Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
  • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
  • A61F2/0063—Implantable repair or support meshes, e.g. hernia meshes
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
  • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
  • A61F2/02—Prostheses implantable into the body
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
  • A61F13/00—Bandages or dressings; Absorbent pads
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
  • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
  • A61F2/0077—Special surfaces of prostheses, e.g. for improving ingrowth
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
  • A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
  • A61F2210/0004—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
  • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
  • A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
  • A61F2250/0051—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in tissue ingrowth capacity, e.g. made from both ingrowth-promoting and ingrowth-preventing parts
• • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
  • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
  • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
  • Y10T156/00—Adhesive bonding and miscellaneous chemical manufacture
  • Y10T156/10—Methods of surface bonding and/or assembly therefor

Definitions

• This invention relates to surgical prostheses for repairing abdominal hernias.
• a hernia is defined as a defect in the strong or fascia layer of the abdominal wall which allows abdominal organs (e.g., intestine and/or omentum) to protrude. Once out of their normal position, these organs can become pinched or twisted. The most common hernia symptoms are abdominal pain, nausea, vomiting, and an abdominal mass or lump that may come and go. Hernias are commonly caused by previous surgical incisions, but can also occur without a previous surgery.
• l material called a mesh is commonly utilized in repairing the defect in order to add extra strength.
• a conventional procedure for repairing a hernia involves making an incision over the site of the hernia, pushing the internal viscera back into the abdominal cavity and closing the opening by stitching or suturing one side firmly to the other. Another procedure involves making the incision, placing a piece of knitted mesh material over the hernial opening, holding or suturing the mesh material firmly in place, and closing the incision.
• a prosthesis for repairing a hernia in accordance with the present invention comprises an adhesion-resistant biodegradable region and an opposing tissue-ingrowth biodegradable region.
• the adhesion- resistant biodegradable region covers a fascial defect of the hernia, and the tissue- ingrowth biodegradable region is located above the adhesion-resistant biodegradable region while being exposed substantially only to the host's subcutaneous tissue (e.g., fat) layer. This orientation allows the tissue-ingrowth biodegradable region to become firmly incorporated with the host's body tissue.
• the adhesion-resistant biodegradable region faces the internal organs and decreases the incidence of adhesions and/or bowel obstruction.
• the adhesion-resistant biodegradable region comprises a rate of biodegradation which is substantially greater than a rate of biodegradation of the tissue-ingrowth biodegradable region.
• the adhesion-resistant biodegradable region comprises a resorbable polymer composition which is different than a resorbable polymer composition of the tissue-ingrowth biodegradable region.
• the adhesion-resistant biodegradable region and the tissue-ingrowth biodegradable region are both surgically attached to the fascia, whereas in another embodiment the tissue-ingrowth biodegradable region is surgically attached to the fascia while the adhesion-resistant biodegradable region is attached to the tissue- ingrowth biodegradable region and optionally to the fascia.
• FIG. 1 is a perspective view of an embodiment of a biodegradable surgical prosthesis in accordance with the present invention
• FIG. 2 is a cross-sectional view of an abdominal wall that has been repaired using an embodiment of the biodegradable surgical prosthesis of the present invention.
• FIG. 3 is a cross-sectional view of an abdominal wall that has been repaired using another embodiment of the biodegradable surgical prosthesis of the present invention.
• a biodegradable surgical prosthesis 10 is shown in FIG. 1 comprising a tissue-ingrowth biodegradable region 12 and an opposing adhesion-resistant biodegradable region 14.
• the biodegradable surgical prosthesis 10 is constructed for use in the repair of soft tissue defects, such as soft tissue defects resulting from incisional and other hernias and soft tissue defects resulting from extirpative tumor surgery.
• the biodegradable surgical prosthesis 10 may also be used in cancer surgeries, such as surgeries involving sarcoma of the extremities where saving a limb is a goal.
• biodegradable surgical prosthesis 10 of the present invention may include laparoscopic or standard hernia repair in the groin area, umbilical hernia repair, paracolostomy hernia repair, femora hernia repair, lumbar hernia repair, and the repair of other abdominal wall defects, thoracic wall defects and diaphragmatic hernias and defects.
• Each of the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 can comprise, for example, a biodegradable, and more preferably bioresorbable, polyhydroxyacid material.
• biodegradable polymers which may be used with the invention, require enzymes of microorganisms for hydrolytic or oxidative degradation, whereas bioresorbable polymers, which are presently preferred, degrade in the physiological environment with the by-products being eliminated or completely bioabsorbed.
• a polymer that loses its weight over time in the living body can be referred to as an absorbable, resorbable, bioabsorbable, or even biodegradable polymer.
• Biodegradable polymers including resorbalbe polymers, can be classified on the basis of their origin as either naturally occurring or synthetic.
• synthetic resorbable polymers for implants polyhydroxyacids occupy the main position.
• Non limiting examples of these each of which may individually or in combination be used to form all or part of the biodegradable prosthesis include poly(L- lactide), poly(glycolide) and polymers or copolymers based on L-lactide, L/DL-lactide, DL-lactide, glycolide, trimethyl carbonate, ⁇ -caprolactone, dioxanone, and physical and chemical combinations thereof.
