CA2137393C - Bone fixation element - Google Patents
Bone fixation element Download PDFInfo
- Publication number
- CA2137393C CA2137393C CA002137393A CA2137393A CA2137393C CA 2137393 C CA2137393 C CA 2137393C CA 002137393 A CA002137393 A CA 002137393A CA 2137393 A CA2137393 A CA 2137393A CA 2137393 C CA2137393 C CA 2137393C
- Authority
- CA
- Canada
- Prior art keywords
- bone
- drill
- shaped
- tip
- shaft
- 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
Links
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
- A61B17/8625—Shanks, i.e. parts contacting bone tissue
- A61B17/8635—Tips of screws
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/16—Bone cutting, breaking or removal means other than saws, e.g. Osteoclasts; Drills or chisels for bones; Trepans
Abstract
A bone plate assembly is described herein. The assembly comprises a bone fixation device having a shaft threaded at the head end and shaped as a drill toward the tip. The part shaped as a drill is self-drilling and self-cutting. The device can be used for fixating bone plates or as an attachment component for external fixation systems comprising support rods and clamps used in osteosynthesis.
Description
_2I37393 11316.A66 BONE FIXATION DEVICE
Field Of The Invention The invention relates to a bone fixation device, specifically a bone screw.
Backcrround Of The Invention Bone screws and wires find wide-ranging applications in osteosynthesis. In osteosynthesis bone screws are used for fixation of bone fragments as well as attachment of longitudinal support rods. Wires are used to fix bone fragments.
Conventional bone screws, particularly the so-called Schanz screws, are used in osteosynthesis for a multiplicity of purposes in positioning and fixing bone fragments. An example of this are components of an osteosynthetic external fixation device (such as that of EP-B1 0 153 546), which in essence consists of one or more connected longitudinal support rods, that can be disconnected from each other, along with the attached clamps or clasps for receiving the Schanz screws. Such an application requires that prior to the placement of the Schanz screws an appropriate hole be drilled into the bone, into which the Schanz screw can then be screw~l. This procedure is complex and time-consuming.
The thread pitch of a bone screw is critical, for it determines the cutting rate (i.e., the advance) of the screw. In other words, for each turn the screw is forced to go forward by 2,137393 the length of the screw pitch. If a screw pitch of about 1.75 mm, typical for bone screws, is selected, then the tip of the tap used to thread the hole will advance an increment of 1.75 mm for each turn. Assuming a drilling machine with a normal rotational speed of about 600 to 800 r.p.m., typically employed in bone surgery is used to drive the tap, this results in an advance of more than a meter per minute. The extraordinarily intense pressure on the bone caused by this advance to the tap tip can result in spontaneous tears or fractures in the bone. The principal disadvantage of having too rapid an advance is evident primarily when the tip has passed through the proximal corticalis and the medullary space and encounters the inner side of the counter-corticalis. There the tip has no chance of centering itself and producing a so-called channel. Instead of the bone being drilled through, it is thrust away by the tip. This leads inevitably to a splitting of the counter-corticalis. If the screw is inserted near the fracture, the applied pressure is dispersed through longitudinal fissures of the counter-corticalis.
Efforts to reduce the axial pressure by reducing the drill r.p.m. are not possible, since the advance is preset by the thread pitch of the screw.
The manipulation procedures for the insertion of bone screws are also extended. The scre~r hole ~nu~t first be bored out with an initial instrument, and then a second instrument must be used to cut the thread. Finally, in a third procedure, the bone screw is screwed in. It is also not uncommon to have a typical bone screw tightened to the limit of its retention force, in order to fix longitudinal support rods or bone plates on the bone.
This is necessary since there is no stable connection between bone screws and the support rods or plates. Owing to the often very high initial stress, up to the retention force limit, screws can tear loose from the bone.
In addition, during the procedure described above, errors can accumulate, resulting in a poor fixation.
