CA1124444A - Addition copolymers of lactide and glycolide and method of preparation - Google Patents
Addition copolymers of lactide and glycolide and method of preparationInfo
- Publication number
- CA1124444A CA1124444A CA306,056A CA306056A CA1124444A CA 1124444 A CA1124444 A CA 1124444A CA 306056 A CA306056 A CA 306056A CA 1124444 A CA1124444 A CA 1124444A
- Authority
- CA
- Canada
- Prior art keywords
- lactide
- glycolide
- percent
- copolymer
- polymer
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- 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
-
- 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
- C08G63/02—Polyesters derived from hydroxycarboxylic acids or from polycarboxylic acids and polyhydroxy compounds
- C08G63/06—Polyesters derived from hydroxycarboxylic acids or from polycarboxylic acids and polyhydroxy compounds derived from hydroxycarboxylic acids
- C08G63/08—Lactones or lactides
Abstract
ABSTRACT
Relatively high molecular weight, fiber-forming, crystalline copolymers of lactide and glycolide are prepared in a two-stage polymerization process. In the first stage there is prepared a random copolymer of a major proportion of an opti-cally active lactide with a minor proportion of glycolide or d,l-lactide. In the second stage, a major amount of glycolide and a minor amount of lactide monomers are admixed with the co-polymer of the first stage and the polymerization resumed until there is obtained a high molecular weight addition copolymer of lactide and glycolide containing from about 50 to 75 wt percent of units derived from glycolide. The polymer is fiber-forming and useful in the preparation of absorbable surgical sutures.
Relatively high molecular weight, fiber-forming, crystalline copolymers of lactide and glycolide are prepared in a two-stage polymerization process. In the first stage there is prepared a random copolymer of a major proportion of an opti-cally active lactide with a minor proportion of glycolide or d,l-lactide. In the second stage, a major amount of glycolide and a minor amount of lactide monomers are admixed with the co-polymer of the first stage and the polymerization resumed until there is obtained a high molecular weight addition copolymer of lactide and glycolide containing from about 50 to 75 wt percent of units derived from glycolide. The polymer is fiber-forming and useful in the preparation of absorbable surgical sutures.
Description
8ACKG~OUND OF THE INVENTION
Field of the Invention This invention relates to synthetic absorbable sutures, and more particularly, to sutures prepared from a novel polymer derived from lactide and glycolide.
Description of the Prior Art Homopolymers and copolymers of lactide and glycolide are well-known in the preparation of synthetic absorbable sutures as disclosed, for exam~le, in U.S. Patent Nos. 3,636,956,
Field of the Invention This invention relates to synthetic absorbable sutures, and more particularly, to sutures prepared from a novel polymer derived from lactide and glycolide.
Description of the Prior Art Homopolymers and copolymers of lactide and glycolide are well-known in the preparation of synthetic absorbable sutures as disclosed, for exam~le, in U.S. Patent Nos. 3,636,956,
2,703,316, 3,468,853, and 3,565,869. Preferred polymers are polyglycolide or copolymers of glycolide with L(-)-lactide which are highly crystalline, fiber-forming materials that can be ex-truded into fibers and have good physical properties and reason-able absorption times when implanted in living animal tissue.
Copolymers of lactide and glycolide for use in the prep-aration of surgical sutures are presently limited to a narrow range of compositions, namely, those copolymers which contain about 80 percent by weight glycolide. ~andom copolymers :~`
~J~
ETH-Ç28 ~3 2~ t containing less than about 80 percent glycolide to about 40 percent glycolide are found to be of low crystallinity, and sutures prepared from such polymers are characterized by low tensile strength and poor strength retention in living animal tissue. Polymers containing less than about 40 percent by weight glycolide and up to 100 percent lactide are fiber-forming and result in strong suture materials, but tensile strength reten-tion and/or the rate of absorption of such sutures in living animal tissue is typically less than desired.
It is an object of the present invention to provide co-polymers of lactide and glycolide having less than about 75 per-cent by weight glycolide which are nevertheless highly crystal-line, fiber-forming materials. It is another object of this invention to provide absorbable sutures comprised of a copolymer of lactide and glycolide containing less than about 75 percent glycolide. It is a further object of this invention to provide a method for preparing highly crystalline polymers of lactide and glycolide containing from about 50 percent to 75 percent by weight glycolide.
SU~RY
In accordance with the present invention, highly crys-talline, fiber-forming addition copolymers of lactide and glyco-lide having from 50 percent to 75 percent by weight glycolide are obtained by first preparing a copolymer containing at least about 60 percent lactide, and thereafter admixing that polymer with z~
additional lactide and glycolide monomers and resuming the poly-merization to obtain the final polymer product. The ratio of lactide to glycolide monomers in the second stage of the poly-merization is selected to provide a final polymer product having the desired composition of from about 50 percent to 75 percent by weight glycolide.
By the method of the present invention there are ob-tained lactide-glycolide addition copolymers which are highly crystalline and useful in forming fibers for surgical sutures.
Sutures prepared from such polymers have significantly higher ' initial tensile strength and better tensile strength retention in living anirnal tissue than sutures prepared from random co-polymers of similar molar composition.
More particularly the present invention relates to a method for preparing a crystalline copolymer of lactide and `- glycolide containing from 50 to 75 wt percent glycolide which comprises: a. preparing a random copolymer comprising a major - portion of an optically active lactide and a minor portion of a monomer selected from the group consisting of glycolide and d,l-lactide, and b. admixing with said random copolymer addi-tional monomers comprising from 70 to 90 wt percent glycolide and 10 to 30 wt percent of an optically active lactide, the quantity of glycolide being sufficient to provide from 50 to 75 wt percent glycolide in the polymer-monomer mixture, and c.
polymerizing said polymer-monomer mixture to obtain said crystalline copolymer of lactide and glycolide, said copolymer having an inherent viscosity determined as a 0.1% solution in hexafluoroisopropanol at 25C of at least about 1.20, a melt-ing point of at least about 160C and a crystallinity of at least about 15~/o. The invention also relates to the copolymer obtained thereby and the synthetic absorbable suture compris-ing at least Gne drawn and oriented filament of such copolymer.
.
. .
zL~
DESCRIPTION OF DRAWINGS
Figure 1 is a perspective view of a needle-suture combination, Figure 2 is a perspective view of a needle-suture combination within a hermetically sealed container, ' Figure 3 illustrates a screw machined from the poly-mer of the present invention, Figure 4 is a cross-sectional view of a composite ;; yarn containing filaments of different composition, and Figure 5 is a plan view of a surgical fabric knitted from fibers of the present invention.
DESCRIPTION OF PREFERRED EMBODIMENTS
In che following description and examples, all parts and percentages are by weight unless otherwise specified.
The method of the present invention comprises a two-stage polymerization process. In the first stage there is a random copolymerization of an optically active lactide and glycolide monomers with the lactide component comprising at least about 60% of the monomer mixture. The polymerization is carried out in a conventional manner using a polymerization reactor equipped with heating and stirring means and in the presence of a polymerization catalyst such as stannous octoate The polymerization is conducted with pure and dry reactants and under an atmosphere of dry nitrogen at temperature suffic-ient to maintain the reaction mixture in a molten state until the polymerization is complete. Random polymerization of lac-tide-glycolide copolymers is described in U.S. Patent Nos.
Copolymers of lactide and glycolide for use in the prep-aration of surgical sutures are presently limited to a narrow range of compositions, namely, those copolymers which contain about 80 percent by weight glycolide. ~andom copolymers :~`
~J~
ETH-Ç28 ~3 2~ t containing less than about 80 percent glycolide to about 40 percent glycolide are found to be of low crystallinity, and sutures prepared from such polymers are characterized by low tensile strength and poor strength retention in living animal tissue. Polymers containing less than about 40 percent by weight glycolide and up to 100 percent lactide are fiber-forming and result in strong suture materials, but tensile strength reten-tion and/or the rate of absorption of such sutures in living animal tissue is typically less than desired.
It is an object of the present invention to provide co-polymers of lactide and glycolide having less than about 75 per-cent by weight glycolide which are nevertheless highly crystal-line, fiber-forming materials. It is another object of this invention to provide absorbable sutures comprised of a copolymer of lactide and glycolide containing less than about 75 percent glycolide. It is a further object of this invention to provide a method for preparing highly crystalline polymers of lactide and glycolide containing from about 50 percent to 75 percent by weight glycolide.
SU~RY
In accordance with the present invention, highly crys-talline, fiber-forming addition copolymers of lactide and glyco-lide having from 50 percent to 75 percent by weight glycolide are obtained by first preparing a copolymer containing at least about 60 percent lactide, and thereafter admixing that polymer with z~
additional lactide and glycolide monomers and resuming the poly-merization to obtain the final polymer product. The ratio of lactide to glycolide monomers in the second stage of the poly-merization is selected to provide a final polymer product having the desired composition of from about 50 percent to 75 percent by weight glycolide.
By the method of the present invention there are ob-tained lactide-glycolide addition copolymers which are highly crystalline and useful in forming fibers for surgical sutures.
Sutures prepared from such polymers have significantly higher ' initial tensile strength and better tensile strength retention in living anirnal tissue than sutures prepared from random co-polymers of similar molar composition.
More particularly the present invention relates to a method for preparing a crystalline copolymer of lactide and `- glycolide containing from 50 to 75 wt percent glycolide which comprises: a. preparing a random copolymer comprising a major - portion of an optically active lactide and a minor portion of a monomer selected from the group consisting of glycolide and d,l-lactide, and b. admixing with said random copolymer addi-tional monomers comprising from 70 to 90 wt percent glycolide and 10 to 30 wt percent of an optically active lactide, the quantity of glycolide being sufficient to provide from 50 to 75 wt percent glycolide in the polymer-monomer mixture, and c.
polymerizing said polymer-monomer mixture to obtain said crystalline copolymer of lactide and glycolide, said copolymer having an inherent viscosity determined as a 0.1% solution in hexafluoroisopropanol at 25C of at least about 1.20, a melt-ing point of at least about 160C and a crystallinity of at least about 15~/o. The invention also relates to the copolymer obtained thereby and the synthetic absorbable suture compris-ing at least Gne drawn and oriented filament of such copolymer.
.
. .
zL~
DESCRIPTION OF DRAWINGS
Figure 1 is a perspective view of a needle-suture combination, Figure 2 is a perspective view of a needle-suture combination within a hermetically sealed container, ' Figure 3 illustrates a screw machined from the poly-mer of the present invention, Figure 4 is a cross-sectional view of a composite ;; yarn containing filaments of different composition, and Figure 5 is a plan view of a surgical fabric knitted from fibers of the present invention.
DESCRIPTION OF PREFERRED EMBODIMENTS
In che following description and examples, all parts and percentages are by weight unless otherwise specified.
The method of the present invention comprises a two-stage polymerization process. In the first stage there is a random copolymerization of an optically active lactide and glycolide monomers with the lactide component comprising at least about 60% of the monomer mixture. The polymerization is carried out in a conventional manner using a polymerization reactor equipped with heating and stirring means and in the presence of a polymerization catalyst such as stannous octoate The polymerization is conducted with pure and dry reactants and under an atmosphere of dry nitrogen at temperature suffic-ient to maintain the reaction mixture in a molten state until the polymerization is complete. Random polymerization of lac-tide-glycolide copolymers is described in U.S. Patent Nos.
3,639,956 and 3,792,010, particularly Example XVII and VIII
thereof respectively.
The second stage of the polymerization method of the present invention consists of further polymerizing the polymer 3 ~ . 2 ~
of the first stage with additional lactide and glycolide mono-mer. In one embodiment, the polymer product of the first stage is solidified by cooling, then ground and dried under vacuum.
The ground polymer is intimately admixed with additional amounts of dry glycolide and optically active lactide monomer, the 5a -;
... . . .
~ 2'.~ 4 respective quantities of these monomers being selected to pro-vide a final polymer having from 50 to 75 percent glycolide.
The polymer-monomer mixture is charged into a poly-; merization reactor equipped with heating and stirring means, and the polymerization carried out under a dry nitrogen atmo-sphere using a procedure which is basically identical to that followed in the first stage. The temperature of the reactor is controlled to maintain the reactants in a molten state. Fol-lowing completion of the polymerization reaction, the polymer product is discharged, solidified by cooling, ground into a powder, and dried under vacuum.
As a permissible alternative polymer composition, the first stage polymerization may be of optically active L(-)-lactide or D(+)-lactide with optically inactive d,l-lactide to form a lactide copolymer. For purposes of clarity, the en-; suing description and example refer primarily to the polymeriza-tion of L(-)-lactide and glycolide in the first stage, but it is understood that D(+)-lactide may be used in place of L(-)-lactide, and d,l-lactide may be used in place of glycolide.
