CA2168822A1 - Utilization of biocompatible adhesive/sealant materials for securing surgical devices - Google Patents
Utilization of biocompatible adhesive/sealant materials for securing surgical devicesInfo
- Publication number
- CA2168822A1 CA2168822A1 CA002168822A CA2168822A CA2168822A1 CA 2168822 A1 CA2168822 A1 CA 2168822A1 CA 002168822 A CA002168822 A CA 002168822A CA 2168822 A CA2168822 A CA 2168822A CA 2168822 A1 CA2168822 A1 CA 2168822A1
- Authority
- CA
- Canada
- Prior art keywords
- group
- surgical device
- sealant
- repeating units
- adhesive
- 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.)
- Abandoned
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
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
- A61L24/046—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
-
- 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
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/02—Surgical adhesives or cements; Adhesives for colostomy devices containing inorganic materials
-
- 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
- A61L24/00—Surgical adhesives or cements; Adhesives for colostomy devices
- A61L24/04—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials
- A61L24/06—Surgical adhesives or cements; Adhesives for colostomy devices containing macromolecular materials obtained by reactions only involving carbon-to-carbon unsaturated bonds
Abstract
A process for enhancing the security of implantable surgical devices secured to bone tissue comprising implanting in bone tissue a surgical device with a biocompatible adhesive and/or sealant selected from the group consisting of:
(a) a material made from monomers of the formula:
CHR1=CX1Y1 wherein X1 and Y1 are each strong electron withdrawing groups, and R1 is hydrogen or, provided that X1 and Y1 are both cyano groups, a C1-C4 alkyl group;
(b) a semi-crystalline aliphatic poly(ester) of the formula:
[-O-R11-C(O)-]y, wherein R11 is selected from the group consisting of -CR12H-, -(CH2)3-O-, -CH2-CH2-O-CH2-, CR12H-CH2, -(CH2)4-, -(CH2)z-O-C(O)- and -(CH2)z-C(O)-CH2-; R12 is hydrogen or methyl; z is an integer in the range of from 1 to 7 and y is an integer in the range of from about 10 to about 20,000; and (c) a slurry of water and a calcium containing compounds with the general formula:
M2+10-nN1+2n(WO43-)6mU2-where n is an integer from 1 to 10, and m is 2 when x is 1, or m is 1 when x is 2, M and N are alkali or alkaline earth metals; WO4 is an acid radical and W is phosphorus, vanadium, sulfur, siliccn, or is substituted in whole or part with carbonate (CO32-);
and U is a halide, hydroxide, or carbonate; pro in an amount effective to increase the amoun force necessary to remove the implanted surgical device. Additionally provided is a surgical device that is at least partially coated with at least one biocompatible adhesive and/or sealant.
(a) a material made from monomers of the formula:
CHR1=CX1Y1 wherein X1 and Y1 are each strong electron withdrawing groups, and R1 is hydrogen or, provided that X1 and Y1 are both cyano groups, a C1-C4 alkyl group;
(b) a semi-crystalline aliphatic poly(ester) of the formula:
[-O-R11-C(O)-]y, wherein R11 is selected from the group consisting of -CR12H-, -(CH2)3-O-, -CH2-CH2-O-CH2-, CR12H-CH2, -(CH2)4-, -(CH2)z-O-C(O)- and -(CH2)z-C(O)-CH2-; R12 is hydrogen or methyl; z is an integer in the range of from 1 to 7 and y is an integer in the range of from about 10 to about 20,000; and (c) a slurry of water and a calcium containing compounds with the general formula:
M2+10-nN1+2n(WO43-)6mU2-where n is an integer from 1 to 10, and m is 2 when x is 1, or m is 1 when x is 2, M and N are alkali or alkaline earth metals; WO4 is an acid radical and W is phosphorus, vanadium, sulfur, siliccn, or is substituted in whole or part with carbonate (CO32-);
and U is a halide, hydroxide, or carbonate; pro in an amount effective to increase the amoun force necessary to remove the implanted surgical device. Additionally provided is a surgical device that is at least partially coated with at least one biocompatible adhesive and/or sealant.
Description
Utilization of Biocompatible ~hs~ive/8ealant ~aterials for 8ecuring 8urgical Devices Field of the Invention This invention relates to securing surgical repair devices to tissue, more specifically this invention relates to securing surgical devices such as screws, plates, bone pins and anchors to bone tissue.
Background of the Invention In orthopedic surgery it is often necessary to reattach cartilage and ligaments to skeletal bones with surgical pins, screws or anchors. For example, metallic ~uL~Ie anchors are currently used to facilitate cartilage or ligament reattachment. In these procedures a hole is drilled into the skeletal bone. A -uLu~e anchor, attached to a ~Lule, is then inserted into the hole in a manner that allows the anchor to engage the sides of the hole and be held in place. The suture is then used to secure the torn cartilage or ligament to the bone.
However, sometimes during or after the healing process these anchors fail to remain in place and must be removed to avoid harm to the patient.
Rec ntly, absorbable ~Lu~e AnchQrs have been proposed as a replacement for metallic ~uLu~e anchors. The perceived advantage of an absorbable anchor over the metallic AnchQr is that after the healing process for the cartilage or ligament is complete the anchor will be absorbed by the patient's body and disappear. However, most bioabsorbable materials are not strong enough to dig into bone tissue. Therefore, bioabsorbable bone ~T~-~014 `- 216~822 anchors tend to have less resistance to being pulled out of the location in which it is secured.
Thus, it would be a significant contribution to the art to provide a method to enhance the secure placement of implantable surgical devices in patients. Additionally, it would be advantageous if a method could be developed to enhance the resistance to removal of bioabsorbable surgical implantable devices.
Summary of the Invention We have discovered a process for enhancing the security of implantable surgical devices secured to bone tissue comprising implanting a surgical device with a biocompatible adhesive and/or sealant provided in an amount effective to increase the security of the implanted surgical device.
In another emhoAiment of the present invention we have also provided an implantable surgical device comprising an implantable surgical device coated with a biocompatible adhesive or sealant.
Detailed Description of the Invention The present invention provides a process for using a surgical device that im~o~es the security and placement of the surgical device in a mammalian body. Also described is an implantable surgical device which has been coated with a biocompatible adhesive or sealant in an amount sufficient to facilitate the placement of the surgical device in the desired location in a patie~t.
Suitable surgical devices which may benefit from having ~X-10~4 an adhesive or sealant coating include but are not limited to surgical screws, pins, plates, anchors, rods, clamps, clips, staples, rivets, hooks, buttons, snaps and the like.
These surgical devices may be made from a biocompatible material using conventional fabrication methods. The clips can be compoC~ of various biocompatible metals, e.g. titanium and tantalum, and polymeric materials.
Preferred bioabsorbable polymeric materials include homopolymers and copolymers of epsilon-caprolactone, glycolide, lactide, para-dioxanone, and trimethylene carbonate. Preferred non-absorbable polymers include nylons, polyesters and polypropylene. All these materials have been demonstrated to be biologically acceptable when used as ~u~les or other implantable medical devices.
The preferred means for fabricating surgical devices from polymeric materials is to inject a suitable polymer melt into an appropriately designed mold at process conditions conventionally employed for such polymer systems. After the polymer melt cools, the molded polymer chApe~ in the mold to meet the design criteria of the device can be readily released from the mold.
One class of suitable biocompatible adhesives or ~e~lAnts that can be used in the practice of the present invention include materials made from monomers of the formula:
(I) CHRI=CXlYl wherein X~ and Y~ are each strong electron withdrawing `- 2~68822 groups, and Rl is hydrogen or, provided that Xl and Y~ are both cyano groups, a C~-C4 alkyl group. Examples of monomers within the scope of formula (I) include ~-cyanoacrylates, vinylidene cyanides, Cl-C4 alkyl homologues of vinylidene cyanides, dialkyl methylene malonates, acylacrylonitriles, vinyl sulfinates, and vinyl sulfonates of the formula CH2=CX2Y2 wherein x2 is S02R2 or -S03R2 and y2 is -CN, COOR2, COCH3, -S02R2 or -S03R2 and R2 is hydrogen or an alkyl group.
Preferred monomers of formula (I) for use in this invention are alpha-cyanoacrylates. These monomers are known in the art and have the formula /CN
( II ) CHR3=C~ -CoOR4 wherein R3 is hydrogen and R4 is a hydrocarbon or substituted hyd-ocarbon group; a group having the formula -R5-o-R6-o-R7, wherein R5 is a 1,2-alkylene group having 2-4 carbon atoms, R6 is an alkylene group having 2-4 carbon atoms, and R7 is an alkyl group having 1-6 carbon atoms; or a group having the formula:
(III) O
Background of the Invention In orthopedic surgery it is often necessary to reattach cartilage and ligaments to skeletal bones with surgical pins, screws or anchors. For example, metallic ~uL~Ie anchors are currently used to facilitate cartilage or ligament reattachment. In these procedures a hole is drilled into the skeletal bone. A -uLu~e anchor, attached to a ~Lule, is then inserted into the hole in a manner that allows the anchor to engage the sides of the hole and be held in place. The suture is then used to secure the torn cartilage or ligament to the bone.
