MODIFICATION OF POLYGLYCOLIC ACID TO ACHIEVE VARIABLE IN-VIVO PHYSICAL PROPERTIES

Abstract: A mixture is described having up to about 50% by weight of an inert filler and a polymer. The polymer is subject to hydrolytic degradation into non-toxic, tissue-­ compatible absorbable components, The polymer has a glycolic acid ester linkage. The mixture is useful in the manufacture of a surgical article or element. A method is also described for achieving variable in­ vivo physical properties of a polymer. The polymer is subject to hydrolytic degradation into non-toxic, tissue-­ compatible absorbable components. The polymer has a glycolic acid ester linkage. A method is also described for achieving variable in-vivo physical properties of a mixture. The mixture has up to about 50% by weight of an inert filler and the above polymer. The method comprises subjecting the polymer or the mixture to hydrolytic treatment and recovering the modified polymer or mixture. The modified polymer or mixture is useful in the manufacture of a surgical article or element.

Description: MODIFICATION OF POLYGLYCOLIC ACID TO ACHIEVE VARIABLE IN-VIVO PHYSICAL PROPERTIES This invention relates to polyglycolie acid blended with suitable fillers or extenders.to achieve variable, in-vivo physical properties. This invention also relates to a method of achieving variable in-vivo physical properties of filled or unfilled polyglycolic acid. The method com prises subjecting the polyglycolic acid to hydrolytic degradation. Unmodified polyglycolic acid maintains its in tegrity for about twenty eight days. In certain surgical uses, e.g. in the colon, the rate of healing is rapid. It is desirable for the surgical implant to disintegrate following the wound healing period. An implanted surgical element may need a re latively high initial tensile strength followed by a rela tively rapid loss of strength and/or disintegration rate. For example, in a gastro-intestinal anastomosis device, a relatively high initial tensile strength is required but disintegration and passage of device fragments should occur in about 8 to 15 days. The filled polyglycolic acid or the method of this invention addresses this need. The filled polygly colic acid or the polyglycolic acid obtained by the method of this invention is suitable for a variety of surgical uses. The rate of strength loss and the disintegration can be altered by chemical and/or physical modification. The advantages of the modified polyglycolide acid of this invention are not known in the prior art. One advantage is the relatively closer control of the modified polyglycolic acid properties, specifically the strength and in-vivo degradation properties. The properties can be controlled by the use of various fillers, for example, barium sulfate and various concentrations of the fillers. The properties can also be controlled by lowering the intrinsic viscosity of the filled or unfilled polyglycolic acid. This can be accomplished by treating the filled or unfilled polyglycolic acid with dilute or concentrated ammonia or by subjecting it to hydrolytic degradation, for example, by distilled water, boiling, soaking or steam treatment. A range of tensile strengths and disintegration rates can thus be obtained. The time and temperature of the ammonia treatment and/or the hydrolytic degradation will determine the initial tensile strength and rate of degradation of the filled or filled polyglycolic acid. Thus, depending on the surgical need, e.g. a staple, a hemostat, a bowel anastomosis ring and the like, a surgeon has available a degradable polymer with a variable range of in-vivo physical properties. Besides tensile strength and degradation rate, a filler can also change the fracture properties, compression strength, elongation, elastic modulus and/or creep properties of polyglycolic acid for other surgical uses. Another advantage of the modified polyglycolic acid (PGA) of this invention is the degradation pattern. The fragments of the filled PGA are relatively small, for example some fragments are on the order of magnitude of about one-sixteenth of an inch. Also, the fractured particles are relatively soft and less sharp, thus reducing the risk of trauma to adjacent tissue. A filler such as barium sulfate does not significantly adhere to the PGA and therefore tends to effect a uniform breakup of the modified PGA. The lack of adherence develops numerous points of weakness in the material. Also, physiological forces may tend to enhance the fracture pattern. Finally, by the use of the mixture and/or method of this invention, the physical properties