CA2191372A1 - Graft bone fixation tool - Google Patents
Graft bone fixation toolInfo
- Publication number
- CA2191372A1 CA2191372A1 CA002191372A CA2191372A CA2191372A1 CA 2191372 A1 CA2191372 A1 CA 2191372A1 CA 002191372 A CA002191372 A CA 002191372A CA 2191372 A CA2191372 A CA 2191372A CA 2191372 A1 CA2191372 A1 CA 2191372A1
- Authority
- CA
- Canada
- Prior art keywords
- screw member
- transmission shaft
- section
- handle grip
- fixation tool
- 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
- 210000000988 bone and bone Anatomy 0.000 title claims abstract description 65
- 230000005540 biological transmission Effects 0.000 claims abstract description 25
- 230000000295 complement effect Effects 0.000 claims abstract description 4
- 210000002435 tendon Anatomy 0.000 abstract description 20
- 238000003780 insertion Methods 0.000 abstract description 11
- 230000037431 insertion Effects 0.000 abstract description 11
- 238000012546 transfer Methods 0.000 abstract description 3
- 150000002500 ions Chemical class 0.000 description 12
- 210000002303 tibia Anatomy 0.000 description 10
- 210000000689 upper leg Anatomy 0.000 description 8
- 210000001519 tissue Anatomy 0.000 description 7
- 239000000463 material Substances 0.000 description 5
- 238000001356 surgical procedure Methods 0.000 description 5
- 210000001699 lower leg Anatomy 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- NLZUEZXRPGMBCV-UHFFFAOYSA-N Butylhydroxytoluene Chemical compound CC1=CC(C(C)(C)C)=C(O)C(C(C)(C)C)=C1 NLZUEZXRPGMBCV-UHFFFAOYSA-N 0.000 description 2
- 230000000399 orthopedic effect Effects 0.000 description 2
- 210000004417 patella Anatomy 0.000 description 2
- 206010043248 Tendon rupture Diseases 0.000 description 1
- 239000000956 alloy Substances 0.000 description 1
- 229910045601 alloy Inorganic materials 0.000 description 1
- 230000004075 alteration Effects 0.000 description 1
- 230000001627 detrimental effect Effects 0.000 description 1
- 210000005028 enteric neuroimmune system Anatomy 0.000 description 1
- 230000002349 favourable effect Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- GWUSZQUVEVMBPI-UHFFFAOYSA-N nimetazepam Chemical compound N=1CC(=O)N(C)C2=CC=C([N+]([O-])=O)C=C2C=1C1=CC=CC=C1 GWUSZQUVEVMBPI-UHFFFAOYSA-N 0.000 description 1
- 230000002035 prolonged effect Effects 0.000 description 1
- 230000001012 protector Effects 0.000 description 1
- 238000007634 remodeling Methods 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0805—Implements for inserting tendons or ligaments
-
- 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
-
- 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
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
- A61F2002/0817—Structure of the anchor
- A61F2002/0823—Modular anchors comprising a plurality of separate parts
- A61F2002/0829—Modular anchors comprising a plurality of separate parts without deformation of anchor parts, e.g. fixation screws on bone surface, extending barbs, cams, butterflies, spring-loaded pins
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
- A61F2002/0817—Structure of the anchor
- A61F2002/0841—Longitudinal channel for insertion tool running through the whole tendon anchor, e.g. for accommodating bone drill, guidewire
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
- A61F2002/0847—Mode of fixation of anchor to tendon or ligament
- A61F2002/0858—Fixation of tendon or ligament between anchor and bone, e.g. interference screws, wedges
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/08—Muscles; Tendons; Ligaments
- A61F2/0811—Fixation devices for tendons or ligaments
- A61F2002/0876—Position of anchor in respect to the bone
- A61F2002/0882—Anchor in or on top of a bone tunnel, i.e. a hole running through the entire bone
-
- 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
- Y10S606/916—Tool for installing or removing orthopedic fastener
Abstract
Disclosed is an improved screw member adapted to be threaded into a gap between two bone parts in BTB tendon transfer surgical operations, and a fixation tool for engaging the screw member. The screw member typically consists of a hollow cylindrical member comprising an axial bore having a hexagonal cross section, and an outer circumferential surface provided with a strictly straight thread. The fixation tool comprises a transmission shaft having an intermediate section having a hexagonal cross section complementary to that of the axial bore of the screw member. Because the transmission shaft is entirely passed through the axial bore of the screw member, the torque for turning the screw member can be positively transmitted to the screw member, and the transmission shaft provides a positive guide action for the insertion of the screw member. The transmission shaft may be either axially slidably but rotatively integrally engaged to a handle grip or integrally attached to a handle grip.
Description
-1- 2t91372 GRA~T BONE FIXATION TOOL
TECHNICAL FIELD
The present invention relates to a graft bone fixation tool for securing a graft bone piece in a bore forrned in a bone, and in particular to a graft bone fixation tool for use in tendon transfer surgical operations in the field of orthopedic surgery.
BACKGROU~ OF IHE rNVE~TIO~
In the field of orthopedic surgery, the method known as the BTB (bone-tendon-bone) method has been used for reconstructing a severed tendon as illustrated in Figures la to 1c. According to the BTB method, a graft consistingof tw-o pieces of bone 2 joined by a tendon 1 is harvested typically from a patella and an adjacent tibia, and sutures 3 are passed through openings formed in the bone pieces 2. Meanwhile, bore 6 and 7 are drilled in the femur 4 and the tibia 5 at a joint whose tendon is severed or otherwise damaged, and is therefore desired to be reconstructed.
By using the sutures 3, the graft tendon 1 along with the graft bone pieces 2 are passed through the bores 6 and 7 formed in the femur 4 and the tibia 5 so that the graft tendon 1 extends between the femur 4 and the tibia 5. A screw member 9 is then threaded into a gap defined between the inner wall of the bore 7 of the tibia 5 and the corresponding bone piece 2 by using a fixation tool 8 so that the bone piece 2 may be securely pressed against the inner wall of the bore 7 ofthe tibia 5. Similarly, another screw member 9 is threaded into a gap defined - - between the inner wall of the bore 6 of the femur 4 and the corresponding bone - - - 25 piece 2 by using the same fixation tool 8 so that the bone piece 2 may be - - - similarly secured against the inner wall of the bore 6 of the femur 4.
As a result, the graft bone pieces 2 are firmIy secured to the femur 4 arld the tibia 5, respectively, and the damaged tendon between the femur 4 and the tibia S is allowed to rebuild itself while the graft tendon 1 e~tending between the two bone pieces 3 keeps the femur 4 and the tibia 5 together.
In such a tendon reconstruction surgery, screw members 10, 11 and 12 illustrated in Figures 2 to 4 in combination with a iïgation tool 13 such as the one illustrated in Figure 5 have col,velltionally been used.
The screw member 10 illustrated in Figure 2 consists of a screw shank 15 3~ which is provided with an engagement recess 14, adapted to be engaged by a bit formed at the tip of the fixation tool 13, in a base end surface thereof, and is.- . ~ .
. -2- 2l9l31~
generally provided with a tapered profile defined by a base section having a straight (parallel) thread and a free end section having a taper thread, and an inner guide bore 20 passed axially entirely through the screw member 10.
