Patent Publication Number: US-2010119587-A1

Title: Solid lipidic particles as pharmaceutically acceptable fillers or carriers for inhalation

Description:
FIELD OF THE INVENTION  
     The present invention relates to new compositions of (active) solid lipidic particles (SLP), e.g. for inhalation, and their use as carriers or as fillers in pharmaceutical compositions. 
     It also relates to new formulations obtained by mixing a SLP composition of the invention and a micronized active compound. 
     It further relates to a method for fabricating said compositions of (active) solid lipidic particles. 
     BACKGROUND OF THE INVENTION 
     It is known to administer to patients drugs in the form of fine active particles. 
     The pulmonary route may present several advantages in the treatment of some diseases, in particular in the treatment of respiratory diseases, over the administration of the same drugs by other routes leading to the systemic delivery of such drugs. 
     Drug inhalation enables a rapid and predictable onset of action and induces fewer side effects than does administration by other routes. 
     However, these advantages are often associated to a limited deposition of the inhaled dose and a short duration action because of the protective mechanisms of the lungs (mucociliary clearance, expectoration, enzymatic system, etc). 
     In other respects, the respiratory tract possesses specific characteristics, such as an exceedingly large surface area (up to 140 m 2 ), a thin absorption mucosal membrane (0.1-0.2 μm) and lacks of first-pass hepatic metabolism, which makes it very attractive as a systemic administration route. 
     Three main delivery systems have been devised for the inhalation of aerosolized drug, namely, pressurized metered-dose inhalers (MDIs), nebulisers and dry powder inhalers (DPIs). 
     The latter are today the most convenient alternative to MDIs as they are breath-actuated and do not require the use of any propellants. 
     The deposition site and the efficiency of inhaled aerosols in the respiratory tract are critically influenced by the dispersion properties of the particles, and the aerodynamic diameter, size distribution, shape and density of generated particles. 
     For an effective inhalation therapy, inhaled active particles should have an aerodynamic diameter between about 0.5 and 5 μm to reach the lower airways. 
     Since micronized drug particles are generally very cohesive and characterized by poor flowing properties, they are usually blended, in dry powder formulations, with coarse and fine carrier particles. These carrier particles are generally carbohydrates, mainly mannitol and lactose, which are approved by the Food and Drug Administration (FDA). 
     Furthermore, the carrier particles should be chemically and physically stable, inert to the drug substance and should not exhibit harmful effects, especially on the respiratory tract. 
     In fact, the number of carriers or fillers acceptable for inhalation purpose is very limited because of many different requirements to meet before they are used. 
     WO02/43693 discloses compositions for inhalation comprising active particles, cholesterol particles and particles of excipient material, i.e. particles of carrier. 
     There is still a need for carriers or fillers that are able to overcome the problems related with the pulmonary administration of drugs such as the limited drug deposition, the irritation of upper airways, the rapid elimination of inhaled particles, the short duration action, etc. 
     This invention proposes the possibility to obtain different compositions for pulmonary administration having satisfactory properties in term of increasing drug deposition and/or delaying or accelerating drug release rate. 
     SUMMARY OF THE INVENTION 
     The present invention provides a new composition of solid lipidic particles (a SLP composition), each particle comprising biocompatible phospholipids and at least one additional biocompatible lipidic compound. 
     More particularly, in a new composition of solid lipidic particles (a SLP composition) of the invention, each particle (or substantially all particles) consist(s) of a homogeneous (or uniform) distribution (or dispersion) of biocompatible phospholipids and of at least one additional biocompatible lipidic compound (also referred to as a matrix of biocompatible phospholipids and at least one additional biocompatible lipidic compound). 
     Each particle is uniform in structure or composition throughout. 
     The present invention also provides new formulations using solid lipidic particles (SLPs) of the invention, as pharmaceutically acceptable carriers, more particularly for inhalation. 
     A SLP composition of the invention can be used as carrier, with micronized active compounds in order to promote the release of the active particles from the carrier particles on the actuation of the inhaler, improving the drug deposition. 
     More particularly, a composition of the invention consists of solid particles, each particle (or substantially all particles) comprising biocompatible phospholipids and at least one additional biocompatible lipidic compound homogeneously distributed. 
     Advantageously, the weight ratio of said phospholipids to said biocompatible lipidic compound(s) is comprised between 0.1:99.9 and 40:60, preferably comprised between 5:95 and 35:65. 
     Advantageously, said phospholipids have a phase transition temperature higher than 45° C. 
     Preferably, said phospholipids comprise or consist of one, two, three, four or more saturated biocompatible phospholipids selected from the class of phosphatidylcholin. More particularly, said saturated biocompatible phospholipid(s) is/are dipalmitoyl phosphatidylcholine (DPPC), distearoyl phosphatidylcholine (DSPS), dibehenyl phosphatidylcholine (DBPC), palmitoyl-stearoyl phosphatidylcholine (PSPC) palmitoyl-behenyl phosphatidylcholine (PBPC), stearoyl-behenyl phosphatidylcholine (SBPC), saturated phospholipid(s) with longer fatty acid residues or any derivative(s) thereof. 
     Preferably, said phospholipids comprise or consist of a combination of distearyl-phosphatidylcholine (DSPC) and dipalmitylphosphatidylcholine (DPPC). 
     Advantageously, in a composition according to the invention, said biocompatible lipidic compound(s) is/are glycerol esters, fatty alcohols, fatty acids, ethers of fatty alcohols, esters of fatty acids, hydrogenated oils, polyoxyethylenated derivatives, sterols or any derivative(s) thereof. Any combination of two, three or more of these compounds can be used. 
     Preferably, said biocompatible lipidic compound(s) is/are cholesterol, cholesterol acetate, and/or glycerol behenate. 
     Advantageously, in a composition according to the invention, the particles have a mean diameter of 0.5 μm to 20 μm. 
     A method for preparing a SLP composition according to the invention comprises the steps of (a) preparing a solution or a suspension containing said biocompatible phospholipids and said other biocompatible lipidic compound(s), and (b) spray-drying said solution or suspension. 
     Another object of the present invention relates to a composition (an active SLP composition) consisting of solid particles, each particle comprising biocompatible phospholipids, at least one other biocompatible lipidic compound and at least one active compound. 
     Advantageously, said lipidic compounds and said active compound(s) are homogeneously dispersed in (throughout) said each particle. 
     Alternatively, said active compound, in a micronized form, is coated by said lipidic compounds, wherein said biocompatible phospholipids and said additional biocompatible lipidic compound(s) are homogeneously dispersed within (throughout) said coating layer. 
     A composition according to the invention can further comprise at least one active compound in particulate form. 
     Said active compound(s) canbe selected from the group consisting of:
         anti-histaminic, anti-allergic agents, antibiotics and any antimicrobial agents, antiviral agents, anticancer agents, antidepressants, antiepileptics, antipains,   steroids, in particular beclomethasone dipropionate, budesonide, flucatisone, and any physiologically acceptable derivatives,   β-agonists, in particular terbutaline, salbutamol, salmoterol, formoterol, and any physiologically acceptable derivatives,   anti-cholinergic agents, in particular ipatropium, oxitropium, tiotropium, and any physiologically acceptable derivatives   cromones, in particular sodium cromoglycate and nedocromil,   leukotrienes, leukotriene antagonist receptors,   muscle relaxants, hypotensives, sedatives,   antigenic molecules,   antibodies,   vaccines,   (poly)peptides, in particular DNase, insulin, cyclosporine, interleukins, cytokines, anti-cytokines and cytokine receptors, vaccines, leuprolide and related analogues, interferons, growth hormones, desmopressin, immunoglobulins, erythropoietin, calcitonin and parathyroid hormone.       

     More particularly, said active compound comprises or consists of budesonide, fluticasone, cromoglycate, or tobramycin. 
     Advantageously, in a composition according to the invention, the weight ratio of said lipidic ingredients to said active compound(s) is comprised between 0.05:99.95 and 99.5:0.05. 
     Preferably, said weight ratio of said lipidic ingredients to said active compound(s) is 95:5, or is 98:2. 
     Advantageously, in a composition of the invention, said active compound(s) can be in a particularly high content. More particularly, said weight ratio of said lipidic ingredients to said active compound(s) can be comprised between (about) 10:90 and (about) 0.05:99.95, preferably is (about) 5:95 or more preferably is (about) 2:98 and even more preferably (about) 0.1:99.9. 
     A composition according to the invention, comprising said active compound(s), is (for use as) a medicament. 
     A composition according to the invention can be used for treating respiratory diseases, wherein said active compound or at least one of said active compounds is a drug (i.e. a medicament or pharmaceutically active compound(s)) for such diseases. 
     Advantageously, a composition according to the invention can be used for systemic administration of drugs (medicaments). 
     More particularly, a composition of the invention can be used for treating asthma, lung cancer, Crohn&#39;s disease, etc. 
     A method for preparing said active SLP composition according to the invention comprises the steps of (a) preparing a solution or a suspension containing said biocompatible phospholipids, said other biocompatible lipidic compound(s), and said active compound(s), and (b) spray-drying said solution or suspension. 
     In a method of the invention, no emulsion step is performed, and no hydration phase is performed. 
     More particularly, a method for making a composition consisting of solid particles comprising biocompatible phospholipids, at least one additional biocompatible lipidic compound, and optionally at least one active compound, comprises the steps of:
         preparing a solution or a suspension containing said phospholipids, said other biocompatible lipidic compound(s), and optionally said active compound(s),   converting, with no emulsion, said solution or suspension into particles.       

     Preferably, in a method of the invention, the step of converting said solution or suspension into particles is performed by means of a spray drying process. 
     A method of the invention can further comprise the steps of:
         optionally, heating said solution or suspension to reach a temperature up to about 60° C. or up to about 70° C.,   in case of a suspension, homogenizing said suspension,   spray drying the said solution or suspension, wherein the spray drying apparatus comprises :
           a gaz heating system in order to increase the temperature of the spraying gaz,   a dried cold air generating system in order to cool down the spray dried particles, and   a cyclone separator, the walls of which are cooled by any suitable means, in order to collect the dried particles.   
               

     Advantageously, the additional biocompatible lipidic compound is selected from the group consisting of glycerol esters (e.g. mono-, di-, and tri-glycerides, in particular, glycerol monostearate, glycerol behenate), fatty alcohols (preferably cetyl alcohol, steary alcohol cetostearyl alcohol or fatty alcohols with more than 18 carbon atoms), fatty acids (preferably palmitic acid, or fatty acids with more carbon atoms such as stearic acid, behenic acid, etc.), ethers of fatty alcohols, esters of fatty acids, hydrogenated oils, polyoxyethylenated derivatives, sterols (e.g. cholesterol, cholesterol esters), and any derivatives thereof. Any combination of two, three or more of these compounds can be used. 
     Advantageously, the additional biocompatible lipidic compound is a solid material at ambient temperature. 
     Preferably, the biocompatible phospholipids and the additional biocompatible lipidic compounds of a composition of the invention are characterized by a high phase transition temperature (T c ), preferably by a T c  higher than about 35° C., more preferably higher than about 45° C., and even more preferably higher than about 50° C. 
     Advantageously, a composition of the invention consists of particles having a mean size between about 0.2 μm and 200 μm, preferably in the range of about 0.2 μm to about 80 μm, and more preferably in the range of about 0.5 μm to about 20 μm. 
     Preferably, a composition of the invention consists of particles having a mean size between about 0.5 μm and 100 μm, preferably in the range of about 1 μm to about 20 μm, and more preferably in the range of about 1 μm to about 5 μm. 
     A SLP composition according to the invention can be used as a carrier or filler of pharmaceutically active compounds. 
     A SLP composition of the invention can be used in a dry powder inhaler, preferably together with at least one active compound, possibly in different formulations such as coated with the lipidic ingredients, homogeneously dispersed with the lipidic ingredients throughout each particle (or substantially all particles), and/or blended in a micronized form with the particles of a SLP composition. 
     Any suitable propellant and/or excipient can be used with a composition of the invention, in particular in pressurised metered dose inhalers and/or nebulizers. 
     A composition according to the invention can be used (for the manufacture of a medicament) for:
         improving the lung drug deposition of said active compound(s);   systemic administration of said active compound(s);   promoting the dispersal of said active compound(s), forming an aerosol on actuation of said inhaler;   improving said active compound(s) fine particle dose value;   improving the tolerance to said active compound(s) during inhalation;   delaying the dissolution (the absorption, the release and/or the dispersion) of said active compound(s) in the lung (depending on the ratio phospholipids/additional lipidic compound(s));   promoting the dissolution (the absorption, the release and/or the dispersion) of said active compound(s) in the lung (depending on the ratio phospholipids/additional lipidic compound(s));   treatment of a respiratory disease; or   for treatment of cancer, more particularly for treatment of lung cancer.       

