US20050191748A1 - Filamentary means for introducing agents into tissue of a living host - Google Patents

Filamentary means for introducing agents into tissue of a living host Download PDF

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Publication number
US20050191748A1
US20050191748A1 US11/107,230 US10723005A US2005191748A1 US 20050191748 A1 US20050191748 A1 US 20050191748A1 US 10723005 A US10723005 A US 10723005A US 2005191748 A1 US2005191748 A1 US 2005191748A1
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poly
cells
core
bioabsorbable
porous
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US11/107,230
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Thomas Barrows
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Aderans Research Institute Inc
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Aderans Research Institute Inc
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Priority claimed from PCT/US2000/003488 external-priority patent/WO2000045736A1/en
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Priority to US11/107,230 priority Critical patent/US20050191748A1/en
Publication of US20050191748A1 publication Critical patent/US20050191748A1/en
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/36Materials 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
    • A61L27/38Materials 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
    • A61L27/3839Materials 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 the site of application in the body
    • A61L27/3843Connective tissue
    • A61L27/3847Bones
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/10Hair or skin implants
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/36Materials 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
    • A61L27/38Materials 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
    • A61L27/3804Materials 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
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0067Means for introducing or releasing pharmaceutical products into the body
    • A61F2250/0068Means for introducing or releasing pharmaceutical products into the body the pharmaceutical product being in a reservoir

Definitions

  • This invention relates to means for the delivery of agents into a living body. More specifically it relates to filaments comprising porous bioabsorbable polymers, which facilitate the implantation of living cells and other agents, such as drugs, into specific tissues, including skin and bone, for the purposes of site-specific drug or cell release, gene therapy, and the facilitation of the regeneration of tissue, including the regeneration of bone and hair tissue.
  • '552 is an implant of a porous core of a bioabsorbable polymer, surrounded by a non-porous surface skin of the bioabsorbable polymer. That particular device is designed for use in delivering a biologically active agent to a living host when implanted therein.
  • the device disclosed by Dunn et al. '552 is also designed so that it can act as a matrix to promote tissue regeneration at an implant site. (Id.)
  • bioabsorbable devices described above were that they could be implanted into a living host and left in place to do what they were designed to do, without the necessity of removal therefrom. The devices would be absorbed by the host over time.
  • the bioabsorbable devices disclosed in the references described above only the device of Dunn et al. '552 is designed to act as both scaffolding and delivery agent. That device has limited flexibility, because of the way it is designed. What is needed is a bioabsorbable fiber or composite thereof, which is capable of being processed into a scaffolding for tissue formation, and which is capable of delivering agents to a living host when implanted therein.
  • the present invention meets that need.
  • the present invention also meets a need for an inexpensive and relatively painless means for regenerating hair.
  • Plastic surgery is one of the few means available to correct male pattern baldness, today.
  • the amount of permanently hair-bearing donor tissue available can significantly affect the feasibility and outcome of the procedure.
  • In vitro growth techniques have been developed to increase the amount of hair follicle cells available for use in such procedures. See, e.g., Seigi Arase, et al. Tokushima J. exp. Med 36: 87-95 (1989); and Edoardo Raposio, et al. Plastic and Reconstructive Surgery pp. 221-226 (July 1998).
  • the present invention utilizes a modified form of the bioabsorbable polymeric means developed for use in implantable devices, as described above, to deliver hair follicle cells transdermally and to promote the regeneration of hair therein.
  • the present invention provides a new means for the introduction of agents into a living host, a means which offers several advantages over known means in use today, such as those described briefly above.
  • the present invention provides a filamentary means for the introduction of agents into a living host, comprising a filament comprising a solid core and a porous sheath which coats at least a portion of the solid core.
  • a filamentary means for the introduction of agents into a living host, comprising a filament comprising a solid core and a porous sheath which coats at least a portion of the solid core.
  • both the solid core and the porous sheath are bioabsorbable.
  • the porous sheath is preferably bioabsorbable but the core need only be biocompatable, not bioabsorabable.
  • the solid core is preferably wire when the filamentary means is designed to be used to deliver an agent, such as hair follicle cells, into the skin of a living host.
  • the solid core is preferably glass or ceramic when the filamentary means is to be used to deliver an agent, such as cells or pharmaceutical agents, into bone through implantation of the filamentary means into the body of the host.
  • the porous sheath is preferably in the form of reticulated foam that is well adhered to the core but is capable of separating from the core after a period of several days in vivo.
  • the agent to be delivered with the filamentary means is a drug
  • the porous sheath is preferably in the form of a hydrogel and the porosity is on a molecular size scale.
  • the filamentary means of the present invention provides means for delivery of cells or other agents from outside the body of a living host into the skin of the host, such as a mammal, with minimal trauma to the host.
  • the filamentary means is comprised of a bioabsorbable core with a bioabsorbable porous sheath which coats at least a portion of the core
  • the filamentary means can be implanted into specific tissue within a living host and used to deliver agents to the specific tissue when implanted therein.
  • the implantable embodiment of the filamentary means can serve as a surface for osteoblast attachment and as a scaffold for bone regeneration upon implantation into the bone tissue of a living host.
  • the above-cited features of the filamentary means of the present invention enable it to be used for a variety of purposes including, but not limited to, hair follicle regeneration, gene therapy and encapsulated cell delivery, bone regeneration, and trans-dermal drug delivery.
  • Another embodiment of the present invention is a method of making a filamentary means for introducing an agent into a living host, comprising providing a solid filament, a bioabsorbable polymer, and a pore-forming agent, mixing the bioabsorbable polymer with the pore-forming agent, coating the resulting mixture onto at least a portion of the filament, and substantially removing or decomposing the pore-forming agent.
  • inventions include devices designed to enable one to use the filamentary means of the invention to deliver various agents into a living host, methods for making such devices, and methods for using the devices of the present invention to deliver agents into a living host.
  • the devices and methods of the present invention enable one to regenerate hair follicles, to introduce genetically altered cells or encapsulated cells to a living host transdermally, to regenerate bones, and to deliver drugs transdermally.
  • the devices and methods of the present invention are described briefly below.
  • One embodiment of the present invention is a hair follicle cell implant device designed to implant hair follicle cells into the skin of a living host.
  • Another embodiment of the hair follicle cell implant device of the present invention is a method of making the implant device.
  • Yet another embodiment is a method of using the implant device to deliver hair follicle cells to implant such cells into the skin of a living host, preferably into the scalp of a human being suffering from male pattern baldness.
  • the hair follicle cell implant device of the present invention comprises a plurality of filaments, each of which has a first end and a second end and comprises a solid core and a bioabsorbable porous sheath which coats the solid core, and a semi-rigid backing with the second end of each filament embedded therein such that the first end of each filament protrudes therefrom.
  • the first end of each filament protrudes from the semi-rigid backing a sufficient length to penetrate the skin of a living host when the device is in contact therewith.
  • the filaments are preferably spaced the same distance apart as hairs on the normal surface of skin of the living host.
  • the hair follicle cell implant device of the present invention is preferably made by the steps comprising: providing a plurality of filaments, each of which has a first end and a second end and comprises a solid core and a bioabsorbable porous sheath which coats the solid core; and fixing the second end of each of the plurality of filaments in a semi-rigid backing such that the filaments are spaced the same distance apart as hairs on the skin of a normal living host, and such that the second end of each of the plurality of filaments protrudes from the semi-rigid backing at a depth sufficient to penetrate the skin of the living host when placed into contact therewith.
  • the hair follicle cell implant device is used to stimulate hair growth according to a method comprising: seeding the boabsorbable porous sheath at the first end of each filament with hair follicle cells, introducing the cells into the skin of a living host by puncturing the skin with the first end of each filament, and removing the device from the skin after sufficient time has passed to allow the porous coating within the skin to separate from the solid core of each filament, leaving the porous coating and hair follicle cells in the skin.
  • hair follicle cell implant device provides means for delivering cultured cells harvested from hair follicles into the skin of a host, such as the bald scalp of a human male, such that said cells are able to generate new hair follicles.
  • the new hair follicles, once generated, will continue to grow and be maintained in the dermis of the host.
  • Another advantage of these embodiments of the present invention is that they provide a means for the simultaneous implantation of hair follicle cells into multiple sites in the skin such that the spacing between each individual implant is approximately the same as the spacing between the hair follicles in the normal scalp.
  • the present invention provides an efficient device and method of restoring a normal density of normally functioning hair follicles in the hairless scalp as an effective, natural, and permanent remedy for baldness.
  • the present invention is a method of using the filamentary means of the present invention to deliver genetically modified cells into normal healthy skin, such that the cells deliver a therapeutically efficacious systemic level of the desired gene product.
  • a filamentary means comprising a filament comprising a solid core having a first end and a second end and a porous sheath which coats at least the first end of the solid core, wherein the porous sheath is bioabsorbable, is used to deliver genetically modified cells into the skin of a living host, according to the steps comprising: providing the filament, seeding the porous sheath at the first end of the filament with the genetically transformed cells, introducing the cells into the skin of the living host by puncturing the skin with the first end of the filament, and removing the filament from the skin after sufficient time has passed to allow the porous coating to separate from the filament at the first end of the solid core of the filament, leaving the porous coating and genetically transformed cells in the skin.
  • An advantage of this embodiment of the present invention is that it provides a means for the delivery of encapsulated or otherwise immunoprotected cells into normal healthy skin such that the cells delivered therewith take over the function of cells in other organs that have lost their required function due to disease such as diabetes.
  • Another advantage of this embodiment of the invention is that it also provides a means for the delivery of genetically modified cells into diseased or ulcerated skin to treat the disease or provide growth factors to heal the ulcers.
  • An advantage of another embodiment of the present invention is that it provides that a rigid scaffold with a highly porous surface, which can be implanted into a living host, and maintained for a long enough period of time to facilitate new bone formation.
  • the porous surface enables this embodiment of the invention to be used as a means for the delivery of osteoblasts and/or other osteoinductive substances into bone defects, gaps, or fusion devices.
  • Another embodiment of the present invention is a device for delivery of a drug through the skin, comprising: a plurality of filaments each of which has a fist end and a second end and comprises a solid core and a bioabsorbable polymer sheath in which the drug is soluble and permeable; a semi-rigid backing having a first side and a second side, wherein the second side of the semi-rigid backing defines a reservoir, wherein each of the plurality of filaments is fixed in the semi-rigid backing such that the first end of each filament protrudes from the first side of the semi-rigid backing and the second end of each filament extends to the second side of the semi-rigid backing such that it is in contact with the reservoir.
  • An advantage to the device of delivery of a drug through the skin of the present invention is that it provides a means for the continuous delivery of drugs through the skin that normally do not penetrate skin from a reservoir placed on the surface of the skin.
  • FIG. 1 a is a schematic view of the filament in longitudinal section, showing the solid core ( 1 ) and the porous sheath ( 2 ), without details of the porous structure.
  • FIG. 1 b is a schematic view of the filament in transverse section, showing the solid core ( 1 ) and porous sheath ( 2 ).
  • FIG. 2 is a schematic sectional view of a hair implant device with an array of the core-sheath filaments ( 3 ) shown imbedded in a semi-rigid backing ( 4 ) which maintains the filaments in a stable, rigid parallel configuration.
  • FIG. 3 is a schematic sectional view of the hair implant device with the array of filaments ( 3 ) imbedded in the semi-rigid backing ( 4 ), immersed in a vessel ( 5 ) containing a tissue culture broth of free floating cells ( 6 ) derived from the hair follicles of a living host.
  • FIG. 4 a depicts a sectional view of a single filament with cultured cells ( 6 ) contained within the porous sheath ( 2 ) surrounding the solid core ( 1 ) of a filament, which has been implanted in the skin through the full thickness of the dermis ( 7 ).
  • the filament has been present in the skin for several days during which time the epidermis ( 8 ) has begun to grow down the outside of the filament.
  • FIG. 4 b depicts a sectional view of the implant site after the filament core ( 1 ) has been removed by pulling out the semi-rigid backing ( 4 ) to which it is attached out of the dermis ( 7 ) and epidermis ( 8 ). Note the resulting separation of the porous, cultured cell laden sheath ( 2 ) from the core. As shown in this figure, the implanted sheath has been present for a long enough time that new matrix cells ( 9 ) are beginning to elongate a new hair shaft ( 10 ).
  • FIG. 5 a depicts a sectional view of a single filament with cultured cells ( 6 ) contained within the porous sheath ( 2 ) surrounding the solid core ( 1 ) of the filament, which has been implanted in the skin through the full thickness of the dermis ( 7 ).
  • the filament is shown in the state in which it would be if it had been present in the skin only long enough for the porous coating to soften and detach from the solid core, but not long enough for the epidermis ( 8 ) to grown down the outside of the filament.
  • FIG. 5 b depicts the implant site after the filament core has been removed by pulling out the semi-rigid backing to which it was attached as shown in FIG. 5 a.
  • pulling out the semi-rigid backing and core has resulted in separation of the cell laden porous sheath ( 2 ) from the solid core.
  • Sufficient time has elapsed that the epidermis ( 8 ) has grown over the implant site, the porous bioabsorbable coating has resorbed, and the implanted cultured cells ( 6 ) have survived and are functioning properly.
  • FIG. 6 is a schematic representation of filaments comprised of a solid core ( 1 ) and a porous coating ( 2 ) that are bonded together.
  • the process that is utilized to create the bonds between the filaments for example by heating and cooling, preferably is the same process that is used to create porosity in the coating
  • FIG. 7 is a scanning electron micrograph (SEM) of the device described in Example 1, at a scale of 1 mm.
  • FIG. 8 is an SEM of the device described in Example 1, viewing the wires on end showing the exposed tips of the wires and the surrounding coatings of porous, bioabsorbable polymer, at a scale of 100 ⁇ m.
  • FIG. 9 is an SEM of the end of a single wire of the device described in Example 1, showing the morphology of the porous coating, at a scale of 20 ⁇ m.
  • the present invention provides filamentary means for delivery of various agents into a living host, a means comprising a filament comprising a solid core and a bioabsorbable porous sheath.
  • a means comprising a filament comprising a solid core and a bioabsorbable porous sheath.
  • the solid core is made of bioabsorbable material, it is preferably material selected from the group consisting of glass, ceramic, and polymeric material.
