Title:  Aerodynamically light particles for pulmonary drug delivery

United States Patent:  6,635,283

Issued:  October 21, 2003

Inventors:  Edwards; David A. (171 Commonwealth Ave., Unit 3, Boston, MA 02116); Caponetti; Giovanni (807 Somerville Ave., Somerville, MA 02143); Hrkach; Jeffrey S. (24 Cambridge Ter., Unit 2, Cambridge, MA 02140); Lotan; Noah (27 Shimkin Street, 34750 Haifa, IL); Hanes; Justin (5416 Purlington Way, Baltimore, MD 21212); Ben-Jebria; Abdellaziz (804 Stratford Dr., Apartment No. 34, State College, PA 16801); Langer; Robert S. (77 Lombard St., Newton, MA 02158)

Appl. No.:  027212

Filed:  December 20, 2001

Abstract

Improved aerodynamically light particles for drug delivery to the pulmonary system, and methods for their synthesis and administration are provided. In a preferred embodiment, the aerodynamically light particles are made of biodegradable material and have a tap density of less than 0.4 g/cm³ and a mass mean diameter between 5 .mu.m and 30 .mu.m. The particles may be formed of biodegradable materials such as biodegradable polymers. For example, the particles may be formed of a functionalized polyester graft copolymer consisting of a linear .alpha.-hydroxy-acid polyester backbone having at least one amino acid group incorporated therein and at least one poly(amino acid) side chain extending from an amino acid group in the polyester backbone. In one embodiment, aerodynamically light particles having a large mean diameter, for example greater than 5 .mu.m, can be used for enhanced delivery of a therapeutic agent to the alveolar region of the lung. The aerodynamically light particles incorporating a therapeutic agent may be effectively aerosolized for administration to the respiratory tract to permit systemic or local delivery of wide variety of therapeutic agents.

SUMMARY OF THE INVENTION

Improved aerodynamically light particles for drug delivery to the pulmonary system, and methods for their synthesis and administration are provided. In a preferred embodiment, the particles are made of a biodegradable material, have a tap density less than 0.4 g/cm³ and a mean diameter between 5 .mu.m and 30 .mu.m. In one embodiment, for example, at least 90% of the particles have a mean diameter between 5 .mu.m and 30 .mu.m. The particles may be formed of biodegradable materials such as biodegradable polymers, proteins, or other water-soluble materials. For example, the particles may be formed of a functionalized polyester graft copolymer consisting of a linear .alpha.-hydroxy-acid polyester backbone having at least one amino acid residue incorporated per molecule therein and at least one poly(amino acid) side chain extending from an amino acid group in the polyester backbone. Other examples include particles formed of water-soluble excipients, such as trehalose or lactose, or proteins, such as lysozyme or insulin. The aerodynamically light particles can be used for enhanced delivery of a therapeutic agent to the airways or the alveolar region of the lung. The particles incorporating a therapeutic agent may be effectively aerosolized for administration to the respiratory tract to permit systemic or local delivery of a wide variety of therapeutic agents. They optionally may be co-delivered with larger carrier particles, not carrying a therapeutic agent, which have for example a mean diameter ranging between about 50 .mu.m and 100 .mu.m.

DETAILED DESCRIPTION OF THE INVENTION

Aerodynamically light, biodegradable particles for improved delivery of therapeutic agents to the respiratory tract are provided. The particles can be used in one embodiment for controlled systemic or local drug delivery to the respiratory tract via aerosolization. In a preferred embodiment, the particles have a tap density less than about 0.4 g/cm³. Features of the particle which can contribute to low tap density include irregular surface texture and porous structure. Administration of the low density particles to the lung by aerosolization permits deep lung delivery of relatively large diameter therapeutic aerosols, for example, greater than 5 .mu.m in mean diameter. A rough surface texture also can reduce particle agglomeration and provide a highly flowable powder, which is ideal for aerosolization via dry powder inhaler devices, leading to lower deposition in the mouth, throat and inhaler device.

