Nanoparticles in the pharmaceutical industry and the use of supercritical fluid technologies for nanoparticle production.

Poor aqueous solubility of drug candidates is a major challenge for the pharmaceutical scientists involved in drug development. Particle size reduction appears as an effective and versatile option for solubility improvement. Nanonization is an attractive solution to improve the bioavailability of the poorly soluble drugs, improved therapies, in vivo imaging, in vitro diagnostics and for the production of biomaterials and active implants. In drug delivery, application of nanotechnology is commonly referred to as Nano Drug Delivery Systems (NDDS). In this article, commercially available nanosized drugs, their dosage forms and proprietors, as well as the methods used for preparation like milling, high pressure homogenization, vacuum deposition, and high temperature evaporation were listed. Unlike the traditional methods used for the particle size reduction, supercritical fluid-processing techniques offer advantages ranging from superior particle size control to clean processing. The primary focus of this review article is the use of supercritical CO2 based technologies for small particle generation. Particles that have the smooth surfaces, small particle size and distribution and free flowing can be obtained with particular SCF techniques. In almost all techniques, the dominating process variables may be thermodynamic and aerodynamic in nature, and the design of the particle collection environment. Rapid Expansion of Supercritical Solutions (RESS), Supercritical Anti Solvent (SAS) and Particles from Gas Saturated Solutions (PGSS) are three groups of processes which lead to the production of fine and monodisperse powders. Few of them may also control crystal polymorphism. Among the aforementioned processes, RESS involves dissolving a drug in a supercritical fluid (SCF) and passing it through an appropriate nozzle. Rapid depressurization of this solution causes an extremely rapid nucleation of the product. This process has been known for a long time but its application is limited. Carbon dioxide, which is the only supercritical fluid that is preferentially used in pharmaceutical processes, is not a good solvent for many Active Pharmaceutical Ingredients (API). Various researchers have modified the RESS process to overcome its solubilizing limitations, by introducing RESOLV, RESAS, and RESS-SC. Overall, all RESS based processes are difficult to scale up. The SAS processes are based on decreasing the solvent power of a polar organic solvent in which the substrate (API & polymer of interest) is dissolved, by saturating it with carbon dioxide (CO2) at supercritical conditions. CO2 causes precipitation and recrystalization of the drug. SAS is scalable and can be applied to a wide variety of APIs and polymers. Minor modifications of basic SAS process include GAS, ASES, SAS-DEM and SAS-EM. Processes where SCF is used as an anti solvent and dispersing agent include SEDS, SAA, and A-SAIS. The mechanisms and applications of these processes were briefly discussed. In PGSS, CO2 is dissolved in organic solutions or melted compounds and it is successfully used for manufacturing drug products as well as for drying purposes. The two widely used methods, PGSSdrying and CAN-BD SCF, were also included in discussions. Among the limitations of the techniques involved, the poor solvent power of CO2, the cost and necessity of voluminous usage of the CO2 can be mentioned. There is still confusion in contribution of each variable on the particle morphology and properties regardless of the number of mechanistic studies available. The advantages of especially SAS and PGSS based techniques are the production of the nano or micro sized spherical particles with smooth surfaces and narrow particle size distribution. Regardless of its advantages, the reasons why 25 years of active research, and more than 10 years of process development could not promote the use of (SCF) technology, and produced only few commercial drug products, necessitate further evaluation of this technique.

Impact of polymers on dissolution performance of an amorphous gelleable drug from surface-coated beads.

A non-ionic amorphous active API ((RR)-3((1R)-3-oxocyclopentyl)-2-[3-chloro-4-methyl sulfonyl]phenyl-N-pyrozin-2ylpropanamide) with a glass transition temperature of 60 degrees C and aqueous solubility of 0.8 mg/mL was layered on the cellulose beads by the help of an anionic (Eudragit L100) and a non-ionic (polyvinylpyrrolidone) PVP K30 polymer respectively. An "immediate" and complete release of API from the anionic (Eudragit L100), and "sustained" but incomplete release from the hygroscopic non-ionic polymer coatings were observed. The effect of the PVP K30, and delivery patterns were investigated. Water uptake of the polymers and flow properties of API upon exposure to humidity as well as moisture sorption of beadlets were determined. Drug-polymer interactions and coating morphologies that were examined via near infrared imaging (NIR), microscopy and FTIR, enlightened any possible drug-polymer interaction. From the anionic polymer coating 93.5% API was dissolved in 50 min whereas the non-ionic polymer coating released 60% drug within 5 h. There were no API-polymer interactions as demonstrated by FTIR, implying that, this factor did not play any role in the differences observed in the release profiles. However, gelling, clumping and agglomeration was observed on the surface of the particles coated with PVP which resulted in slow and incomplete release of the drug. The anionic polymer protected API, by preventing its gelling and clumping in situ while the non-ionic polymer promoted gelling. Because API gels at a critical moisture level and at an associated critical time interval, any delivery system that can protect the drug from reaching to the critical moisture level can control API release. The drug was released via surface erosion from the Eudragit L100 coating, whereas PVP K30, the non-ionic polymer, released API via diffusion process. The results indicate that polymer properties can play a critical role in the release mechanism and kinetics of gelleable drugs. The anionic polymers may protect drugs of similar nature from gelling when exposed to the dissolution media. An understanding of mechanisms involved in drug-polymer interactions will be useful to screen the polymers that are useful in engineering suitable delivery systems for such drugs.

