Rising from the shortcomings of modern day therapeutics there is a need for a controlled approach in carrier‐mediated drug
delivery. Polymeric vesicles, also called polymersomes, are powerful tools to address issues of efficacy, specificity, and
controlled release of drugs to diseased tissues. These recent, biomimetic structures are able to overcome the body's natural
defences, remaining stable for extended time in circulation, have tuneable membrane properties, allowing the control of membrane
permeability and therefore of drug release, and have the potential to be functionalized for active targeting of specific tissues,
reducing undesirable side effects. Extensive work has been carried out in order to attain multifunctional polymeric vesicles
that respond to precise triggers (e.g., temperature, pH, redox, magnetic field, etc) with a spatial and temporal monitoring
what may enable unprecedented control of drug release in the body. These versatile structures can be loaded with different
type of (bio)molecules and nanoparticles, from drugs to contrast agents for medical imaging, and are able to accommodate them
in different subcompartments of the vesicle (i.e., hydrophobic membrane and hydrophilic core). Multimodal targeted delivery
system could be obtained from this unique platform, with abilities in both drug delivery and medical imaging contrast enhancement,
widening the perspectives toward theranostics. Polymersomes offer a promising route toward more effective treatments with
fewer side effects and superior outcomes. WIREs Nanomed Nanobiotechnol 2012, 4:525–546. doi: 10.1002/wnan.1183
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When injected in the body, a particulate drug delivery system faces a wide range of barriers. In circulation, the carrier may be promptly cleared by blood cells, liver, and spleen (clearance by phagocytic uptake or by filtration) or by the kidneys (through excretion) before it has the opportunity to access the target tissue. As a consequence, the delivery system has to display colloidal stability in physiological ionic strength and in contact with existent endogenous anionic molecules (i.e., glycosaminoglycans, opsonins, serum albumin, and other extra‐cellular proteins). Then, it has to interact with the cell surface to be internalized (B). Normally, endocytosed material is trafficked in the early endosome compartment (C), which can be recycled to the cell surface and excreted (D), or fuse with lysosomes, leading to degradation (E) or endosomal escape can occur (F), enabling the action of the loaded drug inside the cell.
Schematic representation of a reduction sensitive polymersome delivery system. Under reduction conditions, the diblock, which is formed by disulfide bond, disassembles leading to polymersome destabilization and subsequent drug release.
Scheme summarizing the different routes employed to obtain targeted polymersomes, emphasizing the number of steps involved in each route—putting aside polymer synthesis. (a) Ligand binding to preformed polymersomes. (b) Functionalization of the polymer in bulk and subsequent polymersomes formation. Targeted polymersomes obtained from functional hydrophilic block containing copolymers. (c) Functional hydrophilic block obtained from chemical modification of the polymer precursor. (d) Amphiphilic copolymer containing a functional hydrophilic block obtained directly from polymer synthesis.29,54,55–57,61–66,68–74,76–78
Design of lactoferrin‐conjugated biodegradable polymersome for glioma targeting (a). Polymersomes are simultaneously loaded with doxorubicin (Dox) as a model antitumor drug and tetrandrine (Tet) as an multi drug resistance (MDR) inhibitor. Lactoferrin (Lf) was conjugated on the surface of polymersomes, as glioma targeting ligand and to help overcome the obstruction of the BBB. Accumulation of targeted polymersomes in glioma (EPR effect and overcoming BBB) was evidenced by fluorescence imaging (b). The specific interaction of Lf‐conjugated polymersomes with glioma cells enhanced drug delivery into these cells, improving the chemotherapy of glioma as showed by the improved survival in rats (c). (Reprinted with permission from Ref 63. Copyright 2012 American Chemical Society)
Schematic representation of the preparation of the immunosensor (a). Amperometric response of the immunosensor (b) for detecting of different concentration of prostate specific antigen (PSA): (a) 10, (b) 5, (c) 1, (d) 0.5, and (e) 0.1 ng/mL. Measure at −0.4 V versus Ag/AgCl toward addition of 1 mM H2O2 in N2‐saturated PBS. (Reprinted with permission from Ref 70. Copyright 2012 Elsevier)
(a) In vitro detection of Tat‐NIR polymersome‐loaded murine dendritic cells (NIR‐DCs). Differential interference contrast and fluorescent confocal microscopy images of a Tat‐NIR polymersome‐labeled murine dendritic cell (bar = 5 µm). Color indicates local fluorescence intensity (blue < red < yellow). (b) Representative image of a 96‐well plate with 100 µL of labeled NIR‐DCs in serial dilution. Top well contains 3000 NIR‐DCs and subsequent wells are 4× dilutions (bar = 5 mm). (c) Quantified fluorescence intensity values versus number of NIR‐DCs per well. (d) In vivo longitudinal tracking of NIR‐dendritic cells (NIR‐DCs) migration to the popliteal lymph node in a mice model. Representative intensity maps (top row) and corresponding lifetime‐gated intensity maps (bottom row) for a single mouse are presented for days 4, 6, 11, and 33 after a single subcutaneous injection of 105 NIR‐DCs into the right footpad. (Reprinted with permission from Ref 99. Copyright 2012 Springer)
works at the interface of biotechnology and materials science. His lab is researching many topics, such as investigating the mechanism of release from polymeric delivery systems with concomitant microstructural analysis and mathematical modeling; studying applications of these systems including the development of effective long-term delivery systems for insulin, anti-cancer drugs, growth factors, gene therapy agents and vaccines; developing controlled release systems that can be magnetically, ultrasonically, or enzymatically triggered to increase release rates; synthesizing new biodegradable polymeric delivery systems which will ultimately be absorbed by the body; creating new approaches for delivering drugs such as proteins and genes across complex barriers such as the blood-brain barrier, the intestine, the lung and the skin; stem cell research including controlling growth and differentiation; and creating new biomaterials with shape memory or surface switching properties.