluminum powder, acetylene black, TWEEN, sodium amyl alcohol, or paraffin oil, and the energy is radiofrequency or microwave. 47. The method of claim 44, wherein the energy absorbing medium comprises a spheroid within the microcapsule, and wherein the spheroid contains amyl alcohol, sorbitan monooleate, SMO-20, graphite/oil, or an oil, and wherein the energy is ultrasound. 48. The method of claim 45, wherein the magnetic particles comprise a mixture of oxides of iron, nickel and zinc, and further comprise a ceramic coating. 49. The method of claim 45, wherein the electromagnetic field is an electromagnetic field with a frequency of from about 20 to about 500 KHz. 50. The method of claim 45, wherein the electromagnetic field is an electromagnetic field with a frequency of from about 85 to about 100 KHz. 51. The method of claim 44, wherein the microcapsules contain a drug precursor in a first internal liquid phase and an activator of the drug precursor in a second internal liquid phase immiscible with the first internal liquid phase and the method further comprises exposing the microcapsules to an energy source effective to mix the immiscible internal liquid phases and increase the kinetics of activation of the drug precursor prior to heating the magnetic particles. 52. The method of claim 51 , wherein the energy source is UV light of 220-390 nanometers. 53. The method of claim 44, wherein the microcapsules also contam a radiocontrast medium. 54. The method of claim 53, wherein the radiocontrast media is halogenated poppy seed oil, cotton seed oil, soybean oil, safflower oil, com oil, sunflower oil, sesame seed oil, or canola oil. 55. The method of claim 54, wherein the microcapsules are administered to a subject and detected at a target site by radiography, prior to heating the internal component. 56. The method of claim 44, wherein the microcapsules are administered to a subject intraarterially, intravenously, intraperitoneally, directly into a tissue, or directly into a tumor. 57. The method of claim 56, wherem the subject is a human. 58. The method of claim 44, wherein the drug delivery solution contains two portions of microcapsules wherein a first portion of the microcapsules have a different specific absorption rate for the energy source than a second portion. 59. The method of claim 58, wherein the first portion and the second portion contain different drugs. 60. A method of treating a tumor in a subject comprising: obtaining a pharmaceutical composition comprising a plurality of microcapsules in a pharmaceutically acceptable solution, each microcapsule comprising: one or more immiscible internal liquid phases enclosed in a polymer shell having a meltmg temperature; a magnetic particle contained in an internal liquid phase in contact with the polymer shell and having a Curie point higher than the melting temperature of the polymer shell and; an anti-cancer d g contained in an internal liquid phase; administering the pharmaceutical composition to the subject in a manner effective to place the microcapsules within or adjacent the tumor; and applying a magnetic field to the microcapsules effective to heat the magnetic particles to a temperature higher than the melting temperature of the polymer shell, thereby melting at least a portion of the polymer shell and releasing the drug. 61. The method of claim 60, wherein the pharmaceutical composition is infused into an artery upstream of the tumor. 62. The method of claim 60, wherein the microcapsules also contain a radiocontrast agent and the microcapsules are visualized prior to application of the magnetic field. 63. The method of claim 62 wherein the radiocontrast agent is a halogenated oil. 64. The method of claim 60, wherein said method is practiced in conjunction with hyperthermia therapy. 65. The method of claim 60, wherein said anti-cancer dmg is cis-platin, doxorubicin, daunorubicin, diaziquone, paclitaxel, aziridinylbenzoquinone, muramyltripeptide, 5-fluorouracil, cyclophosphamide, melphalan, dacarbazine, methotrexate, cytarabine, azaribine, mercaptopurine, thioguanine, vinblastine, vincristine, bleomycin, prednisone, ethinyl estradiol, diethylstilbestrol, tamoxifen, testosterone propionate, or fluoxymesterone. 66. The method of claim 60, wherein said anti-cancer drug is a photodynamic therapy agent. 67. The method of claim 66, wherein said agent is photofrin or dibenzopoφhyrin. 68. A composition comprising a microcapsule comprising two or more immiscible liquid phases enclosed in a polymer shell having a melting temperature, a dmg, and one or more magnetic particles having a Curie point higher than the melting temperature of the polymer shell, wherein the microcapsule is made by the method comprising: formulating a first phase comprising a first solvent, a first polymer soluble in the first phase and immiscible in a second phase, a co-solvent, oil, and water, formulating the second phase immiscible with the first phase, the second phase comprising a second solvent, a second polymer soluble in the second phase and immiscible in the first phase, a surface active agent, and a salt; the surface active agent having a hydrophilic/lipophilic balance value greater than that of the first polymer; the second polymer having a hydrophilic/lipophilic balance value lower than that of the surface active agent; creating an interface between the first and second phases in a manner that limits fluid shear to between about 1 to 100 dynes cm 2 , if carried out under conditions of greater than or about equal to 1 gravity, or between about 2 to 30 dynes/cm 2 , if carried out under conditions of less than or about equal to 1 x 10 "2 gravity, and maintains adsoφtive surface characteristics at the interface. 69. A composition comprising microcapsules, wherein said microcapsules comprise one or more internal liquid phases enclosed within a polymer outer membrane having a meltmg temperature, and further comprising one or more magnetic particles in an internal liquid phase in contact with the outer membrane; and further wherein a first portion of said microcapsules has a polymer outer membrane with a different melting point than a second portion of said microcapsules, and further wherein both the first and second melting points are lower than the Curie point of the magnetic particles. 70. The composition of claim 69, wherein said microcapsules contam a dmg in a least one of said internal liquid phases. 71. The composition of claim 70, wherein said first portion of microcapsules contains a different drug than said second portion of microcapsules.

Inventors: MORRISON DENNIS R, MOSIER BENJAMIN, MORRISON, DENNIS, R., MOSIER, BENJAMIN
Applicants: NASA, NASA/JOHNSON SPACE CENTER
Application year: 1999
Main classification: A61K9
IPC codes: A61K9, A61K41