    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  shows the structural formula of phospholipids that can be used in a composition of the invention. 
         FIG. 2  shows a modified commercially available spray dryer. Some modifications have been made in order to improve the drying efficiency and the product yield obtained by spray drying the solutions or suspensions containing lipidic compounds. 
         FIG. 3  shows the deposition pattern of the formulations given in example 1. The best deposition pattern with the highest FPD values was obtained for SLPs formulation containing the cholesterol/phospholipids weight ratio of 90/10. 
         FIG. 4  shows SEM (scanning electron microscope) microphotographs, at different magnifications of bulk Phospholipon 90H, cholesterol and budesonide powders, and spray dried SLP composition(as lipidic carrier) and a 2% budesonide physical blend formulation. 
       The SLPs show spherical structures consisting of many tiny spherical particles, approximately 0.25-2 μm in diameter slightly fused and agglomerated. In the physical blends, aggregates of flat and irregularly shaped particles of budesonide surround and interact with the spherical SLPs. 
       This  FIG. 4  shows SEM microphotographs (at different magnifications) of : (a) bulk Phospholipon 90H powder (left) and cholesterol (right) used to prepare the solutions for spray-drying, (b) the spray-dried SLPs (lipid carrier), (c) the SLP(90% C10% P)+2% Bud. physical blend formulation, and (d) budesonide (raw material). 
         FIG. 5  shows that the size and the morphological characteristics of matrix active SLPs are similar to that of the SLPs (lipidic carrier). It shows SEM micrographs&#39; (at different magnifications) of: (a) the spray-dried lipidic excipients, (b) the 90% C08% P02% B lipid matrix formulation. 
         FIG. 6  represents scintigraphic images (of the same subject) obtained using the Cyclohaler loaded with M (left inside) and PB (right inside) formulations. 
         FIG. 7  represents mean Plasma concentrations of budesonide epimer B plotted vs time for the three formulations (the active SLP also referred to as lipidic matrix formulation; the blend of SLPs with micronized budesonide also referred to as physical blend formulation; and the comparator product). 
     
    
    
     DESCRIPTION OF THE INVENTION  
     A composition according to the present invention consists of solid particles, each particle comprising biocompatible phospholipids, at least one additional biocompatible lipidic compound and optionally at least one active compound. 
     In particular, said additional biocompatible lipidic compound(s) is/are not (a) phospholipid(s). 
     The term “compound” is also referred to herein as ingredient, agent or substance. 
     A composition of the invention can refer to a “SLP composition”, to an “active SLP composition” according to the invention, and/or to a composition comprising (active) SLPs and at least one active compound in form of particles, the latter composition can also be referred to as “formulation”. 
     The term “SLP” or “SLPs” in the context of the present invention refers to solid lipidic particles, each particle comprising or consisting (essentially) of biocompatible phospholipids and at least one additional biocompatible lipidic compound. 
     In a SLP of the invention, said biocompatible phospholipids and said additional biocompatible lipidic compound(s) are homogeneously distributed (or dispersed) (throughout said particle). 
     Each particle is uniform in structure or composition throughout. 
     Contrary to a liposome structure, there is no phospholipid bilayer surrounding any core. 
     The term “active SLP” or “active SLPs” in the context of the present invention refers to SLPs wherein each particle further comprises at least one active compound. 
     In an active SLP of the invention, said biocompatible phospholipids and said additional biocompatible lipidic compound(s) are homogeneously (uniformly) distributed (or dispersed). 
     In an active SLP of the invention, said active compound(s), together with said biocompatible phospholipids and said additional biocompatible lipidic compound(s) can be homogeneously distributed. 
     In another possible embodiment, said active compound(s) can be coated by (or embedded in) said biocompatible phospholipids and said additional biocompatible lipidic compound(s) which are homogeneously distributed (i.e. homogeneously distributed in the coating layer). 
     Contrary to a liposome structure, there is no phospholipid bilayer. 
     The terms “biocompatible phospholipid(s)” and “biocompatible lipidic compound(s)” in the context of the present invention refer to respectively phospholipid(s) and lipidic compound(s), natural or synthetic, that are known to be biologically compatible, i.e. that should not produce any toxic, injurious or immunologically harmful response in living tissue. 
     A SLP composition of the invention can be used as a carrier, more particularly for inhalation, i.e. it can be mixed with an active compound, for improving the drug lung deposition of said active compound. 
     Such a formulation can also be referred to as a physical blend formulation. 
     An active SLP composition of the invention can be formulated as lipidic matrices or as lipid-coated active ingredient for entrapping both water-soluble and water-insoluble drugs in order to avoid a rapid drug release and absorption, especially when the proportion of the additional biocompatible lipid in the composition is high. In this case, the characteristic peak effect and the limited duration of action generally associated with the pulmonary administration of drugs can be respectively attenuated and improved. 
     An active SLP composition of the invention can also be formulated as lipidic matrices or as lipid-coated active ingredient for entrapping water-insoluble drugs in order to promote the drug release and absorption, when the proportion of phospholipids in the composition is increased. 
     Moreover, as a dried material they (SLPs and active SLPs) offer a better stability (protection of drug in the hydrophobic environment) and a higher encapsulation efficiency (than liposomes for example). 
     Contrary to the classical hydrophilic excipients generally used in DPIs (carbohydrates), the hydrophobic nature of the SLPs associated with the active compound permits to reduce the absorption of the ubiquitous vapour leading to a reduction of the aggregation and the adhesion of particles. 
     This improves the flowing property of the particles into the inhalation device, in particular during filling process, ensures accurate dosing of active ingredients and increases the dispersing property of cohesive dry particles during emission. 
     In an active SLP composition of the present invention, each SLP further comprises an active compound (or active ingredient). Said active compound is thus embedded in physiological lipids for a better tolerance in the pulmonary tract, reducing the inherent local irritation generally associated with DPIs. 
     An active SLP composition of the invention allows protection of the pulmonary tract against irritating drugs and excipients. 
     In a composition of the invention, the SLPs are (essentially) constituted of biocompatible and biodegradable material. 
     Said biocompatible phospholipids and said biocompatible lipidic compound(s) are two physiologically well-tolerated components, and present some interesting characteristics for the delivery of drugs (or of said active compound(s)) by the pulmonary route. 
     The SLPs are (essentially) composed of physiological compounds present in the endogenous lung surfactant, and are thus less affected by the alveolar macrophages clearance mechanism. 
     For example, the phospholipids of the SLPs can be a mixture of disaturated phosphatidylcholines, which correspond to an estimated 55% to 80% of phosphatidylcholine (or 45% to 65% of total phospholipids) of the naturally occurring pulmonary surfactant pool. 
     The endogenous lung surfactant is a complex mixture of lipids and proteins comprising about 85% to about 90% phospholipids (of which about 90% are phosphatidylcholine and 8-10% are phosphatidylglycerol), 6-8% biologically active proteins (Surfactant Proteins, SP-A, SP-B, SP-C and SP-D) and 4-7% neutral lipid (primarily cholesterol) by weight. 
     It is also interesting to note that the phospholipids present in the lung surfactant are largely saturated, with dipalmitoyl phosphatidylcholine (DPPC), representing up to 40% of the total phospholipids present. 
     The endogenous lung surfactant is synthesized, processed, packaged, secreted and recycled by type II pneumocytes. It is stored in characteristic lamellar body organelles in the cytoplasm prior to secretion into the alveolar hypophase. 
     After performing its physical function, the great majority of lung surfactant is reutilised directly or indirectly to augment cellular surfactant stores rather than being lost from the alveolar compartment. Only about 10% to about 15% of alveolar surfactant appears to be taken up into macrophages. Most of this surfactant is presumably degraded rather than reutilised, and this pathway probably accounts for much of the loss from the alveolar compartment over time. 
     A small fraction of 2-5% of alveolar surfactant is also thought to be cleared to the airways. 
     The recycling of alveolar surfactant phospholipids and apoproteins within the type II cell involve that some surfactant components are transported to the lamellar bodies without degradation and are combined intact with newly synthesized surfactant, while others are catabolized to products that are incorporated into synthesis pathways. 
     Recycling of phospholipids, proteins, and other components present in exogenous surfactants by type II pneumocytes is known to occur. 
     In other words, the exogenous phospholipids (from the SLPs or active SLPs of the invention) are expected to be recycled, i.e. reutilised in the endogenous surfactant pool, and thus are expected to be well tolerated. 
     Advantageously, in a composition according to the invention, each particle comprises or consists of:
         one, two, three, four or more biocompatible phospholipids selected from the phospholipid classes including anionic phospholipids, cationic phospholipids, zwitterionic phospholipids and neutral phospholipids, such as for example phosphatidylcholine, phosphatidyl glycerol, phosphatidyl-ethanolamine, phosphatidyl-inositol, phosphatidyl-serine, and   one, two, three, four or more biocompatible lipidic compounds, which are not phospholipids, such as glycerol esters (e.g. mono-, di- or tri-glycerides, in particular glycerol monostearate, glycerol behenate), fatty alcohols (in particular with 16 C or more), fatty acids (in particular with 16 C or more), ethers of fatty alcohols, esters of fatty acids, hydrogenated oils, polyoxyethylenated derivatives, sterols (e.g. cholesterol and its derivatives, in particular cholesterol esters) or any derivatives thereof, and   optionally, one, two, three, four or more active compounds.       

     Preferably, in a composition according to the invention, each particle comprises or consists of:
         one, two three four or more saturated biocompatible phospholipids selected from the class of phosphatidylcholine having a high transition temperature such as dipalmitoyl phosphatidylcholine (DPPC), distearoyl phosphatidylcholine (DSPS), dibehenyl phosphatidylcholine (DBPC), palmitoyl-stearoyl phosphatidylcholine (PSPC) palmitoyl-behenyl phosphatidylcholine (PBPC), stearoyl-behenyl phosphatidylcholine (SBPC), saturated phospholipids with longer fatty acid residues or any derivatives thereof,   one, two, three, four or more biocompatible lipidic compounds with high transition temperature, which are not phospholipids, such as glycerol esters (e.g. mono-, di- or tri-glycerides, in particular glycerol monostearate, glycerol behenate), fatty alcohols (preferably cetyl alcohol, steary alcohol, cetostearyl alcohol or fatty alcohols with more carbon atoms), fatty acids (preferably palmitic acid, stearic acid, behenic acid or fatty acids with more carbon atoms), ethers of fatty alcohols, esters of fatty acids, hydrogenated oils, polyoxyethylenated derivatives, sterols (e.g. cholesterol and its derivatives, in particular cholesterol esters) or any derivatives thereof, and   optionally, one, two, three, four or more (micronized) active compounds.       

