CA2062012C - Bioabsorbable interference bone fixation screw - Google Patents
Bioabsorbable interference bone fixation screw Download PDFInfo
- Publication number
- CA2062012C CA2062012C CA002062012A CA2062012A CA2062012C CA 2062012 C CA2062012 C CA 2062012C CA 002062012 A CA002062012 A CA 002062012A CA 2062012 A CA2062012 A CA 2062012A CA 2062012 C CA2062012 C CA 2062012C
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- CA
- Canada
- Prior art keywords
- bone fixation
- screw
- recited
- fixation screw
- driver
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/84—Fasteners therefor or fasteners being internal fixation devices
- A61B17/86—Pins or screws or threaded wires; nuts therefor
- A61B17/8645—Headless screws, e.g. ligament interference screws
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/84—Fasteners therefor or fasteners being internal fixation devices
- A61B17/86—Pins or screws or threaded wires; nuts therefor
- A61B17/8605—Heads, i.e. proximal ends projecting from bone
- A61B17/861—Heads, i.e. proximal ends projecting from bone specially shaped for gripping driver
- A61B17/8615—Heads, i.e. proximal ends projecting from bone specially shaped for gripping driver at the central region of the screw head
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
- A61B17/84—Fasteners therefor or fasteners being internal fixation devices
- A61B17/86—Pins or screws or threaded wires; nuts therefor
- A61B17/8625—Shanks, i.e. parts contacting bone tissue
- A61B17/863—Shanks, i.e. parts contacting bone tissue with thread interrupted or changing its form along shank, other than constant taper
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
- A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
- A61B17/88—Osteosynthesis instruments; Methods or means for implanting or extracting internal or external fixation devices
- A61B17/8875—Screwdrivers, spanners or wrenches
- A61B17/8877—Screwdrivers, spanners or wrenches characterised by the cross-section of the driver bit
- A61B17/888—Screwdrivers, spanners or wrenches characterised by the cross-section of the driver bit the driver bit acting on the central region of the screw head
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00004—(bio)absorbable, (bio)resorbable, resorptive
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S606/00—Surgery
- Y10S606/907—Composed of particular material or coated
- Y10S606/908—Bioabsorbable material
Abstract
An interference bone fixation screw fabricated from bioabsorbable material includes a body having a proximal end, a distal end and a screw thread disposed therealong from the proximal end to the distal end. A drive recess is formed in the body to extend longitudinally from the proximal end toward the distal end for receiving a rotatable driver. The drive recess defines a plurality of radial force receiving surfaces for receiving concentric forces from the driver applied perpendicularly to the force receiving surfaces.
Description
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BACKGROUND OF T~iE TNVENTION
1 Field Of The Invention 2 The present invention relates to surgical screws for 3 fixation in bone and, more specifically, to bioabsorbable 4 interference bone screws particularly useful in securing a ligament in a bone tunnel.
6 Description Of The Prior Art 7 Graft and prosthetic ligaments are utilized to surgically 8 repair and/ar replace ligaments damaged by injury or disease.
9 Surgical procedures to repair and/or replace ligaments generally involve forming a tunnel in bone, positioning a graft or 11 prosthetic ligament in the bone tunnel, and anchoring the ends, 12 or bone blocks, of the ligament to the walls of the bone tunnel.
13 Various devices are typically employed to secure the bone blocks 14 of the ligament in the bone tunnel, including buttons, staples, expanding cones, unicortical screw posts, as well as interference 16 screws. When interference screws are used, the screws are 17 inserted into the bone tunnel to engage the tunnel wall and the 18 bone blocks of the ligament and, thus, provide an endosteum or 1~ endosteal fixation therebetween.
Surgieal bone screws for fixation in bone and for anchoring 21 ligaments to bone are typically fabricated from medically 22 approved metallic materials that are riot naturally absorbed by 23 the body. An illustrative metallic bone screw is the M.
24 Kurosaka~'' bone screw manufactured by nePuy, a division of wJ ~' I ~? A ' i.J 3.i x~~ ~ y~ u.. y.J
Boehringer Mannheim Corporation, and a further example of a metallic bone screw is shown in U.S. Patent No. 4,'754,749 to Tsou. Most metallic bone screws include a threaded shank joined to an enlarged head having a transverse slot or hexagonal socket formed therein to engage, respectively, a similarly configured, single blade or hexagonal rotatable driver for turning the screw into a bone. The enlarged heads on such screws can protrude from the bone and can cause chronic irritation and inflammation of surrounding body tissue. Metallic bone screws that do not have enlarged heads possess disadvantages because mismatch between screw length and the length of the ligament bone block can result in the screw being inserted too far, or not being inserted to its.
full length, in the bone tunnel. In anterior cruciate ligament repair and reconstruction, insertion of the screw too far can produce intraarticular penetration, and failure to insert the screw its full length can irritate adjacent soft tissue.
Additionally, placement of screws in bone tunnels formed in movable joints can, in certain instances, cause abrading of ligaments during normal motion of the joint. Furthermore, bone screws occasionally back out after insertion; and, when this accurs, the hone screw can protrude into surrounding tissue and cause discomfort. Because metallic bone screws are not assimilated by the body, additional surgical procedures may be required to remove problematic bone screws once the fixated bone and/or tissue has healed.
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Biodegradable bone screws have been proposed, as exemplified in U.S. Patent No. 4,356,572 to Guillemin and International Application PCT/~P 89/00344, and as alluded to in U.S. Patent No.
4,927,421 to Goble et al, Bioabsorbable bone screws possess the advantage of being naturally degradable by the body; and, therefore, contact with surrounding tissue after insertion does not necessitate surgical intervention because 'the screw will be completely absorbed by the body once the bone and/or tissue has healed. However, conventional bioabsorbable bane screws present numerous difficulties due to bioabsorbable materials being considerably softer than metallic compositions. In particular, bone screws made from bioabsorbable materials are susceptible to deformation and deflection when subjected to forces required to drive the screw into relatively hard tissue, such as bone, and the transverse slot and hexagonal socket typically provided in bone screws as drive recesses for receiving standard, similarly configured, rotatable drivers are unsuitable for bone screws fabricated of bioabsorbable material. The high torque that must be applied to bone screws by a driver to produce rotation of the screw in bone can cause shear deformation of the relatively soft bioabsorbable material, and the surfaces of the drive recesses can be sheared, or stripped, by the drivers. Additionally, single blade and hexagonal drivers tend to force the walls of the drive recesses outwardly when rotated therein producing outward expansion, or "mushrooming" of bioabsorbable screws.
Furthermore, some drive recesses extend the entire length of the Ie A
;.~.1 ~ ~ ~~ ~ 4~ ~i~ 1-1 1 bone screw, and these drive recesses require that a significant 2 quantity of material be removed from the bone screw resulting in 3 a reduction in strength of the bone screw and impairing the 4 overall resistance of the screw to deformation and damage when being driven into bone. For similar reasons, bioabsorbable bone 6 screws are generally limited to use in open surgery, as opposed 7 to closed, or endoscopic, surgery, because it is advantageous in 8 endoscopic techniques for the screws to be cannulated, i.e.
9 include a central longitudinal bore, for insertion along a guide wire. Formation of the central bore involves removing additional 11 quantities of material from the screw and, therefore, 12 structurally weakens bioabsorbabie screws.
13 Alternative drive recesses, such as those defining multiple, 14 radially oriented prongs for receiving similarly configured, multi-pronged drivers have been proposed for metallic screws, and 1.6 illustrative drive arrangements are shown in U.S. Patent Nos.