As an alternative method, the second stage of the poly-merization process of the present invention may follow directly upon completion of the first stage by adding the re~uired lactide and glycolide monomers directly to the molten polymer obtained in the first stage. The final polymer product is thereby ob-tained by a semicontinuous process without the necessity for cooling and grinding the random copolymer product of the first stage. It is important, however, that the monomers be added ., ~ -6-~' .
~L~ Z~ 4 together as a mixture and that the stirring means in the reactor ; be capable of quickly and efficiently distributing the added monomers uniformly throughout the molten polymer.
While not wishing to be bound by theory, it is believed that the method of the present invention results in the lactide and glycolide monomers of the second stage grafting onto reactive end groups of the high lactide polymer of the first stage, to form a highly crystalline ordered copolymer having sequential units of high lactide and high glycolide polymers. It is be-lieved that the final product also contains small amounts ofother copolymers of various compositions and structures in solu-tion with the ordered copolymer. For the sa]se of convenience, the polymer products of the present invention are sometimes re-ferred to herein as "addition copolymers", it being understood that this term includes the sequential ordered copolymers as well ; as mixtures of such ordered copolymers with minor amounts of - other copolymers of lactide and glycolide.
The polymers of the present invention are generally ex-tractable with chloroform only to the extent of less than about 5 percent by weight. The polymers are thereby distinguished from simple mixtures of high lactide and high glycolide random co-polymers having the same relative lactide-glycolide composition since in such mixtures, the entire high lactide component is extractable. The low level of extractables in the polymers of the present invention suggest that only a minor proportion of the high lactide copolymer from the first stage of the reaction sur-vives the second stage without further polymerization.
'::
~. .
. ~ .
1~ 2~4'~
The high lactide random copolymer of the first stage reaction may contain from 60 percent to 90 percent optically active lactide, and from 10 percent to 40 percent glycolide or d,l-lactide. A particularly preferred composition is one con-taining from 65 percent to 75 percent lactide and 25 percent to 35 percent glycolide.
; The monomer mixture reacted in the second stage of the polymerization may contain from about 70 percent to 90 percent glycolide and 30 percent to 10 percent lactide. A particularly preferred composition is one containing from 80 percent to 90 percent glycolide.
The final copolymer product of the present invention may contain from about 50 percent to 75 percent glycolide and 50 per-cent to 25 percent lactide. A particularly preferred composition is one containing from 55 percent to 65 percent glycolide. The final copolymer is characterized by having an inherent viscosity of at least 1.20 as determined on a 0.1 percent solution of the `
polymer in hexafluoroisopropanol or chloroform at 25C, a melting point of at least about 160C,and a crystallinity of at least about 15 percent.
It is essential to the method of the present invention that the high lactide copolymer be prepared in the first stage, and the high glycolide monomer mixture be introduced in the second stage. If the reverse is attempted, the result is a low molecular weight, largely amorphous copolymer or mixture of co-polymers which is unsuitable for formation of strong, orientable fibers. In a like manner, random copolymers of lactide and . .~
;
-glycolide containing from about 50 percent to 75 percent glyco-lide are noncrystalline compositions and generally not desirable for the manufacture of surgical sutures.
The polymers of the present invention are melt extruded and drawn in accordance with conventional procedures to form filaments useful as surgical sutures. Sucn filaments are charac-terized by having a straight tensile strength and knot strength of at least about 40,000 psi and 30,000 psi respectively, straight tensile strength retention in vivo of at least about 40 percent after 14 days, and substantially complete absorption in vivo within about 120 days. The filaments are further char-acterized by a crystallinity of at least about 15 percent, and an inherent viscosity of at least about 1.0 as determined on a 0.1 percent solution in HFIP or CHC13 at 25C.
The method and product of the present invention is further illustrated by the following examples.
,., ~' - 70/30 Random Copolymer of L(-)-Lactide and Glycolide There is charged into a metal reactor provided with an agitator and a heating jacket 4180 g of pure dry L(-)-lactide (recrystallized from toluene), 1813 g of pure dry glycolide (dis-` 20 tilled and twice recrystallized from ethyl acetate), 12.2 ml of ` a 0.33 molar solution of stannous octoate in toluene,and 4.23 ml :.
` of a dioxane solution containing 0.1 g distilled diethylene . .
glycol per ml.
~ t~
The solvents are vaporized off and the charge is placed under an atmosphere of dry nitrogen. The temperature of the reactor is increased to 180C and maintained for 30 minutes.
The resulting copolymer is discharged as a viscous melt, cooled and ground to a fine powZer. The ground copolymer is dried under vacuum at 0.1 mm and at room temperature for 24 hours, and main-tained at 50C for an additional 24 hours. The copolymer is then cooled to ambient temperature and stored at 0.1 mm until used.
The polymerization conversion is determined to be 97.8 percent.
The polymerization product is a clear amber, relatively tough copolymer which is amorphous by X-ray determination. In-herent viscosity as determined on a 0.1 percent solution in chloroform at 25C is 1.66 dl/g.
35/65 Addition Copolymer of L(-)-Lactide and Glycolide Into a polymerization reactor is charged 59.5 g of the copolymer of Example 1, 10.9 g of pure L(-)-lactide, and 79.2 g of pure glycolide. The reaction mixture is placed under an atmosphere of dry nitrogen and heated with stirring to tempera-ture about 200C, and maintained at this temperature for 30 min-utes.
The resultant polymer is cooled, ground and dried at room temperature under 0.1 mm vacuum for 16 hours, and maintained at 70C for an additional 7 hours. The resulting light tan, ' tough, opaque copolymer has a crystalline melting point of 195-200C as determined by differential scanning calorimetry. In-herent viscosity as determined at 25C for~a 0.1 percent solution in hexafluoroisopropanol is 1.47 dl/g. The polymer exhibits 30 percent crystallinity as determined by X-ray diffraction.
Twenty-five grams of the polymer is charged into the barrel of a ~lodel 3211 Instron Rheometer fitted with a 40 mil die having an L/D of 24:1. The barrel had been preheated to a temperature of 210C. The polymer is extruded at the rate of 88 cubic centimeters per hour. The resulting filament is col-lected on a spoo:l at a speed which results in a diameter of about 20 mils. The filament is drawn six times at 60C to obtain a monofilament with a diameter of 9 mils having 64,000 psi straight tensile strength at break and 40,000 psi knot strength at break.
31/69 Addition Copolymer o' L(-)-Lactide and Glycolide Into a polymerization reactor is charged 35.6 g of pure dry L(-)-lactide, 15.4 g of pure dry glycolide, 0.11 ml of a 0.33 molar solution of stannous octoate in toluene and 0.036 g of pure crystalline glycolic acid. The reaction mixture is placed under an atmosphere of nitrogen and heated with stirring to a 20 temperature of 180C for 30 minutes and 200C for an additional 30 minutes.
To the clear, molten, viscous copolymer is added a mix-ture of 12.8 g of pure dry L(-)-lactide and 93 g of pure dry . -11-~3 2~9~
glycolide. The reaction mixture is again placed under an atmo-sphere of dry nitrogen and the temperature is increased to 210C.
Stirring is continued for approximately one hour.
The resulting polymer is discharged, cooled, ground and dried under 0.1 mm vacuum at room temperature for 24 hours. The resulting light tan, translucent, tough copolymer has an inherent viscosity as determined at 25C in hexafluoroisopropanol of 1.22 dl/g. The melting point is 194-202C as determined by Mettler hot stage microscopy and the polymer is birefringent and composed of small spherulites.
Twenty-~ive grams of copolymer is charged into the bar-rel of a Model 3211 Instron Rheometer fitted with a 30 mil die.
Polymer is extruded at 88 cc per hour at 204C. The properties of the resulting monofilament are stated in Table I.
90/10 Random Copolymer of L(-)-Lactide and DL-Lactide Into a polymerization reactor is charged 129.6 g of ;~ pure dry L(-)-lactide, 14.4 g of pure dry d,l-lactide, 0.6 ml of a 0.33 molar solution of stannous octoate in toluene, and 1.06 ml of dioxane solution containing 0.1 g/ml of glycolic acid.
; The solvents are removed by vaporization and the charge is placed ; 2 under an atmosphere of dry nitrogen. The charge is heated with stirring for 20 minutes at 180C, 20 minutes at 190C and 20 minutes at 210C. The resultant polymer is discharged, cooled, ground and dried. Inherent viscosity as determined in chloro-form at 25C is 1.80.
''~
~ 2~9~
E~LE 5 34/66 Addition Copolymer of Lactide and Glycolide Into a polymerization reactor is charged 34.4 g of the polymer prepared in Example 4, 12.4 g of pure dry L(-)-lactide, 89.8 g of pure dry glycolide and 0.91 ml of a dioxane solution containing 0.1 g/ml of glycolic acid. The charge is placed under an atmosphere of nitrogen and heated with stirring to 180C for 30 minutes and 200C for an additional 30 minutes. The ;; resulting polymer was discharged, cooled, ground and dried under vacuum at 0.1 mm and room temperature for 16 hours. The ground polymer is maintained under vacuum for an additional 6 hours at 80C and then cooled to ambient temperature. The inherent vis-cosity of the polymer determined at 25C on a 0.1 percent solu-.
tion in hexafluoroisopropanol is 1.78. The polymer has a melt-ing point of 196bC as determined by differential scanning calori-metry and a crystallinity of 21 percent as determined by X-ray diffraction.
Twenty-five grams of copolymer is charged into the bar-rel of a rheometer as in ~xample 3. The barrel is fitted with a 40 mil die and is preheated to 220C and the polymer is ex-truded at 88 cc per hour. The properties of the resulting mono-filament are given in Table I.
TABLE I
Example 3 Example 5 Extrusion temperature 204C 220C
Draw ratio 6x 6x Draw temperature 56C 66C
Diameter 8.0 mils 8.9 mils Straight tensile strength 65,000 psi 71,000 psi Knot tensile strength 49,000 psi 64,000 psi Elongation 58% 42%
; EXAMPLE 6 :
In Vivo Properties of Lactide/Glycolide Monofilaments Oriented monofilaments of lactide/glycolide addition copolymers of various compositions prepared in accordance with the previous examples are cut into 25-30 inch lengths and ; sterilized with ethylene oxide. Short lengths of the sterile fibers are implanted subcutaneously in rats to determine break-ing strength retention, and implanted intramuscularly to deter-mine the rate of absorption in accordance with conventional techniques for in vivo evaluation of absorbable sutures. The implanted fibers were recovered and evaluated after 7, 14 and 21 days. The compositions of the test fibers and the resultant data are given in Tables II and III. Comparative data is also pro-vided for a comparable lactide/glycolide random copolymer con-trol fiber to illustrate the poor strength retention of such d . . Z~
.
copolymers when utilized as surgical sutures. It is noted that tissue reaction is minimal in all cases.
t .
TABLE II
- % Breaking Strength Retention of Sterile Monofilaments of Lactide/Glycolide 5Copolymers Implanted in Rats Final lactide/glycolide Days postimplantation w/w ratio 7 14 21 .. . . .
25/75 Random 30 0 0 35/65 Addition 85 61 33 ' 10 40/60 Addition 82 57 14 50/50 Addition 86 68 56 '''~ .
:, .
~ TABLE III
:
Absorption of Sterile Monofilaments of Lactide/Glycolide Copolymers Implanted in Rats ,.~
~' 15Final lactide/glycolide% Suture area remaining w/w ratio 60 days 90 days 35/65 Addition 3 o 40/60 Addition 55- Traces - 50/50 Addition 62 14 - .
EXAMPLE ~
40/60 Addition Copolymer of L(-)-Lactide/Glycolide Into a polymerization reactor having a-nitrogen atmosphere is charged 2,332 g of L(-)-lactide, 805 g of glycolide, 19.1 ml 5 of a 0.33 molar solution of stannous octoate in toluene, and 2.197 g of glycolic acid, all reactants being pure and dry.
The reaction mixture was slowly heated with stirring to 200C
and maintained at 200C for 45 minutes. To the molten reaction mixture was t~en added with stirring, a mixture of monomers con-sisting of 468 g L(-)-lactide and 3,395 g glycolide. The temperature of the reaction mixture was slowly increased to 217C and maintained at this temperature for 45 minutes to com-plete the polymerization reaction.
The polymerization product was discharged from the reactor, solidified,ground and dried under vacuum for 24 hours.
