Mimicking bone microenvironment: 2D and 3D in vitro models of human osteoblasts.

Understanding the in vitro biology and behavior of human osteoblasts is crucial for developing research models that reproduce closely the bone structure, its functions, and the cell-cell and cell-matrix interactions that occurs in vivo. Mimicking bone microenvironment is challenging, but necessary, to ensure the clinical translation of novel medicines to treat more reliable different bone pathologies. Currently, bone tissue engineering is moving from 2D cell culture models such as traditional culture, sandwich culture, micro-patterning, and altered substrate stiffness, towards more complex 3D models including spheroids, scaffolds, cell sheets, hydrogels, bioreactors, and microfluidics chips. There are many different factors, such cell line type, cell culture media, substrate roughness and stiffness that need consideration when developing in vitro models as they affect significantly the microenvironment and hence, the final outcome of the in vitro assay. Advanced technologies, such as 3D bioprinting and microfluidics, have allowed the development of more complex structures, bridging the gap between in vitro and in vivo models. In this review, past and current 2D and 3D in vitro models for human osteoblasts will be described in detail, highlighting the culture conditions and outcomes achieved, as well as the challenges and limitations of each model, offering a widen perspective on how these models can closely mimic the bone microenvironment and for which applications have shown more successful results.

Carbohydrate Nanoparticles for Brain Delivery.

Many brain tumors and neurological diseases can greatly benefit from the use of emerging nanotechnologies based on targeted nanomedicines that are able to noninvasively transport highly potent and specific pharmaceuticals across the blood-brain barrier. Carbohydrates have received considerable interest as materials for drug carriers due to their natural origin and inherent biodegradability and biocompatibility, as well as due to their hydrophilic character and ease of chemical modification combined with low cost and the possibility for large-scale manufacturing. This chapter provides an overview of the latest research involving the use of carbohydrate-based nanoparticles for drug delivery to the central nervous system. After reviewing the challenges posed by delivering drugs into the brain, the current state-of-the-art approaches for delivery of actives across the blood-brain barrier, including invasive and noninvasive strategies, are presented. A particular focus has been placed on chitosan polymers as they are among the most promising carbohydrate nanocarriers for the preparation and testing of chitosan-based nanomedicines that led, in preclinical proof-of-concept studies, to enhanced brain drug levels and increased pharmacodynamics responses after intravenous, nasal, and oral administration. While chitosan nanoparticles are to date among the most studied and most promising carriers, approaches based on other polysaccharides such as dextran, pullulan, and cellulose warrant further research in the attempt to advance the existing technologies for overcoming the blood-brain barrier.

Chitosan amphiphile coating of peptide nanofibres reduces liver uptake and delivers the peptide to the brain on intravenous administration.

The clinical development of neuropeptides has been limited by a combination of the short plasma half-life of these drugs and their ultimate failure to permeate the blood brain barrier. Peptide nanofibres have been used to deliver peptides across the blood brain barrier and in this work we demonstrate that the polymer coating of peptide nanofibres further enhances peptide delivery to the brain via the intravenous route. Leucine(5)-enkephalin (LENK) nanofibres formed from the LENK ester prodrug - tyrosinyl(1)palmitate-leucine(5)-enkephalin (TPLENK) were coated with the polymer - N-palmitoyl-N-monomethyl-N,N-dimethyl-N,N,N-trimethyl-6-O-glycolchitosan (GCPQ) and injected intravenously. Peptide brain delivery was enhanced because the GCPQ coating on the peptide prodrug nanofibres, specifically enables the peptide prodrug to escape liver uptake, avoid enzymatic degradation to non-active sequences and thus enjoy a longer plasma half life. Plasma half-life is increased 520%, liver AUC0-4 decreased by 54% and brain AUC0-4 increased by 47% as a result of the GCPQ coating. The increased brain levels of the GCPQ coated peptide prodrug nanofibres result in the pharmacological activity of the parent drug (LENK) being significantly increased. LENK itself is inactive on intravenous injection.

Delivery of peptides to the blood and brain after oral uptake of quaternary ammonium palmitoyl glycol chitosan nanoparticles.

The clinical development of therapeutic peptides has been restricted to peptides for non-CNS diseases and parenteral dosage forms due to the poor permeation of peptides across the gastrointestinal mucosa and the blood-brain barrier. Quaternary ammonium palmitoyl glycol chitosan (GCPQ) nanoparticles facilitate the brain delivery of orally administered peptides such as leucine(5)-enkephalin, and here we examine the mechanism of GCPQ facilitated oral peptide absorption and brain delivery. By analyzing the oral biodistribution of radiolabeled GCPQ nanoparticles, the oral biodistribution of the model peptide leucine(5)-enkephalin and coherent anti-Stokes Raman scattering microscopy tissue images after an oral dose of deuterated GCPQ nanoparticles, we have established a number of facts. Although 85-90% of orally administered GCPQ nanoparticles are not absorbed from the gastrointestinal tract, a peak level of 2-3% of the oral GCPQ dose is detected in the blood 30 min after dosing, and these GCPQ particles appear to transport the peptides to the blood. Additionally, although peptide loaded nanoparticles from low (6 kDa) and high (50 kDa) molecular weight GCPQ are taken up by enterocytes, polymer particles with a polymer molecular weight greater than 6 kDa are required to facilitate peptide delivery to the brain after oral administration. By examining our current and previous data, we conclude that GCPQ particles facilitate oral peptide absorption by protecting the peptide from gastrointestinal degradation, adhering to the mucus to increase the drug gut residence time and transporting GCPQ associated peptide across the enterocytes and to the systemic circulation, enabling the GCPQ stabilized peptide to be transported to the brain. Orally administered GCPQ particles are also circulated from the gastrointestinal tract to the liver and onward to the gall bladder, presumably for final transport back to the gastrointestinal tract.