• tissue- ingrowth region 12 can comprise or consist of a non-biodegradable polymer, such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• a non-biodegradable polymer such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may differ in both (A) surface appearance and (B) surface function.
• the tissue-ingrowth biodegradable region 12 can be constructed with at least one of a surface topography (appearance) and a surface composition (function), either of which may facilitate strength, longevity and/or a substantial fibroblastic reaction in the host tissue relative to for example the anti-adhesion biodegradable region 14.
• the adhesion- resistant biodegradable region 14 can be constructed with at least one of a surface topography and a surface composition, either of which may facilitate, relative to the tissue-ingrowth biodegradable region 12, an anti-adhesive effect between the biodegradable surgical implant 10 and host tissues.
• the tissue-ingrowth biodegradable region 12 can be formed to have an open, non-smooth and/or featured surface comprising, for example, alveoli and/or pores distributed regularly or irregularly.
• the tissue-ingrowth biodegradable region 12 can be formed to have, additionally or alternatively, an uneven (e.g., cracked, broken, roughened or flaked) surface which, as with the above-described surfaces, may cause tissue turbulence (e.g., potential tissue inflammation and/or scarring) between host tissues and the tissue-ingrowth biodegradable region 12.
• the patient's fibrous and collagenous tissue may substantially completely overgrow the tissue-ingrowth biodegradable region 12, growing over and affixing the tissue-ingrowth biodegradable region 12 to the tissue.
• the tissue-ingrowth biodegradable region 12 comprises a plurality of alveoli or apertures visible to the naked eye, through or over which the host tissue can grow and achieve substantial fixation.
• pores may be formed into the tissue-ingrowth biodegradable region by punching or otherwise machining, or by using laser energy.
• Non-smooth surfaces may be formed, for example, by abrading the tissue-ingrowth biodegradable region 12 with a relatively course surface (e.g., having a 40 or, preferably, higher grit sandpaper-like surface) or, alternatively, non-smooth surfaces may be generated by bringing the tissue- ingrowth biodegradable region 12 up to its softening or melting temperature and imprinting it with a template (to use the same example, a sandpaper-like surface). The imprinting may occur, for example, during an initial formation process or at a subsequent time.
• the adhesion-resistant biodegradable region 14 can be formed to have a closed, continuous, smooth and/or non-porous surface.
• at least a portion of the adhesion-resistant biodegradable region 14 is smooth comprising no protuberances, alveoli or vessel-permeable pores, so as to attenuate occurrences of adhesions between the tissue-ingrowth biodegradable region 12 and host tissues.
• one side of the press may be formed to generate any of the tissue-ingrowth biodegradable region surfaces discussed above and the other side of the press may be formed to generate an adhesion-resistant biodegradable region surface as discussed above. Additional features (e.g., roughening or forming apertures) may subsequently be added to further define the surface of, for example, the tissue-ingrowth biodegradable region.
• one side of the output orifice may be formed (e.g.
• the adhesion- resistant biodegradable region is extruded to have a smooth surface and in another embodiment the adhesion-resistant biodegradable region is further processed (e.g., smoothed) after being extruded.
• the tissue-ingrowth biodegradable region 12 comprises a first material
• the adhesion-resistant biodegradable region 14 comprises a second material which is different from the first material.
• the tissue- ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may comprise the same or substantially the same materials.
• the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may comprise different materials resulting from, for example, an additive having been introduced to at least one of the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14.
• the adhesion-resistant biodegradable region 14 can be formed to have any of the structures or dimensions disclosed in U.S. Patent No. 6,673,362, entitled BIODEGRADABLE BARRIER MICRO-MEMBRANES FOR ATTENUATION OF SCAR TISSUE DURING HEALING, the entire contents of which are incorporated herein by reference, and/or may be formed with or in combination with any of the materials described herein, preferably to facilitate tissue separation with attenuated (e.g., eliminated) adhesion.
• the adhesion-resistant biodegradable region 14 is constructed to minimize an occurrence of adhesions of host tissues (e.g., internal body viscera) to the biodegradable surgical prosthesis 10.
• host tissues e.g., internal body viscera
• the adhesion-resistant biodegradable region 14 should be sufficiently non-inflammatory while being absorbed so as not to cause adhesions itself. For example, it is believed that resorption into the body too quickly of the adhesion- resistant biodegradable region 14 may yield undesirable drops in local pH levels, thus possibly introducing/elevating, for example, local inflammation, discomfort and/or foreign antibody responses.
• an object of the adhesion-resistant biodegradable region 14 can be to attenuate tissue turbulence and any accompanying inflammation (e.g., swelling).
• the adhesion-resistant biodegradable region 14 and the tissue-ingrowth biodegradable region 12 of the biodegradable surgical prosthesis 10 may be formed of the same material or relatively less divergent materials, functionally speaking, and the adhesion-resistant biodegradable region 14 may be used in conjunction with an anti-inflammatory gel agent applied, for example, onto the adhesion-resistant biodegradable region 14 at a time of implantation of the biodegradable surgical prosthesis 10.
• the adhesion-resistant biodegradable region 14 and the tissue-ingrowth biodegradable region 12 may be formed of any materials or combinations of materials disclosed herein (including embodiments wherein the two regions share the same layer of material) or their substantial equivalents, and the adhesion-resistant biodegradable region 14 may be used in conjunction with an anti-inflammatory gel agent applied, for example, onto the adhesion-resistant biodegradable region 14 at a time of implantation of the biodegradable surgical prosthesis 10.