17 4,084,478 to Simmons; 3,872,904 to Barlow; 3,658,105 to Burt e1 18 al; 3,575,080 to Henney; 3,122,963 to Borgeson; 2,445,978 to 19 Stellin; 2,445,525 to Golden and 2,397,216 to Stellin. These drive recesses are formed in enlarged heads on metallic 21 industrial screws, and typically taper longitudinally to a narrow 22 end for engaging a similarly tapered driver. Multi-pronged drive 23 recesses designed for metallic screws generally cannot be 24 employed successfully in bioabsorbable bone screws because the forces applied by compatible multi-pronged drivers to such drive 26 recesses include outwardly directed force components that cause i't w f,~ ~~ 'i_7 ~ 1~ ..~~ ji w 1 outward expansion, or "mushrooming", in bioabsorbable bone 2 scxews. Furthermore, the walls defining mufti-pronged drive 3 recesses are typically configured to permit outward expansion of 4 the screw material separating the radial prongs of the drive recess when the associated driver imposes force on the walls.
5 Although this configuration is acceptable for metallic screws, it 7 further promotes !'mushrooming" in bioabsorbable bone screws due 8 to the inherent relative softness of bioabsorbable materials.
9 Conventional mufti-pronged drivers also produce shear on the walls of corresponding drive recesses; and, when utilized in 11 bioabsorbable bone screws, the walls can be sheared off, or 12 stripped, by tile drivers. Furthermore, many conventional multi-13 pronged drive recesses have only a small quantity of screw 14 material separating the radial prongs of the drive recesses, and bioabsorbable bone screws having these types of drive recesses 16 are particularly vulnerable to shear deformation and can not 17 withstand high drive forces. Additionally. the lnnnit",a;"~, 18 taper in conventional mufti-pronged drive recesses results in 19 high concentrations of drive forces being applied by the drivers ~0 at the narrow end of the drive recesses where there is relatively 22 less screw material to resist deformation, and bioabsorbable 22 screws having tapered drive recesses are likely to experience ~3 significant deformation when driven into bone.
id l~ ~~ H:. y~
BACKGROUND OF T~iE TNVENTION
1 Field Of The Invention 2 The present invention relates to surgical screws for 3 fixation in bone and, more specifically, to bioabsorbable 4 interference bone screws particularly useful in securing a ligament in a bone tunnel.
6 Description Of The Prior Art 7 Graft and prosthetic ligaments are utilized to surgically 8 repair and/ar replace ligaments damaged by injury or disease.
9 Surgical procedures to repair and/or replace ligaments generally involve forming a tunnel in bone, positioning a graft or 11 prosthetic ligament in the bone tunnel, and anchoring the ends, 12 or bone blocks, of the ligament to the walls of the bone tunnel.
13 Various devices are typically employed to secure the bone blocks 14 of the ligament in the bone tunnel, including buttons, staples, expanding cones, unicortical screw posts, as well as interference 16 screws. When interference screws are used, the screws are 17 inserted into the bone tunnel to engage the tunnel wall and the 18 bone blocks of the ligament and, thus, provide an endosteum or 1~ endosteal fixation therebetween.
Surgieal bone screws for fixation in bone and for anchoring 21 ligaments to bone are typically fabricated from medically 22 approved metallic materials that are riot naturally absorbed by 23 the body. An illustrative metallic bone screw is the M.
24 Kurosaka~'' bone screw manufactured by nePuy, a division of wJ ~' I ~? A ' i.J 3.i x~~ ~ y~ u.. y.J
Boehringer Mannheim Corporation, and a further example of a metallic bone screw is shown in U.S. Patent No. 4,'754,749 to Tsou. Most metallic bone screws include a threaded shank joined to an enlarged head having a transverse slot or hexagonal socket formed therein to engage, respectively, a similarly configured, single blade or hexagonal rotatable driver for turning the screw into a bone. The enlarged heads on such screws can protrude from the bone and can cause chronic irritation and inflammation of surrounding body tissue. Metallic bone screws that do not have enlarged heads possess disadvantages because mismatch between screw length and the length of the ligament bone block can result in the screw being inserted too far, or not being inserted to its.
full length, in the bone tunnel. In anterior cruciate ligament repair and reconstruction, insertion of the screw too far can produce intraarticular penetration, and failure to insert the screw its full length can irritate adjacent soft tissue.
Additionally, placement of screws in bone tunnels formed in movable joints can, in certain instances, cause abrading of ligaments during normal motion of the joint. Furthermore, bone screws occasionally back out after insertion; and, when this accurs, the hone screw can protrude into surrounding tissue and cause discomfort. Because metallic bone screws are not assimilated by the body, additional surgical procedures may be required to remove problematic bone screws once the fixated bone and/or tissue has healed.
. a; .-: ~ r .:
Biodegradable bone screws have been proposed, as exemplified in U.S. Patent No. 4,356,572 to Guillemin and International Application PCT/~P 89/00344, and as alluded to in U.S. Patent No.
4,927,421 to Goble et al, Bioabsorbable bone screws possess the advantage of being naturally degradable by the body; and, therefore, contact with surrounding tissue after insertion does not necessitate surgical intervention because 'the screw will be completely absorbed by the body once the bone and/or tissue has healed. However, conventional bioabsorbable bane screws present numerous difficulties due to bioabsorbable materials being considerably softer than metallic compositions. In particular, bone screws made from bioabsorbable materials are susceptible to deformation and deflection when subjected to forces required to drive the screw into relatively hard tissue, such as bone, and the transverse slot and hexagonal socket typically provided in bone screws as drive recesses for receiving standard, similarly configured, rotatable drivers are unsuitable for bone screws fabricated of bioabsorbable material. The high torque that must be applied to bone screws by a driver to produce rotation of the screw in bone can cause shear deformation of the relatively soft bioabsorbable material, and the surfaces of the drive recesses can be sheared, or stripped, by the drivers. Additionally, single blade and hexagonal drivers tend to force the walls of the drive recesses outwardly when rotated therein producing outward expansion, or "mushrooming" of bioabsorbable screws.
Furthermore, some drive recesses extend the entire length of the Ie A
;.~.1 ~ ~ ~~ ~ 4~ ~i~ 1-1 1 bone screw, and these drive recesses require that a significant 2 quantity of material be removed from the bone screw resulting in 3 a reduction in strength of the bone screw and impairing the 4 overall resistance of the screw to deformation and damage when being driven into bone. For similar reasons, bioabsorbable bone 6 screws are generally limited to use in open surgery, as opposed 7 to closed, or endoscopic, surgery, because it is advantageous in 8 endoscopic techniques for the screws to be cannulated, i.e.
9 include a central longitudinal bore, for insertion along a guide wire. Formation of the central bore involves removing additional 11 quantities of material from the screw and, therefore, 12 structurally weakens bioabsorbabie screws.
13 Alternative drive recesses, such as those defining multiple, 14 radially oriented prongs for receiving similarly configured, multi-pronged drivers have been proposed for metallic screws, and 1.6 illustrative drive arrangements are shown in U.S. Patent Nos.