  • the solid core is made of a biocompatable material, it is preferably material selected from the group consisting of metals or alloys containing the elements of iron, nickel, aluminum, chromium, cobalt, titanium, vanadium, molybdenum, gold, and platinum.
  • the core of the filamentary means is preferably made of bioabsorbable material when the filamentary means is to be used as or as part of an implant to be permanently implanted into the body of a living host.
  • the core of the filamentary means is preferably made of biocompatable material when the filamentary means is to be used in the transdermal delivery of an agent.
  • the bioabsorbable nature of the material of the core and sheath of the preferred permanent implant devices of the present invention enable the living host into which they are implanted to absorb the implant over time.
  • the bioabsorbable porous sheath is preferably comprised of a bioabsorbable polymer, more preferably a bioabsorbable polymer selected from the group consisting of poly(lactic acid), poly(glycolic acid), poly(trimethylene carbonate), poly(amino acid)s, tyrosine-derived poly(carbonate)s, poly(carbonate)s, poly(caprolactone), poly(para-dioxanone), poly(ester)s, poly(ester-amide)s, poly(anhydride)s, poly(ortho ester)s, collagen, gelatin, serum albumin, proteins, carbohydrates, poly(ethylene glycol)s, poly(propylene glycol)s, poly(acrylate ester)s, poly(methacrylate ester)s, poly(vinyl alcohol), and copolymers, blends and mixtures of said polymers.
  • a bioabsorbable polymer selected from the group consisting of poly(lactic acid), poly(glycolic acid),
  • a particularly preferred bioabsorbable polymer for use as a bioabsorbable porous sheath coating on the solid core is poly(lactic acid) or any of the various known copolymers of lactic and glycolic acids such as a copolymer of L-lactide with dl-lactide known as poly(L/DL-lactide).
  • Such bioabsorbable polymers have a long history of safe clinical use in the form of synthetic absorbable suture materials and have been utilized successfully in a number tissue engineering research experiments.
  • these polymers are thermoplastic and soluble in a variety of organic solvents enabling their use in coating wires by known extrusion and solution based processes.
  • An advantageous feature of the filamentary means of the present invention is the porosity of the bioabsorbable porous sheath.
  • a preferred method for creating porosity in the bioabsorbable polymer coating involves the use of “blowing agents”. These are chemical additives that decompose at known temperatures with the liberation of gases that cause foaming in the molten polymer and porosity in the resultant cooled material.
  • Blowing agents are chemical additives that decompose at known temperatures with the liberation of gases that cause foaming in the molten polymer and porosity in the resultant cooled material.
  • a number of useful blowing agents are commercially available under the trade name of CelogenTM (Uniroyal Chemical Co.).
  • One example of a traditional blowing agent is azodicarbonamide.
  • blowing agent that may be especially useful in the present invention due to its compatibility with bioabsorbable polymers is urea dicarboxylic acid anhydride, described in U.S. Pat. No. 4,104,195, the teachings of which are incorporated herein.
  • blowing agents can produce both open cell and closed cell foams. In the present invention open cells are desired and closed cells are to be avoided. Thus the conditions used in the manufacture of the porous coating are preferably optimized to achieve an open cell structure known as “reticulated” foam.
  • the filamentary means of the present invention can be designed to deliver a variety of different agents, depending upon the porosity and composition of the porous sheath.
  • the agent delivered with the filamentary means of the present invention is preferably selected from the group consisting of: cells, growth factors, drugs, recombinant molecules, cell recognition factors, cell binding site molecules, cell attachment molecules, cell adhesion molecules, proteins, glycoproteins, carbohydrates, naturally occurring polymers, synthetic polymers, semi-synthetic polymers, and recombinant polymers.
  • the porous sheath of the filamentary means is designed to deliver the agent into a living host when the agent is coated on the outer surface of the sheath, or mixed, dissolved, or imbedded within the porous sheath.
  • the porous sheath preferably defines pores which are substantially interconnected and large enough to admit the agent.
  • the pores of the porous sheath are preferably open pores produced using blowing agents, as described below.
  • the pores are preferably large enough to admit molecules ranging in molecular weight from about 100 to about 3,000,000 Daltons, more preferably ranging from about 500 to about 100,000 Daltons.
  • the porous sheath preferably defines pores which range in size from about 0.1 micrometers to about 500 micrometers, more preferably which range in size from about 10 to 200 micrometers.
  • the extent to which the porous sheath coats the core of the filamentary means varies according to the application in which the filamentary means is to be used. For example, when only one end of a filament is to be combined with an agent before being used to implant the agent into a living host by puncture the skin of the host, only that end of the filament need include the porous sheath. In contrast, when an entire filament is to be used to deliver an agent to a host, such as happens when the entire filament is implanted into the host, the entire length of the core of the filament is preferably coated with the porous sheath.
  • Tissue engineering is generally defined as the technology of restoring defective or missing tissues or organs by the implantation of living cells that have been cultured and multiplied outside the body.
  • a more detailed description of the philosophy and techniques of tissue engineering has been published by C. W. Patrick Jr., A. G. Mikos and L V. McIntire, eds., Frontiers in Tissue Engineering, Elsevier Science, Inc., New York, 1998, the teachings of which are incorporated herein.
  • cells harvested from a few hair follicles are multiplied in vitro by tissue culture techniques and re-implanted into bald skin, thereby generating hundreds of hairs from each hair that is harvested to seed the tissue cultures.
  • a remarkable feature of the present invention is the means by which the appropriate cells are introduced into the skin and the unique ability of the implants to facilitate regeneration of the cellular architecture of normal hair follicles.
  • the hair follicle cell implant device of the present invention is comprised of three preferred parts: (1) a fine stainless steel or other suitably biocompatible wire or stiff fiber that is capable of easily penetrating the skin; (2) a porous coating on said wire comprised of a bioabsorbable polymer that is suitable as a support for cell attachment and growth; and (3) a means for the semi-rigid backing of multiple coated wires in an array to facilitate the implantation of said multitude of wires into the skin and their subsequent removal at an appropriate time post-implantation.
  • the stainless steel wire is the core, and the porous coating the porous sheath of this particular embodiment of a filament of the present invention.
  • the wire and filament produced therefrom have a first end and a second end.
  • the porous bioabsorbable coating on the wire can be selected from a variety of known polymers and the process of applying the coating and forming the porous structure can be selected from a variety of known processes.
  • the degree of porosity, the thickness of the coating, and the diameter of the wire can be varied as desired to obtain the optimum performance of the implant and the most efficient neogenesis of hair follicles.
  • the wire diameter will be similar to the diameter of the hair that is to be regenerated for each individual patient.
  • the thickness of the coating will be equivalent to the sum of the various cellular layers comprising the hair follicle that surround a normal hair shaft.
  • the preferred coating will not cover the entire length of the wire. Instead, the coating will begin at a position distal to the first end of the wire, depending on the desired depth at which the cells are to be delivered from that end of the wire.
  • the first end of the filament is preferably sharp to facilitate entry into the skin of the living host.
  • the sharp shape of the first end can be produced by cutting the first end of the wire off at an angle after the wire is coated with the porous bioabsorbable polymer. However, it is more preferably produced by cutting the first end of the wire at an angle prior to coating the first end with the porous bioabsorbable polymer.
  • the coating preferably does not cover the most distal end of the first end of the wire, in order to allow first end of the wire to enter the skin of a living host using the lowest possible injection force.
  • a preferred wire for use as the core of the filamentary means of hair follicle cell implant device of the present invention is 316 L stainless steel. This particular metal alloy has been widely used clinically in the form of surgical skin staples.
  • a typical diameter of wire for use in this invention that is similar to the diameter of human hair is about 3 to 5 thousandths of an inch. Although such a fine wire might seem too flexible for use in penetration of the skin, the depth of penetration needed is shallow enough to permit the implant to have a relatively low aspect ratio (length divided by diameter) such that bending of the wire is unlikely to occur.
  • penetration of the skin by such a fine wire sharpened by cutting the end off at an angle will be relatively atraumatic.
  • the skin can first be anesthetized and softened by the application of an analgesic lotion and covered with an occlusive dressing for about an hour prior to implantation of the wires.
  • a novel method of creating the porous sheath on the wire core to create the filaments used to make the device of the present invention is to select a wire core that can be heated electrically, such as nickel-chromium alloy wire.
  • the wire core is then coated with a mixture of polymer and blowing agent below the decomposition temperature of the blowing agent.
  • the porous coating is then formed by connecting the wire to an electrical current to obtain the precise rate of heating, duration of heating time, and ultimate temperature to produce the desired effect. Conducting this operation under the flow of an inert atmosphere of nitrogen or argon, or submerged in oil, is beneficial in protecting the polymer from oxidation and providing rapid cooling and solidification of the highly porous structure created at the instant of blowing agent decomposition.
  • the fibers are imbedded in a semi-rigid backing as follows.
  • the first end of each fiber is placed in a mold.
  • the mold is comprised of a block of any suitable material, such as TeflonTM, with defining holes in a surface of the block that are just sufficiently large in diameter to accommodate the coated wires, and of a depth that corresponds to at least the desired depth that the first end of each fiber is to penetrate the skin when the hair follicle implant device is used to implant hair follicle cells into the skin of a living host.
  • the spacing between the holes preferably corresponds to the spacing between hair follicles in the normal scalp.
  • each fiber When the first end of each fiber is placed in the mold, the second end of each fiber protrudes from the surface of the mold.
  • a layer of silicone resin or other suitable liquid pre-polymer is then coated over the protruding second end of each filament and cured.
  • the resulting implant device is preferably removed from the mold by placing a layer of adhesive tape with a backing that is puncture resistant over the cured resin, and then removing the tape therefrom. Removal of the tape pulls out the wires from the mold to yield the finished implant device (see FIG. 2 ).
  • the implant device is preferably packaged in an appropriate container for protection of the delicate wires until use, and sterilized by ethylene oxide or other suitable means prior to use.
  • a suspension of follicle progenitor cells is obtained. These cells can be harvested from some of the patient's normal follicles. Alternatively, progenitor cells can be obtained from the follicles of living donors or recently deceased organ donors. The finding that follicle progenitor cells were not rejected by an unrelated human recipient has been published by A. J. Reynolds, C. Lawrence, P. R. Caerhalmi-Friedman, A. M. Christiano, and C. A. B. Jahoda, Nature 402: 33-34, Nov. 4, 1999, the teachings of which are incorporated herein.
  • Cells multiplied in a growth medium are loaded into the array of coated wires by seeding the porous sheath of the first end of each filament with the cells, preferably by wicking the growth medium containing the cells into the porous coatings.
  • the cells optionally can be further multiplied by continuing the tissue culture process after seeding the porous sheath of each filament with the cells, to ensure that cell attachment and spreading within the porous matrix has occurred.
  • the first end of each filament is then implanted into the dermis by pressing the seeded implantation device onto the skin, preferably after softening and anesthetizing the skin with the use of an analgesic lotion under an occlusive dressing such as TegadermTM (3M Company).
  • the bioabsorbable coating separates from the wire.
  • the wires and semi-rigid backing can then be removed by pulling off the tape to which they are attached, thereby leaving the porous bioabsorbable matrix and attached follicle cells in the dermis.
  • New hair follicles are generated in the implant sites as the transplanted cells multiply and sort themselves into the appropriate functional layers under the influence of the follicular stem cells carried through from the original donor follicles. Each new hair follicle will then grow a hair shaft in the space that was formerly occupied by the wire.
  • the hair will have the same color and consistency as the donor hair that was used to create the cell culture.
  • the hair follicle cell donor is preferably the living host, and the hair regenerated thereby has the same color and consistency as that of the host.
  • the cells that are obtained from hair follicles of a living host can be genetically modified to express gene products that benefit the living host when implanted therein.
  • the genetically modified cells implanted as described above will serve as a permanent and continuous source of needed substances.
  • An example of such a substance is factor IX which would provide a cure for hemophilia B.
  • new hair growth may not be needed on the scalp and instead could be established on other parts of the body such as on the back or the legs.
  • the follicles harvested to produce the genetically engineered cultured cells can be taken from the same skin in which the new hair will be created. Thus the cosmetic effect of the presence of this superfluous new hair growth will be insignificant.
  • cells that do not produce hair such as dermal fibroblasts can be similarly implanted in the skin. These cells would be suitable for achieving a temporary therapeutic effect.
  • bed sores also known as decubitus ulcers
  • Another major medical problem is non-healing skin ulcers primarily found on the lower extremities of patients with poor circulation due to disease such as diabetes.
  • growth factors such as platelet derived growth factors are capable of facilitating rapid wound healing but cannot heretofore be conveniently administered to ulcers that are exuding fluid.
  • fibroblasts or other suitable cells are genetically modified to express the desired growth factors and are implanted into the ulcer, thereby stimulating tissue regeneration and healing the ulcers.
  • lamellar ichthyosis a disfiguring skin disease characterized by abnormal epidermal differentiation and defective cutaneous barrier function.
  • This skin disorder is caused by the deficiency of an enzyme known as keratinocyte transglutaminasel (Tgasel), the replacement of which is a potential future approach to therapeutic gene delivery in human skin.
  • Tgasel keratinocyte transglutaminasel
  • dermal keratinocytes can be genetically engineered to express the needed enzyme and implanted into the skin by the methods of the present invention.
  • cells that have a very slow rate of division but provide an essential function can be transplanted from one part of the body of a donor into the skin of a living host. Once transplanted, the cells will benefit from the high vascularity of the surrounding tissue.
  • An important example is the transplantation of pancreatic islet cells as a treatment for diabetes.
  • the cells When the donor and host are not the same individual, as is the case when pancreatic islet cells are transplanted into a living host suffering from diabetes, the cells must typically be immunoprotected by encapsulation prior to transplantation. Encapsulation prevents the patient's antibodies from destroying the foreign cells, while allowing lower molecular weight substances including insulin and glucose to diffuse in and out of the capsules containing the donor cells.
  • a serious deficiency of methods of the prior art of introducing such encapsulated cells into the patient is the difficulty of both delivering a large number of cells and providing a high surface area implant to ensure good exchange with the blood supply.
  • encapsulated cells of the prior art have been implanted in a manner that resulted in an inadequate survival rate and an insufficient output of insulin to cure diabetes.
  • the present invention solves these problems by providing a more effective means for the delivery of encapsulated cells.