The ground polymer was maintained at 90C under vacuum for ` 24 hours. The resulting copolymer had an inherent viscosity of 1.27 in hexafluoroisopropanol at 25C.
The copolymer was converted to a multifilament yarn utilizing a one inch diameter, vertical screw extruder equipped with a metering pump and a 10 hole 20 mil diameter spinneret.
The extruder temperature profile was established to obtain a polymer melt temperature of 440F at a point above the spinneret.
The polymer was rnelt spun into air and collected at a constant take-up speed at about 524 grams per hour. The yarn was drawn five times its original length over hot rolls maintained at 145F.
thereof respectively.
The second stage of the polymerization method of the present invention consists of further polymerizing the polymer 3 ~ . 2 ~
of the first stage with additional lactide and glycolide mono-mer. In one embodiment, the polymer product of the first stage is solidified by cooling, then ground and dried under vacuum.
The ground polymer is intimately admixed with additional amounts of dry glycolide and optically active lactide monomer, the 5a -;
... . . .
~ 2'.~ 4 respective quantities of these monomers being selected to pro-vide a final polymer having from 50 to 75 percent glycolide.
The polymer-monomer mixture is charged into a poly-; merization reactor equipped with heating and stirring means, and the polymerization carried out under a dry nitrogen atmo-sphere using a procedure which is basically identical to that followed in the first stage. The temperature of the reactor is controlled to maintain the reactants in a molten state. Fol-lowing completion of the polymerization reaction, the polymer product is discharged, solidified by cooling, ground into a powder, and dried under vacuum.
As a permissible alternative polymer composition, the first stage polymerization may be of optically active L(-)-lactide or D(+)-lactide with optically inactive d,l-lactide to form a lactide copolymer. For purposes of clarity, the en-; suing description and example refer primarily to the polymeriza-tion of L(-)-lactide and glycolide in the first stage, but it is understood that D(+)-lactide may be used in place of L(-)-lactide, and d,l-lactide may be used in place of glycolide.
As an alternative method, the second stage of the poly-merization process of the present invention may follow directly upon completion of the first stage by adding the re~uired lactide and glycolide monomers directly to the molten polymer obtained in the first stage. The final polymer product is thereby ob-tained by a semicontinuous process without the necessity for cooling and grinding the random copolymer product of the first stage. It is important, however, that the monomers be added ., ~ -6-~' .
~L~ Z~ 4 together as a mixture and that the stirring means in the reactor ; be capable of quickly and efficiently distributing the added monomers uniformly throughout the molten polymer.
While not wishing to be bound by theory, it is believed that the method of the present invention results in the lactide and glycolide monomers of the second stage grafting onto reactive end groups of the high lactide polymer of the first stage, to form a highly crystalline ordered copolymer having sequential units of high lactide and high glycolide polymers. It is be-lieved that the final product also contains small amounts ofother copolymers of various compositions and structures in solu-tion with the ordered copolymer. For the sa]se of convenience, the polymer products of the present invention are sometimes re-ferred to herein as "addition copolymers", it being understood that this term includes the sequential ordered copolymers as well ; as mixtures of such ordered copolymers with minor amounts of - other copolymers of lactide and glycolide.
The polymers of the present invention are generally ex-tractable with chloroform only to the extent of less than about 5 percent by weight. The polymers are thereby distinguished from simple mixtures of high lactide and high glycolide random co-polymers having the same relative lactide-glycolide composition since in such mixtures, the entire high lactide component is extractable. The low level of extractables in the polymers of the present invention suggest that only a minor proportion of the high lactide copolymer from the first stage of the reaction sur-vives the second stage without further polymerization.
'::
~. .
. ~ .
1~ 2~4'~
The high lactide random copolymer of the first stage reaction may contain from 60 percent to 90 percent optically active lactide, and from 10 percent to 40 percent glycolide or d,l-lactide. A particularly preferred composition is one con-taining from 65 percent to 75 percent lactide and 25 percent to 35 percent glycolide.
; The monomer mixture reacted in the second stage of the polymerization may contain from about 70 percent to 90 percent glycolide and 30 percent to 10 percent lactide. A particularly preferred composition is one containing from 80 percent to 90 percent glycolide.
The final copolymer product of the present invention may contain from about 50 percent to 75 percent glycolide and 50 per-cent to 25 percent lactide. A particularly preferred composition is one containing from 55 percent to 65 percent glycolide. The final copolymer is characterized by having an inherent viscosity of at least 1.20 as determined on a 0.1 percent solution of the `
polymer in hexafluoroisopropanol or chloroform at 25C, a melting point of at least about 160C,and a crystallinity of at least about 15 percent.
It is essential to the method of the present invention that the high lactide copolymer be prepared in the first stage, and the high glycolide monomer mixture be introduced in the second stage. If the reverse is attempted, the result is a low molecular weight, largely amorphous copolymer or mixture of co-polymers which is unsuitable for formation of strong, orientable fibers. In a like manner, random copolymers of lactide and . .~
;
-glycolide containing from about 50 percent to 75 percent glyco-lide are noncrystalline compositions and generally not desirable for the manufacture of surgical sutures.
The polymers of the present invention are melt extruded and drawn in accordance with conventional procedures to form filaments useful as surgical sutures. Sucn filaments are charac-terized by having a straight tensile strength and knot strength of at least about 40,000 psi and 30,000 psi respectively, straight tensile strength retention in vivo of at least about 40 percent after 14 days, and substantially complete absorption in vivo within about 120 days. The filaments are further char-acterized by a crystallinity of at least about 15 percent, and an inherent viscosity of at least about 1.0 as determined on a 0.1 percent solution in HFIP or CHC13 at 25C.
The method and product of the present invention is further illustrated by the following examples.
,., ~' - 70/30 Random Copolymer of L(-)-Lactide and Glycolide There is charged into a metal reactor provided with an agitator and a heating jacket 4180 g of pure dry L(-)-lactide (recrystallized from toluene), 1813 g of pure dry glycolide (dis-` 20 tilled and twice recrystallized from ethyl acetate), 12.2 ml of ` a 0.33 molar solution of stannous octoate in toluene,and 4.23 ml :.
` of a dioxane solution containing 0.1 g distilled diethylene . .
glycol per ml.
~ t~
The solvents are vaporized off and the charge is placed under an atmosphere of dry nitrogen. The temperature of the reactor is increased to 180C and maintained for 30 minutes.
The resulting copolymer is discharged as a viscous melt, cooled and ground to a fine powZer. The ground copolymer is dried under vacuum at 0.1 mm and at room temperature for 24 hours, and main-tained at 50C for an additional 24 hours. The copolymer is then cooled to ambient temperature and stored at 0.1 mm until used.
The polymerization conversion is determined to be 97.8 percent.
The polymerization product is a clear amber, relatively tough copolymer which is amorphous by X-ray determination. In-herent viscosity as determined on a 0.1 percent solution in chloroform at 25C is 1.66 dl/g.
35/65 Addition Copolymer of L(-)-Lactide and Glycolide Into a polymerization reactor is charged 59.5 g of the copolymer of Example 1, 10.9 g of pure L(-)-lactide, and 79.2 g of pure glycolide. The reaction mixture is placed under an atmosphere of dry nitrogen and heated with stirring to tempera-ture about 200C, and maintained at this temperature for 30 min-utes.
The resultant polymer is cooled, ground and dried at room temperature under 0.1 mm vacuum for 16 hours, and maintained at 70C for an additional 7 hours. The resulting light tan, ' tough, opaque copolymer has a crystalline melting point of 195-200C as determined by differential scanning calorimetry. In-herent viscosity as determined at 25C for~a 0.1 percent solution in hexafluoroisopropanol is 1.47 dl/g. The polymer exhibits 30 percent crystallinity as determined by X-ray diffraction.
Twenty-five grams of the polymer is charged into the barrel of a ~lodel 3211 Instron Rheometer fitted with a 40 mil die having an L/D of 24:1. The barrel had been preheated to a temperature of 210C. The polymer is extruded at the rate of 88 cubic centimeters per hour. The resulting filament is col-lected on a spoo:l at a speed which results in a diameter of about 20 mils. The filament is drawn six times at 60C to obtain a monofilament with a diameter of 9 mils having 64,000 psi straight tensile strength at break and 40,000 psi knot strength at break.
31/69 Addition Copolymer o' L(-)-Lactide and Glycolide Into a polymerization reactor is charged 35.6 g of pure dry L(-)-lactide, 15.4 g of pure dry glycolide, 0.11 ml of a 0.33 molar solution of stannous octoate in toluene and 0.036 g of pure crystalline glycolic acid. The reaction mixture is placed under an atmosphere of nitrogen and heated with stirring to a 20 temperature of 180C for 30 minutes and 200C for an additional 30 minutes.
To the clear, molten, viscous copolymer is added a mix-ture of 12.8 g of pure dry L(-)-lactide and 93 g of pure dry . -11-~3 2~9~
glycolide. The reaction mixture is again placed under an atmo-sphere of dry nitrogen and the temperature is increased to 210C.
Stirring is continued for approximately one hour.
The resulting polymer is discharged, cooled, ground and dried under 0.1 mm vacuum at room temperature for 24 hours. The resulting light tan, translucent, tough copolymer has an inherent viscosity as determined at 25C in hexafluoroisopropanol of 1.22 dl/g. The melting point is 194-202C as determined by Mettler hot stage microscopy and the polymer is birefringent and composed of small spherulites.
Twenty-~ive grams of copolymer is charged into the bar-rel of a Model 3211 Instron Rheometer fitted with a 30 mil die.
Polymer is extruded at 88 cc per hour at 204C. The properties of the resulting monofilament are stated in Table I.
90/10 Random Copolymer of L(-)-Lactide and DL-Lactide Into a polymerization reactor is charged 129.6 g of ;~ pure dry L(-)-lactide, 14.4 g of pure dry d,l-lactide, 0.6 ml of a 0.33 molar solution of stannous octoate in toluene, and 1.06 ml of dioxane solution containing 0.1 g/ml of glycolic acid.
; The solvents are removed by vaporization and the charge is placed ; 2 under an atmosphere of dry nitrogen. The charge is heated with stirring for 20 minutes at 180C, 20 minutes at 190C and 20 minutes at 210C. The resultant polymer is discharged, cooled, ground and dried. Inherent viscosity as determined in chloro-form at 25C is 1.80.
''~
~ 2~9~
E~LE 5 34/66 Addition Copolymer of Lactide and Glycolide Into a polymerization reactor is charged 34.4 g of the polymer prepared in Example 4, 12.4 g of pure dry L(-)-lactide, 89.8 g of pure dry glycolide and 0.91 ml of a dioxane solution containing 0.1 g/ml of glycolic acid. The charge is placed under an atmosphere of nitrogen and heated with stirring to 180C for 30 minutes and 200C for an additional 30 minutes. The ;; resulting polymer was discharged, cooled, ground and dried under vacuum at 0.1 mm and room temperature for 16 hours. The ground polymer is maintained under vacuum for an additional 6 hours at 80C and then cooled to ambient temperature. The inherent vis-cosity of the polymer determined at 25C on a 0.1 percent solu-.
tion in hexafluoroisopropanol is 1.78. The polymer has a melt-ing point of 196bC as determined by differential scanning calori-metry and a crystallinity of 21 percent as determined by X-ray diffraction.
Twenty-five grams of copolymer is charged into the bar-rel of a rheometer as in ~xample 3. The barrel is fitted with a 40 mil die and is preheated to 220C and the polymer is ex-truded at 88 cc per hour. The properties of the resulting mono-filament are given in Table I.
TABLE I
Example 3 Example 5 Extrusion temperature 204C 220C
Draw ratio 6x 6x Draw temperature 56C 66C
Diameter 8.0 mils 8.9 mils Straight tensile strength 65,000 psi 71,000 psi Knot tensile strength 49,000 psi 64,000 psi Elongation 58% 42%
; EXAMPLE 6 :
In Vivo Properties of Lactide/Glycolide Monofilaments Oriented monofilaments of lactide/glycolide addition copolymers of various compositions prepared in accordance with the previous examples are cut into 25-30 inch lengths and ; sterilized with ethylene oxide. Short lengths of the sterile fibers are implanted subcutaneously in rats to determine break-ing strength retention, and implanted intramuscularly to deter-mine the rate of absorption in accordance with conventional techniques for in vivo evaluation of absorbable sutures. The implanted fibers were recovered and evaluated after 7, 14 and 21 days. The compositions of the test fibers and the resultant data are given in Tables II and III. Comparative data is also pro-vided for a comparable lactide/glycolide random copolymer con-trol fiber to illustrate the poor strength retention of such d . . Z~
.
copolymers when utilized as surgical sutures. It is noted that tissue reaction is minimal in all cases.
t .