of the filled or unfilled PGA can be closely matched to the physiological requirements of the surgical procedure or repair. In summary, the advantages of the modified PGA of this invention are a relatively closer control of the physical properties; a smaller particle on fracturing; and a softer particle on fracturing. These advantages are seen in specific surgical uses, e.g. in a gastro-intestinal anastomosis device and in a surgical staple, where the modified PGA can be used to manufacture an improved surgical element. Still other advantages are obtained from the modified PGA. Another advantage is that the in-vivo strength of the modified PGA can be maintained up to at least 14 days. Still another advantage is that the physical properties of the modified PGA can be changed for tissues which heal rapidly, for example, in the bowel. A device can now be manufactured using the modified PGA which has relatively high tensile strength on implant but which rapidly loses its strength with time. The device then breaks down into beads and is either absorbed or passed by the body. A mixture comprising up to about 50% by weight of an inert filler and a polymer which is subject to hydrolytic degradation into non-toxie, tissue-compatible absorbable components, the polymer having a glycolic acid ester linkage, has been invented. In one embodiment, the filler is up to about 40% by weight. In another embodiment, the filler is between about 20 and 25% by weight. In still another embodiment, the filler is selected from the group consisting of barium sulfate, calcium carbonate, tricalcium phosphate, magnesium oxide, glass spheres and nonpolyglycolic acid fibers. In yet another embodiment, the filler is barium sulfate. Finally, in another embodiment the filler is tricalcium phosphate. A method of achieving variable in-vivo physical properties of a polymer which is subject to hydrolytic degradation into non-toxic, tissue-compatible absorbable components, the polymer having a glycolic acid ester linkage, or of a mixture having up to about 50% by weight of an inert filler and the polymer has also been invented. The method comprises subjecting the polymer or the mixture to hydrolytic treatment and recovering a modified polymer mixture. In one embodiment the hydrolytic treatment is by boiling. In another embodiment the hydrolytic treatment is by steam treatment. In still another embodiment, the hydrolytic treatment is by autoclaving. In one embodiment the subjecting step contains the additional step of subjecting the polymer or the mixture to irradiation degradation. In another embodiment, the subjecting step contains the additional step of subejecting the polymer or the mixture to re-pelletizing. In one embodiment, the filler is up to about 40% by weight. In another embodiment, the filler is between about 20 and 25% by weight. In still another embodiment, the filler is selected from the group consisting of barium sulfate, calcium carbonate, tricalcium phosphate, magnesium oxide, glass spheres and nonpolyglycolic acid fibers. In yet another embodiment, the filler is barium sulfate. Finally, in another embodiment, the filler is tricalcium phosphate. In one embodiment the polymer is a homopolymer. In another embodiment, the polymer is polyglycolic acid. In still another embodiment, the polymer is a copolymer. In yet another embodiment, when the polymer is a copolymer, one of the polymer is polyglycolic acid. In other embodiments when the polymer is a copolymer and one of the polymers is polyglycolic acid, the other polymer is obtained from the group consisting of lactides, lactones, oxylates or carbonates. In another embodiment, the lactide is polylactic acid. In still another embodiment, the lactone i s is epsilon-caprolactone. In yet another embodiment, the oxylate is ethylene oxylate. In still yet another embodiment, the carbonate is trimethylene carbonate. Fonally, in another embodiment, when the polymer is a copolymer and one of the polymers is polyglycolic acid, the other polymer is 1,4-dioxonone. A surgical clip, a surgical staple, a bone prosthesis, a bone prosthesis wherein the prosthesis is a mandible prosthesis, a tubular implant, a tubular stenotic device, and a tubular support manufactured from a mixture comprising up to about 50% by weight of an inert filler and a polymer which is subject to hydrolytic degradation into non-toxic, tissue-compatible absorbable components, the polymer having a glycolic acid ester linkage, has also been invented. The manufacture of these surgical articles is by conventional means and/or processes known in the art. In