  • a multitude of small implants each comprising only a few layers of encapsulated cells delivered by the methods of the present invention ensures that the donor cells receive optimal nutrition from the vasculature of the dermis and provide an efficacious, glucose responsive release of insulin into the blood stream.
  • fibers of the present invention are fused together in a three dimensional structure which provides a highly porous matrix for bone regeneration (see FIG. 6 ).
  • the high surface area of the porous coating on the fibers facilitates osteoblast attachment. This allows the option of seeding the material with osteoblasts to provide a tissue engineered implant.
  • the porous coating is preferably selected from polycarbonates such as poly(trimethylene carbonate) and tyrosine-desaminotyrosine derived polycarbonates due to their excellent compatibility with new bone and the absence of acidic degradation products that may contribute to bone resorption or inflammation late in the bioabsorption process.
  • the core fiber is preferably a biocompatible, osteoconductive ceramic or glass such as those known as “bioglass”.
  • the fiber may also be selected from a number of slowly dissolvable or bioabsorbable glasses such as calcium metaphosphate glasses.
  • the process for making the bone regeneration matrix involves providing an osteoconductive ceramic or glass fiber and coating said fiber with a mixture of polymer and blowing agent.
  • the coated fibers are then cut into short lengths and formed into a nonwoven web by any of several known methods.
  • the web is then formed into the desired shape and heated at a temperature that both melts and fuses the coating on the fibers and decomposes the blowing agent to yield a reticulated foam structure.
  • the solid inorganic fibers are unaffected by this process other than becoming glued together to form a rigid structure.
  • the device can then be sterilized, seeded with cells, and stored in a frozen state until needed for implantation to regenerate bone. The surgeon can then sculpt the material just prior to implantation so that it fits into the bone defect. If the material is to be used to regenerate bone within a spinal fusion device, such as an interbody fusion “cage”, the matrix can be pre-formed to fit exactly the dimensions of the cage.
  • Another embodiment of the present invention is a trans-dermal drug delivery device, and a method of using the device. Many drugs could benefit from trans-dermal delivery but lack the properties that are required for penetration of the skin.
  • the present invention overcomes this problem by providing a physical path through the stratum corneum and into the dermis.
  • the trans-dermal drug delivery device of the present invention comprises a semi-solid backing with a plurality of filaments fixed therein, wherein each filament comprises a wire core coated by a porous polymer sheath in which the drug is soluble and permeable.
  • Each filament has a first end and a second end. The second end of each filament is fixed in the semi-solid backing, such that the first end of each filament protrudes from one surface of the semi-solid backing.
  • the semi-solid backing further comprises a drug reservoir which is in contact with the second end of each filament.
  • the trans-dermal drug delivery device of the present invention When the trans-dermal drug delivery device of the present invention is applied to the skin of a living host, the first end of each filament penetrates the outermost barrier layer of the skin and allow the drug to diffuse slowly through the porous sheath of each filament into the blood stream of the living host.
  • the trans-dermal drug delivery device of the present invention is preferably made according to a method similar to the method described above for producing the hair follicle cell implantation device of the present invention, disclosed above.
  • the second ends of each of the plurality of filaments are set in holes in a release liner film corresponding to mold cavity holes that are not as deep as those used to make the hair follicle cell implantation device.
  • the polymer resin that is used to cover the protruding wire ends is a pressure sensitive adhesive with drug blended in, and the puncture resistant backing has adequate moisture vapor transmission for long term coverage of the skin.
  • the device is then sterilized and packaged. To use the device the patient simply separates the protective release liner from the backing, thereby exposing the coated wires and drug/adhesive surface, and applies this to the skin in the same manner as with other trans-dermal drug delivery patches.
  • the drug to be delivered with the trans-dermal drug delivery device of the present invention has a very low solubility in the polymer used to make the porous sheath of the filaments
  • the drug can be mixed with the coating polymer as a suspension prior to formation of the porous sheath.
  • a slow release of the drug is provided directly to the dermis from the drug loaded coating and from there into the blood stream.
  • Suitable coating polymers for use in the drug delivery application include bioabsorbable hydrogels that have porosity on a molecular scale.
  • a mixture of poly(dl-lactide-co-50%-glycolide) (ResomerTM RG504, Boehringer Ingelheim, D-55216 Ingelheim am Rhein, Germany) and 5% by weight of azodicarbonamide (Aldrich Chemical Co., Milwaukee, Wis. 53201) was melt blended by stirring in a test tube immersed in an oil bath maintained at a temperature of 180° C. A small amount of this mixture was placed in the bottom of a 50 ml beaker and re-heated to give a viscous liquid. The above epoxy resin plug was inverted and the wires dipped into the molten polymer mixture to a depth of about 0.3 mm and quickly removed. This produced a thin coating of polymer mixture on the tips of the wires and fine filaments pulled away from the melt and attached to the tips.
  • Crystals of sodium chloride (Morton Popcom Salt) were placed in an electric coffee bean grinder and milled into a fine powder.
  • a 1 ⁇ 2 inch diameter hex bolt was placed on end and a nut threaded onto the bolt just far enough to engage the threads.
  • the cavity formed by the nut and bolt was filled with powdered salt.
  • a thermometer was lowered into the salt and clamped in a vertical position with clamps on a ring stand.
  • the surface of the salt was smoothed out with a spatula.
  • the bolt was heated with a propane torch until the temperature of the salt reached 240° C.
  • the polymer-coated wires were then dipped into the hot salt, pushed about half way in and then quickly pulled out.
  • the adherent salt was removed by dipping the wires in water until the salt dissolved.
  • the water was removed from the device by gently blotting with tissue paper.
  • the device was placed back in a tuberculin syringe barrel for protection and stored in a desiccator. Scanning electron micrographs of device are shown in FIGS. 7-9 .
  • Example 1 The device of Example 1 is soaked in ethanol for 5 minutes and then rinsed with sterile water. The excess water is removed from the porous structure by blotting with a sterile, lint-fee surgical sponge. This process serves both to sterilize the polymer and to improve the ability of cells to be wicked rapidly and completely into the porous polymer.
  • Human dermal papilla cells that have been multiplied in culture are collected and resuspended in an isotonic buffer solution at approximately ten million cells per cubic centimeter.
  • the pre-wet implant is then dipped into the suspension of cells and immediately injected into human skin where the growth of hair is desired.
  • the skin Prior to implantation, the skin is wiped with gauze soaked in 70% isopropanol and then wiped with gauze soaked in BetadineTM. Lidocaine cream is then applied to the skin and covered with a TegadermTM dressing for a minimum of one hour. This pre-implantation procedure serves to kill bacteria and to soften and anesthetize the skin. After implanting the device, the exposed epoxy resin plug is covered with a dressing to prevent it from being disturbed or dislodged.
  • the dressing is removed.
  • the wires are then removed from the skin by pulling on the epoxy resin plug.
  • the cell-laden porous bioabsorbable polymer tips remain under the skin, having separated from the wires as a result of tissue attachment to the porous polymer and moisture induced loosening of the polymer attachment to the metal.
  • the implanted cells multiply and organize into a new hair follicle as the bioabsorbable polymer degrades and is bioabsorbed.
  • the growth of new hair indicates that the restoration process is complete.
  • Poly(70%-L-lactide-co-30%-d,l-lactide) obtained from Purac Biochem, b.v. (Gorinchem, Holland) is melt blended at about 170° C. with 5% by weight azodicarbonamide (Aldrich Chemical Co.) and pelletized.
  • a proprietary bioabsorbable glass fiber produced by MO-SCI Corp. (Twitty Industrial Park, Rolla, Mo. 65401) is obtained as a monofilament single strand that is 100 microns in diameter.
  • a cladding extrusion die is made such that the 100 micron diameter fiber can pass through the die while polymer is extruded to cover and clad the moving fiber.
  • the polymer/azodicarbonamide blend is extruded as a cladding on the glass to give a cross-sectional area ratio of 2:1 core to sheath.
  • the fiber is cut into 3 to 5 millimeter lengths and added to a beaker of water with stirring.
  • the resultant slurry is then poured onto a Büchner funnel equipped with a coarse glass frit and the water allowed to drain.
  • the web is dried under vacuum and carefully transferred into a wire basket.
  • the basket is lowered into a beaker of peanut oil heated to 240° C. for about one second and then immersed in a beaker of hexane.
  • the hot oil causes the polymer to melt and the azodicarbonamide to decompose into gas, thereby converting the polymer into an open-cell foam.
  • the cool hexane causes the polymer to solidify, thereby preserving the porous structure and adhering the glass fibers together at every point that they touch.
  • the hexane also dissolves and removes the oil from the structure without affecting the polymer.
  • Chondrocytes are seeded onto the structure from an aqueous suspension causing the cells to wick into the porous polymer coating on the glass fibers.
  • the structure can then be implanted in a bone defect immediately or allowed to mature in culture prior to implantation. In either case the cells will be retained in the microporous structure of the coating while the macroporous structure of the adhered fibers will allow ample room for Lissue ingrowth and osteoinduction of new bone due to the seeded cells.

Abstract

The present invention provides a filamentary structure for the introduction of agents into a living host, comprising a filament comprising a solid core and a porous sheath which coats at least a portion of the solid core. When the filamentary structure is to be permanently implanted into a living host, both the solid core and the porous sheath are bioabsorbable. When the filamentary structure is to be temporarily implanted into the skin of a living host to deliver agents, such as cells, therein, the porous sheath is preferably bioabsorbable but the core need only be biocompatable, not bioabsorabable. The devices and methods of the present invention enable one to regenerate hair follicles, to introduce genetically altered cells or encapsulated cells to a living host transdermally, to regenerate bones, and to deliver drugs transdermally.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application claims the benefit of U.S. Provisional Application No. 60/119,082, filed Feb. 8, 1999.
  • STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH OR DEVELOPMENT
  • Not Applicable.
  • BACKGROUND OF THE INVENTION
  • This invention relates to means for the delivery of agents into a living body. More specifically it relates to filaments comprising porous bioabsorbable polymers, which facilitate the implantation of living cells and other agents, such as drugs, into specific tissues, including skin and bone, for the purposes of site-specific drug or cell release, gene therapy, and the facilitation of the regeneration of tissue, including the regeneration of bone and hair tissue.
  • Current means for the delivery of agents such as drugs, growth factors, genetically modified cells, and the like into a living body include various pharmaceutical dosage forms, such as ingestable tablets, patches designed to deliver agents transdermally, and surgically implantable devices designed to deliver agents to an implant site. Early implantable devices were not bioabsorbable, and had to be surgically removed after they had been used for their intended purpose. More recently, implants of bioabsorbable polymers have been developed. Such implants are absorbed by the host in which they are implanted after, or in the course of serving their intended purpose. One such device, disclosed by Dunn et al. in U.S. Pat. No. 5,599,552 (“Dunn et al. '552”), is an implant of a porous core of a bioabsorbable polymer, surrounded by a non-porous surface skin of the bioabsorbable polymer. That particular device is designed for use in delivering a biologically active agent to a living host when implanted therein. The device disclosed by Dunn et al. '552 is also designed so that it can act as a matrix to promote tissue regeneration at an implant site. (Id.)
  • Two other types of implantable devices of bioabsorbable polymers are disclosed in U.S. Pat. No. 5,847,012 (“Shalaby et al. '012”). One such device consists of a bioabsorbable microporous polymeric foam with open-cell pores. The other such device consist of an implant with a modified surface, consisting of a surface layer of bioabsorbable microporous polymeric foam with open-cell pores. (Id.) The implants of Shalaby et al. '012 are designed to accept the agent to be delivered, such as a medicament or growth factor, and to deliver the agent to a living patient after implantation therein.
  • Textile technologies have also been adapted for use in making biodegradable woven fabrics as tissue engineering scaffolds. See Introduction of Peter X. Ma and Ruiyun Zhang in J. Bionied. Materials Res. 46(1):60-72 (July 1999). The diameter of the biodegradable fibers used to produce such woven scaffolds is about 15 μm. Ma and Zhang demonstrated that fibers with a considerably smaller diameter, ranging from 50 to 500 nm could be created from biodegradable aliphatic polyesters. The woven scaffolds of Ma and Zhang, and those described therein were designed for use as scaffolds, and not as means for delivery of agents to tissue.
  • The advantage of all the bioabsorbable devices described above was that they could be implanted into a living host and left in place to do what they were designed to do, without the necessity of removal therefrom. The devices would be absorbed by the host over time. Of the bioabsorbable devices disclosed in the references described above, only the device of Dunn et al. '552 is designed to act as both scaffolding and delivery agent. That device has limited flexibility, because of the way it is designed. What is needed is a bioabsorbable fiber or composite thereof, which is capable of being processed into a scaffolding for tissue formation, and which is capable of delivering agents to a living host when implanted therein. The present invention meets that need.
  • The present invention also meets a need for an inexpensive and relatively painless means for regenerating hair. Plastic surgery is one of the few means available to correct male pattern baldness, today. In that particular surgical procedure, the amount of permanently hair-bearing donor tissue available can significantly affect the feasibility and outcome of the procedure. In vitro growth techniques have been developed to increase the amount of hair follicle cells available for use in such procedures. See, e.g., Seigi Arase, et al. Tokushima J. exp. Med 36: 87-95 (1989); and Edoardo Raposio, et al. Plastic and Reconstructive Surgery pp. 221-226 (July 1998). What is needed is a relatively painless and inexpensive means for the regeneration of hair, one which does not involve plastic surgery or other painful and expensive implantation techniques, preferably, a technique which produces hair which looks realistic and similar to other hair on the same host. The present invention utilizes a modified form of the bioabsorbable polymeric means developed for use in implantable devices, as described above, to deliver hair follicle cells transdermally and to promote the regeneration of hair therein.
  • As is shown in the next section, below, the present invention provides a new means for the introduction of agents into a living host, a means which offers several advantages over known means in use today, such as those described briefly above.
  • BRIEF SUMMARY OF THE INVENTION
  • The present invention provides a filamentary means for the introduction of agents into a living host, comprising a filament comprising a solid core and a porous sheath which coats at least a portion of the solid core. When the filamentary means is to be permanently implanted into a living host, both the solid core and the porous sheath are bioabsorbable. When the filamentary means is to be temporarily implanted into the skin of a living host to deliver agents, such as cells, therein, the porous sheath is preferably bioabsorbable but the core need only be biocompatable, not bioabsorabable.