17 4,084,478 to Simmons; 3,872,904 to Barlow; 3,658,105 to Burt e1 18 al; 3,575,080 to Henney; 3,122,963 to Borgeson; 2,445,978 to 19 Stellin; 2,445,525 to Golden and 2,397,216 to Stellin. These drive recesses are formed in enlarged heads on metallic 21 industrial screws, and typically taper longitudinally to a narrow 22 end for engaging a similarly tapered driver. Multi-pronged drive 23 recesses designed for metallic screws generally cannot be 24 employed successfully in bioabsorbable bone screws because the forces applied by compatible multi-pronged drivers to such drive 26 recesses include outwardly directed force components that cause i't w f,~ ~~ 'i_7 ~ 1~ ..~~ ji w 1 outward expansion, or "mushrooming", in bioabsorbable bone 2 scxews. Furthermore, the walls defining mufti-pronged drive 3 recesses are typically configured to permit outward expansion of 4 the screw material separating the radial prongs of the drive recess when the associated driver imposes force on the walls.
5 Although this configuration is acceptable for metallic screws, it 7 further promotes !'mushrooming" in bioabsorbable bone screws due 8 to the inherent relative softness of bioabsorbable materials.
9 Conventional mufti-pronged drivers also produce shear on the walls of corresponding drive recesses; and, when utilized in 11 bioabsorbable bone screws, the walls can be sheared off, or 12 stripped, by tile drivers. Furthermore, many conventional multi-13 pronged drive recesses have only a small quantity of screw 14 material separating the radial prongs of the drive recesses, and bioabsorbable bone screws having these types of drive recesses 16 are particularly vulnerable to shear deformation and can not 17 withstand high drive forces. Additionally. the lnnnit",a;"~, 18 taper in conventional mufti-pronged drive recesses results in 19 high concentrations of drive forces being applied by the drivers ~0 at the narrow end of the drive recesses where there is relatively 22 less screw material to resist deformation, and bioabsorbable 22 screws having tapered drive recesses are likely to experience ~3 significant deformation when driven into bone.
iyJ ~ s !,a ~., . a 2 Accordingly, it is a primary object of the present invention 3 to overcome the above mentioned disadvantages associated with 4 prior art metal and bioabsorbable bone screws.
Another object of the invention is to eliminate radial 6 deformation in a bioabsorbable bone screw when it is driven into 7 bone.
Another object of the invention is to eliminate radial 6 deformation in a bioabsorbable bone screw when it is driven into 7 bone.
8 It is also an object of the invention to eliminate shear 9 deformation in a bioabsorbable bone screw when it is driven into bone.
11 Moreover, it is an object of the invention to prevent 12 outward expansion, or "mushrooming", of a bioabsorbable bone 13 screw when it is driven into bone.
14 A further object of the invention is to provide a bioabsorbable bone screw capable of withstanding high drive 16 forces when driven into bone.
17 Another object of the invention is to provide a 18 bioabsorbable bone screw having a mufti-lobed drive recess 19 receiving a mufti-lobed driver that applies concentric forces to walls of the drive recess in a direction perpendicular to such 21 walls, 22 A still further object of the invention is to provide a 23 bioabsorable bone screw including a drive recess having radially 24 oriented force receiving walls for receiving forces from a driver applied perpendicularly to such walls.
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1 Some of the advantages of the bioabsorbable interference 2 bone fixation screw according to the present invention over the 3 prior art are that the bone screw is naturally degraded and 4 absorbed by the body upon completion of healing of the fixated bone and/or tissue, presents no exterior enlargements that might 6 protrude into bodily tissue, is self-tapping and is suitable for 7 use in closed, or endoscopic, surgery as well as in open surgery.
8 These and other objects, attributes and benefits are 9 achieved with the bioabsorbable interference bone fixation screw of the present invention as characterized by a body having a 11 proximal end, a conically tapered distal end and a helical screw Z2 thread disposed on the body from the proximal end to the distal 13 end and having a major diameter that defines the major diameter 1~ for the bone screw. A drive recess for engaging a rotatable driver is formed in the body to extend longitudinally from the 16 proximal end toward the distal end. The drive recess includes a 17 cylindrical cavity disposed concentrically in the body, and a 18 plurality of lobe openings positioned radially around the cavity 19 in communication therewith and extending longitudinally therealong. Each of the lobe openings is defined by a pair of 21 side walls in radial alignment with the central longitudinal axis 22 of the body, and an..arcuate outer wall joining the side walls, 23 such that the lobe openings are wider at the arcuate outer walls 24 and narrower at the cylindrical cavity. A central longitudinal guide bore is formed in the body to extend longitudinally from 26 the drive recess to the distal end for guiding the screw on a . ,,- , ,<,x. ;:
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l guide wire. A driver configured to be matingly received in the 2 drive recess includes a shaft and a plurality of lobes having 3 side walls extending radially outwardly from the shaft for 4 applying concentric forces to the side walls of the drive recess in a direction perpendicular to such side walls.
S Other objects and advantages of the present invention will 7 become apparent from the following description of the preferred 8 embodiment taken in conjunction with the accompanying drawings 9 wherein like parts in each of the several figures are identified by the same reference characters.
12 Fig. 1 is a side view of the bioabsorbable interference bone 13 fixation screw according to the present invention.
14 Fig. 2 is a proximal end view of the bioabsorbable interference bone fixation screw of Fig. 1.
L6 Fig. 3 is, a perspective view of a driver for rotating the 17 bioabsorbabl e interference bone fixation screw of Fig. 1.
18 Fig. 4 is a cross-sectional view of the driver taken along 19 line 6-6 ofFig. 3.
Fig. 5 is a broken, longitudinal sectional view of the 21 driver ted in'the bone screw of Fig. 1.
inser 22 Fig. 6 is a broken, sectional view snowing the bone screw of 23 Fig. 1 being driven by the driver.
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2 Referring to Figs. 1 and 2, the bone screw 10 according to 3 the present invention includes a longitudinally elongated 4 cylindrical body 12 having a proximal end 14, a distal end 16 and a helical screw thread 18 disposed externally on body 12 from 6 proximal end 14 to distal end 16. Thread 18 includes a proximal 7 thread section 20 extending longitudinally from the proximal end 8 . 14 in the direction of the distal end 16 and a conically tapered distal thread section 24 extending longitudinally from the proximal thread section 20 to the distal end 16. The threads of 11 proximal thread section 20 are of uniform pitch and like-handed;
12 that is, they extend in the same angular direction about the 13 screw. The major diameter (i.e., the diameter of the crests) of 14 the threads in proximal thread section 20 defines the major diameter for the screw, and a cylindrical surface 22 on body 12 16 defines the minor diameter for proximal thread section 20.
17 Distal thread section 24 carries a thread having a major diameter 18 that is less than the major diameter of the threads in proximal 19 thread section 20. The thread for distal thread section 24 tapers conically from the proximal thread section 20 to the 21 distal end 16 in a spiral configuration, and the pitch of this 22 thread is greater than the pitch of the threads fn the proximal 23 thread section 20.
24 A drive recess 30 for receiving a rotatable driver is formed in body 12 to extend longitudinally from proximal end 14 in the 26 direction of distal end 16 to an end wall 32 disposed t a L~ j2 iJ ~r.. :a 1 perpendicular to the central longitudinal axis of body 12. As 2 best shown in Fig. 2, drive recess 30 includes a cylindrical 3 cavity 34 formed concentrically in body 12 to extend 4 longitudinally from proximal end 14 to end wall 32 and three equally spaced lobe openings or chambers 36 radially disposed 6 around cavity 34 in communication therewith and extending 7 longitudinally therealong to end wall 32. Cavity 34 is defined 8 by three inner arcuate walls 38 positioned between lobe openings 9 36 and disposed a constant radial distance from the central longitudinal axis of body 12. Each lobe opening 36 is defined by 11 a pair of spaced, planar side walls 40 and an outer arcuate wall 1?. 42 joining opposing side walls 40. Outer arcuate walls 42 are 13 disposed a constant radial distance from the central longitudinal 14 axis of body 12, and this radial distance is greater than the radial distance far inner arcuate walls 38. Side walls 40 extend 16 radially outwardly from inner arcuate walls 38 and are positioned 17 in radial alignment with the central longitudinal axis of body 18 12, such that lobe openings 36 taper inwardly from an outer end 19 44 defined by outer arcuate walls 42 to a mouth or inner end 46 communicating with cavity 34. Outer arcuate walls 42 are joined 21 to end wall 32 by inwardly curved walls 48, such that the cross-22 section of drive recess 30 is constant through a substantial 23 portion of its length. A central, longitudinal guide bore or 24 cannulation 50 is disposed concentrically within body 12 in communication with drive recess 30 and extends longitudinally 26 from end wall 32 to distal end 16.
