CA2180063A1 - High strength, fast absorbing, melt processable, glycolide-rich, poly(glycolide-co-p-dioxanone) copolymers - Google Patents
High strength, fast absorbing, melt processable, glycolide-rich, poly(glycolide-co-p-dioxanone) copolymersInfo
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- CA2180063A1 CA2180063A1 CA002180063A CA2180063A CA2180063A1 CA 2180063 A1 CA2180063 A1 CA 2180063A1 CA 002180063 A CA002180063 A CA 002180063A CA 2180063 A CA2180063 A CA 2180063A CA 2180063 A1 CA2180063 A1 CA 2180063A1
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- Prior art keywords
- mole percent
- dioxanone
- glycolide
- repeating units
- segmented copolymer
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Classifications
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G63/00—Macromolecular compounds obtained by reactions forming a carboxylic ester link in the main chain of the macromolecule
- C08G63/78—Preparation processes
- C08G63/82—Preparation processes characterised by the catalyst used
- C08G63/823—Preparation processes characterised by the catalyst used for the preparation of polylactones or polylactides
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
- A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
- A61L15/22—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons containing macromolecular materials
- A61L15/26—Macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds; Derivatives thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
- A61L17/06—At least partially resorbable materials
- A61L17/10—At least partially resorbable materials containing macromolecular materials
- A61L17/12—Homopolymers or copolymers of glycolic acid or lactic acid
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/04—Macromolecular materials
- A61L31/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G63/00—Macromolecular compounds obtained by reactions forming a carboxylic ester link in the main chain of the macromolecule
- C08G63/66—Polyesters containing oxygen in the form of ether groups
- C08G63/664—Polyesters containing oxygen in the form of ether groups derived from hydroxy carboxylic acids
Abstract
Absorbable, segmented copolymers of aliphatic polyesters based on lactone monomers glycolide, and p-dioxanone are described. The segmented copolymers exhibit a broad range of properties, especially high strength and stiffness, and fast absorption rates and breaking strength retention (BSR) profiles, useful in a variety of medical devices. Most importantly, for suture applications where Vicryl?-like polyglcolide-polylactide sutures with excellent tensile properties, but shorter BSR profiles than Vicryl? are needed. The copolymers of the present invention have such properties, making them useful in plastic surgery where faster absorption times would lead to less tissue scarring.
Description
~ 1 80063 HIGH 8~RENGTH, FA8T ABQORBING, MELT PROCE88ABLE, GLYCOLIDE-RICH, POLY(GLYCOLIDE-CO-p-DIOXANONB) Technical Field The field of art to which this invention relates is polymers, more specifically, biocompatible, absorbable copolymers; in particular, segmented copolymers of aliphatic polyesters of glycolide, and p-dioxanone.
~ac~qround of the Invention Polymers! including homopolymers and copolymers, which are both biocompatible and absorbable in vivo are known in the art. Such polymers are typically used to manufacture medical devices which are implanted in body tissue and absorb over time. Examples of medical devices manufactured from these absorbable biocompatible polymers include suture anchor devices, sutures, staples, surgical tacks, clips, plates and screws, etc.
Absorbable, biocompatible polymers useful for manufacturing medical devices include both natural and synthetic polymers. Natural polymers include cat gut, cellulose derivatives, collagen, etc. Synthetic polymers may consist of various aliphatic polyesters, polyanhydrides, poly(orthoester)s, and the like.
Natural polymers typically absorb by an enzymatic degradation process in the body, while synthetic absorbable polymers generally degrade primarily by a hydrolytic mechanism.
Synthetic absorbable polymers which are typically used 5 to manufacture medical devices include homopolymers such as poly(glycolide), poly(lactide), poly(e-caprolactone), and poly(p-dioxanone) and copolymers such as poly(lactide-co-glycolide), poly(e-caprolactone-co-glycolide), and poly(glycolide-co-trimethylene carbonate). The polymers may be statistically random copolymers, segmented copolymers, block copolymers, or graft copolymers. It is also known that both homopolymers and copolymers can be used to prepare blends.
U.S. Patents 4,653,497, 4,838,267, 5,080,665 describe several biocompatible, absorbable, poly(p-dioxanone-co-glycolide) copolymers useful as biomedical devices.
U.S. Patents 4,838,267 and 5,080,665 additionally 20 describe poly(p-dioxanone-co-glycolide) block or graft copolymers.
Furthermore, U.S. Patent 4,838,267 describes (See FIGS.
1 and 2) the preparation of poly(p-dioxanone-b-25 glycolide) block copolymers by a two-step, two-reaction vessel process in which preformed, high molecular weight poly(p-dioxanone), that is substantially free of p-dioxanone monomer, is reacted with glycolide monomer at temperatures from about 140C to about 240C to yield block copolymers of the (A-B)n type where A is a long block of repeating units of p-dioxanone (i.e., the homopolymer of poly(p-dioxanone)) and B is a long block of repeating units of glycolide (i.e., the homopolymer of poly(glycolide)). The repeating unit structure as well as a schematic representation of the block copolymer structure are shown in Figures 1 and 2. These copolymers are highly crystalline, due to their blocky structure, yielding materials with long breaking strength retention profiles (BSR), high strength and relatively high stiffness. It should be noted that breaking strength retention is a conventionally known standard method of measuring the strength of a device made of a bioabsorbable polymer, as a function of time under biological conditions in vitro or as a function of time after being implanted in vivo.
Additionally, U.S. Patent 5,080,665 describes block or graft copolymers of poly(p-dioxanone-co-glycolide) prepared by a process in which the p-dioxanone monomer is reacted initially for a certain period of time, typically one hour at about 180C, followed by reaction with glycolide at about 200C. This process leads to block or graft copolymers which are useful due to their formation of a "hard" phase formed from the glycolide repeating unit blocks, and a "soft" phase formed from the p-dioxanone repeating unit blocks as illustrated in FIGS. 3 and 4.
Furthermore, U.S. Patent 4,653,497 describes poly(p-dioxanone)-rich segmented copolymers comprising about 70 weight percent to about 97 weight percent polymerized p-dioxanone with the remaining small portion of the copolymer polymerized with glycolide as illustrated in FIGS. 5 and 6.
Although the above described copolymers yield-materials with excellent properties such as high strength and stiffness and long BSR profiles as found with the block copolymers, or good strength, long elongations, low stiffness and shorter BSR profiles as found for the poly(p-dioxanone)-rich segmented copolymers, there is a need in this art for new copolymer compositions having characteristics of both the block copolymers and the segmented copolymers.
Accordingly, what is needed in this art are novel copolymer compositions which have the block copolymer characteristics of high strength and stiffness, and the segmented copolymer characteristics of shorter BSR
profiles and absorptions rates.
In certain biomedical applications there is a strong need for these requirements, including sutures with strong tensile properties, like those of Vicryl~ or Dexon~, but shorter BSR profiles and absorption rates.
In addition, it would be highly desirable to have such polymers having little or no unreacted monomers present, since it is believed that the presence of certain levels of unreacted monomers can lead to problems such as adverse tissue reaction.
Disclo~ure of the Invention Surprisingly, it has been discovered that by preparing copolymers of poly(glycolide-co-p-dioxanone) rich in glycolide by a process in which a small proportion of p-dioxanone monomer is reacted at low temperatures from about 100C to about 130C follo~wed by reaction with glycolide at higher temperatures of about 180C to about 2! 80063 220C, segmented glycolide-rich copolymers with small proportions of p-dioxanone can be formed that have high strength and stiffness, but short BSR profiles and fast absorption rates, making them useful in a variety of biomedical devices such as suture anchor devices, staples, surgical tacks, clips, plates and screws. The copolymers of the present invention are especially useful for suture applications where Vicryl0-like sutures with excellent tensile properties but shorter BSR profiles than Vicryl0 are needed. The copolymers of the present invention are, therefore, useful in plastic surgical applications, where faster absorption times tend to result in less tissue scarring. That is, for example, an absorbable suture which rapidly loses strength in the sections which have been implanted beneath a patient's skin can be more easily removed, by use of antitension skin tape, without the pain, discomfort and scarring typically suffered by patients who have had conventional sutures implantPd.
Accordingly, novel, absorbable, biocompatible, poly(glycolide-co-p-dioxanone) segmented copolymers are disclosed. The copolymers have a major component comprising about 30 mole percent to about 95 mole percent of repeatinq units of glycolide, and a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
Yet another aspect of the present invention is a biomedical device made from the above described copolymers, especially implantable devices such as suture anchor devices, staples, surgical tacks, clips, plates and screws, and most especially for suture applications where Vicryl0 or Dexon0-like sutures with excellent tensile properties, but shorter BSR profiles than Vicryl~ or Dexon~ are needed for plastic surgery.
An additional aspect of the present invention is a process for producing the segmented copolymers of the present invention. The initial step of the process is to polymerize p-dioxanone in the presence of a catalytically effective amount of catalyst and an initiator at a sufficient temperature and for a sufficient period of time to effectively yield a first mixture of p-dioxanone monomer and p-dioxanone homopolymer. Then, glycolide is added to the first mixture to form a second mixture. Next, the second mixture is polymerized at a sufficient temperature and for a sufficient amount of time to effectively produce a segmented copolymer comprising a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide and a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
Still yet a further aspect of the present invention is the copolymer of the present invention which is a product of the process of the present invention.
The foregoing and other features and advantages of the invention will become more apparent from the following description and accompanying examples.
Brief Description of the Drawings FIG. 1 illustrates a synthetic process for the preparation of poly(p-dioxanone-b-glycolide) block copolymers as described in U.S. Patent 4,838,267.
FIG. 2 illustrates a schematic representation of poly(p-dioxanone-b-glycolideJ block copolymers as described in U.S. Patent 4,~38,267.
5 FIG. 3 illustrates a synthetic process for the preparation of poly(p-dioxanone-co-glycolide) block or graft copolymers as described in U.S. Patent 5,080,665.
FIG. 4 illustrates a schematic representation of poly(p-10 dioxanone-co-glycolide) block or graft copolymers as described in U.S. Patent 5,080,665.
FIG. 5 illustrates a synthetic process for the preparation of poly(p-dioxanone)-rich, poly(p-dioxanone-15 co-glycolide) segmented copolymers as described in U.S.
Patent 4,653,497.
FIG. 6 illustrates a schematic representation of poly(p-dioxanone)-rich, poly(p-dioxanone-co-glycolide) 20 segmented copolymers as described in U.S. Patent 4,653,497.
FIG. 7 illustrates a synthetic process for the preparation of the glycolide-rich, poly(glycolide-co-p-25 dioxanone) segmented copolymers of the presentinventlon .
FIG. 8 illustrates a schematic representation of the glycolide-rich, poly(glycolide-co-p-dioxanone) segmented 30 copolymers of the present invention.