TABLE II
- % Breaking Strength Retention of Sterile Monofilaments of Lactide/Glycolide 5Copolymers Implanted in Rats Final lactide/glycolide Days postimplantation w/w ratio 7 14 21 .. . . .
25/75 Random 30 0 0 35/65 Addition 85 61 33 ' 10 40/60 Addition 82 57 14 50/50 Addition 86 68 56 '''~ .
:, .
~ TABLE III
:
Absorption of Sterile Monofilaments of Lactide/Glycolide Copolymers Implanted in Rats ,.~
~' 15Final lactide/glycolide% Suture area remaining w/w ratio 60 days 90 days 35/65 Addition 3 o 40/60 Addition 55- Traces - 50/50 Addition 62 14 - .
EXAMPLE ~
40/60 Addition Copolymer of L(-)-Lactide/Glycolide Into a polymerization reactor having a-nitrogen atmosphere is charged 2,332 g of L(-)-lactide, 805 g of glycolide, 19.1 ml 5 of a 0.33 molar solution of stannous octoate in toluene, and 2.197 g of glycolic acid, all reactants being pure and dry.
The reaction mixture was slowly heated with stirring to 200C
and maintained at 200C for 45 minutes. To the molten reaction mixture was t~en added with stirring, a mixture of monomers con-sisting of 468 g L(-)-lactide and 3,395 g glycolide. The temperature of the reaction mixture was slowly increased to 217C and maintained at this temperature for 45 minutes to com-plete the polymerization reaction.
The polymerization product was discharged from the reactor, solidified,ground and dried under vacuum for 24 hours.
The ground polymer was maintained at 90C under vacuum for ` 24 hours. The resulting copolymer had an inherent viscosity of 1.27 in hexafluoroisopropanol at 25C.
The copolymer was converted to a multifilament yarn utilizing a one inch diameter, vertical screw extruder equipped with a metering pump and a 10 hole 20 mil diameter spinneret.
The extruder temperature profile was established to obtain a polymer melt temperature of 440F at a point above the spinneret.
The polymer was rnelt spun into air and collected at a constant take-up speed at about 524 grams per hour. The yarn was drawn five times its original length over hot rolls maintained at 145F.
4~
An oriented yarn of 60 denier having a tenacity of 4.3 g per denier with 38 percent elongation was obtained.
The oriented yarn was braided with a 16 x 3 end con-struction to yield a braid of 14.8 mil diameter having a straight ; 5 tensile strength of 43,500 psi, knot break strength of 34,787 psi, and 30 percent elongation. In vivo strength retention determined in accordance with the procedure of Example 6 was determined to be as follows:
Days in vivo 7 I~ 2 % Original st:rength retained 60 41 17 EXA~LE 8 - 40/60 Addition Copolymer of L(-)-Lactide/Glycolide Into a polymerization reactor having a nitrogen atmo-sphere is charged 2,000 g of L(-)-lactide, 690 g of glycolide,
An oriented yarn of 60 denier having a tenacity of 4.3 g per denier with 38 percent elongation was obtained.
The oriented yarn was braided with a 16 x 3 end con-struction to yield a braid of 14.8 mil diameter having a straight ; 5 tensile strength of 43,500 psi, knot break strength of 34,787 psi, and 30 percent elongation. In vivo strength retention determined in accordance with the procedure of Example 6 was determined to be as follows:
Days in vivo 7 I~ 2 % Original st:rength retained 60 41 17 EXA~LE 8 - 40/60 Addition Copolymer of L(-)-Lactide/Glycolide Into a polymerization reactor having a nitrogen atmo-sphere is charged 2,000 g of L(-)-lactide, 690 g of glycolide,
5.5 ml of 0.33 molar stannous octoate in toluene, and 1.885 g of glycolic acid, all reactants being pure and dry. The reaction mixture was gradually heated with stirring to 200C and main-tained at that temperature for 45 minutes to complete the first phase of the polymerization reaction.
To the clear, molten, viscous copolymer is added a mix-ture of monomers consisting of 401 g of L(-)-lactide and 2,910 g of glycolide. The reaction mixture is heated to 217C with stirring and maintained at that temperature for 45 minutes to complete the reaction.
' ET~-428 ~ t~
The product was discharged from the reactor, solidified, ground and dried under vacuum for 24 hours. The ground polymer was maintained at 90C under vacuum for an additional 24 hours.
The resulting copolymer had an inherent viscosity of 1.40 in hexafluoroisopropanol at 25C.
The copolymer was converted to a multifilament yarn utilizing a one-inch diameter, vertical screw extruder equipped with a metering pump and a 10 hole 20 mil spinneret. The ex-truder temperature profile was established to obtain a polymer melt temperature of 250C at a point above the spinneret. The polymer was melt spun into air and collected at a constant take-up speed at about 500 g per hour. The filaments were drawn four `~ times their original length over hot rolls maintained at 145F.
An oriented yarn of 76 denier having a tenacity of 4.4 g per denier with 34 percent elongation and a crystallinity of 16 per-cent was obtained.
The oriented yarn was braided with eight carriers to ob-tain a braid of 11 mil diameter having a straight tensile strength of 51,400 psi, knot break strength of 37,800 psi, and 24 percent elongation. The braid was annealed at 80C for 6 hours under a nitrogen atmosphere, cut into 3 ft long sutures, sterilized by ethylene oxide and implanted in rats to determine in vivo tensile strength retention and absorption rate with the following re-sults:
4~
Tensile Strength Retention Days in vivo 0 7 14 21 r Break strength remaining (%) 100 81 54 31 :, Absorption Weeks in vivo Suture axea remaining (%) 100 93 12 0 . .
.~ :
I0 Examples 9-15 presented in Tables IV(a) and IV(b) are further lactide/glycolide addition copolymers prepared in ac-cordance with the method of the present invention. Data on poly-mer composition and properties are set forth in the tables to-gether with comparable data for a random copolymer and the product of Example 2. It is interesting to note that the poly-mers prepared in accordance with the present invention have higher inherent viscosities and well defined melting points as compared to the random copolymer of similar molar composition.
Polymer hydrolysis rates were obtained by determining the weight loss of polymer chips immersed in a phosphate buffer solution for the time and at the temperature indicated. The phosphate buffer solution is comprised of a solution of 27.6 g sodium dihydrogenphosphate monohydrate in 1,000 ml of water adjusted to a pH of 7.25 with sodium hydroxide.
Polymers were melt extruded and drawn as hereinbefore ~ described to obtain monofilaments which were evaluated for - 5 initial breaking strength and breaking strength retention - in vlvo. The data as presented in Table IV(b) again illustrates the improved properties of filaments prepared from the addition copolymers of the present invention as compared with a random copolymer of comparable composition.
.
. .
~3~2~4 ~U~
. ~ ~ o~ 9 OO~D
., . U~ ~ ~
a) ~ ~ oP o 1 '~' ; Q ~_ Q ~ I o~ ~ o ~ ~ ~ I 1` a~ r~ co co o~ ~ t~
. ~ ~`
., ~1 Sd ~ ~ O~ ~ `CO oU~ , O ~ ,,J
a) ~
.,~ .,.1.,1 ~
U~ o ~ ~ I~ ~ o CO _I ~ CO
~ I ~
.~ ~ E~
H .
~ . ~ . ol-~ou~lno~ o _l E~ O ,1 _~
o ~ ~ o u~ O In u~ O u~ u~ O ., ~ ~ ~ ~C U~
.' ~ 1`
~_ rl c~ o x c~ co ~
~1 C O
~0 ~ ~ ~
'.' O +
_~ ~ o o o o rl F ~ ~ ~ r~
s.~ .~ ~ ~
~ ~ o ~r 1~ r~ I` oo co r~ r--r~
.~ X o ,~
` ETH--428 ..
'. ~ ~t .~
~ ..
.' o ~or~
a~ ~P ~ ~ ~ o I
N o a~
tn S ~ .
~ o ~D ~P OD ~I CO er ~
~1 ~ ~ a~ oo co ~D
O _l ~0 ~1 . O
dP O~ 0 3 S ~ oRJ
CO ., . . U~
.8 ~ 0~ o ~ ~ a~ ~ ,~
~ o a~ a~ co C O
o ~ h H oO ~
~:~ _l ~ , ., ~3 ~
O ~ 1-) 1` S
1: ~ O O a~ O
~ ~ 1 ~ ~
~ ~ I I I I ,~
_I O o O U~ O o ~
~ ~ Z ~ O ~ O ~) .` ~ ~ o ~-~1 ~ ao O
U~ ~ ~ ~ r ,1 8 i 1,i,i,~ ~
` ~ ~ o a~
a) o o, ~ ~ I
X U O
,.
1 d 2 ~ ~ *
While the preceding examples have been directed to the preparation of specific copolymers of lactide and glycolide, these examples are for purposes of illustration only and are not limiting of the invention. Mixtures of these polymers with up to about 50 percent by weight of other compatible nontoxic and absorbable polymers are likewise included within the present in-vention.
It is to be understood that inert additives such as coloring materials and plasticizers can be incorporated with the polymers of the present invention. As used herein, the term "inert" means materials that are chemically inert to the polymer, and biologically inert to living tissue, i.e., do not cause any of the adverse effects previously discussed. Any of a variety of plasticizers such as, for instance, glyceryl ; 15 triacetate, ethyl benzoate, diethyl phthalate, dibutyl phthalate and bis-2-methoxyethyl phthalate can be used if desired. The amount of plasticizer may vary from 1 to about 20 percent or more based on the weight of the polymer. Not only does the plasticizer render the filaments of the present invention even more pliable, it also serves as a processing aid in extrusion and thread preparation.
Filaments of the present invention are adversely af-fected by moisture and are accordingly preferably dried to a substantially moisture-free condition and stored in heLmeti-cally sealed packages, a preferred form of which is shown in thedrawing as FIGUR~ 2. In FIGURE 2, there is shown a suture package 14 having disposed therein a coil of suture 12, one end ,Z~
of which is attached to needle 13. The needle and suture are positioned within a cavity 16 that is evacuated or filled with a dry atmosphere of air or nitrogen. The il~ustrated package is fabricated of two sheets of aluminum foil or an aluminum foil-plastic laminate and heat sealed or bonded with adhesive at theskirt 16 to hermetically seal the cavity and isolate the con-tents of the package from the external atmosphere.
Filaments of the present invention may be annealed in accordance with known techniques to modify initial tensile ~0 strength and elongation, and to regulate ln vivo strength re-tention and absorption characteristics.
Filaments of the present invention may be used as mono-filament or multifilament sutures, or may be woven, braided, or knitted either alone or in combination with other absorbable fibers such as poly(alkylene oxalate), polyglycolide or poly(lactide-co-glycolide), or with nonabsorbable fibers such as nylon, polypropylene, polyethyleneterephthalate, or poly-tetrafluoroethylene to form multifilament sutures and tubular structures having use in the surgical repair of arteries, veins, ducts, esophagi and the like.
Multifilament yarns that contain the absorbable lactide-co-glycolide filaments of the present invention together with nonabsorbable filaments are illustrated in FIGURE 4 wherein the nonabsorbable fiber is represented by the hatched fiber cross section 19. In FIGURE 4, the fibers 20 are extruded from polymer compositions of the present invention as described above. The relative proportions of absorbable filaments 20 and ~7 ,~ ~ b ~, nonabsorbable filaments 19 may be varied to obtain the absorp-tion characteristic desired in the woven fabric or tubular implants.
Composite fabrics of absorbable and nonabsorbable materials fashioned by textile processes including weaving, knitting and nonwoven felting are described in U.S.P. 3,108,357 and U.S.P. 3,463,158. Methods of weaving and crimping tubular vascular prostheses are described in U.S.P. 3,096,560. Similar techniques may be used in the manufacture of surgical aids wherein nonabsorbable fibers are combined with absorbable fibers composed of the polymers of this invention. The sur-gical utility of "bi-component filaments" containing absorbable and nonabsorbable components is described in U.S.P. 3,463,158.
Monofilaments of the polymers of the present invention may be woven or knitted to form an absorbable fabric having the structure illustrated in FIGURE 5, useful surgically in hernia repair and in supporting damaged liver, kidney and other inter-nal organs.
The polymers of the present invention are also useful in the manufacture of cast films and other solid surgical aids such as scleral buckling prostheses. Thus, cylindrical pins, screws as illustrated in FIGURE 3, reinforcing plates, etc., may be machined from the cast polymer having in vivo absorp-tion characteristics depending upon the polymer composition and molecular weight.
