EP1644478A2 - Structures non-tissees absorbables a etages multiples permettant la culture de cellules pancreatiques - Google Patents

Structures non-tissees absorbables a etages multiples permettant la culture de cellules pancreatiques

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Publication number
EP1644478A2
EP1644478A2 EP04777320A EP04777320A EP1644478A2 EP 1644478 A2 EP1644478 A2 EP 1644478A2 EP 04777320 A EP04777320 A EP 04777320A EP 04777320 A EP04777320 A EP 04777320A EP 1644478 A2 EP1644478 A2 EP 1644478A2
Authority
EP
European Patent Office
Prior art keywords
fibers
cell
cells
fibrous matrix
pga
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP04777320A
Other languages
German (de)
English (en)
Other versions
EP1644478A4 (fr
Inventor
Alireza Rezania
Mark Zimmerman
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
LifeScan Inc
Original Assignee
LifeScan Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by LifeScan Inc filed Critical LifeScan Inc
Publication of EP1644478A2 publication Critical patent/EP1644478A2/fr
Publication of EP1644478A4 publication Critical patent/EP1644478A4/fr
Withdrawn legal-status Critical Current

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Classifications

    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N5/00—Undifferentiated human, animal or plant cells, e.g. cell lines; Tissues; Cultivation or maintenance thereof; Culture media therefor
    • C12N5/06—Animal cells or tissues; Human cells or tissues
    • C12N5/0602—Vertebrate cells
    • C12N5/0676—Pancreatic cells
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/28—Materials for coating prostheses
    • A61L27/34—Macromolecular materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/36—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix
    • A61L27/38—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix containing added animal cells
    • A61L27/3804—Materials for grafts or prostheses or for coating grafts or prostheses containing ingredients of undetermined constitution or reaction products thereof, e.g. transplant tissue, natural bone, extracellular matrix containing added animal cells characterised by specific cells or progenitors thereof, e.g. fibroblasts, connective tissue cells, kidney cells
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/40—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L27/44—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L27/48—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix with macromolecular fillers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/56—Porous materials, e.g. foams or sponges
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/58—Materials at least partially resorbable by the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/022—Artificial gland structures using bioreactors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
    • A61F2250/003—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in adsorbability or resorbability, i.e. in adsorption or resorption time
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K35/00—Medicinal preparations containing materials or reaction products thereof with undetermined constitution
    • A61K35/12—Materials from mammals; Compositions comprising non-specified tissues or cells; Compositions comprising non-embryonic stem cells; Genetically modified cells
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N2533/00—Supports or coatings for cell culture, characterised by material
    • C12N2533/30—Synthetic polymers
    • C12N2533/40—Polyhydroxyacids, e.g. polymers of glycolic or lactic acid (PGA, PLA, PLGA); Bioresorbable polymers