FIG. 9 is a graph presenting BSR profiles of size 4-0 fibers (sutures) of Vicryl (90:10 (mol/mol) poly(glycolide-co-lactide)) or Dexon (poly(glycolide)), size 4-0 fibers of poly(p-dioxanone), size 5-0 fibers of a segmented copolymer of U.S. patent 4,653,497, and size 5-0 fibers of a 80:20 (mol/mol) segmented poly(glycolide-co-p-dioxanone) copolymer of the present invention.
FIG. 10 shows the compositional differences between the segmented poly(glycolide-co-p-dioxanone) copolymers of the present invention and the copolymers disclosed in U.S. Patents 4,653,497, 4,838,267 and 5,080,665.
FIG. 11 displays the property differences between the segmented poly(glycolide-co-p-dioxanone) copolymers of the present invention and U.S. Patents 4,653,497, 4,838,267 and 5,080,665, based upon differences in composition and structure.
Description of the Preferred Embodiments The process of the present invention is a one-step, one-reaction vessel, two-temperature process in which a mixture of p-dioxanone monomer and p-dioxanone homopolymer is initially formed at low temperatures of from about 100C to about 130C, preferably 110C. The mixture is then reacted with glycolide at temperatures from about 120C to about 220C to form copolymers in which segments or sequences are composed of both p-dioxanone and glycolate moieties as illustrated in FIGS.
7 and 8. These segmented copolymers are substantially less crystalline than the block or graft copolymers of the prior art and, therefore, yield materials with good strength, but shorter BSR profiles, faster absorption rates, longer elongations and lower stiffness.
More specifically, the poly(glycolide-co-p-dioxanone) segmented copolymers of the present invention are prepared by a process in which p-dioxanone monomer is reacted in a conventional reactor vessel at low temperatures from about 100C to about 130C, preferably about 110C, for a sufficient time effective to cause polymerization, preferably about 4 hours to about 8 hours, followed by reaction with glycolide at higher temperatures of about 180C to about 220C for a sufficient time effective to cause copolymerization, preferably about 1 hour to about 4 hours.
Furthermore, the segmented poly(glycolide-co-p-dioxanone) copolymers will typically consist of about 30 mole percent to about 95 mole percent of glycolate moieties, more preferably about 30 mole percent to about 90 mole percent of glycolate moieties, and most preferably about 30 mole percent to about 50 mole percent of glycolate moieties.
The aliphatic segmented copolyesters useful in the preparation of the segmented copolymers of the present invention will typically be synthesized in a ring opening polymerization. That is, the aliphatic lactone 2S monomers are polymerized in the presence of an organometallic catalyst and an initiator at elevated temperatures. The organometallic catalyst is preferably tin based, e.g., stannous octoate, and is present in the monomer mixture at a molar ratio of monomer to catalyst ranging from about lO,OOo/1 to about lOO,OoO/1. The initiator is typically an alkanol, a glycol, a hydroxyacid, or an amine, and is present in the monomer mixture at a molar ratio of monomer to initiator ranging from about 100/1 to about 5000/1. The polymerization is typically carried out at a temperature range from about 80C to about 240C, preferably from about 100C to about 220C, until the desired molecular weight and viscosity are achieved.
Suitable lactone monomers may be selected from the group consisting of glycolide, lactide (l, d, dl, meso), p-dioxanone, delta-valerolactone, beta-butyrolactone, epsilon-decalactone, 2,5-diketomorpholine, pivalolactone, alpha, alpha-diethylpropiolactone, ethylene carbonate, ethylene oxalate, 3-methyl-1,4-dioxane-2,5-dione, 3,3-diethyl-1,4-dioxan-2,5-dione, gamma-butyrolactone, 1,4-dioxepan-2-one, 1,5-dioxepan-2-one, 1,4-dioxan-2-one, 6,8-dioxabicycloctane-7-one and combinations of two or more thereof. Preferred lactone monomers are selected from the group consisting of glycolide, and p-dioxanone.
More specifically, the segmented copolymers of poly(glycolide-co-p-dioxanone) useful in the practice of the present invention will typically be synthesized by a process in which p-dioxanone is polymerized in a ring opening polymerization in the presence of an organometallic catalyst and an initiator at elevated temperatures. The organometallic catalyst is preferably tin based, e.g., stannous octoate, and is present in the mixture at a molar ratio of monomer to catalyst ranging from about 10,000/1 to about lO0,000/1. The initiator is typically an alkanol, a glycol, a hydroxyacid, or an amine, and is present in the monomer mixture at a molar ratio of monomer to initiator ranging from about loO/l to about 5000/1.
The polymerization is typically carried out ~n a conventional reactor vessel at a temperature range from about 100C to about 130C, preferably 110C, for about 4 hours to about 8 hours, preferably about 5 hours to about 6 hours, yielding a mixture of p-dioxanone monomer and homopolymer. Then, glycolide monomer is added to the mixture of p-dioxanone monomer and homopolymer and the temperature is raised to about 180C to about 220C, preferably from about 190C to about 220C until the desired molecular weight and viscosity are achieved. It should be understood that pure monomers and dry conditions are utilized to achieve such molecular weights.
Under the above described conditions, the segmented copolymers of poly(glycolide-co-p-dioxanone), will typically have a weight average molecular weight of about 20,000 grams per mole to about 300,000 grams per mole, more typically about 40,000 grams per mole to about 200,000 grams per mole, and preferably about 60,000 grams per mole to about 150,000 grams per mole.
These molecular weights provide an inherent viscosity between about 0.5 to about 4.0 deciliters per gram (dL/g), more typically 0.7 to about 3.5 dL/g, and most preferably 1.0 to about 3.0 dL/g as measured in a 0.1 g/dL solution of hexafluoroisopropanol (HFIP) at 25C.
Also, it should be noted that under the above described conditions, the residual monomer content will be less than about 5 wt. %.
The segmented copolymers of poly(glycolide-co-p-dioxanone) will typically consists of about 30 mole percent to about 95 mole percent, more preferably about 30 mole percent to about 90 mole percent of glycolate 2 i 80063 moieties, and most preferably about 30 mole percent to about 50 mole percent of glycolate moieties. The lower limit of glycolate moieties in the copolymers is desirable because the addition of 30 mole percent leads to copolymers which have longer BSR profiles, but lower strength. The upper limit of glycolate moieties in the copolymers is desirable because the addition of 95 mole percent leads to copolymers which have shorter BSR
profiles, but higher strength and stiffness. This leads to copolymers with a desirable range of strength, stiffness and absorption profiles for use in a variety of biomedical applications. One skilled in the art will appreciate that the number of moles of glycolate moieties and p-dioxanone moieties in the copolymer are equivalent to the number of moles of glycolide and p-dioxanone monomers needed to be added to the reaction to form the copolymer.
Articles such as medical devices are molded from the segmented copolymers of the present invention by use of various conventional injection and extrusion molding equipment at temperatures ranging from about 160C to about 220C, more preferably 180C to about 220C, with residence times of about 2 to about 10 minutes, more preferably about 2 to about 5 minutes.
The segmented copolymers of the present invention can be melt processed by numerous methods to prepare a vast array of useful devices. These materials can be injection or compression molded to make implantable medical and surgical devices, including wound closure devices. The preferred devices are suture anchor devices, staples, surgical tacks, clips, plates and screws.
Copolymers of the present invention with low levels of p-dioxanone have particular utility in the preparation of absorbable surgical devices that must be stiff and simultaneously tough. Of particular utility are those compostions having p-dioxanone at about 5 to about 30 mole percent.
Alternatively, the segmented copolymers can be extruded to prepare fibers. The filaments thus produced may be fabricated into sutures or ligatures, attached to surgical needles, packaged, and sterilized by known techniques. The materials of the present invention may be spun as multifilament yarn and woven or knitted to form sponges or gauze, (or non-woven sheets may be prepared) or used in conjunction with other molded compressive structures such as prosthetic devices within the body of a human or animal where it is desirable that the structure have high tensile strength and desirable levels of compliance and/or ductility. Useful embodiments include tubes, including branched tubes, for 2S artery, vein or intestinal repair, nerve splicing, tendon splicing, sheets for tying up and supporting damaged surface abrasions, particularly major abrasions, or areas where the skin and underlying tissues are damaged or surgically removed. Especially, sutures with Vicryl~-like tensile properties but shorter BSR profiles than Vicryl2 are needed, useful in plastic surgical applications where faster absorption times would lead to less ti-ssue scarring. That is, a suture which rapidly loses strength in the portion which is implanted beneath the skin can be more easily removed, by use of antitension skin tape, without the pain, discomfort and scarring typically suffered by patients who have had conventional sutures implanted. Vicryl~ is a trademark for sutres made from polyglycolide-polylactide (90-10) copolymers.
Additionally, the segmented copolymers of the present invention can be molded to form films which, when sterilized, could be useful as adhesion prevention barriers. Another alternative processing technique for the copolymers of the present invention includes solvent casting, particularly for those applications where a drug delivery matrix is desired.
Furthermore, the segmented copolymers of the present invention can be processed by conventional techniques to form foams, which are useful as hemostatic barriers and bone substitutes.
In more detail, the surgical and medical uses of the filaments, films, foams and molded articles of the present invention include, but are not necessarily limited to knitted products, woven or non-woven, and molded products including:
a. burn dressings b. hernia patches c. medicated dressings d. fascial substitutes e. gauze, fabric, sheet, felt or sponge for liver hemostasis f. gauze bandages g. arterial graft or substitutes h. bandages for skin surfaces i. burn dressings j. orthopedic pins, clamps, screws, and plates k. clips 1. staples m. hooks, buttons, and snaps n. bone substitutes o. needles p. intrauterine devices q. draining or testing tubes or capillaries r. surgical instruments s. vascular implants or supports t. vertebral discs u. extracorporeal tubing for kidney and heart-lung machines v. artificial skin and others w. stents x. suture anchors y. injectable defect fillers z. preformed defect fillers al. tissue adhesives and sealants b2. bone waxes c3. cartilage replacements d4. hemostatic barriers Examples The following examples are illustrative of the principles and practice of this invention, although not limited thereto. Numerous additional embodiments within the scope and spirit of the invention will become apparent to those skilled in the art. The examples describe new segmented copolymers of poly(glycolide-co-.
p-dioxanone), said copolymers being useful as biomedical devices.
In the synthetic process, the high molecular weight aliphatic segmented copolyesters are prepared by a method consisting of reacting p-dioxanone via a ring opening polymerization in a conventional reactor vessel at temperatures of about 100C to about 130C for about 4 hours to about 8 hours under an inert nitrogen atmosphere, followed by reaction with glycolide at temperatures of 180C to 220C until the desired molecular weight and viscosity are achieved.
In the examples which follow, the segmented copolymers and monomers were characterized for chemical composition and purity (NMR, FT-IR), thermal analysis (DSC), melt rheology (melt stability and viscosity), and molecular weight (inherent viscosity), and baseline and in vitro mechanical properties (Instron stress/strain).
IH NMR was performed on a 300 MHz NMR using CDC13 or HFAD
as a reference. Thermal analysis of segmented copolymers and monomers was performed on a Dupont 912 Differential Scanning Calorimeter (DSC) at a heating rate of 10C/min.