     The phospholipids that can be used in a composition of the invention can have a structural formula as given in  FIG. 1 , wherein R 1  and R 2  are fatty acid residues, and wherein R 1  and R 2  can be the same or can be different. 
     Preferably, phospholipids to be used in a composition of the invention have a high phase transition temperature (T c ) (also referred to as the melting temperature) higher than about 35° C. or 40° C., more preferably higher than about 45° C., 46° C., 47° C., 48° C. or 49° C., and even more preferably higher than 50° C., 51° C., 52° C. or 53° C. 
     Preferred biocompatible phospholipids of the invention are purified and saturated phosphatidylcholine (e.g. more than about 85 wt. %, preferably more than about 90 wt. % or more than about 95 wt. % in the final purified product), in particular a combination of distearyl-phosphatidylcholine (DSPC) and dipalmitylphosphatidylcholine (DPPC). 
     Examples of biocompatible phospholipids with a high phase transition temperature (T c ) are Phospholipon® 90H, Phospholipon® 100H (Nattermann Phospholipid GmbH, Köln, Germany), comprising respectively 90% and 95% of hydrogenated phosphatidylcholine, consisting of 85% distearyl-phosphatidylcholine (DSPC) and 15% dipalmitylphosphatidylcholine (DPPC), with a transition temperature Tc of about 54° C. 
     Similar commercially available high transition temperature phospholipids developed by Lipoid (Ludwigshafen, Germany) are Lipoid® S PC-3 (high purity soy bean saturated phospholipids, comparable to Phospholipon® 100 H), and high purity synthetic phospholipids (Lipoid® PC 16:0/16:0 (DPPC) and Lipoid® PC 18:0/18:0 (DSPC) 
     For obtaining the products of Nattermann Phospholipid GmbH, crude soy bean lecithin, containing crude phospholipids mixtures and a variety of other compounds such as fatty acids, triglycerides, sterols, carbohydrates and glycolipids, goes through a purification process, without acetone extraction, for preparing very highly purified phospholipids. 
     An initial ethanolic extraction and column chromatography on silica gel yields lecithin that contains 75% to 85% phosphatidylcholine (Phospholipon® 80). Further chromatography yields lecithin containing over 90% of phosphatidylcholine. A further purification step can be performed. Thus a hydrogenation step generates fully saturated phospholipids (Phospholipon® 90H and 100H). 
     The phospholipids can play an important role in the physiological tolerance of the inhaled particles. 
     More over, acting as tension-active ingredient, they can promote the dispersion and dissolution of the inhaled particles in the physiological aqueous fluids. 
     Active SLP compositions containing large amounts of phospholipids thus can increase the release and the absorption of drugs, especially when the active substances have limited solubility or absorption characteristics. 
     The more hydrophobic lipids (the additional biocompatible lipidic compound(s)) can act as a barrier between aqueous fluids and the active substances, especially for matrix (homogeneous mixture of lipidic and active ingredients in each particle) and encapsulated (micronized active particles coated with lipidic ingredients) active SLP compositions, thereby reducing the rate of absorption of the active substance in the body. 
     When the proportion by weight of the additional biocompatible lipidic compound(s) largely exceeds that of phospholipids in the active SLPs, the release of the active substance may occur over longer periods than for a composition comprising phospholipids in majority. 
     Any delayed release of the active substance may provide a lower initial peak of concentration of the active substance, which may result in reduced side effect associated with the active substance. 
     Therefore, depending on the active ingredient to be used, and on the effect on release sought, the proportion by weight of the hydrophobic lipids (the additional biocompatible lipidic compound(s)) may exceed or not that of the phospholipids in a composition of the invention. 
     Thus, in each particle of a composition of the invention, the biocompatible phospholipids and the additional biocompatible lipidic compound(s) can be in any weight ratios (zero excepted). 
     For a SLP composition, wherein each particle consists of biocompatible phospholipids and additional biocompatible lipidic compound(s), said phospholipids can be comprised between about 0.1 wt. % and about 99.9 wt. %, said additional biocompatible lipidic compound(s), constituting the balance, can be comprised between about 0.1 wt. % and about 99.9 wt. %. 
     For compositions with an expected promoting effect on release and/or on absorption of drugs, and depending on the active compound(s) to be used, the phospholipids can be comprised between about 10 wt. % and about 99.9 wt. %, preferably between about 20 wt. % and about 90 wt. %, more preferably between about 25 wt. % and about 80 wt. %, the additional biocompatible lipidic compound(s) constituting the balance. 
     For compositions with an expected delay effect on release of the active ingredient(s), the phospholipids can be comprised between about 0.1 wt. % and about 40 wt. %, preferably between about 0.1 wt. % and about 30 wt. %, more preferably between about 5 wt. % and about 20 wt. %, the additional biocompatible lipidic compound(s) constituting the balance. 
     Generally, the dispersal of the SLPs and/or the dispersal of the micronized drug when added to the SLPs, is promoted when the phospholipids is comprised between about 0.1 wt. % and about 35 wt. %, the additional biocompatible lipidic compound(s) constituting the balance. 
     For an active SLP composition, wherein each particle consists of biocompatible phospholipids, at least one additional biocompatible lipidic compound and at least one active compound, the weight ratio biocompatible phospholipids/additional biocompatible lipidic compound(s) can be comprised between about 0.1:99.9 and about 99.9:0.1. 
     For composition with an expected promoting effect on release and/or on absorption of drugs, and depending on the active compound(s) to be used, the weight ratio biocompatible phospholipids/additional biocompatible lipidic compound(s) can be comprised between about 10:90 and about 99.9:0.1, preferably between about 20:80 and about 90:10, more preferably between about 25:75 and about 80:20. 
     For compositions with an expected delay effect on release of the active ingredient(s), the weight ratio biocompatible phospholipids/additional biocompatible lipidic compound(s) can be comprised between about 0.1:99.9 and about 40:60, preferably between about 0.1:99.9 and about 30:70, more preferably between about 5:95 and about 20:80. 
     Generally, the dispersal of the active SLPs is promoted when the weight ratio biocompatible phospholipids/additional biocompatible lipidic compound(s) is comprised between about 0.1:99.9 and about 35:65. 
     Preferred additional biocompatible lipidic compounds to be used in a composition of the invention are cholesterol, cholesterol acetate, and/or glycerol behenate. 
     Advantageously, in a composition of the invention, each particle comprises or consists of biocompatible phospholipids characterized by a high phase transition temperature (T a ) (preferably higher than about 35° C., more preferably higher than about 45° , and even more preferably higher than 50° C.) and additional biocompatible lipidic compound(s) selected from the group consisting of cholesterol, cholesterol acetate and glycerol behenate. 
     Preferably, in a composition of the invention, each particle comprises or consists of biocompatible phospholipids characterized by a high phase transition temperature (T c ) (higher than about 35° C. or 40° C., more preferably higher than about 45° C., 46° C., 47° C., 48° C. or 49° C., and even more preferably higher than 50° C., 51° C., 52° C. or 53° C.) and cholesterol. 
     In a preferred composition of the invention, said phospholipids are Phospholipon® 90H and/or Phospholipon® 100H and said additional biocompatible lipidic compound(s) is/are cholesterol, cholesterol acetate and/or glycerol behenate. 
     In a preferred composition of the invention, each particle comprises or consists of Phospholipon® 90H and/or Phospholipon® 100H, and cholesterol. 
     Advantageously, the weight ratio Phospholipon®/cholesterol is comprised between about 0.1:99.9 and about 50:50, preferably between about 1:99 and about 40:60, or between about 5:95 and about 35:65, or between about 5:95 and about 30:70, more preferably between about 10:90 and about 30:70, and even more preferably between about 10:90 and about 25:75. 
     Advantageously the proportion by weight of said additional biocompatible lipidic compound(s) exceeds that of the biocompatible phospholipids in a composition of the invention. 
     Preferably, said biocompatible phospholipids (e.g. Phospholipon®) and said additional biocompatible lipidic compound(s) (e.g. cholesterol, cholesterol acetate, glycerol behenate) are respectively present in weight ratios of from about 0.1:99.9 to about 40:60, preferably of from about 1:99 to about 40:60, or of from about 5:95 to about 35:65, or of from about 5:95 to about 30:70, more preferably of from about 10:90 to about 30:70, and even more preferably of from about 10:90 to about 25:75. 
     In a composition of the invention, the active compound(s) can be any drug(s) which are usually administered nasally or orally, in particular by inhalation, e.g. for the treatment of respiratory diseases. 
     The active compound(s) can also be any drug(s) that can be administered nasally or orally by inhalation in order to reach the systemic circulation. 
     The active compound(s) can be anti-histaminic or anti-allergic agents, steroids (for example one or more compound selected from the group consisting of beclomethasone dipropionate, budesonide, flucatisone, and any physiologically acceptable derivatives), β-agonists (for example one or more compound selected from the group consisting of terbutaline, salbutamol, salmoterol, formoterol, and any physiologically acceptable derivatives), anti-cholinergic agents (for example one or more compound selected from the group consisting of ipatropium, oxitropium, tiotropium, and any physiologically acceptable derivatives), cromones (for example sodium cromoglycate or nedocromil), leukotriene antagonist receptors. 
     The active substances can also be antibiotics or any antimicrobial agents, antiviral agents, antipain agents, anticancer agents, muscle relaxants, antidepressants, antiepileptics, hypotensives, sedatives, antigenic molecules, or any agents to be used for local delivery of vaccines to the respiratory tract. 
     The active substances can also be therapeutically active agents for systemic use provided that the agents are capable of being absorbed into the circulatory system via the lung. 
     The active substances can also be peptides or polypeptides such as DNase, leukotrienes, insulin, cyclosporine, interleukins, cytokines, anti-cytokines and cytokine receptors, vaccines, leuprolide and related analogues, interferons, growth hormones, desmopressin, antigenic molecules, immunoglobulins, antibodies, erythropoietin, calcitonin, and parathyroid hormone, etc. 
     In a composition of the invention, the biocompatible phospholipids and the additional biocompatible lipidic compound(s) can be regarded as carriers or fillers. 
     Advantageously, in a composition of the invention, the weight ratio carriers or fillers/active ingredient(s) is comprised between about 0.01 and about 5000, preferably between about 5 and about 100, more preferably between about 10 and about 50. 
     Advantageously, a composition of the invention has a particularly high drug content. More particularly, the weight ratio carriers or fillers/active ingredient(s) can be comprised between about 0,05:99.95 and about 10:90, preferably said ratio is about 5:95, more preferably is about 2:98 and can be even about 0.1:99.9. 
     Advantageously, the particles in a composition of the invention have a mean particle size smaller than about 100 μm, preferably smaller than about 50 μm, 30 μm, 20 μm and more preferably smaller than about 10 μm, 5 μm, or even smaller than about 2 μm, or 1 μm. 
     The size of the particles may be evaluated by using laser diffraction or any other standard methods of particle sizing or by sizing methods allowing the determination of the aerodynamic diameter of particles according to the methods described in the European or US Pharmacopeas. 
     A SLP composition of the invention can be used as carrier for obtaining a new composition/formulation comprising or consisting of SLPs and at least one active ingredient, wherein said active ingredient(s) is/are in the form of solid particles, in particular in the form of micronized particles. 
     Advantageously, in a new formulation of the invention, the active ingredient(s) represent(s) less than about 50 wt. % of said formulation, preferably less than about 20 wt. %, less than about 10 wt. %, or less than about 5 wt. %, and even less than about 3 wt. %, less than about 2 wt. %, or less than about 1 wt. %. 
     When the use of micronized drug (or active ingredient(s)) is required, the micronized drug particles might have a mean particle size lower than about 20 μm, preferably lower than about 5 μm, such as about 2 μm or about 3 μm. 
     For example, at least 99% by weight of active particles can have a size lower than 5 μm. 
     Advantageously, all the SLPs have a mean particle size between about 0.2 μm and about 200 μm, preferably in the range of about 0.2 μm to about 80 μm and more preferably in the range of about 0.5 μm to about 20 μm. 
     Blends, in different proportions, of SLPs having larger particle size (e.g. diameter of about 60 μm, 80 μm, 100 μm, 150 μm or more) and SLPs having smaller particle size (e.g. diameter of less than about 60 μm, 50 μm, 20 μm, μm, 5 μm, 2 μm, 1 μm, 0.5 μm or even less) can be considered in order to enhance the flowability of the compositions of the invention and to promote the delivery of relatively large proportion of active compounds into the lung. 
     Advantageously, the particles obtained according to the invention are spherical with a smooth surface and are present as loose agglomerates with important dispersal properties during inhalation. 
     The new formulation according to the invention can be used in dry powder inhalers. Said dry powder inhaler can be for example a multidose system (reservoir system) or a monodose system, in which the powder is pre-packaged in either capsules (hard gelatine, hydroxypropylmethylcellulose (HPMC), or other pharmaceutically acceptable capsules) or in blisters. 
     A method for making a composition according to the invention is provided, comprising the steps of:
         preparing a solution or a suspension (or colloidal dispersion) containing biocompatible phospholipids, at least one additional biocompatible lipidic compound, and optionally at least one active compound,   converting said solution or suspension into particles, and   optionally adding at least one active compound in particulate form.       