one embodiment, the filler is up to about 40% by weight. In another embodiment, the filler is between about 20 and 25% by weight. In still another embodiment, the filler is selected from the group consisting of barium sulfate, calcium carbonate, tricalcium phosphate, magnesium oxide, glass spheres and nonpolyglycolic acid fibers. In yet another embodiment, the filler is barium sulfate. In an alternative to these embodiments, when the polymer is a copolymer, one of the polymers is polyglycolic acid. In one embodiment, the polymer is a copolymer. In another embodiment, when the polymer is a copolymer, one of the polymers is polyglycolic acid. A surgical package has also been invented. The package comprises a sterile enclosure and therein a clip, a staple, a bone prosthesis, or a tubular implant, stenotic device or support. The method of loading the article into the package, and then sterilizing the article and package can be by conventional means and/or processes known in the art. Description of the Preferred Embodiment In the preferred embodiment, the polymer is homopolymeric or copolymeric glycolic acid. In one embodiment, the filler is barium sulfate. Other absorbable or non-absorbable fillers, such as calcium carbonate, tricalcium phosphate, magnesium oxide, glass spheres, and non-PGA fibers may be useful. A filler level from about 25 to 40% by weight is one embodiment. However, it is to be understood that if no filler is used, the PGA must be hydrolytically treated, e.g. by boiling, soaking or steam treatment to obtain the modified properties. A filler level greater than 50 by weight may also be within the scope of this invention. Different tupes, times and temperatures of hydrolytic treatment are within the scope of this invention. A boiling time of about 30 minutes at about 1000 C may achieve the desired modified properties for many surgical uses. However, shorter or longer times and lower, and even higher, temperatures may be useful in achieving desired modified properties. Also, alternatives to hydrolytic treatment, e.g. irradiation and/or re-running the polymer through an extruder and subsequently re-pelletizing it to obtain a lower inherent viscosity are within the scope of this invention. If increased tensile strength is required, a coupling compound can be used to more firmly adhere the filler to the PGA. Such a coupling compound is a silane. A coupling compound may be useful in hard tissue repair, e.g. in bone fractures, preferably with an absorbable filler. The medical uses of the modified polyglycolic acid of this invention include, but are not necessarily limited to: 1. Solid Products, molded or machined, such as: a. Orthopedic prosthetics, e.g. pins, clamps, screws, intermedullary rods and compression plates b. Clips c. Staples d. Hooks, buttoms, snaps and fasteners e. Bone substitutes (e.g. mandible prosthesis) f. Tubular implants, stenotic devices or supports 2. Fibrillar Products, knitted or woven, in cluding velours, such as: a. Facial substitutes b. Gauze, fabric, sheet, felt or spong c. Sutures, including ligatures 3. Miscellaneous, such as: a. foam as absorbable prosthesis b. Substitute for wire in fixations In combination with other components, such as: 1. Solid Products, molded or machines, e.g. reinforced bone pins, etc. 2. Fibrillar Products The following examples more fully describe the mixture and method of this invention. EXAMPLE 1 The following example relates to the preparation of polyglycolic acid (PGA), or polyglycolic acid filled with 20%, 22.5$, 25% and 40% barium sulfate. PGA in pellet form can be injection molded without preprocessing steps 1. to 3. 1. Material Preparations 1.1 Grinding- PGA in pellet form is ground into 2 mm particles. The ground PGA is then stored in plastic bags in a dry cabinet at 70 F with less than 50 ppm H20 until it is mixed with the BaSO4. 1.2 Mixing The ground PGA is mixed with BaSO4 using con ventional techniques for mixing powders. 1.3 Polymer Drying After. mixing, the polymer blend is vacuum dried by maintaining a temperature of l200C with a vacuum of less than 10 mmHg for six hours. Dry nitrogen at 10 SCFH is run through the polymer. 2. Melt Blending Additional mixing of the PGA/BaS04 blend is accomplished by melt blending the polymer using conventional techniques at a temperature of 2700 C. The resultant blended material is then cooled to ambient temperature under dry conditions of less than 50 ppm H20 for 4 hours. 