A Fisher-Johns melting point apparatus was also utilized to determine melting points of monomers. Thermal gravimetric analysis was performed on a Dupont 951 TGA
at a rate of 10C/min. under a nitrogen atmosphere.
Isothermal melt stability of the segmented copolymers was also determined by a Rheometrics Dynamic Analyzer RDA II for a period of 1 hour at temperatures ranging from 160C to 230C under a nitrogen atmosphere.
Inherent viscosities (I.V., dL/g) of the segmented copolymers were measured using a 50 bore Cannon-Ubbelhode dilution viscometer immersed in a thermostatically controlled water bath at 25C utilizing chloroform or hexafluoroisopropanol (HFIP) as the solvent at a concentration of 0.1 g/dL.
Melt viscosity was determined utilizing a Rheometrics Dynamic Analyzer RDA II at temperatures ranging from 160C to 230C at rate of 1C/min. to 10C/min. at frequencies of ls-l to 100sl under a nitrogen atmosphere.
Fibers of copolymers of the present invention were prepared by a method as described in U.S. Patent 4,643,191, which is incorporated herein by reference.
The copolymers were melt extruded in a conventional manner using an INSTRON3 capillary rheometer or single screw extruder. Rheometer packing temperatures ranged from about 100C to about 200C with dwell times of about 5 to about 15 minutes and ram speeds of about 1 to about 3 cm/min. Extrusion temperatures ranged from about 160C
to about 230C.
The extrudate was typically drawn at a draw rate of 4 2S feet per minute in a single or mulitstage drawing process with drawing temperatures of about 25C to about 75C, giving a final draw ratio of about 4X to about 8X.
Fibers were also annealed under similar conditions as described in U.S. Patent 4,643,191. Annealing temperatures were from about 70C to about 140C, preferably 110C, with annealing times of about 1 hour to about 10 hours, preferably about 4 to 7 hours.
21 ~0063 In vitro studies were determined in a phosphate buffer solution (pH=7.27) at a temperature of 37C for periods of 4, 7, 14, 21, and 28 days. Cylindrical dumbbells (8 to 10 of a total weight of 2.4 to 3.0 grams) or fibers (8 to 10, 6 to 12 inches long) were placed in 100 ml of buffer solution.
Several synthesis examples will be described in the following few pages. Parts and percentages where used are parts and percentages as specified as weight or moles.
~XAMPLE 1 Synthesis of a 80:20 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer To a flame dried 250 ml 2-neck round bottom flask equipped with an overhead mechanical stirrer, nitrogen inlet and glass stopper, 20.42 grams (0.20 moles) of p-dioxanone, 0.057 ml of diethylene glycol as an initiator, and 50.5 microliters of a 0.33 M solution of stannous octoate (in toluene) catalyst were added.
The assembly was then placed in a high temperature oil bath at 110C. The stirred p-dioxanone quickly began to melt. The low viscosity melt quickly increased in viscosity. Stirring of the high viscosity melt was continued for about 6 hours.
Then, 92.90 grams (0.80 moles) of glycolide was added in three equal portions while the temperature was raised gradually to 210C. The glycolide quickly began to melt and the reaction mass slowly began to increase in viscosity. Stirring of the high viscosity melt was continued for another 0.5 hours for a total reaction time of 2 hours at 210C under nitrogen.
The 80:20 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer was removed from the bath, cooled to room temperature under a stream of nitrogen, isolated and ground. The polymer was then dried under vacuum at 80C for about 64 hours. The copolymer conversion was about 96.8%. The inherent viscosity was 1.76 dL/g as measured in a 0.1 g/dL HFIP solution at 25C. The molar ratio of poly(glycolide) to poly(p-dioxanone) was found to be 83.2 to 16.8 by IH NMR.
Synthesis of a 70:30 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer To a flame dried 250 ml 2-neck round bottom flask equipped with an overhead mechanical stirrer, nitrogen inlet and glass stopper, 30.60 grams (0.30 moles) of p-dioxanone, 0.057 ml of diethylene glycol as an initiator, and 50.5 microliters of a 0.33 M solution of stannous octoate (in toluene) catalyst were added.
The assembly was then placed in a high temperature oil bath at 110C. The stirred p-dioxanone quickly began to melt. The low viscosity melt quickly increased in viscosity. Stirring of the high viscosity melt was continued for about 6 hours.
Then, 81.30 grams (0.70 moles) of glycolide was added in three equal portions while the temperature was raised gradually to 210C. The glycolide quickly began to melt and the reaction mass slowly began to increase in viscosity. Stirring of the high viscosity melt was continued for another 0.5 hours for a total reaction time of about 2 hours at 210C under nitrogen.
The 70:30 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer was removed from the bath, cooled to room temperature under a stream of nitrogen, isolated and ground. The polymer was then dried under vacuum at 80C for about 64 hours. The copolymer conversion was about 95.4%. The inherent viscosity was 2.25 dL/g as measured in a 0.1 g/dL HFIP solution at 25C. The molar ratio of poly(glycolide) to poly(p-dioxanone) was found to be 75.2 to 24.8 by IH NMR.
~XAMPLE 3 Synthesis of a 60:40 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer To a flame dried 250 ml 2-neck round bottom flask equipped with an overhead mechanical stirrer, nitrogen inlet and glass stopper, 40.84 grams (0.40 moles) of p-dioxanone, 0.057 ml of diethylene glycol as an initiator, and 50.5 microliters of a 0.33 M solution of stannous octoate (in toluene) catalyst were added.
The assembly was then placed in a high temperature oil bath at llO~C. The stirred p-dioxanone quickly began to melt. The low viscosity melt quickly increased in 21 8~063 viscosity. stirring of the high viscosity melt was continued for about 6 hours.
Then, 69.64 grams (0.60 moles) of glycolide was added in three equal portions while the temperature was raised gradually to 210C. The glycolide quickly began to melt and the reaction mass slowly began to increase in viscosity. Stirring of the high viscosity melt was continued for another 0.5 hours for a total reaction time of about 2 hours at 210C under nitrogen.
The 60:40 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer was removed from the bath, cooled to room temperature under a stream of nitrogen, isolated and ground. The copolymer conversion was about 95.7%.
The inherent viscosity was 1.87 dL/g as measured in a 0.1 g/dL HFIP solution at 25C.
As discussed above, U.S. Patents 4,838,267, and 5,080,665 describe poly(glycolide-co-p-dioxanone) block or graft copolymers. ~.S. Patent 4,653,497 describes poly(p-dioxanone)-rich, segmented poly(p-dioxanone-co-glycolide) copolymers.
The present invention describes glycolide-rich, segmented poly(glycolide-co-p-dioxanone) copolymers.
As shown in FIGS. 1, 2, 3 and 4, block copolymers are copolymers where long blocks of repeating units of each of the homopolymers (i.e., the homopolymers of poly(p-dioxanone), or poly(glycolide)) are connected or linked at a single point. Segmented copolymers, as shown in FIGS. 5, 6, 7, and 8, are copolymers where short segments of repeating units composed of both monomeric units are connected or linked at many points.
The differences in the arrangement or sequences of the repeating units in the copolymer can lead to dramatic changes in the thermal, chemical, physical, and for absorbable polymers, biological properties.
For biocompatible, absorbable aliphatic poly(ester)s, the sequence arrangement of repeating units in the polymer chain has a strong effect on, for example, absorption rates, BSR profiles, strength, and stiffness (FIGS. 10 and 11).
Table 1 shows the dramatic changes in physical properties by comparing the glycolide-rich, segmented poly(glycolide-co-p-dioxanone) copolymers of the present invention, and examples 2 and 3 of the poly(glycolide-b-p-dioxanone) block copolymers of U.S Patent 4,838,267.
For example, it can clearly be seen in Table 1 that the block copolymers (columns 3 and 5 of Table 1) have lower tensile fiber properties than the segmented copolymers (columns 2 and 4 of Table 1). Furthermore, the block copolymers have poor conversions.
Table 1. Properties of Poly(glycolide-co-p-dioxanone) Segmented Copolymers and Poly(glycolide-b-p-dioxanone) Block Copolymers P.oper~ie~5~ --ted Copolymer~Block Copolymer S~; --Led Copolymer Block Copolymer PCA-PDO PGA/PDO PGA/PDO PGA/PDO
Example 1~ Example 2~ Example 2~ Examplo 3~
Initial Compo~ition 80/20 77.87/22.13 70/30 67.24/32.76 (molo-) Initial Compo~ition 81.98/18.02 80/20 77.62/27.38 70/30 (weight) Fiber Diameter 6.7 6.7 6.5 6.3 (mil~) Fiber Tencile136000 47200 78000 57700 Strength (p~i) Fiber Knot Ten~ile 111000 37000 69000 52600 strength (p~i) Fibor Elongation (~) 12.6 40 22.7 52.6 Fiber Young'~ 2428 627 2007 551 Moduluc (kp~i) Polymerization 97 89 96 76 r~
Con~ar~ion (~) Ten~ile Strength- 11700 8600 o In~. molded (p~ O
Block Copolymor~ aro Examplos 2 and 3 from U.S. Patent 4,838,267 S~ ted Copolymer~ are Examples 1 and 2 from the pre~ent invention , The lower fiber properties and poor conversions of the block copolymers are caused by the sequence or arrangement of repeating units within the copolymers.
That is, in the block copolymers, the polymers are composed of long sequences of both homopolymers, with some blocks of poly(p-dioxanone) on the ends of the chain (FIGS. 2 and 4). In contrast, the segmented copolymers, due to their more random sequence of repeating units, are composed mostly of glycolide end blocks (FIG. 8). Consequently, the glycolide end blocks lead to improved stability during polymerization, with less loss of p-dioxanone monomer, since it is not possible for the p-dioxanone segments to depolymerize at the end of the chain as can be found for the block copolymers. Hence, the segmented copolymers have higher conversions (i.e., less than 5 wt.% unreacted monomers, 95% or greater conversions), and better physical properties, especially fiber tensile properties. In addition, the higher conversions, and consequently, good thermal stability, found for the segmented copolymers, allows these materials to be injection molded with good tensile properties (Table 1).
In addition, the present invention requires only a single reactor process for polymerization, where the p-dioxanone monomer is polymerized to approximately 75S
conversion, followed by reaction with glycolide to from copolymers with short segments of poly(p-dioxanone), poly(p-dioxanone-co-glycolide), and poly(glycolide) end blocks. In contrast, the block copolymers of U.S. Patent 4,838,267, require a two-step, two reactor process, where the p-dioxanone is polymerized and then further processed by isolating, grinding, and drying to remove unreacted p-dioxanone monomer. Then, the poly(p-dioxanone) ~s reacted with glycolide to form blockcopolymers with long ~equences of poly(p-dioxanone) and poly(glycolide), with some poly(p-dioxanone) end blocks.
