CA2065906C - Absorbable composition - Google Patents
Absorbable composition Download PDFInfo
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- CA2065906C CA2065906C CA002065906A CA2065906A CA2065906C CA 2065906 C CA2065906 C CA 2065906C CA 002065906 A CA002065906 A CA 002065906A CA 2065906 A CA2065906 A CA 2065906A CA 2065906 C CA2065906 C CA 2065906C
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- Prior art keywords
- block copolymer
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- copolymer
- Prior art date
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- Expired - Lifetime
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- 239000000203 mixture Substances 0.000 title claims description 12
- 229920001400 block copolymer Polymers 0.000 claims abstract description 49
- 238000000034 method Methods 0.000 claims description 41
- RKDVKSZUMVYZHH-UHFFFAOYSA-N 1,4-dioxane-2,5-dione Chemical compound O=C1COC(=O)CO1 RKDVKSZUMVYZHH-UHFFFAOYSA-N 0.000 claims description 23
- 229920001577 copolymer Polymers 0.000 claims description 21
- 238000006243 chemical reaction Methods 0.000 claims description 20
- JJTUDXZGHPGLLC-UHFFFAOYSA-N lactide Chemical compound CC1OC(=O)C(C)OC1=O JJTUDXZGHPGLLC-UHFFFAOYSA-N 0.000 claims description 20
- 239000000178 monomer Substances 0.000 claims description 16
- VPVXHAANQNHFSF-UHFFFAOYSA-N 1,4-dioxan-2-one Chemical compound O=C1COCCO1 VPVXHAANQNHFSF-UHFFFAOYSA-N 0.000 claims description 14
- 239000003054 catalyst Substances 0.000 claims description 11
- KZMGYPLQYOPHEL-UHFFFAOYSA-N Boron trifluoride etherate Chemical compound FB(F)F.CCOCC KZMGYPLQYOPHEL-UHFFFAOYSA-N 0.000 claims description 10
- LYCAIKOWRPUZTN-UHFFFAOYSA-N Ethylene glycol Chemical compound OCCO LYCAIKOWRPUZTN-UHFFFAOYSA-N 0.000 claims description 10
- ADCOVFLJGNWWNZ-UHFFFAOYSA-N antimony trioxide Chemical compound O=[Sb]O[Sb]=O ADCOVFLJGNWWNZ-UHFFFAOYSA-N 0.000 claims description 10
- VXUYXOFXAQZZMF-UHFFFAOYSA-N titanium(IV) isopropoxide Chemical compound CC(C)O[Ti](OC(C)C)(OC(C)C)OC(C)C VXUYXOFXAQZZMF-UHFFFAOYSA-N 0.000 claims description 10
- 229920000359 diblock copolymer Polymers 0.000 claims description 9
- 230000000379 polymerizing effect Effects 0.000 claims description 9
- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 claims description 6
- TXUICONDJPYNPY-UHFFFAOYSA-N (1,10,13-trimethyl-3-oxo-4,5,6,7,8,9,11,12,14,15,16,17-dodecahydrocyclopenta[a]phenanthren-17-yl) heptanoate Chemical compound C1CC2CC(=O)C=C(C)C2(C)C2C1C1CCC(OC(=O)CCCCCC)C1(C)CC2 TXUICONDJPYNPY-UHFFFAOYSA-N 0.000 claims description 5
- RYSXWUYLAWPLES-MTOQALJVSA-N (Z)-4-hydroxypent-3-en-2-one titanium Chemical compound [Ti].C\C(O)=C\C(C)=O.C\C(O)=C\C(C)=O.C\C(O)=C\C(C)=O.C\C(O)=C\C(C)=O RYSXWUYLAWPLES-MTOQALJVSA-N 0.000 claims description 5
- ODNBVEIAQAZNNM-UHFFFAOYSA-N 1-(6-chloroimidazo[1,2-b]pyridazin-3-yl)ethanone Chemical compound C1=CC(Cl)=NN2C(C(=O)C)=CN=C21 ODNBVEIAQAZNNM-UHFFFAOYSA-N 0.000 claims description 5
- USYAMXSCYLGBPT-UHFFFAOYSA-L 3-carboxy-3-hydroxypentanedioate;tin(2+) Chemical compound [Sn+2].OC(=O)CC(O)(C([O-])=O)CC([O-])=O USYAMXSCYLGBPT-UHFFFAOYSA-L 0.000 claims description 5
- GUNJVIDCYZYFGV-UHFFFAOYSA-K Antimony trifluoride Inorganic materials F[Sb](F)F GUNJVIDCYZYFGV-UHFFFAOYSA-K 0.000 claims description 5
- 229910021626 Tin(II) chloride Inorganic materials 0.000 claims description 5
- 229910021627 Tin(IV) chloride Inorganic materials 0.000 claims description 5
- UKLDJPRMSDWDSL-UHFFFAOYSA-L [dibutyl(dodecanoyloxy)stannyl] dodecanoate Chemical compound CCCCCCCCCCCC(=O)O[Sn](CCCC)(CCCC)OC(=O)CCCCCCCCCCC UKLDJPRMSDWDSL-UHFFFAOYSA-L 0.000 claims description 5
- SMZOGRDCAXLAAR-UHFFFAOYSA-N aluminium isopropoxide Chemical compound [Al+3].CC(C)[O-].CC(C)[O-].CC(C)[O-] SMZOGRDCAXLAAR-UHFFFAOYSA-N 0.000 claims description 5
- VSCWAEJMTAWNJL-UHFFFAOYSA-K aluminium trichloride Chemical compound Cl[Al](Cl)Cl VSCWAEJMTAWNJL-UHFFFAOYSA-K 0.000 claims description 5
- PNOXNTGLSKTMQO-UHFFFAOYSA-L diacetyloxytin Chemical compound CC(=O)O[Sn]OC(C)=O PNOXNTGLSKTMQO-UHFFFAOYSA-L 0.000 claims description 5
- RJGHQTVXGKYATR-UHFFFAOYSA-L dibutyl(dichloro)stannane Chemical compound CCCC[Sn](Cl)(Cl)CCCC RJGHQTVXGKYATR-UHFFFAOYSA-L 0.000 claims description 5
- 239000012975 dibutyltin dilaurate Substances 0.000 claims description 5
- WGCNASOHLSPBMP-UHFFFAOYSA-N hydroxyacetaldehyde Natural products OCC=O WGCNASOHLSPBMP-UHFFFAOYSA-N 0.000 claims description 5
- 229910000464 lead oxide Inorganic materials 0.000 claims description 5
- YEXPOXQUZXUXJW-UHFFFAOYSA-N oxolead Chemical compound [Pb]=O YEXPOXQUZXUXJW-UHFFFAOYSA-N 0.000 claims description 5
- CCTFOFUMSKSGRK-UHFFFAOYSA-N propan-2-olate;tin(4+) Chemical compound [Sn+4].CC(C)[O-].CC(C)[O-].CC(C)[O-].CC(C)[O-] CCTFOFUMSKSGRK-UHFFFAOYSA-N 0.000 claims description 5