3. Granulation After the blended material is cooled to ambient temperature, it is granulated into less than 5 mm particles, redried and vacummed sealed in cups. 4. Molding Conditions The PGA or PGA/BaSO4 blend is injection molded into bowel anastomosis rings using conventional molding techniques. Typical molding conditions are: Temperature : 235 C Pressure : 600-1000 psi Cycle Time : 1 min. Injection time : 55 sec. Molding time : 1G-15 sec. 5. Post Molding Treatments The molded device is subjected to the following post treatment conditions. 5.1 Annealing- 110 C with a vacuum of less than 1 ml. of Hg for 3 hours. 5.2 Etching- Placed in boiling H20 for 30 minutes, cooled and then dried in methanol for 2 1/2 hours, followed by drying in a vacuum oven at 500C and less than 1 ml. of Hg for 30 minutes. 6. Sterilization The packaged post treated device is subjected to a gas chamber sterilization employing a sterilant mixture containing ethylene oxide with a diluent such as freon. A typical sterilization cycle is described below: Temperature 300C Pre-Vacuum 26" of Hg RH 20% Gas EO/Freon in a 12/88 ratio Pressure 20 PSIG EO Concentration 11100 mg/L Exposure 7 hours Post Vacuum 26" of Hg EXAMPLE 2 Various samples of a bowel anastomosis ring (BAR) were prepared using the mixtures of Example 2. The preparation of the BAR is described in a U.S. patent application Serial No. 198,448 filed October 20, 1980 in the names of A. L. Kaganov, T. G. Hardy and W.G. Pace. This application is incorporated herein by reference. The hydrolytic treatment was a 30 minute distilled water boil. All of the samples were 28 mm in diameter. The percent barium sulfate and implant subject were as follows: Sample¯No. % BaS04 Implant Subject 1 22.5 Beagle 2 22.5 3 22.5 4 22.5 5 22.5 1? 6 0 40 7 40 Foxhound 8 25 Procedure Prior to anesthetic induction, the animals received an enema and routine preinduction sedication. Under aseptic conditions a low midline laparotomy was made. The descending colon was mobilized and the mesenteric blood vessels supplying a selected segment were doubly ligated and transected. Purse-string sutures were placed proximally and distally to the devascularized colon segment using two purse-string bowel clamps that had been appropriately placed. The colon segment between the clamps was resected flush with the clamps and the segment was discarded. For implantation of the BAR, the proximal clamp was removed first and the colonic stoma triangulated, cleansed with warm saline and dilated. One ring of the BAR was inserted into the proximal stoma and the purse -string suture tied to secure the colon to the BAR struts. This procedure was then repeated to insert the other BAR ring into the distal stoma. Care was taken to align the mesentery- during the BAR insertion procedures. The BAR rings were closed (forced closer together) using finger pressure on the colon serosa. The anastomosis was inspected to insure adequate serosa to serosa to serosa approximation around the circumference of the BAR. When necessary, stitches were taken to insure the adequacy of the purse-string suture and/or the approximation of the serosa to serosa union. When the anastomoses were completed, the colons were replaced and the laparotomles closed in three layers. The dogs were returned to cages and treated with routine post-operative antibiotics. The Beagles were given milk only on the first and second post-operative days. From days 3 to 17, they were fed canned dog food mixed with milk. Water was available at all times. Fecal material were fluoroscoped daily, except weekends. all five Beagles were sacrificed on the 17th post-operative day and anastomotic healing assessed. The Foxhounds were fed intravenously for seven days post-operatively. Radiographs were made daily. Fecal material was examined when warranted. Results The 40% BaSO4' filled BAR implanted in the Beagle began to fragment between the 4th and 7th post-operative day and had been completely excreted by the 12th day. In the Foxhound, the 40% filled BAR had been excreted by the 6th day. The rings of the 22.5% and 25% BASS4 filled BAR separated as early as the 6th post-operative day and began fragmenting between the 8th and 11th post -operative days. BAR fragemtns were found in the fecal material from day 8 through day 16. In no instance were BAR fragments found in the colon in those animals sacrificed on day 17. Gross examination of the Beagles at autopsy showed excellent serosal healing with a thin band of scar tissue formation. The mucosae of the anastomoses ranged from barely perceptible to moderately indurated and slightly hyperemic. Recovered BAR fragments from all the samples were hard and very brittle. When pressed between the fingers, the fragments crumbled easily.

