Mechanistic explanation of the (up to) 3 release phases of PLGA microparticles: Monolithic dispersions studied at lower temperatures.

The aim of this study was to better understand the underlying drug release mechanisms in poly(lactic-co-glycolic acid) (PLGA) microparticles in which the drug is dispersed in the form of tiny particles ("monolithic dispersions"). Differently sized diprophylline-loaded microparticles were prepared using a solid-in-oil-in-water solvent extraction/evaporation technique. The microparticles were characterized before and after exposure to phosphate buffer pH 7.4 at 4, 20 and 37 °C. In vitro drug release was measured from ensembles and single microparticles. GPC, DSC, SEM, gravimetric analysis, drug solubility measurements and optical microscopy were used to elucidate the importance of polymer swelling & degradation, drug dissolution and diffusion. The diprophylline was initially homogeneously distributed throughout the microparticles in the form of tiny crystals. The burst release (1st phase) was strongly temperature-dependent and likely attributable to the dissolution of drug crystals with direct surface access (potentially via tiny pores). The about constant release rate during the 2nd phase also strongly depended on the temperature. It can probably be explained by the dissolution of drug crystals in surface near regions undergoing local swelling. During the observation period, the 3rd (again rapid) drug release phase was only observed at 37 °C, and seems to be caused by substantial PLGA swelling throughout the entire microparticles. This phase starts as soon as a critical polymer molecular weight of about 25 kDa is reached: Significant amounts of water penetrate into the systems, dissolving the remaining diprophylline crystals and substantially increasing the mobility of the dissolved drug molecules. Thus, this study provides additional experimental evidence (obtained at lower temperatures) confirming the hypothesized root causes for drug release from PLGA microparticles containing dispersed drug particles.

Mechanistic explanation of the (up to) 3 release phases of PLGA microparticles: Diprophylline dispersions.

The aim of this study was to better understand the root causes for the (up to) 3 drug release phases observed with poly (lactic-co-glycolic acid) (PLGA) microparticles containing diprophylline particles: The 1st release phase ("burst release"), 2nd release phase (with an "about constant release rate") and 3rd release phase (which is again rapid and leads to complete drug exhaust). The behavior of single microparticles was monitored upon exposure to phosphate buffer pH 7.4, in particular with respect to their drug release and swelling behaviors. Diprophylline-loaded PLGA microparticles were prepared with a solid-in-oil-in-water solvent extraction/evaporation method. Tiny drug crystals were rather homogeneously distributed throughout the polymer matrix after manufacturing. Batches with "small" (63 µm), "medium-sized" (113 µm) and "large" (296 µm) microparticles with a practical drug loading of 5-7% were prepared. Importantly, each microparticle releases the drug "in its own way", depending on the exact distribution of the tiny drug crystals within the system. During the burst release, drug crystals with direct surface access rapidly dissolve. During the 2nd release phase tiny drug crystals (often) located in surface near regions which undergo swelling, are likely released. During the 3rd release phase, the entire microparticle undergoes substantial swelling. This results in high quantities of water present throughout the system, which becomes "gel-like". Consequently, the drug crystals dissolve, and the dissolved drug molecules rather rapidly diffuse through the highly swollen polymer gel.

Towards a better understanding of the different release phases from PLGA microparticles: Dexamethasone-loaded systems.

Dexamethasone-loaded, poly(lactic-co-glycolic acid) (PLGA) microparticles were prepared using an oil-in-water solvent extraction/evaporation method. The drug loading was varied from 2.4 to 61.9%, keeping the mean particle size in the range of 52-61µm. In vitro drug release was characterized by up to 3 phases: (1) an (optional) initial burst release, (2) a phase with an about constant drug release rate, and (3) a final, again rapid, drug release phase. The importance and durations of these phases strongly depended on the initial drug loading. To better understand the underlying mass transport mechanisms, the microparticles were thoroughly characterized before and after exposure to the release medium. The initial burst release seems to be mainly due to the dissolution of drug particles with direct access to the microparticles' surface. The extent of the burst was negligible at low drug loadings, whereas it exceeded 60% at high drug loadings. The second release phase seems to be controlled by limited drug solubility effects and drug diffusion through the polymeric systems. The third drug release phase is likely to be a consequence of substantial microparticle swelling, leading to a considerable increase in the systems' water content and, thus, fundamentally increased drug mobility.

