Multi-Layer Self-Nanoemulsifying Pellets: an Innovative Drug Delivery System for the Poorly Water-Soluble Drug Cinnarizine.

Beside their solubility limitations, some poorly water-soluble drugs undergo extensive degradation in aqueous and/or lipid-based formulations. Multi-layer self-nanoemulsifying pellets (ML-SNEP) introduce an innovative delivery system based on isolating the drug from the self-nanoemulsifying layer to enhance drug aqueous solubility and minimize degradation. In the current study, various batches of cinnarizine (CN) ML-SNEP were prepared using fluid bed coating and involved a drug-free self-nanoemulsifying layer, protective layer, drug layer, moisture-sealing layer, and/or an anti-adherent layer. Each layer was optimized based on coating outcomes such as coating recovery and mono-pellets%. The optimized ML-SNEP were characterized using scanning electron microscopy (SEM), differential scanning calorimetry (DSC), X-ray diffraction (XRD), in vitro dissolution, and stability studies. The optimized ML-SNEP were free-flowing, well separated with high coating recovery. SEM showed multiple well-defined coating layers. The acidic polyvinylpyrrolidone:CN (4:1) solution presented excellent drug-layering outcomes. DSC and XRD confirmed CN transformation into amorphous state within the drug layer. The isolation between CN and self-nanoemulsifying layer did not adversely affect drug dissolution. CN was able to spontaneously migrate into the micelles arising from the drug-free self-nanoemulsifying layer. ML-SNEP showed superior dissolution compared to Stugeron® tablets at pH 1.2 and 6.8. Particularly, on shifting to pH 6.8, ML-SNEP maintained > 84% CN in solution while Stugeron® tablets showed significant CN precipitation leaving only 7% CN in solution. Furthermore, ML-SNEP (comprising Kollicoat® Smartseal 30D) showed robust stability and maintained > 97% intact CN within the accelerated storage conditions. Accordingly, ML-SNEP offer a novel delivery system that combines both enhanced solubilization and stabilization of unstable poorly soluble drugs.

Micropellets coated with Kollicoat® Smartseal 30D for taste masking in liquid oral dosage forms.

The objective of this study was to develop delivery systems for taste masking based on multiparticulates coated with Kollicoat® Smartseal 30D formulated as liquid oral suspensions. Coating of particles containing bitter drugs with Kollicoat® Smartseal reduced drug leaching into aqueous medium, especially when increasing pH, therefore can be used for the formulation of liquid dosage forms. Application of an intermediate layer of ion exchange resins between drug layer and coating can further decrease drug leaching into aqueous vehicle that is beneficial in terms of taste masking. Using optimized compositions of liquid vehicles such as addition of sugar alcohols and ion exchange resin, reconstitutable or ready-to-use liquid dosage forms with micropellets can be developed with bitter taste protection after redispersion lasting longer than 3 weeks, which exceeds the usual period of application.

Curing mechanism of flexible aqueous polymeric coatings.

The objective of this study was to explain curing phenomena for pellets coated with a flexible polymeric coating based on poly(vinyl acetate) (Kollicoat® SR 30D) with regard to the effect of starter cores, thickness of drug layer, adhesion of coating to drug-layered-cores as well as coating properties. In addition, appropriate approaches to eliminate the curing effect were identified. Sugar or MCC cores were layered with the model drugs carbamazepine, theophylline, propranolol HCl, tramadol HCl and metoprolol HCl using HPMC (5 or 25% w/w, based on drug) as a binder. Drug-layered pellets were coated with Kollicoat® SR 30D in a fluidized bed coater using TEC (10% w/w) as plasticizer and talc (35-100% w/w) as anti-tacking agent. Drug release, pellet properties (morphology, water uptake-weight loss and osmolality) and adhesion of the coating to the drug layer were investigated as a function of curing at 60°C or 60°C/75% RH for 24h. The film formation of the aqueous dispersion of Kollicoat® SR 30D was complete, and therefore, a strong curing effect (decrease in drug release) at elevated temperature and humidity (60°C/75% RH) could not be explained by the well-known hydroplasticization and the further gradual coalescence of the colloidal polymer particles. According to the provided mechanistic explanation, the observed curing effect was associated with (1) high flexibility of coating, (2) adhesion between coating and drug layer, (3) water retaining properties of the drug layer, and (4) osmotically active cores. Unwanted curing effects could be minimized/eliminated by the addition of talc or/and pore-forming water soluble polymers in the coating, increasing binder amount or applying an intermediate coating, by increasing the thickness of drug layer or using non-osmotic cores. A new insight into curing phenomena mainly associated with the adhesion between drug layer and coating was provided. Appropriate approaches to avoid unwanted curing effect were identified.

Reduction in burst release after coating poly(D,L-lactide-co-glycolide) (PLGA) microparticles with a drug-free PLGA layer.

The high initial burst release of a highly water-soluble drug from poly (D,L-lactide-co-glycolide) (PLGA) microparticles prepared by the multiple emulsion (w/o/w) solvent extraction/evaporation method was reduced by coating with an additional polymeric PLGA layer. Coating with high encapsulation efficiency was performed by dispersing the core microparticles in peanut oil and subsequently in an organic polymer solution, followed by emulsification in the aqueous solution. Hardening of an additional polymeric layer occurred by oil/solvent extraction. Peanut oil was used to cover the surface of core microparticles and, therefore, reduced or prevented the rapid erosion of core microparticles surface. A low initial burst was obtained, accompanied by high encapsulation efficiency and continuous sustained release over several weeks. Reduction in burst release after coating was independent of the amount of oil. Either freshly prepared (wet) or dried (dry) core microparticles were used. A significant initial burst was reduced when ethyl acetate was used as a solvent instead of methylene chloride for polymer coating. Multiparticle encapsulation within the polymeric layer increased as the size of the core microparticles decreased (< 50 µm), resulting in lowest the initial burst. The initial burst could be controlled well by the coating level, which could be varied by varying the amount of polymer solution, used for coating.

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.

Preparation of preformed porous PLGA microparticles and antisense oligonucleotides loading.

The objective of this study was to load preformed highly porous microparticles with drug. The microparticles were prepared by a modified multiple emulsion (w/o/w) solvent evaporation method with the addition of pore formers (NaCl into the internal aqueous phase or of glycerol monooleate to the poly(lactide-co-glycolide) (PLGA) polymer phase). The drug-free solidified microparticles were then washed with either water (for NaCl) or hexane (for glycerol monooleate) to extract the pore formers. The drug was then loaded into the preformed porous microparticles by incubation in aqueous drug solutions followed by air- or freeze-drying. The drug was strongly bound to the polymeric surface with air-dried microparticles. A biphasic drug release with an initial rapid release phase (burst effect) was followed by a slower release up to several weeks. The initial burst was dependent on the drug loading and could be significantly reduced by wet (non-aqueous) temperature curing.

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.