Density and Size of Aerodynamically Light Particles

Particle Size

The mass mean diameter of the particles can be measured using a Coulter Counter. The aerodynamically light particles are preferably at least about 5 microns in diameter. The diameter of particles in a sample will range depending upon depending on factors such as particle composition and methods of synthesis. The distribution of size of particles in a sample can be selected to permit optimal deposition within targeted sites within the respiratory tract.

The aerodynamically light particles may be fabricated or separated, for example by filtration, to provide a particle sample with a preselected size distribution. For example, greater than 30%, 50%, 70%, or 80% of the particles in a sample can have a diameter within a selected range of at least 5 .mu.m. The selected range within which a certain percentage of the particles must fall may be for example, between about 5 and 30 .mu.m, or optionally between 5 and 15 .mu.m. In one preferred embodiment, at least a portion of the particles have a diameter between about 9 and 11 .mu.m. Optionally, the particle sample also can be fabricated wherein at least 90%, or optionally 95% or 99%, have a diameter within the selected range. The presence of the higher proportion of the aerodynamically light, larger diameter (at least about 5 .mu.m) particles in the particle sample enhances the delivery of therapeutic or diagnostic agents incorporated therein to the deep lung.

In one embodiment, in the particle sample, the interquartile range may be 2 .mu.m, with a mean diameter for example of 7.5, 8.0, 8.5, 9.0, 9.5, 10.0, 10.5, 11.0, 11.5, 12.0, 12.5, 13.0 or 13.5 .mu.m. Thus, for example, at least 30%, 40%, 50% or 60% of the particles may have diameters within the selected range 5.5-7.5 .mu.m, 6.0-8.0 .mu.m, 6.5-8.5 .mu.m, 7.0-9.0 .mu.m, 7.5-9.5 .mu.m, 8.0-10.0 .mu.m, 8.5-10.5 .mu.m, 9.0-11.0 .mu.m, 9.5-11.5 .mu.m, 10.0-12.0 .mu.m, 10.5-12.5 .mu.m, 11.0-13.0 .mu.m, 11.5-13.5 .mu.m, 12.0-14.0 .mu.m, 12.5-14.5 .mu.m or 13.0-15.0 .mu.m. Preferably the said percentages of particles have diameters within a 1 .mu.m range, for example, 6.0-7.0 .mu.m, 10.0-11.0 .mu.m or 13.0-14.0 .mu.m.

The aerodynamically light particles incorporating a therapeutic drug, and having a tap density less than about 0.4 g/cm³, with mean diameters of at least about 5 .mu.m, are more capable of escaping inertial and gravitational deposition in the oropharyngeal region, and are targeted to the airways or the deep lung. The use of larger particles (mean diameter at least about 5 .mu.m) is advantageous since they are able to aerosolize more efficiently than smaller, non-light aerosol particles such as those currently used for inhalation therapies.

In comparison to smaller non-light particles, the larger (at least about 5 .mu.m) aerodynamically light particles also can potentially more successfully avoid phagocytic engulfinent by alveolar macrophages and clearance from the lungs, due to size exclusion of the particles from the phagocytes' cytosolic space. Phagocytosis of particles by alveolar macrophages diminishes precipitously as particle diameter increases beyond 3 .mu.m. Kawaguchi, H. et al., Biomaterials 7: 61-66 (1986); Krenis, L. J. and Strauss, B., Proc. Soc. Exp. Med., 107:748-750 (1961); and Rudt, S. and Muller, R. H., J. Contr. Rel., 22: 263-272 (1992). For particles of statistically isotropic shape (on average, particles of the powder possess no distinguishable orientation), such as spheres with rough surfaces, the particle envelope volume is approximately equivalent to the volume of cytosolic space required within a macrophage for complete particle phagocytosis.