Definitions

  • the present invention relates to biodegradable, implantable devices, e.g. tissue scaffolds which facilitate seeding and subsequent transplantation of cells bearing at least one characteristic of a pancreatic cell, including islets and pancreatic ductal cells, for treatment of diabetes.
  • the present invention also relates to seeding cells bearing at least one characteristic of a pancreatic cell into the bioabsorbable, implantable medical device.
  • the present invention relates to a method for treating diabetes by implanting such device in a diabetic patient .
  • DM Diabetes mellitus results from destruction of beta cells (Type I) in the pancreas or from insensitivity of muscle or adipose tissues to the hormone insulin (Type II) .
  • Current methods of treatment include diet and exercise, oral hypoglycemic agents, insulin injections, insulin pump therapy, and whole pancreas or islet transplantation.
  • the most common treatment of DM involves daily injections of endogenous source such as porcine, bovine, or human insulin. This treatment prevents severe hyperglycemia and ketoacidosis, but does not completely normalize blood glucose levels. In addition, this treatment fails to prevent the complications of the disease process, including premature vascular deterioration.
  • a second approach ' of treating diabetes is by transplantation of whole pancreas organ.
  • transplanting a whole adult pancreas is a major, technically complex operation which requires aggressive immunosuppressive drugs.
  • the applicability of this approach is restricted by the limited availability of cadaver pancreas.
  • a third treatment method involves transplanting islets of Langerhans cells into a diabetic patient.
  • islet grafting has been generally unsuccessful due to aggressive immune rejection of islets. Recent reports (N. Eng. J. Mecl.
  • Diabetologia 45:159-173, 2002
  • the membrane allows passage of small molecules, such as nutrients, oxygen, glucose, and insulin, while restricting the passage of larger humoral immune molecules and immune cells.
  • small molecules such as nutrients, oxygen, glucose, and insulin
  • an immunoisolation device with an abundant animal islet cell source, such as porcine islet cells, to treat DM.
  • porcine islet cells to treat DM.
  • this approach has had little success in large animal models or in clinic due to fibrosis of the device, limited oxygen supply within the pouch, and passage of small humoral immune molecules which ultimately lead to the loss of islet cells or islets.
  • An alternative approach to immunoisolation is the creation of an immunologically privileged site by transplanting Sertoli cells into a nontesticular site in a mammal. See, e.g., US 5,849,285, US 6,149,907, and US 5,958,404. Insulin-producing islets can be subsequently introduced to such immunologically privileged site.
  • the immunologically privileged site would allow transplantation of either human or animal derived islets.
  • One of the drawbacks of this approach is that the transplanted Sertoli and islet cells are not physically restricted to site of transplantation. This can lead to migration of these cells to unwanted tissue sites and ultimately to the loss of islets.
  • the immunologically privileged environment created by Sertoli cells is most effective only when the islets are in the close vicinity of the Sertoli
  • tissue engineering may offer alternative approaches to treat diabetes.
  • Tissue engineering strategies typically utilize biomaterials in combination with cells and/or growth factors to develop biological substitutes that can ultimately restore or improve tissue function.
  • Scaffold materials have been extensively studied as tissue templates, conduits, barriers, and reservoirs useful for tissue repair.
  • synthetic and natural materials in the form of foams, sponges, gels, hydrogels, textiles, and nonwoven structures have been used in vitro and in vivo to reconstruct or regenerate biological tissue, as well as to deliver chemotactic agents for inducing tissue growth (see, e.g., US5770417, US6022743, US5567612, and US5759830) .
  • the present invention provides a biodegradable, bioabsorbable, implantable medical device containing a fibrous matrix suitable for seeding cells bearing at least one characteristic of a pancreatic cell.
  • the device of the present invention contains a fibrous matrix made from fibers A and fibers B, wherein fibers A biodegrade faster than fibers B, and wherein fibers A and fibers B are present in such relative amounts and combined in such fashion that the resulting matrix possesses properties desired for seeding cells bearing at least one characteristic of a pancreatic cell to be used in the treatment of diabetes .