Claims: CLAIMS: 1. A mixture comprising up to about 50% by weight of an inert filler and a polymer which. is subject to hydrolytic degradation into non-toxic, tissue-com- patible absorbable components, said polymer having a glycolic acid ester linkage. 2. A method of achieving variable in-vivo physical properties of a polymer which is subject to hydrolytic degradation into non--toxic, tissue-compatible absorbable components, said polymer having a glycolic acid ester linkage,-or of a mixture having up to about 50% by weight of an inert filler and said polymer,comprising subjecting said polymer or said mixture to hydrolytic treatment and recovering a modified polymer or mixture. 3. A method of Claim 2 wherein said hydrolytic treatment is selected from the group consisting of boiling, steam treatment and autoclaving. 4. A method of Claim 2 wherein said subjecting step contains the additional step of subjecting said polymer or said mixture to irradiation degradation. 5. A method of Claim 2 wherein said subjecting step contains the additional step of subjecting said polymer or said mixture to re-pelletizing. 6. A mixture of Claim I or a method of Claim 2 wherein said filler is up to about 40%by weight. 7. A mixture or a method of Claim 6 wherein said filler is between about 20 and 25% by weight. 8. A mixture of Claim 1, or a method of Claim 2, or a mixture or a method of Claim 6 or 7 wherein said filler is selected from the group consisting of barium sulfate, calcium carbonate, tricalcium phosphate, magnesium oxide, glass spheres and nonpolyglycolic acid fibers.. 9. A mixture or a method of Claim 8 wherein said filler is barium sulfate. 10. A mixture or a method of Claim 8 wherein said filler is tricalcium phosphate. 11. A mixture of Claim 1 or a method of Claim 2 wherein said polymer is a homopolymer. 12. A mixture or a method of Claim 9 or 11 wherein said polymer is polyglycolic acid. 13. A mixture of Claim 1 or a method of Claim 2 wherein said polymer is a copolymer. 14. A mixture or a method of Claim 9 or 13 wherein one of the polymers is polyglycolic acid. 15. A mixture or a method of Claim 14 wherein one of the polymers is polyglycolic acid and the other polymer is poly(l4-dioxonone). 16. A mixture or a method of Claim 14 wherein one of the polymers is polyglycolic acid and the other polymer is obtained from the group consisting of lactides, lactones, oxylates or carbonates 17. A mixture or a method of Claim 16 wherein the lactide is polylactic acid or the lactone is epsilon -caprolactone or the oxylate is ethylene oxylate. 18. A mixture or a method of Claim 16 wherein the carbonate is trimethylene carbonate. 19. A surgical product selected from the group consisting of a surgical clip, a surgical staple, a bone prosthesis, a tubular implant, a tubular stenotic device, or a tubular support manufactured from a mixture of Claim or or a method of Claim 2, or a mixture or a method of Claim 9 or 14. 20. A product of Claim 19 wherein said bone prosthesis is a mandible prosthesis. 21. A surgical package comprising a sterile enclosure and therein a product of Claim 19 or 20.

Inventors: BUDRIS, JOHN PETER, KAGANOV, ALAN LAWRENCE, RITTER, THOMAS ALEXANDER
Applicants: AMERICAN CYANAMID COMPANY
Application year: 1981
Main classification: C08L67
IPC codes: A61L27, C08K3, A61L31