• the tissue-ingrowth biodegradable region 12 can be formed of similar and/or different materials to those set forth above, to facilitate strength, longevity and/or direct post-surgical cell colonization via, for example, invoking a substantial fibroblastic reaction in the host tissue.
• the tissue-ingrowth biodegradable region 12 is constructed to be substantially incorporated into the host tissue and/or to substantially increases the structural integrity of the biodegradable surgical prosthesis 10.
• body tissues e.g., subcutaneous tissue and/or the exterior fascia
• the body upon sensing the presence of the tissue-ingrowth biodegradable region 12 of the present invention, is disposed to send out fibrous tissue which grows in, around and/or through and at least partially entwines itself with the tissue-ingrowth biodegradable region 12. In this manner, the biodegradable surgical prosthesis 10 can become securely attached to the host body tissue.
• the tissue-ingrowth biodegradable region 12 can comprises a biodegradable (e.g., resorbalbe) polymer composition having one or more different characteristics than that or those of a biodegradable (e.g., resorbalbe) polymer composition of the adhesion-resistant biodegradable region 14.
• the different characteristics may include (Ia) time or rate of biodegradation affected by additives, (Ib) time or rate of biodegradation affected by polymer structures/compositions, (2) polymer composition affecting strength or structural integrity, and (3) ability to facilitate fibroblastic reaction.
• the time or rate of biodegradation for the adhesion-resistant biodegradable region 14 may be substantially greater than the rate of biodegradation of the tissue- ingrowth biodegradable region 12.
• This rate differential may be effectuated through, for example, use of (a) additives and/or (b) polymer structures/compositions.
• the characteristic is a time or rate of biodegradation influenced by the incorporation of an additive to at least one of the tissue- ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14.
• a rate of biodegradation of the adhesion-resistant biodegradable region 14 is substantially greater than a rate of biodegradation of the tissue-ingrowth biodegradable region 12.
• an accelerator or retardant can be provided in one or more of the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14.
• the additive may comprise, in typical embodiments, one or more of (i) retardants for retarding a rate of biodegradation of a polymer when added to the polymer and (ii) accelerators for accelerating a rate of biodegradation of a polymer when added to the polymer.
• retardants can be added to (e.g., incorporated into) the tissue-ingrowth biodegradable region 12 and/or accelerators can be added to (e.g., incorporated into) the adhesion-resistant biodegradable region 14.
• Retardants of the present invention can include hydrophobic compounds (i.e., repelling, tending not to combine with, or incapable of dissolving in water), to decrease the rate of biodegradation.
• Agents which may serve as retardants in accordance with the present invention include non-water soluble polymers, e.g. high molecular weight methylcellulose and ethylcellulose, etc., and low water soluble organic compounds.
• Exemplary hydrophobic agents of an implementation of the invention may comprise compounds which have less than about lOO ⁇ g/ml solubility in water at ambient temperature.
• a retardant may include any matter which is hydrophobic, wherein one implementation includes particles, for example powders or granules, which are at least partially made up of hydrophobic polymers.
• Accelerators of the present invention can include hydrophilic compounds (i.e., having an affinity for, readily absorbing, or dissolving in water), to increase the rate of biodegradation.
• the accelerators of the present invention may be physiologically inert, water soluble polymers, e.g. low molecular weight methyl cellulose or hydroxypropyl methyl cellulose; sugars, e.g. monosaccharides such as fructose and glucose, disaccharides such as lactose, sucrose, or polysaccharides such as cellulose, amylose, dextran, etc.
• Exemplary hydrophilic compounds of the invention may comprise components which have at least about lOO ⁇ g/ml solubility in water at ambient temperature.
• an accelerator may include any matter which is hydrophilic, wherein an implementation includes particles, for example powders or granules, which comprise hydrophilic polymers.
• the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 both comprise resorbable compositions, and a resorption retarding agent (retardant) is provided in the tissue-ingrowth biodegradable region 12 so that the tissue-ingrowth biodegradable region 12 biodegrades at a relatively slow rate.
• the retardant may also be provided in the adhesion-resistant biodegradable region 14 at, for example, the same or a lower concentration.
• the tissue-ingrowth biodegradable region 12 biodegrades at a relatively slow rate to provide ample time for host tissues to form over and into the space occupied by the tissue-ingrowth biodegradable region 12.
• the biodegradable surgical prosthesis 10 is biodegraded (e.g., resorbed) into a mammalian body within a period of about 24 months or longer from an initial implantation of the implant into the mammalian body.
• the biodegradable surgical prosthesis 10 loses its mechanical strength within 18 months and, preferably, within 24 months and, more preferably, with a period of or greater than 36 or 48 months from the time of implantation.
• the characteristic is a polymer composition of at least one of the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14.
• a rate of biodegradation of the tissue- ingrowth biodegradable region 12 can be relatively low and/or can be less than a rate of biodegradation of the adhesion-resistant biodegradable region 14.
• the tissue-ingrowth biodegradable region 12 can be formed, for example, with synthesized polymers that have hydrolytically stable linkages in the backbone relative to those of faster biodegrading polymers and/or to those of the adhesion-resistant biodegradable region 14.
• degradation can occur by either surface or bulk erosion. Surface erosion can occur when the rate of erosion exceeds the rate of water penetration into the bulk of the polymer of either the tissue- ingrowth biodegradable region 12 or the adhesion-resistant biodegradable region 14. This type of degradation can be obtained, for example, in oly(anhydrides) and poly(ortho esters).