The screw member 11 illustrated in Figure 3 comprises a screw head 17 5 having an engagement recess 18 adapted to be engaged by a bit formed at the tip of the fixation tool 13, a screw shank 19 having a generally tapered.profile defined by a base end section provided with a straight thread, and a free end section provided with a taper thread, and an inner guide bore 20 passed axially entirely through the screw member 11.
lo The screw member 12 illustrated in Figure 4 consists of a screw shanX 21 .. having a straight screw thread around its outer cil~;ulllfelence, and is provided with a conical guide projection 22 at a tip thereof. The screw member 12 is further provided, in an axial center of the base end thereof, with a larger threaded bore 23 for engaging a bit for fastening the screw member, and a smaller coaxial15 bore 24 having a reversed thread for eng~ging a bit for unfaster~ ng the screw member 12.
Referring to Figure 5, the fixation tool 13 comprises a rotary drive unit 25 adapted to be gIipped by hand, and a tr~n.cmicsion shaft 26 w-hich is integrally attached to the rotary drive unit 25, and is formed with a bit at a free end thereof 20 for engagement with associated engagement means, typically consisting of a hexagonal recess, provided in the screw member 10 (11 or 12). When a screw member having an axial bore such as the screw members 10 and 11 is used, an axial bore 27 is also forrned in the rotary drive unit 25 and the tran.smic.cion shaft . . ~ - - - 26 so that the guide wire 28 for facilitating the insertion of the screw member - . . - -~ - 25 may be passed through this axial bore 27 and the bore of the screw member 10.
.. - Depending on the kind of the screw member, a protector 29 may be fitted on the - ~ - tr~n.cmi.c.cion shaft 26 so as not to damage the surrounding tissues and the graft tendon.
Such conventional arrangements, which employ a screw member such as 30 those described above in combination with the fixation tool as described above, are k~owrl to have a number of problems that ueed to be resolved.
For instance, because the engagement means (engagement recesses 14 and 18) for eng~ging the bit of the fixation tool 13 is reIatively shallow as is the case with the screw members 10 and 11 illustrated in Figures 2 and 3, the 35 necessary torque to firmly thread the screw member into the gap between two adjacent bone parts may not be effectively tr~ncmitted to the screw member particularly when the length of the straight thread section is increased in length to the end of increasing the securing force, and a relatively large effort is therefore required to turn the scre-v member. It is possible that the bit may be dislodgedfrom the enGagement recess of the screw member and thereby damage the 5 adjacent bone parts.
Also, due to possible mic~ nment of the aYial center of the screw member from the intended path of insertion, the so-called screw diversion may occur so that the graft bone pieces 2 may not be secured accùrately and firmly enough for the tendon to recover its original condition in a satisfactory manner0 following the surgery.
When the engagement means for engaging the bit of the fi~ation tool 13 consists of larger and smaller threaded bores 23 and 24 which are coaxial with each other as is the case with the screw member 12 of Figure ~, hvo separate tools will be needed for inserting and removing the screw member, respectively.
5 In particular, when removing the screw member by using the smaller threaded bore 24, the screw thread may not be able to withstand the large torque that maybe required to remove the screw member 12.
When a tapered threaded section or a guide projection is provided in a free end of the screw shank as is the case with the screw members 10 and 11 of 20 Figures 2 and 3, if the screw member is forced too deeply into the gap between two bone parts or the remodeling of the bore in the bone has occurred, the pointed tip of the screw member may damage the surrounding tissues and the graft tendon. Even if the screw member is properly threaded into the gap - ~ - between two bone parts, because the tapered section is not effective in securing 26 the screw member, and the effective length of the screw thread is limited to the - straight thread section of the saew member, the securing force for the bone parts - - - may not be sufficient, and the rehabilitation of the patient may be undesirably prolonged.
More specifically, the length of a graft bone piece 2 harvested from a 30 patella of a person is no more than 20 to 25 mm, and the effective length of the screw member is desired to colrespond to this length so as to m~imi7e the securing force. However, because of the provision of a tapered section and a guide projection, the effective length of the screw member tends to be insufficient to achieve a sufficient force for engagement. If the effective length of the screw 3~ member is increased, the overall length of the screw member becomes so large that the tapered section or the guide projection projects toward the graft tendon, .
~4~ 2191372 thereby increasing the possibility of d~m~ging the graft tendon.
Thus, the problems of the prior art may be summ~n7ed as follows.
Because the effective threaded section of a screw member is limited to its straight or parallel thread section, it may be desired to elimin~te any tapered section to m~-imi7e the securing force for a given length of the screw member. Howe~er, this causes a substantial difficulty in inserting the screw member into a gap in the bone due to lack of a guiding action of its free end. This may be overcome to a certain extent by increasing the thickness of the guide wire. The improved guiding action of the guide wire may allow the use of a screw member without any tapered section.
A thick guide wire however still have two problems. First of all, because the bore for passing the guide wire has to be provided in the bit of thefixation tool also, and provision of such a large central bore in the bit may reduce the mechanical strength of the bit to an unacceptable level. It may collapse when it is engaged with a screw head, and a substantial torque is applied to the bit.
Secondly, the diameter of the guide wire is therefore necessarily less than the diameter of the bit, and a somewhat blunt annular shoulder is inevitably definedbetween the free end of the screw member and the guide wire. ~he blunt annular shoulder is obviously highly detrimental to the smooth insertion of the screw member.
BRIEF SUM~ARY OF THE I~ENIION
In view of such problems of the prior art, a primary object of the present invention is to provide a graft bone fixation tool which allows a graft bone piece - - to be securely lodged in a bore formed in a bone part.A second object of the present invention is to provide a graft bone - - fixation tool which can be easily used without requiring any undue effort for - - ~ inserting a screw member into a gap between two born parts.
- A third object of the present invention is to provide a screw member for insertion between two bone parts which provides a sufflcient securing force.
A fourth object of the present invention is to provide a screw member for insertion between two bone parts which would not damage the graft tendon and the surrounding tissues.
According to the present invention, such objects can be accomplished by providing a graft bone fixation tool, comprising: a tr~n.cmiccion shaft including a typically tapered forward tip and an intermediate section provided with engagement means for torque tr~ncmis~ion, the tr~ncmiccion shaft being adapted -5~ 2191372 to be fitted into and through an axial bore of a screw member provided with associated engagement means for cooperation with the engagement means of the tr~n.~mi.~.cion shaft, the screw member being provided with a screw thread around an outer circumference thereof; and a rotary drive unit provided at a base end of - 5 the tr~n.cmi~.sion shaft for manually rotating the tr~n.~mis.sion shaft so as to apply a torque to the screw member fitted on the intermediate section of the tr~n.cmi~ion shaft.