     For making a SLP composition of the invention, the method comprises the steps of:
         preparing a solution or suspension comprising or consisting (essentially) of biocompatible phospholipids and at least one additional biocompatible lipidic compound, and   converting said solution or suspension into particles.       

     For making an active SLP composition of the invention, the method comprises the steps of:
         preparing a solution or a suspension comprising or consisting (essentially) of biocompatible phospholipids, at least one additional biocompatible lipidic compound and at least one active compound, and   converting said solution or suspension into particles.       

     In a method of the invention, no (heat or cold) emulsion step is performed. 
     In a method of the invention, no hydration step is performed. 
     With no emulsion, and with no hydration phase, said biocompatible phospholipids are not allowed to form a bilayer surrounding a core (in particular a lipid core). 
     In the case of suspensions, some components of the formulation might be partially or totally at the solute state. 
     Advantageously, in a method of the invention, the biocompatible phospholipids, which may have a formula as given in  FIG. 1 , wherein R 1  and R 2  (equal or different) are fatty acid residues, show a high phase transition temperature (Tc), preferably higher than about 35° C. or 40° C., more preferably higher than about 45° C., 46° C., 47° C., 48° C. or 49° C., and even more preferably higher than 50° C., 51° C., 52° C. or 53° C. 
     Advantageously, in a method of the invention, the additional biocompatible lipidic compound(s) is/are selected from the group consisting of glycerol esters (e.g. mono-, di-, and tri-glycerides, in particular glycerol monostearate, glycerol behenate), fatty alcohols (preferably with 16, 18 or more carbon atoms), fatty acids (preferably with 16, 18 or more carbon atoms), sterols (e.g. cholesterol, cholesterol esters), and any derivatives thereof. 
     In a preferred method of the invention, said phospholipids are purified and saturated phosphatidylcholine, e.g. Phospholipon® 90H and/or Phospholipon® 100H, said additional biocompatible lipidic compound(s) is/are cholesterol, cholesterol acetate and/or glycerol behenate. 
     In a method according to the invention, for preparing said solution/suspension, an appropriate solvent system is chosen on the basis of the solubility of the different compounds. 
     Water or any aqueous solution, ethanol, isopropanol and methylene chloride are examples of suitable solvent systems that can be used in a method of the invention. Any mixture of two, three, or more of said solvent systems can be used in a method of the invention. 
     The solvent system used can be heated in order to allow the dissolution of ingredient showing limited solubility characteristics. 
     Advantageously, the solvent system used is heated up to about 60° C., about 65° C., or about 70° C. maximum. 
     Said heating step helps the dissolution process and is not to be confused with an emulsion step. 
     When the lipidic ingredients and, if present, the active substance(s), are not soluble in the solvent system chosen, a method for making a composition of the invention may further comprise, after the step of preparing a suspension containing said phospholipids, said additional biocompatible lipidic compound(s) and optionally said active compound(s), and before the conversion step, a step of homogenizing said suspension. 
     A preferred process for converting said solution or suspension into particles consists of the spray drying process. 
     Spray-drying is a one step process that converts a liquid feed (solution, coarse suspension, colloidal dispersion, etc.) to a dried particulate form. 
     The principal advantages of spray-drying with respect to a composition of the invention are the ability to manipulate and control particle size, size distribution, shape, and density in addition to macroscopic powder properties such as bulk density, flowability, and dispersibility. 
     In classical spray dryers, the inlet and outlet temperatures are not independently controlled. Typically, the inlet temperature is established at a fixed value and the outlet temperature is determined by such factors as the gas flow rate and temperature, chamber dimensions, and feed flow rate. 
     For the purpose of this invention, the existing process and device had to be improved for a better drying efficiency and/or to diminish and even prevent (partial) melting or softening of the lipidic components. 
     On the one hand, the spraying gaz is heated in order to bring the nebulized droplets of the sprayed solution or suspension directly in contact with pre-heated gaz and thus, to increase the evaporation of the solvent system. 
     The temperature of the spraying gaz might be as high as possible, in accordance with the ebullition temperature of the solvent system used, but might not be too high in order to avoid any excessive softening or melting of lipidic ingredients. 
     Spraying -gaz temperatures of about 60° C., of about 65° C., or of about 70° C. can be used in this purpose. 
     A method of the invention can comprise a further step of heating the solution or suspension prepared, before the step of spray drying. 
     In the (main) drying chamber, after the solution or suspension is converted into particles, said particles are cooled down for example by means of dried cold air brought at the bottom level of said (main) drying chamber (see  FIG. 2 ). 
     Said dried cold air can be brought by means of an air cooling system equipped with an air dryer. 
     Furthermore, a jacketed cyclone with cold water circulation can be used to cool the cyclone separator walls and thus reduce even more the adhesion of the lipidic particles. 
     A method for making a composition according to the invention can thus comprise the steps of:
         preparing a solution or a suspension containing biocompatible phospholipids, at least one additional biocompatible lipidic compound, and optionally at least one active compound,   optionally, heating said solution or suspension to reach a temperature up to about 40° C., up to about 50° C., up to about 60° C., or up to 70° C.,   in case of a suspension, homogenizing said suspension,   converting the said solution or suspension into particles by feeding a (modified) spray drying system comprising:
           a gaz heating system in order to increase the temperature of the spraying gaz,   a dried cold air generating system in order to cooling down the spray dried particles,   a cyclone separator, the walls of which are cooled by any suitable means, in order to collect the dried particles.   
               

     A factorial design study has permitted to determine the optimal conditions of spray-drying for the preparation of SLP when ethanolic solutions of lipids were used. 
     For example, a method for making a (active) SLP composition of the invention can comprise the steps of:
         preparing a solution (at 60° C.) containing biocompatible phospholipids and at least one additional biocompatible lipidic compound, and optionally at least one active compound, wherein the solvent is ethanol,   feeding a modified spray drying apparatus with said heated solution for its conversion into particles by adopting the following particular conditions : spraying air heated to 55° C., dried cold air at about −5° C. brought at the bottom level of the (main) drying chamber, cyclone separator walls cooled by cold water circulation at 5° C.       

     A spray drying apparatus is also provided comprising :
         a gaz heating system in order to increase the temperature of the spraying gaz,   a dried cold air generating system in order to cooling down the spray dried particles,   a cyclone separator, the walls of which are cooled by any suitable means, in order to collect the dried particles.       