  • The solid core is preferably wire when the filamentary means is designed to be used to deliver an agent, such as hair follicle cells, into the skin of a living host. The solid core is preferably glass or ceramic when the filamentary means is to be used to deliver an agent, such as cells or pharmaceutical agents, into bone through implantation of the filamentary means into the body of the host.
  • The porous sheath is preferably in the form of reticulated foam that is well adhered to the core but is capable of separating from the core after a period of several days in vivo. When the agent to be delivered with the filamentary means is a drug, the porous sheath is preferably in the form of a hydrogel and the porosity is on a molecular size scale.
  • The filamentary means of the present invention provides means for delivery of cells or other agents from outside the body of a living host into the skin of the host, such as a mammal, with minimal trauma to the host. When the filamentary means is comprised of a bioabsorbable core with a bioabsorbable porous sheath which coats at least a portion of the core, the filamentary means can be implanted into specific tissue within a living host and used to deliver agents to the specific tissue when implanted therein. The implantable embodiment of the filamentary means can serve as a surface for osteoblast attachment and as a scaffold for bone regeneration upon implantation into the bone tissue of a living host. The above-cited features of the filamentary means of the present invention enable it to be used for a variety of purposes including, but not limited to, hair follicle regeneration, gene therapy and encapsulated cell delivery, bone regeneration, and trans-dermal drug delivery.
  • Another embodiment of the present invention is a method of making a filamentary means for introducing an agent into a living host, comprising providing a solid filament, a bioabsorbable polymer, and a pore-forming agent, mixing the bioabsorbable polymer with the pore-forming agent, coating the resulting mixture onto at least a portion of the filament, and substantially removing or decomposing the pore-forming agent.
  • Other embodiments of the present invention include devices designed to enable one to use the filamentary means of the invention to deliver various agents into a living host, methods for making such devices, and methods for using the devices of the present invention to deliver agents into a living host. The devices and methods of the present invention enable one to regenerate hair follicles, to introduce genetically altered cells or encapsulated cells to a living host transdermally, to regenerate bones, and to deliver drugs transdermally. The devices and methods of the present invention are described briefly below.
  • One embodiment of the present invention is a hair follicle cell implant device designed to implant hair follicle cells into the skin of a living host. Another embodiment of the hair follicle cell implant device of the present invention is a method of making the implant device. Yet another embodiment is a method of using the implant device to deliver hair follicle cells to implant such cells into the skin of a living host, preferably into the scalp of a human being suffering from male pattern baldness. The hair follicle cell implant device of the present invention comprises a plurality of filaments, each of which has a first end and a second end and comprises a solid core and a bioabsorbable porous sheath which coats the solid core, and a semi-rigid backing with the second end of each filament embedded therein such that the first end of each filament protrudes therefrom. The first end of each filament protrudes from the semi-rigid backing a sufficient length to penetrate the skin of a living host when the device is in contact therewith. The filaments are preferably spaced the same distance apart as hairs on the normal surface of skin of the living host.
  • The hair follicle cell implant device of the present invention is preferably made by the steps comprising: providing a plurality of filaments, each of which has a first end and a second end and comprises a solid core and a bioabsorbable porous sheath which coats the solid core; and fixing the second end of each of the plurality of filaments in a semi-rigid backing such that the filaments are spaced the same distance apart as hairs on the skin of a normal living host, and such that the second end of each of the plurality of filaments protrudes from the semi-rigid backing at a depth sufficient to penetrate the skin of the living host when placed into contact therewith.
  • The hair follicle cell implant device is used to stimulate hair growth according to a method comprising: seeding the boabsorbable porous sheath at the first end of each filament with hair follicle cells, introducing the cells into the skin of a living host by puncturing the skin with the first end of each filament, and removing the device from the skin after sufficient time has passed to allow the porous coating within the skin to separate from the solid core of each filament, leaving the porous coating and hair follicle cells in the skin.
  • One advantage of the hair follicle cell implant device and methods of making and using the same is that they provide means for delivering cultured cells harvested from hair follicles into the skin of a host, such as the bald scalp of a human male, such that said cells are able to generate new hair follicles. The new hair follicles, once generated, will continue to grow and be maintained in the dermis of the host. Another advantage of these embodiments of the present invention is that they provide a means for the simultaneous implantation of hair follicle cells into multiple sites in the skin such that the spacing between each individual implant is approximately the same as the spacing between the hair follicles in the normal scalp. Regenerated hair grown from follicle cells implanted in such a pattern have a natural, cosmetically appealing look. Thus, the present invention provides an efficient device and method of restoring a normal density of normally functioning hair follicles in the hairless scalp as an effective, natural, and permanent remedy for baldness.
  • In another aspect, the present invention is a method of using the filamentary means of the present invention to deliver genetically modified cells into normal healthy skin, such that the cells deliver a therapeutically efficacious systemic level of the desired gene product. In this embodiment, a filamentary means comprising a filament comprising a solid core having a first end and a second end and a porous sheath which coats at least the first end of the solid core, wherein the porous sheath is bioabsorbable, is used to deliver genetically modified cells into the skin of a living host, according to the steps comprising: providing the filament, seeding the porous sheath at the first end of the filament with the genetically transformed cells, introducing the cells into the skin of the living host by puncturing the skin with the first end of the filament, and removing the filament from the skin after sufficient time has passed to allow the porous coating to separate from the filament at the first end of the solid core of the filament, leaving the porous coating and genetically transformed cells in the skin.
  • An advantage of this embodiment of the present invention is that it provides a means for the delivery of encapsulated or otherwise immunoprotected cells into normal healthy skin such that the cells delivered therewith take over the function of cells in other organs that have lost their required function due to disease such as diabetes. Another advantage of this embodiment of the invention is that it also provides a means for the delivery of genetically modified cells into diseased or ulcerated skin to treat the disease or provide growth factors to heal the ulcers.
  • An advantage of another embodiment of the present invention is that it provides that a rigid scaffold with a highly porous surface, which can be implanted into a living host, and maintained for a long enough period of time to facilitate new bone formation. The porous surface enables this embodiment of the invention to be used as a means for the delivery of osteoblasts and/or other osteoinductive substances into bone defects, gaps, or fusion devices.
  • Another embodiment of the present invention is a device for delivery of a drug through the skin, comprising: a plurality of filaments each of which has a fist end and a second end and comprises a solid core and a bioabsorbable polymer sheath in which the drug is soluble and permeable; a semi-rigid backing having a first side and a second side, wherein the second side of the semi-rigid backing defines a reservoir, wherein each of the plurality of filaments is fixed in the semi-rigid backing such that the first end of each filament protrudes from the first side of the semi-rigid backing and the second end of each filament extends to the second side of the semi-rigid backing such that it is in contact with the reservoir. An advantage to the device of delivery of a drug through the skin of the present invention is that it provides a means for the continuous delivery of drugs through the skin that normally do not penetrate skin from a reservoir placed on the surface of the skin.
  • Other advantages of the filamentary means for the delivery of agents into a living body of the present invention will become apparent upon disclosure of the invention as described below.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 a is a schematic view of the filament in longitudinal section, showing the solid core (1) and the porous sheath (2), without details of the porous structure.
  • FIG. 1 b is a schematic view of the filament in transverse section, showing the solid core (1) and porous sheath (2).
  • FIG. 2 is a schematic sectional view of a hair implant device with an array of the core-sheath filaments (3) shown imbedded in a semi-rigid backing (4) which maintains the filaments in a stable, rigid parallel configuration.
  • FIG. 3 is a schematic sectional view of the hair implant device with the array of filaments (3) imbedded in the semi-rigid backing (4), immersed in a vessel (5) containing a tissue culture broth of free floating cells (6) derived from the hair follicles of a living host.
  • FIG. 4 a depicts a sectional view of a single filament with cultured cells (6) contained within the porous sheath (2) surrounding the solid core (1) of a filament, which has been implanted in the skin through the full thickness of the dermis (7). The filament has been present in the skin for several days during which time the epidermis (8) has begun to grow down the outside of the filament.
  • FIG. 4 b depicts a sectional view of the implant site after the filament core (1) has been removed by pulling out the semi-rigid backing (4) to which it is attached out of the dermis (7) and epidermis (8). Note the resulting separation of the porous, cultured cell laden sheath (2) from the core. As shown in this figure, the implanted sheath has been present for a long enough time that new matrix cells (9) are beginning to elongate a new hair shaft (10).
  • FIG. 5 a depicts a sectional view of a single filament with cultured cells (6) contained within the porous sheath (2) surrounding the solid core (1) of the filament, which has been implanted in the skin through the full thickness of the dermis (7). In this case the filament is shown in the state in which it would be if it had been present in the skin only long enough for the porous coating to soften and detach from the solid core, but not long enough for the epidermis (8) to grown down the outside of the filament.
  • FIG. 5 b depicts the implant site after the filament core has been removed by pulling out the semi-rigid backing to which it was attached as shown in FIG. 5 a. In this case, pulling out the semi-rigid backing and core has resulted in separation of the cell laden porous sheath (2) from the solid core. Sufficient time has elapsed that the epidermis (8) has grown over the implant site, the porous bioabsorbable coating has resorbed, and the implanted cultured cells (6) have survived and are functioning properly.
  • FIG. 6 is a schematic representation of filaments comprised of a solid core (1) and a porous coating (2) that are bonded together. The process that is utilized to create the bonds between the filaments, for example by heating and cooling, preferably is the same process that is used to create porosity in the coating
  • FIG. 7 is a scanning electron micrograph (SEM) of the device described in Example 1, at a scale of 1 mm.
  • FIG. 8 is an SEM of the device described in Example 1, viewing the wires on end showing the exposed tips of the wires and the surrounding coatings of porous, bioabsorbable polymer, at a scale of 100 μm.
  • FIG. 9 is an SEM of the end of a single wire of the device described in Example 1, showing the morphology of the porous coating, at a scale of 20 μm.
  • DETAILED DESCRIPTION OF THE INVENTION
  • The present invention provides filamentary means for delivery of various agents into a living host, a means comprising a filament comprising a solid core and a bioabsorbable porous sheath. When the solid core is made of bioabsorbable material, it is preferably material selected from the group consisting of glass, ceramic, and polymeric material. When the solid core is made of a biocompatable material, it is preferably material selected from the group consisting of metals or alloys containing the elements of iron, nickel, aluminum, chromium, cobalt, titanium, vanadium, molybdenum, gold, and platinum. The core of the filamentary means is preferably made of bioabsorbable material when the filamentary means is to be used as or as part of an implant to be permanently implanted into the body of a living host. The core of the filamentary means is preferably made of biocompatable material when the filamentary means is to be used in the transdermal delivery of an agent. The bioabsorbable nature of the material of the core and sheath of the preferred permanent implant devices of the present invention enable the living host into which they are implanted to absorb the implant over time.
  • The bioabsorbable porous sheath is preferably comprised of a bioabsorbable polymer, more preferably a bioabsorbable polymer selected from the group consisting of poly(lactic acid), poly(glycolic acid), poly(trimethylene carbonate), poly(amino acid)s, tyrosine-derived poly(carbonate)s, poly(carbonate)s, poly(caprolactone), poly(para-dioxanone), poly(ester)s, poly(ester-amide)s, poly(anhydride)s, poly(ortho ester)s, collagen, gelatin, serum albumin, proteins, carbohydrates, poly(ethylene glycol)s, poly(propylene glycol)s, poly(acrylate ester)s, poly(methacrylate ester)s, poly(vinyl alcohol), and copolymers, blends and mixtures of said polymers.
  • A particularly preferred bioabsorbable polymer for use as a bioabsorbable porous sheath coating on the solid core is poly(lactic acid) or any of the various known copolymers of lactic and glycolic acids such as a copolymer of L-lactide with dl-lactide known as poly(L/DL-lactide). Such bioabsorbable polymers have a long history of safe clinical use in the form of synthetic absorbable suture materials and have been utilized successfully in a number tissue engineering research experiments. Moreover, these polymers are thermoplastic and soluble in a variety of organic solvents enabling their use in coating wires by known extrusion and solution based processes.
  • An advantageous feature of the filamentary means of the present invention is the porosity of the bioabsorbable porous sheath. Here again the application of proven technology can be beneficial in achieving the desired pore size and void volume of the porous sheath. A preferred method for creating porosity in the bioabsorbable polymer coating involves the use of “blowing agents”. These are chemical additives that decompose at known temperatures with the liberation of gases that cause foaming in the molten polymer and porosity in the resultant cooled material. A number of useful blowing agents are commercially available under the trade name of Celogen™ (Uniroyal Chemical Co.). One example of a traditional blowing agent is azodicarbonamide. Another blowing agent that may be especially useful in the present invention due to its compatibility with bioabsorbable polymers is urea dicarboxylic acid anhydride, described in U.S. Pat. No. 4,104,195, the teachings of which are incorporated herein. The use of blowing agents can produce both open cell and closed cell foams. In the present invention open cells are desired and closed cells are to be avoided. Thus the conditions used in the manufacture of the porous coating are preferably optimized to achieve an open cell structure known as “reticulated” foam.
  • The filamentary means of the present invention can be designed to deliver a variety of different agents, depending upon the porosity and composition of the porous sheath. The agent delivered with the filamentary means of the present invention is preferably selected from the group consisting of: cells, growth factors, drugs, recombinant molecules, cell recognition factors, cell binding site molecules, cell attachment molecules, cell adhesion molecules, proteins, glycoproteins, carbohydrates, naturally occurring polymers, synthetic polymers, semi-synthetic polymers, and recombinant polymers.
  • The porous sheath of the filamentary means is designed to deliver the agent into a living host when the agent is coated on the outer surface of the sheath, or mixed, dissolved, or imbedded within the porous sheath. The porous sheath preferably defines pores which are substantially interconnected and large enough to admit the agent. The pores of the porous sheath are preferably open pores produced using blowing agents, as described below. The pores are preferably large enough to admit molecules ranging in molecular weight from about 100 to about 3,000,000 Daltons, more preferably ranging from about 500 to about 100,000 Daltons. Alternatively, the porous sheath preferably defines pores which range in size from about 0.1 micrometers to about 500 micrometers, more preferably which range in size from about 10 to 200 micrometers.
  • The extent to which the porous sheath coats the core of the filamentary means varies according to the application in which the filamentary means is to be used. For example, when only one end of a filament is to be combined with an agent before being used to implant the agent into a living host by puncture the skin of the host, only that end of the filament need include the porous sheath. In contrast, when an entire filament is to be used to deliver an agent to a host, such as happens when the entire filament is implanted into the host, the entire length of the core of the filament is preferably coated with the porous sheath.