Thus, the screw member may be provided with a strictly straight thread without any section of taper thread because the forward end of the tran.~mi.~.~ion 10 shaft provides the necessary guide action, the entire length of the screw member can be threaded with the graft bone piece, and the securing force of the screw member for a given length thereof can be m~imi7ed. Also, because the forward tip of the screw member would not project toward the graft tendon ~-ith the result that, as opposed to the conventional screw members provided with a 5 section of taper thread or a guide projection at its tip, the tip of the screw member would not damage the graft tendon or the surrounding tissues while the force effective in securing the graft bone piece is m~imi7ed. Because the screw member is tumed by the tr~n.cmic~ion shaft with the inner circumference of the scre~- member fully engaged with the tr~n.smis.cion shaft over the entire length of 20 the screw member, the drive torque is effectively transmitted to the screw member, and the screw member can be firmly threaded into the gap. Also, the -dislodgment of the bit from the tr~n.~mi~.~ion shaft or the deformation of the engagement means can be avoided, and the tr~n~mi.s.cion shaft provides a - favorable guiding action.
- - ............. .: . - .- - 25 The tr~n.~mi.c.~ion shaft may be provided with an axial bore for passing a . - guide wire thele~hlough. In that case, because no taper may- be provided in the - : - --- :-- :.. .- -- tip of the screw member, a guide shaft of a relatively large diameter can be e~tended from the tip of the screw member with the result that diverging of the movement of the screw member from the int~nded path of insertion can be 30 avoided as opposed to the conventional guide wire which is known to be too flexible ~or ef~ecti~e guide action.
The screw member may consist of a hollow cylindrical member having a strictly straight thread around its cLL~;u~ ellce. And, its axial bore may be either straight bore having a uniform diameter or have a stepped shape defining 35 an annular shoulder facing the rotary drive ur~it.
According to a ple~elled embodiment of the present in~ention, the rotary -6- 2l91372 drive unit comprises a handle grip, a rotary tube integrally attached to the handle grip, and an axial bore passed through the handle grip and the rotary tube for receiving the intermediate section of the tr~n.smi.c.sion shaft in an axially slidable but rotatively integral manner, a free end of the rotary tube being adapted to abut 5 an opposing axial end of the screw member.
According to a second preferred embodiment of the present invention, the rotary drive unit comprises a handle grip, and a base end of the tr~nsmi~.sion shaf-, is integrally attached to the handle grip, the fixation tool further comprising - an adjustment tube that can be fitted on the trancmi.s.sion shaft in such a manner that a free end of the rotary tube-abuts an opposing axial end of the screw member when the screw member is fitted on the intermediate section of the tr~nsmis.sion shaft in an axially slidable but rotatively integral manner.
According to a third preferred embodiment of the present invention, the rotary drive unit comprises a handle grip, and a base end of the tr~n.smic.sion shaft is integrally attached to the handle grip, the tr~n.smi~cion shaft comprising a base end section, extending between the intermediate section and the handle grip, which has a larger outer diameter than the intermediate section so as to define an annular shoulder facing away from the handle grip.
BRIEF DESCRIPTION OF THE DRAWINGS
Now the present invention is described in the following with reference to the appended drawings, in which:
Figures la to 1c are illustrative views showing the tendon transfer surgery using the collve"Lional graft bone fixation tool;
.. . Figure 2 is a lonGiturlin~l sectional view of a collvellLional screw member 25 used for securing a graft bone piece to a bone- part;
- - - - -: - Figure 3 is a lon2itudinal sectional view of another co"ve,~Lional screw ---- - member;
~ Figure 4 is a lon~itu-1in~l sectional view of yet another collv~l"ional screw member;
Figure 5 is an overall front view of a collv~"~ional graft bone fixation tool;
Figures 6a to 6c are illustrative views showing an embodiment of the screw member and an associated tr~nsmi.c.cion shaft used in the graft bone fixation tool of the present invention;
Figure 7 is an illustrative view showing a first embodiment of the graft bone fi~ation tool according to the present invention, along with the manner in '-which this tool is used for inserting a screw mernber into a gap behveen a graftbone piece and an adjacent wall of a bore formed in a bone part;
Figure 8 is a perspective view showing the handle grip of the graft bone piece fixation tool illustrated in Figure 7;
Figure 9 is a partly broken away perspective view of a second embodirnent of the graft bone fixation tool according to the present invention;
Figure 10 is a partly perspective view of a third embodiment of the graft bone fixation tool according to the present invention;
- Figures 11a, 11b and 11c are views similar to Figures 6a, 6b and 6c, 0 respectively, showing an alternate embodiment of the screw member suitable for use with the third embodiment illustrated in Ficure 10, along with the associated tr~n~mi.~cion shaft of the graft bone fixation tool illustrated in Figure 10; and Figure 12 is a sectional view of yet another embodiment of the screw member.
16 DETAILED DESCRIPTION OF THE PREFERRED E~30DL~ENIS
Figures 6a and 6b illustrate an embodiment of the screw member 30 according to the present invention which essentially consists of hollow cylindrical member having a straight (parallel) screw thread 39 on outer ci~;u~felelltial surface thereof, and a bore 40 having a hexagonal cross sectionand passed a~ially entirely through the screw member 30. The m~t~n~l of the screw thread typically consists of an alloy having a property suitable for use in living tissues, but may also consist of suitable plastic material.
Referring to Figure 7, the graft bone fixation tool according to the present - ~ - invention comprises a tr~n~mi.~.~ion shaft 34 which is adapted to be snugly passed .. 25 through the bore 40 of the screw member 30 in an axially slidable but rotatively - ~ . integral manner, and a rotary drive unit 36 which is provided with an axial bore - - -- '-- - - for snugly receiving the tr~n~mi~.~ion shaft 34 likewise in an axially slidable but rotatively integral manner. As illustrated in Figure 8, the rotary drive unit 36comprises a handle grip 41 adapted to be held by hand, and a rotary tube 42 integrally attached to the handle grip 41. The axial bore of the rotary drive unit 36 passes through the handle grip 41 and the rotary tube 42. As shown in Figure 6c, the free end of the tr~n~mi~.cion shaft 34 is provided with a tapered, rounded or otherwise pointed tip 32. As discussed hereinafter, the tr~n.~mi~.~isn shaft 34 may be optionally provided with an axial bore 49 which extends over its entire length so that a guide wire may be passed therethrough.
How this fixation tool is used for threading the screw member 30 into a gap between the graft bone piece 2 and the wall of the bore 7 formed in the tibia S is now described in the following with reference to Figure 7.
First of all, the tr~ncmic.cion shaft 34 is passed through the axial bore of the rotary drive unit 36, and the screw member 30 is fitted on the forward end of B the trancmiccion shaft 34 projecting from the free end of the rotary shaft 42.
The forward end of the transmission shaft 34 is then passed into the gap definedbetween the graft bone piece 2 and the adjacent wall of the bore 7 formed in thetibia 5. The tapered forward end of the tr~ncmiccion shaft 34 provides a guidirlg action for the insertion of the screw member 30 in the gap between the two bone 0 parts. Once the screw member 30 is placed at the mouth of the gap, the screwmember 30 can be urged into the gap by holding the handle grip 41 by hand, and pushinOg the Iear end of the screw member 30 with the forward end of the rotary tube 42. By turning the handle grip 41 by hand in this condition, the screw member 30 may be threaded into the gap. The necessary torque can be positively tr~n.cmitted from the grip handle 41 to the screw member 30 via the tran.cmi.c.cion shaft 34 by virtue of the complementary shape of the inner bore 40 of the screw member 30, and the inner bore of the rotary drive unit 36. Because the tr~n.cmic.cion shaft 34 is passed axially through the screw member 30, the diversion of the screw member 30 from the intended path for insertion can be positively prevented, and the screw member 30 can be accurately guided into the gap.