  • fibers A are formed from a copolymer of PGA and PLA, where PGA constitutes from about of 50 to about 95 weight percent and PLA constitutes from about 5 to about 50 weight percent; and fibers B are formed from a copolymer of PGA and PLA, where PGA constitutes from about 2 to about 50 weight percent and PLA constitutes from about 50 to about 98 weight percent.
  • the weight ratio of fibers A versus fibers B ranges from about 19:1 to about 1:19, more preferably from about 9:1 to about 1:9.
  • the bioabsorbable, implantable medical device has been seeded with cells bearing at least one characteristic of a pancreatic cell.
  • the present invention provides a method for treating diabetes by implanting in a diabetic patient a bioabsorbable, implantable medical device, seeded with cells bearing at least one characteristic of a pancreatic cell.
  • a bioabsorbable, implantable medical device seeded with cells bearing at least one characteristic of a pancreatic cell.
  • Figure 1 depicts mice islets seeded within a 100% 90/10 PGA/PLA nonwoven mat. The cells were viable as evidenced by positive fluorescent staining for Calcein.
  • Figure 2 depicts rat ductal cells seeded within a 100% 90/10 PGA/PLA nonwoven mat. The cells were viable as evidenced by positive fluorescent staining for Calcein.
  • the present invention provides a biodegradable bioabsorbable, implantable medical device containing a fibrous matrix suitable for incorporating or seeding cells bearing at least one characteristic of a pancreatic cell.
  • the present invention also provides a bioabsorbable, implantable medical device containing a fibrous matrix incorporated with cells bearing at least one characteristic of a pancreatic cell, as well as methods for making such device incorporated with the desired cells.
  • the present invention provides a method for treating diabetes by implanting such device in a diabetic patient.
  • the present invention provides a bioabsorbable, implantable medical device containing a fibrous matrix suitable for seeding cells bearing at least one characteristic of a pancreatic cell.
  • matrix refers to a three-dimensional porous material that is suitable for seeding cells bearing at least one characteristic of a pancreatic beta cell and is biocompatible, biodegradable and resorbable by the body.
  • biocompatible is meant that the matrix of the present invention does not substantially adversely affect any desired characteristics of the cells to be seeded within the matrix, or the cells or tissues in the area of a living subject where the device is to be implanted, or any other areas of the living subject.
  • biodegradable or “absorbable” is meant that the matrix will be gradually degraded or absorbed after the device made of the matrix is delivered to a site of interest inside the body of a living subject.
  • a living subject is meant to include any mammalian subject, including a primate, porcine, canine or urine subject, and particularly a human subject.
  • the matrix of the present device permits tissue ingrowth in order for the growing tissue to replace the resorbing matrix.
  • the matrix of the present device is also capable of providing and maintaining structural support required for a particular device for so long as is required to affect the repair and/or regeneration of the tissue, including that time in which the matrix is being resorbed by the body.
  • the device of the present invention has a desirable rate of resorption which approximates the rate of replacement of the fibrous matrix by tissue.
  • devices of the present invention advantageously balance the properties of biodegradability, resorption, structural integrity over time and the ability to facilitate tissue in-growth.
  • the matrix is constructed from at least two different fibrous materials, e.g. fibers, one of which iodegrades faster than the other.
  • the fibers are of such composition and structure and are combined in such a way, with respect to both relative fiber amounts and matrix structure, to enhance retention and function of seeded cells bearing at least one characteristic of a pancreatic cell, especially a pancreatic beta cell, and to facilitate infiltration and ingrowth of tissue.