- 235000011150 stannous chloride Nutrition 0.000 claims description 5
- 239000001119 stannous chloride Substances 0.000 claims description 5
- HPGGPRDJHPYFRM-UHFFFAOYSA-J tin(iv) chloride Chemical compound Cl[Sn](Cl)(Cl)Cl HPGGPRDJHPYFRM-UHFFFAOYSA-J 0.000 claims description 5
- YUOWTJMRMWQJDA-UHFFFAOYSA-J tin(iv) fluoride Chemical compound [F-].[F-].[F-].[F-].[Sn+4] YUOWTJMRMWQJDA-UHFFFAOYSA-J 0.000 claims description 5
- KSBAEPSJVUENNK-UHFFFAOYSA-L tin(ii) 2-ethylhexanoate Chemical group [Sn+2].CCCCC(CC)C([O-])=O.CCCCC(CC)C([O-])=O KSBAEPSJVUENNK-UHFFFAOYSA-L 0.000 claims description 4
- 230000002040 relaxant effect Effects 0.000 claims description 3
- ISKQADXMHQSTHK-UHFFFAOYSA-N [4-(aminomethyl)phenyl]methanamine Chemical compound NCC1=CC=C(CN)C=C1 ISKQADXMHQSTHK-UHFFFAOYSA-N 0.000 claims 4
- 239000002685 polymerization catalyst Substances 0.000 claims 4
- 229920000642 polymer Polymers 0.000 description 11
- 238000004519 manufacturing process Methods 0.000 description 6
- 238000006116 polymerization reaction Methods 0.000 description 5
- 238000001727 in vivo Methods 0.000 description 4
- 239000000463 material Substances 0.000 description 4
- 238000001125 extrusion Methods 0.000 description 3
- JJTUDXZGHPGLLC-IMJSIDKUSA-N 4511-42-6 Chemical group C[C@@H]1OC(=O)[C@H](C)OC1=O JJTUDXZGHPGLLC-IMJSIDKUSA-N 0.000 description 2
- AEMRFAOFKBGASW-UHFFFAOYSA-N Glycolic acid Polymers OCC(O)=O AEMRFAOFKBGASW-UHFFFAOYSA-N 0.000 description 2
- 238000007334 copolymerization reaction Methods 0.000 description 2
- 230000014759 maintenance of location Effects 0.000 description 2
- 229920002463 poly(p-dioxanone) polymer Polymers 0.000 description 2
- 239000000622 polydioxanone Substances 0.000 description 2
- ZOXJGFHDIHLPTG-UHFFFAOYSA-N Boron Chemical compound [B] ZOXJGFHDIHLPTG-UHFFFAOYSA-N 0.000 description 1
- 241000272168 Laridae Species 0.000 description 1
- 229920000954 Polyglycolide Polymers 0.000 description 1
- ATJFFYVFTNAWJD-UHFFFAOYSA-N Tin Chemical compound [Sn] ATJFFYVFTNAWJD-UHFFFAOYSA-N 0.000 description 1
- 239000002253 acid Substances 0.000 description 1
- 229910052782 aluminium Inorganic materials 0.000 description 1
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 1
- 229910052787 antimony Inorganic materials 0.000 description 1
- WATWJIUSRGPENY-UHFFFAOYSA-N antimony atom Chemical compound [Sb] WATWJIUSRGPENY-UHFFFAOYSA-N 0.000 description 1
- 229910052796 boron Inorganic materials 0.000 description 1
- 150000001875 compounds Chemical class 0.000 description 1
- AYOHIQLKSOJJQH-UHFFFAOYSA-N dibutyltin Chemical compound CCCC[Sn]CCCC AYOHIQLKSOJJQH-UHFFFAOYSA-N 0.000 description 1
- 150000002148 esters Chemical class 0.000 description 1
- 239000000835 fiber Substances 0.000 description 1
- -1 glycolic acid ester Chemical class 0.000 description 1
- 229920001519 homopolymer Polymers 0.000 description 1
- 230000000704 physical effect Effects 0.000 description 1
- 239000011541 reaction mixture Substances 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 229920001059 synthetic polymer Polymers 0.000 description 1
- 229910052718 tin Inorganic materials 0.000 description 1
- 229910052719 titanium Inorganic materials 0.000 description 1
- 239000010936 titanium Substances 0.000 description 1
- 229920000428 triblock copolymer Polymers 0.000 description 1
- YFHICDDUDORKJB-UHFFFAOYSA-N trimethylene carbonate Chemical compound O=C1OCCCO1 YFHICDDUDORKJB-UHFFFAOYSA-N 0.000 description 1
- PAPBSGBWRJIAAV-UHFFFAOYSA-N ε-Caprolactone Chemical compound O=C1CCCCCO1 PAPBSGBWRJIAAV-UHFFFAOYSA-N 0.000 description 1
Classifications
-
- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G63/00—Macromolecular compounds obtained by reactions forming a carboxylic ester link in the main chain of the macromolecule
- C08G63/66—Polyesters containing oxygen in the form of ether groups
- C08G63/664—Polyesters containing oxygen in the form of ether groups derived from hydroxy carboxylic acids
-
- 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
The invention relates to a block copolymer which comprises a proportion of units having the formula:
as one of the blocks, and another of the blocks comprising a proportion of units having the formula:
and a proportion of units having the formula:
as one of the blocks, and another of the blocks comprising a proportion of units having the formula:
and a proportion of units having the formula:
Description
I
.:.~ ~ X03-432 (1204) 2~~~~~~, ABSORBABLE COMPOSITTON
BACKGROUND OF Z'HE INVENTION
1. Field of the Invention This invention relates to a copolymer, and more particularly to a surgical article manufactured from the copolymer and to a method of manufacturing the copolymer and surgical article.