  • A discussion of more specific preferred features of the filamentary means of the present invention, as used in additional embodiments of the present invention follows. It is contemplated that additional advantages and features of the present invention will become evident to one of ordinary skill in the art of the present invention upon review of the present disclosure.
  • Hair Follicle Regeneration.
  • One of the embodiments of the present invention provides materials and methods for a tissue engineering approach to hair follicle regeneration. Tissue engineering is generally defined as the technology of restoring defective or missing tissues or organs by the implantation of living cells that have been cultured and multiplied outside the body. A more detailed description of the philosophy and techniques of tissue engineering has been published by C. W. Patrick Jr., A. G. Mikos and L V. McIntire, eds., Frontiers in Tissue Engineering, Elsevier Science, Inc., New York, 1998, the teachings of which are incorporated herein.
  • In a preferred embodiment of the present invention, cells harvested from a few hair follicles are multiplied in vitro by tissue culture techniques and re-implanted into bald skin, thereby generating hundreds of hairs from each hair that is harvested to seed the tissue cultures. A remarkable feature of the present invention is the means by which the appropriate cells are introduced into the skin and the unique ability of the implants to facilitate regeneration of the cellular architecture of normal hair follicles.
  • The hair follicle cell implant device of the present invention is comprised of three preferred parts: (1) a fine stainless steel or other suitably biocompatible wire or stiff fiber that is capable of easily penetrating the skin; (2) a porous coating on said wire comprised of a bioabsorbable polymer that is suitable as a support for cell attachment and growth; and (3) a means for the semi-rigid backing of multiple coated wires in an array to facilitate the implantation of said multitude of wires into the skin and their subsequent removal at an appropriate time post-implantation. The stainless steel wire is the core, and the porous coating the porous sheath of this particular embodiment of a filament of the present invention. The wire and filament produced therefrom have a first end and a second end.
  • The porous bioabsorbable coating on the wire can be selected from a variety of known polymers and the process of applying the coating and forming the porous structure can be selected from a variety of known processes. Similarly, the degree of porosity, the thickness of the coating, and the diameter of the wire can be varied as desired to obtain the optimum performance of the implant and the most efficient neogenesis of hair follicles. In general, the wire diameter will be similar to the diameter of the hair that is to be regenerated for each individual patient. The thickness of the coating will be equivalent to the sum of the various cellular layers comprising the hair follicle that surround a normal hair shaft. The preferred coating will not cover the entire length of the wire. Instead, the coating will begin at a position distal to the first end of the wire, depending on the desired depth at which the cells are to be delivered from that end of the wire.
  • The first end of the filament is preferably sharp to facilitate entry into the skin of the living host. The sharp shape of the first end can be produced by cutting the first end of the wire off at an angle after the wire is coated with the porous bioabsorbable polymer. However, it is more preferably produced by cutting the first end of the wire at an angle prior to coating the first end with the porous bioabsorbable polymer. The coating preferably does not cover the most distal end of the first end of the wire, in order to allow first end of the wire to enter the skin of a living host using the lowest possible injection force.
  • A preferred wire for use as the core of the filamentary means of hair follicle cell implant device of the present invention is 316L stainless steel. This particular metal alloy has been widely used clinically in the form of surgical skin staples. A typical diameter of wire for use in this invention that is similar to the diameter of human hair is about 3 to 5 thousandths of an inch. Although such a fine wire might seem too flexible for use in penetration of the skin, the depth of penetration needed is shallow enough to permit the implant to have a relatively low aspect ratio (length divided by diameter) such that bending of the wire is unlikely to occur. In addition, penetration of the skin by such a fine wire sharpened by cutting the end off at an angle will be relatively atraumatic. As an aid to penetration and patient comfort, the skin can first be anesthetized and softened by the application of an analgesic lotion and covered with an occlusive dressing for about an hour prior to implantation of the wires.
  • A novel method of creating the porous sheath on the wire core to create the filaments used to make the device of the present invention is to select a wire core that can be heated electrically, such as nickel-chromium alloy wire. The wire core is then coated with a mixture of polymer and blowing agent below the decomposition temperature of the blowing agent. The porous coating is then formed by connecting the wire to an electrical current to obtain the precise rate of heating, duration of heating time, and ultimate temperature to produce the desired effect. Conducting this operation under the flow of an inert atmosphere of nitrogen or argon, or submerged in oil, is beneficial in protecting the polymer from oxidation and providing rapid cooling and solidification of the highly porous structure created at the instant of blowing agent decomposition.
  • Upon obtaining a plurality of fibers, each comprising a desired wire coated with a bioabsorbable porous sheath, the fibers are imbedded in a semi-rigid backing as follows. The first end of each fiber is placed in a mold. The mold is comprised of a block of any suitable material, such as Teflon™, with defining holes in a surface of the block that are just sufficiently large in diameter to accommodate the coated wires, and of a depth that corresponds to at least the desired depth that the first end of each fiber is to penetrate the skin when the hair follicle implant device is used to implant hair follicle cells into the skin of a living host. The spacing between the holes preferably corresponds to the spacing between hair follicles in the normal scalp. When the first end of each fiber is placed in the mold, the second end of each fiber protrudes from the surface of the mold. Once the plurality of fibers has been placed into the mold, a layer of silicone resin or other suitable liquid pre-polymer is then coated over the protruding second end of each filament and cured. The resulting implant device is preferably removed from the mold by placing a layer of adhesive tape with a backing that is puncture resistant over the cured resin, and then removing the tape therefrom. Removal of the tape pulls out the wires from the mold to yield the finished implant device (see FIG. 2). The implant device is preferably packaged in an appropriate container for protection of the delicate wires until use, and sterilized by ethylene oxide or other suitable means prior to use.
  • In order to use the above hair follicle cell implant device to regenerate hair follicles, a suspension of follicle progenitor cells is obtained. These cells can be harvested from some of the patient's normal follicles. Alternatively, progenitor cells can be obtained from the follicles of living donors or recently deceased organ donors. The finding that follicle progenitor cells were not rejected by an unrelated human recipient has been published by A. J. Reynolds, C. Lawrence, P. R. Caerhalmi-Friedman, A. M. Christiano, and C. A. B. Jahoda, Nature 402: 33-34, Nov. 4, 1999, the teachings of which are incorporated herein.
  • Cells multiplied in a growth medium are loaded into the array of coated wires by seeding the porous sheath of the first end of each filament with the cells, preferably by wicking the growth medium containing the cells into the porous coatings. The cells optionally can be further multiplied by continuing the tissue culture process after seeding the porous sheath of each filament with the cells, to ensure that cell attachment and spreading within the porous matrix has occurred. The first end of each filament is then implanted into the dermis by pressing the seeded implantation device onto the skin, preferably after softening and anesthetizing the skin with the use of an analgesic lotion under an occlusive dressing such as Tegaderm™ (3M Company). After several days the bioabsorbable coating separates from the wire. The wires and semi-rigid backing can then be removed by pulling off the tape to which they are attached, thereby leaving the porous bioabsorbable matrix and attached follicle cells in the dermis. New hair follicles are generated in the implant sites as the transplanted cells multiply and sort themselves into the appropriate functional layers under the influence of the follicular stem cells carried through from the original donor follicles. Each new hair follicle will then grow a hair shaft in the space that was formerly occupied by the wire. The hair will have the same color and consistency as the donor hair that was used to create the cell culture. The hair follicle cell donor is preferably the living host, and the hair regenerated thereby has the same color and consistency as that of the host.
  • Gene Therapy and Encapsulated Cell Delivery.
  • In a related embodiment of the present invention, the cells that are obtained from hair follicles of a living host can be genetically modified to express gene products that benefit the living host when implanted therein. Because the hair follicle cells are rapidly multiplying and renewing themselves as hair grows, the genetically modified cells implanted as described above will serve as a permanent and continuous source of needed substances. An example of such a substance is factor IX which would provide a cure for hemophilia B. In this case, new hair growth may not be needed on the scalp and instead could be established on other parts of the body such as on the back or the legs. The follicles harvested to produce the genetically engineered cultured cells can be taken from the same skin in which the new hair will be created. Thus the cosmetic effect of the presence of this superfluous new hair growth will be insignificant.
  • In another embodiment, cells that do not produce hair such as dermal fibroblasts can be similarly implanted in the skin. These cells would be suitable for achieving a temporary therapeutic effect. For example, bed sores, also known as decubitus ulcers, are a significant cause of patient discomfort, infection risk, and health care cost in nursing homes. Another major medical problem is non-healing skin ulcers primarily found on the lower extremities of patients with poor circulation due to disease such as diabetes. It is well known that growth factors such as platelet derived growth factors are capable of facilitating rapid wound healing but cannot heretofore be conveniently administered to ulcers that are exuding fluid. In this embodiment of the present invention, fibroblasts or other suitable cells are genetically modified to express the desired growth factors and are implanted into the ulcer, thereby stimulating tissue regeneration and healing the ulcers.
  • Other disorders and diseases of the skin that can be treated with similar embodiments include lamellar ichthyosis, a disfiguring skin disease characterized by abnormal epidermal differentiation and defective cutaneous barrier function. This skin disorder is caused by the deficiency of an enzyme known as keratinocyte transglutaminasel (Tgasel), the replacement of which is a potential future approach to therapeutic gene delivery in human skin. Thus dermal keratinocytes can be genetically engineered to express the needed enzyme and implanted into the skin by the methods of the present invention.
  • In another embodiment, cells that have a very slow rate of division but provide an essential function can be transplanted from one part of the body of a donor into the skin of a living host. Once transplanted, the cells will benefit from the high vascularity of the surrounding tissue. An important example is the transplantation of pancreatic islet cells as a treatment for diabetes. When the donor and host are not the same individual, as is the case when pancreatic islet cells are transplanted into a living host suffering from diabetes, the cells must typically be immunoprotected by encapsulation prior to transplantation. Encapsulation prevents the patient's antibodies from destroying the foreign cells, while allowing lower molecular weight substances including insulin and glucose to diffuse in and out of the capsules containing the donor cells.
  • A serious deficiency of methods of the prior art of introducing such encapsulated cells into the patient is the difficulty of both delivering a large number of cells and providing a high surface area implant to ensure good exchange with the blood supply. Thus, encapsulated cells of the prior art have been implanted in a manner that resulted in an inadequate survival rate and an insufficient output of insulin to cure diabetes. The present invention solves these problems by providing a more effective means for the delivery of encapsulated cells. Thus a multitude of small implants each comprising only a few layers of encapsulated cells delivered by the methods of the present invention ensures that the donor cells receive optimal nutrition from the vasculature of the dermis and provide an efficacious, glucose responsive release of insulin into the blood stream.
  • Bone Regeneration.
  • In another embodiment of the present invention, fibers of the present invention are fused together in a three dimensional structure which provides a highly porous matrix for bone regeneration (see FIG. 6). In addition to the porosity created by the spaces between the fibers which is beneficial for bone ingrowth, the high surface area of the porous coating on the fibers facilitates osteoblast attachment. This allows the option of seeding the material with osteoblasts to provide a tissue engineered implant. In this case the porous coating is preferably selected from polycarbonates such as poly(trimethylene carbonate) and tyrosine-desaminotyrosine derived polycarbonates due to their excellent compatibility with new bone and the absence of acidic degradation products that may contribute to bone resorption or inflammation late in the bioabsorption process. The core fiber is preferably a biocompatible, osteoconductive ceramic or glass such as those known as “bioglass”. The fiber may also be selected from a number of slowly dissolvable or bioabsorbable glasses such as calcium metaphosphate glasses.
  • The process for making the bone regeneration matrix involves providing an osteoconductive ceramic or glass fiber and coating said fiber with a mixture of polymer and blowing agent. The coated fibers are then cut into short lengths and formed into a nonwoven web by any of several known methods. The web is then formed into the desired shape and heated at a temperature that both melts and fuses the coating on the fibers and decomposes the blowing agent to yield a reticulated foam structure. The solid inorganic fibers are unaffected by this process other than becoming glued together to form a rigid structure. The device can then be sterilized, seeded with cells, and stored in a frozen state until needed for implantation to regenerate bone. The surgeon can then sculpt the material just prior to implantation so that it fits into the bone defect. If the material is to be used to regenerate bone within a spinal fusion device, such as an interbody fusion “cage”, the matrix can be pre-formed to fit exactly the dimensions of the cage.
  • Trans-Dermal Drug Delivery.
  • Another embodiment of the present invention is a trans-dermal drug delivery device, and a method of using the device. Many drugs could benefit from trans-dermal delivery but lack the properties that are required for penetration of the skin. The present invention overcomes this problem by providing a physical path through the stratum corneum and into the dermis.
  • The trans-dermal drug delivery device of the present invention comprises a semi-solid backing with a plurality of filaments fixed therein, wherein each filament comprises a wire core coated by a porous polymer sheath in which the drug is soluble and permeable. Each filament has a first end and a second end. The second end of each filament is fixed in the semi-solid backing, such that the first end of each filament protrudes from one surface of the semi-solid backing. The semi-solid backing further comprises a drug reservoir which is in contact with the second end of each filament.
  • When the trans-dermal drug delivery device of the present invention is applied to the skin of a living host, the first end of each filament penetrates the outermost barrier layer of the skin and allow the drug to diffuse slowly through the porous sheath of each filament into the blood stream of the living host.
  • The trans-dermal drug delivery device of the present invention is preferably made according to a method similar to the method described above for producing the hair follicle cell implantation device of the present invention, disclosed above. In the present case, the second ends of each of the plurality of filaments are set in holes in a release liner film corresponding to mold cavity holes that are not as deep as those used to make the hair follicle cell implantation device. The polymer resin that is used to cover the protruding wire ends is a pressure sensitive adhesive with drug blended in, and the puncture resistant backing has adequate moisture vapor transmission for long term coverage of the skin. The device is then sterilized and packaged. To use the device the patient simply separates the protective release liner from the backing, thereby exposing the coated wires and drug/adhesive surface, and applies this to the skin in the same manner as with other trans-dermal drug delivery patches.