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1 Preferably, the minor diameter for the proximal thread 2 section 20 defined by the surface 22 is 55~ to 75~ the major 3 diameter for the screw; the thread 18 is configured in accordance 4 with ISO 5835/1; the length of the drive recess 30 from proximal end 14 to end wall 32 is approximately 48~ to 95~ the overall 6 length of body 12 measured from proximal end 14 to distal end 16;
7 the inner arcuate walls 38 of the cavity 34 define arcs of a 8 circle having a diameter that is approximately 47~ the minor 9 diameter of the proximal thread section 20; the outer arcuate walls 42 of the lobe openings 36 define arcs subtending 11 approximately 50° along a circle having a diameter that is 12 approximately 78~ the minor diameter of proximal thread section 13 20 and these arcs are shorter in length than the arcs defined by 14 inner arcuate walls 38.
The relative proportions of the bone screw produce numerous 16 structural and functional advantages. The relatively large minor 17 diameter for the thread 18 in the proximal thread section 20 18 increases the quantity of screw material surrounding the drive 19 recess 30 and, therefore, the strength of the bone screw in resisting shear and radial deformation when being rotated by a 21 driver received in the drive recess. The size of the minor 22 diameter for the proximal thread section 20 relative to the major 23 diameter for the bone screw increases the overall strength of the 24 body 12 yet provides thread 18 with sufficient depth to insure proper fixation in bone. The conical taper for the distal thread 26 section 24 and the spiral configuration and relatively greater i a .~ ~.i 1 pitch of the thread in the distal thread section assists 2 advancement of the bone screw and eliminates the need for a 3 tapping procedure. The length of the drive recess 30 relative to 4 the overall length of the body 12 and to the minor diameter for the proximal thread section 20 allows drive forces to be 6 distributed through body 12 and increases the magnitude of force 7 that the bone screw can withstand. Furthermore, the length of 8 the drive recess 30 is selected to limit the quantity of material 9 removed from the screw and maintain structural integrity around the cannulation 76. Additionally, drive recess 30 distributes 11 drive forces equally throughout its length due to the cross-12 section of the drive recess being constant through a substantial 13 portion of its length. The diameters of the circles defined by 14 the inner arcuate walls 38 and the outer arcuate walls 42 of the drive recess 30 further insure that a quantity of screw material 16 sufficient to withstand drive forces surrounds the drive recess 17 30, and the length of the arcs defined by the outer arcuate walls 18 42 provides relatively large quantities of screw material between 19 the lobe openings 36.
Bone screw ZO is fabricated entirely from a bioabsorbable or 21 biodegradable polymer or copolymer having an absorption or 22 degradation time selected in accordance with the anticipated 23 healing time for the fixated tissue. Table I set forth below 24 lists polymers (and copolymers and terpolymers thereof) suitable far bone screw 10, and these polymers are all biodegradable into 26 water-soluble, non-toxic materials that are safely eliminated by '~~ f ~.j p'1 n ,~ ~~ ' ?
:,d i.r t1 r~r Y>l 1 the body. Although the illustrative polymers are normally 2 linear, suitable cross linked resins can be prepared therefrom.
i~.j Y.$
~' ' %.3 ~ ~ ~ '. ~e 'TABLE I
Polymer Polycaprolactone Poly (L
-lactide) Poly (DL lactide) -Polyglycolide 95:5 Poly (DL lactide co-glycolide) - -90:10Poly (DL lactide co-glycolide) - -85:15Poly (DL lactide co-glycolide) - -75:25Poly (DL lactide co-glycolide) - -54:50Poly (DL lactide co-glycolide) - -90:14Poly (DL lactide co-caprolactone) -75:25Poly (DL lactide co-caprolactone) - -50:54Poly (DL lactide - co-caprolactone) -A preferred material for bone screw l4 is Poly (L-Lactide), and the preferred chemical specifications for raw poly-lactide acid employed for bone screw i4 are set forth below in Table II.
'~~i ~' ~3 a i,~ ~i.~ i.~ rl il ~. ~~e TABLE II
Raw Polv-Lactic Acid Residual Tin (Stannous actoate): Less than 200ppm Residual Metals (FE, Cr, Ni, Pb): Less than 50ppm each Residual Lactide Dimer: Less than 1~
Intrinsic Viscosity: 6.5-8.5 dL/g in chloroform at 25°C
Bone screw 10 is preferably formed by an injection molding process, and the preferred characteristics of the bone screw thusly formed are set forth below in Table III.
TABLE III
Bone Screw Ultimate Tensile Strength: 9,000 - 15,000 psi Tensile Modulus: 330,000 - 530,000 psi Maximum Bending Strength: 12,900 - 20,900 psi Bending Modulus: 417,000 - 617,000 psi Intrinsic Viscosity: 2.0-4:5 dL/g in ~hloxoform at 25°C
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1 A rotatable driver 60 for engagement in drive recess 30 is 2 shown in Figs. 3 and 4 and includes a longitudinally elongated, 3 cylindrical shaft 62 having a proximal end 64 joined to a handle 4 66, a distal end 68 defining a distal end wall 70 disposed perpendicular to the central longitudinal axis of shaft 62, and 1 three lobes 72 disposed radially on shaft 62 to extend 2 longitudinally from proximal end 64 to distal end 68. Lobes 72 3 each include spaced, planar side walls 74 extending radially 4 outwardly with respect to the central longitudinal axis of shaft 5 62 and an outer arcuate wall 76 joining side walls 74, such that 6 side walls 74 are closer together at shaft 62 and farther apart 7 at outer arcuate wall 76. Outer arcuate walls 76 are joined to 8 distal end wall 70 by inwardly curved walls 78, such that the 9 cross-sections of lobes 72 and shaft 62 are constant through a substantial portion of their length. A longitudinal guide bore 11 80 is formed concentrically in shaft 62 and handle 66 to extend 12 the entire length of shaft 62 and handle 66. As shown in Figs. 5 13 and 6, shaft 62 is sized to be matingly received in cavity 34 of 14 drive recess 30 and lobes 72 are sized to be matingly received in lobe openings 36 of drive recess 30.
16 In operation, bone screw10 can be employed in ligament 17 repair nd/or reconstructionurgery to attach a bone block a s on a 18 ligament to the wall of a tunnel. For example, for ligament bone 19 fixation in endoscopic intraarticular replacement of the anterior cruciate ligament of the knee,appropriate portals are made 21 leading to the knee joint insertion of an arthroscope far and :~a i e.~ ;~,r ~s~ ~'~. ~..e 1 other instruments, and bone tunnels are formed, respectively, in 2 the proximal tibia and distal femur. A ligament, either graft 3 or prosthetic, having bone blocks at its ends is passed through 4 the femoral tunnel, across the joint, and through the tibial tunnel to position a bone block in the femoral and tibial 6 tunnels. Sutures carried by the bone blocks permit the ligament 7 to be placed in tension. Bone screw 10 is inserted via guide 8 bore 50 over a guide wire positioned in the femoral bone tunnel 9 between the bone block positioned therein and the tunnel wall.