However, sometimes during or after the healing process these anchors fail to remain in place and must be removed to avoid harm to the patient.
Rec ntly, absorbable ~Lu~e AnchQrs have been proposed as a replacement for metallic ~uLu~e anchors. The perceived advantage of an absorbable anchor over the metallic AnchQr is that after the healing process for the cartilage or ligament is complete the anchor will be absorbed by the patient's body and disappear. However, most bioabsorbable materials are not strong enough to dig into bone tissue. Therefore, bioabsorbable bone ~T~-~014 `- 216~822 anchors tend to have less resistance to being pulled out of the location in which it is secured.
Thus, it would be a significant contribution to the art to provide a method to enhance the secure placement of implantable surgical devices in patients. Additionally, it would be advantageous if a method could be developed to enhance the resistance to removal of bioabsorbable surgical implantable devices.
Summary of the Invention We have discovered a process for enhancing the security of implantable surgical devices secured to bone tissue comprising implanting a surgical device with a biocompatible adhesive and/or sealant provided in an amount effective to increase the security of the implanted surgical device.
In another emhoAiment of the present invention we have also provided an implantable surgical device comprising an implantable surgical device coated with a biocompatible adhesive or sealant.
Detailed Description of the Invention The present invention provides a process for using a surgical device that im~o~es the security and placement of the surgical device in a mammalian body. Also described is an implantable surgical device which has been coated with a biocompatible adhesive or sealant in an amount sufficient to facilitate the placement of the surgical device in the desired location in a patie~t.
Suitable surgical devices which may benefit from having ~X-10~4 an adhesive or sealant coating include but are not limited to surgical screws, pins, plates, anchors, rods, clamps, clips, staples, rivets, hooks, buttons, snaps and the like.
These surgical devices may be made from a biocompatible material using conventional fabrication methods. The clips can be compoC~ of various biocompatible metals, e.g. titanium and tantalum, and polymeric materials.
Preferred bioabsorbable polymeric materials include homopolymers and copolymers of epsilon-caprolactone, glycolide, lactide, para-dioxanone, and trimethylene carbonate. Preferred non-absorbable polymers include nylons, polyesters and polypropylene. All these materials have been demonstrated to be biologically acceptable when used as ~u~les or other implantable medical devices.
The preferred means for fabricating surgical devices from polymeric materials is to inject a suitable polymer melt into an appropriately designed mold at process conditions conventionally employed for such polymer systems. After the polymer melt cools, the molded polymer chApe~ in the mold to meet the design criteria of the device can be readily released from the mold.
One class of suitable biocompatible adhesives or ~e~lAnts that can be used in the practice of the present invention include materials made from monomers of the formula:
(I) CHRI=CXlYl wherein X~ and Y~ are each strong electron withdrawing `- 2~68822 groups, and Rl is hydrogen or, provided that Xl and Y~ are both cyano groups, a C~-C4 alkyl group. Examples of monomers within the scope of formula (I) include ~-cyanoacrylates, vinylidene cyanides, Cl-C4 alkyl homologues of vinylidene cyanides, dialkyl methylene malonates, acylacrylonitriles, vinyl sulfinates, and vinyl sulfonates of the formula CH2=CX2Y2 wherein x2 is S02R2 or -S03R2 and y2 is -CN, COOR2, COCH3, -S02R2 or -S03R2 and R2 is hydrogen or an alkyl group.
Preferred monomers of formula (I) for use in this invention are alpha-cyanoacrylates. These monomers are known in the art and have the formula /CN
( II ) CHR3=C~ -CoOR4 wherein R3 is hydrogen and R4 is a hydrocarbon or substituted hyd-ocarbon group; a group having the formula -R5-o-R6-o-R7, wherein R5 is a 1,2-alkylene group having 2-4 carbon atoms, R6 is an alkylene group having 2-4 carbon atoms, and R7 is an alkyl group having 1-6 carbon atoms; or a group having the formula:
(III) O
wherein R8 is -CH2-,-CH-, or -C (CH3) 2- and R9 is an organic radical.
Examples of suitable hydrocarbon and substituted E~H-1014 hydrocarbon groups include straight chain or branched chain alkyl groups having 1-16 carbon atoms; straight chain or branched chain Cl-CI6 alkyl groups substituted with one or more biologically compatible substituents such as an acyloxy group, an alkoxy group, an aryloxy group, a haloalkyl group, a halogen atom, a dialkylamino group, an alkylarylamino group, or a cyano group;
straight chain or branched chain alkenyl groups having 2 to 16 carbon atoms; straight chain or branched chain alkynyl groups having 2 to 12 carbon atoms; cycloalkyl ~L OU~; arylalkyl ~L OU~S; alkylaryl groups and aryl Y' ~
In the cyanoacrylate monomer of formula (II), R4is preferably an alkyl group having 1-10 carbon atoms or a group having the formula -AORI, wherein A is a divalent straight or branched chain alkylene or oxyalkylene radical having 2-8 carbon atoms, and Rl is a straight or branched alkyl radical having 1-8 carbon atoms.
Examples of yLO~ Le~esented by the formula -AORI include 1-methoxy-2-~o~yl, 2-butoxy ethyl, isopropoxy-ethyl, and 2-ethoxy ethyl.
The most preferred alpha-cyanoacrylate monomers used in this invention are methyl alpha-cyanoacrylate, butyl alpha-cyanoacrylate, octyl alpha-cyanoacrylate, 1-methoxy-2-propyl cyanoacrylate, 2-butoxy ethyl cyanoacrylate, and isopLo~oxy-ethyl cyanoacrylate.
The alpha-cyanoacrylates of formula (II) wherein R4 is a hydrocarbon or substituted hyd~o~arbon group can be prepared according to methods known in the ar~.
Reference is made, for example, to U.S. Patents Nos.
2,721,858 and 3,254,111, each of which is hereby ~16882~
incorporated by reference herein. For example, the alpha-cyanoacrylates can be prepared by reacting an alkyl cyanoacetate with formaldehyde in a non-aqueous organic solvent and in the presence of a basic catalyst, followed by pyrolysis of the anhydrous intermediate polymer in the presence of a polymerization inhibitor.
The alpha-cyanoacrylate monomers prepared with low moisture content and essentially free of impurities are preferred for biomedical use.
The alpha-cyanoacrylates of formula (II) wherein R4 is a group having the formula R5-o-R6-o-R7 can be prepared according to the method disclosed in U.S. Patent No.
Examples of suitable hydrocarbon and substituted E~H-1014 hydrocarbon groups include straight chain or branched chain alkyl groups having 1-16 carbon atoms; straight chain or branched chain Cl-CI6 alkyl groups substituted with one or more biologically compatible substituents such as an acyloxy group, an alkoxy group, an aryloxy group, a haloalkyl group, a halogen atom, a dialkylamino group, an alkylarylamino group, or a cyano group;
straight chain or branched chain alkenyl groups having 2 to 16 carbon atoms; straight chain or branched chain alkynyl groups having 2 to 12 carbon atoms; cycloalkyl ~L OU~; arylalkyl ~L OU~S; alkylaryl groups and aryl Y' ~
In the cyanoacrylate monomer of formula (II), R4is preferably an alkyl group having 1-10 carbon atoms or a group having the formula -AORI, wherein A is a divalent straight or branched chain alkylene or oxyalkylene radical having 2-8 carbon atoms, and Rl is a straight or branched alkyl radical having 1-8 carbon atoms.
Examples of yLO~ Le~esented by the formula -AORI include 1-methoxy-2-~o~yl, 2-butoxy ethyl, isopropoxy-ethyl, and 2-ethoxy ethyl.
The most preferred alpha-cyanoacrylate monomers used in this invention are methyl alpha-cyanoacrylate, butyl alpha-cyanoacrylate, octyl alpha-cyanoacrylate, 1-methoxy-2-propyl cyanoacrylate, 2-butoxy ethyl cyanoacrylate, and isopLo~oxy-ethyl cyanoacrylate.
The alpha-cyanoacrylates of formula (II) wherein R4 is a hydrocarbon or substituted hyd~o~arbon group can be prepared according to methods known in the ar~.
Reference is made, for example, to U.S. Patents Nos.
