Quantifying cellular protrusion in alginate capsules with covalently crosslinked shells.

This work describes viability and distribution of INS-1E beta cells in shell-crosslinked alginate capsules, focussing on cells located near the capsule surface. Capsules were formed by air-shearing alginate suspensions of INS-1E cells into a gelling bath, and coating with poly-l-lysine (PLL) and 50% hydrolysed poly(methylvinylether-alt-maleic anhydride) to form crosslinked networks reinforcing the capsule surfaces. The percentage of cells at the capsule surface were determined using 2D and 3D confocal colocalization mapping. Encapsulated INS-1E cells showed high cell viability and progressive cell clustering out to six weeks. About 30% of cells were initially colocated with the 20 micrometer thick alginate-PLL-PMM50 shell, with 7% of cells protruded at the capsule surfaces, both reflecting random cell distributions. Protruding cells may cause cell-based immune responses, weaken capsules, and potentially result in cell escape from the capsules. The data shown indicate that reinforcing capsules with crosslinked shells may assist in preventing cell exposure and escape.

Cross-Linked Hydrogels Formed through Diels-Alder Coupling of Furan- and Maleimide-Modified Poly(methyl vinyl ether-alt-maleic acid).

The Diels-Alder [4 + 2] cycloaddition between furan- and maleimide-functional polyanions was used to form cross-linked synthetic polymer hydrogels. Poly(methyl vinyl ether-alt-maleic anhydride) was reacted with furfurylamine or N-(2-aminoethyl)maleimide in acetonitrile to form pairs of furan- and maleimide-functionalized poly(methyl vinyl ether-alt-maleic acid)s. Mixtures of these mutually reactive polyanions in water gelled within 15 min to 18 h, depending on degree of functionalization and polymer concentrations. Solution and magic-angle spinning (1)H NMR were used to confirm the formation of the Diels-Alder adduct, to analyze competing hydrolytic side reactions, and demonstrate postgelation functionalization. The effect of the degree of furan and maleimide functionalization, polymer concentration, pH, and calcium ion concentration, on gelation time, gel mechanical properties, and equilibrium swelling, are described. Release of dextran as a model drug was studied using fluorescence spectroscopy, as a function of gel composition and calcium treatment.

Synthetic polycations with controlled charge density and molecular weight as building blocks for biomaterials.

A series of polycations prepared by RAFT copolymerization of N-(3-aminopropyl)methacrylamide hydrochloride (APM) and N-(2-hydroxypropyl)methacrylamide, with molecular weights of 15 and 40 kDa, and APM content of 10-75 mol%, were tested as building blocks for electrostatically assembled hydrogels such as those used for cell encapsulation. Complexation and distribution of these copolymers within anionic calcium alginate gels, as well as cytotoxicity, cell attachment, and cell proliferation on surfaces grafted with the copolymers were found to depend on composition and molecular weight. Copolymers with lower cationic charge density and lower molecular weight showed less cytotoxicity and cell adhesion, and were more mobile within alginate gels. These findings aid in designing improved polyelectrolyte complexes for use as biomaterials.

Tunable hydrogel thin films from reactive synthetic polymers as potential two-dimensional cell scaffolds.

This article describes the formation of cross-linked 10-200-nm-thick polymer hydrogel films by alternating the spin-coating of two mutually reactive polymers from organic solutions, followed by hydrolysis of the resulting multilayer film in aqueous buffer. Poly(methyl vinyl ether-alt-maleic anhydride) (PMM) was deposited from acetonitrile solution, and poly(N-3-aminopropylmethacrylamide-co-N-2-hydroxypropylmethacrylamide) (PAPMx, where x corresponds to the 3-aminopropylmethacrylamide content ranging from 10 to 100%) was deposited from methanol. Multilayer films were formed in up to 20 deposition cycles. The films cross-linked during formation by reaction between the amine groups of PAPMx and the anhydride groups of PMM. The resulting multilayer films were covalently postfunctionalized by exposure to fluoresceinamine, decylamine, d-glucamine, or fluorescently labeled PAPMx solutions prior to the hydrolysis of residual anhydride in aqueous PBS buffer. This allowed tuning the hydrophobicity of the film to give static water contact angles ranging from about 5 to 90°. Increasing the APM content in PAPMx from 10 to 100% led to apparent Young's moduli from 300 to 700 kPa while retaining sufficient anhydride groups to allow postfunctionalization of the films. This allowed the resulting (PMM/PAPMx) multilayer films to be turned into adhesion-promoting or antifouling surfaces for C2C12 mouse myoblasts and MCF 10A premalignant human mammary epithelial cells.

Systematic study of alginate-based microcapsules by micropipette aspiration and confocal fluorescence microscopy.

Micropipette aspiration and confocal fluorescence microscopy were used to study the structure and mechanical properties of calcium alginate hydrogel beads (A beads), as well as A beads that were additionally coated with poly-L-lysine (P) and sodium alginate (A) to form, respectively, AP and APA hydrogels. A beads were found to continue curing for up to 500 h during storage in saline, due to residual calcium chloride carried over from the gelling bath. In subsequent saline washes, micropipette aspiration proved to be a sensitive indicator of gel weakening and calcium loss. Aspiration tests were used to compare capsule stiffness before and after citrate extraction of calcium. They showed that the initial gel strength is largely due to the calcium alginate gel cores, while the long term strength is solely due to the poly-L-lysine-alginate polyelectrolyte complex (PEC) shells. Confocal fluorescence microscopy showed that calcium chloride exposure after PLL deposition led to PLL redistribution into the hydrogel bead, resulting in thicker but more diffuse and weaker PEC shells. Adding a final alginate coating to form APA capsules did not significantly change the PEC membrane thickness and stiffness, but did speed the loss of calcium from the bead core.