2. Background of the Art Absorbable synthetic polymer sutures known in the prior art are usually manufactured, sold, and used as multifilament braids. The known absorbable polymers S containing a qlycolic acid ester linkage seem to be well suited for use in fabricating braided sutures. However, monofilament sutures fabricated from such polymers tend to be relatively stiff, particularly in the larger diameters.
Yet, some surgeons prefer the suturing characteristics of a 20 monofilament suture because of its smooth, continuousw surface. Thus, it has been recognized for some years that there is a need in surgery for flexible, absorbable, monofilament sutures which retain a safe and us~ful proportion of their strength for a relatively long period of 25 time in vivo. .
To be fully useful as an absorbable suture it is essential that a monofilament or multifilament not only be absorbable and flexible but it must also be capable of a ' relatively long period of in vivo strength retention. An~
30 appr°priate strength retention target for this type suture is considered to lae about 35-70 days in vivo. ' . " ' 35 .. .
I
-. , ~. ; ~ _2..
1 U.S. Patent No. 4,429,080 to Casey et al discloses a triblock copolymer wherein the end blocks comprise polyglycolide, and the middle block comprises a glycolide/trimethylene carbonate copolymer.
A new polymer has been developed for use in the fabrication of absorbable monofilament or mul~tifilament sutures.
SUMMARY OF THE TNVENTION
Provided herein is a block copolymer for use in the fabrication of bioabsorbable articles: and a method for making the same. The block copolymer is composed of glycolide as one block, and lactide/polydioxanone as the other block. The lactide/polydioxanone is first copolymerized at a first reaction temperature. The reaction temperature is then increased and glycolide i;a added to the reaction mixture. The resulting copolymer can be fabricated into both monofilament and multifilament absorbable sutures with advantageous flexibility and knot pull characteristics.
DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS
Bioabsorbable materials useful for fabricating surgical articles, such as sutures, surgical clips, etc., include homopolymers and copolymers of glycolide, lactide, (both glycolides and lactides are examples of hard phase forming monomers) 1-4-dioxanone, trimethylene carbonate, and caprolactone.
1 The present invention relates to a block copolymer having one block composed of units of glycolide:
O O
[-O-CHI-C-0-CH2-'C-]
and another black composed of units of L-lactide:
O O
[-O-CHCH3°~-O-CHCH3-C-]
copalymerized with randomly intermingled units of 1,4-dioxanone:
O
[ --O-CHZ -CHI -O-CHZ-i~-The block capolymer is preferably a diblock copolymer prepared by first capolymerizing the lactide manomer with 1,4-dioxanone and then polymerizing that copolymer with glycolide.
Catalysts suitable for carrying out the polymerization include compounds of tin, aluminum, antimony, lead, boron, and titanium. A preferred catalyst is stannous octoate. Other catalysts include stannous chloride, dibutyl tin dilaurate, dibutyl tin diacatate, dibutyl tin dichloride, stannic chloride pentahydrate, aluminum isopropoxide, antimony trioxide, stannic fluoride, stannous citrate, stannous acetate, antimony trifluoride, tin tetraisopropoxide, lead oxide, tetraisopropyl titanate, titanium acetyl acetonate, tetraoctylene~glycol titanate, boron trifluoride etherate, and aluminum trichloride.
The preferred composition range of the monomer units of the block copolymer in terms of weight % of the final block copolymer is set Earth below in Table 1.
.. -4-Block Cogolytner Composition weight per cent) Monomer unit Hroad Ranae Preferred Ranae glycolide 55% to 85% 65% to 75%
lactide I% to 20% 3% to 8%
1,4-dioxanone 10% to 40% 20% to 30%
In the examples below a preferred composition of the block copolymer of the present invention includes 70 wt%
of glycolide, 25.5 wt.% 1,4-dioxanone, and 4.5 wt.% lactide.
The polymerization reaction may be carried out at a temperature of from 100°C to 250°C. The first step is the polymerization of the lactide and 1,4-dioxanone, which is carried out at a temperature of between about 100°C and 150°C and preferably about 120°C. This reaction temperature is maintained until the polymerization is substantially completed, i.e., about 30 minutes.
The second step comprises raising the reaction temperature to between about 200°C az~d 250°C, and~adding glycolide preferably when the temperature has reached about 200°C. The glycolide will then copolymerize with the lactide/dioxanone copolymer to create a separate block in a diblock copolymer.
The resulting copolymer may then be sub3ected to further processing such as extruding, drawing, relaxing, etc.
The preferred area for use of the present:
invention is in the fabrication of sterile synthetic absorbable surgical articles, specifically sutures, wherein 1 glycolide is employed as the predominant monomer. The sutures may be either multifilament or monofilament.