2,721,858 and 3,254,111, each of which is hereby ~16882~
incorporated by reference herein. For example, the alpha-cyanoacrylates can be prepared by reacting an alkyl cyanoacetate with formaldehyde in a non-aqueous organic solvent and in the presence of a basic catalyst, followed by pyrolysis of the anhydrous intermediate polymer in the presence of a polymerization inhibitor.
The alpha-cyanoacrylate monomers prepared with low moisture content and essentially free of impurities are preferred for biomedical use.
The alpha-cyanoacrylates of formula (II) wherein R4 is a group having the formula R5-o-R6-o-R7 can be prepared according to the method disclosed in U.S. Patent No.
4,364,876 (Kimura et al.), which is hereby incorporated lS by reference herein. In the Kimura et al. method, the alpha-cyanoacrylates are prepared by producing a cyanoacetate by esterifying cyanoacetic acid with an alcohol or by transesterifying an alkyl cyanoacetate and an alcohol; condensing the cyanoacetate and formaldehyde or para-formaldehyde in the presence of a catalyst at a molar ratio of O.S-l.S:1, preferably 0.8-1.2:1, to obtain a con~nC~te; depolymerizing the condensation reaction mixture either directly or after removal of the con~n~tion catalyst to yield crude cyanoacrylate; and distilling the crude cyanoacrylate to form a high purity cyanoacrylate.
The alpha-cyanoacrylates of formula (II) wherein R4 is a group having the formula -R8-c,-o-R9 ho can be prepared according to the procedure described in U.S. Patent No. 3,995,641 (Kronenthal et al.), which is hereby incorporated by reference herein. In the Kronenthal et al. method, such alpha-cyanoacrylate monomers are prepared by reacting an alkyl ester of an alpha-cyanoacrylic acid with a cyclic 1,3-diene to form a Diels-Alder adduct which is then subjected to alkaline hydrolysis followed by acidification to form the corresponding alpha-cyanoacrylic acid adduct. The alpha-cyanoacrylic acid adduct is preferably esterified by an alkyl bromoacetate to yield the corresponding carbalkoxymethyl alpha-cyanoacrylate adduct.
Alternatively, the alpha-cyanoacrylic acid adduct may be converted to the alpha-cyanoacrylyl halide adduct by reaction with thionyl chloride. The alpha-cyanoacrylyl halide adduct is then reacted with an alkyl hydroxyacetate or a methyl substituted alkyl hyd~oxy~cetate to yield the coLLe_ronding carhAlkQxymethyl alpha-cyanoacrylate adduct or carbalkoxy alkyl alpha-cyanoacrylate adduct, ~rectively. The cyclic 1,3-diene blocking group is finally removed and the carbalkoxy methyl alpha-cyanoacrylate adduct or the carbalkoxy alkyl alpha-cyanoacrylate adduct is converted into the ~ L e_~onding carbalkoxy alkyl alpha-cyanoacrylate by heating the adduct in the presence of a slight deficit of maleic anhydride.
Another type of biocompatible adhesives or sealant that may be used in the practice of the present inYention are copolymers of formula (I) or one monomer of formula (I) and a monomer of the formula:
(IV) CHZ=CXIY
ET~-1014 wherein Xl and yl are as described for formula (I) and Z
is -CH=CH2. Examples of monomers of formula (IV) include cyanopentadienoates and alpha-cyanoacrylates of the formula:
CN
(V) CHZ=C~
CoOR4 wherein Z is -CH=CH2 and R4 is as defined above. The monomers of formula (IV) wherein R4 is an alkyl group of 1-10 carbon atoms, i.e., the 2-cyanopenta-2,4-dienoic acid esters, can be prepared by reacting an appropriate 2-cyanoacetate with acrolein in the presence of a catalyst such as zinc chloride. This method of preparing 2-cyanopenta-2,4,4-dienoic acid esters is disclosed, for example, in U.S. Patent No. 3,554,990, which is hereby incorporated by reference herein.
Optionally, a biocompatibilizing agent may be added to the cyanoacrylate adhesive such as are disclosed in U.S.
Patent 5,328,687, hereby incorporated by reference.
Suitable bioabsorbable sealants include semi-crystalline aliphatic ester homopolymers, and copolymers made from polymers of the formula:
(VI) t-O-RI1-C(O)-]y~
wherein Rll is selected from the group consisting of -CRI2H - , - ( CH2) 3 - 0 - , -CH2-CH2-O-CH2-, CRI2H-CH2, -(CH2)4-, -(CH2)z-O-C(O)- and -(CH2)z-C(O)-CH2-; Rl2 is hyd~o~en or '- 21~882~
methyl; z is an integer in the range of from 1 to 7; and y is an integer in the range of from about 10 to about 20,000.
Many nontoxic bioabsorbable aliphatic ester polymers that are semi-crystalline solids at room temperature, may be used in the present invention. The polymers of this invention are generally characterized as being solids at body temperature (37C) and preferably will be melt at temperatures of less than 60C. Suitable bioabsorbable polymers include solid poly(~-caprolactone), poly(p-dioxanone), or poly(trimethylene carbonate) homopolymers and copolymers of ~-caprolactone and trimethylene carbonate. Copolymers of ~-caprolactone should be composed of from about 100 molepercent to about 70 mole percent and preferably from 95 mole percent to 85 mole percent of ~-caprolactone repeating units with the remainder of the polymer being a plurality of second lactone repeating units. The second lactone repeating units will be selected from the group consisting of glycolide repeating units, lactide repeating units, 1,4-dioxanone repeating units, 1,4-dioxepAn-2-one repeating units, 1,5-dioxepan-2-one repeating units, trimethylene carbonate repeating units, and combinations thereof. Preferred are copolymers of ~-caprolactone that are semicrystalline solids at body temperature. The solid polymers of trimethylene carbonate should be com~ of from in the range of from about 1 to about 20 mole percent or from about 100 to about 80 mole percent of trimethylene carbonate with the remainder of the copolymer being composed of a plurality of lactone repeating units selected from the group consisting of glycolide repeating units, lactide repeating units, p-dioxanone repeating units, ~-`- 2168822 caprolactone repeating units, and combinations thereof.
It is preferred for the trimethylene carbonate copolymers to have crystalline regions formed by the second lactone repeating units wherein the crystalline regions provide at least 5 percent crystallinity to the final copolymer. The solid polymers may be linear, branched, or star branched; block copolymers or terpolymers; segmented block copolymers or terpolymers.
These polymers will also be purified to substantially remove unreacted monomers which may cause an inflammatory reaction in tissue.
The most preferred polymers for use as the adhesive/sealant are semicrystalline polymers selected from the group consisting of poly(~-caprolactone), poly(~-caprolactone-co-trimethylene carbonate), poly(~-caprolactone-co-lactide), poly(~-caprolactone-co-p-dioY~none), and poly(~-caprolactone co-glycolide). The mole percent of ~-caprolactone repeating units in these polymers should be in the range of from 100 to about 80 mole percent and preferably in the range of from 95 to 85 mole percent. Most preferably these polymers will be statistically random copolymers.
The polymers used as the adhesive/sealant should have an inherent viscosity as determined in a 0.1 g/dL solution of hexafluoroisopropanol (HFIP) at 25C ranging from about 0.1 dL/g to about 2.0 dL/g, preferably from about 0.15 dL/g to about 1.5 dL/g, and most preferably from 0.2 dL/g to 1.0 dL/g. A polymer with an inherent viscosity below 0.1 dL/g may fail to crystal~ize at room temperature, and a polymer with an inherent viscosity above 2.0 dL/g may make the polymer have too high of a melting point.
The aliphatic poly(ester)s are generally prepared by a ring opening polymerization of the desired proportions of one or more lactone monomers in the presence of an organometallic catalyst and an initiator at elevated temperatures. The organometallic catalyst is preferably a tin-based catalyst, e.g. stannous octoate, and is present in the monomer mixture at a molar ratio of monomer to catalyst ranging from about 15,000/1 to about 80,000/1. The initiator is typically an alkanol (such as l-dodecanol), a polyol (such as 1,2-propanediol, 1,3-propanediol, diethylene glycol, or glycerol, poly(ethylene glycol)s, poly(propylene glycol)s and poly(ethylene-co-propylene glycol)s), a hydroxyacid, or an amine, and is present in the monomer mixture at a molar ratio of monomer to initiator ranging from about 100/1 to about 5000/1. The polymerization is typically carried out at a temperature range from about 80 to about 220C, preferably 160 to 190C, until the desired molecular weight and viscosity are achieved.
The aliphatic polyesters described above will be solids at room temperature but may be heated to provide a ~L~y like or liquid material that may be applied as a sealant to C~lrrort surgical devices or to secure a surgical device. In one embodiment of the present invention, the aliphatic polyester would be heated to its melting point and applied to the desired location before it resolidifed. In this emhoAiment, if a bone pin were inserted in a hole drilled in bone tissue, melted polyester would be ~OULed into the hole before or after the pin was insert to help secure the bone pin in t~e bone tissue. Alternatively, the aliphatic polyester ` 21G882~
could be heated until it softens and then used as a putty and placed at the desired location and act as a filler.