Hence, the process of the present invention leads to the copolymers having end blocks of glycolide which prevents depolymerization and yields high conversions and excellent physical properties. Thus, the segmented copolymers of the present invention have a more elegant, simple, single reactor polymerization process than those of the block copolymers. This not only leads to advantageous properties, but is vital for large scale manufacturing development, being more cost effective and less time consuming.
Furthermore, the physical characteristics of the segmented copolymers of the present invention should allow for a variety of needs to be met for a wide range of medical devices. For example, there is a great need for absorbable polymers in plastic surgery wound closure, where high initial strength but very short BSR
profiles are required. Currently, Vicryl~ or Dexon~
sutures are used (Table 2). Dexon2 is a trademark for sutures made from braided poylcolide.
~Nslsr~I~oNo~ '0 S 8ZIS
a~ '0~ :azIs 0 0009 00008 0/OL ~zO~d~ x:a O OOOZ9 000910Z/08 ~1aldu~x:a oaa/~d 6~ aM
000~ 00058 00096 ~I/N 0008T10/001 ~NOX:10 O 000~ OOOZL 00056 ~/N 000LT101/06 ~d /~dOd .Cep-8Z~ep-lZ JCep-~l ~ep-L ~ep-~no~ ep-o aZ9~ ~15 (~ed) t~ ua ~S al~uuaL ~U,~e~,s ~au~lodo:~
s~au~lodo;) (auouexolp-d-o~-~pllo~ 6) .~loa pa~uau~aS pue ( t~p~:)el-o~ p~lo:~l6) ~1~I] q~ (~pllo~ 6~1od) Nox:aa o~
OI~A-U~ s~Cep ~o uo~ un~ e se s ~q~ o ~6u~s ~llsu~L ~1~6le~S z alqeL o o~
g However, as shown in FIG. 9, Vicryl~ has a very long BSR
profile. Consequently, this can lead to tissue scaring, an event which plastic surgeons want to avoid. The segmented glycolide-rich, poly(glycolide-co-p-dioxanone) copolymers of the present invention also have high zero-day fiber tensile properties. This would also allow the surgeon to suture the wounds securely. However, because of their very fast absorption rates and very short BSR
profiles, less scarring will occur (Table 2, FIG. 9) than found with currently marketed, longer BSR sutures like Vicryl~ and Dexon~. This behavior is caused by the unique structure of short poly(glycolide) end blocks found in the segmented copolymers of the present invention, which produces improved tensile properties and fast absorption rates.
The differences in properties between the copolymers of the present invention and U.S. Patents 4,653,497, 4,838,267 and 5,080,665, due to differences in the structure and composition, are clearly indicated in Figure 11. That is, surprisingly we have discovered that by moving towards compositions rich in glycolide where the copolymer structure is composed of short segments (i.e., segmented copolymer), and away from blocky structures, it is possible to obtain polymers with both high strength and short BSR profiles. That is, the block copolymer compositions yield h;gh strength and longer BSR profiles or lower strength and longer BSR profiles.
In addition, segmented copolymers, rich in p-dioxanone, yield polymers with lower strength and longer BSR
profiles.
This surprising behavior is also clearly indicated in Figure 9, which shows that the copolymers of poly(glycolide-co-p-dioxanone) of this invention have higher strength than either of the homopolymers of poly(glycolide) (i.e., Dexon~) or poly(p-dioxanone), but much shorter BSR profiles than even Vicryl0, DexonO, poly(p-dioxanone) or the segmented p-dioxanone-rich, poly(p-dioxanone-co-glycolide) copolymers of U.S. Patent 4,653,497. That is, the segmented copolymers of this invention lose all strength in less than 10 days, whereas the glycolide and p-dioxanone homopolymers and the copolymers of U.S. patent 4,653,497 maintain strength for 3 weeks or longer.
That is, it is unexpected, based upon composition, to obtain a copolymer of poly(glycolide-co-p-dioxanone) which has the tensile strength of either of the homopolymers of poly(p-dioxanone) or poly(glycolide), but a much shorter BSR profile than either homopolymer.
Therefore, it can be seen that glycolide-rich, poly(glycolide-co-p-dioxanone) segmented copolymers of the present invention possess a surprising and unexpected unique combination of high strength and stiffness, and very short BSR profiles and fast absorption rates. The copolymers of the present invention are useful in numerous applications requiring absorbable polymers which have high strength and stiffness and short BSR profiles. They are particularly useful, for example, in plastic surgical applications where the surgeon needs to secure the wound, but requires fast absorption to prevent tissue scaring.
Although this invention has been shown and described with respect to detailed embodiments thereof, it will understood by those skilled in the art that various -changes in form and detail thereof may be made without departing from the spirit and scope of the claimed invention.
~ac~qround of the Invention Polymers! including homopolymers and copolymers, which are both biocompatible and absorbable in vivo are known in the art. Such polymers are typically used to manufacture medical devices which are implanted in body tissue and absorb over time. Examples of medical devices manufactured from these absorbable biocompatible polymers include suture anchor devices, sutures, staples, surgical tacks, clips, plates and screws, etc.
Absorbable, biocompatible polymers useful for manufacturing medical devices include both natural and synthetic polymers. Natural polymers include cat gut, cellulose derivatives, collagen, etc. Synthetic polymers may consist of various aliphatic polyesters, polyanhydrides, poly(orthoester)s, and the like.
Natural polymers typically absorb by an enzymatic degradation process in the body, while synthetic absorbable polymers generally degrade primarily by a hydrolytic mechanism.
Synthetic absorbable polymers which are typically used 5 to manufacture medical devices include homopolymers such as poly(glycolide), poly(lactide), poly(e-caprolactone), and poly(p-dioxanone) and copolymers such as poly(lactide-co-glycolide), poly(e-caprolactone-co-glycolide), and poly(glycolide-co-trimethylene carbonate). The polymers may be statistically random copolymers, segmented copolymers, block copolymers, or graft copolymers. It is also known that both homopolymers and copolymers can be used to prepare blends.
U.S. Patents 4,653,497, 4,838,267, 5,080,665 describe several biocompatible, absorbable, poly(p-dioxanone-co-glycolide) copolymers useful as biomedical devices.
U.S. Patents 4,838,267 and 5,080,665 additionally 20 describe poly(p-dioxanone-co-glycolide) block or graft copolymers.
Furthermore, U.S. Patent 4,838,267 describes (See FIGS.
1 and 2) the preparation of poly(p-dioxanone-b-25 glycolide) block copolymers by a two-step, two-reaction vessel process in which preformed, high molecular weight poly(p-dioxanone), that is substantially free of p-dioxanone monomer, is reacted with glycolide monomer at temperatures from about 140C to about 240C to yield block copolymers of the (A-B)n type where A is a long block of repeating units of p-dioxanone (i.e., the homopolymer of poly(p-dioxanone)) and B is a long block of repeating units of glycolide (i.e., the homopolymer of poly(glycolide)). The repeating unit structure as well as a schematic representation of the block copolymer structure are shown in Figures 1 and 2. These copolymers are highly crystalline, due to their blocky structure, yielding materials with long breaking strength retention profiles (BSR), high strength and relatively high stiffness. It should be noted that breaking strength retention is a conventionally known standard method of measuring the strength of a device made of a bioabsorbable polymer, as a function of time under biological conditions in vitro or as a function of time after being implanted in vivo.
Additionally, U.S. Patent 5,080,665 describes block or graft copolymers of poly(p-dioxanone-co-glycolide) prepared by a process in which the p-dioxanone monomer is reacted initially for a certain period of time, typically one hour at about 180C, followed by reaction with glycolide at about 200C. This process leads to block or graft copolymers which are useful due to their formation of a "hard" phase formed from the glycolide repeating unit blocks, and a "soft" phase formed from the p-dioxanone repeating unit blocks as illustrated in FIGS. 3 and 4.
Furthermore, U.S. Patent 4,653,497 describes poly(p-dioxanone)-rich segmented copolymers comprising about 70 weight percent to about 97 weight percent polymerized p-dioxanone with the remaining small portion of the copolymer polymerized with glycolide as illustrated in FIGS. 5 and 6.
Although the above described copolymers yield-materials with excellent properties such as high strength and stiffness and long BSR profiles as found with the block copolymers, or good strength, long elongations, low stiffness and shorter BSR profiles as found for the poly(p-dioxanone)-rich segmented copolymers, there is a need in this art for new copolymer compositions having characteristics of both the block copolymers and the segmented copolymers.
Accordingly, what is needed in this art are novel copolymer compositions which have the block copolymer characteristics of high strength and stiffness, and the segmented copolymer characteristics of shorter BSR
profiles and absorptions rates.
In certain biomedical applications there is a strong need for these requirements, including sutures with strong tensile properties, like those of Vicryl~ or Dexon~, but shorter BSR profiles and absorption rates.
In addition, it would be highly desirable to have such polymers having little or no unreacted monomers present, since it is believed that the presence of certain levels of unreacted monomers can lead to problems such as adverse tissue reaction.
Disclo~ure of the Invention Surprisingly, it has been discovered that by preparing copolymers of poly(glycolide-co-p-dioxanone) rich in glycolide by a process in which a small proportion of p-dioxanone monomer is reacted at low temperatures from about 100C to about 130C follo~wed by reaction with glycolide at higher temperatures of about 180C to about 2! 80063 220C, segmented glycolide-rich copolymers with small proportions of p-dioxanone can be formed that have high strength and stiffness, but short BSR profiles and fast absorption rates, making them useful in a variety of biomedical devices such as suture anchor devices, staples, surgical tacks, clips, plates and screws. The copolymers of the present invention are especially useful for suture applications where Vicryl0-like sutures with excellent tensile properties but shorter BSR profiles than Vicryl0 are needed. The copolymers of the present invention are, therefore, useful in plastic surgical applications, where faster absorption times tend to result in less tissue scarring. That is, for example, an absorbable suture which rapidly loses strength in the sections which have been implanted beneath a patient's skin can be more easily removed, by use of antitension skin tape, without the pain, discomfort and scarring typically suffered by patients who have had conventional sutures implantPd.
Accordingly, novel, absorbable, biocompatible, poly(glycolide-co-p-dioxanone) segmented copolymers are disclosed. The copolymers have a major component comprising about 30 mole percent to about 95 mole percent of repeatinq units of glycolide, and a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
Yet another aspect of the present invention is a biomedical device made from the above described copolymers, especially implantable devices such as suture anchor devices, staples, surgical tacks, clips, plates and screws, and most especially for suture applications where Vicryl0 or Dexon0-like sutures with excellent tensile properties, but shorter BSR profiles than Vicryl~ or Dexon~ are needed for plastic surgery.
An additional aspect of the present invention is a process for producing the segmented copolymers of the present invention. The initial step of the process is to polymerize p-dioxanone in the presence of a catalytically effective amount of catalyst and an initiator at a sufficient temperature and for a sufficient period of time to effectively yield a first mixture of p-dioxanone monomer and p-dioxanone homopolymer. Then, glycolide is added to the first mixture to form a second mixture. Next, the second mixture is polymerized at a sufficient temperature and for a sufficient amount of time to effectively produce a segmented copolymer comprising a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide and a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
Still yet a further aspect of the present invention is the copolymer of the present invention which is a product of the process of the present invention.