• the hydrolysis of bulk degrading bioresorbable polymers as described herein may typically proceed by loss of molecular weight at first, followed by loss of mass in a second stage.
• hydrolysis is a preferred degradation mechanism for heterochain polymers in vivo.
• the degradation of poly( ⁇ -caprolactone) and related polyesters such as poly(lactide) and its copolymers first involves non-enzymatic hydrolysis of ester linkages, autocatalyzed by the generation of carboxylic acid end groups, followed by the loss of mass.
• lengthening of the in vivo elimination time of bioresorbable polymers can be determined by one or more of the nature of the polymer chemical linkage, the solubility of the degradation products, the size (e.g., thickness), shape and density of the region or prosthesis, the drug or additive content, the molecular weight of the polymer, the extent of cross-linking of the polymer, and the implantation site.
• the size and form of the region or prosthesis can be used to control at least one of biodegradation time and rate. For instance, a smaller surface to mass ratio can be implemented to retard the rate of biodegradation of the tissue-ingrowth biodegradable region 12.
• a relatively thick construction of the tissue-ingrowth biodegradable region 12 is believed to decelerate the absorption time or rate thereof, compared to times or rates of absorption of thinner prostheses of the same material.
• the tissue-ingrowth biodegradable region 12 of the present invention can have a uniform thickness greater than about 500 microns, or greater than about 1000 microns, and even greater than about 1500 or 3000 microns.
• a tissue-ingrowth biodegradable region 12 of a biodegradable surgical prosthesis 10 can be shaped at the time of surgery by bringing the material to its glass transition temperature, using heating iron, hot air, heated sponge or hot water bath methods.
• poly lactides which become somewhat rigid or brittle at greater thicknesses can be softened by formation with another polymer or copolymer, such as poly- ⁇ -caprolactone.
• the poly lactides may alternatively or additionally be combined with one or more non-biodegradable polymers, such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• one or more non-biodegradable polymers such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• tissue-ingrowth biodegradable regions 12 are formed by polymers (e.g., homo and/or copolymers) derived from one or more cyclic esters, such as lactide (i.e., L, D, DL, or combinations thereof), ⁇ -caprolactone, and glycolide
• compositions can comprise about 1 to 99% ⁇ -caprolactone, or 20 to 40% ⁇ -caprolactone, with the remainder of the polymer comprising a lactide such as poly(L-lactide).
• tissue-ingrowth regions 12 are formed by polymers (e.g., homo and/or copolymers) derived from one or more cyclic esters and/or other materials
• part or all of the tissue-ingrowth regions 12 can comprise or consist of one or more non- biodegradable polymers, such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• non- biodegradable polymers such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• softening polymers such as other lactones may be used with or as a substitute for ⁇ - caprolactone.
• one or more non-biodegradable polymers such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof, may be used with or as a substitute for ⁇ -caprolactone and/or other softening polymers or lactones.
• a preferred form of polymer for the tissue-ingrowth biodegradable region 12 is semicrystalline poly(L-lactide), which can have a degradation time in the order of 3 to 5 years, as compared to poly(DL-lactide) which degrades in 12 to 16 months.
• Polyhydroxyacids degrade to monomeric acids and subsequently to carbon dioxide and water. These are removed from the body via respiratory routes and the kidneys (the Krebs cycle).
• Included among the polyesters of interest are polymers of D-lactic acid, L- lactic acid, racemic lactic acid, glycolic acid, polycaprolactone, and copolymers/combinations thereof.
• part or all, in any combination, of the polymer (e.g., polyester) or polymers can comprise or consist of a non-biodegradable polymer, such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• a non-biodegradable polymer such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• a slowly biodegrading polymer can be achieved for the tissue-ingrowth biodegradable region 12, while for the adhesion-resistant biodegradable region 14 degradation may be substantially enhanced with a racemate.
• Copolymers of lactic and glycolic acid can be of particular interest, wherein the rate of biodegradation can be controlled by the ratio of glycolic to lactic acid.
• the degradation of lactic acid and/or glycolic acid polymers in biological medium occurs exclusively by a chemical mechanism of nonspecific hydrolysis. The products of this hydrolysis are metabolized and then eliminated by the human body. Chemical hydrolysis of the polymer is complete, whereby the more pronounced its amorphous character and the lower its molecular mass, the more rapidly it occurs.
• the tissue-ingrowth biodegradable region 12 may be formed, for example, using at least one polymer or copolymer having a less pronounced amorphous character and/or an increased molecular mass. Although the most rapidly degraded copolymer has roughly equal amounts of glycolic and lactic acid, either homopolymer is more resistant to degradation making it more suitable for formation of the tissue- ingrowth biodegradable region 12. Biodegradation rate or time thus may be decreased, for example, in the context of forming a tissue-ingrowth biodegradable region 12, by acting on the composition of the mixture and/or on the molecular mass of the polymer(s).
• the biocompatibility of the poly(lactide) and poly(lactide-co-glycolide) polymers makes them suitable supports for cellular growth and tissue regeneration in the context of the present invention. It should also be considered that, other things being equal, the ratio of glycolic acid to lactic acid may also affect the brittleness of the resulting biodegradable surgical prosthesis.
• the characteristic may be a strength, structural integrity, or a related parameter, wherein, for example, the effects of bulging, wrinkling and/or curling of the biodegradable surgical prosthesis 10 may be attenuated. Since the present invention seeks to allot a substantially greater proportion of the biodegradable surgical prosthesis' strength and structural integrity to the tissue-ingrowth biodegradable region 12, the focus of adding strength or structural integrity to the biodegradable surgical prosthesis 10 is directed on the tissue-ingrowth biodegradable region 12.