Aerodynamically light particles thus are capable of a longer term release of a therapeutic agent. Following inhalation, aerodynamically light biodegradable particles can deposit in the lungs (due to their relatively low tap density), and subsequently undergo slow degradation and drug release, without the majority of the particles being phagocytosed by alveolar macrophages. The drug can be delivered relatively slowly into the alveolar fluid, and at a controlled rate into the blood stream, minimizing possible toxic responses of exposed cells to an excessively high concentration of the drug. The aerodynamically light particles thus are highly suitable for inhalation therapies, particularly in controlled release applications. The preferred mean diameter for aerodynamically light particles for inhalation therapy is at least about 5 .mu.m, for example between about 5 and 30 .mu.m.

The particles may be fabricated with the appropriate material, surface roughness, diameter and tap density for localized delivery to selected regions of the respiratory tract such as the deep lung or upper airways. For example, higher density or larger particles may be used for upper airway delivery, or a mixture of different sized particles in a sample, provided with the same or different therapeutic agent may be administered to target different regions of the lung in one administration.

Particle Density and Deposition

The particles having a diameter of at least about 5 .mu.m and incorporating a therapeutic or diagnostic agent preferably are aerodynamically light. As used herein, the phrase "aerodynamically light particles" refers to particles having a tap density less than about 0.4 g/cm³. The tap density of particles of a dry powder may be obtained using a GeoPyc.TM. (Micrometrics Instrument Corp., Norcross, Ga. 30093). Tap density is a standard measure of the envelope mass density. The envelope mass density of an isotropic particle is defined as the mass of the particle divided by the minimum sphere envelope volume within which it can be enclosed.

Inertial impaction and gravitational settling of aerosols are predominant deposition mechanisms in the airways and acini of the lungs during normal breathing conditions. Edwards, D. A., J. Aerosol Sci. 26:293-317 (1995). The importance of both deposition mechanisms increases in proportion to the mass of aerosols and not to particle (or envelope) volume. Since the site of aerosol deposition in the lungs is determined by the mass of the aerosol (at least for particles of mean aerodynamic diameter greater than approximately 1 .mu.m), diminishing the tap density by increasing particle surface irregularities and particle porosity permits the delivery of larger particle envelope volumes into the lungs, all other physical parameters being equal.

The low tap density particles have a small aerodynamic diameter in comparison to the actual envelope sphere diameter. The aerodynamic diameter, d_aer, is related to the envelope sphere diameter, d (Gonda, I., "Physico-chemical principles in aerosol delivery," in Topics in Pharmaceutical Sciences 1991 (eds. D. J. A. Crommelin and K. K. Midha), pp. 95-117, Stuttgart: Medpham Scientific Publishers, 1992) by the formula:

d_aer =d/.rho.

where the envelope mass .rho. is in units of g/cm³. Maximal deposition of monodisperse aerosol particles in the alveolar region of the human lung (.about.60%) occurs for an aerodynamic diameter of approximately d_aer =3 .mu.m, Heyder, J. et al, J. Aerosol Sci., 17: 811-825 (1986). Due to their small envelope mass density, the actual diameter d of aerodynamically light particles comprising a monodisperse inhaled powder that will exhibit maximum deep-lung deposition is:

d=3/.rho. .mu.m (where .rho.<1 g/cm³);

where d is always greater than 3 .mu.m. For example, aerodynamically light particles that display an envelope mass density, .rho.=0.1 g/cm³, will exhibit a maximum deposition for particles having envelope diameters as large as 9.5 .mu.m. The increased particle size diminishes interparticle adhesion forces. Visser, J., Powder Technology, 58:1-10. Thus, large particle size increases efficiency of aerosolization to the deep lung for particles of low envelope mass density, in addition to contributing to lower phagocytic losses.

Particle Materials

In order to serve as efficient and safe drug carriers in drug delivery systems, the aerodynamically light particles preferably are biodegradable and biocompatible, and optionally are capable of biodegrading at a controlled rate for delivery of a drug. The particles can be made of any material which is capable of forming a particle having a tap density less than about 0.4 g/cm³. Both inorganic and organic materials can be used. For example, ceramics may be used. Other non-polymeric materials (e.g. fatty acids) may be used which are capable of forming aerodynamically light particles as defined herein. Different properties of the particle can contribute to the aerodynamic lightness including the composition forming the particle, and the presence of irregular surface structure or pores or cavities within the particle.