The foregoing and other features and advantages of the invention will become more apparent from the following description and accompanying examples.
Brief Description of the Drawings FIG. 1 illustrates a synthetic process for the preparation of poly(p-dioxanone-b-glycolide) block copolymers as described in U.S. Patent 4,838,267.
FIG. 2 illustrates a schematic representation of poly(p-dioxanone-b-glycolideJ block copolymers as described in U.S. Patent 4,~38,267.
5 FIG. 3 illustrates a synthetic process for the preparation of poly(p-dioxanone-co-glycolide) block or graft copolymers as described in U.S. Patent 5,080,665.
FIG. 4 illustrates a schematic representation of poly(p-10 dioxanone-co-glycolide) block or graft copolymers as described in U.S. Patent 5,080,665.
FIG. 5 illustrates a synthetic process for the preparation of poly(p-dioxanone)-rich, poly(p-dioxanone-15 co-glycolide) segmented copolymers as described in U.S.
Patent 4,653,497.
FIG. 6 illustrates a schematic representation of poly(p-dioxanone)-rich, poly(p-dioxanone-co-glycolide) 20 segmented copolymers as described in U.S. Patent 4,653,497.
FIG. 7 illustrates a synthetic process for the preparation of the glycolide-rich, poly(glycolide-co-p-25 dioxanone) segmented copolymers of the presentinventlon .
FIG. 8 illustrates a schematic representation of the glycolide-rich, poly(glycolide-co-p-dioxanone) segmented 30 copolymers of the present invention.
FIG. 9 is a graph presenting BSR profiles of size 4-0 fibers (sutures) of Vicryl (90:10 (mol/mol) poly(glycolide-co-lactide)) or Dexon (poly(glycolide)), size 4-0 fibers of poly(p-dioxanone), size 5-0 fibers of a segmented copolymer of U.S. patent 4,653,497, and size 5-0 fibers of a 80:20 (mol/mol) segmented poly(glycolide-co-p-dioxanone) copolymer of the present invention.
FIG. 10 shows the compositional differences between the segmented poly(glycolide-co-p-dioxanone) copolymers of the present invention and the copolymers disclosed in U.S. Patents 4,653,497, 4,838,267 and 5,080,665.
FIG. 11 displays the property differences between the segmented poly(glycolide-co-p-dioxanone) copolymers of the present invention and U.S. Patents 4,653,497, 4,838,267 and 5,080,665, based upon differences in composition and structure.
Description of the Preferred Embodiments The process of the present invention is a one-step, one-reaction vessel, two-temperature process in which a mixture of p-dioxanone monomer and p-dioxanone homopolymer is initially formed at low temperatures of from about 100C to about 130C, preferably 110C. The mixture is then reacted with glycolide at temperatures from about 120C to about 220C to form copolymers in which segments or sequences are composed of both p-dioxanone and glycolate moieties as illustrated in FIGS.
7 and 8. These segmented copolymers are substantially less crystalline than the block or graft copolymers of the prior art and, therefore, yield materials with good strength, but shorter BSR profiles, faster absorption rates, longer elongations and lower stiffness.
More specifically, the poly(glycolide-co-p-dioxanone) segmented copolymers of the present invention are prepared by a process in which p-dioxanone monomer is reacted in a conventional reactor vessel at low temperatures from about 100C to about 130C, preferably about 110C, for a sufficient time effective to cause polymerization, preferably about 4 hours to about 8 hours, followed by reaction with glycolide at higher temperatures of about 180C to about 220C for a sufficient time effective to cause copolymerization, preferably about 1 hour to about 4 hours.
Furthermore, the segmented poly(glycolide-co-p-dioxanone) copolymers will typically consist of about 30 mole percent to about 95 mole percent of glycolate moieties, more preferably about 30 mole percent to about 90 mole percent of glycolate moieties, and most preferably about 30 mole percent to about 50 mole percent of glycolate moieties.
The aliphatic segmented copolyesters useful in the preparation of the segmented copolymers of the present invention will typically be synthesized in a ring opening polymerization. That is, the aliphatic lactone 2S monomers are polymerized in the presence of an organometallic catalyst and an initiator at elevated temperatures. The organometallic catalyst is preferably tin based, e.g., stannous octoate, and is present in the monomer mixture at a molar ratio of monomer to catalyst ranging from about lO,OOo/1 to about lOO,OoO/1. The initiator is typically an alkanol, a glycol, a hydroxyacid, or an amine, and is present in the monomer mixture at a molar ratio of monomer to initiator ranging from about 100/1 to about 5000/1. The polymerization is typically carried out at a temperature range from about 80C to about 240C, preferably from about 100C to about 220C, until the desired molecular weight and viscosity are achieved.
Suitable lactone monomers may be selected from the group consisting of glycolide, lactide (l, d, dl, meso), p-dioxanone, delta-valerolactone, beta-butyrolactone, epsilon-decalactone, 2,5-diketomorpholine, pivalolactone, alpha, alpha-diethylpropiolactone, ethylene carbonate, ethylene oxalate, 3-methyl-1,4-dioxane-2,5-dione, 3,3-diethyl-1,4-dioxan-2,5-dione, gamma-butyrolactone, 1,4-dioxepan-2-one, 1,5-dioxepan-2-one, 1,4-dioxan-2-one, 6,8-dioxabicycloctane-7-one and combinations of two or more thereof. Preferred lactone monomers are selected from the group consisting of glycolide, and p-dioxanone.
More specifically, the segmented copolymers of poly(glycolide-co-p-dioxanone) useful in the practice of the present invention will typically be synthesized by a process in which p-dioxanone is polymerized in a ring opening polymerization in the presence of an organometallic catalyst and an initiator at elevated temperatures. The organometallic catalyst is preferably tin based, e.g., stannous octoate, and is present in the mixture at a molar ratio of monomer to catalyst ranging from about 10,000/1 to about lO0,000/1. The initiator is typically an alkanol, a glycol, a hydroxyacid, or an amine, and is present in the monomer mixture at a molar ratio of monomer to initiator ranging from about loO/l to about 5000/1.
The polymerization is typically carried out ~n a conventional reactor vessel at a temperature range from about 100C to about 130C, preferably 110C, for about 4 hours to about 8 hours, preferably about 5 hours to about 6 hours, yielding a mixture of p-dioxanone monomer and homopolymer. Then, glycolide monomer is added to the mixture of p-dioxanone monomer and homopolymer and the temperature is raised to about 180C to about 220C, preferably from about 190C to about 220C until the desired molecular weight and viscosity are achieved. It should be understood that pure monomers and dry conditions are utilized to achieve such molecular weights.
Under the above described conditions, the segmented copolymers of poly(glycolide-co-p-dioxanone), will typically have a weight average molecular weight of about 20,000 grams per mole to about 300,000 grams per mole, more typically about 40,000 grams per mole to about 200,000 grams per mole, and preferably about 60,000 grams per mole to about 150,000 grams per mole.
These molecular weights provide an inherent viscosity between about 0.5 to about 4.0 deciliters per gram (dL/g), more typically 0.7 to about 3.5 dL/g, and most preferably 1.0 to about 3.0 dL/g as measured in a 0.1 g/dL solution of hexafluoroisopropanol (HFIP) at 25C.
Also, it should be noted that under the above described conditions, the residual monomer content will be less than about 5 wt. %.
The segmented copolymers of poly(glycolide-co-p-dioxanone) will typically consists of about 30 mole percent to about 95 mole percent, more preferably about 30 mole percent to about 90 mole percent of glycolate 2 i 80063 moieties, and most preferably about 30 mole percent to about 50 mole percent of glycolate moieties. The lower limit of glycolate moieties in the copolymers is desirable because the addition of 30 mole percent leads to copolymers which have longer BSR profiles, but lower strength. The upper limit of glycolate moieties in the copolymers is desirable because the addition of 95 mole percent leads to copolymers which have shorter BSR
profiles, but higher strength and stiffness. This leads to copolymers with a desirable range of strength, stiffness and absorption profiles for use in a variety of biomedical applications. One skilled in the art will appreciate that the number of moles of glycolate moieties and p-dioxanone moieties in the copolymer are equivalent to the number of moles of glycolide and p-dioxanone monomers needed to be added to the reaction to form the copolymer.
Articles such as medical devices are molded from the segmented copolymers of the present invention by use of various conventional injection and extrusion molding equipment at temperatures ranging from about 160C to about 220C, more preferably 180C to about 220C, with residence times of about 2 to about 10 minutes, more preferably about 2 to about 5 minutes.
The segmented copolymers of the present invention can be melt processed by numerous methods to prepare a vast array of useful devices. These materials can be injection or compression molded to make implantable medical and surgical devices, including wound closure devices. The preferred devices are suture anchor devices, staples, surgical tacks, clips, plates and screws.
Copolymers of the present invention with low levels of p-dioxanone have particular utility in the preparation of absorbable surgical devices that must be stiff and simultaneously tough. Of particular utility are those compostions having p-dioxanone at about 5 to about 30 mole percent.
Alternatively, the segmented copolymers can be extruded to prepare fibers. The filaments thus produced may be fabricated into sutures or ligatures, attached to surgical needles, packaged, and sterilized by known techniques. The materials of the present invention may be spun as multifilament yarn and woven or knitted to form sponges or gauze, (or non-woven sheets may be prepared) or used in conjunction with other molded compressive structures such as prosthetic devices within the body of a human or animal where it is desirable that the structure have high tensile strength and desirable levels of compliance and/or ductility. Useful embodiments include tubes, including branched tubes, for 2S artery, vein or intestinal repair, nerve splicing, tendon splicing, sheets for tying up and supporting damaged surface abrasions, particularly major abrasions, or areas where the skin and underlying tissues are damaged or surgically removed. Especially, sutures with Vicryl~-like tensile properties but shorter BSR profiles than Vicryl2 are needed, useful in plastic surgical applications where faster absorption times would lead to less ti-ssue scarring. That is, a suture which rapidly loses strength in the portion which is implanted beneath the skin can be more easily removed, by use of antitension skin tape, without the pain, discomfort and scarring typically suffered by patients who have had conventional sutures implanted. Vicryl~ is a trademark for sutres made from polyglycolide-polylactide (90-10) copolymers.
Additionally, the segmented copolymers of the present invention can be molded to form films which, when sterilized, could be useful as adhesion prevention barriers. Another alternative processing technique for the copolymers of the present invention includes solvent casting, particularly for those applications where a drug delivery matrix is desired.
Furthermore, the segmented copolymers of the present invention can be processed by conventional techniques to form foams, which are useful as hemostatic barriers and bone substitutes.