• Properties which may be adjusted in accordance with the present invention to augment the mechanical performance of the tissue-ingrowth biodegradable region 12 are monomer selection, polymerization and process conditions, and the presence of additives (e.g. fillers). These properties, in turn, can be adjusted so as to influence one or more of the hydrophilicity, crystallinity, melt and glass transition temperatures, molecular weight, molecular weight distribution, end groups, sequence distribution (random versus block), and the presence of residual monomer or additives in the tissue-ingrowth biodegradable region 12. Furthermore, a portion or all of these properties in combination then can influence the rate of biodegradation of the tissue-ingrowth biodegradable region 12.
• Lactide is the cyclic dimer of lactic acid, which exists in three stereoisomeric forms, L-lactide, naturally occurring isomer, D-lactide and meso-lactide, which contains an L-lactyl unit and a D-lactyl unit in the ring. Additionally, DL-lactide is an equimolar mixture of L- and D-lactides.
• the tissue-ingrowth biodegradable region 12 comprises poly(L-lactide), which has been found to exhibit high tensile strength and low elongation and consequently to have a high modulus, rendering it more suitable than many amorphous polymers for load-bearing applications such as hernia mending and sutures.
• Poly(L-lactide) has a melting point around 17O 0 C and glass transition temperature in the range of 55-6O 0 C.
• Poly(DL-lactide) is an amorphous polymer (Tg 45-55 0 C), having a random distribution of both isomeric forms of lactic acid and lacking the ability to arrange into a crystalline organized structure.
• Poly(DL-lactide) has a lower tensile strength, slightly higher elongation and substantially more rapid degradation time, making it more attractive for use in, for example, construction of the adhesion-resistant biodegradable region 14.
• Poly( ⁇ -caprolactone) is a ductile semicrystalline polymer, melting in the range of 54- 64°C. The glass transition temperature of -60 0 C can be increased by copolymerisation with lactide, which also may enhance the biodegradation of the polymer.
• one or more non-biodegradable polymers such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof, may be combined with the poly( ⁇ -caprolactone).
• the tissue-ingrowth biodegradable region 12 of a biodegradable surgical prosthesis 10 in accordance with an aspect of the present invention can be manufactured of biodegradable polymers by using one polymer or a polymer alloy.
• the biodegradable surgical prosthesis 10 can be strengthened by reinforcing the material with fibers manufactured from a resorbable polymer or of a polymer alloy, or with biodegradable glass fibers, such as ⁇ -tricalsiumphosphate fibers, bio-glass fibers or CaM fibers, as described in, e.g., publication EP146398, the entire disclosure of which is incorporated herein by reference.
• the surgical prosthesis 10 can be modified (e.g., strengthened) by including (e.g., for reinforcement) fibers or other elements manufactured from or with, in part or entirely, non-biodegradable polymers, such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• non-biodegradable polymers such as, for example, one or more of (a) various thermoplastic resins that are polymers of, for example, propylene, (b) polymethacrylate, (c) polymethylmethacrylate (PMMA), or (d) combinations thereof.
• the tissue- ingrowth biodegradable region 12 can further, or alternatively, comprise or consist of at least one outer layer, which is a surface layer that improves the toughness of the implant and/or operates as a hydrolysis barrier.
• an interior of the biodegradable surgical prosthesis 10 may additionally or alternatively comprise or consist of a stiffer and/or stronger layer or core.
• the biodegradable surgical prosthesis can be coated (e.g., brush, spray, bond, or dip coated) with an outer layer having different chemical and mechanical properties (e.g., hydrolysis and/or strength retention) than the core of the region or prosthesis.
• an outer layer having greater resistance to hydrolysis than the biodegradable surgical prostheses' strength-enhanced core can be used, enabling the prosthesis (after insertion in a patient) to retain its strength and biodegrade over a longer period of time than it would have without such an outer coating or enhanced interior.
• the characteristic may comprise an ability to facilitate a substantial fibroblastic reaction in the host tissue.
• the tissue-ingrowth biodegradable region 12 can be constructed to facilitate a fibroblastic reaction, while the adhesion-resistant biodegradable region 14 preferably does not cause a fibroblastic reaction.
• the facilitation by the tissue-ingrowth biodegradable region 12 of a fibroblastic reaction can be based on one or more of the above-discussed characteristics (e.g., time or rate of biodegradation affected by additives, time or rate of biodegradation affected by polymer structures/compositions, and polymer composition affecting strength or structural integrity), since the biodegradable surgical prosthesis 10 will need to maintain its structure long enough for reacting tissues to take a firm hold.
• the tissue-ingrowth biodegradable region 12 of the present invention can comprise or consist of at least one outer layer, which is a tissue ingrowth promoter.
• all or substantially all of the biodegradable surgical prosthesis IU, except for the adhesion-resistant biodegradable region 14, comprises a tissue ingrowth promoter.
• the biodegradable surgical implant 10 When applied to a roughened tissue-ingrowth biodegradable region 12 comprising, for example, at least one of protuberances, alveoli and pores, the biodegradable surgical implant 10 can provide interstitial space for the host body tissue to enter by ingrowth. Tissue ingrowth promoters can render the interstitial space conducive to the ingrowth therein of body tissue by providing chemically and/or physically improved surface characteristics.
• the tissue-ingrowth biodegradable region 12 may comprises a substance for cellular control, such as at least one of a chemotactic substance for influencing cell migration, an inhibitory substance for influencing cell-migration, a mitogenic growth factor for influencing cell proliferation, a growth factor for influencing cell differentiation, and factors which promote neoangiogenesis (formation of new blood vessels).