Polymeric Particles

The particles may be formed from any biocompatible, and preferably biodegradable polymer, copolymer, or blend, which is capable of forming particles having a tap density less than about 0.4 g/cm³.

Surface eroding polymers such as polyanhydrides may be used to form the aerodynamically light particles. For example, polyanhydrides such as poly[(p-carboxyphenoxy)-hexane anhydride] (PCPH) may be used. Biodegradable polyanhydrides are described, for example, in U.S. Pat. No. 4,857,311, the disclosure of which is incorporated herein by reference.

In another embodiment, bulk eroding polymers such as those based on polyesters including poly(hydroxy acids) can be used. For example, polyglycolic acid (PGA) or polylactic acid (PLA) or copolymers thereof may be used to form the aerodynamically light particles, wherein the polyester has incorporated therein a charged or functionalizable group such as an amino acid as described below.

Other polymers include polyamides, polycarbonates, polyalkylenes such as polyethylene, polypropylene, poly(ethylene glycol), poly(ethylene oxide), poly(ethylene terephthalate), poly vinyl compounds such as polyvinyl alcohols, polyvinyl ethers, and polyvinyl esters, polymers of acrylic and methacrylic acids, celluloses and other polysaccharides, and peptides or proteins, or copolymers or blends thereof which are capable of forming aerodynamically light particles with a tap density less than about 0.4 g/cm³. Polymers may be selected with or modified to have the appropriate stability and degradation rates in vivo for different controlled drug delivery applications.

Polyester Graft Copolymers

In one preferred embodiment, the aerodynamically light particles are formed from functionalized polyester graft copolymers, as described in Hrkach et al., Macromolecules, 28:4736-4739 (1995); and Hrkach et al., "Poly(L-Lactic acid-co-amino acid) Graft Copolymers: A Class of Functional Biodegradable Biomaterials" in Hydrogels and Biodegradable Polymers for Bioapplications, ACS Symposium Series No. 627, Raphael M. Ottenbrite et al., Eds., American Chemical Society, Chapter 8, pp. 93-101, 1996, the disclosures of which are incorporated herein by reference. The functionalized graft copolymers are copolymers of polyesters, such as poly(glycolic acid) or poly(lactic acid), and another polymer including functionalizable or ionizable groups, such as a poly(amino acid). In a preferred embodiment, comb-like graft copolymers are used which include a linear polyester backbone having amino acids incorporated therein, and poly(amino acid) side chains which extend from the amino acid residues in the polyester backbone. The polyesters may be polymers of .alpha.-hydroxy acids such as lactic acid, glycolic acid, hydroxybutyric acid and hydroxy valeric acid, or derivatives or combinations thereof. The inclusion of ionizable side chains, such as polylysine, in the polymer has been found to enable the formation of more aerodynamically light particles, using techniques for making microparticles known in the art, such as solvent evaporation. Other ionizable groups, such as amino or carboxyl groups, may be incorporated, covalently or noncovalently, into the polymer to enhance surface roughness and porosity. For example, polyalanine could be incorporated into the polymer.

An exemplary polyester graft copolymer, which may be used to form aerodynamically light polymeric particles is the graft copolymer, poly(lactic acid-co-lysine-graft-lysine) (PLAL-Lys), which has a polyester backbone consisting of poly(L-lactic acid-co-L-lysine) (PLAL), and grafted poly-lysine chains. PLAL-Lys is a comb-like graft copolymer having a backbone composition, for example, of 98 mol % lactic acid and 2 mol % lysine and poly(lysine) side chains extending from the lysine sites of the backbone.