Once the screw member 30 is threaded into the gap by a prescribed distance, the tr~ncmiccion shaft 34 and the rotary drive unit 36 can be removed from the screw member 30 by pulling them away from the screw member 32.
-- - ---. . 25 In the case of the fixation tool illustrated in Figure 9, the base end of the . . tr~ncmic.cion shaft 34 is integrally attached to the handle grip 41, and to provide a -- - - - - - - support for the screw member 30 from the rear as the rotary tube 42 did in the first embodiment, an adjnstment tube 44, which may be selected from a plurality of adjustment tubes having diLLerellt lengths, is interchangeably fitted on the tran.cmi.c.cion shaft 34. The operation and the function of this figation tool are otherwise simiIar to those of the first fixation tool.
In the case of the third embodiment of the graft bone fixation tool illustrated in Figure 10, the tr~n.cmic.sion shaft 35 is likewise integrally attached to the handle grip 45 of the rotary drive unit 36. The base end section 35a of the tr~n.cmi.c.cion shaft 35, which is provided with a round cross section as illustrated in Figure 11, is integrally attached to the handle grip 45, and the free end of the ..
-9- ~191312 tr~nsmicsisn shaft is provided with an intermediate section 35b having a hexagonal cross section, and a tapered tip 33 which provides a guiding action similarly as the tapered tips of the first and second embodiments. Because the outer diameter of the base end section 35a is at least larger than the minimum outer diameter of the intermediate section 35b, an annular shoulder 35c is defined beh~-een the he~agonal intermediate section 35b and the round base end section 35a. In this case, as illustrated in Figures 11a and 11b, the scre-v member 31 likewise consists of a hollow cylindrical member having a straight thread 46 around its outer circurnference. The screw member 31 is provided with an axial 0 bore 47 consisting of a base end section 47a having a circ~lar cross section corresponding to that of the base end section 35a of the transmission shaft 35, and a free end section 47b having a he~agonal cross section corresponding to that ofthe intermediate section 35b of the transmission shaft 35. An annular shoulder 47c is defined between the base end section 47a and the free end section 47b of the a~ial bore 47 of the screw member 31.
According to the third embodiment of the fixation tool, once the screw member 31 is fitted on the tr~nsmission shaft 35, the screw member 31 is rotatively enga ed by the inter_ediate section 35b of the transrnission shaft, and the screw member 31 is supported from the rear by the annular shoulder 35c of the tr~n~micsion shaft 35 eng~oing the associated armular shoulder 47c defined in the axial bore ~7 of the screw member 31. The operation and the function of this fixation tool are similar to those of the second embodiment of the graft bone fixation tool.
Sometirnes, the scIew member may consist of a m~t~ori~l which can be - - 25 gradually absorbed by the living body. Therefore, the scIew member is not required to be removed after the bone has been fully reconstructed. In such a - - case, the wall thickness of the screw member may prematurely t1iminish by being absorbed by the living body during use, and may lose the required mechanical strength over time. Therefore, if the original wall thickness is too small or the material of the screw member is absorbed by the living body too rapidly, the screw member may prematurely collapse under the pressure from the surrounding bone which has grown over time. Therefore, depending on various conditions, it may be desirable to place a plug called "blocker" into the central bore of the screw member after the screw member has been securely lodged in the bone part.
By doing so, the screw member can retain its mechanical strength against extemal pressure. The blocker may also consist of a material which can be -lo- 2191372 absorbed by the living body. As one can readily appreciate, the use of such a blocl~er is not limited to the case where a material that can be absorbed by theliving body is used. When the material of the screw member is not provided with a sufficient mechanical strength by itself against the extemal pressure applied thereto by the surrounding bone part growing over time, it is advantageous to use a blocker.
In Figure 6a is illustrated, in im~gin~ry lines, a blocker 50 which is fitted into the central bore 40 of the screw member 30. Figure 12 illustrates yet another embodiment of the screw member 52 fitted with a bloc~er ~1. In this 0 case, the bloc~er 51 as well as the associated central bore ~3 is provided with a threaded section 51a and 53a for securely retaining the blocker 51 in the central bore 53 of the screw member 51.
The present invention is not limited by the above described embodiments, and can be variously modified without departing from the scope of the present invention.
For instance, the screw member was provided strictly ~ith a straight thread around its outer circumference over its entire length in the above described embodiments, but may be partly provided with a taper thread and/or a guide projection to an extent permi.ssihle in each application without departing from the spirit of the present invention. Obviously, the screw member is typically provided with some chamferin~, and it should not be considered as deviating -from the teachin~ of this patent application.
The engagement means used between the screw member and the - tr~n~miccion shaft as well as that optionally used between the tr~ncmi~cion shaft - ~ :- 25 and the rotary drive unit is not limited to the arrangement involving a hexagonal cross section, but may consist of any arrangement as long as it allows the two - - - parts to be separated away from each other in the axial direction but firmly secures the two parts together for integral Iotation with each other.
In the same way as the bore was formed in the axial center of the collv~"Lional fixation tool for passing the guide wire therethrou~h, bores 49 and 50 (~ rures 6c and 11c) may be passed through the tr~n~mis~ion shaft and the rotary drive unit so as to receive the guide wire, and thereby guide the tr~ncmi.c~ion shaft to the intended path of insertion in a similar fashion to the col.YellLional practice.
The advantages of the present invention may be sl~mmari7ed as given in the following, but it should not be understood as being exclusive of other possible . .
advantages.
Because the screw member is turned by the tran.~mic.~ion shaft with the inner cilcu~lrciellce of the screw member fully engaged with the tr~n~mi.s.sion shaft over the entire length of the screw member, the drive torque is effectively tr~ncrnitted to the screw member, and the screw member can be firmly threaded into the gap. Also, the dislodgment of the bit from the tr~n~m;c~ion shaft or the deformation of the engagement means can be avoided.
The screw member is not thrown off from the axial center as it is threaded into the gap because it is securely supported by the transmission shaf.0 which is passed through the scre-v member. Therefore, the grafi bone piece can be easily and reliably attached to a desired location without d~m~oino the grafttendon or the surrounding tissues.
When the sciew member is provided with a strictly straight thread without any section of taper thread, the entire length of the screw member can be threaded with the graft bone piece 2, and the securing force of the screw memberfor a given length thereof can be m~imi7ed. Also, because the forward tip of the screw member would not project toward the graft tendon with the result that,as opposed to the conventional screw members provided with a section of taper thread or a guide projection at its tip, the tip of the screw member would not damage the graft tendon or the surrounding tissues while the force effective ir securing the graft bone piece is m~imi7ed.
Furthermore, when there is no taper in the tip of the screw member, because a guide shaft of a relatively large diameter can be extended from the tip - - ~ of the screw member, dive~ g of the movement of the screw member from the . .
- -- ~ - 25 intended path of insertion can be avoided as opposed to the conventional guide wire which is known to be too fle~ible for effective guide action.