Many different embodiments of this invention will be apparent to those skilled in the art and may be made without ,. ~
'~ 2~4~ ~
departing from the spirit and scope thereof. It is accordingly understood that this invention is not limited to the specific embodiments thereof except as definecl in the appended claims.
To the clear, molten, viscous copolymer is added a mix-ture of monomers consisting of 401 g of L(-)-lactide and 2,910 g of glycolide. The reaction mixture is heated to 217C with stirring and maintained at that temperature for 45 minutes to complete the reaction.
' ET~-428 ~ t~
The product was discharged from the reactor, solidified, ground and dried under vacuum for 24 hours. The ground polymer was maintained at 90C under vacuum for an additional 24 hours.
The resulting copolymer had an inherent viscosity of 1.40 in hexafluoroisopropanol at 25C.
The copolymer was converted to a multifilament yarn utilizing a one-inch diameter, vertical screw extruder equipped with a metering pump and a 10 hole 20 mil spinneret. The ex-truder temperature profile was established to obtain a polymer melt temperature of 250C at a point above the spinneret. The polymer was melt spun into air and collected at a constant take-up speed at about 500 g per hour. The filaments were drawn four `~ times their original length over hot rolls maintained at 145F.
An oriented yarn of 76 denier having a tenacity of 4.4 g per denier with 34 percent elongation and a crystallinity of 16 per-cent was obtained.
The oriented yarn was braided with eight carriers to ob-tain a braid of 11 mil diameter having a straight tensile strength of 51,400 psi, knot break strength of 37,800 psi, and 24 percent elongation. The braid was annealed at 80C for 6 hours under a nitrogen atmosphere, cut into 3 ft long sutures, sterilized by ethylene oxide and implanted in rats to determine in vivo tensile strength retention and absorption rate with the following re-sults:
4~
Tensile Strength Retention Days in vivo 0 7 14 21 r Break strength remaining (%) 100 81 54 31 :, Absorption Weeks in vivo Suture axea remaining (%) 100 93 12 0 . .
.~ :
I0 Examples 9-15 presented in Tables IV(a) and IV(b) are further lactide/glycolide addition copolymers prepared in ac-cordance with the method of the present invention. Data on poly-mer composition and properties are set forth in the tables to-gether with comparable data for a random copolymer and the product of Example 2. It is interesting to note that the poly-mers prepared in accordance with the present invention have higher inherent viscosities and well defined melting points as compared to the random copolymer of similar molar composition.
Polymer hydrolysis rates were obtained by determining the weight loss of polymer chips immersed in a phosphate buffer solution for the time and at the temperature indicated. The phosphate buffer solution is comprised of a solution of 27.6 g sodium dihydrogenphosphate monohydrate in 1,000 ml of water adjusted to a pH of 7.25 with sodium hydroxide.
Polymers were melt extruded and drawn as hereinbefore ~ described to obtain monofilaments which were evaluated for - 5 initial breaking strength and breaking strength retention - in vlvo. The data as presented in Table IV(b) again illustrates the improved properties of filaments prepared from the addition copolymers of the present invention as compared with a random copolymer of comparable composition.
.
. .
~3~2~4 ~U~
. ~ ~ o~ 9 OO~D
., . U~ ~ ~
a) ~ ~ oP o 1 '~' ; Q ~_ Q ~ I o~ ~ o ~ ~ ~ I 1` a~ r~ co co o~ ~ t~
. ~ ~`
., ~1 Sd ~ ~ O~ ~ `CO oU~ , O ~ ,,J
a) ~
.,~ .,.1.,1 ~
U~ o ~ ~ I~ ~ o CO _I ~ CO
~ I ~
.~ ~ E~
H .
~ . ~ . ol-~ou~lno~ o _l E~ O ,1 _~
o ~ ~ o u~ O In u~ O u~ u~ O ., ~ ~ ~ ~C U~
.' ~ 1`
~_ rl c~ o x c~ co ~
~1 C O
~0 ~ ~ ~
'.' O +
_~ ~ o o o o rl F ~ ~ ~ r~
s.~ .~ ~ ~
~ ~ o ~r 1~ r~ I` oo co r~ r--r~
.~ X o ,~
` ETH--428 ..
'. ~ ~t .~
~ ..
.' o ~or~
a~ ~P ~ ~ ~ o I
N o a~
tn S ~ .
~ o ~D ~P OD ~I CO er ~
~1 ~ ~ a~ oo co ~D
O _l ~0 ~1 . O
dP O~ 0 3 S ~ oRJ
CO ., . . U~
.8 ~ 0~ o ~ ~ a~ ~ ,~
~ o a~ a~ co C O
o ~ h H oO ~
~:~ _l ~ , ., ~3 ~
O ~ 1-) 1` S
1: ~ O O a~ O
~ ~ 1 ~ ~
~ ~ I I I I ,~
_I O o O U~ O o ~
~ ~ Z ~ O ~ O ~) .` ~ ~ o ~-~1 ~ ao O
U~ ~ ~ ~ r ,1 8 i 1,i,i,~ ~
` ~ ~ o a~
a) o o, ~ ~ I
X U O
,.
1 d 2 ~ ~ *
While the preceding examples have been directed to the preparation of specific copolymers of lactide and glycolide, these examples are for purposes of illustration only and are not limiting of the invention. Mixtures of these polymers with up to about 50 percent by weight of other compatible nontoxic and absorbable polymers are likewise included within the present in-vention.
It is to be understood that inert additives such as coloring materials and plasticizers can be incorporated with the polymers of the present invention. As used herein, the term "inert" means materials that are chemically inert to the polymer, and biologically inert to living tissue, i.e., do not cause any of the adverse effects previously discussed. Any of a variety of plasticizers such as, for instance, glyceryl ; 15 triacetate, ethyl benzoate, diethyl phthalate, dibutyl phthalate and bis-2-methoxyethyl phthalate can be used if desired. The amount of plasticizer may vary from 1 to about 20 percent or more based on the weight of the polymer. Not only does the plasticizer render the filaments of the present invention even more pliable, it also serves as a processing aid in extrusion and thread preparation.
Filaments of the present invention are adversely af-fected by moisture and are accordingly preferably dried to a substantially moisture-free condition and stored in heLmeti-cally sealed packages, a preferred form of which is shown in thedrawing as FIGUR~ 2. In FIGURE 2, there is shown a suture package 14 having disposed therein a coil of suture 12, one end ,Z~
of which is attached to needle 13. The needle and suture are positioned within a cavity 16 that is evacuated or filled with a dry atmosphere of air or nitrogen. The il~ustrated package is fabricated of two sheets of aluminum foil or an aluminum foil-plastic laminate and heat sealed or bonded with adhesive at theskirt 16 to hermetically seal the cavity and isolate the con-tents of the package from the external atmosphere.
Filaments of the present invention may be annealed in accordance with known techniques to modify initial tensile ~0 strength and elongation, and to regulate ln vivo strength re-tention and absorption characteristics.
Filaments of the present invention may be used as mono-filament or multifilament sutures, or may be woven, braided, or knitted either alone or in combination with other absorbable fibers such as poly(alkylene oxalate), polyglycolide or poly(lactide-co-glycolide), or with nonabsorbable fibers such as nylon, polypropylene, polyethyleneterephthalate, or poly-tetrafluoroethylene to form multifilament sutures and tubular structures having use in the surgical repair of arteries, veins, ducts, esophagi and the like.
Multifilament yarns that contain the absorbable lactide-co-glycolide filaments of the present invention together with nonabsorbable filaments are illustrated in FIGURE 4 wherein the nonabsorbable fiber is represented by the hatched fiber cross section 19. In FIGURE 4, the fibers 20 are extruded from polymer compositions of the present invention as described above. The relative proportions of absorbable filaments 20 and ~7 ,~ ~ b ~, nonabsorbable filaments 19 may be varied to obtain the absorp-tion characteristic desired in the woven fabric or tubular implants.
Composite fabrics of absorbable and nonabsorbable materials fashioned by textile processes including weaving, knitting and nonwoven felting are described in U.S.P. 3,108,357 and U.S.P. 3,463,158. Methods of weaving and crimping tubular vascular prostheses are described in U.S.P. 3,096,560. Similar techniques may be used in the manufacture of surgical aids wherein nonabsorbable fibers are combined with absorbable fibers composed of the polymers of this invention. The sur-gical utility of "bi-component filaments" containing absorbable and nonabsorbable components is described in U.S.P. 3,463,158.
Monofilaments of the polymers of the present invention may be woven or knitted to form an absorbable fabric having the structure illustrated in FIGURE 5, useful surgically in hernia repair and in supporting damaged liver, kidney and other inter-nal organs.
The polymers of the present invention are also useful in the manufacture of cast films and other solid surgical aids such as scleral buckling prostheses. Thus, cylindrical pins, screws as illustrated in FIGURE 3, reinforcing plates, etc., may be machined from the cast polymer having in vivo absorp-tion characteristics depending upon the polymer composition and molecular weight.
Many different embodiments of this invention will be apparent to those skilled in the art and may be made without ,. ~
'~ 2~4~ ~
departing from the spirit and scope thereof. It is accordingly understood that this invention is not limited to the specific embodiments thereof except as definecl in the appended claims.
Claims (23)
1. A method for preparing a crystalline copolymer of lactide and glycolide containing from 50 to 75 wt percent glycolide which comprises:
a. preparing a random copolymer comprising a major portion of an optically active lactide and a minor portion of a monomer selected from the group con-sisting of glycolide and d,l-lactide, and b. admixing with said random copolymer additional monomers comprising from 70 to 90 wt percent glycolide and 10 to 30 wt percent of an optically active lactide, the quantity of glycolide being sufficient to provide from 50 to 75 wt percent glycolide in the polymer-monomer mixture, and c. polymerizing said polymer-monomer mixture to obtain said crystalline copolymer of lactide and gly-colide , said copolymer having an inherent viscosity determined as a 0.1% solution in hexafluoroisopropanol at 25°C of at least about 1.20, a melting point of at least about 160°C and a crystallinity of at least about 15%.
a. preparing a random copolymer comprising a major portion of an optically active lactide and a minor portion of a monomer selected from the group con-sisting of glycolide and d,l-lactide, and b. admixing with said random copolymer additional monomers comprising from 70 to 90 wt percent glycolide and 10 to 30 wt percent of an optically active lactide, the quantity of glycolide being sufficient to provide from 50 to 75 wt percent glycolide in the polymer-monomer mixture, and c. polymerizing said polymer-monomer mixture to obtain said crystalline copolymer of lactide and gly-colide , said copolymer having an inherent viscosity determined as a 0.1% solution in hexafluoroisopropanol at 25°C of at least about 1.20, a melting point of at least about 160°C and a crystallinity of at least about 15%.
2. The method of Claim 1 wherein said random co-polymer comprises from 60 to 90 wt percent of optically active lactide and from 10 to 40 wt percent of another monomer selected from the group consisting of glycolide and d,l-lactide.
3. The method of Claim 2 wherein the optically active lactide is L(-)-lactide and the other monomer is glycolide.
4. The method of Claim 3 wherein the random copolymer comprises from 65 to 75 wt percent of L(-)-lactide and from 25 to 35 mol percent qlycolide.
5. The method of Claim 2 wherein the optically active lactide is L(-)-lactide and the other monomer is d,l-lactide.
6. The method of Claim 5 wherein the random copolymer comprises from 65 to 75 wt percent of L(-)-lactide and from 25 to 35 wt percent d,l-lactide.
7. The method of Claim 1 wherein the optically active lactide admixed with the random copolymer according to Step (b) is L(-)-lactide.
8. The method of Claim 7 wherein the mixture of L(-)-lactide and glycolide admixed with the random copolymer according to Step (b) comprises from 80 to 90 wt percent glycolide and from 10 to 20 wt percent L(-)-lactide.
9. The method of Claim 1 wherein the random copolymer is ground to produce a particulate material prior to admixing with additional monomers according to Step (b).
10. The copolymer product of the process of Claim 1.
11. The copolymer product of the process of Claim 2.
12. The copolymer product of the process of Claim 6.
13. The copolymer product of the process of Claim 8.
14. A synthetic absorbable suture comprising at least one drawn and oriented filament of a copolymer of Claim 10.
15. A synthetic absorbable suture comprising at least one drawn and oriented filament of a copolymer of Claim 11.
16. A synthetic absorbable suture comprising at least one drawn and oriented filament of a copolymer of Claim 12.
17. A synthetic absorbable suture comprising at least one drawn and oriented filament of a copolymer of Claim 13.
18. A surgical prosthesis comprising a fabric manu-factured at least in part from synthetic absorbable fibers com-prising drawn and oriented filaments of a copolymer of Claim 10.