Driver 60 is placed over the guide wire via guide bore 80 and is 11 guided into mating engagement with drive recess 30 as shown in 12 Fig. 5. Driver 60 is xotated to drive bone screw 10 into 13 interference fit between the bone block and the wall of the 14 femoral bone tunnel. With the ligament held in tension, a second bone screw 10 is inserted to secure the remaining bone block with 16 respect to the wall of the tibial bone tunnel.
17 As shown in Fig. 6, when driver 60 is rotated, the leading 18 radial side walls 74 of lobes 72 apply radial forces equally 19 against corresponding rad9.al side walls 40 of lobe openings 36, and these rotational forces are concentric to the central 21 longitudinal axis of body 12. The forces applied by side walls 22 74 to side walls 40 are directed perpendicularly, and not 23 outwardly, against side walls 40. Therefore, forces are applied 24 by driver 60 only in the direction needed to drive screw 10, and extraageous forces that would otherwise produce distortion or 26 outward expansion of screw 10 are eliminated. Because lobe i~J ~ L~ n.,~ f~ ~. id 1 openings 36 taper inwardly from outer ends 44 to mouths 46, the 2 screw material separating lobe openings 36 is restricted, or 3 confined, against outward expansion when the leading side walls 4 74 of driver 60 are forced against corresponding side walls 40.
1 Having described a preferred embodiment of a new and 2 improved bioabsorbable interference bone fixation screw, it is 3 believed that other modifications, variations and changes will be 4 suggested to those skilled in the art in view of the teachings set forth herein. It is therefore to be understood that all such 6 variations, modifications and changes are believed to fall within 7 the scope of the present invention as defined by the appended 8 claims.
11 Moreover, it is an object of the invention to prevent 12 outward expansion, or "mushrooming", of a bioabsorbable bone 13 screw when it is driven into bone.
14 A further object of the invention is to provide a bioabsorbable bone screw capable of withstanding high drive 16 forces when driven into bone.
17 Another object of the invention is to provide a 18 bioabsorbable bone screw having a mufti-lobed drive recess 19 receiving a mufti-lobed driver that applies concentric forces to walls of the drive recess in a direction perpendicular to such 21 walls, 22 A still further object of the invention is to provide a 23 bioabsorable bone screw including a drive recess having radially 24 oriented force receiving walls for receiving forces from a driver applied perpendicularly to such walls.
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1 Some of the advantages of the bioabsorbable interference 2 bone fixation screw according to the present invention over the 3 prior art are that the bone screw is naturally degraded and 4 absorbed by the body upon completion of healing of the fixated bone and/or tissue, presents no exterior enlargements that might 6 protrude into bodily tissue, is self-tapping and is suitable for 7 use in closed, or endoscopic, surgery as well as in open surgery.
8 These and other objects, attributes and benefits are 9 achieved with the bioabsorbable interference bone fixation screw of the present invention as characterized by a body having a 11 proximal end, a conically tapered distal end and a helical screw Z2 thread disposed on the body from the proximal end to the distal 13 end and having a major diameter that defines the major diameter 1~ for the bone screw. A drive recess for engaging a rotatable driver is formed in the body to extend longitudinally from the 16 proximal end toward the distal end. The drive recess includes a 17 cylindrical cavity disposed concentrically in the body, and a 18 plurality of lobe openings positioned radially around the cavity 19 in communication therewith and extending longitudinally therealong. Each of the lobe openings is defined by a pair of 21 side walls in radial alignment with the central longitudinal axis 22 of the body, and an..arcuate outer wall joining the side walls, 23 such that the lobe openings are wider at the arcuate outer walls 24 and narrower at the cylindrical cavity. A central longitudinal guide bore is formed in the body to extend longitudinally from 26 the drive recess to the distal end for guiding the screw on a . ,,- , ,<,x. ;:
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l guide wire. A driver configured to be matingly received in the 2 drive recess includes a shaft and a plurality of lobes having 3 side walls extending radially outwardly from the shaft for 4 applying concentric forces to the side walls of the drive recess in a direction perpendicular to such side walls.
S Other objects and advantages of the present invention will 7 become apparent from the following description of the preferred 8 embodiment taken in conjunction with the accompanying drawings 9 wherein like parts in each of the several figures are identified by the same reference characters.
12 Fig. 1 is a side view of the bioabsorbable interference bone 13 fixation screw according to the present invention.
14 Fig. 2 is a proximal end view of the bioabsorbable interference bone fixation screw of Fig. 1.
L6 Fig. 3 is, a perspective view of a driver for rotating the 17 bioabsorbabl e interference bone fixation screw of Fig. 1.
18 Fig. 4 is a cross-sectional view of the driver taken along 19 line 6-6 ofFig. 3.
Fig. 5 is a broken, longitudinal sectional view of the 21 driver ted in'the bone screw of Fig. 1.
inser 22 Fig. 6 is a broken, sectional view snowing the bone screw of 23 Fig. 1 being driven by the driver.
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2 Referring to Figs. 1 and 2, the bone screw 10 according to 3 the present invention includes a longitudinally elongated 4 cylindrical body 12 having a proximal end 14, a distal end 16 and a helical screw thread 18 disposed externally on body 12 from 6 proximal end 14 to distal end 16. Thread 18 includes a proximal 7 thread section 20 extending longitudinally from the proximal end 8 . 14 in the direction of the distal end 16 and a conically tapered distal thread section 24 extending longitudinally from the proximal thread section 20 to the distal end 16. The threads of 11 proximal thread section 20 are of uniform pitch and like-handed;
12 that is, they extend in the same angular direction about the 13 screw. The major diameter (i.e., the diameter of the crests) of 14 the threads in proximal thread section 20 defines the major diameter for the screw, and a cylindrical surface 22 on body 12 16 defines the minor diameter for proximal thread section 20.
17 Distal thread section 24 carries a thread having a major diameter 18 that is less than the major diameter of the threads in proximal 19 thread section 20. The thread for distal thread section 24 tapers conically from the proximal thread section 20 to the 21 distal end 16 in a spiral configuration, and the pitch of this 22 thread is greater than the pitch of the threads fn the proximal 23 thread section 20.
24 A drive recess 30 for receiving a rotatable driver is formed in body 12 to extend longitudinally from proximal end 14 in the 26 direction of distal end 16 to an end wall 32 disposed t a L~ j2 iJ ~r.. :a 1 perpendicular to the central longitudinal axis of body 12. As 2 best shown in Fig. 2, drive recess 30 includes a cylindrical 3 cavity 34 formed concentrically in body 12 to extend 4 longitudinally from proximal end 14 to end wall 32 and three equally spaced lobe openings or chambers 36 radially disposed 6 around cavity 34 in communication therewith and extending 7 longitudinally therealong to end wall 32. Cavity 34 is defined 8 by three inner arcuate walls 38 positioned between lobe openings 9 36 and disposed a constant radial distance from the central longitudinal axis of body 12. Each lobe opening 36 is defined by 11 a pair of spaced, planar side walls 40 and an outer arcuate wall 1?. 42 joining opposing side walls 40. Outer arcuate walls 42 are 13 disposed a constant radial distance from the central longitudinal 14 axis of body 12, and this radial distance is greater than the radial distance far inner arcuate walls 38. Side walls 40 extend 16 radially outwardly from inner arcuate walls 38 and are positioned 17 in radial alignment with the central longitudinal axis of body 18 12, such that lobe openings 36 taper inwardly from an outer end 19 44 defined by outer arcuate walls 42 to a mouth or inner end 46 communicating with cavity 34. Outer arcuate walls 42 are joined 21 to end wall 32 by inwardly curved walls 48, such that the cross-22 section of drive recess 30 is constant through a substantial 23 portion of its length. A central, longitudinal guide bore or 24 cannulation 50 is disposed concentrically within body 12 in communication with drive recess 30 and extends longitudinally 26 from end wall 32 to distal end 16.