Absorbable monofilament sutures fabricated from such copolymers have been found to be useful in that they are more flexible and more resistant to in vivo strength loss than corresponding size monafilament sutures fabricated from a polymer containing only glycolic acid ester linkage.
The surgical articles are fabricated from the copolymer using conventionally employed forming procedures, O such as extrusion, and subseguently sterilized. The resulting surgical articles are employed in a conventional manner.
Surgical sutures fabricated from the polymer of the present invention display good flexibility and knot pull strength.
The following examples illustrate~proaedures which are useful in can~unct~.on with the practice of the present invention but are not to be taken as being limiting thereto.
A conventional polymerization reactor was preheated to a temperature of 120°C. Quantities of 510 grams of 1,4-dioxanone, and 90 grams of L-lactide were added to the reactor with 0.2 grams of stannous oataate catalyst.
The reactor was held at 120°C. for 60 hours until copolymerization was substantially completed. A sample of the polymer, designated as Sample 1, was taken at this point: Then the reactor temperature was gradually increased. When the reactor temperature reached 180°C, Sample 2 was taken of the polymer. When the temperature reached 200°C, 100 grams of glycolide was added to create a 6-- .
1 block copolymer having at least one glycolide block and at least one lactide/dioxanone block. When the reactor temperature reached 220°C the polymer was stirred for 10 minutes. The polymer was then extruded and Sample 3 was taken. Samples 1, 2, and 3 were tested for inherent viscosity (dl/g), and enthalpy change (a H) in calories/gramr The enthalpy was measured on a differential scanning calorimeter which measured the specific heat of the sample over a range of temperatures with a scan rate of 20°C/anin. The change in enthalpy is an indication of the extent of crystallinity.
The inherent viscosity of a polymer is an indicator of its molecular weight, and was measured for the above-mentioned samples in accordance with standard measuring techniques arid equipment known to those skilled in the art.
Table 2 below sets forth inherent viscosity and enthalpy data for samples 1, 2, and 3.
Enthalpy Sample Inherent Viscositv ~(~H) _ 1 Or61 11.1 @ 59°C
2 0.61 10.63 @ 332°C
.:.~ ~ X03-432 (1204) 2~~~~~~, ABSORBABLE COMPOSITTON
BACKGROUND OF Z'HE INVENTION
1. Field of the Invention This invention relates to a copolymer, and more particularly to a surgical article manufactured from the copolymer and to a method of manufacturing the copolymer and surgical article.
2. Background of the Art Absorbable synthetic polymer sutures known in the prior art are usually manufactured, sold, and used as multifilament braids. The known absorbable polymers S containing a qlycolic acid ester linkage seem to be well suited for use in fabricating braided sutures. However, monofilament sutures fabricated from such polymers tend to be relatively stiff, particularly in the larger diameters.
Yet, some surgeons prefer the suturing characteristics of a 20 monofilament suture because of its smooth, continuousw surface. Thus, it has been recognized for some years that there is a need in surgery for flexible, absorbable, monofilament sutures which retain a safe and us~ful proportion of their strength for a relatively long period of 25 time in vivo. .
To be fully useful as an absorbable suture it is essential that a monofilament or multifilament not only be absorbable and flexible but it must also be capable of a ' relatively long period of in vivo strength retention. An~
30 appr°priate strength retention target for this type suture is considered to lae about 35-70 days in vivo. ' . " ' 35 .. .
I
-. , ~. ; ~ _2..
1 U.S. Patent No. 4,429,080 to Casey et al discloses a triblock copolymer wherein the end blocks comprise polyglycolide, and the middle block comprises a glycolide/trimethylene carbonate copolymer.
A new polymer has been developed for use in the fabrication of absorbable monofilament or mul~tifilament sutures.
SUMMARY OF THE TNVENTION
Provided herein is a block copolymer for use in the fabrication of bioabsorbable articles: and a method for making the same. The block copolymer is composed of glycolide as one block, and lactide/polydioxanone as the other block. The lactide/polydioxanone is first copolymerized at a first reaction temperature. The reaction temperature is then increased and glycolide i;a added to the reaction mixture. The resulting copolymer can be fabricated into both monofilament and multifilament absorbable sutures with advantageous flexibility and knot pull characteristics.
DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS
Bioabsorbable materials useful for fabricating surgical articles, such as sutures, surgical clips, etc., include homopolymers and copolymers of glycolide, lactide, (both glycolides and lactides are examples of hard phase forming monomers) 1-4-dioxanone, trimethylene carbonate, and caprolactone.
1 The present invention relates to a block copolymer having one block composed of units of glycolide:
O O
[-O-CHI-C-0-CH2-'C-]
and another black composed of units of L-lactide:
O O
[-O-CHCH3°~-O-CHCH3-C-]
copalymerized with randomly intermingled units of 1,4-dioxanone:
O
[ --O-CHZ -CHI -O-CHZ-i~-The block capolymer is preferably a diblock copolymer prepared by first capolymerizing the lactide manomer with 1,4-dioxanone and then polymerizing that copolymer with glycolide.
Catalysts suitable for carrying out the polymerization include compounds of tin, aluminum, antimony, lead, boron, and titanium. A preferred catalyst is stannous octoate. Other catalysts include stannous chloride, dibutyl tin dilaurate, dibutyl tin diacatate, dibutyl tin dichloride, stannic chloride pentahydrate, aluminum isopropoxide, antimony trioxide, stannic fluoride, stannous citrate, stannous acetate, antimony trifluoride, tin tetraisopropoxide, lead oxide, tetraisopropyl titanate, titanium acetyl acetonate, tetraoctylene~glycol titanate, boron trifluoride etherate, and aluminum trichloride.
The preferred composition range of the monomer units of the block copolymer in terms of weight % of the final block copolymer is set Earth below in Table 1.