- Although the present invention has been described in terms of preferred embodiments thereof, it is obvious to a person skilled in the art that various alterations and modifications are possible without departing from the scope of the present irlvention which is set forth in the appended claims.
TECHNICAL FIELD
The present invention relates to a graft bone fixation tool for securing a graft bone piece in a bore forrned in a bone, and in particular to a graft bone fixation tool for use in tendon transfer surgical operations in the field of orthopedic surgery.
BACKGROU~ OF IHE rNVE~TIO~
In the field of orthopedic surgery, the method known as the BTB (bone-tendon-bone) method has been used for reconstructing a severed tendon as illustrated in Figures la to 1c. According to the BTB method, a graft consistingof tw-o pieces of bone 2 joined by a tendon 1 is harvested typically from a patella and an adjacent tibia, and sutures 3 are passed through openings formed in the bone pieces 2. Meanwhile, bore 6 and 7 are drilled in the femur 4 and the tibia 5 at a joint whose tendon is severed or otherwise damaged, and is therefore desired to be reconstructed.
By using the sutures 3, the graft tendon 1 along with the graft bone pieces 2 are passed through the bores 6 and 7 formed in the femur 4 and the tibia 5 so that the graft tendon 1 extends between the femur 4 and the tibia 5. A screw member 9 is then threaded into a gap defined between the inner wall of the bore 7 of the tibia 5 and the corresponding bone piece 2 by using a fixation tool 8 so that the bone piece 2 may be securely pressed against the inner wall of the bore 7 ofthe tibia 5. Similarly, another screw member 9 is threaded into a gap defined - - between the inner wall of the bore 6 of the femur 4 and the corresponding bone - - - 25 piece 2 by using the same fixation tool 8 so that the bone piece 2 may be - - - similarly secured against the inner wall of the bore 6 of the femur 4.
As a result, the graft bone pieces 2 are firmIy secured to the femur 4 arld the tibia 5, respectively, and the damaged tendon between the femur 4 and the tibia S is allowed to rebuild itself while the graft tendon 1 e~tending between the two bone pieces 3 keeps the femur 4 and the tibia 5 together.
In such a tendon reconstruction surgery, screw members 10, 11 and 12 illustrated in Figures 2 to 4 in combination with a iïgation tool 13 such as the one illustrated in Figure 5 have col,velltionally been used.
The screw member 10 illustrated in Figure 2 consists of a screw shank 15 3~ which is provided with an engagement recess 14, adapted to be engaged by a bit formed at the tip of the fixation tool 13, in a base end surface thereof, and is.- . ~ .
. -2- 2l9l31~
generally provided with a tapered profile defined by a base section having a straight (parallel) thread and a free end section having a taper thread, and an inner guide bore 20 passed axially entirely through the screw member 10.
The screw member 11 illustrated in Figure 3 comprises a screw head 17 5 having an engagement recess 18 adapted to be engaged by a bit formed at the tip of the fixation tool 13, a screw shank 19 having a generally tapered.profile defined by a base end section provided with a straight thread, and a free end section provided with a taper thread, and an inner guide bore 20 passed axially entirely through the screw member 11.
lo The screw member 12 illustrated in Figure 4 consists of a screw shanX 21 .. having a straight screw thread around its outer cil~;ulllfelence, and is provided with a conical guide projection 22 at a tip thereof. The screw member 12 is further provided, in an axial center of the base end thereof, with a larger threaded bore 23 for engaging a bit for fastening the screw member, and a smaller coaxial15 bore 24 having a reversed thread for eng~ging a bit for unfaster~ ng the screw member 12.
Referring to Figure 5, the fixation tool 13 comprises a rotary drive unit 25 adapted to be gIipped by hand, and a tr~n.cmicsion shaft 26 w-hich is integrally attached to the rotary drive unit 25, and is formed with a bit at a free end thereof 20 for engagement with associated engagement means, typically consisting of a hexagonal recess, provided in the screw member 10 (11 or 12). When a screw member having an axial bore such as the screw members 10 and 11 is used, an axial bore 27 is also forrned in the rotary drive unit 25 and the tran.smic.cion shaft . . ~ - - - 26 so that the guide wire 28 for facilitating the insertion of the screw member - . . - -~ - 25 may be passed through this axial bore 27 and the bore of the screw member 10.
.. - Depending on the kind of the screw member, a protector 29 may be fitted on the - ~ - tr~n.cmi.c.cion shaft 26 so as not to damage the surrounding tissues and the graft tendon.
Such conventional arrangements, which employ a screw member such as 30 those described above in combination with the fixation tool as described above, are k~owrl to have a number of problems that ueed to be resolved.
For instance, because the engagement means (engagement recesses 14 and 18) for eng~ging the bit of the fixation tool 13 is reIatively shallow as is the case with the screw members 10 and 11 illustrated in Figures 2 and 3, the 35 necessary torque to firmly thread the screw member into the gap between two adjacent bone parts may not be effectively tr~ncmitted to the screw member particularly when the length of the straight thread section is increased in length to the end of increasing the securing force, and a relatively large effort is therefore required to turn the scre-v member. It is possible that the bit may be dislodgedfrom the enGagement recess of the screw member and thereby damage the 5 adjacent bone parts.
Also, due to possible mic~ nment of the aYial center of the screw member from the intended path of insertion, the so-called screw diversion may occur so that the graft bone pieces 2 may not be secured accùrately and firmly enough for the tendon to recover its original condition in a satisfactory manner0 following the surgery.
When the engagement means for engaging the bit of the fi~ation tool 13 consists of larger and smaller threaded bores 23 and 24 which are coaxial with each other as is the case with the screw member 12 of Figure ~, hvo separate tools will be needed for inserting and removing the screw member, respectively.
5 In particular, when removing the screw member by using the smaller threaded bore 24, the screw thread may not be able to withstand the large torque that maybe required to remove the screw member 12.
When a tapered threaded section or a guide projection is provided in a free end of the screw shank as is the case with the screw members 10 and 11 of 20 Figures 2 and 3, if the screw member is forced too deeply into the gap between two bone parts or the remodeling of the bore in the bone has occurred, the pointed tip of the screw member may damage the surrounding tissues and the graft tendon. Even if the screw member is properly threaded into the gap - ~ - between two bone parts, because the tapered section is not effective in securing 26 the screw member, and the effective length of the screw thread is limited to the - straight thread section of the saew member, the securing force for the bone parts - - - may not be sufficient, and the rehabilitation of the patient may be undesirably prolonged.
More specifically, the length of a graft bone piece 2 harvested from a 30 patella of a person is no more than 20 to 25 mm, and the effective length of the screw member is desired to colrespond to this length so as to m~imi7e the securing force. However, because of the provision of a tapered section and a guide projection, the effective length of the screw member tends to be insufficient to achieve a sufficient force for engagement. If the effective length of the screw 3~ member is increased, the overall length of the screw member becomes so large that the tapered section or the guide projection projects toward the graft tendon, .
~4~ 2191372 thereby increasing the possibility of d~m~ging the graft tendon.
Thus, the problems of the prior art may be summ~n7ed as follows.
