Encapsulation of water-soluble drugs by an o/o/o-solvent extraction microencapsulation method.

A new o/o/o-solvent extraction microencapsulation method based on less toxic solvents is presented in this study. The drug is dissolved/dispersed into a poly(D,L-lactide)/or poly (D,L-lactide-co-glycolide) (PLGA) solution in a water-miscible organic solvent (e.g., dimethylsulfoxide or 2-pyrrolidone) (o(1)), followed by emulsification into an oil phase (o(2)) (e.g., peanut oil). This emulsion is added to the external phase (o(3)) to solidify the drug-containing polymer droplets. The polymer solvent and the oil are extracted in an external phase (o(3)) (e.g., ethanol), which is a nonsolvent for the polymer and miscible with both the polymer solvent and the oil. One major advantage of this method is the reduced amount of solvent/nonsolvent volumes. In addition, very high encapsulation efficiencies were achieved at polymer concentration of 20%, w/w for all investigated polymers and o(1)/o(2) phase ratios with ethanol as the external (o(3)) phase. The encapsulation efficiency was very low (<20%) with water as external phase. The particle size of the microparticles increased with increasing polymer concentration and o(1)/o(2) phase ratio and larger microparticles were obtained with 2-pyrrolidone compared to dimethylsulfoxide as polymer solvent (o(1)). After an initial burst, in vitro drug release from the microparticles increased for the investigated polymer as follows: Resomer(®) RG 506>RG 756>R 206. A third more rapid release phase was observed after 6 weeks with Resomer(®) RG 506 due to polymer degradation. Similar drug release patterns were obtained with the o/o/o and w/o/w multiple emulsion methods because of similar porous structures. This new method has the advantages of less toxic solvents, much lower preparation volume and solvent consumption and high encapsulation efficiencies when compared to the classical w/o/w method.

Drug release from and sterilization of in situ cubic phase forming monoglyceride drug delivery systems.

Since a monoglyceride-based cubic phase is too viscous to be injected parenterally, mixtures of monoglyceride, water and water-miscible cosolvents were investigated as low viscosity injectable in situ cubic phase-forming formulations. Upon contact with the release medium, a highly viscous cubic phase formed rapidly and served as an extended release matrix for the oligonucleotide drug. Extended drug release was obtained with all formulations. The drug release followed the square root of time relationship indicating a diffusion-controlled release mechanism. The release depended on the type of cosolvent and followed the order of ethanol>PEG 300>2-pyrrolidone>DMSO. Higher water or monoglycerides contents decreased the drug release because of an increased viscosity and increased swollen matrix thickness. The bioburden of different commercially available monoglycerides and of the prepared in situ cubic phase-forming formulations met USP XXIII requirements. Monoglycerides can be successfully sterilized by gamma irradiation or by autoclaving and the in situ cubic phase-forming formulations by autoclaving and aseptic filtration. The monoglycerides and in situ cubic phase-forming formulations retained their phase behaviour and release properties after sterilization.

Effect of water-soluble polymers on the physical stability of aqueous polymeric dispersions and their implications on the drug release from coated pellets.

