Well‐defined amphiphilic linear‐dendritic prodrugs (MPEG‐b‐PAMAM‐DOX) are synthesized by conjugating doxorubicin (DOX), to MPEG‐b‐PAMAM through the acid‐labile hydrazone bond. The amphiphilic prodrugs form self‐assembled nanoparticles in deionized water and encapsulate the hydrophobic anticancer drug 10‐hydroxycamptothecin (HCPT) with a high drug loading efficiency. Studies on drug release and cellular uptake of the co‐delivery system reveal that both drugs are released in a pH‐dependent manner and effectively taken up by MCF‐7 cells. In vitro methyl thiazolyl tetrazolium (MTT) assays and drug‐induced apoptosis tests demonstrate the HCPT‐loaded nanoparticles suppress cancer cell growth more efficiently than the MPEG‐b‐PAMAM‐DOX prodrugs, free HCPT, and physical mixtures of MPEG‐b‐PAMAM‐DOX and HCPT at equivalent DOX or HCPT doses.
Poly(doxorubicin) (PDOX) is synthesized with Mn of 1.66 × 104 and DOX content of 78% as prodrug for tumor‐specific triggered release, via a facile condensation polymerization of DOX‐SS‐DOX and adipic dihydrazide. The PDOX nanoparticles (PDOX‐NPs) could completely release DOX‐SH within 1.5 days at the simulated tumor microenvironment, but no measurable leakage in the physiological media. The in vitro controlled release results show that the releasing rate is influenced by the dosage and independent of the particle size, while the solubility of the degraded products should be the main determining factor for the drug release from the PDOX‐NPs. The PDOX‐NPs are expected to be promising prodrug nanopharmaceutics for the on‐demand self‐delivery of DOX with enhanced anticancer efficacy in future tumor treatment. 相似文献
The development of thermo‐responsive and reduction‐sensitive polymeric micelles based on an amphiphilic block copolymer poly[(PEG‐MEMA)‐co‐(Boc‐Cyst‐MMAm)]‐block‐PEG (denoted PEG‐P‐SS‐HP) for the intracellular delivery of anticancer drugs is reported. PTX, as model drug, was loaded into the PEG‐P‐SS‐HP micelles with an encapsulation efficiency >90%, resulting in a high drug loading content (up to 35 wt%). The PTX‐loaded PEG‐P‐SS‐HP micelles show slow drug release in PBS and rapid release after incubation with DTT. The PTX‐loaded micelles display a better cytotoxic effect than the free drug, whereas empty micelles are found to be non‐toxic. The thermo‐responsive and reduction‐sensitive polymeric micelles described may serve as promising carriers for cytostatic drugs.
A supramolecular block copolymer is prepared by the molecular recognition of nucleobases between poly(2‐(2‐methoxyethoxy)ethyl methacrylate‐co‐oligo(ethylene glycol) methacrylate)‐SS‐poly(ε‐caprolactone)‐adenine (P(MEO2MA‐co‐OEGMA)‐SS‐PCL‐A) and uracil‐terminated poly(ethylene glycol) (PEG‐U). Because the block copolymer is linked by the combination of covalent (disulfide bond) and noncovalent (A U) bonds, it not only has similar properties to conventional covalently linked block copolymers but also possesses a dynamic and tunable nature. The copolymer can self‐assemble into micelles with a PCL core and P(MEO2MA‐co‐OEGMA)/PEG shell. The size and morphologies of the micelles/aggregates can be adjusted by altering the temperature, pH, salt concentration, or adding dithiothreitol (DTT) to the solution. The controlled release of Nile red is achieved at different environmental conditions.
Summary: Spherical micelles have been formed by mixing, in DMF, a poly(styrene)‐block‐poly(2‐vinylpyridine)‐block‐poly(ethylene oxide) (PS‐block‐P2VP‐block‐PEO) triblock copolymer with either poly(acrylic acid) (PAA) or a tapered triblock copolymer consisting of a PAA central block and PEO macromonomer‐based outer blocks. Noncovalent interactions between PAA and P2VP result in the micellar core while the outer corona contains both PS and PEO chains. Segregation of the coronal chains is observed when the tapered copolymer is used.
Inclusion of comb‐like chains with short PEO teeth in the corona triggers the nanophase segregation of PS and PEO as illustrated here (PS = polystyrene; PEO = poly(ethylene oxide)). 相似文献
A hyaluronic acid‐based anionic nanogel formed by self‐assembly of cholesteryl‐group‐bearing HA is designed for protein delivery. The HA nanogel spontaneously binds various types of proteins without denaturation, such as recombinant human growth hormone, erythropoietin, exendin‐4, and lysozyme. The HA nanogel shows unique colloidal properties, in particular that an injectable hydrogel is formed by salt‐induced association of the HA nanogel. A pharmacokinetic study in rats shows that an in situ gel formulation, prepared by simply mixing rhGH and HA nanogel in phosphate buffer, maintains plasma rhGH levels within a narrow range over one week. Therefore, HA nanogels offer a simple method for easy formulation of therapeutic proteins and are effective for sustained protein release systems.
Polymer nanoparticles are prepared by self‐assembly of visible light and pH sensitive perylene‐functionalized copolymers which are synthesized by quaternization between 1‐(bromomethyl)perylene and the dimethylaminoethyl units of poly(dimethylaminoethyl methacrylate) (PDMAEMA). The perylene‐containing polymethacrylate segments afford the system visible light responsiveness and the unquaternized PDMAEMA segments afford the system pH responsiveness. The self‐assembled nanoparticles exhibit a unique dual stimuli response. They can be photocleaved under visible light irradiation, shrunken to smaller nanoparticles at high pH, and swollen at low pH. The structural change endows the nanoparticle with great potential as a sensitive nanocarrier for controlled release of Nile Red and lysozyme under this stimulation. The visible light responsiveness and synergistic effect on the release of loaded molecules with the dual stimulation may obviate the need for harsh conditions such as UV light or extreme pH stimulation, rendering the system more applicable under mild conditions.