.. -4-Block Cogolytner Composition weight per cent) Monomer unit Hroad Ranae Preferred Ranae glycolide 55% to 85% 65% to 75%
lactide I% to 20% 3% to 8%
1,4-dioxanone 10% to 40% 20% to 30%
In the examples below a preferred composition of the block copolymer of the present invention includes 70 wt%
of glycolide, 25.5 wt.% 1,4-dioxanone, and 4.5 wt.% lactide.
The polymerization reaction may be carried out at a temperature of from 100°C to 250°C. The first step is the polymerization of the lactide and 1,4-dioxanone, which is carried out at a temperature of between about 100°C and 150°C and preferably about 120°C. This reaction temperature is maintained until the polymerization is substantially completed, i.e., about 30 minutes.
The second step comprises raising the reaction temperature to between about 200°C az~d 250°C, and~adding glycolide preferably when the temperature has reached about 200°C. The glycolide will then copolymerize with the lactide/dioxanone copolymer to create a separate block in a diblock copolymer.
The resulting copolymer may then be sub3ected to further processing such as extruding, drawing, relaxing, etc.
The preferred area for use of the present:
invention is in the fabrication of sterile synthetic absorbable surgical articles, specifically sutures, wherein 1 glycolide is employed as the predominant monomer. The sutures may be either multifilament or monofilament.
Absorbable monofilament sutures fabricated from such copolymers have been found to be useful in that they are more flexible and more resistant to in vivo strength loss than corresponding size monafilament sutures fabricated from a polymer containing only glycolic acid ester linkage.
The surgical articles are fabricated from the copolymer using conventionally employed forming procedures, O such as extrusion, and subseguently sterilized. The resulting surgical articles are employed in a conventional manner.
Surgical sutures fabricated from the polymer of the present invention display good flexibility and knot pull strength.
The following examples illustrate~proaedures which are useful in can~unct~.on with the practice of the present invention but are not to be taken as being limiting thereto.
A conventional polymerization reactor was preheated to a temperature of 120°C. Quantities of 510 grams of 1,4-dioxanone, and 90 grams of L-lactide were added to the reactor with 0.2 grams of stannous oataate catalyst.
The reactor was held at 120°C. for 60 hours until copolymerization was substantially completed. A sample of the polymer, designated as Sample 1, was taken at this point: Then the reactor temperature was gradually increased. When the reactor temperature reached 180°C, Sample 2 was taken of the polymer. When the temperature reached 200°C, 100 grams of glycolide was added to create a 6-- .
1 block copolymer having at least one glycolide block and at least one lactide/dioxanone block. When the reactor temperature reached 220°C the polymer was stirred for 10 minutes. The polymer was then extruded and Sample 3 was taken. Samples 1, 2, and 3 were tested for inherent viscosity (dl/g), and enthalpy change (a H) in calories/gramr The enthalpy was measured on a differential scanning calorimeter which measured the specific heat of the sample over a range of temperatures with a scan rate of 20°C/anin. The change in enthalpy is an indication of the extent of crystallinity.
The inherent viscosity of a polymer is an indicator of its molecular weight, and was measured for the above-mentioned samples in accordance with standard measuring techniques arid equipment known to those skilled in the art.
Table 2 below sets forth inherent viscosity and enthalpy data for samples 1, 2, and 3.
Enthalpy Sample Inherent Viscositv ~(~H) _ 1 Or61 11.1 @ 59°C
2 0.61 10.63 @ 332°C
3 0.90 14.99 @ 211°C
. . . _'7 .., 1 The above data indicate that sample 3, which was taken from the polymer after the glycolide was copolymerized with the lactide/dioxanone capolymer, exhibited a higher inherent viscosity and, therefore, a higher molecular weight. This indicates copolymerization of the glycolide occurred. Also shown is a greater a H, which indicates a greater degree of crystallinity. These physical properties, i.e., higher molecular weight and greater crystallinity, indicate that the material is suitable for fabrication into a fiber.
The block copolymer of Example 1 was extruded, ground and dried at from 20 to 120°C at a pressure of less than l0 torr. The resulting material was then formed by extrusion into a monofilament with an Instron rheometer (Dc=0.0301"; Lc=1.001"~ at a temperature of 203°C. The extrusion speed was 3 inches per minute. The monofilament was then dried at room temperature overnight. The monofilament was then drawn at a 4.5x draw ratio in an oven at 60°C by being passed around two godgets. The first godget providing a linear tangential velocity of 10 feet per minute and the second~godget providing a linear tangential velocity of 45 feet per minute.
The drawn monofilament was then tested for straight pull and knot pull strength. An Instron Series 1X
Automated Materials Testing System v4.03e was, employed with the following parameters and oonditions: Interface type 1011 series: Sample rate = 20.00 pts/sec.: crosshead speed =
2.0 inches/min.; humidity = 50%~ temperature = 73°F.
' ' w8°
1 Specimens of the monofilament were tested and the results of the testing are set forth below in Table 3.
(Specimen diameter = 0.0073 inches/0.1854 mm) STRAIGHT PULL KNOT-PULL
Avg. load @ maximum load (lbs.> 3.111 2.780 Avg. Elongation at maximum load % 27.59 22.470 Avg. Young's P3odulus (kpsi) 541.8 ---°
The filament of Example 2 was then subjected to controlled shrinkage or relaxation in accordance with the following method.
The manofilament was placed in a hat air oven at a temperature of 75°C far 10 minutes. The length of the filament before treatment was 91.8cm. After treatment, the filament length was 82.6cm. Thus, the observed shrinkage was 10%.
After relaxation, the filament was tested for inherent viscosity and mechanical properties in accordance with the methods as described in Examples 1 arid 2: The results of the testing are set forth below in Table 4.