  • Biodegradable materials suitable for use in the preparation of fibers and fibrous matrices include various biodegradable polymers such as aliphatic polyesters, poly (amino acids), copoly (ether-esters) , polyalkylene oxalates, polyamides, poly (iminocarbonates) , polyorthoesters, polyoxaesters, polyamidoesters, poly (anhydrides) , polyphosphazenes, or copolymers or blends thereof. Certain polyoxaester copolymers can further include amine groups.
  • fibers and fibrous matrices are preferably made of biodegradable polymers selected from polylacetic acid (PLA) , polyglycolic acid (PGA) , ⁇ - polycaprolactone (PCL) , polydioxanone (PDO) , polyoxaesters, or copolymers or blends thereof.
  • the scaffold, matrix or construct of the present device is characterized by having interconnecting pores or voids, which facilitate the transport of nutrients and/or invasion of cells into the scaffold.
  • the interconnected voids range in size from about 20 to 500 microns, preferably 50 to 400 microns, and constitute about 70 to 95 percent of the total volume of the construct.
  • the fibrous matrix of the present device is characterized as an organized network in the form of threads, yarns, nets, laces, felts and nonwovens, or a combination of these various forms.
  • the fibrous matrix of the present device is constructed by combining at least two different bioabsorbable fibrous materials, e.g. fibers or filaments, one of which biodegrades faster than the other.
  • the terms "fibers A" and "fibers B" used herein refer to the two different types of fibers used to make the matrix of the present device.
  • the fibers may be solid, or hollow, or may be of a sheath/core construction.
  • filaments may be co-extruded to produce a sheath/core construct, where each filament contains a sheath of biodegradable polymer that surrounds one or more cores made of another biodegradable polymer. Filaments with a fast-absorbing sheath surrounding a slow-absorbing core may be desirable in instances where extended support is necessary for tissue ingrowth.
  • filaments can be formed by coating biodegradable fibers, e.g., biodegradable glass fibers, with a biodegradable polymer.
  • a continuous multifilament yarn (Yarn A) is formed from a copolymer of PGA and PLA, where PGA constitutes from about of 50 to about 95 weight percent and PLA constitutes from about 5 to about 50 weight percent.
  • Another continuous multifilament yarn (Yarn B) is formed from a copolymer of PGA and PLA, where PGA constitutes from about 2 to about 50 weight percent and PLA constitutes from about 50 to about 98 weight percent.
  • Yarn A degrades faster than Yarn B.
  • Both types of filaments are of a diameter from about 2 to about 200 microns, preferably from about 5 to about 100 microns.
  • Yarn A and Yarn B are both cut into uniform lengths between 1/4" and 2". Fiber in this form is known as "staple fiber”.
  • Predetermined amounts of staple fiber produced from Yarn A and Yarn B are combined to form the matrix.
  • the predetermined amounts of fibers from Yarn A and Yarn B, respectively, may vary depending upon, for example, the composition of the respective fibers, the construction of the respective fibers, and the particular organization of the respective fibers, which determines the structure of the fibrous matrix produced from the organized fibers.
  • the relative amounts of the two types of fibers are selected in order to produce a fibrous matrix with the desired properties for seeding cells bearing at least one characteristic of a pancreatic cell.
  • the selection is such that the matrix produced not only possesses the structural integrity required for tissue repair and/or regeneration, but also enhances tissue growth and infiltration into the matrix.
  • the selection is such that the rate of resorption of the matrix approximates the rate of replacement of the matrix by tissue, thus preserving the structural integrity of the implant throughout the treatment period.
  • the weight ratio of fibers A e.g., staple fiber from Yarn A
  • fibers B e.g., staple fiber from Yarn B
  • the two different types of fibers can be combined by any means convenient and suitable, e.g., by a wet lay process or a dry lay process.
  • This powder possesses a low melting temperature and acts as a binding agent later in the process to increase the tensile strength and shear strength of the nonwoven structure, or fibrous matrix.
  • the preferred particulate powder size of PCL is in the range of 10-500 ⁇ m in diameter, and more preferably 10-150 ⁇ m in diameter.
  • Additional binding agents include a biodegradable polymeric binders selected from the group consisting of polylactic acid, polydioxanone and polyglycolic acid.