PURPOSE: To investigate the physical stability and drug release-related properties of the aqueous polymer dispersions Kollicoat((R)) SR 30 D and Aquacoat((R)) ECD (an ethylcellulose-based dispersion) in the presence water-soluble polymers (pore formers) with special attention to the potential flocculation of the polymer dispersions. METHODS: A precise characterization of the flocculation phenomena in undiluted samples was monitored with turbidimetric measurements using the Turbiscan Lab-Expert. Theophylline or propranolol HCl drug-layered pellets were coated with Kollicoat((R)) SR 30 D and Aquacoat((R)) ECD by the addition of water-soluble polymers polyvinyl pyrrolidone (Kollidon((R)) 30 and 90 F), polyvinyl alcohol-polyethylene glycol graft copolymer (Kollicoat((R)) IR), and hydroxypropyl methylcellulose (Pharmacoat((R)) 603 or 606) in a fluidized bed coater Glatt GPCG-1 and drug release was performed according to UPS paddle method. RESULTS: Stable dispersions were obtained with both Kollicoat((R)) SR 30 D (a polyvinyl acetate-based dispersion) and Aquacoat((R)) ECD with up to 50% hydrophilic pore formers polyvinyl alcohol-polyethylene glycol graft copolymer (Kollicoat((R)) IR) and polyvinyl pyrrolidone (Kollidon((R)) 30). In general, Kollicoat((R)) SR 30 D was more stable against flocculation than Aquacoat((R)) ECD. Stable dispersions were also obtained with higher amounts of water-soluble polymer or by reducing the concentration of the polymer dispersion. Flocculated dispersions resulted in porous films and, thus, in a sharp increase in drug release. CONCLUSIONS: Kollicoat((R)) SR 30 D was more resistant to flocculation upon addition of water-soluble polymers than Aquacoat((R)) ECD. The continuous adjustment of drug release from Kollicoat((R)) SR 30-coated pellets was possible with Kollicoat((R)) IR amounts over a broad range.

Reduction in burst release of PLGA microparticles by incorporation into cubic phase-forming systems.

A high initial burst release of an phosphorothioate oligonucleotide drug from poly(lactide-co-glycolide) (PLGA) microparticles prepared by the w/o/w solvent extraction/evaporation was reduced by incorporating the microparticles into the following glycerol monooleate (GMO) formulations: 1) pure molten GMO, 2) preformed cubic phase (GMO+water) or 3) low viscosity in situ cubic phase-forming formulations (GMO+water+cosolvent). The in situ cubic phase-forming formulations had a low viscosity in contrast to the first two formulations resulting in good dispersability of the microparticles and good syringability/injectability. Upon contact with an aqueous phase, a highly viscous cubic phase formed immediately entrapping the microparticles. A low initial burst and a continuous extended release over several weeks was obtained with all investigated formulations. The drug release profile could be well controlled by the cosolvent composition with the in situ systems.

pH-independent pulsatile drug delivery system based on hard gelatin capsules and coated with aqueous dispersion Aquacoat ECD.

The objective of this study was to develop a rupturable, capsule-based pulsatile drug delivery system with pH-independent properties prepared using aqueous coating. The drug release is induced by rupturing of the top-coating, resulting by expanding of swellable layer upon water penetration through the top-coating. Croscarmellose sodium (AcDiSol) is a preferable superdisintegrant compared to low substituted hydroxypropylcellulose (L-HPC) and sodium starch glycolate (Explotab), because of controlled lag time, followed by a quick and complete drug release. However, due to its anionic character, AcDiSol showed pH-dependent swelling characteristics (pH 7.4 > 0.1N HCl) resulting in a pH-dependent lag time. The pH dependency could be eliminated by the addition of fumaric acid to the swelling layer, which allowed to keep an acidic micro-environment. Formation of the rupturable top-coating was successfully performed using an aqueous dispersion of ethylcellulose (Aquacoat) ECD), whereby sufficient drying during the coating was needed to avoid swelling of the AcDiSol layer. A higher coating level was required, when aqueous dispersion was used, compared to organic coatings. However, an advantageous aspect of the aqueous coating was the lower sensitivity of the lag time to a deviation in the coating level.

Development of pulsatile multiparticulate drug delivery system coated with aqueous dispersion Aquacoat ECD.