.. ) Post shrinkage data Inherent viscosity 0.79/0.82 Diameter 0.209mm (.00823 inches) Avg, load 1.24 kg (2.728 lbs.) at maximum load (knot pull) Avg. load at 1.45 kg (3.20 lbs.) 'o maximum load (straight pull) Elongation at 39~
maximum load (straight pull) Young's Modules 513>2 kpsi (straight gull) The data of the above examples indicate that the copolymer of the present invention is advantageous for the manufacture~of a monofilament suture. The black copolymer described above is bioabsorbable and, as seen from the Young°s modules value, is flexible, strong, and possesses advantageous handling characteristics.
. . . _'7 .., 1 The above data indicate that sample 3, which was taken from the polymer after the glycolide was copolymerized with the lactide/dioxanone capolymer, exhibited a higher inherent viscosity and, therefore, a higher molecular weight. This indicates copolymerization of the glycolide occurred. Also shown is a greater a H, which indicates a greater degree of crystallinity. These physical properties, i.e., higher molecular weight and greater crystallinity, indicate that the material is suitable for fabrication into a fiber.
The block copolymer of Example 1 was extruded, ground and dried at from 20 to 120°C at a pressure of less than l0 torr. The resulting material was then formed by extrusion into a monofilament with an Instron rheometer (Dc=0.0301"; Lc=1.001"~ at a temperature of 203°C. The extrusion speed was 3 inches per minute. The monofilament was then dried at room temperature overnight. The monofilament was then drawn at a 4.5x draw ratio in an oven at 60°C by being passed around two godgets. The first godget providing a linear tangential velocity of 10 feet per minute and the second~godget providing a linear tangential velocity of 45 feet per minute.
The drawn monofilament was then tested for straight pull and knot pull strength. An Instron Series 1X
Automated Materials Testing System v4.03e was, employed with the following parameters and oonditions: Interface type 1011 series: Sample rate = 20.00 pts/sec.: crosshead speed =
2.0 inches/min.; humidity = 50%~ temperature = 73°F.
' ' w8°
1 Specimens of the monofilament were tested and the results of the testing are set forth below in Table 3.
(Specimen diameter = 0.0073 inches/0.1854 mm) STRAIGHT PULL KNOT-PULL
Avg. load @ maximum load (lbs.> 3.111 2.780 Avg. Elongation at maximum load % 27.59 22.470 Avg. Young's P3odulus (kpsi) 541.8 ---°
The filament of Example 2 was then subjected to controlled shrinkage or relaxation in accordance with the following method.
The manofilament was placed in a hat air oven at a temperature of 75°C far 10 minutes. The length of the filament before treatment was 91.8cm. After treatment, the filament length was 82.6cm. Thus, the observed shrinkage was 10%.
After relaxation, the filament was tested for inherent viscosity and mechanical properties in accordance with the methods as described in Examples 1 arid 2: The results of the testing are set forth below in Table 4.
.. ) Post shrinkage data Inherent viscosity 0.79/0.82 Diameter 0.209mm (.00823 inches) Avg, load 1.24 kg (2.728 lbs.) at maximum load (knot pull) Avg. load at 1.45 kg (3.20 lbs.) 'o maximum load (straight pull) Elongation at 39~
maximum load (straight pull) Young's Modules 513>2 kpsi (straight gull) The data of the above examples indicate that the copolymer of the present invention is advantageous for the manufacture~of a monofilament suture. The black copolymer described above is bioabsorbable and, as seen from the Young°s modules value, is flexible, strong, and possesses advantageous handling characteristics.
Claims (53)
1. A block copolymer which comprises a proportion of units having the formula:
as one of said blocks, and another of said blocks comprising a proportion of units having the formula:
and a proportion of units having the formula:
said units of formula (II) and formula (III) being randomly combined.
as one of said blocks, and another of said blocks comprising a proportion of units having the formula:
and a proportion of units having the formula:
said units of formula (II) and formula (III) being randomly combined.
2. The block copolymer of claim 1, wherein said block copolymer is a diblock copolymer.
3. The block copolymer of claim 1 or 2, wherein from about 55 weight % to about 85 weight % of the block copolymer comprises units of formula (I), from about 1 weight % to about 20 weight % of the block copolymer comprises units of formula (II), and from about 10 weight % to about 40 weight % of the block copolymer: comprises units of formula (III).
4. A surgical article manufactured from a block copolymer which comprises a proportion of units having the formula:
as one of said blocks, and another of said blocks comprising a proportion of units having the formula:
and a proportion of units having the formula:
said units of formula (II) and formula (III) being randomly combined.
as one of said blocks, and another of said blocks comprising a proportion of units having the formula:
and a proportion of units having the formula:
said units of formula (II) and formula (III) being randomly combined.
5. The surgical article of claim 4, wherein said block copolymer is a diblock copolymer.
6. The surgical article of claim 4 or 5, wherein said surgical article is a suture.
7. The surgical article of claim 6, wherein said suture is a monofilament suture.
8. The surgical article of any one of claims 4 to 7, wherein from about 55 weight % to about 85 weight % of the block copolymer comprises units of formula (I), and from about 1 weight % to about 20 weight % of the block copolymer comprises units of formula (II), and from about 10 weight % to about 40 weight % of the block copolymer comprises units of formula (III).
9. A method for preparing a bioabsorbable block copolymer, comprising:
(a) polymerizing a mixture of lactide and 1,4-dioxanone at a first reaction temperature to create a copolymer thereof;
(b) polymerizing glycolide wth the lactide/1,4-dioxanone copolymer of step (a) at a second reaction temperature to create the bioabsorbable block copolymer.
(a) polymerizing a mixture of lactide and 1,4-dioxanone at a first reaction temperature to create a copolymer thereof;
(b) polymerizing glycolide wth the lactide/1,4-dioxanone copolymer of step (a) at a second reaction temperature to create the bioabsorbable block copolymer.
10. The method of claim 9, wherein said first reaction temperature comprises a temperature of from about 100°C to about 150°C.
11. The method of claim 9 or 10, wherein said second reaction temperature comprises a temperature of from about 200°C to about 250°C.