  • the screen allows water to pass through, but traps the fiber. If PCL powder is included in the mixture, some of the powder is trapped as well. After the water has drained through the screen, the mat of fibers is removed. The mat containing PCL powder fibers is then subjected to heat in order to melt the PCL.
  • the melt temperature range is between about 60°C and about 100°C, preferably between 60-80°C. It is crucial to perform this step at a temperature that is above the melting point of PCL powder or similar binding agent, and below the softening point of the fibers. This is necessary to avoid damaging the staple fibers.
  • the powder melts flows around the filaments and cools to a solid state.
  • the molten powder When the molten powder returns to a solid state, some of the points where the filaments intersect are encapsulated in solid polymer and locked in place. The powder thus acts as a binding agent, increasing the strength of the matrix.
  • the matrix is rinsed overnight in water, followed by another overnight incubation in ethanol to remove any residual chemicals or processing aids used during the manufacturing process.
  • the matrix may then be sterilized by a number of standard techniques, such as exposure to ethylene oxide or gamma radiation.
  • a dry lay process is used to form the matix, predetermined amounts of the two different types of fibers are opened and carded on standard nonwoven machinery, resulting in webbed staple fibers.
  • the webbed staple fibers are needle punched to form a dry lay needle-punched, fibrous nonwoven mat or matrix.
  • the nonwoven fibrous matrices may be formed into different shapes, or configurations, such as disks, rectangles, squares, stars and tubes, by thermal or non-thermal punching of the nonwoven sheets with dies of appropriate shape and dimension.
  • the fibrous matrix has a gradient structure.
  • a fibrous implant may have a gradual or rapid, but continuous, transition from rapidly degrading fibers at the periphery of the implant, to slowly degrading fibers at the center, relatively speaking. Alternatively, the transition may occur between the top of the matrix to the bottom of the matrix.
  • One profile for transition from rapidly degrading fibers to slowly degrading fibers may be, for instance, from about 100% rapidly degrading fibers, to about 75% rapidly degrading fibers/25% slowly degrading fibers, to about 50% rapidly degrading fibers/50% slowly degrading fibers, to about 25% rapidly degrading fibers/75% slowly degrading fibers, to about 100% slowly degrading fibers, proceeding from the periphery of the implant to the center.
  • the three-dimensional matrices of the present invention may be coated with a biodegradable, fibrous and porous polymer coating, e.g. a sheet, preferably produced by an electrostatic spinning process.
  • the electrostatically spun polymer coating can provide the nonwoven matrices with enhanced mechanical properties and the ability to hold sutures.
  • Exemplary biodegradable polymeric coats may be prepared from polymers selected from the group consisting of polylactic acid, polyglycolic acid, polycaprolactone and copolymers thereof. It should be recognized that the device of the present invention may include a homogenous mixture of filaments in the form of a sheet, or nonwoven matrix. However, the mixture need not be homogenous and the final form need not be a sheet. Devices containing a non-homogenous mixture of filaments may be desirable in applications where total absorption time and/or loss of strength over time varies throughout the material.
  • a multi-layered device composed of a first layer in which the majority of filaments are prepared from a (90/10) PGA/PLA copolymer, and a second layer in which the majority of filaments are prepared from a (95/5) PLA/PGA copolymer.
  • a first layer in which the majority of filaments are prepared from a (90/10) PGA/PLA copolymer
  • a second layer in which the majority of filaments are prepared from a (95/5) PLA/PGA copolymer.
  • Similar structures may be produced in any shape.
  • cylinders or prisms with fast (or slow) absorbing cores may be produced during a nonwoven process by segregating the different filaments during the forming process .
  • the porous nonwoven matrix can be chemically crosslinked or combined with hydrogels, such as alginates, hyaluronic acid, collagen gels, and poly (N-isopropylacryalmide) .
  • the matrix may be modified, either through physical or chemical means, to contain biological or synthetic factors that promote attachment, proliferation, differentiation, and/or matrix synthesis of targeted cell types.