In more detail, the surgical and medical uses of the filaments, films, foams and molded articles of the present invention include, but are not necessarily limited to knitted products, woven or non-woven, and molded products including:
a. burn dressings b. hernia patches c. medicated dressings d. fascial substitutes e. gauze, fabric, sheet, felt or sponge for liver hemostasis f. gauze bandages g. arterial graft or substitutes h. bandages for skin surfaces i. burn dressings j. orthopedic pins, clamps, screws, and plates k. clips 1. staples m. hooks, buttons, and snaps n. bone substitutes o. needles p. intrauterine devices q. draining or testing tubes or capillaries r. surgical instruments s. vascular implants or supports t. vertebral discs u. extracorporeal tubing for kidney and heart-lung machines v. artificial skin and others w. stents x. suture anchors y. injectable defect fillers z. preformed defect fillers al. tissue adhesives and sealants b2. bone waxes c3. cartilage replacements d4. hemostatic barriers Examples The following examples are illustrative of the principles and practice of this invention, although not limited thereto. Numerous additional embodiments within the scope and spirit of the invention will become apparent to those skilled in the art. The examples describe new segmented copolymers of poly(glycolide-co-.
p-dioxanone), said copolymers being useful as biomedical devices.
In the synthetic process, the high molecular weight aliphatic segmented copolyesters are prepared by a method consisting of reacting p-dioxanone via a ring opening polymerization in a conventional reactor vessel at temperatures of about 100C to about 130C for about 4 hours to about 8 hours under an inert nitrogen atmosphere, followed by reaction with glycolide at temperatures of 180C to 220C until the desired molecular weight and viscosity are achieved.
In the examples which follow, the segmented copolymers and monomers were characterized for chemical composition and purity (NMR, FT-IR), thermal analysis (DSC), melt rheology (melt stability and viscosity), and molecular weight (inherent viscosity), and baseline and in vitro mechanical properties (Instron stress/strain).
IH NMR was performed on a 300 MHz NMR using CDC13 or HFAD
as a reference. Thermal analysis of segmented copolymers and monomers was performed on a Dupont 912 Differential Scanning Calorimeter (DSC) at a heating rate of 10C/min.
A Fisher-Johns melting point apparatus was also utilized to determine melting points of monomers. Thermal gravimetric analysis was performed on a Dupont 951 TGA
at a rate of 10C/min. under a nitrogen atmosphere.
Isothermal melt stability of the segmented copolymers was also determined by a Rheometrics Dynamic Analyzer RDA II for a period of 1 hour at temperatures ranging from 160C to 230C under a nitrogen atmosphere.
Inherent viscosities (I.V., dL/g) of the segmented copolymers were measured using a 50 bore Cannon-Ubbelhode dilution viscometer immersed in a thermostatically controlled water bath at 25C utilizing chloroform or hexafluoroisopropanol (HFIP) as the solvent at a concentration of 0.1 g/dL.
Melt viscosity was determined utilizing a Rheometrics Dynamic Analyzer RDA II at temperatures ranging from 160C to 230C at rate of 1C/min. to 10C/min. at frequencies of ls-l to 100sl under a nitrogen atmosphere.
Fibers of copolymers of the present invention were prepared by a method as described in U.S. Patent 4,643,191, which is incorporated herein by reference.
The copolymers were melt extruded in a conventional manner using an INSTRON3 capillary rheometer or single screw extruder. Rheometer packing temperatures ranged from about 100C to about 200C with dwell times of about 5 to about 15 minutes and ram speeds of about 1 to about 3 cm/min. Extrusion temperatures ranged from about 160C
to about 230C.
The extrudate was typically drawn at a draw rate of 4 2S feet per minute in a single or mulitstage drawing process with drawing temperatures of about 25C to about 75C, giving a final draw ratio of about 4X to about 8X.
Fibers were also annealed under similar conditions as described in U.S. Patent 4,643,191. Annealing temperatures were from about 70C to about 140C, preferably 110C, with annealing times of about 1 hour to about 10 hours, preferably about 4 to 7 hours.
21 ~0063 In vitro studies were determined in a phosphate buffer solution (pH=7.27) at a temperature of 37C for periods of 4, 7, 14, 21, and 28 days. Cylindrical dumbbells (8 to 10 of a total weight of 2.4 to 3.0 grams) or fibers (8 to 10, 6 to 12 inches long) were placed in 100 ml of buffer solution.
Several synthesis examples will be described in the following few pages. Parts and percentages where used are parts and percentages as specified as weight or moles.
~XAMPLE 1 Synthesis of a 80:20 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer To a flame dried 250 ml 2-neck round bottom flask equipped with an overhead mechanical stirrer, nitrogen inlet and glass stopper, 20.42 grams (0.20 moles) of p-dioxanone, 0.057 ml of diethylene glycol as an initiator, and 50.5 microliters of a 0.33 M solution of stannous octoate (in toluene) catalyst were added.
The assembly was then placed in a high temperature oil bath at 110C. The stirred p-dioxanone quickly began to melt. The low viscosity melt quickly increased in viscosity. Stirring of the high viscosity melt was continued for about 6 hours.
Then, 92.90 grams (0.80 moles) of glycolide was added in three equal portions while the temperature was raised gradually to 210C. The glycolide quickly began to melt and the reaction mass slowly began to increase in viscosity. Stirring of the high viscosity melt was continued for another 0.5 hours for a total reaction time of 2 hours at 210C under nitrogen.
The 80:20 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer was removed from the bath, cooled to room temperature under a stream of nitrogen, isolated and ground. The polymer was then dried under vacuum at 80C for about 64 hours. The copolymer conversion was about 96.8%. The inherent viscosity was 1.76 dL/g as measured in a 0.1 g/dL HFIP solution at 25C. The molar ratio of poly(glycolide) to poly(p-dioxanone) was found to be 83.2 to 16.8 by IH NMR.
Synthesis of a 70:30 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer To a flame dried 250 ml 2-neck round bottom flask equipped with an overhead mechanical stirrer, nitrogen inlet and glass stopper, 30.60 grams (0.30 moles) of p-dioxanone, 0.057 ml of diethylene glycol as an initiator, and 50.5 microliters of a 0.33 M solution of stannous octoate (in toluene) catalyst were added.
The assembly was then placed in a high temperature oil bath at 110C. The stirred p-dioxanone quickly began to melt. The low viscosity melt quickly increased in viscosity. Stirring of the high viscosity melt was continued for about 6 hours.
Then, 81.30 grams (0.70 moles) of glycolide was added in three equal portions while the temperature was raised gradually to 210C. The glycolide quickly began to melt and the reaction mass slowly began to increase in viscosity. Stirring of the high viscosity melt was continued for another 0.5 hours for a total reaction time of about 2 hours at 210C under nitrogen.
The 70:30 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer was removed from the bath, cooled to room temperature under a stream of nitrogen, isolated and ground. The polymer was then dried under vacuum at 80C for about 64 hours. The copolymer conversion was about 95.4%. The inherent viscosity was 2.25 dL/g as measured in a 0.1 g/dL HFIP solution at 25C. The molar ratio of poly(glycolide) to poly(p-dioxanone) was found to be 75.2 to 24.8 by IH NMR.
~XAMPLE 3 Synthesis of a 60:40 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer To a flame dried 250 ml 2-neck round bottom flask equipped with an overhead mechanical stirrer, nitrogen inlet and glass stopper, 40.84 grams (0.40 moles) of p-dioxanone, 0.057 ml of diethylene glycol as an initiator, and 50.5 microliters of a 0.33 M solution of stannous octoate (in toluene) catalyst were added.
The assembly was then placed in a high temperature oil bath at llO~C. The stirred p-dioxanone quickly began to melt. The low viscosity melt quickly increased in 21 8~063 viscosity. stirring of the high viscosity melt was continued for about 6 hours.
Then, 69.64 grams (0.60 moles) of glycolide was added in three equal portions while the temperature was raised gradually to 210C. The glycolide quickly began to melt and the reaction mass slowly began to increase in viscosity. Stirring of the high viscosity melt was continued for another 0.5 hours for a total reaction time of about 2 hours at 210C under nitrogen.
The 60:40 (mol/mol) poly(glycolide-co-p-dioxanone) segmented copolymer was removed from the bath, cooled to room temperature under a stream of nitrogen, isolated and ground. The copolymer conversion was about 95.7%.
The inherent viscosity was 1.87 dL/g as measured in a 0.1 g/dL HFIP solution at 25C.
As discussed above, U.S. Patents 4,838,267, and 5,080,665 describe poly(glycolide-co-p-dioxanone) block or graft copolymers. ~.S. Patent 4,653,497 describes poly(p-dioxanone)-rich, segmented poly(p-dioxanone-co-glycolide) copolymers.
The present invention describes glycolide-rich, segmented poly(glycolide-co-p-dioxanone) copolymers.
As shown in FIGS. 1, 2, 3 and 4, block copolymers are copolymers where long blocks of repeating units of each of the homopolymers (i.e., the homopolymers of poly(p-dioxanone), or poly(glycolide)) are connected or linked at a single point. Segmented copolymers, as shown in FIGS. 5, 6, 7, and 8, are copolymers where short segments of repeating units composed of both monomeric units are connected or linked at many points.
The differences in the arrangement or sequences of the repeating units in the copolymer can lead to dramatic changes in the thermal, chemical, physical, and for absorbable polymers, biological properties.
For biocompatible, absorbable aliphatic poly(ester)s, the sequence arrangement of repeating units in the polymer chain has a strong effect on, for example, absorption rates, BSR profiles, strength, and stiffness (FIGS. 10 and 11).
Table 1 shows the dramatic changes in physical properties by comparing the glycolide-rich, segmented poly(glycolide-co-p-dioxanone) copolymers of the present invention, and examples 2 and 3 of the poly(glycolide-b-p-dioxanone) block copolymers of U.S Patent 4,838,267.
For example, it can clearly be seen in Table 1 that the block copolymers (columns 3 and 5 of Table 1) have lower tensile fiber properties than the segmented copolymers (columns 2 and 4 of Table 1). Furthermore, the block copolymers have poor conversions.
Table 1. Properties of Poly(glycolide-co-p-dioxanone) Segmented Copolymers and Poly(glycolide-b-p-dioxanone) Block Copolymers P.oper~ie~5~ --ted Copolymer~Block Copolymer S~; --Led Copolymer Block Copolymer PCA-PDO PGA/PDO PGA/PDO PGA/PDO
Example 1~ Example 2~ Example 2~ Examplo 3~
Initial Compo~ition 80/20 77.87/22.13 70/30 67.24/32.76 (molo-) Initial Compo~ition 81.98/18.02 80/20 77.62/27.38 70/30 (weight) Fiber Diameter 6.7 6.7 6.5 6.3 (mil~) Fiber Tencile136000 47200 78000 57700 Strength (p~i) Fiber Knot Ten~ile 111000 37000 69000 52600 strength (p~i) Fibor Elongation (~) 12.6 40 22.7 52.6 Fiber Young'~ 2428 627 2007 551 Moduluc (kp~i) Polymerization 97 89 96 76 r~
Con~ar~ion (~) Ten~ile Strength- 11700 8600 o In~. molded (p~ O
Block Copolymor~ aro Examplos 2 and 3 from U.S. Patent 4,838,267 S~ ted Copolymer~ are Examples 1 and 2 from the pre~ent invention , The lower fiber properties and poor conversions of the block copolymers are caused by the sequence or arrangement of repeating units within the copolymers.