  • Alternatively, when the drug to be delivered with the trans-dermal drug delivery device of the present invention has a very low solubility in the polymer used to make the porous sheath of the filaments, the drug can be mixed with the coating polymer as a suspension prior to formation of the porous sheath. In this case a slow release of the drug is provided directly to the dermis from the drug loaded coating and from there into the blood stream. Suitable coating polymers for use in the drug delivery application include bioabsorbable hydrogels that have porosity on a molecular scale.
  • EXAMPLE 1 Porous Coated Wires for Implantation of Follicle Progenitor Cells
  • An array of 21 wires, 0.0035 inches in diameter (nickel-chromium alloy, California Fine Wire Co., Grover Beach, Calif. 93433), was made by imbedding the wires in epoxy resin contained in the cut-off end of a tuberculin syringe. The wires were first placed in a 2 mm thick disc with 0.0063 inch diameter holes arranged in a pattern of one surrounded by 7 surrounded by 13. The wires were pushed into the disc until flush with the surface. The opposite surface had various lengths of wire protruding. This surface was placed in contact with the liquid epoxy resin mixture such that the protruding wires became imbedded. The surface of the disc in contact with the epoxy was first coated with a thin layer of petrolatum to prevent adhesion. Upon curing of the epoxy resin, the disc was pulled off to expose 21 wires extending exactly 2 mm from the surface of the 4.5 mm diameter plug of epoxy resin.
  • A mixture of poly(dl-lactide-co-50%-glycolide) (Resomer™ RG504, Boehringer Ingelheim, D-55216 Ingelheim am Rhein, Germany) and 5% by weight of azodicarbonamide (Aldrich Chemical Co., Milwaukee, Wis. 53201) was melt blended by stirring in a test tube immersed in an oil bath maintained at a temperature of 180° C. A small amount of this mixture was placed in the bottom of a 50 ml beaker and re-heated to give a viscous liquid. The above epoxy resin plug was inverted and the wires dipped into the molten polymer mixture to a depth of about 0.3 mm and quickly removed. This produced a thin coating of polymer mixture on the tips of the wires and fine filaments pulled away from the melt and attached to the tips.
  • Crystals of sodium chloride (Morton Popcom Salt) were placed in an electric coffee bean grinder and milled into a fine powder. A ½ inch diameter hex bolt was placed on end and a nut threaded onto the bolt just far enough to engage the threads. The cavity formed by the nut and bolt was filled with powdered salt. A thermometer was lowered into the salt and clamped in a vertical position with clamps on a ring stand. The surface of the salt was smoothed out with a spatula. The bolt was heated with a propane torch until the temperature of the salt reached 240° C. The polymer-coated wires were then dipped into the hot salt, pushed about half way in and then quickly pulled out. The adherent salt was removed by dipping the wires in water until the salt dissolved. The water was removed from the device by gently blotting with tissue paper. The device was placed back in a tuberculin syringe barrel for protection and stored in a desiccator. Scanning electron micrographs of device are shown in FIGS. 7-9.
  • EXAMPLE 2 Use of the Device of Example 1 to Produce New Hair Follicles
  • The device of Example 1 is soaked in ethanol for 5 minutes and then rinsed with sterile water. The excess water is removed from the porous structure by blotting with a sterile, lint-fee surgical sponge. This process serves both to sterilize the polymer and to improve the ability of cells to be wicked rapidly and completely into the porous polymer.
  • Human dermal papilla cells that have been multiplied in culture are collected and resuspended in an isotonic buffer solution at approximately ten million cells per cubic centimeter. The pre-wet implant is then dipped into the suspension of cells and immediately injected into human skin where the growth of hair is desired.
  • Prior to implantation, the skin is wiped with gauze soaked in 70% isopropanol and then wiped with gauze soaked in Betadine™. Lidocaine cream is then applied to the skin and covered with a Tegaderm™ dressing for a minimum of one hour. This pre-implantation procedure serves to kill bacteria and to soften and anesthetize the skin. After implanting the device, the exposed epoxy resin plug is covered with a dressing to prevent it from being disturbed or dislodged.
  • Approximately 48 hours after implantation, the dressing is removed. The wires are then removed from the skin by pulling on the epoxy resin plug. The cell-laden porous bioabsorbable polymer tips remain under the skin, having separated from the wires as a result of tissue attachment to the porous polymer and moisture induced loosening of the polymer attachment to the metal.
  • During the next period of several weeks the implanted cells multiply and organize into a new hair follicle as the bioabsorbable polymer degrades and is bioabsorbed. The growth of new hair indicates that the restoration process is complete.
  • EXAMPLE 3 Porous Scaffold for Tissue-Engineered Bone
  • Poly(70%-L-lactide-co-30%-d,l-lactide) obtained from Purac Biochem, b.v. (Gorinchem, Holland) is melt blended at about 170° C. with 5% by weight azodicarbonamide (Aldrich Chemical Co.) and pelletized. A proprietary bioabsorbable glass fiber produced by MO-SCI Corp. (Twitty Industrial Park, Rolla, Mo. 65401) is obtained as a monofilament single strand that is 100 microns in diameter.
  • A cladding extrusion die is made such that the 100 micron diameter fiber can pass through the die while polymer is extruded to cover and clad the moving fiber. The polymer/azodicarbonamide blend is extruded as a cladding on the glass to give a cross-sectional area ratio of 2:1 core to sheath.
  • The fiber is cut into 3 to 5 millimeter lengths and added to a beaker of water with stirring. The resultant slurry is then poured onto a Büchner funnel equipped with a coarse glass frit and the water allowed to drain. This produces a “wet-laid” non-woven web of fibers. The web is dried under vacuum and carefully transferred into a wire basket. The basket is lowered into a beaker of peanut oil heated to 240° C. for about one second and then immersed in a beaker of hexane. The hot oil causes the polymer to melt and the azodicarbonamide to decompose into gas, thereby converting the polymer into an open-cell foam. The cool hexane causes the polymer to solidify, thereby preserving the porous structure and adhering the glass fibers together at every point that they touch. The hexane also dissolves and removes the oil from the structure without affecting the polymer.
  • Chondrocytes are seeded onto the structure from an aqueous suspension causing the cells to wick into the porous polymer coating on the glass fibers. The structure can then be implanted in a bone defect immediately or allowed to mature in culture prior to implantation. In either case the cells will be retained in the microporous structure of the coating while the macroporous structure of the adhered fibers will allow ample room for Lissue ingrowth and osteoinduction of new bone due to the seeded cells.
  • While the present invention has now been described with some detail and specificity, those skilled in the art will appreciate the various modifications, including variations, additions, and omissions, that may be made in what has been described. Accordingly, it is intended that the scope of the present invention be limited solely by the broadest interpretation that lawfully can be accorded the appended claims.

Claims (23)

1-34. (canceled)
35. A method of facilitating the growth of new bone comprising the steps of:
a) providing an implantable device comprising a plurality of filaments, wherein each filament comprises a solid core and a porous sheath of a bioabsorbable material which coats at least a portion of the core;
b) seeding the implantable device osteogenic substance; and
c) implanting the device in a site where bone regeneration is desired.
36. (canceled)
37. The method of claim 35, wherein the core is removed from the implantable device before the device is implanted.
38. The method of claim 35 wherein the plurality of filaments forms a three-dimensional porous matrix.
39. The method of claim 35, wherein the bioabsorbable sheath polymer is selected from the group consisting of poly(lactic acid), poly(glycolic acid), poly(trimethylene carbonate), poly(amino acid)s, tyrosine-derived poly(carbonate)s, poly(carbonate)s, poly(caprolactone), poly(para-dioxanone), poly(ester)s, poly(ester-amide)s, poly(anhydride)s, poly(ortho ester)s, proteins, carbohydrates, poly(ethylene glycol)s, poly(propylene glycol)s, poly(acrylate ester)s, poly(methacrylate ester)s, poly(vinyl alcohol), and copolymers, blends and mixtures of said polymers.
40. The method of claim 39, wherein the bioabsorbable sheath polymer is poly(lactic acid).
41. The method of claim 35, wherein the core comprises a ceramic.
42. The method of claim 35, wherein the core comprises a glass.
43. The method of claim 35, wherein the core comprises a metal.
44. The method of claim 35, wherein the osteogenic substance comprises a cell selected from the group consisting of an osteoblast and a chondrocyte.
45. The method of claim 35, wherein the implantable device is sculpted prior to implanting the device.
46. The method of claim 35, wherein the site is an intervertebral space in the spine where fusion is desired.
47. The method of claim 35, wherein the site is a bone defect or gap.
48. The method of claim 35, wherein the implantable device is stored in a frozen state prior to implanting the device.
49. An implantable device comprising a plurality of filaments and an osteogenic substance, wherein each filament comprises a solid core and a porous sheath of a bioabsorbable material which coats at least a portion of the core.
50. The device of claim 49, wherein the plurality of filaments forms a three-dimensional porous matrix.
51. The device of claim 49, wherein the bioabsorbable sheath polymer is selected from the group consisting of poly(lactic acid), poly(glycolic acid), poly(trimethylene carbonate), poly(amino acid)s, tyrosine-derived poly(carbonate)s, poly(carbonate)s, poly(caprolactone), poly(para-dioxanone), poly(ester)s, poly(ester-amide)s, poly(anhydride)s, poly(ortho ester)s, proteins, carbohydrates, poly(ethylene glycol)s, poly(propylene glycol)s, poly(acrylate ester)s, poly(methacrylate ester)s, poly(vinyl alcohol), and copolymers, blends and mixtures of said polymers.
52. The device of claim 51, wherein the bioabsorbable sheath polymer is poly(lactic acid).
53. The device of claim 49, wherein the core comprises a ceramic.
54. The device of claim 49, wherein the core comprises a glass.
55. The device of claim 49, wherein the core comprises a metal.
56. The device of claim 49, wherein the osteogenic substance comprises a cell selected from the group consisting of an osteoblast and a chondrocyte.
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Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070092496A1 (en) * 2005-10-17 2007-04-26 Aderans Research Institute, Inc. Method of delivering cells to the skin
US20070122387A1 (en) * 2005-11-22 2007-05-31 Aderans Research Institute, Inc. Hair grafts derived from plucked hair
US20070148138A1 (en) * 2005-11-22 2007-06-28 Aderans Research Institute, Inc. Hair follicle graft from tissue engineered skin
US20080311044A1 (en) * 2007-06-12 2008-12-18 Aderans Research Institute, Inc. Methods of determining hair follicle inductive properties
WO2019027864A1 (en) * 2017-07-31 2019-02-07 Lorstan Pharmaceutical Llc Hair implants comprising enhanced anchoring and medical safety features
US10561490B2 (en) 2017-07-31 2020-02-18 Loria Products Llc Hair implants comprising enhanced anchoring and medical safety features
US10925718B2 (en) 2017-07-31 2021-02-23 Loria Products Llc Extension apparatus for artificial hair implants
USD916290S1 (en) 2019-03-05 2021-04-13 Loria Products Llc Hair implant
USD917050S1 (en) 2019-08-26 2021-04-20 Loria Products Llc Hair implant
US11564789B2 (en) 2017-07-31 2023-01-31 Loria Products Llc Hair implants comprising enhanced anchoring and medical safety features

Families Citing this family (29)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6884427B1 (en) * 1999-02-08 2005-04-26 Aderans Research Institute, Inc. Filamentary means for introducing agents into tissue of a living host
WO2002015952A1 (en) * 2000-08-08 2002-02-28 Bioamide, Inc. Scaffolds for tissue engineered hair
WO2002085447A2 (en) * 2001-04-20 2002-10-31 Alza Corporation Microprojection array having a beneficial agent containing coating
US20040068284A1 (en) * 2002-01-29 2004-04-08 Barrows Thomas H. Method for stimulating hair growth and kit for carrying out said method
NL1023462C2 (en) * 2003-05-19 2004-11-24 Doorzand Trocar Protector B V Insertion sleeve assembly.