  • the bioactive factors can be included in the matrix for controlled release of the factor to elicit a desired biological function.
  • Growth factors, extracellular matrix proteins, and biologically relevant peptide fragments that can be used with the matrices of the current invention include, but are not limited to, members of TGF- ⁇ family, including TGF- ⁇ l, 2, and 3, bone morphogenic proteins (BMP-2, -4, 6, -12, -13 and -14), fibroblast growth factors-1 and -2, platelet-derived growth factor-AA, and -BB, platelet rich plasma, insulin growth factor (IGF-I, II) growth differentiation factor (GDF-5, -6, -8, -10), angiogen, erythropoiethin, placenta growth factor, angiogenic factors such as vascular endothelial cell-derived growth factor (VEGF) , glucacgon- like peptide I, exendin-4, pleiotrophin, endothelin, parathyroid hormone, stem cell factor, colony stimulating factor, tenascin-C, tropoelastin, thrombin-derived peptides, anti
  • the biological factors can be obtained either through a commercial source, isolated and purified from a tissue or chemically synthesized.
  • the three- dimensional device of the present invention is incorporated or seeded with cells bearing at least one marker characteristic of a pancreatic cell.
  • the term "cells”, as used herein, refers to isolated cells, cells lines (including cells engineered in vi tro) , any preparation of living tissue, including primary tissue explants and preparations thereof.
  • pancreatic cell is meant to include cells of both endocrine and exocrine pancreatic tissues.
  • the endocrine pancreas is composed of hormone-producing cells arranged in clusters or islets of Langerhans .
  • pancreatic polypeptide PP
  • the endocrine pancreas includes the pancreatic acini and the pancreatic duct.
  • Pancreatic acinar cells synthesize a range of digestive enzymes.
  • Ductal cells secret bicarbonate ions and water in response to the hormone secreted from the gastrointestinal tract.
  • pancreatic cells include alpha cells, beta cells, delta cells, PP cells, acinar cells, ductal cells or other cells in a mammalian pancreas.
  • Markers characteristic of a pancreatic cell include the expression of cell surface proteins or the encoding genes, the expression of intracellular proteins or the encoding genes, cell morphological characteristics, and the production of secretory products such as glucagons, insulin and somatostatin.
  • known immunofluorescent, immunochemical, polymerase chain reaction, in si tu hybridization, Northern blot analysis, chemical or radiochemical methods can readily ascertain the presence of absence of a islet cell specific characteristic.
  • the device of the present invention is incorporated with pancreatic islets.
  • islets as used herein includes both islets isolated from a mammalian pancreas as masses formed by alpha cells, beta cells, delta cells and PP cells, and islets formed in vitro from isolated or engineered islet cells or cells that bear at least one marker, preferably two or more markers, characteristic of an islet cell.
  • the present device is seeded with cells engineered in vi tro having at least one marker characteristic of a pancreatic islet cell, preferably, a pancreatic beta cell.
  • pancreatic beta cells Markers characteristic of pancreatic beta cells have been described, and include the expression of the Pdxl , Ngn3 f Hlxb9 , Nkx6 , Isll , Pax 6 , Neurod, Hnfla r Hnf6 genes and the encoded proteins, and the secretion of insulin, among others.
  • Such cells can be produced in vi tro by, e.g., differentiating adipose stromal cells .
  • the device of the present invention is incorporated with pancreatic ductal cells .
  • Other cells, such as Sertoli cells can be co-seeded with the cells having at least one marker characteristic of a pancreatic cell.
  • the scaffold is contacted and incubated with a suspension containing the cells, or clusters of cells (e.g., islets) or the tissue preparation to be seeded.
  • the incubation can be performed for a short period of time ( ⁇ 1 day) just prior to implantation, or for longer (> 1 clay) period to allow for enhanced cell attachment and matrix synthesis within the nonwoven scaffold prior to implantation.
  • the present invention provides a method for treating a human diabetic patient by implanting at a site in the patient, a device of the present invention which is seeded with cells bearing at least one characteristic of a pancreatic cell.
  • the cells seeded in the device for treating the patient can be of an autologous, allogenic or xenogenic origin.