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1 Preferably, the minor diameter for the proximal thread 2 section 20 defined by the surface 22 is 55~ to 75~ the major 3 diameter for the screw; the thread 18 is configured in accordance 4 with ISO 5835/1; the length of the drive recess 30 from proximal end 14 to end wall 32 is approximately 48~ to 95~ the overall 6 length of body 12 measured from proximal end 14 to distal end 16;
7 the inner arcuate walls 38 of the cavity 34 define arcs of a 8 circle having a diameter that is approximately 47~ the minor 9 diameter of the proximal thread section 20; the outer arcuate walls 42 of the lobe openings 36 define arcs subtending 11 approximately 50° along a circle having a diameter that is 12 approximately 78~ the minor diameter of proximal thread section 13 20 and these arcs are shorter in length than the arcs defined by 14 inner arcuate walls 38.
The relative proportions of the bone screw produce numerous 16 structural and functional advantages. The relatively large minor 17 diameter for the thread 18 in the proximal thread section 20 18 increases the quantity of screw material surrounding the drive 19 recess 30 and, therefore, the strength of the bone screw in resisting shear and radial deformation when being rotated by a 21 driver received in the drive recess. The size of the minor 22 diameter for the proximal thread section 20 relative to the major 23 diameter for the bone screw increases the overall strength of the 24 body 12 yet provides thread 18 with sufficient depth to insure proper fixation in bone. The conical taper for the distal thread 26 section 24 and the spiral configuration and relatively greater i a .~ ~.i 1 pitch of the thread in the distal thread section assists 2 advancement of the bone screw and eliminates the need for a 3 tapping procedure. The length of the drive recess 30 relative to 4 the overall length of the body 12 and to the minor diameter for the proximal thread section 20 allows drive forces to be 6 distributed through body 12 and increases the magnitude of force 7 that the bone screw can withstand. Furthermore, the length of 8 the drive recess 30 is selected to limit the quantity of material 9 removed from the screw and maintain structural integrity around the cannulation 76. Additionally, drive recess 30 distributes 11 drive forces equally throughout its length due to the cross-12 section of the drive recess being constant through a substantial 13 portion of its length. The diameters of the circles defined by 14 the inner arcuate walls 38 and the outer arcuate walls 42 of the drive recess 30 further insure that a quantity of screw material 16 sufficient to withstand drive forces surrounds the drive recess 17 30, and the length of the arcs defined by the outer arcuate walls 18 42 provides relatively large quantities of screw material between 19 the lobe openings 36.
Bone screw ZO is fabricated entirely from a bioabsorbable or 21 biodegradable polymer or copolymer having an absorption or 22 degradation time selected in accordance with the anticipated 23 healing time for the fixated tissue. Table I set forth below 24 lists polymers (and copolymers and terpolymers thereof) suitable far bone screw 10, and these polymers are all biodegradable into 26 water-soluble, non-toxic materials that are safely eliminated by '~~ f ~.j p'1 n ,~ ~~ ' ?
:,d i.r t1 r~r Y>l 1 the body. Although the illustrative polymers are normally 2 linear, suitable cross linked resins can be prepared therefrom.
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Polymer Polycaprolactone Poly (L
-lactide) Poly (DL lactide) -Polyglycolide 95:5 Poly (DL lactide co-glycolide) - -90:10Poly (DL lactide co-glycolide) - -85:15Poly (DL lactide co-glycolide) - -75:25Poly (DL lactide co-glycolide) - -54:50Poly (DL lactide co-glycolide) - -90:14Poly (DL lactide co-caprolactone) -75:25Poly (DL lactide co-caprolactone) - -50:54Poly (DL lactide - co-caprolactone) -A preferred material for bone screw l4 is Poly (L-Lactide), and the preferred chemical specifications for raw poly-lactide acid employed for bone screw i4 are set forth below in Table II.
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Raw Polv-Lactic Acid Residual Tin (Stannous actoate): Less than 200ppm Residual Metals (FE, Cr, Ni, Pb): Less than 50ppm each Residual Lactide Dimer: Less than 1~
Intrinsic Viscosity: 6.5-8.5 dL/g in chloroform at 25°C
Bone screw 10 is preferably formed by an injection molding process, and the preferred characteristics of the bone screw thusly formed are set forth below in Table III.
TABLE III
Bone Screw Ultimate Tensile Strength: 9,000 - 15,000 psi Tensile Modulus: 330,000 - 530,000 psi Maximum Bending Strength: 12,900 - 20,900 psi Bending Modulus: 417,000 - 617,000 psi Intrinsic Viscosity: 2.0-4:5 dL/g in ~hloxoform at 25°C
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1 A rotatable driver 60 for engagement in drive recess 30 is 2 shown in Figs. 3 and 4 and includes a longitudinally elongated, 3 cylindrical shaft 62 having a proximal end 64 joined to a handle 4 66, a distal end 68 defining a distal end wall 70 disposed perpendicular to the central longitudinal axis of shaft 62, and 1 three lobes 72 disposed radially on shaft 62 to extend 2 longitudinally from proximal end 64 to distal end 68. Lobes 72 3 each include spaced, planar side walls 74 extending radially 4 outwardly with respect to the central longitudinal axis of shaft 5 62 and an outer arcuate wall 76 joining side walls 74, such that 6 side walls 74 are closer together at shaft 62 and farther apart 7 at outer arcuate wall 76. Outer arcuate walls 76 are joined to 8 distal end wall 70 by inwardly curved walls 78, such that the 9 cross-sections of lobes 72 and shaft 62 are constant through a substantial portion of their length. A longitudinal guide bore 11 80 is formed concentrically in shaft 62 and handle 66 to extend 12 the entire length of shaft 62 and handle 66. As shown in Figs. 5 13 and 6, shaft 62 is sized to be matingly received in cavity 34 of 14 drive recess 30 and lobes 72 are sized to be matingly received in lobe openings 36 of drive recess 30.
16 In operation, bone screw10 can be employed in ligament 17 repair nd/or reconstructionurgery to attach a bone block a s on a 18 ligament to the wall of a tunnel. For example, for ligament bone 19 fixation in endoscopic intraarticular replacement of the anterior cruciate ligament of the knee,appropriate portals are made 21 leading to the knee joint insertion of an arthroscope far and :~a i e.~ ;~,r ~s~ ~'~. ~..e 1 other instruments, and bone tunnels are formed, respectively, in 2 the proximal tibia and distal femur. A ligament, either graft 3 or prosthetic, having bone blocks at its ends is passed through 4 the femoral tunnel, across the joint, and through the tibial tunnel to position a bone block in the femoral and tibial 6 tunnels. Sutures carried by the bone blocks permit the ligament 7 to be placed in tension. Bone screw 10 is inserted via guide 8 bore 50 over a guide wire positioned in the femoral bone tunnel 9 between the bone block positioned therein and the tunnel wall.