     In a method of the invention, the step of spray-drying can be replaced by any process suitable for making particles out of a solution, a suspension, or a colloidal dispersion containing said phospholipids, said additional biocompatible lipidic compound(s) and optionally said active compound(s). 
     Examples of such processes include freeze drying, spray freeze drying, gas phase condensation, or supercritical fluid methods. 
     When one or more ingredients of the composition are not soluble in the solvent system (i.e. suspension system), milling processes or high speed or high pressure homogenization techniques can be used in order to obtain appropriate particle size of the active or lipidic ingredients prior to the step of conversion of a suspension to dried particles. 
     In a method of the invention, the SLPs used as carrier and micronized particles of active ingredient may be mixed in any suitable way. The SLPs are preferably sieved (using stainless steel sieves of aperture diameters 315 μm for example) prior to be blended with the micronized active particles in an appropriate mixer. 
     Three different laboratory scale mixers namely Turbula 2C as a tumbling mixer, Collette MP-20 as a planetary mixer and Mi-Pro as a High shear mixer have shown quite satisfactory powder homogenisation results for mixing time comprised between about 10 minutes and about 60 minutes at optimal speeds. 
     A composition of the invention, in a powder form, may be used in a dry powder inhaler. 
     In a composition of the invention, the lipidic ingredients can promote the dispersal of the active particles to form an aerosol on actuation of the inhaler. 
     A composition of the invention may also comprise any suitable propellant and/or excipient for use in a pressurized metered dose inhaler (pMDI) and/or nebulizers. 
     A composition of the invention may also be formulated in suspension of active SLPs in appropriate vehicle as pressurized or ultra sonic nebulizers. 
     In a composition of the invention, the active substance may exert its pharmacological effect over a significantly longer period than the period over which the active substance exerts it pharmacological effect when inhaled alone. 
     In a composition of the invention, the absorption of the active ingredient can be promoted after inhalation in comparison with formulation for inhalation containing the active ingredient alone. 
     In a composition of the invention, the tolerance to the inhaled particles is increased in presence of lipidic ingredients. 
     A composition of the invention may also contain particles of a common excipient material for inhalation use, as fine excipient particles and/or carrier particles. 
     A composition of the invention may also contain any acceptable pharmacologically inert material or combination of materials. For example, sugar alcohols; polyols such as sorbitol, mannitol and xylitol, and crystalline sugars, including monosaccharides (glucose, arabinose) and disaccharides (lactose, maltose, saccharose, dextrose); inorganic salts such as sodium chloride and calcium carbonate; organic salts such as sodium lactate; other organic salts such as urea, polyssacharides (starch and its derivatives); oligosaccarides such as cyclodextrins and dextrins. 
     The invention is described in further details in the following examples, which are intended for illustration purposes only, and should not be construed as limiting the scope of the invention in any way. 
     Examples 
     Example 1 
     This example illustrates one aspect of the invention : new formulations based on blends of SLPs, used as pharmaceutical carrier, and micronized active compounds. 
     Said new formulations comprise, based on the total weight, 98% of SLPs used as carriers (with a weight ratio Phospholipon® 90H/cholesterol ranging from 40:60 to 0.1:99.9) and 2% micronized budesonide. 
     A method for making the SLP compositions comprises the preparation of a solution of cholesterol, and a solution of Phospholipon 90H. Different solvent systems can be used, preferably ethanol, isopropanol or methylene chloride. 
     The solutions have to be combined such that the total solute concentration is greater than 1 gram per litre, and spray dried to form SLPs with appropriate particle size for inhalation. 
     Spray-drying is carried out, using a modified laboratory scale spray dryer, Büchi mini spray dryer B-191 (Büchi Laboratory Techniques, Switzerland). 
     On the one hand, the spraying gas (air) is heated to increase the drying efficiency, and on the other hand, dried cold air is generated at the bottom level of the main drying chamber, using an air cooling system equipped with an air dryer, in order to decrease the outlet air temperature (see  FIG. 2 ). 
     Furthermore, a jacketed cyclone with cold water circulation is used to cool the cyclone separator walls and thus to reduce the adhesion of the particles. 
     A factorial design study has permitted to determine the optimal conditions of spray-drying for the preparation of SLPs when ethanolic solutions of lipids were used : inlet air temperature, 70° C.; outlet air temperature, 28-34° C.; spraying air flow, 800 l/h heated at 55° C.; drying air flow, 35m 3 /h; solution feed rate, 2.5-3.0 g/min; nozzle size, 0.5 mm; generation of cold air −5° C. at 10 m 3 /h; cold water circulation in the jacketed cyclone at 5° C. 
     Using different weight ratios Phospholipon® 90H/cholesterol, ranging from 40:60 to 0.1:99.9, different SLP compositions are obtained. 
     For each SLP composition, the particle size distribution is measured by laser diffractometry, using a dry sampling system with a suitable SOP (Standard Operating Procedure), (Scirocco®, Mastersizer 2000, Malvern, UK). 
     The size distributions are expressed in terms of the mass median diameter d(0.5), i.e. the size in microns which 50% of the sample is smaller and 50% is larger, and in terms of the volume (mass) mean diameter D[4,3]. 
     For obtaining said new formulations, each SLP composition is premixed with active micronized particles of budesonide for between 5 and 15 minutes in a mortar (with a spatula, without crushing), and then blended for between 5 and 30 minutes in a tumbling blender (Turbula Mixer, Switzerland). 
     Particle size distribution results obtained by laser diffractometry for the different SLP formulations are given in Table 1. 
     As shown in Table 1, the mass median diameter and the volume mean diameter are tiny and range from 1.7 μm to 3.1 μm and from 2.0 μm to 3.9 μm, respectively. 
     The particle size distribution results (data not shown) obtained for the different formulations are unimodal, narrow and range from 0.3 μm to 10 μm, with more than 90% of the particles having a diameter below 5.0 μm, which corresponds to upper size limits required for an optimal deep lung deposition. 
     The addition of micronized budesonide to the SLPs does not affect the particle size distribution&#39;s narrowness. 
     
       
         
           
               
             
               
                 TABLE 1 
               
             
            
               
                   
               
               
                 Particle size distribution of formulations given in 
               
               
                 example 1, determined by using a laser diffraction method 
               
               
                 (mean ± s.d. values obtained from 3 determinations, n = 3) 
               
            
           
           
               
               
               
               
            
               
                 Formulations (% w/w) 
                   
                 d (0.5) μm 
                 D [4, 3] μm 
               
               
                   
               
            
           
           
               
               
               
               
            
               
                   66% C34% P* 
                   
                 2.9 ± 0.3 
                 3.9 ± 0.8 
               
               
                   
                 +2% Bud** 
                 3.1 ± 0.3 
                 3.9 ± 0.9 
               
               
                   75% C25% P 
                   
                 1.67 ± 0.03 
                 1.88 ± 0.03 
               
               
                   
                 +2% Bud 
                 1.92 ± 0.03 
                 2.25 ± 0.02 
               
               
                   90% C10% P 
                   
                 1.60 ± 0.05 
                 1.9 ± 0.1 
               
               
                   
                 +2% Bud 
                 1.70 ± 0.04 
                 2.00 ± 0.06 
               
               
                 99.9% C0.1% P 
                   
                 1.88 ± 0.04 
                 2.4 ± 0.1 
               
               
                   
                 +2% Bud 
                 2.14 ± 0.03 
                 2.80 ± 0.04 
               
               
                   
               
               
                 *C: Cholesterol, P: Phospholipon ® 90H; 
               
               
                 **Bud: Budesonide. 
               
            
           
         
       
     
     It can be seen that decreasing the phospholipids/cholesterol ratio (from 34% to 10% of Phospholipon 90H) reduces slightly the mean particle size, whereas SLPs obtained for compositions containing more than 34% of phospholipids tend to stick to the cyclone separator walls of the spray dryer. 
     This phenomenon can be explained by the physical state of phospholipids during  t he spray-drying process. Indeed, the phase transition temperature (Tc) of the phospholipids plays an important role in determining the particle size characteristics of the phospholipids-based powders. The higher the phase transition temperature of the phospholipids the lower will be the mean particle size of SLPs and thus, the mass median aerodynamic diameter (MMAD). 
     In this respect, Phospholipon 90H is preferred, showing one of the highest Tc (around 54° C.), for the preparation of SLPs. 
     For compositions containing more than 34% of Phospholipon 90H, a significant softening of phospholipids during the spray-drying process and consequently a certain aggregation of particles are observed. The use of other phospholipids (saturated phospholipids with longer fatty acids residues) with higher transition temperature should permit to overcome this limitation in the phospholipids content of the compositions. 
     Beyond 10% Phospholipon 90H, the particles tend to grow slightly. 
     The Fine Particle Dose (FPD) for the different formulations of SLPs has been determined by the method described in the European Pharmacopoeia 4 for the aerodynamic assessment of fine particle, using Apparatus C—Multi-stage 
     Liquid Impinger (MsLI). 
     A dry powder inhalation device (Cyclohaler®, Novartis, Switzerland) was equipped with a No. 3 HPMC capsule (Capsugel, France) loaded with 10 mg of the formulations (200 μg of budesonide) so obtained. 
     In parallel, the In Vitro deposition test has been performed on a marketed form of budesonide (Pulmicort® Turbohaler® 200 μg, Astra Zeneca). 
     The airflow rate, corresponding to a pressure drop of 4 kPa and drawing 4 litres of air through the device, was determined by the uniformity of delivered dose test for each inhaler. 
     The test was conducted at a flow rate of 100 L/min during 2.4 seconds and at 60 L/min during 4 seconds for the formulations from a Cyclohaler® and the Pulmicort® Turbohaler®, respectively. 
     At least 3 FPD determinations were performed on each test substance and analysis were carried out by a suitable and validated analytical HPLC method. 
     The HPLC system consisted of a High-Performance Liquid Chromatography (HP 1100 series, Agilent Technologies, Belgium) equipped with a quaternary pump, an automatically injector, an oven heated at 40° C. and a spectrophotometer set at 240 nm. The separation system, as prescribed in the budesonide monograph, (Ph. Eur., 4th. Ed., 2002), was a 12 cm×4.6 mm stainless steel (5 μm particle size) reversed-phase C18 column (Alltima, Alltech, Belgium). Mobile phase (Acetonitrile-phosphate buffer solution adjusted to pH 3.2 with phosphoric acid, 32:68) was run at a flow rate of 1.5 ml/min. 
     The mass of test substance deposited on each stage was determined from the HPLC analysis of the recovered solutions. Starting at the filter, a cumulative mass deposition (undersize in percentage) vs. cut-off diameter of the respective stages was derived and the Fine Particle Dose (FPD) was calculated by interpolation the mass of active ingredient less than 5 μm. 
     The FPD is the dose (expressed in weight/nominal dose) of particles having an aerodynamic diameter inferior to 5 μm. It is considered to be directly proportional to the amount of drug able to reach the pulmonary tract in vivo, and consequently, the higher the value of FPD, the higher the estimated lung deposition. 
     The fine particle assessment results for the formulations and the marketed form of budesonide, represented by the FPD, are summarized in Table 2. 
     
       
         
           
               
             
               
                 TABLE 2 
               
             
            
               
                   
               
               
                 in vitro deposition study, with formulations given in example 1 vs 
               
               
                 Pulmicort ® Turbohaler ® (loaded dose = 200 μg, n = 3) 
               
            
           
           
               
               
               
               
               
               
            
               
                   
                 SLP 
                 SLP 
                 SLP 
                 SLP 
                   
               
               
                   
                 (66% C 
                 (75% C 
                 (90% C 
                 (99.9% C 
                   
               
               
                   
                 34% P) + 
                 25% P) + 
                 10% P) + 
                 0.1% P) + 
               
               
                   
                 2% Bud 
                 2% Bud 
                 2% Bud 
                 2% Bud 
                 Pulmicort ® 
               
               
                   
                   
               
            
           
           
               
               
               
               
               
               
            
               
                 FPD (μg) 
                 81 ± 3 
                 106 ± 1 
                 113 ± 5 
                 105 ± 3 
                 68 ± 5 
               
               
                   
               
               
                 *C: Cholesterol, P: Phospholipon ® 90H; 
               
               
                 **Bud: Budesonide. 
               
            
           
         
       
     
     The different formulations present substantially higher FPD values than the reference, which is very promising. 
     The results are in accordance with the particle size determination, obtained by laser diffraction, since that the FPD value augments when the formulation content of Phospholipon 90H is reduced from 34% to 10%. 
     Indeed, as discussed above, the decreasing of Phospholipon content of the formulations tends to reduce the particles aggregation and consequently gives a better deep lung deposition. 
     On the other hand, it seems that a cholesterol/Phospholipon 90H ratio of 90/10 is the most appropriate one as it gives the highest FPD and the best deposition pattern ( FIG. 3 ). 
     Surface topographies of these powders were investigated and the scanning electron microphotographs are illustrated in  FIG. 4 . 
     In the bulk form, Phospholipon 90H appears as aggregated flat pebbles ( FIG. 4   a , left). The original cholesterol is shown as plate-like fine crystals with diameters of approximately 500-1000 μm ( FIG. 4   a , right). Processing of the solutions of lipids by spray-drying yielded a powder with a substantially different physical appearance. SEM micrographs of the SLPs show spherical structures consisting of many tiny spherical particles, approximately 0.25-2 μm in diameter, slightly fused and agglomerated ( FIG. 4   b ). 
     The physical blends of SLP with the active substance appears to consist of these slightly fused and aggregated lipidic micro particles surrounding and interacting with aggregates of flat and irregularly shaped particles of budesonide ( FIG. 4   c ). The tap density is evaluated to be around 0.21 g/cm 3 . 
     Example 2 
     This example illustrate another aspect of the invention : an active SLP composition (lipidic matrix composition) wherein each particle comprises, by weight, 98% of lipidic fillers and 2% budesonide, with a weight ratio cholesterol/Phospholipon® 90H/budesonide of about 90:08:02). 
     The method carried out for preparing the active 
     SLP composition comprises the steps of:
         preparing a solution of cholesterol, a solution of Phospholipon® 90H, and a solution of budesonide using an appropriate solvent (ethanol or isopropanol),   mixing the three solutions such that the total solute concentration is greater than 1 gram per litre, and   spray drying the resulting solution, using the modified       

     Büchi mini spray dryer B-191 (Büchi laboratory-Techniques, Switzerland) to form particles. 
     The particle size distribution and the Fine Particle Dose are determined as mentioned in example 1. The results are shown in Table 3. 
     