• a substance for cellular control such as at least one of a chemotactic substance for influencing cell migration, an inhibitory substance for influencing cell-migration, a mitogenic growth factor for influencing cell proliferation, a growth factor for influencing cell differentiation, and factors which promote neoangiogenesis (formation of new blood vessels).
• one or several growth promoting factors can be introduced into or onto the tissue-ingrowth biodegradable region 12, such as fibroblast growth factor, epidermal growth factor, platelet derived growth factor, macrophage derived growth factor, alveolar derived growth factor, monocyte derived growth factor, magainin, and so forth.
• one or more medico-surgically useful substances may be incorporated into or onto the tissue-ingrowth biodegradable region 12, such as those which accelerate or beneficially modify a growth or healing process.
• the tissue-ingrowth biodegradable region 12 can carry (e.g., via mixing during formation, implanting, or coating) one or more therapeutic agents chosen for one or more of antimicrobial properties, capabilities for promoting repair or reconstruction and/or new tissue growth and/or for specific indications.
• Antimicrobial agents such as broad spectrum antibiotics (gentamicin sulphate, erythromycin or derivatized glycopeptides) can be carried (e.g., via mixing during formation, implanting or coating) to aid in combating clinical and sub-clinical infections in a tissue repair site thus facilitating ingrowth of host tissues onto and/or into the tissue- ingrowth biodegradable region 12.
• broad spectrum antibiotics gentamicin sulphate, erythromycin or derivatized glycopeptides
• one or more of the above additives may be incorporated into the polymer of the tissue-ingrowth biodegradable region 12 itself prior to forming the tissue-ingrowth biodegradable region 12 as part of the biodegradable surgical prosthesis 10, for example, by addition to the polymer in suitable amounts so that at the conclusion of the polymeric particle manufacturing process, the material of the tissue-ingrowth biodegradable region 12 will contain a predetermined amount of one or more of such substances which for example will be released gradually as the polymer is biodegraded.
• the biodegradable surgical prosthesis 10 can be used to facilitate repair of, for example, a hernia in the ventral region of a body.
• FIG. 3 shows an implanted biodegradable surgical prosthesis 10 having both an adhesion-resistant biodegradable region 14 and a tissue- ingrowth biodegradable region 12 partially disposed on one side and having a tissue- ingrowth biodegradable region 12 disposed on a second side of the biodegradable surgical prosthesis 10.
• the abdominal wall includes muscle 15 enclosed and held in place by an exterior fascia 16 and an interior fascia 19.
• An interior layer, called the peritoneum 22, covers the interior side of the interior fascia 19.
• the peritoneum 22 is a softer, more pliable layer of tissue that forms a sack-like enclosure for the intestines and other internal viscera.
• a layer of skin 25 and a layer of subcutaneous fat 28 cover the exterior fascia 16.
• Surgical repair of a soft tissue defect can be performed by using, for example, conventional techniques or advanced laparoscopic methods to close substantially all of a soft tissue defect.
• an incision can be made through the skin 25 and subcutaneous fat 28, after which the skin 25 and fat 28 can be peeled back followed by any protruding internal viscera (not shown) being positioned internal to the hernia.
• an incision can be made in the peritoneum 22 followed by insertion of the biodegradable surgical prosthesis 10 into the hernia opening so that the biodegradable surgical prosthesis 10 is centrally located in the hernia opening.
• tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may be attached by, e.g., suturing to the same layer of the abdominal wall, e.g., the relatively-strong exterior fascia 16.
• the adhesion-resistant biodegradable region 14 may be attached to another member, such as the interior fascia 19 and/or the peritoneum 22. In FIG.
• the tissue-ingrowth biodegradable region 12 is surgically attached to the exterior fascia 16 while the adhesion-resistant biodegradable region is attached to the tissue-ingrowth biodegradable region 12 and/or optionally to the exterior fascia 16 using, e.g., heat bonding, suturing, and/or other affixation protocols disclosed herein or their substantial equivalents.
• heat bonding suturing, and/or other affixation protocols disclosed herein or their substantial equivalents.
• the size of the biodegradable surgical prosthesis 10 typically will be determined by the size of the defect. Use of the biodegradable surgical prosthesis 10 in a tension- free closure may be associated with less pain and less incidence of post surgical fluid accumulation.
• Exemplary sutures 31 and 34 may be implemented as shown to at least partially secure the biodegradable surgical prosthesis to the abdominal wall structure. The sutures 31 and 34 can be preferably implemented so that no lateral tension is exerted on the exterior fascia 16 and/or muscle 15. When disrupted, the skin 25 and fat 28 may be returned to their normal positions, with for example the incisional edges of the skin 25 and fat 28 being secured to one another using suitable means such as subsurface sutures.
• one or both of the tissue- ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 of the biodegradable surgical prosthesis 10 can be heat bonded (or in a modified embodiment, otherwise attached, such as by suturing). Heat bonding may be achieved, for example, with a bipolar electro-cautery device, ultrasonicly welding, or similar sealing between the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 and/or directly to surrounding tissues. Such a device can be used to heat the biodegradable surgical prosthesis 10 at various locations, such as at edges and/or at points in the middle, at least above its glass transition temperature, and preferably above its softening point temperature.
• the material is heated, e.g., along with adjacent tissue, such that the two components bond together at their interface.