That is, in the block copolymers, the polymers are composed of long sequences of both homopolymers, with some blocks of poly(p-dioxanone) on the ends of the chain (FIGS. 2 and 4). In contrast, the segmented copolymers, due to their more random sequence of repeating units, are composed mostly of glycolide end blocks (FIG. 8). Consequently, the glycolide end blocks lead to improved stability during polymerization, with less loss of p-dioxanone monomer, since it is not possible for the p-dioxanone segments to depolymerize at the end of the chain as can be found for the block copolymers. Hence, the segmented copolymers have higher conversions (i.e., less than 5 wt.% unreacted monomers, 95% or greater conversions), and better physical properties, especially fiber tensile properties. In addition, the higher conversions, and consequently, good thermal stability, found for the segmented copolymers, allows these materials to be injection molded with good tensile properties (Table 1).
In addition, the present invention requires only a single reactor process for polymerization, where the p-dioxanone monomer is polymerized to approximately 75S
conversion, followed by reaction with glycolide to from copolymers with short segments of poly(p-dioxanone), poly(p-dioxanone-co-glycolide), and poly(glycolide) end blocks. In contrast, the block copolymers of U.S. Patent 4,838,267, require a two-step, two reactor process, where the p-dioxanone is polymerized and then further processed by isolating, grinding, and drying to remove unreacted p-dioxanone monomer. Then, the poly(p-dioxanone) ~s reacted with glycolide to form blockcopolymers with long ~equences of poly(p-dioxanone) and poly(glycolide), with some poly(p-dioxanone) end blocks.
Hence, the process of the present invention leads to the copolymers having end blocks of glycolide which prevents depolymerization and yields high conversions and excellent physical properties. Thus, the segmented copolymers of the present invention have a more elegant, simple, single reactor polymerization process than those of the block copolymers. This not only leads to advantageous properties, but is vital for large scale manufacturing development, being more cost effective and less time consuming.
Furthermore, the physical characteristics of the segmented copolymers of the present invention should allow for a variety of needs to be met for a wide range of medical devices. For example, there is a great need for absorbable polymers in plastic surgery wound closure, where high initial strength but very short BSR
profiles are required. Currently, Vicryl~ or Dexon~
sutures are used (Table 2). Dexon2 is a trademark for sutures made from braided poylcolide.
~Nslsr~I~oNo~ '0 S 8ZIS
a~ '0~ :azIs 0 0009 00008 0/OL ~zO~d~ x:a O OOOZ9 000910Z/08 ~1aldu~x:a oaa/~d 6~ aM
000~ 00058 00096 ~I/N 0008T10/001 ~NOX:10 O 000~ OOOZL 00056 ~/N 000LT101/06 ~d /~dOd .Cep-8Z~ep-lZ JCep-~l ~ep-L ~ep-~no~ ep-o aZ9~ ~15 (~ed) t~ ua ~S al~uuaL ~U,~e~,s ~au~lodo:~
s~au~lodo;) (auouexolp-d-o~-~pllo~ 6) .~loa pa~uau~aS pue ( t~p~:)el-o~ p~lo:~l6) ~1~I] q~ (~pllo~ 6~1od) Nox:aa o~
OI~A-U~ s~Cep ~o uo~ un~ e se s ~q~ o ~6u~s ~llsu~L ~1~6le~S z alqeL o o~
g However, as shown in FIG. 9, Vicryl~ has a very long BSR
profile. Consequently, this can lead to tissue scaring, an event which plastic surgeons want to avoid. The segmented glycolide-rich, poly(glycolide-co-p-dioxanone) copolymers of the present invention also have high zero-day fiber tensile properties. This would also allow the surgeon to suture the wounds securely. However, because of their very fast absorption rates and very short BSR
profiles, less scarring will occur (Table 2, FIG. 9) than found with currently marketed, longer BSR sutures like Vicryl~ and Dexon~. This behavior is caused by the unique structure of short poly(glycolide) end blocks found in the segmented copolymers of the present invention, which produces improved tensile properties and fast absorption rates.
The differences in properties between the copolymers of the present invention and U.S. Patents 4,653,497, 4,838,267 and 5,080,665, due to differences in the structure and composition, are clearly indicated in Figure 11. That is, surprisingly we have discovered that by moving towards compositions rich in glycolide where the copolymer structure is composed of short segments (i.e., segmented copolymer), and away from blocky structures, it is possible to obtain polymers with both high strength and short BSR profiles. That is, the block copolymer compositions yield h;gh strength and longer BSR profiles or lower strength and longer BSR profiles.
In addition, segmented copolymers, rich in p-dioxanone, yield polymers with lower strength and longer BSR
profiles.
This surprising behavior is also clearly indicated in Figure 9, which shows that the copolymers of poly(glycolide-co-p-dioxanone) of this invention have higher strength than either of the homopolymers of poly(glycolide) (i.e., Dexon~) or poly(p-dioxanone), but much shorter BSR profiles than even Vicryl0, DexonO, poly(p-dioxanone) or the segmented p-dioxanone-rich, poly(p-dioxanone-co-glycolide) copolymers of U.S. Patent 4,653,497. That is, the segmented copolymers of this invention lose all strength in less than 10 days, whereas the glycolide and p-dioxanone homopolymers and the copolymers of U.S. patent 4,653,497 maintain strength for 3 weeks or longer.
That is, it is unexpected, based upon composition, to obtain a copolymer of poly(glycolide-co-p-dioxanone) which has the tensile strength of either of the homopolymers of poly(p-dioxanone) or poly(glycolide), but a much shorter BSR profile than either homopolymer.
Therefore, it can be seen that glycolide-rich, poly(glycolide-co-p-dioxanone) segmented copolymers of the present invention possess a surprising and unexpected unique combination of high strength and stiffness, and very short BSR profiles and fast absorption rates. The copolymers of the present invention are useful in numerous applications requiring absorbable polymers which have high strength and stiffness and short BSR profiles. They are particularly useful, for example, in plastic surgical applications where the surgeon needs to secure the wound, but requires fast absorption to prevent tissue scaring.
Although this invention has been shown and described with respect to detailed embodiments thereof, it will understood by those skilled in the art that various -changes in form and detail thereof may be made without departing from the spirit and scope of the claimed invention.
Claims (21)
1. An absorbable, biocompatible segmented copolymer comprising:
a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide; and, a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide; and, a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
2. The segmented copolymer of claim 1 wherein the copolymer has a molecular weight such that the inherent viscosity is from about 0.6 dL/g to about 3.0 dL/g as measured in HFIP at 25°C at a concentration of 0.1 g/dL.
3. The segmented copolymer of claim 1 wherein the major component comprises about 30 mole percent to about 90 mole percent of repeating units of glycolide, and wherein the minor component comprises about 70 mole percent to about 10 mole percent of repeating units of p-dioxanone.
4. The segmented copolymer of claim 3 wherein the copolymer has a molecular weight such that the inherent viscosity is from about 0.6 dL/g to about 3.0 dL/g as measured in HFIP at 25°C at a concentration of 0.1 g/dL.
5. The segmented copolymer of claim 1 wherein the repeating units of glycolide comprise about 30 mole percent to about 50 mole percent of the copolymer, and wherein the repeating units of p-dioxanone comprise about 50 mole percent to about 70 mole percent of the copolymer.
6. The segmented copolymer of claim 5 wherein the copolymer has a molecular weight such that the inherent viscosity is from about 0.6 dL/g to about 3.0 dL/g as measured in HFIP at 25°C at a concentration of 0.1 g/dL.
7. An absorbable device for use in medical applications, the medical device comprising a segmented copolymer, said copolymer comprising:
a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide; and, a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide; and, a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
8. An absorbable device for use in medical applications, the medical device comprising a segmented copolymer, said copolymer comprising:
a major component comprising about 30 mole percent to about 90 mole percent of repeating units of glycolide, and, a minor component comprising about 70 mole percent to about 10 mole percent of repeating units of p-dioxanone.
a major component comprising about 30 mole percent to about 90 mole percent of repeating units of glycolide, and, a minor component comprising about 70 mole percent to about 10 mole percent of repeating units of p-dioxanone.
9. An absorbable device for use in medical applications, the medical device comprising a segmented copolymer, said copolymer comprising:
about 30 mole percent to about 50 mole percent of repeating units of glycolide; and, about 70 mole percent to about 50 mole percent of repeating units of p-dioxanone.
about 30 mole percent to about 50 mole percent of repeating units of glycolide; and, about 70 mole percent to about 50 mole percent of repeating units of p-dioxanone.
10. A process for producing a segmented copolymer of p-dioxanone and glycolide, said process comprising heating a mixture of p-dioxanone monomer, p-dioxanone homopolymer, and glycolide monomer, to a sufficient temperature for a period of time to effectively produce a segmented copolymer comprising a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide and a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
11. A process for producing a segmented copolymer comprising the steps of:
a) polymerizing p-dioxanone in the presence of a catalytically effective amount of catalyst and an initiator at a sufficient temperature and for a sufficient period of time to yield a first mixture of p-dioxanone monomer and p-dioxanone homopolymer; and , b) adding glycolide to the first mixture to form a second mixture; and, c) polymerizing the second mixture at a sufficient temperature and for a sufficient amount of time to form a segmented copolymer comprising a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide and a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
a) polymerizing p-dioxanone in the presence of a catalytically effective amount of catalyst and an initiator at a sufficient temperature and for a sufficient period of time to yield a first mixture of p-dioxanone monomer and p-dioxanone homopolymer; and , b) adding glycolide to the first mixture to form a second mixture; and, c) polymerizing the second mixture at a sufficient temperature and for a sufficient amount of time to form a segmented copolymer comprising a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide and a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone.
12. The process of claim 11 for producing a segmented copolymer wherein the temperature for the initial polymerization is about 100°C to about 130°C and the time is about 5 to about 6 hours and the temperature for the second polymerization is about 180°C to about 220°C, and the time is about 1 hour to about 4 hours.
13. The process of claim 12 wherein the amount of catalyst utilized is from about 10,000/1 to about 100,000/1, based on the molar ratio of monomer to catalyst, and wherein the catalyst is preferably tin based.
14. The process of claim 13 wherein the catalyst is stannous octoate.
15. The process of claim 12 wherein the amount of catalyst used comprises from about 100/1 to about 5,000/1, based on the molar ratio of monomer to initiator, and wherein the initiator is selected from the group consisting of alkanol, glycol, hydroxyacid, amine, and combinations thereof.
16. The process of claim 12 wherein the lactone monomer added in step (b) is glycolide and the temperature of the polymerization of the second mixture is about 180°C to about 220°C.