       
         
           
               
             
               
                 TABLE 3 
               
             
            
               
                   
               
               
                 Particle size distribution and Fine particle dose of the 90% 
               
               
                 C08% P02% Bud active SLP composition vs Pulmicort ® 
               
               
                 Turbohaler ® (n = 3) 
               
            
           
           
               
               
               
               
               
            
               
                   
                 Formulation 
                 d (0.5) μm 
                 V (4/3) μm 
                 FPD μg 
               
               
                   
                   
               
               
                   
                 90% C08% P02% Bud 
                 1.9 ± 0.1 
                 2.3 ± 0.1 
                 108 ± 7 
               
               
                   
                 Pulmicort ® 
                 — 
                 — 
                  68 ± 5 
               
               
                   
                 Turbohaler ® 
               
               
                   
                   
               
               
                   
                 C: Cholesterol, 
               
               
                   
                 P: Phospholipon ® 90H; 
               
               
                   
                 Bud: Budesonide. 
               
            
           
         
       
     
     As it can be observed, the mass median diameter and the volume mean diameter are tiny, 1.9 μm and 2.3 μm, respectively. Furthermore, the matrix formulation is found to be greatly superior in term of deposition than the reference. 
     SEM micrographs show spherical structures consisting of many tiny spherical particles, between approximately 0.25 μm and 2 μm in diameter, slightly fused and agglomerated ( FIG. 5   a ). The tap density is evaluated to be 0.20g/cm 3 . 
     The addition of budesonide in order to prepare the lipid matrix form (active SLPs) does not affect the physical appearance of the obtained powder ( FIG. 5   b ). 
     Example 3 
     The FPD of other formulations containing 1% and 5% of micronized fluticasone propionate, blended with a SLP composition obtained as described in example 1, wherein the weight ratio Phospholipon® 90H/cholesterol is 10:90, and the FPD of another active SLP composition, prepared as described in example 2, wherein each particle comprises, by weight, 97.5% of lipidic fillers and 2.5% fluticasone propionate, with a weight ratio cholesterol/Phospholipon® 90H/fluticasone of about 90:07,5:02,5) have been determined and compared to a marketed form of the drug (Flixotide® Diskus®, GSK). 
     Particle size distribution results obtained by laser diffractometry for the SLPs are given in Table 4. 
     They show that the mass median diameter and the volume mean diameter are tiny, 1.8 μm and 2.0 μm, and 2.7 μm and 3.1 μm for the active SLP composition and the SLP physical blend composition, respectively. 
     The particle size distribution results obtained for these formulations are unimodal (data not shown), narrow and range from 0.2 μm to 12 μm, with about 90% of the particles having a diameter below 5 μm, which corresponds to upper size limits required for an optimal deep lung deposition. 
     The addition of the micronized active substance to the SLP does not affect the particle size distribution&#39;s narrowness. 
     
       
         
           
               
             
               
                 TABLE 4 
               
             
            
               
                   
               
               
                 Particle size distribution of the SLPs and formulation given in 
               
               
                 example 3, determined by using a laser diffraction method (n = 3). 
               
            
           
           
               
               
               
               
               
            
               
                   
                 Formulations (% w/w) 
                   
                 d (0.5) μm 
                 D [4, 3] μm 
               
               
                   
                   
               
            
           
           
               
               
               
               
               
            
               
                   
                 90% C10% P* 
                   
                 2.7 ± 0.2 
                 3.1 ± 0.2 
               
               
                   
                   
                 +1% Flut** 
                 2.9 ± 0.4 
                 3.4 ± 0.6 
               
               
                   
                   
                 +5% Flut** 
                 2.9 ± 0.5 
                 3.5 ± 0.5 
               
            
           
           
               
               
               
               
               
            
               
                   
                 90% C07.5% P02.5% Flut 
                   
                 1.8 ± 0.5 
                 2.0 ± 0.4 
               
               
                   
                   
               
               
                   
                 *C: Cholesterol, P: Phospholipon ® 90H; 
               
               
                   
                 **Flut: Fluticasone propionate. 
               
            
           
         
       
     
     The Fine Particle Dose (FPD) has been determined by the method described in the European Pharmacopoeia 4 for the aerodynamic assessment of fine particle, using Apparatus C—Multi-stage Liquid Impinger (MsLI). 
     A dry powder inhalation device (Cyclohaler®, Novartis, Switzerland) was equipped with a No. 3 HPMC capsule (Capsugel, France) loaded with 10 mg of the formulations (100 μg, 250 μg and 500 μg fluticasone) so obtained. 
     In parallel, the In Vitro deposition test has been performed on the marketed form of fluticasone propionate (Flixotide® Diskus®, GSK). 
     The airflow rate, corresponding to a pressure drop of 4 kPa and drawing 4 litres of air through the device, was determined by the uniformity of delivered dose test for each inhaler. 
     The test was conducted at a flow rate of 100 L/min during 2.4 secondes and at 80 L/min during 3 secondes for the formulation from the Cyclohaler® and the Diskus® inhalation device, respectively. 
     At least 3 FPD determinations were performed on each test substance and analysis were carried out by a suitable and validated analytical HPLC method. 
     The HPLC system consisted of a High-Performance Liquid Chromatography (HP 1100 series, Agilent Technologies, Belgium) equipped with a quaternary pump, an automatically injector, an oven heated at 30° C. and a spectrophotometer set at 240 nm. The separation system was a 12 cm×4.6 mm stainless steel (5 μm particle size) reversed-phase C18 column (Alltima, Alltech, Belgium). The mobile phase (Acetonitrile—phosphate buffer solution adjusted to pH 3.5 with phosphoric acid—methanol, 15:35:50) was run at a flow rate of 1.5 ml/min. 
     The mass of test substance deposited on each stage was determined from the HPLC analysis of the recovered solutions. Starting at the filter, a cumulative mass deposition (undersize in percentage) vs. cut-off diameter of the respective stages was derived and the Fine Particle Dose (FPD) was calculated by interpolation the mass of active ingredient less than 5 μm. 
     The FPD is the dose (expressed in weight for a given nominal dose) of particles having an aerodynamic diameter inferior to 5 μm. It is considered to be directly proportional to the amount of drug able to reach the pulmonary tract in vivo, and consequently, the higher the value of FPD, the higher the estimated lung deposition. 
     The fine particle assessment results for the SLP formulations and the marketed form of fluticasone propionate, represented by the FPD, are summarized in Table 5. The experiments were repeated and completed by new compositions and are summarized in Table 5b is. 
     
       
         
           
               
             
               
                 TABLE 5 
               
             
            
               
                   
               
               
                 In vitro deposition study, with formulation given in example 3 
               
               
                 (loaded dose = 100 μg, n = 3) vs. Flixotide Diskus ® 
               
               
                 (loaded dose = 500 μg, n = 3) 
               
            
           
           
               
               
               
            
               
                   
                 SLP (90% C10% P) + 
                 Flixotide 
               
               
                   
                 1% Flut * 
                 Diskus ® 
               
               
                   
                   
               
            
           
           
               
               
               
               
            
               
                   
                 FPD (μg) 
                 35.5 ± 0.4 
                 70 ± 10 
               
               
                   
                 FPF (%) 
                 35.5 ± 0.4 
                 14 ± 2  
               
               
                   
                   
               
            
           
         
       
     
     
       
         
           
               
             
               
                 TABLE 5BIS 
               
             
            
               
                   
               
               
                 In vitro deposition study, with formulation given in example 3 
               
               
                 (loaded dose = 100 μg*/500 μg**/250 μg***, n = 3) 
               
               
                 vs. Flixotide Diskus ® (loaded dose = 500 μg, n = 3) 
               
            
           
           
               
               
               
               
               
            
               
                   
                 SLP (90% 
                 SLP (90% 
                   
                   
               
               
                   
                 C10% P) + 
                 C10% P) + 
                 90% C07.5% 
                 Flixotide 
               
               
                   
                 1% Flut* 
                 5% Flut** 
                 P02.5% Flut*** 
                 Diskus ® 
               
               
                   
                   
               
            
           
           
               
               
               
               
               
            
               
                 FPD (μg) 
                 36 ± 1 
                 33 ± 2 
                 128 ± 5 
                 115 ± 6 
               
               
                 FPF (%) 
                 36 ± 1 
                 33 ± 2 
                  51 ± 2 
                  23 ± 1 
               
               
                   
               
            
           
         
       
     
     To compare more accurately these data, the FPF should be used (the Fine Particle Fraction in percent, %), i.e. the dose (expressed in weight %) of particles having an aerodynamic diameter inferior to 5 μm in relation to the nominal dose (FPD/loaded dose×100). 
     The new formulations and more particularly the active SLP formulation are found to be greatly superior in term of deposition than the reference. 
     Example 4 
     This example illustrates another embodiment, wherein a SLP composition is prepared with a method comprising the steps of preparing a suspension of phospholipids and cholesterol, homogenizing said suspension and spray drying. 
     A new formulation is prepared comprising, by weight, 98% of the SLP composition used as carrier (wherein the weight ratio Phospholipon® 90H/cholesterol is of 10:90) and 2% micronized budesonide. 
     The method for preparing said SLP composition comprises the steps of:
         preparing an aqueous suspension of Phospholipon® 90H and cholesterol,   homogenizing this suspension with high speed homogenizer at 24000 rpm during 10 minutes,   pre-milling (7 minutes at 6000 Psi then 4 minutes at 12000 Psi) and milling for between 5 and 30 minutes at 24000 Psi the aqueous suspension with a high pressure homogeniser,   spray drying the size reduced suspension, using a modified Büchi mini spray dryer B-191, (Büchi laboratory-Techniques, Switzerland) to form SLPs carriers.       

     These SLPs are mixed with active micronized particles of budesonide for between 5 and 15 minutes in a glass mortar (with a spatula, without crushing) then blended for between 5 and 30 minutes in a tumbling blender (Turbula Mixer, Switzerland) for obtaining the new formulation. 
     The particle size distribution and the Fine Particle Dose of this formulation are determined as mentioned in example 1. The results are shown in Table 6. 
     
       
         
           
               
             
               
                 TABLE 6 
               
             
            
               
                   
               
               
                 Particle size distribution and Fine particle dose of the 90% C10% P + 
               
               
                 2% B formulation vs Pulmicort ® Turbohaler ® (n = 3) 
               
            
           
           
               
               
               
               
            
               
                 Formulation 
                 d (0.5) μm 
                 V (4/3) μm 
                 FPD μg 
               
               
                   
               
               
                 Budesonide (raw material) 
                 0.8 ± 0.1 
                  1.0 ± 0.1 
                 — 
               
               
                 90% C10% P + 02% B 
                 9.9 ± 0.2 
                 18.5 ± 0.4 
                 84 ± 5 
               
               
                 Pulmicort ® Turbohaler ® 
                 — 
                 — 
                 68 ± 5 
               
               
                   
               
               
                 C: Cholesterol, 
               
               
                 P: Phospholipon ® 90H; 
               
               
                 B: budesonide. 
               
            
           
         
       
     
     Even if the particles have a diameter above 5.0 μm, there is an optimal deep lung deposition, characterised by an FPD of 84 μg for a loaded dose of 200 μg of budesonide (test conducted at 100 L/min during 2.4 seconds, Cyclohaler® inhalation device). 
     The higher FDP obtained could be explained by the fact that the small particles of budesonide are easily separated from the lipidic excipients, by the energy of the airflow during the inhalation, and reach the lowest stages of the MsLI apparatus. 
     Example 5 
     This example illustrates another embodiment, wherein an active SLP composition is prepared with a method comprising the steps of preparing a solution of phospholipids cholesterol and budesonide, evaporating the solvent at reduced pressure, and milling the solid residue of evaporation to obtain appropriate particle size for inhalation. 
     The formulation prepared in this example consists of, by weight, 92% of lipidic fillers and 8% budesonide, with a weight ratio Phospholipon® 90H/cholesterol/budesonide of 60:32:08. 
     The method carried out for preparing this formulation comprises the steps of:
         preparing a solution of Phospholipon® 90H, cholesterol and budesonide in methylene chloride,   mixing the three solutions such that the total solute concentration is greater than 1 gram per litre,   evaporating the solvent slowly in a rotary evaporator at reduced pressure, and   milling by means of an air jet-mill (MCOne jet-mill, Jetpharma, Italy), to obtain micronized active SLPs.       

     The particle size distribution and the Fine Particle Dose are determined as mentioned in example 1. 
     Example 6 
     According to example 1, the invention features a composition having particles comprising, by weight, 98% of SLPs used as lipidic carrier (with a weight ratio cholesterol acetate/Phospholipon® 90H 90:10) and 2% micronized budesonide. A solution containing 100 gram per litre of the combined lipids in isopropanol (heated at 55° C.), was spray dried to form lipid carrier microparticles with appropriate particle size for inhalation. The SLPs (carrier) are premixed with active micronized particles of budesonide for between 5 and 15 minutes in a mortar (with a spatula, without crushing), and then blended for between 5 and 30 minutes in a tumbling blender. 
     Example 7 
     According to example 1, the invention features a composition having particles comprising, by weight, 98% of SLPs used as lipidic carrier (with a weight ratio glycerol behenate/Phospholipon® 90H 90:10) and 2% micronized budesonide. A solution containing 100 gram per litre of the combined lipid in methylene chloride, was spray dried to form lipid carrier microparticles with appropriate particle size for inhalation. The SLPs (carrier) are premixed with active micronized particles of budesonide for between 5 and 15 minutes in a mortar (with a spatula, without crushing), and then blended for between 5 and 30 minutes in a tumbling blender. 
     Example 8 
     According to example 2, the invention features a lipid matrix composition having particles comprising, by weight, 98% of lipidic ingredients as fillers and 2% micronized budesonide, with a weight ratio cholesterol acetate/Phospholipon® 90H/budesonide 90:8:2), wherein the method of preparing the formulation comprises preparing a solution of cholesterol acetate, Phospholipon® 90H and budesonide in isopropanol, and spray drying to form active SLP matrix formulation with appropriate particle size for inhalation. 
     Example 9 
     According to example 2, the invention features a lipid matrix composition having particles comprising, by weight, 98% of lipidic ingredients as fillers and 2% micronized budesonide, with a weight ratio glycerol behenate/Phospholipon® 90H/budesonide 97.9:0.1:2), wherein the method of preparing the formulation comprises preparing a solution of glycerol behenate, Phospholipon® 90H and budesonide in methylene chloride, and spray drying to form active SLP matrix formulation with appropriate particle size for inhalation. 
     Example 10 
     This example illustrates another embodiment, wherein the formulation is based on blends of fine and coarse SLP, used as pharmaceutical carrier, and micronized active compounds. 
     Since the micronized drug particles are generally very cohesive and characterized by poor flowing properties, they are usually blended, in dry powder formulations, with coarse particles. It improves particles flowability during filling process and ensures accurate dosing of active ingredients. More over, it is known that a ternary component, constituted of fine particles carrier, can be added in order to reduce the force of adhesion between coarse carrier particles and active particles and give the most effective dry powder aerosol. 
     The fine spray-dried SLPs (about 2 μm mean diameter) and the coarse SLP (about 80 μm mean diameter), as carriers, are mixed for 10 minutes using a Turbula Mixer 2C tumbling blender. Then the micronized budesonide is added and the ternary blend is mixed for 60 minutes. 
     Example 11 
     This example illustrates another aspect of the invention : a lipid coating composition wherein each particle comprises, by weight, 2% of lipidic ingredients (with a weight ratio Phospholipon® 90H/cholesterol of about 25:75) and 98% of a micronized drug practically insoluble in the coating solution. 
     The method carried out for preparing this active lipid coating composition comprises the steps of:
         preparing a solution of cholesterol, a solution of Phospholipon® 90H, and a suspension of disodium cromoglycate in ethanol,   mixing them such that the total solute concentration is greater than 1 gram per litre, and   spray drying the resulting solution, using the modified Büchi mini spray dryer B-191 (Büchi laboratory-Techniques, Switzerland) to form active lipid coated particles.       

     Example 12 
     In order to confirm the promising in vitro deposition test results, two of the SLP compositions were selected on the basis of the aerodynamic behaviour and compared to Pulmicort® Turbuhaler® by an in vivo scintigraphic evaluation and a pharmacokinetic study of the bioavailability of inhaled budesonide after a single oral dose in six healthy volunteers. 
     The first formulation was a physical blend SLP formulation (PB). It consisted in a physical blend of 2% (by weight) micronized budesonide and 98% of SLPs used as carriers (with a weight ratio Phospholipon® 90H/cholesterol of 90:10). Size#3 HPMC capsules were loaded with 10.00 mg of powder (see example 1). 
     The second formulation was an active SLP composition formulated as a lipidic matrix (M), containing 2% budesonide, 8% Phospholipon®90H and 90% of cholesterol. Size#3 HPMC capsules were loaded with 10.00 mg of powder (see example 2). 
     The active SLPs (M) and the physical blend formulation (PB) were obtained by spray-drying an isopropanol solution containing the lipids and active compound, through a laboratory scale spray dryer as described in examples 1 and 2. 
     The third formulation was the comparator product, the Pulmicort Turbuhaler®. 
     The study design was an open single-dose, three-treatment, three-period cross-over study with a 7 days wash-out period between the three phases of the study. Approvals were obtained from the Ethics Committee of Erasme Hospital (Ref.: P2004/202) and the Belgian Minister of Social Affairs and Public Health (Ref.: EudraCT n° 2004-004658-14). 
     Scintigraphic images of the chest and lateral oropharynx were recorded immediately after the drug inhalation (DHD-SMV, Sopha Medical, France). The empty device, capsule, mouthpiece and exhalation filter were also counted. 
     Venous blood samples were collected at pre-dose and at 10, 20, 30, 40, 50 min, 1 h, 1 h30, 2 h, 2 h30, 3 h, 3 h30, 4 h, 4 h30, 5 h, 6 h post-dose. The concentration of budesonide was measured using a validated LC/MS-MS method (High-Performance Liquid Chromatography (HP 1100 series, Agilent Technologies, Belgium) and API3000 triple quadrupole mass spectrometer (Applied Biosystems—MDS Sciex, Concord, Canada). 
     For the physical blend formulation (PB), the drug was labeled by mixing it to a small amount of water containing  99m Tc pertechnetate. The water was removed by freeze drying, leaving the radiolabel attached to the drug particles and the radiolabelled active drug passed through a 315 μm sieve before being blended with the lipidic carrier. 
     The active SLP formulation (matricial formulation (M)) was radiolabelled by adding directly the water containing  99m Tc pertechnetate. 
     At last, a Pulmicort Turbuhaler® device was emptied and the spheres of budesonide were mixed with 99mTc in water until they were totally wet. After the freeze-drying, the device was re-filled with the radiolabelled powder and primed by firing 10 shots to waste. 
     In order to demonstrate the quality of the radiolabelling method, i.e. the particle physical characteristics were not modified by the radiolabelling and the radiolabel was effectively deposited at the surface of particles; experiments were carried out prior to the clinical part of the investigation. For each formulation, the particle size of the unlabelled drug (n=3) was determined and compared against the particle size distribution of the radiolabelled drug (n=3) and of the radiolabel (n=3). The measurements were made with a Multistage Liquid Impinger (MsLI, Copley instruments, U.K.) operating at an air flow rate corresponding to a pressure drop of 4kPa over each inhaler (Eur. Ph. 5 th  edition). The test was carried out at 100 L/min during 2.4 secondes and at 60 L/min during 4 seconds for the Cyclohaler® and the Pulmicort Turbuhaler® respectively. Drug and radiolabel content were determined by a validated analytical HPLC method and by gamma counting (Cobra gamma counter, Packard Bioscinece, UK), respectively. The fraction of drug or radiolabel, corresponding (by interpolation) to particles having an aerodynamic diameter inferior to 5 μm, was defined as the Fine Particle Dose (FPD) and was calculated as percentage of the nominal dose. 
     The results are summarized in Table 7. 
     
       
         
           
               
             
               
                 TABLE 7 
               
             
            
               
                   
               
               
                 Radiolabelling validation data (MsLI, n = 3) 
               
            
           
           
               
               
            
               
                   
                 FPD (% nominal dose) 
               
            
           
           
               
               
               
               
               
            
               
                   
                   
                 drug before 
                 drug after 
                   
               
               
                   
                 Formulations 
                 labelling 
                 labelling 
                 radiolabel 
               
               
                   
                   
               
               
                   
                 PB 
                 58 ± 3 
                 55 ± 2 
                 59 ± 3 
               
               
                   
                 M 
                 47 ± 1 
                 44 ± 1 
                 48 ± 3 
               
               
                   
                 Pulmicort 
                 34 ± 2 
                 — 
                 — 
               
               
                   
                   
               
            
           
         
       
     
     The validation data demonstrated that the radiolabelling process did not significantly alter the particle size distribution and was considered suitable for use for the SLP, contrary to the Pulmicort Turbuhaler® radiolabelling method. Therefore, the marketed formulation was used without being radiolabelled during the clinical study and thus was not evaluated by scintigraphy. 
     Scintigraphic images showing deposition patterns of the upper part of the body of one subject for each of the SLP formulations are shown in  FIG. 6 . 
     The fractionation of the delivered dose between the whole lungs, oropharynx, inhaler device and exhalation filter for SLP products is shown in Table 8. 
     The lung deposition of the comparator formulation via this scintigraphy technique could not be assessed. However, as a benchmark product, Pulmicort® has been widely studied and evaluated in numerous and various studies; Budesonide lung deposition from the Turbuhaler DPI was shown to be about 30%. Thus, the results were in good agreement with the in vitro fine particle assessment. 
     
       
         
           
               
             
               
                 TABLE 8 
               
             
            
               
                   
               
               
                 Mean fractionation of the dose between lungs, oropharynx, 
               
               
                 device and exhaled air filter, for the PB and M formulations 
               
               
                 in 6 healthy volunteers. 
               