Because the effective threaded section of a screw member is limited to its straight or parallel thread section, it may be desired to elimin~te any tapered section to m~-imi7e the securing force for a given length of the screw member. Howe~er, this causes a substantial difficulty in inserting the screw member into a gap in the bone due to lack of a guiding action of its free end. This may be overcome to a certain extent by increasing the thickness of the guide wire. The improved guiding action of the guide wire may allow the use of a screw member without any tapered section.
A thick guide wire however still have two problems. First of all, because the bore for passing the guide wire has to be provided in the bit of thefixation tool also, and provision of such a large central bore in the bit may reduce the mechanical strength of the bit to an unacceptable level. It may collapse when it is engaged with a screw head, and a substantial torque is applied to the bit.
Secondly, the diameter of the guide wire is therefore necessarily less than the diameter of the bit, and a somewhat blunt annular shoulder is inevitably definedbetween the free end of the screw member and the guide wire. ~he blunt annular shoulder is obviously highly detrimental to the smooth insertion of the screw member.
BRIEF SUM~ARY OF THE I~ENIION
In view of such problems of the prior art, a primary object of the present invention is to provide a graft bone fixation tool which allows a graft bone piece - - to be securely lodged in a bore formed in a bone part.A second object of the present invention is to provide a graft bone - - fixation tool which can be easily used without requiring any undue effort for - - ~ inserting a screw member into a gap between two born parts.
- A third object of the present invention is to provide a screw member for insertion between two bone parts which provides a sufflcient securing force.
A fourth object of the present invention is to provide a screw member for insertion between two bone parts which would not damage the graft tendon and the surrounding tissues.
According to the present invention, such objects can be accomplished by providing a graft bone fixation tool, comprising: a tr~n.cmiccion shaft including a typically tapered forward tip and an intermediate section provided with engagement means for torque tr~ncmis~ion, the tr~ncmiccion shaft being adapted -5~ 2191372 to be fitted into and through an axial bore of a screw member provided with associated engagement means for cooperation with the engagement means of the tr~n.~mi.~.cion shaft, the screw member being provided with a screw thread around an outer circumference thereof; and a rotary drive unit provided at a base end of - 5 the tr~n.cmi~.sion shaft for manually rotating the tr~n.~mis.sion shaft so as to apply a torque to the screw member fitted on the intermediate section of the tr~n.cmi~ion shaft.
Thus, the screw member may be provided with a strictly straight thread without any section of taper thread because the forward end of the tran.~mi.~.~ion 10 shaft provides the necessary guide action, the entire length of the screw member can be threaded with the graft bone piece, and the securing force of the screw member for a given length thereof can be m~imi7ed. Also, because the forward tip of the screw member would not project toward the graft tendon ~-ith the result that, as opposed to the conventional screw members provided with a 5 section of taper thread or a guide projection at its tip, the tip of the screw member would not damage the graft tendon or the surrounding tissues while the force effective in securing the graft bone piece is m~imi7ed. Because the screw member is tumed by the tr~n.cmic~ion shaft with the inner circumference of the scre~- member fully engaged with the tr~n.smis.cion shaft over the entire length of 20 the screw member, the drive torque is effectively transmitted to the screw member, and the screw member can be firmly threaded into the gap. Also, the -dislodgment of the bit from the tr~n.~mi~.~ion shaft or the deformation of the engagement means can be avoided, and the tr~n~mi.s.cion shaft provides a - favorable guiding action.
- - ............. .: . - .- - 25 The tr~n.~mi.c.~ion shaft may be provided with an axial bore for passing a . - guide wire thele~hlough. In that case, because no taper may- be provided in the - : - --- :-- :.. .- -- tip of the screw member, a guide shaft of a relatively large diameter can be e~tended from the tip of the screw member with the result that diverging of the movement of the screw member from the int~nded path of insertion can be 30 avoided as opposed to the conventional guide wire which is known to be too flexible ~or ef~ecti~e guide action.
The screw member may consist of a hollow cylindrical member having a strictly straight thread around its cLL~;u~ ellce. And, its axial bore may be either straight bore having a uniform diameter or have a stepped shape defining 35 an annular shoulder facing the rotary drive ur~it.
According to a ple~elled embodiment of the present in~ention, the rotary -6- 2l91372 drive unit comprises a handle grip, a rotary tube integrally attached to the handle grip, and an axial bore passed through the handle grip and the rotary tube for receiving the intermediate section of the tr~n.smi.c.sion shaft in an axially slidable but rotatively integral manner, a free end of the rotary tube being adapted to abut 5 an opposing axial end of the screw member.
According to a second preferred embodiment of the present invention, the rotary drive unit comprises a handle grip, and a base end of the tr~nsmi~.sion shaf-, is integrally attached to the handle grip, the fixation tool further comprising - an adjustment tube that can be fitted on the trancmi.s.sion shaft in such a manner that a free end of the rotary tube-abuts an opposing axial end of the screw member when the screw member is fitted on the intermediate section of the tr~nsmis.sion shaft in an axially slidable but rotatively integral manner.
According to a third preferred embodiment of the present invention, the rotary drive unit comprises a handle grip, and a base end of the tr~n.smic.sion shaft is integrally attached to the handle grip, the tr~n.smi~cion shaft comprising a base end section, extending between the intermediate section and the handle grip, which has a larger outer diameter than the intermediate section so as to define an annular shoulder facing away from the handle grip.
BRIEF DESCRIPTION OF THE DRAWINGS
Now the present invention is described in the following with reference to the appended drawings, in which:
Figures la to 1c are illustrative views showing the tendon transfer surgery using the collve"Lional graft bone fixation tool;
.. . Figure 2 is a lonGiturlin~l sectional view of a collvellLional screw member 25 used for securing a graft bone piece to a bone- part;
- - - - -: - Figure 3 is a lon2itudinal sectional view of another co"ve,~Lional screw ---- - member;
~ Figure 4 is a lon~itu-1in~l sectional view of yet another collv~l"ional screw member;
Figure 5 is an overall front view of a collv~"~ional graft bone fixation tool;
Figures 6a to 6c are illustrative views showing an embodiment of the screw member and an associated tr~nsmi.c.cion shaft used in the graft bone fixation tool of the present invention;
Figure 7 is an illustrative view showing a first embodiment of the graft bone fi~ation tool according to the present invention, along with the manner in '-which this tool is used for inserting a screw mernber into a gap behveen a graftbone piece and an adjacent wall of a bore formed in a bone part;
Figure 8 is a perspective view showing the handle grip of the graft bone piece fixation tool illustrated in Figure 7;
Figure 9 is a partly broken away perspective view of a second embodirnent of the graft bone fixation tool according to the present invention;
Figure 10 is a partly perspective view of a third embodiment of the graft bone fixation tool according to the present invention;
- Figures 11a, 11b and 11c are views similar to Figures 6a, 6b and 6c, 0 respectively, showing an alternate embodiment of the screw member suitable for use with the third embodiment illustrated in Ficure 10, along with the associated tr~n~mi.~cion shaft of the graft bone fixation tool illustrated in Figure 10; and Figure 12 is a sectional view of yet another embodiment of the screw member.
