摘要:
Connective tissue, including neo-tendons and ligaments, has been constructed using biodegradable synthetic scaffolds seeded with tenocytes. The scaffolds are preferably formed from biodegradable fibers formed of a polymer such as polyglycolic acid-polylactic acid copolymers, and seeded with cells isolated from autologous tendon or ligament by means of enzymatic digestion or direct seeding into tissue culture dishes from explants. The cell polymer constructs are then surgically transplanted to replace missing segments of functioning tendon or ligament.
摘要:
Connective tissue, including neo-tendons and ligaments, has been constructed using biodegradable synthetic scaffolds seeded with tenocytes. The scaffolds are preferably formed from biodegradable fibers formed of a polymer such as polyglycolic acid-polylactic acid copolymers, and seeded with cells isolated from autologous tendon or ligament by means of enzymatic digestion or direct seeding into tissue culture dishes from explants. The cell polymer constructs are then surgically transplanted to replace missing segments of functioning tendon or ligament.
摘要:
Connective tissue, including neo-tendons and ligaments, has been constructed using biodegradable synthetic scaffolds seeded with tenocytes. The scaffolds are preferably formed from biodegradable fibers formed of a polymer such as polyglycolic acid-polylactic acid copolymers, and seeded with cells isolated from autologous tendon or ligament by means of enzymatic digestion or direct seeding into tissue culture dishes from explants. The cell polymer constructs are then surgically transplanted to replace missing segments of functioning tendon or ligament.
摘要:
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.
摘要:
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. Examples are provided showing the growth of hyaline cartilage for joint relinings, the growth of elastic cartilage for plastic or reconstructive replacement of cartilage structures, and repair of large bone defects.
摘要:
Polymeric materials are used to make a pliable, non-toxic, injectable porous template for vascular ingrowth. The pore size, usually between approximately 100 and 300 microns, allows vascular and connective tissue ingrowth throughout approximately 10 to 90% of the matrix following implantation, and the injection of cells uniformly throughout the implanted matrix without damage to the cells or patient. The introduced cells attach to the connective tissue within the matrix and are fed by the blood vessels. The preferred material for forming the matrix or support structure is a biocompatible synthetic polymer which degrades in a controlled manner by hydrolysis into harmless metabolites, for example, polyglycolic acid, polylactic acid, polyorthoester, polyanhydride, or copolymers thereof. The rate of tissue ingrowth increases as the porosity and/or the pore size of the implanted devices increases. The time required for the tissue to fill the device depends on the polymer crystallinity and is less for amorphous polymers versus semicrystalline polymers. The vascularity of the advancing tissue is consistent with time and independent of the biomaterial composition and morphology.
摘要:
Polymeric materials are used,to make a pliable, non-toxic, injectable porous template for vascular ingrowth. The pore size, usually between approximately 100 and 300 microns, allows vascular and connective tissue ingrowth throughout approximately 10 to 90% of the matrix following implantation, and the injection of cells uniformly throughout the implanted matrix without damage to the cells or patient. The introduced cells attach to the connective tissue within the matrix and are fed by the blood vessels. The preferred material for forming the matrix or support structure is a biocompatible synthetic polymer which degrades in a controlled manner by hydrolysis into harmless metabolites, for example, polyglycolic acid, polylactic acid, polyorthoester, polyanhydride, or copolymers thereof. The rate of tissue ingrowth increases as the porosity and/or the pore size of the implanted devices increases. The time required for the tissue to fill the device depends on the polymer crystallinity and is less for amorphous polymers versus semicrystalline polymers. The vascularity of the advancing tissue is consistent with time and independent of the biomaterial composition and morphology.
摘要:
A matrix structure containing attached cells such as endocrine cells, fibroblasts, endothelial cells or genitourinary cells is implanted in a patient adjacent tissue having a high surface area and vasculature such as mesentery, omentum or peritoneum tissue. Large volumes of cells can be attached to the matrix and the matrix implanted with minimum trauma and blood loss into a patient to produce a functional organ equivalent. Multiple matrix structures containing cells can be implanted to functionally resemble naturally occurring organs. Implanting multiple matrices between folds of the mesentery is particularly well suited for growth of endocrine structures, including liver, pancreas, and adrenal gland. The matrix structure is preferably formed from a biodegradable artificial polymer. Collagen and non-biodegradable materials can also be used, and the matrix structure can be overlaid with a material that enhances cell attachment. Materials such as angiogenesis factors can be incorporated into a matrix and implanted prior to implanting the matrix containing cells or the materials can be incorporated into the matrix containing cells. Cells attached to the matrix may be cultured in vitro prior to implanting. Matrix structures containing different types of cells can be implanted juxtapositioned with each other.
摘要:
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.
摘要:
Polymeric materials are used to make a pliable, non-toxic, injectable porous template for vascular ingrowth. The pore size, usually between approximately 100 and 300 microns, allows vascular and connective tissue ingrowth throughout approximately 10 to 90% of the matrix following implantation, and the injection of cells uniformly throughout the implanted matrix without damage to the cells or patient. The introduced cells attach to the connective tissue within the matrix and are fed by the blood vessels. The preferred material for forming the matrix or support structure is a biocompatible synthetic polymer which degrades in a controlled manner by hydrolysis into harmless metabolites, for example, polyglycolic acid, polylactic acid, polyorthoester, polyanhydride, or copolymers thereof. The rate of tissue ingrowth increases as the porosity and/or the pore size of the implanted devices increases. The time required for the tissue to fill the device depends on the polymer crystallinity and is less for amorphous polymers versus semicrystalline polymers. The vascularity of the advancing tissue is consistent with time and independent of the biomaterial composition and morphology.