Abstract

Injectable liposomes are characterized by a suitable size and unique lipid mixtures, which require time-consuming and nonstraightforward production processes. The complexity of the manufacturing methods may affect liposome solubility, the phase transition temperatures of the membranes, the average particle size, and the associated particle size distribution, with a possible impact on the drug encapsulation and release. By leveraging the precise steady-state control over the mixing of miscible liquids and a highly efficient heat transfer, microfluidic technology has proved to be an effective and direct methodology to produce liposomes. This approach results particularly efficient in reducing the number of the sizing steps, when compared to standard industrial methods. Here, Microfluidic Hydrodynamic Focusing chips were produced and used to form liposomes upon tuning experimental parameters such as lipids concentration and Flow-Rate-Ratios (FRRs). Although modelling evidenced the dependence of the laminar flow on the geometric constraints and the FRR conditions, for the specific formulation investigated in this study, the lipids concentration was identified as the primary factor influencing the size of the liposomes and their polydispersity index. This was attributed to a predominance of the bending elasticity modulus over the vesiculation index in the lipid mixture used. Eventually, liposomes of injectable size were produced using microfluidic one-pot synthesis in continuous flow.

Highlights

  • Liposome vesicles with 50–250 nm size represent very suitable vector systems for targeted drug delivery [1,2]

  • This study assessed the feasibility of the continuous-flow production of injectable liposomes characterized by a unique phospholipid mixture in Microfluidic Hydrodynamic Focusing (MHF) chips

  • staggered herringbone micromixer (SHM) microfluidic chips have a more complex design and require more expensive fabrication processes, and their scale-up is only possible by parallelization

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Summary

Introduction

Liposome vesicles with 50–250 nm size represent very suitable vector systems for targeted drug delivery [1,2]. Lipophilic molecules or long alkyl chain-surrounded nanoparticles may be entrapped within the hydrophobic compartment of the lipid membrane [3]. For use as biomedical formulations, the steric stabilization of liposomes is typically addressed via surface functionalization of phospholipids, with the purpose to prolong their blood circulation time and circumvent their possible capture by the mononuclear phagocytic system [1,4]. Polyethylene glycol (PEG) chains grafted on the liposome surface were employed to increase their relatively low stability in vitro and to prevent their immediate uptake and clearance by the reticuloendothelial system. The use of long-chain PEG precursors in liposome formulations leads to operative complications during synthesis by introducing solubility restrictions, influencing the transitions temperature of the membranes and, the ultimate size of liposomes [7]

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