19. A surgical prosthesis comprising a solid surgi-cal aid cast or machined from an absorbable polymer comprising a copolymer of Claim 10.
20. An absorbable surgical suture comprising at least one drawn and oriented filament of a crystalline copolymer of lactide and glycolide containing from about 50 to 75 percent glycolide, said suture having a crystallinity of at least 15 per-cent, an inherent viscosity of at least 1.0 as determined on a 0.1 percent solution in HFIP at 25°C, a straight tensile and and knot strength of at least 40,000 psi and 30,000 psi respec-tively, straight tensile strength retention in vivo of at least 40 percent after 14 days, and substantially complete absorption in vivo within about 120 days.
21. A suture of Claim 20 wherein said crystalline co-polymer is an addition product of (a) a random copolymer of lactide and glycolide containing from 60 to 90 percent lactide, and (b) a mixture of lactide and glycolide monomers containing from 70 to 90 percent glycolide.
22. A suture of Claim 21 wherein the lactide is L(-)-lactide.
23. A suture of Claim 20 wherein said crystalline co-polymer is an addition product of (a) a random copolymer of L(-)-lactide and d,l-lactide containing from 60 to 90 percent L(-)-lactide, and (b) a mixture of L(-)-lactide and glycolide monomers containing from 70 to 90 percent glycolide.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US809,737 | 1977-06-24 | ||
| US05/809,737 US4137921A (en) | 1977-06-24 | 1977-06-24 | Addition copolymers of lactide and glycolide and method of preparation |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1124444A true CA1124444A (en) | 1982-05-25 |
Family
ID=25202112
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA306,056A Expired CA1124444A (en) | 1977-06-24 | 1978-06-22 | Addition copolymers of lactide and glycolide and method of preparation |
Country Status (5)
| Country | Link |
|---|---|
| US (2) | US4137921A (en) |
| CA (1) | CA1124444A (en) |
| DE (1) | DE2827289A1 (en) |
| FR (1) | FR2401185B1 (en) |
| GB (1) | GB1595269A (en) |
Families Citing this family (186)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4243775A (en) * | 1978-11-13 | 1981-01-06 | American Cyanamid Company | Synthetic polyester surgical articles |
| US4300565A (en) * | 1977-05-23 | 1981-11-17 | American Cyanamid Company | Synthetic polyester surgical articles |
| US4214586A (en) * | 1978-11-30 | 1980-07-29 | Ethicon, Inc. | Anastomotic coupling device |
| DE2917446A1 (en) * | 1979-04-28 | 1980-11-06 | Merck Patent Gmbh | SURGICAL MATERIAL |
| DE2947985A1 (en) * | 1979-11-28 | 1981-09-17 | Vsesojuznyj naučno-issledovatel'skij i ispytatel'nyj institut medicinskoj techniki, Moskva | Matrix material for fixing bone fractures - consisting of a copolymer of hydrophilic and hydrophobic monomers reinforced with resorbable non-non-toxic fibres |
| DE3378250D1 (en) * | 1982-04-22 | 1988-11-24 | Ici Plc | Continuous release formulations |
| US4520821A (en) * | 1982-04-30 | 1985-06-04 | The Regents Of The University Of California | Growing of long-term biological tissue correction structures in vivo |
| DE3218151A1 (en) * | 1982-05-14 | 1983-11-17 | Akzo Gmbh, 5600 Wuppertal | MICROPOROUS, POWDER-SHAPED POLYLACTIDES AND METHOD FOR THE PRODUCTION THEREOF |
| US4429080A (en) | 1982-07-01 | 1984-01-31 | American Cyanamid Company | Synthetic copolymer surgical articles and method of manufacturing the same |
| NL8202893A (en) * | 1982-07-16 | 1984-02-16 | Rijksuniversiteit | ORGANIC Tolerant, ANTHITHROMBOGENIC MATERIAL, SUITABLE FOR RECOVERY SURGERY. |
| NL8202894A (en) * | 1982-07-16 | 1984-02-16 | Rijksuniversiteit | POLYESTER FILAMENT MATERIAL. |
| US4605730A (en) * | 1982-10-01 | 1986-08-12 | Ethicon, Inc. | Surgical articles of copolymers of glycolide and ε-caprolactone and methods of producing the same |
| US4523591A (en) * | 1982-10-22 | 1985-06-18 | Kaplan Donald S | Polymers for injection molding of absorbable surgical devices |
| US4443430A (en) * | 1982-11-16 | 1984-04-17 | Ethicon, Inc. | Synthetic absorbable hemostatic agent |
| US4565851A (en) * | 1983-04-25 | 1986-01-21 | Eastman Kodak Company | Containers having improved gas barrier properties |
| US4470416A (en) * | 1983-06-17 | 1984-09-11 | Ethicon, Inc. | Copolymers of lactide and/or glycolide with 1,5-dioxepan-2-one |
| US4522593A (en) * | 1983-07-07 | 1985-06-11 | Fischer Dan E | Knitted gingival retraction cord |
| US4670286A (en) * | 1983-09-20 | 1987-06-02 | Allied Corporation | Method of forming prosthetic devices |
| US4594407A (en) * | 1983-09-20 | 1986-06-10 | Allied Corporation | Prosthetic devices derived from krebs-cycle dicarboxylic acids and diols |
| EP0342278B1 (en) * | 1984-03-06 | 1996-09-04 | United States Surgical Corporation | A process for making two-phase compositions for absorbable surgical devices |
| CA1256638A (en) * | 1984-07-06 | 1989-06-27 | Motoaki Tanaka | Polymer and its production |
| DE3428640A1 (en) * | 1984-08-03 | 1986-02-06 | Akzo Gmbh, 5600 Wuppertal | MICROPOROUS, POWDER-SHAPED POLYLACTIDES |
| US4595713A (en) * | 1985-01-22 | 1986-06-17 | Hexcel Corporation | Medical putty for tissue augmentation |
| US4652264A (en) * | 1985-04-25 | 1987-03-24 | American Cyanamid Company | Prosthetic tubular article |
| US4923470A (en) * | 1985-04-25 | 1990-05-08 | American Cyanamid Company | Prosthetic tubular article made with four chemically distinct fibers |
| US4889119A (en) * | 1985-07-17 | 1989-12-26 | Ethicon, Inc. | Surgical fastener made from glycolide-rich polymer blends |
| US4741337A (en) * | 1985-07-17 | 1988-05-03 | Ethicon, Inc. | Surgical fastener made from glycolide-rich polymer blends |
| US4973333A (en) * | 1985-09-20 | 1990-11-27 | Richards Medical Company | Resorbable compressing screw and method |
| US4643191A (en) * | 1985-11-29 | 1987-02-17 | Ethicon, Inc. | Crystalline copolymers of p-dioxanone and lactide and surgical devices made therefrom |
| US4653497A (en) * | 1985-11-29 | 1987-03-31 | Ethicon, Inc. | Crystalline p-dioxanone/glycolide copolymers and surgical devices made therefrom |
| US5061281A (en) * | 1985-12-17 | 1991-10-29 | Allied-Signal Inc. | Bioresorbable polymers and implantation devices thereof |
| US4792336A (en) * | 1986-03-03 | 1988-12-20 | American Cyanamid Company | Flat braided ligament or tendon implant device having texturized yarns |
| NZ219708A (en) * | 1986-04-07 | 1989-04-26 | Johnson & Johnson Prod Inc | Absorbable ligament and tendon prosthesis containing l-lactide/glycolide polymer |
| US4839130A (en) * | 1986-07-17 | 1989-06-13 | United States Surgical Corporation | Process of making an absorbable surgical device |
| US4744365A (en) * | 1986-07-17 | 1988-05-17 | United States Surgical Corporation | Two-phase compositions for absorbable surgical devices |
| US4857602A (en) * | 1986-09-05 | 1989-08-15 | American Cyanamid Company | Bioabsorbable surgical suture coating |
| DE3635679A1 (en) * | 1986-10-21 | 1988-05-05 | Dynamit Nobel Ag | Surgical suture material |
| US6309635B1 (en) | 1986-11-20 | 2001-10-30 | Children's Medical Center Corp. | Seeding parenchymal cells into compression resistant porous scaffold after vascularizing in vivo |
| US5567612A (en) * | 1986-11-20 | 1996-10-22 | Massachusetts Institute Of Technology | Genitourinary cell-matrix structure for implantation into a human and a method of making |
| US5804178A (en) * | 1986-11-20 | 1998-09-08 | Massachusetts Institute Of Technology | Implantation of cell-matrix structure adjacent mesentery, omentum or peritoneum tissue |
| JPH0781204B2 (en) * | 1987-04-21 | 1995-08-30 | 株式会社バイオマテリアルユニバ−ス | Polylactic acid fiber |
| US4844854A (en) * | 1987-09-22 | 1989-07-04 | United States Surgical Corporation | Process for making a surgical device using two-phase compositions |
| US5152781A (en) * | 1987-12-17 | 1992-10-06 | Allied-Signal Inc. | Medical devices fabricated from homopolymers and copolymers having recurring carbonate units |
| US5145945A (en) * | 1987-12-17 | 1992-09-08 | Allied-Signal Inc. | Homopolymers and copolymers having recurring carbonate units |
| US4891263A (en) * | 1987-12-17 | 1990-01-02 | Allied-Signal Inc. | Polycarbonate random copolymer-based fiber compositions and method of melt-spinning same and device |
| US4916207A (en) * | 1987-12-17 | 1990-04-10 | Allied-Signal, Inc. | Polycarbonate homopolymer-based fiber compositions and method of melt-spinning same and device |
| US5256764A (en) * | 1987-12-17 | 1993-10-26 | United States Surgical Corporation | Medical devices fabricated from homopolymers and copolymers having recurring carbonate units |
| US5274074A (en) * | 1987-12-17 | 1993-12-28 | United States Surgical Corporation | Medical devices fabricated from homopolymers and copolymers having recurring carbonate units |
| US5120802A (en) * | 1987-12-17 | 1992-06-09 | Allied-Signal Inc. | Polycarbonate-based block copolymers and devices |
| US4916193A (en) * | 1987-12-17 | 1990-04-10 | Allied-Signal Inc. | Medical devices fabricated totally or in part from copolymers of recurring units derived from cyclic carbonates and lactides |
| US4838267A (en) * | 1988-02-12 | 1989-06-13 | Ethicon, Inc. | Glycolide/p-dioxanone block copolymers |
| US5092884A (en) * | 1988-03-24 | 1992-03-03 | American Cyanamid Company | Surgical composite structure having absorbable and nonabsorbable components |
| US5180765A (en) * | 1988-08-08 | 1993-01-19 | Biopak Technology, Ltd. | Biodegradable packaging thermoplastics from lactides |
| US5444113A (en) * | 1988-08-08 | 1995-08-22 | Ecopol, Llc | End use applications of biodegradable polymers |
| US6323307B1 (en) | 1988-08-08 | 2001-11-27 | Cargill Dow Polymers, Llc | Degradation control of environmentally degradable disposable materials |
| US5502158A (en) * | 1988-08-08 | 1996-03-26 | Ecopol, Llc | Degradable polymer composition |
| US5424346A (en) * | 1988-08-08 | 1995-06-13 | Ecopol, Llc | Biodegradable replacement of crystal polystyrene |
| JP2714454B2 (en) * | 1988-11-07 | 1998-02-16 | 三井東圧化学株式会社 | Method for producing bioabsorbable polyester |
| US5133739A (en) * | 1990-02-06 | 1992-07-28 | Ethicon, Inc. | Segmented copolymers of ε-caprolactone and glycolide |
| CA2035592C (en) * | 1990-02-06 | 2001-10-23 | Rao S. Bezwada | Segmented copolymers of .epsilon.-caprolactone and glycolide |
| JPH04226125A (en) * | 1990-06-23 | 1992-08-14 | Boehringer Ingelheim Kg | Manufacture of poly-d, l-lactide and its use as carrier for active substance |
| EP0463194A1 (en) * | 1990-06-23 | 1992-01-02 | Boehringer Ingelheim Kg | Process for the preparation of poly(D,L-lactide) and its use as a drug carrier |
| US5320624A (en) * | 1991-02-12 | 1994-06-14 | United States Surgical Corporation | Blends of glycolide and/or lactide polymers and caprolactone and/or trimethylene carbonate polymers and absorbable surgical devices made therefrom |