Driver 60 is placed over the guide wire via guide bore 80 and is 11 guided into mating engagement with drive recess 30 as shown in 12 Fig. 5. Driver 60 is xotated to drive bone screw 10 into 13 interference fit between the bone block and the wall of the 14 femoral bone tunnel. With the ligament held in tension, a second bone screw 10 is inserted to secure the remaining bone block with 16 respect to the wall of the tibial bone tunnel.
17 As shown in Fig. 6, when driver 60 is rotated, the leading 18 radial side walls 74 of lobes 72 apply radial forces equally 19 against corresponding rad9.al side walls 40 of lobe openings 36, and these rotational forces are concentric to the central 21 longitudinal axis of body 12. The forces applied by side walls 22 74 to side walls 40 are directed perpendicularly, and not 23 outwardly, against side walls 40. Therefore, forces are applied 24 by driver 60 only in the direction needed to drive screw 10, and extraageous forces that would otherwise produce distortion or 26 outward expansion of screw 10 are eliminated. Because lobe i~J ~ L~ n.,~ f~ ~. id 1 openings 36 taper inwardly from outer ends 44 to mouths 46, the 2 screw material separating lobe openings 36 is restricted, or 3 confined, against outward expansion when the leading side walls 4 74 of driver 60 are forced against corresponding side walls 40.
1 Having described a preferred embodiment of a new and 2 improved bioabsorbable interference bone fixation screw, it is 3 believed that other modifications, variations and changes will be 4 suggested to those skilled in the art in view of the teachings set forth herein. It is therefore to be understood that all such 6 variations, modifications and changes are believed to fall within 7 the scope of the present invention as defined by the appended 8 claims.
Claims (32)
1. An interference bone fixation screw to be rotated by a driver comprising a body having a proximal end, a distal end, a length between said proximal and distal ends and a longitudinal axis;
thread means for engaging bone disposed on said body from said proximal end to said distal end; and drive recess means disposed in said proximal end of said body including a plurality of equally spaced lobe openings having force receiving surfaces in radial alignment with said longitudinal axis for receiving rotational forces from the driver said force receiving surfaces extending longitudinally within said body along a substantial portion of said length, said interference bone fixation screw being made of bioabsorbable material in its entirety.
thread means for engaging bone disposed on said body from said proximal end to said distal end; and drive recess means disposed in said proximal end of said body including a plurality of equally spaced lobe openings having force receiving surfaces in radial alignment with said longitudinal axis for receiving rotational forces from the driver said force receiving surfaces extending longitudinally within said body along a substantial portion of said length, said interference bone fixation screw being made of bioabsorbable material in its entirety.
2. An interference bone fixation screw as recited in claim 1 wherein said drive recess means further includes a cylindrical cavity disposed concentrically in said body and said force receiving surfaces are positioned radially around said cavity.
3. An interference bone fixation screw as recited in claim 2 further including a longitudinal guide bore disposed concentrically in said body to extend longitudinally from said cavity to said distal end.
4. An interference bone fixation screw as recited in claim 3 wherein said drive recess means includes an end wall disposed in said body perpendicular to said longitudinal axis and said drive recess means extends longitudinally in said body from said proximal end to said end wall.
5. An interference bone fixation screw as recited in claim 4 wherein said thread means includes a helical screw thread.
6. An interference bone fixation screw as recited in claim 5 wherein said helical screw thread defines a major diameter and said body defines a minor diameter along said helical screw thread.
7. An interference bone fixation screw as recited in claim 6 wherein said minor diameter is approximately 55% to 75%
said major diameter.
said major diameter.
8. An interference bone fixation screw as recited in claim 7 wherein said helical screw thread is of uniform pitch.
9. An interference bone fixation screw as recited in claim 8 wherein said screw thread further includes a spiral screw thread extending longitudinally from said helical screw thread to said distal end.
10. An interference bone fixation screw as recited in claim 9 wherein said spiral screw thread has a pitch and said spiral screw thread pitch is greater than said helical screw thread pitch.
11. An interference bone fixation screw as recited in claim 10 wherein said interference bone fixation screw is made entirely of Poly (L-Lactide).
12. An interference bone fixation screw as recited in claim 1 wherein said force receiving surfaces extend within said body from 48% to 95% of said length.
13. An interference bone fixation screw to be rotated by a driver comprising a cylindrical body having a proximal end, a distal end, a length between said proximal and distal ends and a longitudinal axis;
a screw thread disposed on said body to extend longitudinally therealong; and drive recess means disposed in said proximal end of said body including a plurality of equally spaced lobe openings having outer ends disposed a first radial distance from said longitudinal axis and inner ends disposed a second radial distance from said longitudinal axis less than said first radial distance, said lobe openings tapering inwardly from said outer ends to said inner ends to define planar force receiving walls between said outer ends and said inner ends for receiving rotational forces from the driver, said interference bone fixation screw being made entirely of bioabsorbable material.
a screw thread disposed on said body to extend longitudinally therealong; and drive recess means disposed in said proximal end of said body including a plurality of equally spaced lobe openings having outer ends disposed a first radial distance from said longitudinal axis and inner ends disposed a second radial distance from said longitudinal axis less than said first radial distance, said lobe openings tapering inwardly from said outer ends to said inner ends to define planar force receiving walls between said outer ends and said inner ends for receiving rotational forces from the driver, said interference bone fixation screw being made entirely of bioabsorbable material.
14. An interference bone fixation screw as recited in claim 13 wherein said lobe openings extend longitudinally within said body along a substantial portion of said length.
15. An interference bone fixation screw as recited in claim 13 or 14 wherein said drive recess means includes a cylindrical cavity disposed concentrically in said proximal end of said body and said inner ends of said lobe openings communicate with said cylindrical cavity.
16. An interference bone fixation screw as recited in claim 15 wherein said cylindrical cavity is defined by a plurality of inner concave arcuate walls positioned, respectively, between said inner ends of said lobe openings.
17. An interference bone fixation screw as recited in claim 16 wherein said outer ends of said lobe openings are defined by outer concave arcuate walls joining said force receiving walls.
18. An interference bone fixation screw as recited in claim 17 wherein said outer arcuate walls define arcs of a circle, said inner arcuate walls define arcs of a circle and said arcs defined by said inner arcuate walls are longer than said arcs defined by said outer arcuate walls.
19. An interference bone fixation screw as recited in claim 18 wherein said screw thread defines a major diameter and said body defines a minor diameter extending longitudinally from said proximal end toward said distal end.
20. An interference bone fixation screw as recited in claim 19 wherein the diameter of said circle defined by said outer arcuate walls is approximately 78% said minor diameter.
21. An interference bone fixation screw as recited in claim 20 wherein the diameter of said circle defined by said inner arcuate walls is 20% to 70% of said minor diameter.
22. An interference bone fixation screw as recited in claim 21 wherein said arcs defined by said outer arcuate walls subtend approximately 50°.
23. An interference bone fixation screw as recited in claim 22 wherein there are three of said lobe openings.
24. An interference bone fixation screw as recited in claim 13 wherein said force receiving surfaces extend within said body from 48% to 95% of said length.