17. The process of claim 16 wherein the segmented copolymer has a molecular weight such that the inherent viscosity is about 0.6 dL/g to about 3.0 dL/g as measured in HFIP at 25°C at a concentration of 0.1 g/dL.
18. The process of claim 11 wherein the segmented copolymer comprises:
a major component comprising about 30 mole percent to about 90 mole percent of repeating units of glycolide and, a minor component comprising about 70 mole percent to about 10 mole percent of repeating units of p-dioxanone.
a major component comprising about 30 mole percent to about 90 mole percent of repeating units of glycolide and, a minor component comprising about 70 mole percent to about 10 mole percent of repeating units of p-dioxanone.
19. The process of claim 11 whereln the segmented copolymer comprises:
about 30 mole percent to about 50 mole percent of repeating units of glycolide and, about 70 mole percent to about 50 mole percent of repeating units of p-dioxanone.
about 30 mole percent to about 50 mole percent of repeating units of glycolide and, about 70 mole percent to about 50 mole percent of repeating units of p-dioxanone.
20. An absorbable, biocompatible segmented copolymer comprising:
a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide; and, a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone, wherein said segmented copolymer is the product of the process comprising the steps of:
a) polymerizing p-dioxanone in the presence of a catalytically effective amount of catalyst and an initiator at a sufficient temperature and for a sufficient period of time to yield a first mixture of p-dioxanone monomer and p-dioxanone homopolymer; and, b) adding glycolide to the first mixture to form a second mixture; and, c) polymerizing the second mixture at a sufficient temperature and for a sufficient amount of time.
a major component comprising about 30 mole percent to about 95 mole percent of repeating units of glycolide; and, a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone, wherein said segmented copolymer is the product of the process comprising the steps of:
a) polymerizing p-dioxanone in the presence of a catalytically effective amount of catalyst and an initiator at a sufficient temperature and for a sufficient period of time to yield a first mixture of p-dioxanone monomer and p-dioxanone homopolymer; and, b) adding glycolide to the first mixture to form a second mixture; and, c) polymerizing the second mixture at a sufficient temperature and for a sufficient amount of time.
21. An absorbable, biocompatible segmented copolymer comprising:
a major component comprising about 30 mol percent to about 95 mole percent of repeating units of glycolide; and, a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone, wherein said segmented copolymer is the product of the process comprising heating a mixture of p-dioxanone monomer, p-dioxanone homopolymer, and glycolide monomer, to a sufficient temperature and for a sufficient period of time.
a major component comprising about 30 mol percent to about 95 mole percent of repeating units of glycolide; and, a minor component comprising about 70 mole percent to about 5 mole percent of repeating units of p-dioxanone, wherein said segmented copolymer is the product of the process comprising heating a mixture of p-dioxanone monomer, p-dioxanone homopolymer, and glycolide monomer, to a sufficient temperature and for a sufficient period of time.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/497,127 | 1995-06-30 | ||
| US08/497,127 US5633343A (en) | 1995-06-30 | 1995-06-30 | High strength, fast absorbing, melt processable, gycolide-rich, poly(glycolide-co-p-dioxanone) copolymers |
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| Publication Number | Publication Date |
|---|---|
| CA2180063A1 true CA2180063A1 (en) | 1996-12-31 |
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ID=23975580
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| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002180063A Abandoned CA2180063A1 (en) | 1995-06-30 | 1996-06-27 | High strength, fast absorbing, melt processable, glycolide-rich, poly(glycolide-co-p-dioxanone) copolymers |
Country Status (7)
| Country | Link |
|---|---|
| US (1) | US5633343A (en) |
| EP (1) | EP0751165A3 (en) |
| JP (1) | JP3556773B2 (en) |
| AU (1) | AU5608596A (en) |
| BR (1) | BR9602945A (en) |
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Families Citing this family (31)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8226683B2 (en) * | 1994-03-11 | 2012-07-24 | Poly-Med, Inc. | High strength nitrogenous caprolactone copolymers and biomedical constructs therefrom |
| US5773563A (en) * | 1994-03-11 | 1998-06-30 | Poly-Med, Inc. | Absorbable ε-caprolactone polymers |
| US20020188037A1 (en) * | 1999-04-15 | 2002-12-12 | Chudzik Stephen J. | Method and system for providing bioactive agent release coating |
| WO1999055396A1 (en) * | 1998-04-27 | 1999-11-04 | Surmodics, Inc. | Bioactive agent release coating |
| US6235869B1 (en) * | 1998-10-20 | 2001-05-22 | United States Surgical Corporation | Absorbable polymers and surgical articles fabricated therefrom |
| US6794485B2 (en) * | 2000-10-27 | 2004-09-21 | Poly-Med, Inc. | Amorphous polymeric polyaxial initiators and compliant crystalline copolymers therefrom |
| US6645618B2 (en) | 2001-06-15 | 2003-11-11 | 3M Innovative Properties Company | Aliphatic polyester microfibers, microfibrillated articles and use thereof |
| GB0202233D0 (en) * | 2002-01-31 | 2002-03-20 | Smith & Nephew | Bioresorbable polymers |
| US6890649B2 (en) * | 2002-04-26 | 2005-05-10 | 3M Innovative Properties Company | Aliphatic polyester microfibers, microfibrillated articles and use thereof |
| US7097850B2 (en) | 2002-06-18 | 2006-08-29 | Surmodics, Inc. | Bioactive agent release coating and controlled humidity method |
| US20030232087A1 (en) * | 2002-06-18 | 2003-12-18 | Lawin Laurie R. | Bioactive agent release coating with aromatic poly(meth)acrylates |
| US6794484B2 (en) * | 2002-06-28 | 2004-09-21 | Ethicon, Inc. | Crystallizable polylactone copolymers prepared from mono- and di-functional polymerization initiators |
| US6831149B2 (en) * | 2002-06-28 | 2004-12-14 | Ethicon, Inc. | Polymerization process using mono-and di-functional initiators to prepare fast crystallizing polylactone copolymers |
| KR100684682B1 (en) * | 2002-09-24 | 2007-02-22 | 아사히 가세이 케미칼즈 가부시키가이샤 | Glycolic Acid Copolymer and Method for Production Thereof |
| US7148315B2 (en) * | 2002-10-23 | 2006-12-12 | Ethicon, Inc. | Monomer addition techniques to control manufacturing of bioabsorbable copolymers |
| GB0329654D0 (en) | 2003-12-23 | 2004-01-28 | Smith & Nephew | Tunable segmented polyacetal |
| US20060083772A1 (en) * | 2004-04-06 | 2006-04-20 | Dewitt David M | Coating compositions for bioactive agents |
| CN1964748A (en) * | 2004-04-06 | 2007-05-16 | 苏莫迪克斯公司 | Coating compositions for bioactive agents |
| CA2563347C (en) | 2004-04-20 | 2014-01-14 | Genzyme Corporation | Surgical mesh-like implant |
| US8083805B2 (en) * | 2005-08-16 | 2011-12-27 | Poly-Med, Inc. | Absorbable endo-urological devices and applications therefor |
| CA2679365C (en) | 2006-11-30 | 2016-05-03 | Smith & Nephew, Inc. | Fiber reinforced composite material |
| JP5416090B2 (en) | 2007-04-18 | 2014-02-12 | スミス アンド ネフュー ピーエルシー | Expansion molding of shape memory polymer |
| US9770534B2 (en) | 2007-04-19 | 2017-09-26 | Smith & Nephew, Inc. | Graft fixation |
| EP2142227B1 (en) | 2007-04-19 | 2012-02-29 | Smith & Nephew, Inc. | Multi-modal shape memory polymers |
| US20090004253A1 (en) * | 2007-06-29 | 2009-01-01 | Brown Laura J | Composite device for the repair or regeneration of tissue |
| US8968362B2 (en) | 2010-04-08 | 2015-03-03 | Covidien Lp | Coated looped suture |
| US8858980B2 (en) * | 2012-04-12 | 2014-10-14 | Poly-Med, Inc. | Synthetic mechanical hemostatic composition, method of making and use thereof |
| WO2016100915A2 (en) * | 2014-12-19 | 2016-06-23 | Poly-Med, Inc. | Absorbable copolymers with improved thermal stability |
| EP3085820B1 (en) | 2015-04-22 | 2017-12-20 | Sofradim Production | A method for forming a barbed suture and the barbed suture thus obtained |
| EP3085332B1 (en) | 2015-04-23 | 2019-02-27 | Sofradim Production | Package for a surgical mesh |
| US9896560B2 (en) * | 2015-06-02 | 2018-02-20 | Ethicon, Inc. | Lyophilized foams of end block containing absorbable polymers |
Family Cites Families (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4653497A (en) * | 1985-11-29 | 1987-03-31 | Ethicon, Inc. | Crystalline p-dioxanone/glycolide copolymers and surgical devices made therefrom |
| US4838267A (en) * | 1988-02-12 | 1989-06-13 | Ethicon, Inc. | Glycolide/p-dioxanone block copolymers |
| US5076807A (en) * | 1989-07-31 | 1991-12-31 | Ethicon, Inc. | Random copolymers of p-dioxanone, lactide and/or glycolide as coating polymers for surgical filaments |
| US5080665A (en) * | 1990-07-06 | 1992-01-14 | American Cyanamid Company | Deformable, absorbable surgical device |
| US5225520A (en) * | 1991-04-17 | 1993-07-06 | United States Surgical Corporation | Absorbable composition |
| US5403347A (en) * | 1993-05-27 | 1995-04-04 | United States Surgical Corporation | Absorbable block copolymers and surgical articles fabricated therefrom |
| US5470340A (en) * | 1993-10-06 | 1995-11-28 | Ethicon, Inc. | Copolymers of (p-dioxanone/glycolide and/or lactide) and p-dioxanone |
-
1995
- 1995-06-30 US US08/497,127 patent/US5633343A/en not_active Expired - Lifetime
-
1996
- 1996-06-19 AU AU56085/96A patent/AU5608596A/en not_active Abandoned
- 1996-06-27 JP JP18536996A patent/JP3556773B2/en not_active Expired - Lifetime
- 1996-06-27 CA CA002180063A patent/CA2180063A1/en not_active Abandoned
- 1996-06-28 ZA ZA9605537A patent/ZA965537B/en unknown
- 1996-07-01 BR BR9602945A patent/BR9602945A/en not_active Application Discontinuation
- 1996-07-01 EP EP96304849A patent/EP0751165A3/en not_active Withdrawn
Also Published As
| Publication number | Publication date |
|---|---|
| US5633343A (en) | 1997-05-27 |
| AU5608596A (en) | 1997-01-09 |
| EP0751165A3 (en) | 1997-06-11 |
| EP0751165A2 (en) | 1997-01-02 |
| ZA965537B (en) | 1997-12-29 |
| BR9602945A (en) | 1998-04-28 |
| JPH0912689A (en) | 1997-01-14 |
| JP3556773B2 (en) | 2004-08-25 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued |