Abstract A new pathway for the synthesis of HPMA graft copolymers was developed and their self‐assembly into hybrid hydrogels was investigated. Linear water‐soluble polyHPMA was chosen as the polymer backbone, whereas coiled‐coil forming peptides, covalently attached to the backbone, formed the grafts. Peptides of different chain lengths were chosen for evaluation. The results revealed that graft length greatly affected gelation ability. At least four heptads were needed to facilitate the hybrid system to form hydrogels under the experimental conditions used. The major factors affecting the kinetics of hydrogel self‐assembly were concentration and temperature. magnified image
Cathepsin K is the major enzyme responsible for the degradation of the protein matrix of bone and probably for the destruction of articular cartilage in rheumatoid arthritis joints. These processes occur mainly in the resorption lacuna and within the lysosomal compartment. Here, we have designed, synthesized, and evaluated new lysosomotropic (water-soluble) polymer-cathepsin K inhibitor conjugates. In particular, we characterized the relationship between conjugate structures and their activity to inhibit cathepsins K, B, L, and papain. A potent selective cathepsin K inhibitor, 1,5-bis(N-benzyloxycarbonylleucyl)carbohydrazide, was modified to 1-(N-benzyloxycarbonylleucyl)-5-(phenylalanylleucyl)carbohydrazide (I) to facilitate polymer conjugation. It was conjugated to the polymer chain termini of two water-soluble polymers [alpha-methoxy poly(ethylene glycol), abbreviated as mPEG-I; semitelechelic poly[N-(2-hydroxypropyl)methacrylamide], abbreviated as ST-PHPMA-I]. The conjugation of inhibitor I to N-(2-hydroxypropyl)methacrylamide (HPMA) copolymer side chains was accomplished via either a Gly-Gly spacer (PHPMA-GG-I) or with no spacer between I and the copolymer backbone (PHPMA-I). Kinetic analysis revealed that free inhibitor I possessed an apparent second-order rate constant against cathepsin K (k(obs)/[I] = 1.3 x 10(6) M(-1) s(-1)) similar to that of unmodified 1,5-bis(Cbz-Leu) carbohydrazide, while I conjugated to the chain termini of mPEG and ST-PHPMA-COOH had slightly lower values (about 5 x 10(5) M(-1) s(-1)). The k(obs)/[I] values for I attached to the side chains of HPMA copolymers (PHPMA-GG-I and PHPMA-I) were about 3 x 10(4) M(-1) s(-1). When tested against cathepsin L, inhibitor I and all its polymer conjugates produced k(obs)/[I] values 1-2 orders of magnitude less than those determined for cathepsin K, while for cathepsin B and papain, the values were 2-4 orders of magnitude lower. The ability of mPEG-I and ST-PHPMA-I to inhibit cathepsin K activity in synovial fibroblasts was also evaluated. Both polymer-bound inhibitors were internalized by endocytosis and were ultimately trafficked to the lysosomal compartment. ST-PHPMA-I was internalized faster than mPEG-I. The inhibitory activity in the synovial fibroblast assay correlated with the rate of internalization.
It is essential to understand cellular responses on photodynamic therapy (PDT) to design delivery systems that maximize cytotoxic effects coupled with minimal induction of side effects or protective mechanisms (or both). Here, we investigated mechanisms of toxicity in human ovarian carcinoma A2780 cells treated with structurally diverse N-(2-hydroxypropyl)methacrylamide (HPMA) copolymer (P)–mesochlorin e6 monoethylenediamine (Mce6) conjugates that possessed differential subcellular accumulation or covalent attachments of photosensitizers (or both). Apoptosis and necrosis were observed after photoactivation, with increased apoptotic responses observed in cells exposed to conjugates possessing Mce6 linkage via a lysosomally degradable tetrapeptide spacer (HPMA copolymer–Mce6 conjugates containing Mce6 bound via glycylphenylalanylleucylglycine [GFLG] linker [P-GFLG-Mce6], HPMA copolymer–Mce6 conjugates containing Mce6 bound via a GFLG spacer and containing nuclear localization sequence, PKKKRKV132K(FITC)C [NLS(fluorescein-5-isothiocyanate [FITC])] bound via a thioether linkage [P-NLS(FITC)-GFLG-Mce6]). Furthermore, the induction of necrosis was more pronounced in cells exposed to conjugates containing both a nuclear localization sequence (NLS) and Mce6 bound by a degradable linker (P-NLS(FITC)-GFLG-Mce6). Caspase-independent mechanisms of cell death were identified in cells treated with nuclear-targeted conjugates possessing Mce6 attached using a nondegradable tether (HPMA copolymer–Mce6 conjugates containing Mce6 bound via a GG spacer and containing NLS(FITC) bound via a thioether linkage [P-NLS(FITC)-GG-Mce6]), whereas low levels of apoptosis and necrosis were detected in cells exposed to photoactivated nontargeted HPMA copolymer–Mce6 conjugates containing Mce6 coupled through a nondegradable spacer (HPMA copolymer–Mce6 conjugates containing Mce6 bound via GG linker [P-GG-Mce6]). Variations in gene expression were observed in cells on PDT. Specifically, HSP70 expression was solely detected in cells treated with P-GFLG-Mce6, whereas the loss of detection of several genes were observed in cells treated with P-NLS(FITC)-GFLG-Mce6. Variations in cellular responses on PDT using different HPMA copolymer–Mce6 conjugates will prove useful in the design of optimal HPMA copolymer PDT delivery systems.
N-(2-hydroxypropyl)methacrylamide (HPMA) copolymers containing pendant saccharide moieties (galactosamine, lactose, and triantennary galactose) were synthesized. The relationship between the content of saccharide moieties and three-dimensional arrangement of galactose residues and their biorecognition and internalization by human hepatocarcinoma HepG2 cells was investigated. The results obtained clearly indicated preferential binding of the trivalent galactose and the lactose-containing copolymers to these cells. The higher the saccharide moieties content in HPMA copolymers, the higher the levels of binding. The biorecognition of the glycosylated HPMA copolymers by HepG2 cells was inhibited by free lactose. The data on the internalization and subcellular trafficking of HPMA copolymer conjugates obtained by confocal fluorescence microscopy correlated well with the flow cytometric analysis of their biorecognition by target cells. Structural features of the glycosides responsible for the specific recognition of the HPMA copolymers have been identified. The results underline the potential of glycosylated HPMA copolymers for delivery of pharmaceutical agents to hepatocarcinoma cells.
Solution properties of the statistical copolymers of alkyl methacrylates (AMA) with α-methyl-ω-hydroxy-poly(oxyethylene) methacrylates (MPOEMA) (nonionic polysoaps) were studied using static and dynamic ligh scattering as a function of monomer composition and concentration in aqueous and methyl cellosolve solutions. The solubility of the copolymers in water was found to be dependent on molar contant of AMA. While copolymers with low content of hexyl methacrylate (HMA) (0 and 20 mole %) were directly soluble in water, forming true solutions with a low content of large swollen aggregates, copolymers with a higher content of HMA or lauryl methacrylate (LMA) were not directly dispersable in water. A special procedure, the stepwise dialysis from methyl cellosolve solutions against water, had to be used to prepare them in the pseudomicellar form. The copolymers were directly soluble in methyl cellosolve and its water solution containing up to 60 vol.% of water. Nevertheless, the light scattering experiments were dominated by light scattering of swollen particles of aggregated copolymer molecules. The copolymers were not soluble in the mixtures containing 70-100 vol.% of water. Paramaters of aggregates in the mixture with 60 vol.% of water and in pure water were found to be very similar.
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