12. The method of any one of claims 9 to 11, wherein step (a) is carried out in the presence of a polymerization catalyst.
13. The method of claim 12, wherein said catalyst is selected from the group consisting of stannous chloride, dibutyl tin dilaurate, dibutyl tin diacetate, dibutyl tin dichloride, stannic chloride pentahydrate, aluminum isopropoxide, antimony trioxide, stannic fluoride, stannous citrate, stannous acetate, antimony trifluoride, tin tetraisopropoxide, lead oxide, tetraisopropyl titanate, titanium acetyl acetonate, tetraoctylene glycol titanate, boron trifluoride etherate, and aluminum trichloride.
14. A method for making a bioabsorbable surgical article, comprising:
(a) polymerizing a mixture of lactide and 1,4-dioxanone at a first reaction temperature to create a copolymer thereof;
(b) polymerizing glycolide with the lactide/1,4-dioxanone copolymer of step (a) at a second reaction temperature to create a bioabsorbable block copolymer;
(c) forming said block copolymer.
(a) polymerizing a mixture of lactide and 1,4-dioxanone at a first reaction temperature to create a copolymer thereof;
(b) polymerizing glycolide with the lactide/1,4-dioxanone copolymer of step (a) at a second reaction temperature to create a bioabsorbable block copolymer;
(c) forming said block copolymer.
15. The method of claim 14, wherein said forming includes the step of extruding the block copolymer into a filament.
16. The method of claim 14 or 15, wherein the bioabsorbable surgical article comprises a suture.
17. The method of any one of claims 14 to 16, wherein said first reaction temperature comprises a temperature of from about 100°C to about 150°C.
18. The method of any one of claims 14 to 17, wherein said second reaction temperature comprises a temperature of from about 200°C to about 250°C.
19. The method of any one of claims 14 to 18, wherein step (a) is carried out in the presence of a polymerization catalyst.
20. The method of any one of claims 14 to 19, wherein from about 55 weight to about 85 weight % of the block copolymer comprises units derived from glycolide, from about 1 weight % to about 20 weight % of the block copolymer comprises units derived from lactide and from about 10 weight to about 40 weight % of the block copolymer comprises units derived from 1,4-dioxanone.
21. The method of claim 16, additionally comprising drawing the suture and relaxing the suture.
22. The method of any one of claims 14 to 21, wherein said block copolymer is a diblock copolymer.
23. The method of claim 19, wherein said catalyst is stannous octoate.
24. The method of claim 19, wherein said catalyst is selected from the group consisting of stannous chloride, dibutyl tin dilaurate, dibutyl tin diacetate, dibutyl tin dichloride, stannic chloride pentahydrate, aluminum isopropoxide, antimony trioxide, stannic fluoride, stannous citrate, stannous acetate, antimony trifluoride, tin tetraisopropoxide, lead oxide, tetraisopropyl titanate, titanium acetyl acetonate, tetraoctylene glycol titanate, boron trifluoride etherate, and aluminum trichloride.
25. A block copolymer which comprises a proportion of units of one or more hard phase forming monomers as one of said blocks, and another of said blocks comprising a proportion of units having the formula:
randomly combined with a proportion of units of one or more hard phase forming monomers, said hard phase forming monomers selected from the group consisting of glycolide, lactide and mixtures thereof.
randomly combined with a proportion of units of one or more hard phase forming monomers, said hard phase forming monomers selected from the group consisting of glycolide, lactide and mixtures thereof.
26. The block copolymer of claim 25, wherein said block copolymer is a diblock copolymer.
27. The block copolymer of any one of claims 25 to 26, wherein from about 1 weight % to about 20 weight % of the block copolymer comprises units having the formula:
28. The block copolymer of any one of claims 25 to 26, wherein the hard phase forming monomers comprise about 10 weight % to about 40 weight % of the block containing units of formula:
29. A surgical article manufactured from a block copolymer which comprises a proportion of units of one or more hard phase forming momoners as one of said blocks, and another of said blocks comprising a proportion of units having the formula:
randomly combined with a proportion of units of one or more hard phase forming monomers, said hard phase forming monomers selected from the group consisting of glycolide, lactide and mixtures thereof.
randomly combined with a proportion of units of one or more hard phase forming monomers, said hard phase forming monomers selected from the group consisting of glycolide, lactide and mixtures thereof.
30. The surgical article of claim 29, wherein said block copolymer is a diblock copolymer.
31. The surgical article of claim 29 or 30, wherein said surgical article is a suture.
32. The surgical article of claim 31, wherein said suture is a monofilament suture.
33. The surgical article of any one of claims 29 to 32, wherein from about 1 weight % to about 20 weight % of the block copolymer comprises units having the formula:
34. A method for preparing a bioabsorbable block copolymer, comprising:
(a) polymerizing a mixture of one or more hard phase forming monomers and 1,4-dioxan 2-one at a first reaction temperature to create a copolymer thereof;
(b) polymerizing one or more hard phase forming monomers with the copolymer of step (a) at a second reaction temperature to create the bioabsorbable block copolymer, wherein said hard phase forming monomers are selected from the group consisting of glycolide, lactide and mixtures thereof.
(a) polymerizing a mixture of one or more hard phase forming monomers and 1,4-dioxan 2-one at a first reaction temperature to create a copolymer thereof;
(b) polymerizing one or more hard phase forming monomers with the copolymer of step (a) at a second reaction temperature to create the bioabsorbable block copolymer, wherein said hard phase forming monomers are selected from the group consisting of glycolide, lactide and mixtures thereof.
35. The method of claim 34, wherein said block copolymer is a diblock copolymer.
36. The method of claim 34 or 35, wherein said first reaction temperature comprises a temperature of from about 100°C to about 150°C.
37. The method of any one of claims 34 to 36, wherein said second reaction temperature comprises a temperature of from about 200°C to about 250°C.
38. The method of any one of claims 34 to 37, wherein step (a) is carried out in the presence of a polymerization catalyst.