PLAL-Lys may be synthesized as follows. First, the PLAL copolymer consisting of L-lactic acid units and approximately 1-2% N .epsilon. carbobenzoxy-L-lysine (Z-L-lysine) units is synthesized as described in Barrera et al., J. Am. Chem. Soc., 115:11010 (1993). Removal of the Z protecting groups of the randomly incorporated lysine groups in the polymer chain of PLAL yields the free .epsilon.-amine which can undergo further chemical modification. The use of the poly(lactic acid) copolymer is advantageous since it biodegrades into lactic acid and lysine, which can be processed by the body. The existing backbone lysine groups are used as initiating sites for the growth of poly(amino acid) side chains.

The lysine .epsilon.-amino groups of linear poly(L-lactic acid-co-L-lysine) copolymers initiate the ring opening polymerization of an amino acid N-.epsilon. carboxyanhydride (NCA) to produce poly(L-lactic acid-co-amino acid) comblike graft copolymers. In a preferred embodiment, NCAs are synthesized by reacting the appropriate amino acid with triphosgene. Daly et al., Tetrahedron Lett., 29:5859 (1988). The advantage of using triphosgene over phosgene gas is that it is a solid material, and therefore, safer and easier to handle. It also is soluble in THF and hexane so any excess is efficiently separated from the NCAs.

The ring opening polymerization of amino acid N-carboxyanhydrides (NCAs) is initiated by nucleophilic initiators such as amines, alcohols, and water. The primary amine initiated ring opening polymerization of NCAs allows good control over the degree of polymerization when the monomer to initiator ratio (M/I) is less than 150. Kricheldorf, H. R. in Models of Biopolymers by Ring-Opening Polymerization, Penczek, S., Ed., CRC Press, Boca Raton, 1990, Chapter 1; Kricheldorf, H. R. .alpha.-Aminoacid-N-Carboxy Anhydrides and Related Heterocycles, Springer-Verlag, Berlin, 1987; and Imanishi, Y. in Ring-Opening Polymerization, Ivin, K. J. and Saegusa, T., Eds., Elsevier, London, 1984, Volume 2, Chapter 8. Methods for using lysine .epsilon.-amino groups as polymeric initiators for NCA polymerizations are described in the art. Sela, M. et al., J. Am. Chem. Soc., 78: 746 (1956).

In the reaction of an amino acid NCA with PLAL, the nucleophilic primary .epsilon.-amino of the lysine side chain attacks C-5 of the NCA leading to ring opening and formation of the amino acid amide, along with the evolution of CO₂. Propagation takes place via further attack of the amino group of the amino acid amides on subsequent NCA molecules. The degree of polymerization of the poly(amino acid) side chains, the corresponding amino acid content in the graft copolymers and their resulting physical and chemical characteristics can be controlled by changing the M/I ratio for the NCA polymerization--that is, changing the ratio of NCA to lysine .epsilon.-amino groups of pLAL. Thus, in the synthesis, the length of the poly(amino acid), such as poly(lysine), side chains and the total amino acid content in the polymer may be designed and synthesized for a particular application.

The poly(amino acid) side chains grafted onto or incorporated into the polyester backbone can include any amino acid, such as aspartic acid, alanine or lysine, or mixtures thereof. The functional groups present in the amino acid side chains, which can be chemically modified, include amino, carboxylic acid, thiol, guanido, imidazole and hydroxyl groups. As used herein, the term "amino acid" includes natural and synthetic amino acids and derivatives thereof. The polymers can be prepared with a range of amino acid side chain lengths, for example, about 10-100 or more amino acids, and with an overall amino acid content of, for example, 7-72% or more depending on the reaction conditions. The grafting of poly(amino acids) from the pLAL backbone may be conducted in a solvent such as dioxane, DMF, or CH₂ Cl₂ or mixtures thereof. In a preferred embodiment, the reaction is conducted at room temperature for about 2-4 days in dioxane.

Alternatively, the aerodynamically light particles for pulmonary drug delivery may be formed from polymers or blends of polymers with different polyester/amino acid backbones and grafted amino acid side chains, For example, poly(lactic acid-co-lysine-graft-alanine-lysine) (PLAL-Ala-Lys), or a blend of PLAL-Lys with poly(lactic acid-co-glycolic acid-block-ethylene oxide) (PLGA-PEG) (PLAL-Lys-PLGA-PEG) may be used.