  • the site where the device can be implanted can be any clinically relevant site, such as the liver, the natural pancreas, the renal subcapsular space, the mesentery, the omentum, a subcutaneous pocket, or the peritoneum.
  • the site can be an immunologically privileged site, either naturally existing or created using, e.g., Sertoli cells.
  • Example 1 Preparation Of Three-Dimensional Nonwoven Fibrous Matrices Or Mats
  • a copolymer of PGA/PLA (90/10) was melt- extruded into a continuous multifilament yarn by conventional methods of making yarn and subsequently oriented in order to 'increase strength, elongation and energy required to rupture. The same method was used to prepare yarns of a 95/5 PLA/PGA copolymer.
  • the yarns comprised filaments of approximately 20 microns in diameter. These yarns were then cut and crimped into uniform 2-inch lengths to form a 2-inch staple fiber.
  • a dry lay needle-punched nonwoven mat was then prepared utilizing the 90/10 PGA/PLA copolymer staple fiber and the 95/5 PLA/PGA fiber.
  • the staple fibers were opened and carded on standard nonwoven machinery.
  • the resulting mat was in the form of webbed staple fibers.
  • the webbed staple fibers were needle punched to form the dry lay needle- punched, fibrous nonwoven mat.
  • a number of dry lay nonwoven matrices were then prepared utilizing fiber selection as follows: (a) 100% of fiber prepared from the (90/10) PGA/PLA copolymer; (b) 100% of fiber prepared from the (95/5) PLA/PGA copolymer; (c) a fiber mixture of 50% by weight of fibers prepared from the (95/5) PLA/PGA copolymer and 50% by weight of fibers prepared from the (90/10) PGA/PLA copolymer; d) 100% of the fiber prepared from PDO polymer.
  • Example 2 Seeding Of Murine Islets Within Nonwoven Scaffolds Islets were isolated from Balb/c mice by collagenase digestion of the pancreas and Ficoll density gradient centrifugation followed by hand picking of islets.
  • Nonwoven scaffolds comprised of 100% 90/10 PGA/PLA, 100% PDO, or 50:50 mix of 100% 90/10 PGA/PLA: 95/5 PLA/PGA, were prepared as described in Example 1 and seeded with 500 fresh islets and cultured for 1 day in Ham' s-FlO medium (Gibco Life Technologies, Rockville, MD) supplemented with bovine serum albumin (0.5%), nicotinamide (10 mM) , D-glucose (10 mM) , L-glutamine (2 mM) , IBMX (3-Isobutyl-l- methylxanthine, 50 mM) , and penicillin/streptomycin.
  • the islets residing in the scaffolds were stained with calcein and ethidium homodimer (Molecular Probes, Oregon) to determine the viability of the seeded cells.
  • Majority of the islets stained positive for calcein, indicating viable cells within the lumen of the pouch.
  • Figure 1 depicts viable islets seeded within a 100% 90/10 PGA/PLA nonwoven scaffold.
  • Recipient mice were anesthetized with an intraperitoneal injection of a Ketamine/Xylazine cocktail.
  • the cell seeded scaffolds (8 mm in diameter) or MATRIGEL gel were wrapped with the thin layer of the epididymal fat pad and sutured to the surrounding fat tissue. The incision was sutured and the skin closed with surgical clips.
  • Tail vein blood was collected every 2 days to measure non-fasting blood glucose levels. Grafts were removed at various times to confirm a return to hyperglycemia and also for histological analysis.
  • mice transplanted with the nonwoven scaffold were normoglycemic; whereas all of the mice transplanted with islets seeded in the MATRIGEL gel reverted to hyperglycemia after 6 days of transplantation.
  • the blood glucose levels reverted to hyperglycemic levels (>500 mg/dl) .
  • Example 4 Seeding Of Murine Pancreatic Ducts Within A Nonwoven Scaffold Pancreatic ducts were isolated from Sprague Dawley rats (SD) by collagenase digestion of the pancreas and Ficoll density gradient centrifugation followed by hand picking of pancreatic ducts. About 100 ducts were seeded onto a nonwoven scaffold comprised of 100% PGA/PLA fibers.
  • the ducts were cultured on the scaffold (5 mm in diameter) for 4 wks in Ham' s-FlO medium (Gibco Life Technologies, Rockville, MD) , supplemented with bovine serum albumin (0.5%), nicotinamide (10 mM) , D-glucose (10 mM) , L-glutamine (2 mM) , IBMX (3-Isobutyl-l-methylxanthine, 50 mM) , and penicillin/streptomycin.
  • the cells residing in the scaffolds were stained with calcein and ethidium homodimer (Molecular Probes, Oregon) to determine the viability of the seeded cells. Majority of the cells stained positive for calcein, indicating viable cells within the lumen of the pouch.
  • Figure 2 depicts viable ductal cells seeded within a 100% 90/10 PGA/PLA nonwoven scaffold.