Other suitable bioabsorbable sealants include calcium containing compounds with the general formula:
M2+1~nNl+2n(W043-)6mUX~
where n is an integer from 1 to 10, and m is 2 when x is 1, or m is 1 when x is 2, M and N are alkali or alkaline earth metals, preferably calcium, magnesium, sodium, zinc, and potassium. W04 iS an acid radical, where W is preferably phosphorus, vanadium, sulfur or silicon, or is substituted in whole or part with carbonate (C032-). U is an anion, preferably halide, hydroxide, or carbonate.
Most preferred are calcium cont~ining sealants selected from the group consisting of mono-, di-, octa-, ~-tri-, ~-tri-, or tetra-calcium phosphate, hydroxyapatite, fluorapatite, calcium sulfate, calcium fluoride and mix~e-~ thereof.
The calcium containing sealants can also contain a bioactive glass comprising metal oxides such as calcium oxide, silicon dioxide, sodium oxide, phosphorus pentoxide, and mixL~-eæ thereof, and the like. The calcium containing sealants will preferably have a particle size of about 10 microns to about 1000 microns, and more preferably about 100 microns to about 500 microns.
The calcium cont~;ning sealants will generally be applied in an aqueous slurry. The amount of calcium containing material in the slurry will generally be in the range from about 10 weight percent to about go weight percent. The slurry will preferably be retained in place at the desired location until it solidifies or develops a putty like consistency The adhesive and/or sealant may be applied to at least one surface of the medical device that is to be contacted with the bone tissue or applied to the site where the surgical device is to be secured. For example, when a bone pin or anchor is placed in a hole drilled in bone tissue the pin or anchor surfaces that will contact the bone tissue will be coated with adhesive and placed in intimate contact with the bone tissue. The adhesive will then adhere to the device and the bone and enhance the security of the pin or anchor in the hole.
Alternatively, the adhesive may be applied to the site where the surgical device is to be secured and the surgical device applied thereafter in an appropriate time so that the adhesive or sealant can set. If a seA 1 Ant is used the sealant may serve as a filling and support agent for the medical device. For example, when using a bone plate with multiple op~nings for fasteners (such as screws), the sealant would be applied to the surface to contact the bone to provide a putty like base on which to mount the bone plate on to simplify installation of the bone plate.
Those skilled in the art will readily be able to determine the a~o~iate amount of adhesive and/or sealant to apply in a given surgical application.
Similarly, the amount of an adhesive and/or sealant to be applied to a surgical device before implantation will ~TX-1014 ~1~88~2 be a discretionary matter depending on the operation and the specific circumstances of the operation.
The adhesives and/or sealants of the present invention will generally be applied in a liquid form. The adhesive and/or sealant will generally be applied through a small diameter delivery device such as a syringe, with or without mech~nical assistance, a caulking gun, a soft-sided tube, and the like.
The following nonlimiting examples are provided to illustrate the practice of the present invention.
Example 1 Synthesis of the Anthracene Adduct of Dimethyl Methylidene Malonate. 178.0 grams (1.00 mol) of powdered anthracene, 60.0 grams (2.00 mol) of powdered paraformaldehyde, 132.0 grams (1.00 mol) of dimethyl malonate, 10.0 grams (50 mmol) of cupric acetate monohydrate, 225 mL of glacial acetic acid, and 450 mL
of xylene were added to a two liter, three necked, round bottom flask. In the exhaust hood, the flask was immersed into an oil bath and secured with a clamp. A
mec~Anical stirrer, a stainless steel thermocouple cG....e_Led to a thermowatch which controlled the immersion heater, and a water cooled distillation apparatus were then installed. The still was connected to a dry nitrogen gas line via a Firestone valve. The contents of the reaction flask were heated to 100C for 18 hours; then, the pot temperature was raised until the azeoL~ic mixture of acetic acid, water, and xylene started to distill out. The oil bath temperature ranged ~H-1014 21688~2 from 125C to 145C during the distillation. The still head temperature varied from 95C to 110C. When most of the solvents were removed, the resulting suspension was allowed to cool down to room temperature. The residue was dissolved in chloroform, and in portions, transferred into a separatory funnel, washed with an equal volume of saturated ammonium chloride solution, washed with saturated sodium chloride solution, dried over anhydrous magnesium sulfate, and suction filtered.
The filtrate was transferred into a round bottom flask and the chloroform removed by evaporation. The crude product [305 grams; 9S % yield, but impure] was then recrystallized from xylene [1 gram/2 mL] using activated charcoal at -50C. 228 grams of recrystallized adduct were collected [75 % recovery; 71 % yield overall, although the material is still contaminated with small amounts of anthracene]. The material was recrystallized again to produce about 188 grams of doubly recrystallized adduct [82 % recovery; 58 % yield overall; still contained some anthracene]. The material was recrystallized again yielding 158 grams of triply recrystallized material [84 % recovery; 49 %
overall yield]. The crystals were isolated by suction filtration, washed with methanol, and vacuumed dried at 50C after each recrystallization.
Example 2 Synthesis of Dimethyl Methylidene Nalonate (DM~MJ. 500 grams of mineral oil, 120.0 grams (373 mmol) of the anthracene adduct of dimethyl methylidene malonate, 64.9 grams (375 mmol) of N-phenylmaleimide, and a. 50 grams (3.5 mmol) of phosphorous pentoxide were added to a silanized, flame dried, one liter round bottom flask containing a magnetic stirring bar. This mixture was degassed on a vacuum manifold overnight. Then, a silanized distillation head and fraction cutter were installed, and the flask immersed in an oil bath already set at 225C under a nitrogen atmosphere. After fifteen minutes, a yellow solution was obtained. One hour later, the oil bath was removed and the contents of the -flask were allowed to cool down to 50C. High vacuum was then applied to the reaction system. A pressure of around 450 microns was typical in the beginning of the distillation, and the pressure fell to around 300 microns by the end of the distillation. Once the system stabilized at low pressure, the dimethyl methylidene malonate distilled over between 50C and 55C [the oil bath temperature ranged from 50C to around 70C]. 31.0 grams of dimethyl methylidene malonate were collected in the middle fraction [58 % yield; > 99 mole % pure by NNR
spectroscopy].
Example 3 Synthesis of Poly[~-caprolactone] (PCLJ. In the glove box, 120 ~L (40 ~mol) of a 0.33 M stannous octoate solution in toluene, 2.3 mL (24 mmol) of distilled diethylene glycol, and 205.3 grams (1.8 mol) of distilled ~-caprolactone were transferred into a silanized, flame dried, 500 mL, round bottom flask equipped with a stainless steel me~h~nical stirrer and a nitrogen gas blanket. The reaction flask was immersed in an oil bath already set at 75C. After fifteen minutes, a clear solution was ob~ine~ and then the oil bath temperature was raised to 190C for 19 hours. The stirrer b~ade was removed, and the polymer melt was allowed to cool down to room temperature in an inert atmosphere. After about two hours, the polymer started to crystallize and became opaque. The polymer was isolated by wrapping the flask in aluminum foil, freezing the flask in liquid nitrogen, and removing the broken glass. Then, the frozen polymer was ground on a Wiley mill and sieved through a screen. 35.2 grams of a fine powder were saved; 161.8 grams of the coarse grounds were vacuum dried at 40C for 12 hours.-160.9 grams of devolatized PCL were collected. The PCL
was vacuum dried again under the same conditions without any weight loss. The inherent viscosity was measured in chloroform at 25C and found to be 0.3 dL/g tc = 0.10 g/dL]. The number average molecular weight was 9,000 g/mol and the weight average molecular weight was 16,000 g/mol as determined by gel permeation chromatography in HFIP using PMMA stAn~rds. The monomer conversion was 97.6 mole percent as determined by 300 MHz IH NMR spectrum in HFAD/C6D6; 2.4 mole percent unreacted monomer was also detected. The polymer melted between 60C and 65C using a Fisher-Johns apparatus.
In the glove box, 25 grams of PCL and 0.25 grams of sucrose ta nucleating agent] were added to a silanized, flame dried, 100 mL, round bottom flask equipped with a stainless steel mec-h~nical stirrer and a nitrogen gas blanket. The reaction flask was immersed in an oil bath set at 125C. After the PCL had melted, the mixture was blended for one hour and then allowed to cool down to room temperature under an inert atmosphere. The polymer was isolated by wrapping the flask in aluminum foil, freezing the flask in liquid nitrogen, and removing the broken glass. The frozen polymer was crushed and vacuum dried at room temperature overnight and then stored under nitrogen gas until used in the bone pin study described below.
