Injectable gels have the potential to encapsulate drugs for sustained release of protein therapeutics for use in the eye. Hyaluronic acid (HA) is a biodegradable clinically used material and poly N-isopropylacrylamide (pNIPAAM) is a stimuli responsive polymer that can display a lower critical solution temperature (LCST) at physiological conditions. Two gel systems incorporating HA were prepared in the presence of the antibody infliximab (INF): i) 1% and 5% tyramine-substituted HA (HA-Tyr) was enzymatically crosslinked in the presence of INF to form HA-Tyr-INF and ii) NIPAAM was chemically crosslinked in the presence of HA and INF with 1 and 3% poly(ethylene glycol) diacrylate (PEGDA) to form PEGDA-pNIPAAM-HA-INF. The PEGDA-pNIPAAM-HA-INF hydrogels displayed LCSTs at temperatures ranging from 31.4 ± 0.2 to 35.7 ± 0.3 °C. Although all the gels prepared were injectable, INF-loaded gels with lower crosslinking density (1% PEGDA-pNIPAAM-HA and 1% HA-Tyr) showed lower elastic (G') and viscous (G″) moduli compared to higher crosslinked gels (3% PEGDA-pNIPAAM-HA-INF and 5% HA-Tyr-INF) resulting in differences in swelling ratio (SR). Moduli may be correlated with overall stiffness of the gel. All hydrogels demonstrated sustained release of INF in a two-compartment in vitro outflow model of the human eye called the PK-Eye. The 1% PEGDA-pNIPAAM-HA-INF hydrogel displayed the slowest release (24.9 ± 0.4% INF release by day 9) in phosphate buffered saline (PBS, pH 7.4), which is a better release profile than the free drug alone (tested under the same conditions). These results suggest that PEGDA-pNIPAAM-HA has potential for the continued development of formulations to prolong the intraocular release of proteins.

to an improvement in the loading capacities of DOPC-based liposomes only. Up to 3.6-fold 11 decrease in drug loading was observed after liposome purification, likely due to the loss of 12 adsorbed and loosely entrapped DTX in the SEC column. Our in vitro toxicity results in PC3 13 monolayer showed that non-purified, DTX-loaded DOPC:Chol liposomes were initially (24 h) 14 more potent than the purified ones, due to the fast action of the surface-adsorbed drug. 15However, we hypothesize that over time (48 and 72 h) the purified, DTX-loaded DOPC:Chol 16 liposomes became more toxic due to high intracellular release of encapsulated DTX. Finally, 17 our cytotoxicity results in PC3 spheroids showed the superior activity of DTX-loaded liposomes 18 compared to free DTX, which could overcome the DTX poor tissue penetration, drug 19 resistance, and improve its therapeutic efficacy following systemic administration. 20 21

Proteins and peptides have emerged in recent years to treat a wide range of multifaceted diseases such as cancer, diabetes and inflammation. The emergence of polypeptides has yielded advancements in the fields of biopharmaceutical production and formulation. Polypeptides often display poor pharmacokinetics, limited permeability across biological barriers, suboptimal biodistribution, and some proclivity for immunogenicity. Frequent administration of polypeptides is generally required to maintain adequate therapeutic levels, which can limit efficacy and compliance while increasing adverse reactions. Many strategies to increase the duration of action of therapeutic polypeptides have been described with many clinical products having been developed. This review describes approaches to optimise polypeptide delivery organised by the commonly used routes of administration. Future innovations in formulation may hold the key to the continued successful development of proteins and peptides with optimal clinical properties.

A reverse microemulsion approach has been explored for the synthesis of layered gadolinium hydroxide (LGdH) nanoparticles in this work. This method uses oleylamine as a multifunctional agent, acting as surfactant, oil phase and base. 1-butanol is additionally used as a co-surfactant. A systematic study of the key reaction parameters was undertaken, including the volume ratio of surfactant (oleylamine) to water, the reaction time, synthesis temperature, and the amount of cosurfactant (1-butanol) added. It proved possible to obtain pristine LGdH materials at temperatures of 120 °C or below with an oleylamine : water ratio of 1:4. Using larger amounts of surfactant or higher temperatures caused the formation of Gd(OH) 3 , either as the sole product or as a major impurity phase. The LGdH particles produced have sizes of ca. 200 nm, with this size being largely independent of temperature or reaction time. Adjusting the amount of 1-butanol co-surfactant added permits the size to be varied between 200 and 300 nm.