            
           
           
               
               
               
               
            
               
                   
                 Deposition 
                 Formulation 
                   
               
            
           
           
               
               
               
               
               
            
               
                   
                 area 
                 PB 
                 M 
                 P-value 
               
               
                   
                   
               
               
                   
                 Lungs 
                 62.8 ± 4.9 
                 49.9 ± 3.7 
                  0.003 (**) 
               
               
                   
                 Oropharynx 
                 26.8 ± 3.8 
                 38.0 ± 3.1 
                  0.006 (**) 
               
               
                   
                 Device 
                 10.4 ± 2.6 
                 12.1 ± 2.2 
                  0.04 (*) 
               
               
                   
                 Exhaled air 
                 0.13 ± 0.08 
                 0.11 ± 0.07 
                 &gt;0.05 (NS) 
               
               
                   
                   
               
               
                   
                 Data are expressed as percentage 
               
               
                   
                 (**): p &lt; 0.01 
               
               
                   
                 (*): p &lt; 0.05 
               
               
                   
                 (NS): not significantly different 
               
            
           
         
       
     
     The quantification of plasma levels of budesonide (corresponding practically to the pulmonary absorption) is illustrated in  FIG. 7 . 
     AUCs were found to be significantly higher for PB and M formulations than for the Pulmicort Turbuhaler® (p&lt;0.05). The pharmacokinetic data were also in compliance with the in vitro fine particle doses, as a higher drug deposition induces higher plasma drug concentration and AUCs values. 
     Example 13 
     This example illustrates the use of lipid compositions for formulations with particularly high drug content (in this example up to 98% drug). Lipid compositions (cholesterol—Phospholipon 90H blends) were used for coating tobramycin particles in order to improve drug targeting to the lung. Lipid deposition results in a modification of the surface properties of micron-sized tobramycin particles, which enables deep deposition in the lung. 
     Suspensions with different concentrations of tobramycin and lipids were prepared. While tobramycin is practically insoluble in isopropanol (0.05 mg/ml), lipids are dissolved in it and coat the micron-sized particles during atomisation using a modified Büchi Mini Spray Dryer B-191a (Büchi laboratory-Techniques, Switzerland). 
     Firstly, lipids were dissolved in 50 ml isopropanol. Then, tobramycin was added and the suspension was homogenized with a CAT high speed homogenizer X620 (CAT M. Zipperer, Staufen, Germany) at 24000 rpm for 10 minutes. The suspensions were then spray dried with constant stirring. Table 9 gives an overview comparison of some powder formulations evaluated. 
     
       
         
           
               
             
               
                 TABLE 9 
               
             
            
               
                   
               
               
                 Composition of the spray dried suspensions used for 
               
               
                 the preparation of the coated tobramycin DPI formulations 
               
               
                 and lipid content of the formulations (dried forms). 
               
            
           
           
               
               
               
            
               
                   
                 Dried Forms 
                   
               
            
           
           
               
               
               
               
            
               
                   
                 Suspensions 
                   
                 Cholesterol/ 
               
            
           
           
               
               
               
               
               
            
               
                   
                 Tobramycin 
                 Lipids 
                 Lipids 
                 Phospholipon 
               
               
                   
                 (% w/v) 
                 (% w/v) 
                 (%)* 
                 (%) (w/w) 
               
               
                   
                   
               
            
           
           
               
               
               
               
               
               
            
               
                   
                 F1 
                 2 
                 0.10 
                 5 
                 75/25 
               
               
                   
                 F2 
                 5 
                 0.25 
                 5 
                 75/25 
               
               
                   
                 F3 
                 10 
                 0.50 
                 5 
                 75/25 
               
               
                   
                 F4 
                 5 
                 0.10 
                 2 
                 75/25 
               
               
                   
                 F5 
                 5 
                 0.50 
                 10 
                 75/25 
               
               
                   
                 F6 
                 5 
                 0.25 
                 5 
                 66/34 
               
               
                   
                 F7 
                 5 
                 0.25 
                 5 
                 90/10 
               
               
                   
                   
               
               
                   
                 *Data expressed in percentage of tobramycin&#39;s weight. 
               
            
           
         
       
     
     Particle size distribution results obtained by laser diffractometry for the coated particles are given in Table 10. 
     
       
         
           
               
             
               
                 TABLE 10 
               
             
            
               
                   
               
               
                 Particle size characteristics of the formulations (mean ± S.D., 
               
               
                 n = 3) measured with the Mastersizer 2000 ® laser 
               
               
                 diffractometer in dry powder form. 
               
            
           
           
               
               
               
               
               
            
               
                   
                   
                 d (0.5) 
                 D [4, 3] 
                 % &lt;5.0 μm 
               
               
                   
                   
               
               
                   
                 Tobra μ* 
                 1.29 ± 0.02 
                 1.54 ± 0.01 
                 99.3 ± 0.2 
               
               
                   
                 F1 
                 1.24 ± 0.02 
                 1.46 ± 0.03 
                 99.8 ± 0.1 
               
               
                   
                 F2 
                 1.28 ± 0.03 
                 1.48 ± 0.05 
                 99.7 ± 0.1 
               
               
                   
                 F3 
                 1.23 ± 0.01 
                 1.46 ± 0.01 
                 99.6 ± 0.1 
               
               
                   
                 F4 
                 1.27 ± 0.01 
                 1.50 ± 0.01 
                 99.6 ± 0.1 
               
               
                   
                 F5 
                 1.38 ± 0.03 
                 1.54 ± 0.04 
                 99.9 ± 0.1 
               
               
                   
                 F6 
                 1.38 ± 0.02 
                 1.55 ± 0.01 
                 99.8 ± 0.1 
               
               
                   
                 F7 
                 1.29 ± 0.01 
                 1.50 ± 0.01 
                 99.6 ± 0.1 
               
               
                   
                   
               
               
                   
                 *Micronized tobramycin. 
               
            
           
         
       
     
     The results show that the median particle sizes appeared to be similar for all powder formulations exhibiting a d(0.5) value of about 1.2-1.4 μm. 
     The particle size distributions of the formulations are unimodal, narrow and range from 0.24 to 6 μm, with more than 90% of particles having a diameter below 2.8 μm, which is required for an optimal deep lung deposition. The mass median diameters and the volume mean diameters of the formulations are very tiny and ranged from 1.23 μm to 1.38 μm and from 1.46 μm to 1.55 μm, respectively. 
     There are no major differences between lipid-coated formulations and the micronized tobramycin. So, the coating of the micronized tobramycin particles with lipidic excipients does not affect the particle size of the raw material. 
     The Fine Particle Dose has been determined by the method described in the European Pharmacopoeia 4 for the aerodynamic assessment of fine particle, using Apparatus C—Multi-stage Liquid Impinger (MsLI) 
     A dry powder inhalation device (Cyclohaler®, Novartis, Switzerland) was filled with a No. 3 HPMC capsule (Capsugel, France) loaded with 15 mg powder. 
     The flow rate was adjusted to a pressure drop of 4 kPa, as typical for inspiration by a patient, resulting in a flow rate of 100 l/min during 2.4 seconds. 
     At least 3 FPD determinations were performed on each formulation and analysis were carried out by a suitable and validated analytical HPLC method. In order to increase the UV absorptivity of the molecule, a derivatization method was applied. The suitable and validated quantification method is described in the USP 25. 
     The HPLC system consisted of a High Performance Liquid Chromatography system (HP 1100 series, Agilent technologies, Belgium), equipped with a quartenary pump, an autosampler and a variable wavelength UV detector set at 360 nm. The separation system was a 39 cm×3.9 mm stainless steel (5 μm particle size) reversed-phase C18 column (Alltima, Alltech, Belgium). Samples of 20 μl volume were injected. The mobile phase was prepared by dissolving 2 g of Tris(hydroxymethyl)aminomethane in 800 ml of water. After this, 20 ml of H 2 SO 4  1 N was added and then the solution was diluted with acetonitrile to obtain 2 l, mixed and passed through a filter of 0.2 μm porosity. The flow rate was 1.2 ml/min. 
     The mass of test substance deposited on each stage was determined from the HPLC analysis of the recovered solutions. Starting at the filter, a cumulative mass deposition (undersize in percentage) vs. cut-off diameter of the respective stages was derived and the Fine Particle Dose (FPD) was calculated by interpolation the mass of active ingredient less than 5 μm. 
     The FPD is the dose (expressed in weight for a given nominal dose) of particles having an aerodynamic diameter inferior to 5 μm. It is considered to be directly proportional to the amount of drug able to reach the pulmonary tract in vivo, and consequently, the higher the value FPD, the higher the estimated lung deposition. 
     The Fine Particle Fraction (FPF) is the dose (expressed in weight %) of particles having an aerodynamic diameter inferior to 5 μm in relation to the nominal dose (FPD/loaded dose×100). 
     The fine particle assessment results for the formulations are summarized in Table 11. 
     
       
         
           
               
             
               
                 TABLE 11 
               
             
            
               
                   
               
               
                 In vitro deposition study, with formulation given in example 3 vs. 
               
               
                 micronized tobramycin (raw material) (loaded dose = 15 mg, n = 3). 
               
            
           
           
               
               
               
               
            
               
                   
                 Formulations 
                 FPD (mg) 
                 FPF (%) 
               
               
                   
                   
               
               
                   
                 Tobra μ 
                 7.2 ± 0.6 
                 48.1 ± 0.4 
               
               
                   
                 F1 
                 9.8 ± 0.5 
                 65.1 ± 0.5 
               
               
                   
                 F2 
                 10.2 ± 0.2  
                 68.2 ± 0.2 
               
               
                   
                 F3 
                 10.3 ± 0.8  
                 68.3 ± 0.8 
               
               
                   
                 F4 
                 7.6 ± 0.5 
                 50.5 ± 0.5 
               
               
                   
                 F5 
                 9.1 ± 0.2 
                 60.8 ± 0.3 
               
               
                   
                 F6 
                 8.7 ± 0.4 
                 57.7 ± 0.4 
               
               
                   
                 F7 
                 8.7 ± 0.1 
                 57.9 ± 0.2 
               
               
                   
                   
               
            
           
         
       
     
     The FPF, which is around 48% for the uncoated micronized tobramycin, is increased by up to about 68% for the most effective lipid-coated formulation, in terms of deep lung penetration. The evaluation of the influence of the coating level (F4, F2 and F5, 2, 5 and 10% w/w lipids, respectively) showed that the deposition of only 5% w/w lipids (in the dry basis) is sufficient in order to improve particle dispersion properties during inhalation. These results reveal the need to add sufficient amounts of covering material in order to significantly modify particle surface properties and reduce their tendency to agglomeration, while limiting the lipid level in the formulations in order to avoid any undesirable sticking and to allow the delivery of more of the active drug to the deep lung. 
     It seems that a cholesterol/Phospholipon 90H ratio of 75:25 is the most appropriate one as it reveals the best deposition pattern and gives the highest FPF. 
     The highest FPF values, of about 68%, were obtained for the formulations prepared by spray drying from suspensions containing 2, 5 or 10% w/v of tobramycin and coated with 5% of lipids with the most appropriate cholesterol/Phospholipon 90H ratio of 75:25. 
     These FPF results are especially elevated and very promising comparing to the FPF value of the commercially available tobramycin nebulizers product Tobi®, which contains 300 mg of tobramycin free base in 5 ml of sodium chloride at pH 6.0. An in vivo study on this product has shown that, after 15 minutes of nebulization, only 5% of the nominal dose was deposited in the lung. 
     These new lipid-coated tobramycin DPI formulations, based on the use of very low excipient levels (drug levels up to 98% and even more) and presenting very high lung deposition properties offer very important perspectives in improving the delivery of drugs to the pulmonary tract. These formulations are more particularly useful for drugs that are active at relatively high doses, such as antibiotics, as they permit the delivery of a high concentration of antibiotic directly to the site of infection while minimizing systemic exposition. A reduction in administration time and in systemic side effects allows improved suitability of these formulations for patients.