Phase behavior of amorphous molecular dispersions II: Role of hydrogen bonding in solid solubility and phase separation kinetics.

PURPOSE: To determine the factors influencing "solid solubility" and phase separation kinetics of drugs from amorphous solid dispersions. METHODS: Solid dispersions of griseofulvin-poly(vinyl pyrrolidone) (PVP) and indoprofen-PVP were prepared using solvent evaporation technique. Dispersions demonstrating single Tg were exposed to 40 degrees C/69% RH for 90 days. Drug solid solubility in the polymer and phase separation rates were determined from changes in Tg of solid dispersions. FTIR spectroscopy and XRD were used to characterize drug-polymer interactions and drug crystallinity, respectively. RESULTS: Freshly prepared solid dispersion of up to 30% w/w griseofulvin and indoprofen were molecularly miscible with PVP. Hydrogen bonding was evident in indoprofen-PVP, but not in griseofulvin-PVP dispersions. When exposed to 40 degrees C/69% RH, griseofulvin phase separated completely, whereas the solid solubility of indoprofen was determined as 13% w/w. The first-order rate constants of phase separation for 10%. 20%, and 30% w/w griseofulvin dispersions were estimated as 4.66, 5.19, and 12.50 (x10(2)) [day(-1)], and those of 20% and 30% w/w indoprofen dispersions were 0.62 and 1.25 (x10(2)) [day(-1)], respectively. CONCLUSIONS: Solid solubility of griseofulvin and indoprofen in PVP is approximately 0% w/w and approximately 13% w/w, respectively. Drug-polymer hydrogen bonding in indoprofen-PVP dispersions favors solid solubility. Phase separation rate of drug from the solid dispersions depends on the initial drug content and the nature of drug-polymer interactions.

Phase behavior of amorphous molecular dispersions I: Determination of the degree and mechanism of solid solubility.

PURPOSE: To understand the phase behavior and the degree and mechanism of the solid solubility in amorphous molecular dispersions by the use of thermal analysis. METHODS: Amorphous molecular dispersions of trehalose-dextran and trehalose-PVP were prepared by co-lyophilization. The mixtures were exposed to 23 degrees C, 40 degrees C, and 50 degrees C [75% relative humidity (RH)] and 23 degrees C (69% RH) storage conditions, respectively. Thermal analysis was conducted by modulated differential scanning calorimeter (MDSC). RESULTS: Upon exposure to moisture, two glass transition temperatures (TgS), one for phase-separated amorphous trehalose (Tg1) and the other for polymer-trehalose mixture (Tg2), were observed. With time, Tg2 increased and reached to a plateau (Tg(eq)), whereas Tg1 disappeared. The disappearance of Tg1 was attributed to crystallization of the phase-separated amorphous trehalose. It was observed that Tg(eq) was always less than Tg of pure polymer. The lower Tg(eq) when compared to Tg of pure polymer may be the result of solubility of a fraction of trehalose in the polymers chosen. The miscible fraction of trehalose was estimated to be 12% and 18% wt/wt in dextran at 50 degrees C/75% RH and 23 degrees C/75% RH, respectively, and 10% wt/wt in PVP at 23 degrees C/69% RH. CONCLUSIONS: Mixing behavior of trehalose-dextran and trehalose-PVP dispersions were examined both experimentally and theoretically. A method determining the "extent of molecular miscibility," referred to as "solid solubility," was developed and mechanistically and thermodynamically analyzed. Solid dispersions prepared at trehalose concentrations below the "solid solubility limit" were physically stable even under accelerated stability conditions.

Multi-unit controlled release systems of nifedipine and nifedipine:pluronic F-68 solid dispersions: characterization of release mechanisms.

Nifedipine (N) and nifedipine. Pluronic F-68 solid dispersion (SD) pellets were developed and characterizedfor drug release mechanisms from a multi-unit erosion matrix system for controlled release. Nifedipine was micronized using a jet mill. Solid dispersion with Pluronic F-68 was prepared by the fusion method. Nifedipine and SD were characterized by particle size analysis, solubility, differential scanning calorimetry (DSC), and x-ray diffraction (XRD) studies. Samples were subsequently processed into matrix pellets by extrusion/spheronization using Eudragit L 100-55 and Eudragit S 100 as release rate-controlling polymers. Drug release mechanisms from pellets were characterized by microscopy and mercury intrusion porosimetry; DSC and XRD studies indicated no polymorphic changes in N after micronization and also confirmed the formation of SD of N with Pluronic F-68. Pellets of N showed a 24-hr drug release profile following zero-order kinetics. Pellets of SD showed a 12-hr release profile followingfirst-order kinetics. Aqueous solubility of N after SD formation was found to be increased 10-fold. Due to increased solubility of N in SD, the drug release mechanism from the multi-unit erosion matrix changed from pure surface erosion to an erosion/diffusion mechanism, thereby altering the release rate and kinetics.