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Abstract

L'invention concerne un dispositif biodégradable implantable contenant une matrice fibreuse construit à partir de fibres A et de fibres B, dans laquelle les fibres A présentent une vitesse de biodégradation plus élevée que les fibres B, et les fibres A et les fibres B sont présentes en quantités relatives et sont arrangées de telle manière que la matrice fibreuse présente les propriétés souhaitables pour permettre la mise en culture et la transplantation subséquente de cellules présentant au moins une caractéristique de cellule pancréatique. L'invention concerne également un dispositif biodégradable implantable contenant une matrice fibreuse ensemencée avec des cellules présentant au moins une caractéristique d'une cellule pancréatique. Une méthode de traitement du diabète consistant à implanter à un patient diabétique un dispositif comprenant des cellules ensemencées, est en outre décrite.
EP04777320A 2003-06-30 2004-06-29 Structures non-tissees absorbables a etages multiples permettant la culture de cellules pancreatiques Withdrawn EP1644478A4 (fr)

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US48380503P 2003-06-30 2003-06-30
PCT/US2004/021044 WO2005005609A2 (fr) 2003-06-30 2004-06-29 Structures non-tissees absorbables a etages multiples permettant la culture de cellules pancreatiques

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GB0618787D0 (en) 2006-09-23 2006-11-01 Univ Nottingham Degradable composite
RU2484090C2 (ru) * 2007-12-07 2013-06-10 Эбботт Гмбх Унд Ко.Кг 5-галогензамещенные производные оксиндола и их применение для лечения вазопрессинзависимых заболеваний
GB201317636D0 (en) 2013-10-04 2013-11-20 Isis Innovation Scaffold
AU2017317607B2 (en) 2016-10-19 2018-05-17 Beta Cell Technologies Pty Ltd Cell population seeding in dermal matrices for endocrine
US11730696B2 (en) 2016-10-20 2023-08-22 Australian Foundation for Diabetes Research Cell associated scaffolds for delivery of agents
CN109395095B (zh) * 2017-09-18 2021-09-24 武汉原生原代生物医药科技有限公司 体内用生物膜及其制备方法和用途

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WO2002051463A2 (fr) * 2000-12-22 2002-07-04 Ethicon, Inc. Dispositifs implantables biodegradables pour la reparation ou la regeneration musculosquelettique
US20020119179A1 (en) * 2000-12-22 2002-08-29 Alireza Rezania Implantable biodegradable devices for musculoskeletal repair or regeneration

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DE69121587T3 (de) * 1990-12-06 2000-05-31 Gore & Ass Implantierbare bioresorbierbare artikel
US6113640A (en) * 1997-06-11 2000-09-05 Bionx Implants Oy Reconstructive bioabsorbable joint prosthesis
US6350284B1 (en) * 1998-09-14 2002-02-26 Bionx Implants, Oy Bioabsorbable, layered composite material for guided bone tissue regeneration
US6306424B1 (en) * 1999-06-30 2001-10-23 Ethicon, Inc. Foam composite for the repair or regeneration of tissue

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WO2002051463A2 (fr) * 2000-12-22 2002-07-04 Ethicon, Inc. Dispositifs implantables biodegradables pour la reparation ou la regeneration musculosquelettique
US20020119179A1 (en) * 2000-12-22 2002-08-29 Alireza Rezania Implantable biodegradable devices for musculoskeletal repair or regeneration

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Title
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WO2005005609A2 (fr) 2005-01-20
EP1644478A4 (fr) 2008-07-23

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