In the synthesis, the graft copolymers may be tailored to optimize different characteristics of the aerodynamically light particle including: i) interactions between the agent to be delivered and the copolymer to provide stabilization of the agent and retention of activity upon delivery; ii) rate of polymer degradation and, thereby, rate of drug release profiles; iii) surface characteristics and targeting capabilities via chemical modification; and iv) particle porosity.

Formation of Aerodynamically Light Polymeric Particles

Aerodynamically light polymeric particles may be prepared using single and double emulsion solvent evaporation, spray drying, solvent extraction and other methods well known to those of ordinary skill in the art. The aerodynamically light particles may be made, for example using methods for making microspheres or microcapsules known in the art.

Methods developed for making microspheres for drug delivery are described in the literature, for example, as described by Mathiowitz and Langer, J. Controlled Release 5,13-22 (1987); Mathiowitz, et al., Reactive Polymers 6, 275-283 (1987); and Mathiowitz, et al, J. Appl. Polymer Sci. 35, 755-774 (1988), the teachings of which are incorporated herein. The selection of the method depends on the polymer selection, the size, external morphology, and crystallinity that is desired, as described, for example, by Mathiowitz, et al., Scanning Microscopy 4, 329-340 (1990); Mathiowitz, et, al., J. Appl. Polymer Sci. 45, 125-134 (1992); and Benita, et al., J. Pharm. Sci. 73, 1721-1724 (1984), the teachings of which are incorporated herein.

In solvent evaporation, described for example, in Mathiowitz, et al., (1990), Benita, and U.S. Pat. No. 4,272,398 to Jaffe, the polymer is dissolved in a volatile organic solvent, such as methylene chloride. Several different polymer concentrations can be used, for example, between 0.05 and 0.20 g/ml. The drug, either in soluble form or dispersed as fine particles, is added to the polymer solution, and the mixture is suspended in an aqueous phase that contains a surface active agent such as poly(vinyl alcohol). The aqueous phase may be, for example, a concentration of 1% poly(vinyl alcohol) w/v in distilled water. The resulting emulsion is stirred until most of the organic solvent evaporates, leaving solid microspheres, which may be washed with water and dried overnight in a lyophilizer.

Microspheres with different sizes (1-1000 microns) and morphologies can be obtained by this method which is useful for relatively stable polymers such as polyesters and polystyrene. However, labile polymers such as polyanhydrides may degrade due to exposure to water. For these polymers, solvent removal may be preferred.

Solvent removal was primarily designed for use with polyanhydrides. In this method, the drug is dispersed or dissolved in a solution of a selected polymer in a volatile organic solvent like methylene chloride. The mixture is then suspended in oil, such as silicon oil, by stirring, to form an emulsion. Within 24 hours, the solvent diffuses into the oil phase and the emulsion droplets harden into solid polymer microspheres. Unlike solvent evaporation, this method can be used to make microspheres from polymers with high melting points and a wide range of molecular weights. Microspheres having a diameter for example between one and 300 microns can be obtained with this procedure.

Targeting of Particles

Targeting molecules can be attached to the aerodynamically light particles via reactive functional groups on the particles. For example, targeting molecules can be attached to the amino acid groups of functionalized polyester graft copolymer particles, such as PLAL-Lys particles. Targeting molecules permit binding interaction of the particle with specific receptor sites, such as those within the lungs. The particles can be targeted by attachment of ligands which specifically or non-specifically bind to particular targets. Exemplary targeting molecules include antibodies and fragments thereof including the variable regions, lectins, and hormones or other organic molecules capable of specific binding for example to receptors on the surfaces of the target cells.