Poly(methyl vinyl ether-alt-maleic acid) polymers for cell encapsulation.

Polyanions based on poly(methyl vinyl ether-alt-maleic acid) were investigated as materials for cell encapsulation. These water-soluble polyanions having molecular masses ranging from 20 to 1980 kDa were prepared by functionalization of poly(methyl vinyl ether-alt-maleic anhydride) with 5-aminofluorescein and/or α-methoxy-ω-amino-poly(ethylene glycol), followed by base hydrolysis of the residual anhydride groups to form the corresponding poly(methyl vinyl ether-alt-sodium maleate). Their potential to replace alginate both in the core and, in particular, the outer shell of calcium alginate-poly(L-lysine)-alginate (APA) capsules was determined using confocal fluorescence microscopy, osmotic pressure tests, permeability studies, protein binding and cell viability assays. These polymers were shown to be able to replace the outer layer of alginate, forming more resilient capsule shells. The resulting capsules showed similar permeability and resistance to bovine serum albumin binding, as well as superior viability for encapsulated cells, when compared to standard APA capsules. In addition, these polymers showed promise for use as functional additives to the capsule cores.

Cross-linked microcapsules formed from self-deactivating reactive polyelectrolytes.

Poly(methyl vinyl ether-alt-maleic anhydride) (PMM(0)) was partially hydrolyzed in a 9/1 acetonitrile-d(3)/D(2)O mixture and then diluted with an aqueous buffer and coated onto poly-L-lysine (PLL)-coated calcium alginate capsules. The resulting 50% hydrolyzed polymer (PMM(50)) is bound to the surface-immobilized PLL through both electrostatic and covalent interactions, resulting in a shell-cross-linked hydrogel capsule that is resistant to chemical challenges. Further hydrolysis of PMM(50) in aqueous buffer was monitored by potentiometry and was found to proceed with a half-life time of about 2.5 min at 20 degrees C such that residual anhydride groups not consumed by cross-linking with PLL would be deactivated by hydrolysis within several minutes of shell formation, removing potential sites for undesired protein binding. Initial protein-binding tests involving incubation of the capsules in bovine serum albumin solutions for 24 h showed no indication of protein binding. The effects of coating temperature, PLL concentration and molecular weight, PMM(50) molecular weight, and multiple PLL-PMM(50) coatings on shell morphology and behavior were studied using confocal fluorescence microscopy as well as chemical challenges involving sodium citrate and sodium hydroxide. The resilience of the cross-linked shell improved with increasing concentrations of PLL and decreasing molecular weight of PMM(50), both of which resulted in more polyelectrolyte being bound to the capsule. The permeability of these covalently cross-linked capsules was studied using fluorescently labeled dextrans and was found to be comparable to standard calcium alginate-PLL-alginate (APA) capsules.

Core-cross-linked alginate microcapsules for cell encapsulation.

Self-cross-linkable polyelectrolyte pairs comprised of poly(methacrylic acid, sodium salt-co-2-[methacryloyloxy]ethyl acetoacetate) (70:30 mol ratio, A70) and poly-L-lysine are incorporated into CaAlg beads to form either a covalently cross-linked shell or a core-cross-linked bead. In both cases the reactive polyanion is added to a solution of sodium alginate that may contain live cells and dropped into a calcium chloride gelling bath. Subsequent exposure to poly-L-lysine (15-30 kDa) leads to formation of a cross-linked shell, while exposure to lower molecular weight poly-L-lysine (4-15 kDa) leads to formation of an interpenetrating matrix of covalently cross-linked synthetic polymer within the CaAlg template. The resulting spherical composites are resistant to chemical and mechanical stress yet remain cyto-compatible. This approach to cell-encapsulation may be useful for cell immuno-isolation in therapeutic cell transplants.

Self-cross-linking polyelectrolyte complexes for therapeutic cell encapsulation.

Self-cross-linking polyelectrolytes are used to strengthen the surface of calcium alginate beads for cell encapsulation. Poly([2-(methacryloyloxy)ethyl]trimethylammonium chloride), containing 30 mol % 2-aminoethyl methacrylate, and poly(sodium methacrylate), containing 30 mol % 2-(methacryloyloxy)ethyl acetoacetate, were prepared by radical polymerization. Sequential deposition of these polyelectrolytes on calcium alginate films or beads led to a shell consisting of a covalently cross-linked polyelectrolyte complex that resisted osmotic pressure changes as well as challenges with citrate and high ionic strength. Confocal laser fluorescence microscopy revealed that both polyelectrolytes were concentrated in the outer 7-25 microm of the calcium alginate beads. The thickness of this cross-linked shell increased with exposure time. GPC studies of solutions permeating through analogous flat model membranes showed molecular weight cut-offs between 150 and 200 kg/mol for poly(ethylene glycol), suitable for cell encapsulation. C 2C 12 mouse cells were shown to be viable within calcium alginate capsules coated with the new polyelectrolytes, even though some of the capsules showed fibroid overcoats when implanted in mice due to an immune response.

Multilayered polymer microspheres by thermal imprinting during microsphere growth.

Modulation of the polymerization temperature in precipitation polymerizations was used to form onion-type polymer microspheres consisting of multiple nested layers. Specifically, the copolymerization of chloromethylstyrene and divinylbenzene-55 in acetonitrile, at temperatures ramping between 65 and 75 degrees C, led to monodisperse, cross-linked microspheres of about 10 mum diameter that have radial density profiles closely reflecting the thermal profiles used. This thermal imprinting is attributed to the copolymer formed being close to its theta point during the polymerization. As the microspheres grow by continuously capturing oligomers from solution, the resulting transient surface gel layer expands and contracts with temperature, and thus records the reaction temperature profile in the form of a corresponding density profile, even as it cross-links.