~1~8822 Example 4 Bone Pin Pullout Force Measurements. Materials and Methods: Rabbit femurs were cleaned and frozen. They were defrosted before testing and allowed to warm up to 37 C.
A hole was drilled in the femoral condyle with a 2.7 mm drill bit. Bone pins made of poly~glycolic acid] having a nominal diameter of 2.8 mm were roughened with sand paper to im~ove adhesion and were inserted into the femoral condyle with no adhesive, with Vetbond (n-butyl cyanoacrylate), dimethyl methylene malonate (DMMM) from Example 2 and with low molecular weight poly[~-caprolactone] (PCL) from Example 3. The cure time was one minute for the Vetbond and DMMM and thirty minutes for the low molecular weight PCL. Mech~nical testing was conducted on an Instron model 1122 tensile tester at a cross head speed of 0.5 inches per minute. The femur was held in the bottom fixture, and the bone pin was pulled out by the upper fixture. The force was measured and the maximum force recorded.
Results: The pullout force data are summarized in Table 1. These data clearly show that the average pullout force increased significantly when an adhesive was used; the increase in pullout strength varied from 4 to 11 times that of the force IIQe~e~ to remove the bone pin without any glue being applied.
~1~88~
Table 1. Pullout Strengths Pullout Strengths (kg) Test Bone Pin Vetbond DMMM PCL
Only 1 0.661 6.95 3.43 2.3 2 0.765 8.35 7.41 2.94 3 -- 9.82 6.79 2.19 4 -- 5.66 2.27 3.41 Average 0.71 7.70 4.98 2.71
The alpha-cyanoacrylates of formula (II) wherein R4 is a group having the formula -R8-c,-o-R9 ho can be prepared according to the procedure described in U.S. Patent No. 3,995,641 (Kronenthal et al.), which is hereby incorporated by reference herein. In the Kronenthal et al. method, such alpha-cyanoacrylate monomers are prepared by reacting an alkyl ester of an alpha-cyanoacrylic acid with a cyclic 1,3-diene to form a Diels-Alder adduct which is then subjected to alkaline hydrolysis followed by acidification to form the corresponding alpha-cyanoacrylic acid adduct. The alpha-cyanoacrylic acid adduct is preferably esterified by an alkyl bromoacetate to yield the corresponding carbalkoxymethyl alpha-cyanoacrylate adduct.
Alternatively, the alpha-cyanoacrylic acid adduct may be converted to the alpha-cyanoacrylyl halide adduct by reaction with thionyl chloride. The alpha-cyanoacrylyl halide adduct is then reacted with an alkyl hydroxyacetate or a methyl substituted alkyl hyd~oxy~cetate to yield the coLLe_ronding carhAlkQxymethyl alpha-cyanoacrylate adduct or carbalkoxy alkyl alpha-cyanoacrylate adduct, ~rectively. The cyclic 1,3-diene blocking group is finally removed and the carbalkoxy methyl alpha-cyanoacrylate adduct or the carbalkoxy alkyl alpha-cyanoacrylate adduct is converted into the ~ L e_~onding carbalkoxy alkyl alpha-cyanoacrylate by heating the adduct in the presence of a slight deficit of maleic anhydride.
Another type of biocompatible adhesives or sealant that may be used in the practice of the present inYention are copolymers of formula (I) or one monomer of formula (I) and a monomer of the formula:
(IV) CHZ=CXIY
ET~-1014 wherein Xl and yl are as described for formula (I) and Z
is -CH=CH2. Examples of monomers of formula (IV) include cyanopentadienoates and alpha-cyanoacrylates of the formula:
CN
(V) CHZ=C~
CoOR4 wherein Z is -CH=CH2 and R4 is as defined above. The monomers of formula (IV) wherein R4 is an alkyl group of 1-10 carbon atoms, i.e., the 2-cyanopenta-2,4-dienoic acid esters, can be prepared by reacting an appropriate 2-cyanoacetate with acrolein in the presence of a catalyst such as zinc chloride. This method of preparing 2-cyanopenta-2,4,4-dienoic acid esters is disclosed, for example, in U.S. Patent No. 3,554,990, which is hereby incorporated by reference herein.
Optionally, a biocompatibilizing agent may be added to the cyanoacrylate adhesive such as are disclosed in U.S.
Patent 5,328,687, hereby incorporated by reference.
Suitable bioabsorbable sealants include semi-crystalline aliphatic ester homopolymers, and copolymers made from polymers of the formula:
(VI) t-O-RI1-C(O)-]y~
wherein Rll is selected from the group consisting of -CRI2H - , - ( CH2) 3 - 0 - , -CH2-CH2-O-CH2-, CRI2H-CH2, -(CH2)4-, -(CH2)z-O-C(O)- and -(CH2)z-C(O)-CH2-; Rl2 is hyd~o~en or '- 21~882~
methyl; z is an integer in the range of from 1 to 7; and y is an integer in the range of from about 10 to about 20,000.
Many nontoxic bioabsorbable aliphatic ester polymers that are semi-crystalline solids at room temperature, may be used in the present invention. The polymers of this invention are generally characterized as being solids at body temperature (37C) and preferably will be melt at temperatures of less than 60C. Suitable bioabsorbable polymers include solid poly(~-caprolactone), poly(p-dioxanone), or poly(trimethylene carbonate) homopolymers and copolymers of ~-caprolactone and trimethylene carbonate. Copolymers of ~-caprolactone should be composed of from about 100 molepercent to about 70 mole percent and preferably from 95 mole percent to 85 mole percent of ~-caprolactone repeating units with the remainder of the polymer being a plurality of second lactone repeating units. The second lactone repeating units will be selected from the group consisting of glycolide repeating units, lactide repeating units, 1,4-dioxanone repeating units, 1,4-dioxepAn-2-one repeating units, 1,5-dioxepan-2-one repeating units, trimethylene carbonate repeating units, and combinations thereof. Preferred are copolymers of ~-caprolactone that are semicrystalline solids at body temperature. The solid polymers of trimethylene carbonate should be com~ of from in the range of from about 1 to about 20 mole percent or from about 100 to about 80 mole percent of trimethylene carbonate with the remainder of the copolymer being composed of a plurality of lactone repeating units selected from the group consisting of glycolide repeating units, lactide repeating units, p-dioxanone repeating units, ~-`- 2168822 caprolactone repeating units, and combinations thereof.
It is preferred for the trimethylene carbonate copolymers to have crystalline regions formed by the second lactone repeating units wherein the crystalline regions provide at least 5 percent crystallinity to the final copolymer. The solid polymers may be linear, branched, or star branched; block copolymers or terpolymers; segmented block copolymers or terpolymers.
These polymers will also be purified to substantially remove unreacted monomers which may cause an inflammatory reaction in tissue.
The most preferred polymers for use as the adhesive/sealant are semicrystalline polymers selected from the group consisting of poly(~-caprolactone), poly(~-caprolactone-co-trimethylene carbonate), poly(~-caprolactone-co-lactide), poly(~-caprolactone-co-p-dioY~none), and poly(~-caprolactone co-glycolide). The mole percent of ~-caprolactone repeating units in these polymers should be in the range of from 100 to about 80 mole percent and preferably in the range of from 95 to 85 mole percent. Most preferably these polymers will be statistically random copolymers.
The polymers used as the adhesive/sealant should have an inherent viscosity as determined in a 0.1 g/dL solution of hexafluoroisopropanol (HFIP) at 25C ranging from about 0.1 dL/g to about 2.0 dL/g, preferably from about 0.15 dL/g to about 1.5 dL/g, and most preferably from 0.2 dL/g to 1.0 dL/g. A polymer with an inherent viscosity below 0.1 dL/g may fail to crystal~ize at room temperature, and a polymer with an inherent viscosity above 2.0 dL/g may make the polymer have too high of a melting point.
The aliphatic poly(ester)s are generally prepared by a ring opening polymerization of the desired proportions of one or more lactone monomers in the presence of an organometallic catalyst and an initiator at elevated temperatures. The organometallic catalyst is preferably a tin-based catalyst, e.g. stannous octoate, and is present in the monomer mixture at a molar ratio of monomer to catalyst ranging from about 15,000/1 to about 80,000/1. The initiator is typically an alkanol (such as l-dodecanol), a polyol (such as 1,2-propanediol, 1,3-propanediol, diethylene glycol, or glycerol, poly(ethylene glycol)s, poly(propylene glycol)s and poly(ethylene-co-propylene glycol)s), a hydroxyacid, or an amine, and is present in the monomer mixture at a molar ratio of monomer to initiator ranging from about 100/1 to about 5000/1. The polymerization is typically carried out at a temperature range from about 80 to about 220C, preferably 160 to 190C, until the desired molecular weight and viscosity are achieved.
