Selecting polymers for drug encapsulation in pharmaceutical formulations is usually made after extensive trial and error experiments. To speed up excipient choice procedures, we have explored coarse-grained computer simulations (dissipative particle dynamics (DPD) and coarse-grained molecular dynamics using the MARTINI force field) of polymer -drug interactions to study the encapsulation of prednisolone (log p ¼ 1.6), paracetamol (log p ¼ 0.3) and isoniazid (log p ¼ 21.1) in poly(L-lactic acid) (PLA) controlled release microspheres, as well as the encapsulation of propofol (log p ¼ 4.1) in bioavailability enhancing quaternary ammonium palmitoyl glycol chitosan (GCPQ) micelles. Simulations have been compared with experimental data. DPD simulations, in good correlation with experimental data, correctly revealed that hydrophobic drugs ( prednisolone and paracetamol) could be encapsulated within PLA microspheres and predicted the experimentally observed paracetamol encapsulation levels (5 -8% of the initial drug level) in 50 mg ml 21 PLA microspheres, but only when initial paracetamol levels exceeded 5 mg ml 21 . However, the mesoscale technique was unable to model the hydrophilic drug (isoniazid) encapsulation (4 -9% of the initial drug level) which was observed in experiments. Molecular dynamics simulations using the MARTINI force field indicated that the self-assembly of GCPQ is rapid, with propofol residing at the interface between micellar hydrophobic and hydrophilic groups, and that there is a heterogeneous distribution of propofol within the GCPQ micelle population. GCPQpropofol experiments also revealed a population of relatively empty and drug-filled GCPQ particles.

In order to enhance the delivery of poorly-soluble drugs, we have explored aquasomes (three-layered, ceramic core based, oligosaccharide coated nanoparticles) as potential carriers for the delivery of model hydrophobic drug piroxicam (log P = 3.1). Ceramic nanoparticles were prepared using two techniques; namely, co-precipitation by refluxing and co-precipitation by sonication. Core preparation was finally done using sonication approach; based on the higher % yield (42.4 ± 0.4%) and shorter duration (1 day) compared to the reflux method (27.4 ± 2.05%, 6 days). Lactose loading onto ceramic core was achieved using adsorption. Colorimetric analysis of lactose coating was done using Anthrone method. Optimization of process variables namely, incubation time and core to coat ratio (for sugar loading) was carried out. Optimum time of incubation was 3 h and the core to coat ratio was 4:1. The drug loading was achieved by incubating the sugar loaded cores in different concentrations of piroxicam solution and it was found that 1.5% w/v piroxicam was optimal. Structural characterization using Fourier-Transform Infra Red Spectroscopy (FTIR) confirmed the presence of sugar coating onto the core. Morphological evaluation using transmission electron microscopy (TEM) revealed spherical nanoparticles (size 56.56 ± 5.93 nm for lactose coated core and 184.75 ± 13.78 nm for piroxicam loaded aquasomes) confirming the nanometric dimensions.

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