25. An interference bone fixation screw to be rotated by a driver comprising a cylindrical body having a proximal end, a distal end, a length between said proximal and distal ends and a longitudinal axis;
a screw thread disposed on said body to extend longitudinally from said proximal end to said distal end;
and a drive recess in said proximal end of said body for matingly receiving the driver including a plurality of equally spaced lobe openings extending longitudinally within said body along a substantial portion of said length, each of said lobe openings being defined by a pair of spaced side walls extending radially outwardly with respect to said longitudinal axis for receiving rotational forces from the driver applied perpendicular to said side walls, said interference bone fixation screw being made of bioabsorbable material in its entirety.
a screw thread disposed on said body to extend longitudinally from said proximal end to said distal end;
and a drive recess in said proximal end of said body for matingly receiving the driver including a plurality of equally spaced lobe openings extending longitudinally within said body along a substantial portion of said length, each of said lobe openings being defined by a pair of spaced side walls extending radially outwardly with respect to said longitudinal axis for receiving rotational forces from the driver applied perpendicular to said side walls, said interference bone fixation screw being made of bioabsorbable material in its entirety.
26. An interference bone fixation screw as recited in claim 25 wherein the cross-section of said drive recess is constant through a substantial portion of said longitudinal length of said drive recess.
27. An interference bone fixation screw as recited in claim 26 wherein the longitudinal length of said drive recess is approximately 48% to 95% the length of said body.
28. In combination, an interference bone fixation screw comprising a cylindrical body having a proximal end, a distal end and a longitudinal axis;
thread means disposed on said body for engaging bone;
and drive recess means in said proximal end of said body including a cylindrical cavity disposed concentrically in said body and extending along a length thereof and a plurality of lobe openings disposed around said cavity in communication therewith along the length thereof, each of said lobe openings being defined by force receiving walls extending radially outwardly from said cavity, said force receiving surfaces extending longitudinally within said body along a substantial portion of said length;
said interference bone fixation screw being fabricated entirely of bioabsorbable material; and a driver for rotating said screw and having a configuration mating with said drive recess means, said driver including cylindrical shaft means for being received in said cavity and a plurality of lobe means having force transmitting walls extending radially outwardly from said shaft means for applying forces to said force receiving walls when said driver is rotated.
thread means disposed on said body for engaging bone;
and drive recess means in said proximal end of said body including a cylindrical cavity disposed concentrically in said body and extending along a length thereof and a plurality of lobe openings disposed around said cavity in communication therewith along the length thereof, each of said lobe openings being defined by force receiving walls extending radially outwardly from said cavity, said force receiving surfaces extending longitudinally within said body along a substantial portion of said length;
said interference bone fixation screw being fabricated entirely of bioabsorbable material; and a driver for rotating said screw and having a configuration mating with said drive recess means, said driver including cylindrical shaft means for being received in said cavity and a plurality of lobe means having force transmitting walls extending radially outwardly from said shaft means for applying forces to said force receiving walls when said driver is rotated.
29. A combination as recited in claim 28 wherein said drive recess means includes an end wall disposed in said body perpendicular to said longitudinal axis, said cavity extends longitudinally from said proximal end to said end wall and said shaft means includes an end surface on said driver for engaging said end wall.
30. A combination as recited in claim 29 and further including a guide bore in said body extending longitudinally from said drive recess end wall to said distal end and a guide passage in said shaft means of said driver aligned with said guide bore when said shaft means is received in said cavity.
31. A driver for rotating a bioabsorbable bone screw having a body with a proximal end and a drive recess extending longitudinally within a substantial length of the body, said driver comprising a cylindrical shaft an a plurality of lobes extending from said shaft along a substantial length thereof, each of said lobes carrying radially oriented, spaced, planar side walls which diverge outwardly from the axis of said shaft and are joined by an arcuate outer wall forming part of a cylinder concentric with said shaft for engaging walls of the drive recess of the screw whereby said driver engages the screw along a substantial length of the screw body for rotating the screw.
32. A driver for rotating a bioabsorbable bone screw as recited in claim 31 wherein said shaft terminates at a distal end wall disposed perpendicular to the longitudinal axis of the shaft and said outer arcuate walls of said lobes terminate at inwardly curved walls joining said distal end wall.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US66467991A | 1991-03-05 | 1991-03-05 | |
| US07/664,679 | 1991-03-05 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2062012A1 CA2062012A1 (en) | 1992-09-06 |
| CA2062012C true CA2062012C (en) | 2003-04-29 |
Family
ID=24666988
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002062012A Expired - Lifetime CA2062012C (en) | 1991-03-05 | 1992-02-27 | Bioabsorbable interference bone fixation screw |
Country Status (8)
| Country | Link |
|---|---|
| US (1) | US5470334A (en) |
| EP (1) | EP0502698B1 (en) |
| JP (1) | JPH05103795A (en) |
| AT (1) | ATE160082T1 (en) |
| AU (1) | AU654840B2 (en) |
| CA (1) | CA2062012C (en) |
| DE (1) | DE69223079T2 (en) |
| ES (1) | ES2109309T3 (en) |
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| US8574273B2 (en) | 2009-09-09 | 2013-11-05 | Innovision, Inc. | Bone screws and methods of use thereof |
| US9993276B2 (en) | 2013-03-15 | 2018-06-12 | Innovision, Inc. | Bone screws and methods of use thereof |
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| AU689846B2 (en) * | 1994-03-29 | 1998-04-09 | Zimmer Gmbh | Screw made of biodegradable material for bone surgery purposes, and screwdriver suitable therefor |
| US5885299A (en) | 1994-09-15 | 1999-03-23 | Surgical Dynamics, Inc. | Apparatus and method for implant insertion |
| US5611814A (en) * | 1994-11-16 | 1997-03-18 | Lorenc; Z. Paul | Resorbable surgical appliances and endoscopic soft tissue suspension procedure |
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- 1992-02-27 CA CA002062012A patent/CA2062012C/en not_active Expired - Lifetime
- 1992-02-28 AU AU11284/92A patent/AU654840B2/en not_active Ceased
- 1992-03-03 DE DE69223079T patent/DE69223079T2/en not_active Expired - Lifetime
- 1992-03-03 ES ES92301816T patent/ES2109309T3/en not_active Expired - Lifetime
- 1992-03-03 EP EP92301816A patent/EP0502698B1/en not_active Expired - Lifetime
- 1992-03-03 AT AT92301816T patent/ATE160082T1/en not_active IP Right Cessation
- 1992-03-05 JP JP4048352A patent/JPH05103795A/en active Pending
- 1992-06-22 US US07/902,352 patent/US5470334A/en not_active Expired - Lifetime
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8574273B2 (en) | 2009-09-09 | 2013-11-05 | Innovision, Inc. | Bone screws and methods of use thereof |
| US9993276B2 (en) | 2013-03-15 | 2018-06-12 | Innovision, Inc. | Bone screws and methods of use thereof |
| US10751102B2 (en) | 2013-03-15 | 2020-08-25 | Innovision, Inc. | Bone screws and methods of use thereof |
Also Published As
| Publication number | Publication date |
|---|---|
| AU1128492A (en) | 1992-09-10 |
| AU654840B2 (en) | 1994-11-24 |
| JPH05103795A (en) | 1993-04-27 |
| DE69223079D1 (en) | 1997-12-18 |
| DE69223079T2 (en) | 1998-03-05 |
| CA2062012A1 (en) | 1992-09-06 |
| EP0502698A1 (en) | 1992-09-09 |
| US5470334A (en) | 1995-11-28 |
| EP0502698B1 (en) | 1997-11-12 |
| ATE160082T1 (en) | 1997-11-15 |
| ES2109309T3 (en) | 1998-01-16 |
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| Date | Code | Title | Description |
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| EEER | Examination request | ||
| MKLA | Lapsed | ||
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Effective date: 20121202 |