The aliphatic polyesters described above will be solids at room temperature but may be heated to provide a ~L~y like or liquid material that may be applied as a sealant to C~lrrort surgical devices or to secure a surgical device. In one embodiment of the present invention, the aliphatic polyester would be heated to its melting point and applied to the desired location before it resolidifed. In this emhoAiment, if a bone pin were inserted in a hole drilled in bone tissue, melted polyester would be ~OULed into the hole before or after the pin was insert to help secure the bone pin in t~e bone tissue. Alternatively, the aliphatic polyester ` 21G882~
could be heated until it softens and then used as a putty and placed at the desired location and act as a filler.
Other suitable bioabsorbable sealants include calcium containing compounds with the general formula:
M2+1~nNl+2n(W043-)6mUX~
where n is an integer from 1 to 10, and m is 2 when x is 1, or m is 1 when x is 2, M and N are alkali or alkaline earth metals, preferably calcium, magnesium, sodium, zinc, and potassium. W04 iS an acid radical, where W is preferably phosphorus, vanadium, sulfur or silicon, or is substituted in whole or part with carbonate (C032-). U is an anion, preferably halide, hydroxide, or carbonate.
Most preferred are calcium cont~ining sealants selected from the group consisting of mono-, di-, octa-, ~-tri-, ~-tri-, or tetra-calcium phosphate, hydroxyapatite, fluorapatite, calcium sulfate, calcium fluoride and mix~e-~ thereof.
The calcium containing sealants can also contain a bioactive glass comprising metal oxides such as calcium oxide, silicon dioxide, sodium oxide, phosphorus pentoxide, and mixL~-eæ thereof, and the like. The calcium containing sealants will preferably have a particle size of about 10 microns to about 1000 microns, and more preferably about 100 microns to about 500 microns.
The calcium cont~;ning sealants will generally be applied in an aqueous slurry. The amount of calcium containing material in the slurry will generally be in the range from about 10 weight percent to about go weight percent. The slurry will preferably be retained in place at the desired location until it solidifies or develops a putty like consistency The adhesive and/or sealant may be applied to at least one surface of the medical device that is to be contacted with the bone tissue or applied to the site where the surgical device is to be secured. For example, when a bone pin or anchor is placed in a hole drilled in bone tissue the pin or anchor surfaces that will contact the bone tissue will be coated with adhesive and placed in intimate contact with the bone tissue. The adhesive will then adhere to the device and the bone and enhance the security of the pin or anchor in the hole.
Alternatively, the adhesive may be applied to the site where the surgical device is to be secured and the surgical device applied thereafter in an appropriate time so that the adhesive or sealant can set. If a seA 1 Ant is used the sealant may serve as a filling and support agent for the medical device. For example, when using a bone plate with multiple op~nings for fasteners (such as screws), the sealant would be applied to the surface to contact the bone to provide a putty like base on which to mount the bone plate on to simplify installation of the bone plate.
Those skilled in the art will readily be able to determine the a~o~iate amount of adhesive and/or sealant to apply in a given surgical application.
Similarly, the amount of an adhesive and/or sealant to be applied to a surgical device before implantation will ~TX-1014 ~1~88~2 be a discretionary matter depending on the operation and the specific circumstances of the operation.
The adhesives and/or sealants of the present invention will generally be applied in a liquid form. The adhesive and/or sealant will generally be applied through a small diameter delivery device such as a syringe, with or without mech~nical assistance, a caulking gun, a soft-sided tube, and the like.
The following nonlimiting examples are provided to illustrate the practice of the present invention.
Example 1 Synthesis of the Anthracene Adduct of Dimethyl Methylidene Malonate. 178.0 grams (1.00 mol) of powdered anthracene, 60.0 grams (2.00 mol) of powdered paraformaldehyde, 132.0 grams (1.00 mol) of dimethyl malonate, 10.0 grams (50 mmol) of cupric acetate monohydrate, 225 mL of glacial acetic acid, and 450 mL
of xylene were added to a two liter, three necked, round bottom flask. In the exhaust hood, the flask was immersed into an oil bath and secured with a clamp. A
mec~Anical stirrer, a stainless steel thermocouple cG....e_Led to a thermowatch which controlled the immersion heater, and a water cooled distillation apparatus were then installed. The still was connected to a dry nitrogen gas line via a Firestone valve. The contents of the reaction flask were heated to 100C for 18 hours; then, the pot temperature was raised until the azeoL~ic mixture of acetic acid, water, and xylene started to distill out. The oil bath temperature ranged ~H-1014 21688~2 from 125C to 145C during the distillation. The still head temperature varied from 95C to 110C. When most of the solvents were removed, the resulting suspension was allowed to cool down to room temperature. The residue was dissolved in chloroform, and in portions, transferred into a separatory funnel, washed with an equal volume of saturated ammonium chloride solution, washed with saturated sodium chloride solution, dried over anhydrous magnesium sulfate, and suction filtered.
The filtrate was transferred into a round bottom flask and the chloroform removed by evaporation. The crude product [305 grams; 9S % yield, but impure] was then recrystallized from xylene [1 gram/2 mL] using activated charcoal at -50C. 228 grams of recrystallized adduct were collected [75 % recovery; 71 % yield overall, although the material is still contaminated with small amounts of anthracene]. The material was recrystallized again to produce about 188 grams of doubly recrystallized adduct [82 % recovery; 58 % yield overall; still contained some anthracene]. The material was recrystallized again yielding 158 grams of triply recrystallized material [84 % recovery; 49 %
overall yield]. The crystals were isolated by suction filtration, washed with methanol, and vacuumed dried at 50C after each recrystallization.
Example 2 Synthesis of Dimethyl Methylidene Nalonate (DM~MJ. 500 grams of mineral oil, 120.0 grams (373 mmol) of the anthracene adduct of dimethyl methylidene malonate, 64.9 grams (375 mmol) of N-phenylmaleimide, and a. 50 grams (3.5 mmol) of phosphorous pentoxide were added to a silanized, flame dried, one liter round bottom flask containing a magnetic stirring bar. This mixture was degassed on a vacuum manifold overnight. Then, a silanized distillation head and fraction cutter were installed, and the flask immersed in an oil bath already set at 225C under a nitrogen atmosphere. After fifteen minutes, a yellow solution was obtained. One hour later, the oil bath was removed and the contents of the -flask were allowed to cool down to 50C. High vacuum was then applied to the reaction system. A pressure of around 450 microns was typical in the beginning of the distillation, and the pressure fell to around 300 microns by the end of the distillation. Once the system stabilized at low pressure, the dimethyl methylidene malonate distilled over between 50C and 55C [the oil bath temperature ranged from 50C to around 70C]. 31.0 grams of dimethyl methylidene malonate were collected in the middle fraction [58 % yield; > 99 mole % pure by NNR
spectroscopy].
Example 3 Synthesis of Poly[~-caprolactone] (PCLJ. In the glove box, 120 ~L (40 ~mol) of a 0.33 M stannous octoate solution in toluene, 2.3 mL (24 mmol) of distilled diethylene glycol, and 205.3 grams (1.8 mol) of distilled ~-caprolactone were transferred into a silanized, flame dried, 500 mL, round bottom flask equipped with a stainless steel me~h~nical stirrer and a nitrogen gas blanket. The reaction flask was immersed in an oil bath already set at 75C. After fifteen minutes, a clear solution was ob~ine~ and then the oil bath temperature was raised to 190C for 19 hours. The stirrer b~ade was removed, and the polymer melt was allowed to cool down to room temperature in an inert atmosphere. After about two hours, the polymer started to crystallize and became opaque. The polymer was isolated by wrapping the flask in aluminum foil, freezing the flask in liquid nitrogen, and removing the broken glass. Then, the frozen polymer was ground on a Wiley mill and sieved through a screen. 35.2 grams of a fine powder were saved; 161.8 grams of the coarse grounds were vacuum dried at 40C for 12 hours.-160.9 grams of devolatized PCL were collected. The PCL
was vacuum dried again under the same conditions without any weight loss. The inherent viscosity was measured in chloroform at 25C and found to be 0.3 dL/g tc = 0.10 g/dL]. The number average molecular weight was 9,000 g/mol and the weight average molecular weight was 16,000 g/mol as determined by gel permeation chromatography in HFIP using PMMA stAn~rds. The monomer conversion was 97.6 mole percent as determined by 300 MHz IH NMR spectrum in HFAD/C6D6; 2.4 mole percent unreacted monomer was also detected. The polymer melted between 60C and 65C using a Fisher-Johns apparatus.