• the heat bonding may also be used initially, for example, to secure the tissue-ingrowth biodegradable region 12 to the adhesion-resistant biodegradable region 14. Since the tissue-ingrowth biodegradable region 12 serves more of a load-bearing function, a tew typical embodiments may exclude heat-bonding as the sole means for securing this region to host tissues.
• the technique of heat bonding the biodegradable surgical prosthesis 10 to itself or body tissue may be combined with another attachment method for enhanced anchoring.
• the biodegradable surgical prosthesis 10 may be temporarily affixed in position using two or more points of heat bonding using an electro-cautery device, and sutures, staples or glue can subsequently (or in other embodiments, alternatively) be added to secure the biodegradable surgical prosthesis 10 into place.
• tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may be arranged to form more than one layer or substantially one layer, or the regions may both belong to a single, integrally formed layer.
• tissue-ingrowth biodegradable region 12 and the opposing adhesion- resistant biodegradable region 14 may be arranged in two layers, wherein one of the regions is disposed on top of, and opposite to, the other region.
• tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may be combined on a single side of the biodegradable surgical prosthesis 10 in, for example, substantially one layer, wherein the regions are adjacent each other on one side of the biodegradable surgical prosthesis 10.
• a biodegradable surgical prosthesis having a tissue-ingrowth biodegradable region on at least one (and preferably, both) side(s) thereof may be manufactured using any of the techniques described herein and, subsequently, an adhesion-resistant biodegradable region may be formed on, e.g., one side, by smoothing, filling, or otherwise processing an area of the tissue-ingrowth biodegradable region with a suitable material as disclosed herein or technique (e.g., coating or filling with a liquid or flowable polymer composition, and/or mechanically smoothing) to thereby form an adhesion-resistant biodegradable region having adhesion-resistant properties relative to those of the tissue-ingrowth biodegradable region.
• a suitable material e.g., coating or filling with a liquid or flowable polymer composition, and/or mechanically smoothing
• a patch of adhesion-resistant biodegradable region 14 may be sized and affixed (e.g., heat bonded, such as with a bipolar electro ⁇ cautery device, ultrasonicly welded, or similarly affixed) at a time of implantation directly to at least one of the tissue-ingrowth biodegradable region 12 and surrounding host tissues.
• the affixing may be accomplished using, for example, press or adhesive bonding, or sutures.
• at least part of the affixing may occur at a time of manufacture of the biodegradable surgical prosthesis 10 before packaging.
• the patch of adhesion-resistant biodegradable region 14 alternatively may be partially affixed (e.g., using techniques enumerated in this paragraph) at, for example, a non-perimeter or central area thereof to an area (e.g., a non- perimeter or central area) of the tissue-ingrowth biodegradable region 12, so that a surgeon can trim the adhesion-resistant biodegradable region 14 (and/or the tissue- ingrowth biodegradable region 12) at a time of implantation while the adhesion-resistant biodegradable implant 14 is affixed to the tissue-ingrowth biodegradable region 12.
• a tissue-ingrowth biodegradable region 12 may substantially surround an adhesion-resistant biodegradable region 14 on one side of the biodegradable surgical prosthesis 10, and only a tissue-ingrowth biodegradable region 12 may be formed on the other side of the biodegradable surgical prosthesis 10.
• the adhesion-resistant biodegradable region 14 of the biodegradable surgical prosthesis 10 can be sized and shaped so as to substantially cover any opening created by the soft tissue defect, with the tissue-ingrowth biodegradable regions 12 facilitating surgical attachment to, and incorporation into, the host tissue on at least one side of, and, preferably, on both sides of, the biodegradable surgical prosthesis 10.
• the tissue-ingrowth biodegradable region 12 and/or the adhesion-resistant biodegradable region 14 on a given surface or surfaces of the biodegradable surgical prosthesis 10 each may be of any size or shape suited to fit the particular soft tissue defect.
• either of the tissue-ingrowth biodegradable region 12 and/or the adhesion-resistant biodegradable region 14 on a given surface of the biodegradable surgical prosthesis 10 may have shapes of ovals, rectangles and various complex or other shapes wherein, for each such implementation, the two regions may have essentially the same, or different, proportions and/or dimensions relative to one another.
• tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may be employed to produce the biodegradable surgical prosthesis 10, which typically has one or two layers defining the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14.
• Useful techniques include solvent evaporation methods, phase separation methods, interfacial methods, extrusion methods, molding methods, injection molding methods, heat press methods and the like as known to those skilled in the art.
• the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may comprise two distinct layers or may be integrally formed together as one layer.
• An exemplary process for making a biodegradable surgical prosthesis of the present invention having an adhesion-resistant biodegradable region, and a tissue- ingrowth biodegradable region with an additive includes the steps of (a) forming a polymer layer to define the anti-adhesion biodegradable region such as described in U.S. Patent No. 6,673,362; (b) providing a water hydrolysable polymer; (c) forming the hydrolysable polymer into an implantable solid portion; and (d) attaching the polymer layer to the implantable solid portion whereby the solid portion defines a tissue-ingrowth biodegradable region.
• the step of forming the hydrolysable polymer into an implantable solid portion can comprise adding a retardant to the hydrolysable polymer to form a mixture, followed by forming a layer from the mixture and subsequently drying and purifying the layer to form the implantable solid portion.
• the tissue-ingrowth biodegradable region 12 and the adhesion-resistant biodegradable region 14 may be partially or substantially entirely formed or joined together. Joining can be achieved by mechanical methods, such as by suturing or by the use of metal clips, for example, hemoclips, or by other methods, such as chemical or heat bonding.