16 DETAILED DESCRIPTION OF THE PREFERRED E~30DL~ENIS
Figures 6a and 6b illustrate an embodiment of the screw member 30 according to the present invention which essentially consists of hollow cylindrical member having a straight (parallel) screw thread 39 on outer ci~;u~felelltial surface thereof, and a bore 40 having a hexagonal cross sectionand passed a~ially entirely through the screw member 30. The m~t~n~l of the screw thread typically consists of an alloy having a property suitable for use in living tissues, but may also consist of suitable plastic material.
Referring to Figure 7, the graft bone fixation tool according to the present - ~ - invention comprises a tr~n~mi.~.~ion shaft 34 which is adapted to be snugly passed .. 25 through the bore 40 of the screw member 30 in an axially slidable but rotatively - ~ . integral manner, and a rotary drive unit 36 which is provided with an axial bore - - -- '-- - - for snugly receiving the tr~n~mi~.~ion shaft 34 likewise in an axially slidable but rotatively integral manner. As illustrated in Figure 8, the rotary drive unit 36comprises a handle grip 41 adapted to be held by hand, and a rotary tube 42 integrally attached to the handle grip 41. The axial bore of the rotary drive unit 36 passes through the handle grip 41 and the rotary tube 42. As shown in Figure 6c, the free end of the tr~n~mi~.cion shaft 34 is provided with a tapered, rounded or otherwise pointed tip 32. As discussed hereinafter, the tr~n.~mi~.~isn shaft 34 may be optionally provided with an axial bore 49 which extends over its entire length so that a guide wire may be passed therethrough.
How this fixation tool is used for threading the screw member 30 into a gap between the graft bone piece 2 and the wall of the bore 7 formed in the tibia S is now described in the following with reference to Figure 7.
First of all, the tr~ncmic.cion shaft 34 is passed through the axial bore of the rotary drive unit 36, and the screw member 30 is fitted on the forward end of B the trancmiccion shaft 34 projecting from the free end of the rotary shaft 42.
The forward end of the transmission shaft 34 is then passed into the gap definedbetween the graft bone piece 2 and the adjacent wall of the bore 7 formed in thetibia 5. The tapered forward end of the tr~ncmiccion shaft 34 provides a guidirlg action for the insertion of the screw member 30 in the gap between the two bone 0 parts. Once the screw member 30 is placed at the mouth of the gap, the screwmember 30 can be urged into the gap by holding the handle grip 41 by hand, and pushinOg the Iear end of the screw member 30 with the forward end of the rotary tube 42. By turning the handle grip 41 by hand in this condition, the screw member 30 may be threaded into the gap. The necessary torque can be positively tr~n.cmitted from the grip handle 41 to the screw member 30 via the tran.cmi.c.cion shaft 34 by virtue of the complementary shape of the inner bore 40 of the screw member 30, and the inner bore of the rotary drive unit 36. Because the tr~n.cmic.cion shaft 34 is passed axially through the screw member 30, the diversion of the screw member 30 from the intended path for insertion can be positively prevented, and the screw member 30 can be accurately guided into the gap.
Once the screw member 30 is threaded into the gap by a prescribed distance, the tr~ncmiccion shaft 34 and the rotary drive unit 36 can be removed from the screw member 30 by pulling them away from the screw member 32.
-- - ---. . 25 In the case of the fixation tool illustrated in Figure 9, the base end of the . . tr~ncmic.cion shaft 34 is integrally attached to the handle grip 41, and to provide a -- - - - - - - support for the screw member 30 from the rear as the rotary tube 42 did in the first embodiment, an adjnstment tube 44, which may be selected from a plurality of adjustment tubes having diLLerellt lengths, is interchangeably fitted on the tran.cmi.c.cion shaft 34. The operation and the function of this figation tool are otherwise simiIar to those of the first fixation tool.
In the case of the third embodiment of the graft bone fixation tool illustrated in Figure 10, the tr~n.cmic.sion shaft 35 is likewise integrally attached to the handle grip 45 of the rotary drive unit 36. The base end section 35a of the tr~n.cmi.c.cion shaft 35, which is provided with a round cross section as illustrated in Figure 11, is integrally attached to the handle grip 45, and the free end of the ..
-9- ~191312 tr~nsmicsisn shaft is provided with an intermediate section 35b having a hexagonal cross section, and a tapered tip 33 which provides a guiding action similarly as the tapered tips of the first and second embodiments. Because the outer diameter of the base end section 35a is at least larger than the minimum outer diameter of the intermediate section 35b, an annular shoulder 35c is defined beh~-een the he~agonal intermediate section 35b and the round base end section 35a. In this case, as illustrated in Figures 11a and 11b, the scre-v member 31 likewise consists of a hollow cylindrical member having a straight thread 46 around its outer circurnference. The screw member 31 is provided with an axial 0 bore 47 consisting of a base end section 47a having a circ~lar cross section corresponding to that of the base end section 35a of the transmission shaft 35, and a free end section 47b having a he~agonal cross section corresponding to that ofthe intermediate section 35b of the transmission shaft 35. An annular shoulder 47c is defined between the base end section 47a and the free end section 47b of the a~ial bore 47 of the screw member 31.
According to the third embodiment of the fixation tool, once the screw member 31 is fitted on the tr~nsmission shaft 35, the screw member 31 is rotatively enga ed by the inter_ediate section 35b of the transrnission shaft, and the screw member 31 is supported from the rear by the annular shoulder 35c of the tr~n~micsion shaft 35 eng~oing the associated armular shoulder 47c defined in the axial bore ~7 of the screw member 31. The operation and the function of this fixation tool are similar to those of the second embodiment of the graft bone fixation tool.
Sometirnes, the scIew member may consist of a m~t~ori~l which can be - - 25 gradually absorbed by the living body. Therefore, the scIew member is not required to be removed after the bone has been fully reconstructed. In such a - - case, the wall thickness of the screw member may prematurely t1iminish by being absorbed by the living body during use, and may lose the required mechanical strength over time. Therefore, if the original wall thickness is too small or the material of the screw member is absorbed by the living body too rapidly, the screw member may prematurely collapse under the pressure from the surrounding bone which has grown over time. Therefore, depending on various conditions, it may be desirable to place a plug called "blocker" into the central bore of the screw member after the screw member has been securely lodged in the bone part.
By doing so, the screw member can retain its mechanical strength against extemal pressure. The blocker may also consist of a material which can be -lo- 2191372 absorbed by the living body. As one can readily appreciate, the use of such a blocl~er is not limited to the case where a material that can be absorbed by theliving body is used. When the material of the screw member is not provided with a sufficient mechanical strength by itself against the extemal pressure applied thereto by the surrounding bone part growing over time, it is advantageous to use a blocker.
In Figure 6a is illustrated, in im~gin~ry lines, a blocker 50 which is fitted into the central bore 40 of the screw member 30. Figure 12 illustrates yet another embodiment of the screw member 52 fitted with a bloc~er ~1. In this 0 case, the bloc~er 51 as well as the associated central bore ~3 is provided with a threaded section 51a and 53a for securely retaining the blocker 51 in the central bore 53 of the screw member 51.
The present invention is not limited by the above described embodiments, and can be variously modified without departing from the scope of the present invention.