In the glove box, 25 grams of PCL and 0.25 grams of sucrose ta nucleating agent] were added to a silanized, flame dried, 100 mL, round bottom flask equipped with a stainless steel mec-h~nical stirrer and a nitrogen gas blanket. The reaction flask was immersed in an oil bath set at 125C. After the PCL had melted, the mixture was blended for one hour and then allowed to cool down to room temperature under an inert atmosphere. The polymer was isolated by wrapping the flask in aluminum foil, freezing the flask in liquid nitrogen, and removing the broken glass. The frozen polymer was crushed and vacuum dried at room temperature overnight and then stored under nitrogen gas until used in the bone pin study described below.
~1~8822 Example 4 Bone Pin Pullout Force Measurements. Materials and Methods: Rabbit femurs were cleaned and frozen. They were defrosted before testing and allowed to warm up to 37 C.
A hole was drilled in the femoral condyle with a 2.7 mm drill bit. Bone pins made of poly~glycolic acid] having a nominal diameter of 2.8 mm were roughened with sand paper to im~ove adhesion and were inserted into the femoral condyle with no adhesive, with Vetbond (n-butyl cyanoacrylate), dimethyl methylene malonate (DMMM) from Example 2 and with low molecular weight poly[~-caprolactone] (PCL) from Example 3. The cure time was one minute for the Vetbond and DMMM and thirty minutes for the low molecular weight PCL. Mech~nical testing was conducted on an Instron model 1122 tensile tester at a cross head speed of 0.5 inches per minute. The femur was held in the bottom fixture, and the bone pin was pulled out by the upper fixture. The force was measured and the maximum force recorded.
Results: The pullout force data are summarized in Table 1. These data clearly show that the average pullout force increased significantly when an adhesive was used; the increase in pullout strength varied from 4 to 11 times that of the force IIQe~e~ to remove the bone pin without any glue being applied.
~1~88~
Table 1. Pullout Strengths Pullout Strengths (kg) Test Bone Pin Vetbond DMMM PCL
Only 1 0.661 6.95 3.43 2.3 2 0.765 8.35 7.41 2.94 3 -- 9.82 6.79 2.19 4 -- 5.66 2.27 3.41 Average 0.71 7.70 4.98 2.71
Claims (18)
1. A process for enhancing the security of implantable surgical devices secured to bone tissue comprising securing a surgical device with a biocompatible adhesive and/or sealant selected from the group consisting of:
(a) a material made from monomers of the formula:
CHR1=CX1Y1 wherein X1 and Y1 are each strong electron withdrawing groups, and R1 is hydrogen or, provided that X1 and Y1 are both cyano groups, a C1-C4 alkyl group;
(b) a bioabsorbable semi-crystalline aliphatic poly(ester) of the formula:
[-O-R11-C(O)-]y, wherein R11 is selected from the group consisting of -CR12H-, -(CH2)3-O-, -CH2-CH2-O-CH2-, CR12H-CH2, -(CH2)4-, -(CH2)Z-O-C(O)- and -(CH2)z-C(O)-CH2-; R12 is hydrogen or methyl; z is an integer in the range of from 1 to 7 and y is an integer in the range of from about 10 to about 20,000; and (c) a slurry of water and a calcium containing compound with the general formula:
M2+10-nN1+2n(WO43-)6mUx-where n is an integer from 1 to 10, and m is 2 when x is 1, or m is 1 when x is 2, M and N are alkali or alkaline earth metals; WO4 is an acid radical and W is phosphorus, vanadium, sulfur, silicon, or is substituted in whole or part with carbonate (CO32-);
and U is a halide, hydroxide, or carbonate;
provided in an amount effective to increase the amount of force necessary to remove the implanted surgical device.
(a) a material made from monomers of the formula:
CHR1=CX1Y1 wherein X1 and Y1 are each strong electron withdrawing groups, and R1 is hydrogen or, provided that X1 and Y1 are both cyano groups, a C1-C4 alkyl group;
(b) a bioabsorbable semi-crystalline aliphatic poly(ester) of the formula:
[-O-R11-C(O)-]y, wherein R11 is selected from the group consisting of -CR12H-, -(CH2)3-O-, -CH2-CH2-O-CH2-, CR12H-CH2, -(CH2)4-, -(CH2)Z-O-C(O)- and -(CH2)z-C(O)-CH2-; R12 is hydrogen or methyl; z is an integer in the range of from 1 to 7 and y is an integer in the range of from about 10 to about 20,000; and (c) a slurry of water and a calcium containing compound with the general formula:
M2+10-nN1+2n(WO43-)6mUx-where n is an integer from 1 to 10, and m is 2 when x is 1, or m is 1 when x is 2, M and N are alkali or alkaline earth metals; WO4 is an acid radical and W is phosphorus, vanadium, sulfur, silicon, or is substituted in whole or part with carbonate (CO32-);
and U is a halide, hydroxide, or carbonate;
provided in an amount effective to increase the amount of force necessary to remove the implanted surgical device.
2. The process of claim 1 wherein the sealant and/or adhesive is applied to the site where the implantable surgical device is to be secured.
3. The process of claim 1 wherein the surgical device is selected from the group consisting of screws, pins, plates, anchors, rods, clamps, clips, staples, rivets, hooks, buttons and snaps.
4. The process of claim 1 wherein the surgical device is made of a bioabsorbable polymeric material.
5. The process of claim 1 wherein the adhesive and/or sealant is selected from the group consisting of .alpha.-cyanoacrylates, vinylidene cyanides, C1-C4 alkyl homologues of vinylidene cyanides, dialkyl methylene malonates, acylacrylonitriles, vinyl sulfinates and vinyl sulfonates.
6. The process of claim 1 wherein the adhesive and/or sealant is selected from the group consisting of materials having the formula:
wherein R3 is hydrogen and R4 is a hydrocarbon, a substituted hydrocarbon group, a group having the formula -R5-O-R6-O-R7, wherein R5 is a 1,2-alkylene group having 2-4 carbon atoms, R6 is an alkylene group having 2-4 carbon atoms, and R7 is an alkyl group having 1-6 carbon atoms; or a group having the formula:
wherein R8 is -CH2-, , or -C(CH3)2- and R9 is an organic radical.
wherein R3 is hydrogen and R4 is a hydrocarbon, a substituted hydrocarbon group, a group having the formula -R5-O-R6-O-R7, wherein R5 is a 1,2-alkylene group having 2-4 carbon atoms, R6 is an alkylene group having 2-4 carbon atoms, and R7 is an alkyl group having 1-6 carbon atoms; or a group having the formula:
wherein R8 is -CH2-, , or -C(CH3)2- and R9 is an organic radical.
7. The process of claim 1 wherein the adhesive and/or sealant is selected from the group consisting of methyl alpha-cyanoacrylate, butyl alpha-cyanoacrylate, octyl alpha-cyanoacrylate, 1-methoxy-2-propyl cyanoacrylate, 2-butoxy ethyl cyanoacrylate, and isopropoxy-ethyl cyanoacrylate.
8. The process of claim 1 wherein the adhesive and/or sealant is a bioabsorbable semi-crystalline aliphatic poly(ester) homopolymer selected from the group consisting of poly(.epsilon.-caprolactone), poly(p-dioxanone), and poly(trimethylene carbonate).
9. The process of claim 1 wherein the adhesive and/or sealant is a bioabsorbable semi-crystalline aliphatic poly(ester) copolymer composed of from about 100 mole percent to about 70 mole percent of .epsilon.-caprolactone repeating units with the remainder of the polymer being a plurality of second lactone repeating units selected from the group consisting of glycolide repeating units, lactide repeating units, 1,4-dioxanone repeating units, 1,4-dioxepan-2-one repeating units, 1,5-dioxepan-2-one repeating units, trimethylene carbonate repeating units, and combinations thereof.
10. The process of claim 1 wherein the adhesive and/or sealant is applied to the implantable surgical device and the surgical device is then secured to the bone tissue.
11. An implantable surgical device comprising an implantable surgical device that is at least partially coated with a biocompatible adhesive and/or sealant selected from the group consisting of:
(a) a material made from monomers of the formula:
CHR1=CX1Y1 wherein X1 and Y1 are each strong electron withdrawing groups, and R1 is hydrogen or, provided that X1 and Y1 are both cyano groups, a C1-C4 alkyl group;
(b) a bioabsorbable semi-crystalline aliphatic poly(ester) of the formula:
[-O-R11-C(O)-]y, wherein R11 is selected from the group consisting of -CR12H-, -(CH2)3-O-, -CH2-CH2-O-CH2-, CR12H-CH2, -(CH2)4-, -(CH2)z-O-C(O)- and -(CH2)z-C(O)-CH2-; R12 is hydrogen or methyl; z is an integer in the range of from 1 to 7 and y is an integer in the range of from about 10 to about 20,000; and (c) a slurry of water and a calcium containing compound with the general formula:
M2+10-nN1+2n(WO43-)6mUx-where n is an integer from 1 to 10, and m is 2 when x is 1, or m is 1 when x is 2, M and N are alkali or alkaline earth metals; WO4 is an acid radical and W is phosphorus, vanadium, sulfur, silicon, or is substituted in whole or part with carbonate (CO32-);
and U is a halide, hydroxide, or carbonate; provided in an amount effective to increase the amount of force necessary to remove the implanted surgical device.