The objective of this study was to develop and evaluate a pulsatile multiparticulate drug delivery system (DDS), coated with aqueous dispersion Aquacoat ECD. A rupturable pulsatile drug delivery system consists of (i) a drug core; (ii) a swelling layer, comprising a superdisintegrant and a binder; and (iii) an insoluble, water-permeable polymeric coating. Upon water ingress, the swellable layer expands, resulting in the rupturing of outer membrane with subsequent rapid drug release. Regarding the cores, the lag time was shorter, when 10% (w/w) theophylline was layered on sugar cores compared with cores consisting of 100% theophylline. Regarding swelling layer, the release after lag time was fast and complete, when cross-linked carboxymethyl cellulose (AcDiSol) was used as a swelling agent. In contrast, a sustained release was achieved after the lag time, when low-substituted hydroxypropyl cellulose (L-HPC) and sodium starch glycolate (Explotab) were used as swelling agents. The optimal level of AcDiSol to achieve a fast and complete release after the lag time was 26% (w/w) (based on the weight of the coated pellets) for poorly soluble theophylline and 48% (w/w) for highly soluble propranolol HCl. The lag time can be controlled by the coating level of an outer membrane and increased with increasing coating level of the outer membrane. Outer membrane, formed using aqueous dispersion Aquacoat ECD was brittle and ruptured sufficiently to ensure fast drug release, compared to ethylcellulose membrane formed using organic solution. The addition of talc led to increase brittleness of membrane and was very advantageous because of (i) reduced sensitivity of lag time on variations in the coating level and (ii) fast and complete drug release. Drug release starts only after rupturing of outer membrane, which was illustrated by microscopical observation of pellet during release.

Development of pulsatile release tablets with swelling and rupturable layers.

A tablet system consisting of cores coated with two layers of swelling and rupturable coatings was prepared and evaluated as pulsatile drug delivery system. Cores containing buflomedil HCl as model drug were prepared by direct compression of different ratios of spray-dried lactose and microcrystalline cellulose and were then coated sequentially with an inner swelling layer containing a superdisintegrant (croscarmellose sodium) and an outer rupturable layer of ethylcellulose. The effect of core composition, level of swelling layer and rupturable coating, and magnesium stearate in rupturable layer was investigated. Mechanical properties of ethylcellulose films in the dry and wet state were characterized with a puncture test. Rupture and dissolution tests were performed using the USP XXIV paddle method at 50 rpm in 0.1 N HCl. The lag time of the pulsatile release tablets decreased with increasing amount of microcrystalline cellulose in the cores and increased with increasing levels of both swelling layer and rupturable ethylcellulose coating. Increasing levels of the ethylcellulose coating retarded the water uptake and thus prolonged the lag time. Addition of magnesium stearate to the ethylcellulose coating lowered the mechanical strength of the film and improved the robustness of the system.

Improvement in the disintegration of shellac-coated soft gelatin capsules in simulated intestinal fluid.

Shellac is a natural enteric polymer, which results in good gastric resistance; however, it often dissolves too slowly in intestinal fluids. The objective of this study was to improve the disintegration of shellac-coated soft gelatin capsules in simulated intestinal fluids (phosphate buffer pH 6.8) through the addition of pore-formers, such as organic acids and hydrophilic polymers, while retaining gastric resistance. The mechanical properties (% elongation at rupture, puncture strength at break and modulus at puncture), media uptake and weight loss of shellac films were determined upon exposure in 0.1 N HCl and/or phosphate buffer pH 6.8. Organic acids (e.g., sorbic acid) acted as plasticizers, they reduced the glass transition temperature of ethanol-cast shellac films. The addition of additives effectively decreased the disintegration times in phosphate buffer pH 6.8, while the behavior in 0.1 N HCl remained unchanged. In addition, the hardness and disintegration of shellac-coated soft gelatin capsules were monitored through the whole disintegration experiments. The best disintegration was achieved with sorbic acid as pore-former. Sorbic acid remained in the shellac coating at low pH, but leached in pH 6.8 buffer, thus resulting in good gastric resistance and rapid disintegration in simulated intestinal fluids. The disintegration time of ethanolic shellac-coated soft gelatin capsules decreased with increasing amount of pore-former. The slow disintegration of aqueous shellac-coated soft gelatin capsules could be also improved by the addition of hydrophilic polymers, such as hydroxypropyl methylcellulose (HPMC). However, higher HPMC concentrations were required when compared to sorbic acid.