US20050123507A1 (en) * 2003-06-30 2005-06-09 Mahmoud Ameri Formulations for coated microprojections having controlled solubility
BRPI0412029A (en) * 2003-06-30 2006-09-05 Alza Corp formulations for coated microprojections containing nonvolatile counterions
FI120333B (en) * 2003-08-20 2009-09-30 Bioretec Oy A porous medical device and a method of making it
US7597885B2 (en) * 2004-03-26 2009-10-06 Aderans Research Institute, Inc. Tissue engineered biomimetic hair follicle graft
US7556821B2 (en) 2004-05-13 2009-07-07 Alza Corporation Apparatus and method for transdermal delivery of parathyroid hormone agents
AR050212A1 (en) * 2004-08-13 2006-10-04 Aderans Res Inst Inc ORGANOGENESIS FROM DISCELLED CELLS
AU2005302484A1 (en) * 2004-10-28 2006-05-11 Microchips, Inc. Orthopedic and dental implant devices providing controlled drug delivery
CA2610646C (en) * 2005-06-02 2012-09-04 Arizona Board Of Regents On Behalf Of The University Of Arizona Prevascularized devices and related methods
WO2007001624A2 (en) * 2005-06-28 2007-01-04 Microchips, Inc. Medical and dental implant devices for controlled drug delivery
EP1933936B1 (en) * 2005-10-13 2019-03-20 Synthes GmbH Drug-impregnated encasement
CN102600548A (en) * 2006-02-09 2012-07-25 阿德兰斯研究学院有限公司 Apparatus and methods for delivering fluid and material to a subject
JP5386180B2 (en) 2006-02-28 2014-01-15 ザ トラスティーズ オブ コロンビア ユニヴァーシティ イン ザ シティ オブ ニューヨーク Method for compact aggregation of dermal cells
WO2008042216A2 (en) * 2006-09-28 2008-04-10 Follica, Inc. Methods, kits, and compositions for generating new hair follicles and growing hair
US7922688B2 (en) * 2007-01-08 2011-04-12 Restoration Robotics, Inc. Automated delivery of a therapeutic or cosmetic substance to cutaneous, subcutaneous and intramuscular tissue regions
US8036448B2 (en) 2007-04-05 2011-10-11 Restoration Robotics, Inc. Methods and devices for tattoo application and removal
CN102573860A (en) * 2009-10-02 2012-07-11 巴克斯特国际公司 Hematopoietic stem cells for use in the treatment of a kidney injury
US20110288652A1 (en) * 2010-05-20 2011-11-24 Indiana University Research & Technology Corporation Materials and methods for treating critically sized defects in mouse bone
DE102010029942A1 (en) * 2010-06-10 2011-12-15 Robert Bosch Gmbh injection needle
TWI590843B (en) 2011-12-28 2017-07-11 信迪思有限公司 Films and methods of manufacture
US20130216495A1 (en) 2012-02-21 2013-08-22 Baxter Healthcare Sa Pharmaceutical composition comprising cd34+ cells
USD690004S1 (en) 2012-03-16 2013-09-17 Aderans Research Institute, Inc. Holder for a device for delivering cellular material and physiologic fluids
US10085892B2 (en) 2013-03-07 2018-10-02 Life Sciences Llc Apparatus and method for wound infection prevention
KR102249720B1 (en) 2013-06-21 2021-05-11 디퍼이 신테스 프로덕츠, 인코포레이티드 Films and methods of manufacture
US9757330B2 (en) 2013-10-18 2017-09-12 Industrial Technology Research Institute Recipe for in-situ gel, and implant, drug delivery system formed thereby

Citations (93)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2946769A (en) * 1954-04-23 1960-07-26 Union Carbide Corp Linear polymers containing regularly recurring ester and amide linkages
US3025323A (en) * 1957-01-18 1962-03-13 Union Carbide Corp Amide diols and their esters
US3596292A (en) * 1969-02-20 1971-08-03 Franklin Institute Hair implant structure
US3966766A (en) * 1973-03-26 1976-06-29 Schering Corporation Monocyclic macrocyclic compounds and complexes thereof
US4052988A (en) * 1976-01-12 1977-10-11 Ethicon, Inc. Synthetic absorbable surgical devices of poly-dioxanone
US4104195A (en) * 1974-11-07 1978-08-01 Bayer Aktiengesellschaft Blowing agents based on urea dicarboxylic acid anhydride
US4209607A (en) * 1978-05-12 1980-06-24 Ethicon, Inc. Polyesteramides derived from bis-oxamidodiols and dicarboxylic acids
US4226243A (en) * 1979-07-27 1980-10-07 Ethicon, Inc. Surgical devices of polyesteramides derived from bis-oxamidodiols and dicarboxylic acids
US4242931A (en) * 1979-02-22 1981-01-06 Burke Clement Gear wrench
US4343931A (en) * 1979-12-17 1982-08-10 Minnesota Mining And Manufacturing Company Synthetic absorbable surgical devices of poly(esteramides)
US4384061A (en) * 1980-10-02 1983-05-17 Basf Aktiengesellschaft Thermosetting polycondensates containing amide and imide groups, and their use
US4429080A (en) * 1982-07-01 1984-01-31 American Cyanamid Company Synthetic copolymer surgical articles and method of manufacturing the same
US4458678A (en) * 1981-10-26 1984-07-10 Massachusetts Institute Of Technology Cell-seeding procedures involving fibrous lattices
US4505266A (en) * 1981-10-26 1985-03-19 Massachusetts Institute Of Technology Method of using a fibrous lattice
US4529792A (en) * 1979-12-17 1985-07-16 Minnesota Mining And Manufacturing Company Process for preparing synthetic absorbable poly(esteramides)
US4604097A (en) * 1985-02-19 1986-08-05 University Of Dayton Bioabsorbable glass fibers for use in the reinforcement of bioabsorbable polymers for bone fixation devices and artificial ligaments
US4643734A (en) * 1983-05-05 1987-02-17 Hexcel Corporation Lactide/caprolactone polymer, method of making the same, composites thereof, and prostheses produced therefrom
US4719917A (en) * 1987-02-17 1988-01-19 Minnesota Mining And Manufacturing Company Surgical staple
US4851521A (en) * 1985-07-08 1989-07-25 Fidia, S.P.A. Esters of hyaluronic acid
US4919664A (en) * 1986-02-21 1990-04-24 Oliver Roy F Stimulation of hair growth
US5061284A (en) * 1990-04-10 1991-10-29 Laghi Aldo A Silicone follicled hair implant
US5091173A (en) * 1989-06-29 1992-02-25 The University Of Dundee Hair growth composition
US5133739A (en) * 1990-02-06 1992-07-28 Ethicon, Inc. Segmented copolymers of ε-caprolactone and glycolide
US5141522A (en) * 1990-02-06 1992-08-25 American Cyanamid Company Composite material having absorbable and non-absorbable components for use with mammalian tissue
US5147400A (en) * 1989-05-10 1992-09-15 United States Surgical Corporation Connective tissue prosthesis
US5194473A (en) * 1989-05-26 1993-03-16 Mitsui Toatsu Chemicals, Inc. Modified polyester composition and preparation process and use thereof
US5198507A (en) * 1990-06-12 1993-03-30 Rutgers, The State University Of New Jersey Synthesis of amino acid-derived bioerodible polymers
US5286837A (en) * 1992-01-15 1994-02-15 Minnesota Mining And Manufacturing Company Process for increasing stability of poly(esteramides)
US5393323A (en) * 1993-11-05 1995-02-28 L'air Liquide S.A. Aromatic polyethersulfone gas separation membranes
US5403347A (en) * 1993-05-27 1995-04-04 United States Surgical Corporation Absorbable block copolymers and surgical articles fabricated therefrom
US5415378A (en) * 1993-05-11 1995-05-16 Cooper Industries, Inc. Valve assembly
US5423778A (en) * 1989-12-14 1995-06-13 Elof Eriksson System and method for transplantation of cells
US5486593A (en) * 1987-12-17 1996-01-23 United States Surgical Corporation Medical devices fabricated from copolymers having recurring carbonate units
US5502092A (en) * 1994-02-18 1996-03-26 Minnesota Mining And Manufacturing Company Biocompatible porous matrix of bioabsorbable material
US5514378A (en) * 1993-02-01 1996-05-07 Massachusetts Institute Of Technology Biocompatible polymer membranes and methods of preparation of three dimensional membrane structures
US5522841A (en) * 1993-05-27 1996-06-04 United States Surgical Corporation Absorbable block copolymers and surgical articles fabricated therefrom
US5545208A (en) * 1990-02-28 1996-08-13 Medtronic, Inc. Intralumenal drug eluting prosthesis
US5556783A (en) * 1991-03-27 1996-09-17 Trustees Of Univ. Of Penna Methods of culturing and modulating the growth of hair follicular stem cells
US5578046A (en) * 1994-02-10 1996-11-26 United States Surgical Corporation Composite bioabsorbable materials and surgical articles made thereform
US5599552A (en) * 1989-07-24 1997-02-04 Atrix Laboratories, Inc. Biodegradable polymer composition
US5611811A (en) * 1994-04-29 1997-03-18 Star-Wood, Inc. Micro and mini hair transplant device
US5639645A (en) * 1993-09-22 1997-06-17 Mitsubishi Corporation Recombinant Δ9 desaturase and a gene encoding the same
US5661132A (en) * 1989-12-14 1997-08-26 Auragen, Inc. Wound healing
US5667961A (en) * 1987-03-26 1997-09-16 Centre International De Recherches Dermatologigues Galderma (Cird Galderma) Skin substitute
US5674286A (en) * 1991-02-12 1997-10-07 United States Surgical Corporation Bioabsorbable medical implants
US5690961A (en) * 1994-12-22 1997-11-25 Hercules Incorporated Acidic polysaccharides crosslinked with polycarboxylic acids and their uses
US5697976A (en) * 1992-06-15 1997-12-16 United States Surgical Corporation Bioabsorbable implant material
US5697901A (en) * 1989-12-14 1997-12-16 Elof Eriksson Gene delivery by microneedle injection
US5721049A (en) * 1993-11-15 1998-02-24 Trustees Of The University Of Pennsylvania Composite materials using bone bioactive glass and ceramic fibers
US5723508A (en) * 1996-01-25 1998-03-03 Northwestern University Method of fabricating emulsion freeze-dried scaffold bodies and resulting products
US5756094A (en) * 1991-03-27 1998-05-26 Trustees Of The University Of Pennsylvania Methods for stimulating follicular growth
US5770417A (en) * 1986-11-20 1998-06-23 Massachusetts Institute Of Technology Children's Medical Center Corporation Three-dimensional fibrous scaffold containing attached cells for producing vascularized tissue in vivo
US5847012A (en) * 1993-08-13 1998-12-08 Smith & Nephew, Inc. Microporous polymeric foams and microtextured surfaces
US5919893A (en) * 1997-01-28 1999-07-06 United States Surgical Corporation Polyesteramide, its preparation and surgical devices fabricated therefrom
US5939323A (en) * 1996-05-28 1999-08-17 Brown University Hyaluronan based biodegradable scaffolds for tissue repair
US5945115A (en) * 1991-10-15 1999-08-31 Atrix Laboratories, Inc. Polymeric compositions useful as controlled release implants
US5993374A (en) * 1997-06-17 1999-11-30 Radiance Medical Systems, Inc. Microcapsules for site-specific delivery
US5997568A (en) * 1996-01-19 1999-12-07 United States Surgical Corporation Absorbable polymer blends and surgical articles fabricated therefrom
US6027744A (en) * 1998-04-24 2000-02-22 University Of Massachusetts Medical Center Guided development and support of hydrogel-cell compositions
US6031148A (en) * 1990-12-06 2000-02-29 W. L. Gore & Associates, Inc. Implantable bioabsorbable article
US6051750A (en) * 1992-08-07 2000-04-18 Tissue Engineering, Inc. Method and construct for producing graft tissue from an extracellular matrix
US6093200A (en) * 1994-02-10 2000-07-25 United States Surgical Composite bioabsorbable materials and surgical articles made therefrom
US6120788A (en) * 1997-10-16 2000-09-19 Bioamide, Inc. Bioabsorbable triglycolic acid poly(ester-amide)s
US6147135A (en) * 1998-12-31 2000-11-14 Ethicon, Inc. Fabrication of biocompatible polymeric composites
US6350284B1 (en) * 1998-09-14 2002-02-26 Bionx Implants, Oy Bioabsorbable, layered composite material for guided bone tissue regeneration
US20020049426A1 (en) * 1995-06-07 2002-04-25 Mark D. Butler Implantable containment apparatus for a therapeutical device
US6383220B1 (en) * 1998-11-30 2002-05-07 Isotis N.V. Artificial skin
US20020083216A1 (en) * 2000-12-21 2002-06-27 International Business Machines Corporation Multi-platform command line interpretation
US6423252B1 (en) * 2000-06-23 2002-07-23 Ethicon, Inc. Methods of making micropatterned foams
US6436424B1 (en) * 2000-03-20 2002-08-20 Biosphere Medical, Inc. Injectable and swellable microspheres for dermal augmentation
US6474344B2 (en) * 2000-02-03 2002-11-05 Shiro Yamada Artificial hair for implantation and process for producing the artificial hair
US6503539B2 (en) * 1998-02-27 2003-01-07 Biora Bioex Ab Matrix protein compositions for wound healing
US20030009113A1 (en) * 2001-07-09 2003-01-09 Lorin Olson Micro-needles and methods of manufacture and use thereof
US6511748B1 (en) * 1998-01-06 2003-01-28 Aderans Research Institute, Inc. Bioabsorbable fibers and reinforced composites produced therefrom
US20030072784A1 (en) * 1999-03-04 2003-04-17 Tepha, Inc. Bioabsorbable, biocompatible polymers for tissue engineering
US20030077311A1 (en) * 1999-06-30 2003-04-24 Vyakarnam Murty N. Foam composite for the repair or regeneration of tissue
US6569143B2 (en) * 1999-10-14 2003-05-27 Becton, Dickinson And Company Method of intradermally injecting substances
US20030161815A1 (en) * 2002-02-12 2003-08-28 Intercytex Limited Cell delivery system
US6613798B1 (en) * 2000-03-30 2003-09-02 Curis, Inc. Small organic molecule regulators of cell proliferation
US20030195625A1 (en) * 2002-04-15 2003-10-16 Garcia Castro Marco A. Biodegradable follicle hair implant
US20030198646A1 (en) * 2002-04-17 2003-10-23 Stenn Kurt Stricker Compositions and methods for inducing new hair follicle formation and hair growth in a desired orientation
US6639051B2 (en) * 1997-10-20 2003-10-28 Curis, Inc. Regulation of epithelial tissue by hedgehog-like polypeptides, and formulations and uses related thereto
US20030203003A1 (en) * 1999-08-06 2003-10-30 Nelson Kevin D. Drug releasing biodegradable fiber implant
US20030211083A1 (en) * 2001-03-15 2003-11-13 Jean-Marie Vogel Injectable microspheres for tissue construction
US20040033598A1 (en) * 1999-12-30 2004-02-19 University Of Massachusetts, A Massachusetts Corporation Compositions and methods for generating skin
US20040039438A1 (en) * 1998-04-11 2004-02-26 Inflow Dynamics, Inc., A Delaware Corporation Vascular and endoluminal stents with multi-layer coating including porous radiopaque layer
US6699287B2 (en) * 1998-09-24 2004-03-02 Korea Atomic Energy Research Institute Dermal scaffold using alkaline pre-treated chitosan matrix or alkaline pre-treated chitosan and alkaline pre-treated collagen mixed matrix
US20040054410A1 (en) * 2000-08-08 2004-03-18 Barrows Thomas H Scaffolds for tissue engineered hair
US20040057937A1 (en) * 1997-04-30 2004-03-25 Jahoda Amanda Jane Dermal sheath tissue in wound healing
US20040068284A1 (en) * 2002-01-29 2004-04-08 Barrows Thomas H. Method for stimulating hair growth and kit for carrying out said method
US20040096514A1 (en) * 1999-03-05 2004-05-20 Biosphere Medical, Inc. Injectable microspheres for dermal augmentation and tissue bulking
US6773713B2 (en) * 2001-02-23 2004-08-10 University Of Massachusetts Injection molding of living tissues
US6884427B1 (en) * 1999-02-08 2005-04-26 Aderans Research Institute, Inc. Filamentary means for introducing agents into tissue of a living host

Patent Citations (100)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2946769A (en) * 1954-04-23 1960-07-26 Union Carbide Corp Linear polymers containing regularly recurring ester and amide linkages
US3025323A (en) * 1957-01-18 1962-03-13 Union Carbide Corp Amide diols and their esters
US3596292A (en) * 1969-02-20 1971-08-03 Franklin Institute Hair implant structure
US3966766A (en) * 1973-03-26 1976-06-29 Schering Corporation Monocyclic macrocyclic compounds and complexes thereof
US4104195A (en) * 1974-11-07 1978-08-01 Bayer Aktiengesellschaft Blowing agents based on urea dicarboxylic acid anhydride
US4052988A (en) * 1976-01-12 1977-10-11 Ethicon, Inc. Synthetic absorbable surgical devices of poly-dioxanone
US4209607A (en) * 1978-05-12 1980-06-24 Ethicon, Inc. Polyesteramides derived from bis-oxamidodiols and dicarboxylic acids
US4242931A (en) * 1979-02-22 1981-01-06 Burke Clement Gear wrench
US4226243A (en) * 1979-07-27 1980-10-07 Ethicon, Inc. Surgical devices of polyesteramides derived from bis-oxamidodiols and dicarboxylic acids
US4529792A (en) * 1979-12-17 1985-07-16 Minnesota Mining And Manufacturing Company Process for preparing synthetic absorbable poly(esteramides)
US4343931A (en) * 1979-12-17 1982-08-10 Minnesota Mining And Manufacturing Company Synthetic absorbable surgical devices of poly(esteramides)
US4384061A (en) * 1980-10-02 1983-05-17 Basf Aktiengesellschaft Thermosetting polycondensates containing amide and imide groups, and their use
US4458678A (en) * 1981-10-26 1984-07-10 Massachusetts Institute Of Technology Cell-seeding procedures involving fibrous lattices
US4505266A (en) * 1981-10-26 1985-03-19 Massachusetts Institute Of Technology Method of using a fibrous lattice
US4429080A (en) * 1982-07-01 1984-01-31 American Cyanamid Company Synthetic copolymer surgical articles and method of manufacturing the same
US4643734A (en) * 1983-05-05 1987-02-17 Hexcel Corporation Lactide/caprolactone polymer, method of making the same, composites thereof, and prostheses produced therefrom
US4604097A (en) * 1985-02-19 1986-08-05 University Of Dayton Bioabsorbable glass fibers for use in the reinforcement of bioabsorbable polymers for bone fixation devices and artificial ligaments
US4604097B1 (en) * 1985-02-19 1991-09-10 Univ Dayton
US4851521A (en) * 1985-07-08 1989-07-25 Fidia, S.P.A. Esters of hyaluronic acid
US4919664A (en) * 1986-02-21 1990-04-24 Oliver Roy F Stimulation of hair growth
US5770417A (en) * 1986-11-20 1998-06-23 Massachusetts Institute Of Technology Children's Medical Center Corporation Three-dimensional fibrous scaffold containing attached cells for producing vascularized tissue in vivo
US4719917A (en) * 1987-02-17 1988-01-19 Minnesota Mining And Manufacturing Company Surgical staple
US5667961A (en) * 1987-03-26 1997-09-16 Centre International De Recherches Dermatologigues Galderma (Cird Galderma) Skin substitute
US5486593A (en) * 1987-12-17 1996-01-23 United States Surgical Corporation Medical devices fabricated from copolymers having recurring carbonate units
US5147400A (en) * 1989-05-10 1992-09-15 United States Surgical Corporation Connective tissue prosthesis
US5194473A (en) * 1989-05-26 1993-03-16 Mitsui Toatsu Chemicals, Inc. Modified polyester composition and preparation process and use thereof
US5091173A (en) * 1989-06-29 1992-02-25 The University Of Dundee Hair growth composition
US5599552A (en) * 1989-07-24 1997-02-04 Atrix Laboratories, Inc. Biodegradable polymer composition
US5423778A (en) * 1989-12-14 1995-06-13 Elof Eriksson System and method for transplantation of cells
US5697901A (en) * 1989-12-14 1997-12-16 Elof Eriksson Gene delivery by microneedle injection
US5661132A (en) * 1989-12-14 1997-08-26 Auragen, Inc. Wound healing
US5133739A (en) * 1990-02-06 1992-07-28 Ethicon, Inc. Segmented copolymers of ε-caprolactone and glycolide
US5141522A (en) * 1990-02-06 1992-08-25 American Cyanamid Company Composite material having absorbable and non-absorbable components for use with mammalian tissue
US5545208A (en) * 1990-02-28 1996-08-13 Medtronic, Inc. Intralumenal drug eluting prosthesis
US5997468A (en) * 1990-02-28 1999-12-07 Medtronic, Inc. Intraluminal drug eluting prosthesis method
US5061284A (en) * 1990-04-10 1991-10-29 Laghi Aldo A Silicone follicled hair implant
US5198507A (en) * 1990-06-12 1993-03-30 Rutgers, The State University Of New Jersey Synthesis of amino acid-derived bioerodible polymers
US6031148A (en) * 1990-12-06 2000-02-29 W. L. Gore & Associates, Inc. Implantable bioabsorbable article
US5674286A (en) * 1991-02-12 1997-10-07 United States Surgical Corporation Bioabsorbable medical implants
US5756094A (en) * 1991-03-27 1998-05-26 Trustees Of The University Of Pennsylvania Methods for stimulating follicular growth
US5556783A (en) * 1991-03-27 1996-09-17 Trustees Of Univ. Of Penna Methods of culturing and modulating the growth of hair follicular stem cells
US5945115A (en) * 1991-10-15 1999-08-31 Atrix Laboratories, Inc. Polymeric compositions useful as controlled release implants
US5286837A (en) * 1992-01-15 1994-02-15 Minnesota Mining And Manufacturing Company Process for increasing stability of poly(esteramides)
US5697976A (en) * 1992-06-15 1997-12-16 United States Surgical Corporation Bioabsorbable implant material
US6051750A (en) * 1992-08-07 2000-04-18 Tissue Engineering, Inc. Method and construct for producing graft tissue from an extracellular matrix
US5514378A (en) * 1993-02-01 1996-05-07 Massachusetts Institute Of Technology Biocompatible polymer membranes and methods of preparation of three dimensional membrane structures
US5415378A (en) * 1993-05-11 1995-05-16 Cooper Industries, Inc. Valve assembly
US5403347A (en) * 1993-05-27 1995-04-04 United States Surgical Corporation Absorbable block copolymers and surgical articles fabricated therefrom
US5522841A (en) * 1993-05-27 1996-06-04 United States Surgical Corporation Absorbable block copolymers and surgical articles fabricated therefrom
US5847012A (en) * 1993-08-13 1998-12-08 Smith & Nephew, Inc. Microporous polymeric foams and microtextured surfaces
US5898040A (en) * 1993-08-13 1999-04-27 Poly-Med, Inc. Microporous polymeric foams and microtextured surfaces
US5639645A (en) * 1993-09-22 1997-06-17 Mitsubishi Corporation Recombinant Δ9 desaturase and a gene encoding the same
US5393323A (en) * 1993-11-05 1995-02-28 L'air Liquide S.A. Aromatic polyethersulfone gas separation membranes
US5721049A (en) * 1993-11-15 1998-02-24 Trustees Of The University Of Pennsylvania Composite materials using bone bioactive glass and ceramic fibers
US6093200A (en) * 1994-02-10 2000-07-25 United States Surgical Composite bioabsorbable materials and surgical articles made therefrom
US5578046A (en) * 1994-02-10 1996-11-26 United States Surgical Corporation Composite bioabsorbable materials and surgical articles made thereform
US5502092A (en) * 1994-02-18 1996-03-26 Minnesota Mining And Manufacturing Company Biocompatible porous matrix of bioabsorbable material
US5611811A (en) * 1994-04-29 1997-03-18 Star-Wood, Inc. Micro and mini hair transplant device
US5690961A (en) * 1994-12-22 1997-11-25 Hercules Incorporated Acidic polysaccharides crosslinked with polycarboxylic acids and their uses
US20020049426A1 (en) * 1995-06-07 2002-04-25 Mark D. Butler Implantable containment apparatus for a therapeutical device
US5997568A (en) * 1996-01-19 1999-12-07 United States Surgical Corporation Absorbable polymer blends and surgical articles fabricated therefrom
US5723508A (en) * 1996-01-25 1998-03-03 Northwestern University Method of fabricating emulsion freeze-dried scaffold bodies and resulting products
US5939323A (en) * 1996-05-28 1999-08-17 Brown University Hyaluronan based biodegradable scaffolds for tissue repair
US5919893A (en) * 1997-01-28 1999-07-06 United States Surgical Corporation Polyesteramide, its preparation and surgical devices fabricated therefrom
US20040057937A1 (en) * 1997-04-30 2004-03-25 Jahoda Amanda Jane Dermal sheath tissue in wound healing
US5993374A (en) * 1997-06-17 1999-11-30 Radiance Medical Systems, Inc. Microcapsules for site-specific delivery
US6365172B1 (en) * 1997-10-16 2002-04-02 Bioamide, Inc. Device of bioabsorbable triglycolic acid poly(ester-amide)s, and methods of making the same
US6120788A (en) * 1997-10-16 2000-09-19 Bioamide, Inc. Bioabsorbable triglycolic acid poly(ester-amide)s
US6639051B2 (en) * 1997-10-20 2003-10-28 Curis, Inc. Regulation of epithelial tissue by hedgehog-like polypeptides, and formulations and uses related thereto
US20030134099A1 (en) * 1998-01-06 2003-07-17 Bioamide, Inc. Bioabsorbable fibers and reinforced composites produced therefrom
US6511748B1 (en) * 1998-01-06 2003-01-28 Aderans Research Institute, Inc. Bioabsorbable fibers and reinforced composites produced therefrom
US6503539B2 (en) * 1998-02-27 2003-01-07 Biora Bioex Ab Matrix protein compositions for wound healing
US20040039438A1 (en) * 1998-04-11 2004-02-26 Inflow Dynamics, Inc., A Delaware Corporation Vascular and endoluminal stents with multi-layer coating including porous radiopaque layer
US6027744A (en) * 1998-04-24 2000-02-22 University Of Massachusetts Medical Center Guided development and support of hydrogel-cell compositions
US6350284B1 (en) * 1998-09-14 2002-02-26 Bionx Implants, Oy Bioabsorbable, layered composite material for guided bone tissue regeneration
US6699287B2 (en) * 1998-09-24 2004-03-02 Korea Atomic Energy Research Institute Dermal scaffold using alkaline pre-treated chitosan matrix or alkaline pre-treated chitosan and alkaline pre-treated collagen mixed matrix
US6383220B1 (en) * 1998-11-30 2002-05-07 Isotis N.V. Artificial skin
US6147135A (en) * 1998-12-31 2000-11-14 Ethicon, Inc. Fabrication of biocompatible polymeric composites
US6303697B1 (en) * 1998-12-31 2001-10-16 Ethicon, Inc. Fabrication of biocompatible polymeric composites
US6884427B1 (en) * 1999-02-08 2005-04-26 Aderans Research Institute, Inc. Filamentary means for introducing agents into tissue of a living host
US20030072784A1 (en) * 1999-03-04 2003-04-17 Tepha, Inc. Bioabsorbable, biocompatible polymers for tissue engineering
US20040096514A1 (en) * 1999-03-05 2004-05-20 Biosphere Medical, Inc. Injectable microspheres for dermal augmentation and tissue bulking
US20030077311A1 (en) * 1999-06-30 2003-04-24 Vyakarnam Murty N. Foam composite for the repair or regeneration of tissue
US20030203003A1 (en) * 1999-08-06 2003-10-30 Nelson Kevin D. Drug releasing biodegradable fiber implant
US6569143B2 (en) * 1999-10-14 2003-05-27 Becton, Dickinson And Company Method of intradermally injecting substances
US20040033598A1 (en) * 1999-12-30 2004-02-19 University Of Massachusetts, A Massachusetts Corporation Compositions and methods for generating skin
US6474344B2 (en) * 2000-02-03 2002-11-05 Shiro Yamada Artificial hair for implantation and process for producing the artificial hair
US6436424B1 (en) * 2000-03-20 2002-08-20 Biosphere Medical, Inc. Injectable and swellable microspheres for dermal augmentation
US6613798B1 (en) * 2000-03-30 2003-09-02 Curis, Inc. Small organic molecule regulators of cell proliferation
US6423252B1 (en) * 2000-06-23 2002-07-23 Ethicon, Inc. Methods of making micropatterned foams
US20040054410A1 (en) * 2000-08-08 2004-03-18 Barrows Thomas H Scaffolds for tissue engineered hair
US20020083216A1 (en) * 2000-12-21 2002-06-27 International Business Machines Corporation Multi-platform command line interpretation
US6773713B2 (en) * 2001-02-23 2004-08-10 University Of Massachusetts Injection molding of living tissues
US20030211083A1 (en) * 2001-03-15 2003-11-13 Jean-Marie Vogel Injectable microspheres for tissue construction
US20030208138A1 (en) * 2001-07-09 2003-11-06 Lorin Olson Micro-needles and methods of manufacture and use thereof
US20030009113A1 (en) * 2001-07-09 2003-01-09 Lorin Olson Micro-needles and methods of manufacture and use thereof
US20040068284A1 (en) * 2002-01-29 2004-04-08 Barrows Thomas H. Method for stimulating hair growth and kit for carrying out said method
US20030161815A1 (en) * 2002-02-12 2003-08-28 Intercytex Limited Cell delivery system
US20030195625A1 (en) * 2002-04-15 2003-10-16 Garcia Castro Marco A. Biodegradable follicle hair implant
US20030198646A1 (en) * 2002-04-17 2003-10-23 Stenn Kurt Stricker Compositions and methods for inducing new hair follicle formation and hair growth in a desired orientation

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US20070092496A1 (en) * 2005-10-17 2007-04-26 Aderans Research Institute, Inc. Method of delivering cells to the skin
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US20070148138A1 (en) * 2005-11-22 2007-06-28 Aderans Research Institute, Inc. Hair follicle graft from tissue engineered skin
US20100178683A1 (en) * 2005-11-22 2010-07-15 Aderans Research Insitute, Inc. Hair follicle graft from tissue engineered skin
US9023380B2 (en) 2005-11-22 2015-05-05 Aderans Research Institute, Inc. Hair follicle graft from tissue engineered skin
US20080311044A1 (en) * 2007-06-12 2008-12-18 Aderans Research Institute, Inc. Methods of determining hair follicle inductive properties
US7985537B2 (en) 2007-06-12 2011-07-26 Aderans Research Institute, Inc. Methods for determining the hair follicle inductive properties of a composition
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