Landscapes

• Health & Medical Sciences (AREA)
• Animal Behavior & Ethology (AREA)
• Life Sciences & Earth Sciences (AREA)
• Veterinary Medicine (AREA)
• Engineering & Computer Science (AREA)
• Biomedical Technology (AREA)
• Heart & Thoracic Surgery (AREA)
• Vascular Medicine (AREA)
• Public Health (AREA)
• General Health & Medical Sciences (AREA)
• Cardiology (AREA)
• Oral & Maxillofacial Surgery (AREA)
• Transplantation (AREA)
• Materials For Medical Uses (AREA)
• Prostheses (AREA)

Priority Applications (12)

Applications Claiming Priority (4)

Publications (2)

Family

ID=35908205

Family Applications (1)

Country Status (12)

Cited By (23)

Families Citing this family (42)

Family Cites Families (76)

• 2005
  • 2005-08-12 ES ES05786506T patent/ES2395154T3/es not_active Expired - Lifetime
  • 2005-08-12 WO PCT/US2005/028834 patent/WO2006020922A2/en not_active Ceased
  • 2005-08-12 MX MX2007001628A patent/MX2007001628A/es active IP Right Grant
  • 2005-08-12 CN CN2005800274829A patent/CN101018512B/zh not_active Expired - Fee Related
  • 2005-08-12 EP EP05786506A patent/EP1776065B1/en not_active Expired - Lifetime
  • 2005-08-12 AT AT05786506T patent/ATE545384T1/de active
  • 2005-08-12 JP JP2007525850A patent/JP4906723B2/ja not_active Expired - Fee Related
  • 2005-08-12 KR KR1020077003292A patent/KR100895135B1/ko not_active Expired - Fee Related
  • 2005-08-12 CA CA2573564A patent/CA2573564C/en not_active Expired - Fee Related
  • 2005-08-12 AU AU2005272684A patent/AU2005272684B2/en not_active Ceased
• 2007
  • 2007-02-11 IL IL181264A patent/IL181264A0/en unknown
  • 2007-12-05 US US11/951,049 patent/US20080091222A1/en not_active Abandoned
  • 2007-12-05 US US11/951,027 patent/US20080091276A1/en not_active Abandoned
• 2009
  • 2009-03-02 AU AU2009200816A patent/AU2009200816B2/en not_active Ceased
• 2011
  • 2011-05-12 AU AU2011202203A patent/AU2011202203B2/en not_active Expired - Fee Related

Non-Patent Citations (1)

Also Published As

Similar Documents

Legal Events