| US6228954B1 (en) | 1991-02-12 | 2001-05-08 | United States Surgical Corporation | Blends of glycolide and/or lactide polymers and caprolactone and/or trimethylene carbonate polymers and absorabable surgical devices made therefrom |
| AU2900792A (en) * | 1991-10-24 | 1993-05-21 | Children's Medical Center Corporation | Neomorphogenesis of urological structures in vivo from cell culture |
| US5242910A (en) * | 1992-10-13 | 1993-09-07 | The Procter & Gamble Company | Sustained release compositions for treating periodontal disease |
| TW333456B (en) | 1992-12-07 | 1998-06-11 | Takeda Pharm Ind Co Ltd | A pharmaceutical composition of sustained-release preparation the invention relates to a pharmaceutical composition of sustained-release preparation which comprises a physiologically active peptide. |
| US6387363B1 (en) | 1992-12-31 | 2002-05-14 | United States Surgical Corporation | Biocompatible medical devices |
| US6090925A (en) | 1993-03-09 | 2000-07-18 | Epic Therapeutics, Inc. | Macromolecular microparticles and methods of production and use |
| US5709854A (en) * | 1993-04-30 | 1998-01-20 | Massachusetts Institute Of Technology | Tissue formation by injecting a cell-polymeric solution that gels in vivo |
| US8795332B2 (en) | 2002-09-30 | 2014-08-05 | Ethicon, Inc. | Barbed sutures |
| US6241747B1 (en) | 1993-05-03 | 2001-06-05 | Quill Medical, Inc. | Barbed Bodily tissue connector |
| US5403347A (en) * | 1993-05-27 | 1995-04-04 | United States Surgical Corporation | Absorbable block copolymers and surgical articles fabricated therefrom |
| US5522841A (en) * | 1993-05-27 | 1996-06-04 | United States Surgical Corporation | Absorbable block copolymers and surgical articles fabricated therefrom |
| US5447725A (en) * | 1993-06-11 | 1995-09-05 | The Procter & Gamble Company | Methods for aiding periodontal tissue regeneration |
| US5531716A (en) * | 1993-09-29 | 1996-07-02 | Hercules Incorporated | Medical devices subject to triggered disintegration |
| US5942496A (en) * | 1994-02-18 | 1999-08-24 | The Regent Of The University Of Michigan | Methods and compositions for multiple gene transfer into bone cells |
| US5962427A (en) * | 1994-02-18 | 1999-10-05 | The Regent Of The University Of Michigan | In vivo gene transfer methods for wound healing |
| US6074840A (en) | 1994-02-18 | 2000-06-13 | The Regents Of The University Of Michigan | Recombinant production of latent TGF-beta binding protein-3 (LTBP-3) |
| US5763416A (en) * | 1994-02-18 | 1998-06-09 | The Regent Of The University Of Michigan | Gene transfer into bone cells and tissues |
| US20020193338A1 (en) * | 1994-02-18 | 2002-12-19 | Goldstein Steven A. | In vivo gene transfer methods for wound healing |
| US5431679A (en) * | 1994-03-10 | 1995-07-11 | United States Surgical Corporation | Absorbable block copolymers and surgical articles fabricated therefrom |
| US6551618B2 (en) | 1994-03-15 | 2003-04-22 | University Of Birmingham | Compositions and methods for delivery of agents for neuronal regeneration and survival |
| US6339130B1 (en) * | 1994-07-22 | 2002-01-15 | United States Surgical Corporation | Bioabsorbable branched polymers containing units derived from dioxanone and medical/surgical devices manufactured therefrom |
| US5578662A (en) | 1994-07-22 | 1996-11-26 | United States Surgical Corporation | Bioabsorbable branched polymers containing units derived from dioxanone and medical/surgical devices manufactured therefrom |
| CA2158420C (en) | 1994-09-16 | 2007-05-01 | Mark S. Roby | Absorbable polymer and surgical articles fabricated therefrom |
| US6206908B1 (en) | 1994-09-16 | 2001-03-27 | United States Surgical Corporation | Absorbable polymer and surgical articles fabricated therefrom |
| US5618313A (en) * | 1994-10-11 | 1997-04-08 | United States Surgical Corporation | Absorbable polymer and surgical articles fabricated therefrom |
| US5716404A (en) * | 1994-12-16 | 1998-02-10 | Massachusetts Institute Of Technology | Breast tissue engineering |
| US6123727A (en) * | 1995-05-01 | 2000-09-26 | Massachusetts Institute Of Technology | Tissue engineered tendons and ligaments |
| US5855610A (en) | 1995-05-19 | 1999-01-05 | Children's Medical Center Corporation | Engineering of strong, pliable tissues |
| US6129761A (en) * | 1995-06-07 | 2000-10-10 | Reprogenesis, Inc. | Injectable hydrogel compositions |
| US5741685A (en) * | 1995-06-07 | 1998-04-21 | Children's Medical Center Corporation | Parenchymal cells packaged in immunoprotective tissue for implantation |
| US5633342A (en) * | 1995-10-27 | 1997-05-27 | Chronopol, Inc. | Method for the synthesis of environmentally degradable block copolymers |
| DE69728307T2 (en) | 1996-01-19 | 2005-02-17 | United States Surgical Corp., Norwalk | Absorbable polymer mixtures and surgical articles made therefrom |
| EP0907338A4 (en) * | 1996-04-01 | 1999-09-01 | American Cyanamid Co | Crystalline copolymers and methods of producing such copolymers |
| US5844067A (en) * | 1996-04-18 | 1998-12-01 | Erneta; Modesto | Process for producing absorbable segmented copolymers with a substantially uniform sequence distribution |
| JP3731838B2 (en) * | 1996-04-30 | 2006-01-05 | 株式会社クレハ | Polyglycolic acid oriented film and method for producing the same |
| US6368356B1 (en) | 1996-07-11 | 2002-04-09 | Scimed Life Systems, Inc. | Medical devices comprising hydrogel polymers having improved mechanical properties |
| US6060534A (en) | 1996-07-11 | 2000-05-09 | Scimed Life Systems, Inc. | Medical devices comprising ionically and non-ionically crosslinked polymer hydrogels having improved mechanical properties |
| ZA978537B (en) | 1996-09-23 | 1998-05-12 | Focal Inc | Polymerizable biodegradable polymers including carbonate or dioxanone linkages. |
| US6191236B1 (en) | 1996-10-11 | 2001-02-20 | United States Surgical Corporation | Bioabsorbable suture and method of its manufacture |
| US5952088A (en) * | 1996-12-31 | 1999-09-14 | Kimberly-Clark Worldwide, Inc. | Multicomponent fiber |
| US5931855A (en) | 1997-05-21 | 1999-08-03 | Frank Hoffman | Surgical methods using one-way suture |
| WO1999006563A1 (en) | 1997-07-30 | 1999-02-11 | Emory University | Novel bone mineralization proteins, dna, vectors, expression systems |
| US7923250B2 (en) | 1997-07-30 | 2011-04-12 | Warsaw Orthopedic, Inc. | Methods of expressing LIM mineralization protein in non-osseous cells |
| US6089009A (en) | 1997-08-28 | 2000-07-18 | Belmont Textile Machinery Co., Inc. | Fluid-jet false-twisting method and product |
| US6007565A (en) * | 1997-09-05 | 1999-12-28 | United States Surgical | Absorbable block copolymers and surgical articles fabricated therefrom |
| US6165217A (en) | 1997-10-02 | 2000-12-26 | Gore Enterprise Holdings, Inc. | Self-cohering, continuous filament non-woven webs |
| US6268434B1 (en) | 1997-10-31 | 2001-07-31 | Kimberly Clark Worldwide, Inc. | Biodegradable polylactide nonwovens with improved fluid management properties |
| US6201068B1 (en) | 1997-10-31 | 2001-03-13 | Kimberly-Clark Worldwide, Inc. | Biodegradable polylactide nonwovens with improved fluid management properties |
| US6277927B1 (en) | 1997-11-26 | 2001-08-21 | United States Surgical Corporation | Absorbable block copolymers and surgical articles fabricated therefrom |
| US6544455B1 (en) | 1997-12-22 | 2003-04-08 | Kimberly-Clark Worldwide, Inc. | Methods for making a biodegradable thermoplastic composition |
| US6309988B1 (en) | 1997-12-22 | 2001-10-30 | Kimberly-Clark Worldwide, Inc. | Biodisintegratable nonwovens with improved fluid management properties |
| US6306782B1 (en) | 1997-12-22 | 2001-10-23 | Kimberly-Clark Worldwide, Inc. | Disposable absorbent product having biodisintegratable nonwovens with improved fluid management properties |
| US6261677B1 (en) * | 1997-12-22 | 2001-07-17 | Kimberly-Clark Worldwide, Inc. | Synthetic fiber |
| US6135987A (en) * | 1997-12-22 | 2000-10-24 | Kimberly-Clark Worldwide, Inc. | Synthetic fiber |
| JPH11203837A (en) | 1998-01-16 | 1999-07-30 | Sony Corp | Editing system and method therefor |
| US6194483B1 (en) | 1998-08-31 | 2001-02-27 | Kimberly-Clark Worldwide, Inc. | Disposable articles having biodegradable nonwovens with improved fluid management properties |
| US6197860B1 (en) | 1998-08-31 | 2001-03-06 | Kimberly-Clark Worldwide, Inc. | Biodegradable nonwovens with improved fluid management properties |
| US6565874B1 (en) * | 1998-10-28 | 2003-05-20 | Atrix Laboratories | Polymeric delivery formulations of leuprolide with improved efficacy |
| DE19944128A1 (en) | 1999-09-15 | 2001-04-12 | November Ag Molekulare Medizin | Process for marking an animal and products derived from it |
| US6362308B1 (en) | 2000-08-10 | 2002-03-26 | Alkermes Controlled Therapeutics Inc. Ii | Acid end group poly(d,l-lactide-co-glycolide) copolymers high glycolide content |
| AU9051501A (en) | 2000-08-16 | 2002-02-25 | Tyco Healthcare | High consistency absorbable polymeric resin |
| EP1309279A4 (en) * | 2000-08-17 | 2008-04-09 | Tyco Healthcare | Sutures and coatings made from therapeutic absorbable glass |
| US8470359B2 (en) | 2000-11-13 | 2013-06-25 | Qlt Usa, Inc. | Sustained release polymer |
| US6913765B2 (en) | 2001-03-21 | 2005-07-05 | Scimed Life Systems, Inc. | Controlling resorption of bioresorbable medical implant material |
| US7056331B2 (en) | 2001-06-29 | 2006-06-06 | Quill Medical, Inc. | Suture method |
| GB0116341D0 (en) * | 2001-07-04 | 2001-08-29 | Smith & Nephew | Biodegradable polymer systems |
| US6848152B2 (en) | 2001-08-31 | 2005-02-01 | Quill Medical, Inc. | Method of forming barbs on a suture and apparatus for performing same |
| US6747121B2 (en) | 2001-09-05 | 2004-06-08 | Synthes (Usa) | Poly(L-lactide-co-glycolide) copolymers, methods for making and using same, and devices containing same |
| GB0202233D0 (en) * | 2002-01-31 | 2002-03-20 | Smith & Nephew | Bioresorbable polymers |
| US6773450B2 (en) * | 2002-08-09 | 2004-08-10 | Quill Medical, Inc. | Suture anchor and method |
| US8100940B2 (en) | 2002-09-30 | 2012-01-24 | Quill Medical, Inc. | Barb configurations for barbed sutures |
| US20040088003A1 (en) | 2002-09-30 | 2004-05-06 | Leung Jeffrey C. | Barbed suture in combination with surgical needle |
| US7148315B2 (en) * | 2002-10-23 | 2006-12-12 | Ethicon, Inc. | Monomer addition techniques to control manufacturing of bioabsorbable copolymers |
| US20040260398A1 (en) * | 2003-02-10 | 2004-12-23 | Kelman David C. | Resorbable devices |
| US20060076295A1 (en) * | 2004-03-15 | 2006-04-13 | The Trustees Of Columbia University In The City Of New York | Systems and methods of blood-based therapies having a microfluidic membraneless exchange device |
| JP4489761B2 (en) | 2003-03-14 | 2010-06-23 | ザ トラスティーズ オブ コロンビア ユニヴァーシティ イン ザ シティ オブ ニューヨーク | System and method for blood-based therapy with a microfluidic membraneless device |
| US7624487B2 (en) | 2003-05-13 | 2009-12-01 | Quill Medical, Inc. | Apparatus and method for forming barbs on a suture |
| NL1023720C2 (en) * | 2003-06-23 | 2004-12-28 | Univ Eindhoven Tech | Method for changing the transport properties of a material, method for releasing a drug from an implant, as well as implant with drug. |
| WO2005027988A2 (en) * | 2003-09-05 | 2005-03-31 | Norian Corporation | Bone cement compositions having fiber-reinforcement and/or increased flowability |
| US7141354B2 (en) * | 2003-09-30 | 2006-11-28 | Dai Nippon Printing Co., Ltd. | Photo radical generator, photo sensitive resin composition and article |
| US7309232B2 (en) * | 2003-10-10 | 2007-12-18 | Dentigenix Inc. | Methods for treating dental conditions using tissue scaffolds |
| US20060034943A1 (en) * | 2003-10-31 | 2006-02-16 | Technology Innovations Llc | Process for treating a biological organism |
| GB0329654D0 (en) * | 2003-12-23 | 2004-01-28 | Smith & Nephew | Tunable segmented polyacetal |
| WO2005105172A1 (en) | 2004-04-20 | 2005-11-10 | Genzyme Corporation | Surgical mesh-like implant |
| EP1763703A4 (en) * | 2004-05-12 | 2010-12-08 | Massachusetts Inst Technology | Manufacturing process, such as three-dimensional printing, including solvent vapor filming and the like |
| CN104224253A (en) | 2004-05-14 | 2014-12-24 | 伊西康有限责任公司 | Suture methods and devices |
| US8012501B2 (en) | 2004-06-10 | 2011-09-06 | Synthes Usa, Llc | Flexible bone composite |
| WO2006026397A2 (en) * | 2004-08-26 | 2006-03-09 | Stout Medical Group, L.P. | Sutures and methods of making the same |
| JP2009504929A (en) * | 2005-08-18 | 2009-02-05 | スミス アンド ネフュー ピーエルシー | High-strength devices and composite materials |
| US9849216B2 (en) | 2006-03-03 | 2017-12-26 | Smith & Nephew, Inc. | Systems and methods for delivering a medicament |
| ATE542583T1 (en) * | 2006-05-22 | 2012-02-15 | Univ Columbia | METHOD FOR MEMBRANE-LESS MICROFLUID EXCHANGE IN AN H-FILTER AND FILTERING OF THE EXTRACTION FLUID OUTPUT STREAMS |
| CA2679365C (en) * | 2006-11-30 | 2016-05-03 | Smith & Nephew, Inc. | Fiber reinforced composite material |
| EP2115008B1 (en) * | 2007-03-01 | 2019-09-18 | De Staat der Nederlanden, vert. door de Minister van Volksgezondheid, Welzijn en Sport, namens de Minister, Projectdirectie ALT, het INTRAVACC | Biodegradable material based on opened starch |
| US8486439B2 (en) * | 2007-03-01 | 2013-07-16 | Bioneedle Technologies Group B.V. | Parenteral formulation |
| US20080255612A1 (en) * | 2007-04-13 | 2008-10-16 | Angiotech Pharmaceuticals, Inc. | Self-retaining systems for surgical procedures |
| WO2008129245A1 (en) * | 2007-04-18 | 2008-10-30 | Smith & Nephew Plc | Expansion moulding of shape memory polymers |
| AU2008243035B2 (en) * | 2007-04-19 | 2013-09-12 | Smith & Nephew, Inc. | Graft fixation |
| WO2008131197A1 (en) * | 2007-04-19 | 2008-10-30 | Smith & Nephew, Inc. | Multi-modal shape memory polymers |
| DE102007036101A1 (en) * | 2007-08-01 | 2009-02-05 | Boehringer Ingelheim Pharma Gmbh & Co. Kg | New glycolide-rich copolymers |
| ES2479290T3 (en) | 2007-09-27 | 2014-07-23 | Ethicon Llc | A system for cutting a retainer in a suture |
| BRPI0820129B8 (en) * | 2007-12-19 | 2021-06-22 | Angiotech Pharm Inc | process of formation of a self-retaining suture and self-retaining suture |
| US8916077B1 (en) | 2007-12-19 | 2014-12-23 | Ethicon, Inc. | Self-retaining sutures with retainers formed from molten material |
| US8118834B1 (en) | 2007-12-20 | 2012-02-21 | Angiotech Pharmaceuticals, Inc. | Composite self-retaining sutures and method |
| US8615856B1 (en) | 2008-01-30 | 2013-12-31 | Ethicon, Inc. | Apparatus and method for forming self-retaining sutures |
| ES2602570T3 (en) * | 2008-01-30 | 2017-02-21 | Ethicon Llc | Apparatus and method for forming self-retaining sutures |
| JP2011514182A (en) * | 2008-02-04 | 2011-05-06 | ザ トラスティーズ オブ コロンビア ユニバーシティ イン ザ シティ オブ ニューヨーク | Fluid separation apparatus, system, and method |
| EP2249712B8 (en) * | 2008-02-21 | 2018-12-26 | Ethicon LLC | Method and apparatus for elevating retainers on self-retaining sutures |
| US8216273B1 (en) | 2008-02-25 | 2012-07-10 | Ethicon, Inc. | Self-retainers with supporting structures on a suture |
| US8641732B1 (en) | 2008-02-26 | 2014-02-04 | Ethicon, Inc. | Self-retaining suture with variable dimension filament and method |
| US20090228021A1 (en) * | 2008-03-06 | 2009-09-10 | Leung Jeffrey C | Matrix material |
| JP5619726B2 (en) | 2008-04-15 | 2014-11-05 | エシコン・エルエルシーEthicon, LLC | Self-retaining suture with bidirectional retainer or unidirectional retainer |
| US8961560B2 (en) | 2008-05-16 | 2015-02-24 | Ethicon, Inc. | Bidirectional self-retaining sutures with laser-marked and/or non-laser marked indicia and methods |
| WO2010014021A1 (en) | 2008-07-30 | 2010-02-04 | Mesynthes Limited | Tissue scaffolds derived from forestomach extracellular matrix |
| US8932328B2 (en) | 2008-11-03 | 2015-01-13 | Ethicon, Inc. | Length of self-retaining suture and method and device for using the same |
| WO2011140283A2 (en) | 2010-05-04 | 2011-11-10 | Angiotech Pharmaceuticals, Inc. | Self-retaining systems having laser-cut retainers |
| EP2579787B1 (en) | 2010-06-11 | 2016-11-30 | Ethicon, LLC | Suture delivery tools for endoscopic and robot-assisted surgery |
| CN103747746B (en) | 2010-11-03 | 2017-05-10 | 伊西康有限责任公司 | Drug-eluting self-retaining sutures and methods relating thereto |
| MX342984B (en) | 2010-11-09 | 2016-10-19 | Ethicon Llc | Emergency self-retaining sutures and packaging. |
| WO2012129534A2 (en) | 2011-03-23 | 2012-09-27 | Angiotech Pharmaceuticals, Inc. | Self-retaining variable loop sutures |
| US20130172931A1 (en) | 2011-06-06 | 2013-07-04 | Jeffrey M. Gross | Methods and devices for soft palate tissue elevation procedures |
| EP2732832A3 (en) | 2012-11-14 | 2015-07-01 | Universitair Medisch Centrum Groningen (UMCG) | Drug delivery device comprising an active compound and a thermo-sensitive polymeric material |
| CN111926408A (en) * | 2020-07-06 | 2020-11-13 | 中国纺织科学研究院有限公司 | Purple poly (glycolide-lactide) fiber, preparation method and application thereof and surgical suture |
| CN111945247A (en) * | 2020-07-06 | 2020-11-17 | 中国纺织科学研究院有限公司 | Purple bright and clean polylactide and poly (glycolide-lactide) composite fiber, preparation method and application thereof and surgical suture |
Family Cites Families (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3297033A (en) * | 1963-10-31 | 1967-01-10 | American Cyanamid Co | Surgical sutures |
| US3442871A (en) * | 1966-05-04 | 1969-05-06 | American Cyanamid Co | Process for polymerizing a glycolide |
| US3422181A (en) * | 1966-05-23 | 1969-01-14 | American Cyanamid Co | Method for heat setting of stretch oriented polyglycolic acid filament |
| BE758156R (en) * | 1970-05-13 | 1971-04-28 | Ethicon Inc | ABSORBABLE SUTURE ELEMENT AND ITS |
| US3867190A (en) * | 1971-10-18 | 1975-02-18 | American Cyanamid Co | Reducing capillarity of polyglycolic acid sutures |
| US3736646A (en) * | 1971-10-18 | 1973-06-05 | American Cyanamid Co | Method of attaching surgical needles to multifilament polyglycolic acid absorbable sutures |
| US3839297A (en) * | 1971-11-22 | 1974-10-01 | Ethicon Inc | Use of stannous octoate catalyst in the manufacture of l(-)lactide-glycolide copolymer sutures |
| ZA782039B (en) * | 1977-05-23 | 1979-09-26 | American Cyanamid Co | Surgical articles |
-
1977
- 1977-06-24 US US05/809,737 patent/US4137921A/en not_active Expired - Lifetime
-
1978
- 1978-05-15 GB GB19544/78A patent/GB1595269A/en not_active Expired
- 1978-06-12 US US05/914,692 patent/US4157437A/en not_active Expired - Lifetime
- 1978-06-21 DE DE19782827289 patent/DE2827289A1/en active Granted
- 1978-06-22 CA CA306,056A patent/CA1124444A/en not_active Expired
- 1978-06-23 FR FR7818876A patent/FR2401185B1/en not_active Expired
Also Published As
| Publication number | Publication date |
|---|---|
| US4157437A (en) | 1979-06-05 |
| GB1595269A (en) | 1981-08-12 |
| FR2401185A1 (en) | 1979-03-23 |
| US4137921A (en) | 1979-02-06 |
| DE2827289A1 (en) | 1979-01-11 |
| DE2827289C2 (en) | 1989-01-12 |
| FR2401185B1 (en) | 1985-07-12 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA1124444A (en) | Addition copolymers of lactide and glycolide and method of preparation | |
| US4438253A (en) | Poly(glycolic acid)/poly(alkylene glycol) block copolymers and method of manufacturing the same | |
| CA1123984A (en) | Block copolymers of lactide and glycolide and surgical prosthesis therefrom | |
| US4243775A (en) | Synthetic polyester surgical articles | |
| US4441496A (en) | Copolymers of p-dioxanone and 2,5-morpholinediones and surgical devices formed therefrom having accelerated absorption characteristics | |
| CA1112795A (en) | Synthetic absorbable surgical devices of poly(alkylene oxalates) | |
| US3797499A (en) | Polylactide fabric graphs for surgical implantation | |
| US4605730A (en) | Surgical articles of copolymers of glycolide and ε-caprolactone and methods of producing the same | |
| US4300565A (en) | Synthetic polyester surgical articles | |
| US4700704A (en) | Surgical articles of copolymers of glycolide and ε-caprolactone and methods of producing the same | |
| US5486593A (en) | Medical devices fabricated from copolymers having recurring carbonate units | |
| US4205399A (en) | Synthetic absorbable surgical devices of poly(alkylene oxalates) | |
| US5120802A (en) | Polycarbonate-based block copolymers and devices | |
| JPH06122Y2 (en) | Synthetic copolymer surgical suture | |
| US4452973A (en) | Poly(glycolic acid)/poly(oxyethylene) triblock copolymers and method of manufacturing the same | |
| US5152781A (en) | Medical devices fabricated from homopolymers and copolymers having recurring carbonate units | |
| US4920203A (en) | Medical devices fabricated from homopolymers and copolymers having recurring carbonate units | |
| EP0113739B1 (en) | Polyester containing filament material | |
| US5145945A (en) | Homopolymers and copolymers having recurring carbonate units | |
| CA1124943A (en) | Synthetic absorbable surgical devices of poly-dioxanone | |
| US5007923A (en) | Crystalline copolyesters of amorphous (lactide/glycolide) and p-dioxanone | |
| US4838267A (en) | Glycolide/p-dioxanone block copolymers | |
| CA1224600A (en) | SURGICAL ARTICLES OF COPOLYMERS OF GLYCOLIDE AND .epsilon.- CAPROLACTONE AND METHODS OF PRODUCING THE SAME | |
| US7968656B2 (en) | Absorbable copolyesters of poly(ethoxyethylene diglycolate) and glycolide | |
| US5442032A (en) | Copolymers of 1,4-dioxepan-2-one and 1,5,8,12-tetraoxacyclotetradecane-7-14-dione |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKEX | Expiry |