39. The method of claim 38, wherein said catalyst is stannous octoate.
40. The method of claim 38, wherein said catalyst is selected from the group consisting of stannous chloride, dibutyl tin dilaurate, dibutyl tin diacetate, dibutyl tin dichloride, stannic chloride pentahydrate, aluminum isopropoxide, antimony trioxide, stannic fluoride, stannous citrate, stannous acetate, antimony trifluoride, tin tetraisopropoxide, lead oxide, tetraisopropyl titanate, titanium acetyl acetonate, tetraoctylene glycol titanate, boron trifluoride etherate, and aluminum trichloride.
41. A method for making a bioabsorbable surgical article, comprising:
(a) polymerizing a mixture of one or more hard phase forming monomers and 1,4-dioxan-2-one at a first reaction temperature to create a copolymer thereof;
(b) polymerizing one or more hard phase forming monomers with the copolymer of step (a) at a second reaction temperature to create a bioabsorbable block copolymer;
(c) forming a surgical article from said block copolymer;
wherein said hard phase forming monomers are selected from the group consisting of glycolide, lactide and mixtures thereof.
(a) polymerizing a mixture of one or more hard phase forming monomers and 1,4-dioxan-2-one at a first reaction temperature to create a copolymer thereof;
(b) polymerizing one or more hard phase forming monomers with the copolymer of step (a) at a second reaction temperature to create a bioabsorbable block copolymer;
(c) forming a surgical article from said block copolymer;
wherein said hard phase forming monomers are selected from the group consisting of glycolide, lactide and mixtures thereof.
42. The method of claim 41, wherein said forming includes the step of extruding the block copolymer into a filament.
43. The method of claim 41 or 42, wherein the bioabsorbable surgical article comprises a suture.
44. The method of claim 43, additionally comprising drawing the suture and relaxing the suture.
45. The method of any one of claims 41 to 44, wherein said block copolymer is a diblock copolymer.
46. The method of any one of claims 41 to 45, wherein said first reaction temperature comprises a temperature of from about 100°C to about 150°C.
47. The method of any one of claim 41 to 46, wherein said second reaction temperature comprises a temperature of from about 200°C to about 250°C.
48. The method of any one of claims 41 to 47, wherein step (a) is carried out in the presence of a polymerization catalyst.
49. The method of claim 48, wherein the catalyst is stannous octoate.
50. The method of claim 48, wherein said catalyst is selected from the group consisting of stannous chloride, dibutyl tin dilaurate, dibutyl tin diacetate, dibutyl tin dichloride, stannic chloride pentahydrate, aluminum isopropoxide, antimony trioxide, stannic fluoride, stannous citrate, stannous acetate, antimony trifluoride, tin tetraisopropoxide, lead oxide, tetraisopropyl titanate, titanium acetyl acetonate, tetraoctylene glycol titanate, boron trifluoride etherate, and aluminum trichloride.
51. The method of any one of claims 41 to 50, wherein from about 55 weight %
to about 85 weight % of the block copolymer comprises units derived from glycolide.
to about 85 weight % of the block copolymer comprises units derived from glycolide.
52. The method of any one of claims 41 to 50, wherein from about 1 weight % to about 20 weight % of the block copolymer comprises units derived from lactide.
53. The method of any one of claims 41 to 50, wherein from about 10 weight %
to about 40 weight % of the block copolymer comprises units derived from 1,4-dioxan-2-one.
to about 40 weight % of the block copolymer comprises units derived from 1,4-dioxan-2-one.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/686,815 | 1991-04-17 | ||
| US07/686,815 US5225520A (en) | 1991-04-17 | 1991-04-17 | Absorbable composition |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2065906A1 CA2065906A1 (en) | 1992-10-18 |
| CA2065906C true CA2065906C (en) | 2003-07-08 |
Family
ID=24757882
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002065906A Expired - Lifetime CA2065906C (en) | 1991-04-17 | 1992-04-13 | Absorbable composition |
Country Status (5)
| Country | Link |
|---|---|
| US (2) | US5225520A (en) |
| EP (1) | EP0509508B1 (en) |
| CA (1) | CA2065906C (en) |
| DE (1) | DE69233481T2 (en) |
| ES (1) | ES2238672T3 (en) |
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| US5502159A (en) * | 1991-04-17 | 1996-03-26 | United States Surgical Corporation | Absorbable composition |
| US5403347A (en) * | 1993-05-27 | 1995-04-04 | United States Surgical Corporation | Absorbable block copolymers and surgical articles fabricated therefrom |
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| US4438253A (en) * | 1982-11-12 | 1984-03-20 | American Cyanamid Company | Poly(glycolic acid)/poly(alkylene glycol) block copolymers and method of manufacturing the same |
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-
1991
- 1991-04-17 US US07/686,815 patent/US5225520A/en not_active Expired - Lifetime
-
1992
- 1992-04-13 CA CA002065906A patent/CA2065906C/en not_active Expired - Lifetime
- 1992-04-16 ES ES92106629T patent/ES2238672T3/en not_active Expired - Lifetime
- 1992-04-16 EP EP92106629A patent/EP0509508B1/en not_active Expired - Lifetime
- 1992-04-16 DE DE69233481T patent/DE69233481T2/en not_active Expired - Lifetime
-
1993
- 1993-05-03 US US08/058,515 patent/US5314989A/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| DE69233481T2 (en) | 2006-01-12 |
| EP0509508B1 (en) | 2005-02-23 |
| DE69233481D1 (en) | 2005-03-31 |
| EP0509508A2 (en) | 1992-10-21 |
| US5314989A (en) | 1994-05-24 |
| CA2065906A1 (en) | 1992-10-18 |
| US5225520A (en) | 1993-07-06 |
| EP0509508A3 (en) | 1992-11-25 |
| ES2238672T3 (en) | 2005-09-01 |
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