Oil-cyclodextrin based beads for oral delivery of poorly-soluble drugs.

The main interest of cyclodextrins results from their ability to form inclusion complexes with hydrophobic molecules. This property is employed in pharmaceutical industry to facilitate the formulation of poorly-soluble and/or fragile drugs. Cyclodextrins are also used to form or stabilise dispersed systems. An original multiparticulate system named "beads" is obtained thanks to the interactions occurring between the molecules of α cyclodextrin and the triglycerides of vegetable oils. Beads are prepared by a simple process involving the external shaking of a mixture of an aqueous solution of α cyclodextrin with soybean oil. This is done without any organic solvent or surface-active agent. Once freezedried, beads have a diameter of 1.6 mm and a high lipid content. They consist in a partially crystalline matrix of cyclodextrin surrounding microdomains of oil. The coating of beads with a layer of α cyclodextrin improves their resistance in gastro- intestinal fluids and prolongs the release of drugs. Beads can also be manufactured from mineral oils with α cyclodextrin and from silicone oils with γ cyclodextrin. Poorly-soluble drugs which do not form inclusion complexes with α cyclodextrin are encapsulated in beads with high efficiency and drug loading. In rats, the oral bioavailability of isotretinoin is twofold enhanced with uncoated beads as compared to the lipid content of a soft capsule. The relative oral bioavailability of indomethacin is improved with both coated and uncoated beads versus a commercial hard capsule. Beads demonstrate an important potential for the encapsulation of poorly-soluble and/or fragile compounds and their delivery by oral route.

Beads made of α-cyclodextrin and soybean oil: the drying method influences bead properties and drug release.

Freeze-dried beads made of α-cyclodextrin and soybean oil were reported previously as an efficient system for the oral delivery of lipophilic drugs. In the present study, oven-drying was evaluated as another method for drying beads. Oven-drying was optimised and the properties of the resulting beads were assessed. The behavior of oven-dried beads and the release of indomethacin from these beads were evaluated in vitro in simulated gastrointestinal fluids and compared with those of freeze-dried beads. The stability of freeze-dried and oven-dried unloaded beads stored at 25°C for 12 months and at 40°C for 6 months in closed and open vials was also studied by different techniques. An oven-drying time of 6 hours at 25°C was chosen as optimal conditions. Oven-dried beads exhibited a sticky texture making them difficult to handle. They were harder, less fragile and smaller than the freeze-dried ones. The characteristics of oven-dried beads make them more resistant in vitro even in media containing bile salt. The rate of indomethacin release from oven-dried beads was much slower than that from the freeze-dried ones. Whatever the drying method, beads must be stored at room temperature protected from humidity. However, no products of oil degradation were detected with both kinds of beads. This work clearly emphasized that the drying method of the beads had a strong influence on their properties, behavior in simulated gastrointestinal fluids and drug release.

Formulations based on alpha cyclodextrin and soybean oil: an approach to modulate the oral release of lipophilic drugs.

The purpose of this work was to investigate the potential of α-cyclodextrin combined to soybean oil-based formulations to modulate the release of a model drug, indomethacin. Dry emulsion, naked and coated beads were prepared from the same initial formulation using the same manufacturing process. Dry emulsion was selected to accelerate drug release while beads coated with α-cyclodextrin were designed to sustain it. Indomethacin-loaded systems were prepared, characterised and evaluated in vitro. Pharmacokinetic studies were performed in fasted and fed rats. The presence of the α-cyclodextrin coat was confirmed by confocal microscopy, and an increase of the mass and diameter of the beads. The layer of α-cyclodextrin improved their resistance in simulated gastro-intestinal fluids. In vitro, the dissolution of indomethacin was slower with coated beads than with emulsion and naked beads. Lipid-based formulations showed an increase of relative bioavailability of IND versus Indocid®. Whatever the formulation, greater and faster release of indomethacin was noticed in sodium taurocholate-rich medium and in fed rats. Compared to naked beads, an increased Cp(max) with a shorter T(max) was observed with the emulsion while T(max) and MRT were increased and Cp(max) reduced with the coated beads. Interestingly, formulations based on alpha cyclodextrin and soybean oil can modify the release of a lipophilic drug depending on the system formed.