Creep-resistant elastomeric networks prepared by photocrosslinking fumaric acid monoethyl ester-functionalized poly(trimethylene carbonate) oligomers.

Biodegradable elastomeric networks were prepared from ethyl fumarate-functionalized poly(trimethylene carbonate) oligomers. Photocrosslinkable macromers were synthesized by reacting three-armed, hydroxyl group-terminated poly(trimethylene carbonate) oligomers with fumaric acid monoethyl ester at room temperature using N,N-dicyclohexylcarbodiimide as a coupling agent and 4-dimethylamino pyridine as a catalyst. Poly(trimethylene carbonate) macromers with molecular weights ranging between 4500 and 13,900 were prepared and crosslinked by ultraviolet-initiated radical polymerization. The gel contents of the resulting transparent networks varied between 74% and 80%. All obtained networks had low glass transition temperatures, which varied between -18 and -13 degrees C. They showed rubber-like behavior and excellent mechanical properties, with tensile strengths and elongations at break of up to 17.5 MPa and 750%, respectively. Moreover, static- and dynamic creep experiments showed that these amorphous networks were highly elastic and resistant to creep. In cyclic tensile testing to 50% strain, the permanent deformation after 20 cycles was 0%, while static creep tests at 35% of the yield stress did not indicate creep or permanent deformation after removal of the load. Porous structures were prepared by photopolymerizing the macromers in the presence of salt particles, and subsequent leaching of the salt. Such networks, built up of non-toxic compounds and designed to release benign degradation products, may find application as tissue engineering scaffolds for dynamic cell culture.

In situ gelling hydrogels incorporating microparticles as drug delivery carriers for regenerative medicine.

Aqueous solutions of blends of biodegradable triblock copolymers, composed of poly(D,L-lactide-co-glycolide) (PLGA) and poly(ethylene glycol) (PEG) with varied D,L-lactide to glycolide ratios, displayed thermosensitivity and formed a gel at body temperature. The gel window of the blend solutions could be tuned by varying the blending ratio between the two components. Furthermore, the storage modulus of the resultant hydrogel from the copolymer blends at body temperature was higher than that of each individual component. Incorporation of poly(D,L-lactide) (PDLLA) microparticles (0.5-40% w/v) within the in situ gelling hydrogel did not change the sol-gel transition temperatures of the polymer solutions, while the mechanical strength of the resultant hydrogels was enhanced when the content of the microparticles was increased up to 30% and 40%. Incorporation of proteins into both the gel and microparticle components resulted in composites that controlled the kinetics of protein release. Protein within the gel phase was released over a 10-day period whilst protein in the microparticles was released over a period of months. This system can be used to deliver two drugs with differing release kinetics and could be used to orchestrate tissue regeneration responses over differing timescales.

Accelerated formation of multicellular 3-D structures by cell-to-cell cross-linking.

The three-dimensional (3-D) arrangement of cells within tissues is integral to their development and function. Advances in stem cell science and regenerative medicine have stimulated interest in the replication of this architecture in vitro. We have developed a versatile method for controlling short-term cell-cell and cell-matrix interactions via a facile cell surface engineering process that enables the rapid formation of specific 3-D interactions for a range of cell types. We demonstrate that chemical modification of cell surfaces and matrix proteins can artificially accelerate the cell adhesion process and confirm the ability to control the formation of multicellular aggregates with defined architectures and heterotypic cell types. Direct comparison with a natural aggregation process seen during differentiation of embryonic stem (ES) cells revealed increased expression of developmental regulatory proteins and a concomitant enhancement of ES cell differentiation. Furthermore, this new methodology has numerous applications in generating layered structures. For example, we demonstrate improved transfer of therapeutic human keratinocytes onto a dermal layer in a skin repair model.

Incorporation of proteins within alginate fibre-based scaffolds using a post-fabrication entrapment method.

In this study, a physical entrapment process was explored for the incorporation of proteins within preformed fibrous alginates and the release profile was tuned by varying the processing parameters. The entrapment process was carried out in a series of aqueous solutions at room temperature and involved pre-swelling of the fibrous alginate within a Na(+)-rich solution, followed by exposure to the protein of choice and entrapping it by re-establishing cross-links of alginate with BaCl2. Entrapment and release of fluorescein isothiocyanate-labelled bovine serum albumin (FITC-BSA), a model protein, was studied. It was found that a sustained release of the incorporated protein in cell culture medium for about 6 days was achieved. The main factors determining the release profile included the NaCl/CaCl2 ratio in the pre-swelling solution, protein concentration, and the exposure time. To retard protein release, alginate fibres with entrapped FITC-BSA were processed together with poly(D, L-lactide) (PDLLA) into porous alginate fibre/PDLLA composites using supercritical CO2. In this manner, release of the protein for up to 3 months was achieved.

Novel surface entrapment process for the incorporation of bioactive molecules within preformed alginate fibers.

A physical entrapment technique has been developed for the surface engineering of preformed alginate fibers. Surface engineering was carried out at room temperature in aqueous solutions without additional solvent, a catalyst/initiator, a chemical cross-linking agent, or a temperature increase. Entrapment of surface-modifying molecules was achieved by exposing the alginate fibers to a Na(+)-rich NaCl/CaCl2 mixture solution, which caused the formation of a moderate dissociation layer into which the modifier could diffuse within a few seconds. The surface dissociation was then reversed by the addition of a large excess of multivalent cations, which resulted in collapse of the interface and immobilization of the modifying species. Rhodamine-tagged poly(ethylene glycol)s of different molecular weights were used as model molecules to investigate the effect of process parameters on the entrapment efficiency. It was found that the entrapment efficiency as well as the distribution of the modifier within the alginate fibers was determined by several factors, including the NaCl/CaCl2 ratio in the preswelling solution, exposure time, and concentration and molecular weight of the modifiers. The morphology of the fibers was not significantly changed in terms of shape and size after the entrapment process. By this technique, poly(L-lysine) (PLL) coupled with cell adhesion peptide sequence GRGDS (PLL-GRGDS) was entrapped within alginate fibers, and it was demonstrated that the modification promoted the attachment of mouse 3T3 fibroblasts.

Preparation of biodegradable networks by photo-crosslinking lactide, epsilon-caprolactone and trimethylene carbonate-based oligomers functionalized with fumaric acid monoethyl ester.

Biodegradable polymer networks were prepared from fumaric acid derivatives of oligomeric esters. Photo-crosslinkable macromers were prepared by reacting star-shaped hydroxyl-group terminated lactide, epsilon-caprolactone and trimethylene carbonate based oligomers and fumaric acid monoethyl ester in the presence of N,N-dicyclohexylcarbodiimide and 4-dimethylamino pyridine at room temperature. The functionalization method is facile and suited for many hydroxyl-terminated oligomers. The reactivity of the fumarate end groups is such that, upon crosslinking by UV radical polymerization, networks with high gel contents (up to 96%) can be obtained without the addition of reactive diluents. The physical properties of the networks can be tuned by adjusting the composition, architecture and molecular weight of the oligomeric precursors. Such networks, built up of non-toxic compounds and designed to release benign degradation products, may find wide application in tissue engineering and other areas of biomedical research.

Delivery systems for bone growth factors - the new players in skeletal regeneration.

Given the challenge of an increasing elderly population, the ability to repair and regenerate traumatised or lost tissue is a major clinical and socio-economic need. Pivotal in this process will be the ability to deliver appropriate growth factors in the repair cascade in a temporal and tightly regulated sequence using appropriately designed matrices and release technologies within a tissue engineering strategy. This review outlines the current concepts and challenges in growth factor delivery for skeletal regeneration and the potential of novel delivery matrices and biotechnologies to influence the healthcare of an increasing ageing population.

Preparation of interconnected highly porous polymeric structures by a replication and freeze-drying process.

Three-dimensional degradable porous polymeric structures with high porosities (93-98%) and well-interconnected pore networks have been prepared by freeze-drying polymer solutions in the presence of a leachable template followed by leaching of the template. Templates of the pore network were prepared by fusing sugar or salt particles to form a well-connected structure. The interstices of the template were then filled with a polymer solution (5-15% w/v) in 1,4-dioxane, followed by freeze-drying of the solvent. Subsequent leaching of the sugar template ensures the connectivity of the pore network. The scaffold architecture consists of relatively large interconnected pores modeled after the template and smaller pores resulting from the freeze-drying process. The total porosity of the resultant porous structures is determined by the interstitial space of the leachable template and by the polymer concentration in the freeze-drying solution. The freezing temperature also has an effect on the final morphology of the porous structures. Compared with freeze-drying and combination of freeze-drying /particulate leaching techniques, this method facilitates higher interconnectivity of the scaffolds. Porous structures have been prepared from several relevant polymers in the biomedical and tissue-engineering field: poly(D,L-lactide) (PDLLA), 1000PEOT70PBT30, a segmented poly(ether ester) based on polyethylene oxide and polybutylene terephthalate, and poly(epsilon-caprolactone) (PCL). The mechanical properties of the porous structures prepared by this technique depend on the nature of the polymer, porosity, and the freezing temperature. With porosities in the range of 95-97%, the compression moduli of scaffolds prepared from the different polymers could be varied between 13.0 and 301.5 kPa.

Porous polymeric structures for tissue engineering prepared by a coagulation, compression moulding and salt leaching technique.

A technique for the preparation of porous polymeric structures involving coagulation, compression moulding and particulate leaching has been developed. The technique combines the advantages of thermal processing methods and particulate leaching. A high molecular weight polymer solution in an organic solvent containing dispersed water-soluble salt particles is precipitated into an excess of non-solvent. The polymer-salt composite is then processed by thermal processing methods into devices of varying shapes and sizes, which can subsequently be extracted to give the desired porous structures. The porosities of the scaffolds could be varied between 70% and 95% by adjusting the polymer to salt ratio and the pore size could be controlled independently by varying the leachable particle size. This versatility provides for the optimisation of scaffolds used in medicine and in tissue engineering. Compared with commonly used porosifying methods such as sintering, compression moulding combined with salt leaching, and freeze-drying, this process allows excellent control over pore size and porosity and yields scaffolds with a much more homogeneous pore morphology. We have prepared porous structures from several relevant polymers in the biomedical field: poly(D,L-lactide), poly(epsilon-caprolactone) and 1000PEOT70PBT30, a segmented poly(ether ester) based on polyethylene oxide and polybutylene terephthalate.