Therapeutic Agents

Any of a variety of therapeutic, prophylactic or diagnostic agents can be incorporated within the aerodynamically light particles. The aerodynamically light particles can be used to locally or systemically deliver a variety of therapeutic agents to an animal. Examples include synthetic inorganic and organic compounds, proteins and peptides, polysaccharides and other sugars, lipids, and nucleic acid sequences having therapeutic, prophylactic or diagnostic activities. Nucleic acid sequences include genes, antisense molecules which bind to complementary DNA to inhibit transcription, and ribozymes. The agents to be incorporated can have a variety of biological activities, such as vasoactive agents, neuroactive agents, hormones, anticoagulants, inimunomodulating agents, cytotoxic agents, prophylactic agents, antibiotics, antivirals, antisense, antigens, and antibodies. In some instances, the proteins may be antibodies or antigens which otherwise would have to be administered by injection to elicit an appropriate response. Compounds with a wide range of molecular weight can be encapsulated, for example, between 100 and 500,000 grams per mole.

Proteins are defined as consisting of 100 amino acid residues or more; peptides are less than 100 amino acid residues. Unless otherwise stated, the term protein refers to both proteins and peptides. Examples include insulin and other hormones. Polysaccharides, such as heparin, can also be administered.

The aerodynamically light polymeric aerosols are useful as carriers for a variety of inhalation therapies. They can be used to encapsulate small and large drugs, release encapsulated drugs over time periods ranging from hours to months, and withstand extreme conditions during aerosolization or following deposition in the lungs that might otherwise harm the encapsulated therapeutic.

The aerodynamically light particles may include a therapeutic agent for local delivery within the lung, such as agents for the treatment of asthma, emphysema, or cystic fibrosis, or for systemic treatment. For example, genes for the treatment of diseases such as cystic fibrosis can be administered, as can beta agonists for asthma. Other specific therapeutic agents include, but are not limited to, insulin, calcitonin, leuprolide (or LHRH), G-CSF, parathyroid hormone-related peptide, somatostatin, testosterone, progesterone, estradiol, nicotine, fentanyl, norethisterone, clonidine, scopolomine, salicylate, cromolyn sodium, salmeterol, formeterol, albuterol, and vallium.

Administration

The particles including a therapeutic agent may be administered alone or in any appropriate pharmaceutical carrier, such as a liquid, for example saline, or a powder, for administration to the respiratory system. They can be co-delivered with larger carrier particles, not including a therapeutic agent, the latter possessing mass mean diameters for example in the range 50 .mu.m -100 .mu.m.

Aerosol dosage, formulations and delivery systems may be selected for a particular therapeutic application, as described, for example, in Gonda, I. "Aerosols for delivery of therapeutic and diagnostic agents to the respiratory tract," in Critical Reviews in Therapeutic Drug Carrier Systems, 6:273-313, 1990; and in Moren, "Aerosol dosage, forms and formulations," in: Aerosols in Medicine. Principles, Diagnosis and Therapy, Moren, et al., Eds, Esevier, Amsterdam, 1985, the disclosures of which are incorporated herein by reference.

The greater efficiency of aerosolization by aerodynamically light particles of relatively large size permits more drug to be delivered than is possible with the same mass of non-light aerosols. The relatively large size of aerodynamically light aerosols depositing in the deep lungs also minimizes potential drug losses caused by particle phagocytosis. The use of aerodynamically light polymeric aerosols as therapeutic carriers provides the benefits of biodegradable polymers for controlled release in the lungs and long-time local action or systemic bioavailability. Denaturation of macromolecular drugs can be minimized during aerosolization since macromolecules are contained and protected within a polymeric shell. Coencapsulation of peptides with peptidase-inhibitors can minimize peptide enzymatic degradation.

Claim 1 of 23 Claims

What is claimed is:

1. A mass of biocompatible particles, suitable for pulmonary delivery, comprising particles having therapeutic, prophylactic or diagnostic agent, and having a mass mean diameter of at least 6.5 .mu.m and an aerodynamic diameter of less than 4 .mu.m, wherein at least 46% of the mass of particles are deposited after the first bifurcation of the lungs.

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