For instance, the screw member was provided strictly ~ith a straight thread around its outer circumference over its entire length in the above described embodiments, but may be partly provided with a taper thread and/or a guide projection to an extent permi.ssihle in each application without departing from the spirit of the present invention. Obviously, the screw member is typically provided with some chamferin~, and it should not be considered as deviating -from the teachin~ of this patent application.
The engagement means used between the screw member and the - tr~n~miccion shaft as well as that optionally used between the tr~ncmi~cion shaft - ~ :- 25 and the rotary drive unit is not limited to the arrangement involving a hexagonal cross section, but may consist of any arrangement as long as it allows the two - - - parts to be separated away from each other in the axial direction but firmly secures the two parts together for integral Iotation with each other.
In the same way as the bore was formed in the axial center of the collv~"Lional fixation tool for passing the guide wire therethrou~h, bores 49 and 50 (~ rures 6c and 11c) may be passed through the tr~n~mis~ion shaft and the rotary drive unit so as to receive the guide wire, and thereby guide the tr~ncmi.c~ion shaft to the intended path of insertion in a similar fashion to the col.YellLional practice.
The advantages of the present invention may be sl~mmari7ed as given in the following, but it should not be understood as being exclusive of other possible . .
advantages.
Because the screw member is turned by the tran.~mic.~ion shaft with the inner cilcu~lrciellce of the screw member fully engaged with the tr~n~mi.s.sion shaft over the entire length of the screw member, the drive torque is effectively tr~ncrnitted to the screw member, and the screw member can be firmly threaded into the gap. Also, the dislodgment of the bit from the tr~n~m;c~ion shaft or the deformation of the engagement means can be avoided.
The screw member is not thrown off from the axial center as it is threaded into the gap because it is securely supported by the transmission shaf.0 which is passed through the scre-v member. Therefore, the grafi bone piece can be easily and reliably attached to a desired location without d~m~oino the grafttendon or the surrounding tissues.
When the sciew member is provided with a strictly straight thread without any section of taper thread, the entire length of the screw member can be threaded with the graft bone piece 2, and the securing force of the screw memberfor a given length thereof can be m~imi7ed. Also, because the forward tip of the screw member would not project toward the graft tendon with the result that,as opposed to the conventional screw members provided with a section of taper thread or a guide projection at its tip, the tip of the screw member would not damage the graft tendon or the surrounding tissues while the force effective ir securing the graft bone piece is m~imi7ed.
Furthermore, when there is no taper in the tip of the screw member, because a guide shaft of a relatively large diameter can be extended from the tip - - ~ of the screw member, dive~ g of the movement of the screw member from the . .
- -- ~ - 25 intended path of insertion can be avoided as opposed to the conventional guide wire which is known to be too fle~ible for effective guide action.
- Although the present invention has been described in terms of preferred embodiments thereof, it is obvious to a person skilled in the art that various alterations and modifications are possible without departing from the scope of the present irlvention which is set forth in the appended claims.
Claims (8)
The embodiments of the invention, in which an exclusive property or privilege isclaimed, are defined as follows:
1. A graft bone fixation tool, comprising:
a transmission shaft including a forward tip and an intermediate section provided with engagement means for torque transmission, said transmission shaft being adapted to be fitted into and through an axial bore of a screw member provided with associated engagement means for cooperation with said engagement means of said transmissionshaft, said screw member being provided with a screw thread around an outer circumference thereof; and a rotary drive unit provided at a base end of said transmission shaft for manually rotating said transmission shaft so as to apply a torque to said screw member fitted on said intermediate section of said transmission shaft.
a transmission shaft including a forward tip and an intermediate section provided with engagement means for torque transmission, said transmission shaft being adapted to be fitted into and through an axial bore of a screw member provided with associated engagement means for cooperation with said engagement means of said transmissionshaft, said screw member being provided with a screw thread around an outer circumference thereof; and a rotary drive unit provided at a base end of said transmission shaft for manually rotating said transmission shaft so as to apply a torque to said screw member fitted on said intermediate section of said transmission shaft.
2. A graft bone fixation tool according to claim 1, wherein said forward tip of said transmission shaft is provided with a tapered or otherwise pointed tip.
3. A graft bone fixation tool according to claim 1, wherein said screw member consists of a hollow cylindrical member having a strictly straight thread around its circumference.
4. A graft bone fixation tool according to claim 1, wherein said rotary drive unit comprises a handle grip, a rotary tube integrally attached to said handle grip, and an axial bore passed through said handle grip and said rotary tube for receiving said intermediate section of said transmission shaft in an axially slidable but rotatively integral manner, a free end of said rotary tube being adapted to abut an opposing axial end of said screw member.
5. A graft bone fixation tool according to claim 1, wherein said rotary drive unit comprises a handle grip, and a base end of said transmission shaft is integrally attached to said handle grip, said fixation tool further comprising an adjustment tube that can be fitted on said transmission shaft in such a manner that a free end of said rotary tube abuts an opposing axial end of said screw member when said screw member is fitted on saidintermediate section of said transmission shaft in an axially slidable but rotatively integral manner.
6. A graft bone fixation tool according to claim 1, wherein said rotary drive unit comprises a handle grip, and a base end of said transmission shaft is integrally attached to said handle grip, said transmission shaft comprising a base end section, extending between said intermediate section and said handle grip, which has a larger outer diameter than said intermediate section so as to define an annular shoulder facing away from said handle grip.
7. A graft bone fixation tool according to claim 1, wherein said inner bore of said screw member is provided a base end section which is complementary in cross section to said base end section of said transmission shaft, and a free end section which is complementary in cross section to said intermediate section of said transmission shaft so that an annular shoulder facing said handle grip is defined between said base end section and said free end section of said axial bore of said screw member for cooperation with said annular shoulder of said transmission shaft.
8. A graft bone fixation tool according to claim 1, wherein said transmission shaft is provided with an axial bore for passing a guide wire therethrough.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP33108295A JP3766709B2 (en) | 1995-05-08 | 1995-11-27 | Bone fixation joint |
| JP7-331082 | 1995-11-27 | ||
| US08/576,867 US5688285A (en) | 1995-08-29 | 1995-12-21 | Graft bone fixation tool |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2191372A1 true CA2191372A1 (en) | 1997-05-28 |
Family
ID=26573738
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002191372A Abandoned CA2191372A1 (en) | 1995-11-27 | 1996-11-27 | Graft bone fixation tool |
Country Status (3)
| Country | Link |
|---|---|
| US (1) | US5688285A (en) |
| EP (1) | EP0775473A1 (en) |
| CA (1) | CA2191372A1 (en) |
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-
1995
- 1995-12-21 US US08/576,867 patent/US5688285A/en not_active Expired - Fee Related
-
1996
- 1996-11-26 EP EP96308508A patent/EP0775473A1/en not_active Withdrawn
- 1996-11-27 CA CA002191372A patent/CA2191372A1/en not_active Abandoned
Also Published As
| Publication number | Publication date |
|---|---|
| US5688285A (en) | 1997-11-18 |
| EP0775473A1 (en) | 1997-05-28 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued |
Effective date: 19991129 |
|
| FZDE | Discontinued |
Effective date: 19991129 |
|
| FZDE | Discontinued |
Effective date: 19991129 |