(a) a material made from monomers of the formula:
CHR1=CX1Y1 wherein X1 and Y1 are each strong electron withdrawing groups, and R1 is hydrogen or, provided that X1 and Y1 are both cyano groups, a C1-C4 alkyl group;
(b) a bioabsorbable semi-crystalline aliphatic poly(ester) of the formula:
[-O-R11-C(O)-]y, wherein R11 is selected from the group consisting of -CR12H-, -(CH2)3-O-, -CH2-CH2-O-CH2-, CR12H-CH2, -(CH2)4-, -(CH2)z-O-C(O)- and -(CH2)z-C(O)-CH2-; R12 is hydrogen or methyl; z is an integer in the range of from 1 to 7 and y is an integer in the range of from about 10 to about 20,000; and (c) a slurry of water and a calcium containing compound with the general formula:
M2+10-nN1+2n(WO43-)6mUx-where n is an integer from 1 to 10, and m is 2 when x is 1, or m is 1 when x is 2, M and N are alkali or alkaline earth metals; WO4 is an acid radical and W is phosphorus, vanadium, sulfur, silicon, or is substituted in whole or part with carbonate (CO32-);
and U is a halide, hydroxide, or carbonate; provided in an amount effective to increase the amount of force necessary to remove the implanted surgical device.
12. The surgical devices of claim 11 wherein the surgical device is selected from the group consisting of screws, pins, plates, anchors, rods, clamps, clips, staples, rivets, hooks, buttons and snaps.
13. The surgical device of claim 11 wherein the surgical device is made of a bioabsorbable polymeric material.
14. The surgical device of claim 11 wherein the adhesive and/or sealant that at least partially coats the surgical device is selected from the group consisting of .alpha.-cyanoacrylates, vinylidene cyanides, C1-C4 alkyl homologues of vinylidene cyanides, dialkyl methylene malonates, acylacrylonitriles, vinyl sulfinates and vinyl sulfonates.
15. The surgical device of claim 11 wherein the adhesive and/or sealant that at least partially coats the surgical device is selected from the group consisting of materials having the formula:
wherein R3 is hydrogen and R4 is a hydrocarbon, a substituted hydrocarbon group, a group having the formula -R5-O-R6-O-R7, wherein R5 is a 1,2-alkylene group having 2-4 carbon atoms, R6 is an alkylene group having 2-4 carbon atoms, and R7 is an alkyl group having 1-6 carbon atoms; or a group having the formula:
wherein R8 is -CH2-, , or -C(CH3)2- and R9 is an organic radical.
wherein R3 is hydrogen and R4 is a hydrocarbon, a substituted hydrocarbon group, a group having the formula -R5-O-R6-O-R7, wherein R5 is a 1,2-alkylene group having 2-4 carbon atoms, R6 is an alkylene group having 2-4 carbon atoms, and R7 is an alkyl group having 1-6 carbon atoms; or a group having the formula:
wherein R8 is -CH2-, , or -C(CH3)2- and R9 is an organic radical.
16. The surgical device of claim 11 wherein the adhesive and/or sealant that at least partially coats the surgical device is selected from the group consisting of methyl alpha-cyanoacrylate, butyl alpha-cyanoacrylate, octyl alpha-cyanoacrylate, 1-methoxy-2-propyl cyanoacrylate, 2-butoxy ethyl cyanoacrylate, and isopropoxy-ethyl cyanoacrylate.
17. The surgical device of claim 11 wherein the adhesive and/or sealant that at least partially coats the surgical device is a bioabsorbable semi-crystalline aliphatic poly(ester) homopolymer selected from the group consisting of poly(.epsilon.-caprolactone), poly(p-dioxanone), and poly(trimethylene carbonate).
18. The surgical device of claim 11 wherein the adhesive and/or sealant that at least partially coats the surgical device is a bioabsorbable semi-crystalline aliphatic poly(ester) copolymer composed of from about 100 mole percent to about 70 mole percent of .epsilon.-caprolactone repeating units with the remainder of the polymer being a plurality of second lactone repeating units selected from the group consisting of glycolide repeating units, lactide repeating units, 1,4-dioxanone repeating units, 1,4-dioxepan-2-one repeating units, 1,5-dioxepan-2-one repeating units, trimethylene carbonate repeating units, and combinations thereof.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/385,015 | 1995-02-07 | ||
| US08/385,015 US5550172A (en) | 1995-02-07 | 1995-02-07 | Utilization of biocompatible adhesive/sealant materials for securing surgical devices |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2168822A1 true CA2168822A1 (en) | 1996-08-08 |
Family
ID=23519689
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002168822A Abandoned CA2168822A1 (en) | 1995-02-07 | 1996-02-05 | Utilization of biocompatible adhesive/sealant materials for securing surgical devices |
Country Status (8)
| Country | Link |
|---|---|
| US (1) | US5550172A (en) |
| EP (1) | EP0727230B1 (en) |
| JP (1) | JPH08252306A (en) |
| AU (1) | AU4339096A (en) |
| BR (1) | BR9600353A (en) |
| CA (1) | CA2168822A1 (en) |
| DE (1) | DE69637081T2 (en) |
| ZA (1) | ZA96936B (en) |
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| USRE33221E (en) * | 1982-04-29 | 1990-05-22 | American Dental Association Health Foundation | Dental restorative cement pastes |
| USRE33161E (en) * | 1982-04-29 | 1990-02-06 | American Dental Association Health Foundation | Combinations of sparingly soluble calcium phosphates in slurries and pastes as mineralizers and cements |
| US4440789A (en) * | 1982-11-16 | 1984-04-03 | Ethicon, Inc. | Synthetic absorbable hemostatic composition |
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| US4612053A (en) * | 1983-10-06 | 1986-09-16 | American Dental Association Health Foundation | Combinations of sparingly soluble calcium phosphates in slurries and pastes as mineralizers and cements |
| US4668295A (en) * | 1985-04-25 | 1987-05-26 | University Of Dayton | Surgical cements |
| GB2197329B (en) * | 1986-09-10 | 1990-01-10 | Showa Denko Kk | Hard tissue substitute composition |
| JP2558262B2 (en) * | 1986-11-04 | 1996-11-27 | 住友大阪セメント 株式会社 | Artificial joint fixation material |
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| JP2548745B2 (en) * | 1987-10-15 | 1996-10-30 | 住友大阪セメント株式会社 | Bone cement composition |
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| JPH0241171A (en) * | 1988-07-28 | 1990-02-09 | Mamoru Nagase | Artificial bone cured and formed by mixing tricalcium phosphate, acid, protein, water and hydroxyapatite |
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| CA2027921C (en) * | 1989-10-19 | 1997-12-09 | Nobuo Nakabayashi | Bone cement composition, cured product thereof, implant material and process for the preparation of the same |
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| US5328687A (en) * | 1993-03-31 | 1994-07-12 | Tri-Point Medical L.P. | Biocompatible monomer and polymer compositions |
-
1995
- 1995-02-07 US US08/385,015 patent/US5550172A/en not_active Expired - Lifetime
-
1996
- 1996-02-05 CA CA002168822A patent/CA2168822A1/en not_active Abandoned
- 1996-02-06 AU AU43390/96A patent/AU4339096A/en not_active Abandoned
- 1996-02-06 ZA ZA9600936A patent/ZA96936B/en unknown
- 1996-02-06 DE DE69637081T patent/DE69637081T2/en not_active Expired - Fee Related
- 1996-02-06 EP EP96300790A patent/EP0727230B1/en not_active Expired - Lifetime
- 1996-02-07 JP JP8044075A patent/JPH08252306A/en active Pending
- 1996-02-07 BR BR9600353A patent/BR9600353A/en not_active Application Discontinuation
Also Published As
| Publication number | Publication date |
|---|---|
| EP0727230B1 (en) | 2007-05-16 |
| AU4339096A (en) | 1996-08-15 |
| DE69637081D1 (en) | 2007-06-28 |
| BR9600353A (en) | 1998-01-27 |
| EP0727230A2 (en) | 1996-08-21 |
| EP0727230A3 (en) | 1999-02-03 |
| DE69637081T2 (en) | 2008-01-17 |
| US5550172A (en) | 1996-08-27 |
| ZA96936B (en) | 1997-08-06 |
| JPH08252306A (en) | 1996-10-01 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued |