Abstract: A cell-scaffold composition is prepared in vitro for implanting to produce functional organ tissue in vivo. The scaffold is three-dimensional and is composed of fibers of a biocompatible, biodegradable, synthetic polymer. Cells derived from vascularized organ tissue are attached in vitro to the surface of the fibers uniformly throughout the scaffold in an amount effective to produce functional vascularized organ tissue in vivo. Fibers of the scaffold are spaced apart such that the maximum distance over which diffusion of nutrients and gases must occur through a mass of cells attached to the fibers is between 100 and 300 microns. The diffusion provides free exchange of nutrients, gases and waste to and from cells proliferating throughout the scaffold in an amount effective to maintain cell viability throughout the scaffold in the absence of vascularization.

Abstract: Cells for implantation into a patient are packaged within a barrier of immunoprotective tissue prior to implantation to obviate or minimize rejection of the cells. The preferred immunoprotective tissue for forming the barrier is cartilage. The tissue is formed into a layer that is thin enough to allow diffusion of nutrients and gases into the center of a cell mass packaged within the immunoprotective tissue. Typically the layer is less than 300 microns, preferably between 5 and 20 microns. Cells to be implanted, typically dissociated parenchymal cells including hepatocytes, Islets of Langerhans, or other cells having metabolic functions, are then placed on the tissue layer, and the layer is folded to seal the cells to be implanted within the tissue layer. In the preferred embodiment, the dissociated cells are first seeded onto a polymeric fiber matrix.

Abstract: Methods and artificial matrices for the growth and implantation of cartilaginous structures and surfaces and bone are disclosed. In the preferred embodiments, chondrocytes are grown on biodegradable, biocompatible fibrous polymeric matrices. Optionally, the cells are proliferated in vitro until an adequate cell volume and density has developed for the cells to survive and proliferate in vivo. One advantage of the matrices is that they can be cast or molded into a desired shape, on an individual basis, so that the final product closely resembles a patient's own ear or nose. Alternatively, flexible matrices can be used which can be manipulated at the time of implantation, as in a joint, followed by remodeling through cell growth and proliferation in vivo. The cultured cells can also be maintained on the matrix in a nutrient media for production of bioactive molecules such as angiogenesis inhibiting factor.

Abstract: Methods and compositions are described herein for reconstruction or augmentation of breast tissue. Dissociated cells, preferably muscle cells, are implanted in combination with a suitable biodegradable, polymeric matrix to form new tissue. There are two forms of matrices which can be used: a polymeric hydrogel formed of a material such as alginate having cells suspended therein, and a fibrous matrix having an interstitial spacing between about 100 and 300 microns. Preferred polymeric materials are those degrading over about one to two months, such as polylactic acid-glycolic acid copolymers. The matrices can be seeded prior to implantation or implanted, allowed to vascularize, then seeded with cells. In a preferred embodiment, the cell-matrix structures are implanted in combination with tissue expander devices. As cell-matrix is implanted, or cells proliferate and form new tissue, the expander size is decreased, until it can be removed and the desired reconstruction or augmentation is obtained.

Abstract: Methods and artificial matrices for the growth and implantation of urological structures and surfaces are disclosed in which urothelial cells are grown in culture on biodegradable, biocompatible, fibrous matrices formed of polymers, such as polyglycolic acid, polylactic acid, or other polymers which degrade over time. The cells can be cultured in vitro until an adequate cell volume and density has developed for the cells to survive and proliferate in vivo. Alternatively, when adequate cell numbers for implantation are available, the cells can be attached to the matrix and implanted directly, without proliferation in vitro. The implants approximate the desired urological structure to be replaced or repaired, such as the kidney, urether, bladder, urethra, and the like. Implantation is followed by remodeling through cell growth and proliferation in vivo.

Abstract: Biocompatible porous polymer membranes are prepared by dispersing salt particles in a biocompatible polymer solution. The solvent in which the polymer is dissolved is evaporated to produce a polymer/salt composite membrane. The polymer can then be heated and cooled at a predetermined constant rate to provide the desired amount of crystallinity. Salt particles are leached out of the membrane by immersing the membrane in water or another solvent for the salt but not the polymer. The membrane is dried, resulting in a porous, biocompatible membrane to which dissociated cells can attach and proliferate. A three-dimensional structure can be manufactured using the polymer membranes by preparing a contour drawing of the shape of the structure, determining the dimensions of thin cross-sectional layers of the shape, forming porous polymer membranes corresponding to the dimensions of the layers, and laminating the membranes together to form a three-dimensional matrix having the desired shape.

Abstract: Polymers more suitable for use in organ transplantation are formed by coupling biologically active moieties to the free amino groups of polymers formed by incorporation of .alpha. amino acids into polymers formed of alpha hydroxy acids such as lactic acids. In the preferred embodiment, the peptides are coupled to the free amino groups.

Abstract: Methods and artificial matrices for the growth and implantation of cartilaginous structures and surfaces are disclosed. In the preferred embodiments, chondrocytes are grown on biodegradable, biocompatible fibrous polymeric matrices. Optionally, the cells are proliferated in vitro until an adequate cell volume and density has developed for the cells to survive and proliferate in vivo. One advantage of the matrices is that they can be cast or molded into a desired shape, on an individual basis, so that the final product closely resembles a patient's own ear or nose. Alternatively, flexible matrices can be used which can be manipulated at the time of implantation, as in a joint, followed by remodeling through cell growth and proliferation in vivo. The cultured cells can also be maintained on the matrix in a nutrient media for production of bioactive molecules such as angiogenesis inhibiting factor.