Wires can be inserted into bone without large-scale preliminary work, but they damage the bone owing to the associated high temperatures which arise from friction between bone and wire. In addition, the axial stability of bone fragments fixed with wires is not very great, so that the result may be a loss of positioning.
Summary Of The Invention In accordance with the invention, these difficulties are met by a bone fixation device having a tip shaped like a drill.
Specifically, the invention comprises a bone fixation device comprising a shaft having a head and a tip, the part of said shaft adjacent said tip being shaped as a spiral drill and at least a part of the shaft adjacent the head being threaded.
According to the invention there is provided a bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft. with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part shaped as a drill is self-drilling and self-cutting.
Further, the invention provides a bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part shaped as a drill is shaped as a spiral drill.
Additionally, the invention provides a bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part of the shaft adjacent to the tip is shaped as a double-lipped drill.
Stated another way, the first part (i.e. the part near the tip) of a device according to the invention is shaped as a self-cutting, self-drilling, double lipped spiral drill. Its exterior is at most the diameter of the root of the threaded portion. The front part is advantageously 3-l8mm, preferably 4-l2mm long.
3a Brief Description Of The Drawings The invention will be further described with reference to the accompanying drawing in which:
Fig. 1 is a schematic representation of a bone-fixation device according to the invention.
Fig. 2 is an axial view of the bone fixation device according to Fig. 1.
Fig. 3 is a longitudinal section detail through the winding of the bone fixation device according to Fig. 1.
Fig. 4 is a cross section along the line A-A of Fig. 1.
The bone fixation device shown in Figs. 1-4 essentially consists of a head part 1, a shaft 3 provided with a thread 2, and a front part 4 with a tip 5.
The front part 4 is shaped as a self-cutting, self-drilling, double-lipped spiral drill, whose exterior diameter is smaller than the core diameter of thread 2. The drill shape extends the full length of front part 4. Front part 4 most preferably has a length of 7-9mm, depending on the total length of the device.
The head end 1, as shown in Fig. 2, is provided with a central indentation 6 in the form of a hexagonal socket; this serves for admission of an instrument for screwing the device in a bone. The thread 2 may be a self-tapping thread.
The dimensions of the spiral drill are prpfer~bly as follows:
Point angle 60-120°, preferably 80-90°
Rake or helix angle 10-40°, preferably 20-30°
Margin 0.2-l.Omm, preferably 0.3-0.6mm ;137393 Screw height 0.3-l.5mm, preferably 0.6-0.8mm Drill core 0.1-0.6, preferably 0.3-0.5 times the outside diameter The bone fixation device can have a multiplicity of applications. For example, it can be used for fixation of bone plates or as an attachment component for external fixation systems comprising support rods and clamps used in osteosynthesis.
In use the device according to the invention is applied as one would apply a normal self-tapping screw, driving the device in manually with a suitable screwdriver.
Field Of The Invention The invention relates to a bone fixation device, specifically a bone screw.
Backcrround Of The Invention Bone screws and wires find wide-ranging applications in osteosynthesis. In osteosynthesis bone screws are used for fixation of bone fragments as well as attachment of longitudinal support rods. Wires are used to fix bone fragments.
Conventional bone screws, particularly the so-called Schanz screws, are used in osteosynthesis for a multiplicity of purposes in positioning and fixing bone fragments. An example of this are components of an osteosynthetic external fixation device (such as that of EP-B1 0 153 546), which in essence consists of one or more connected longitudinal support rods, that can be disconnected from each other, along with the attached clamps or clasps for receiving the Schanz screws. Such an application requires that prior to the placement of the Schanz screws an appropriate hole be drilled into the bone, into which the Schanz screw can then be screw~l. This procedure is complex and time-consuming.
The thread pitch of a bone screw is critical, for it determines the cutting rate (i.e., the advance) of the screw. In other words, for each turn the screw is forced to go forward by 2,137393 the length of the screw pitch. If a screw pitch of about 1.75 mm, typical for bone screws, is selected, then the tip of the tap used to thread the hole will advance an increment of 1.75 mm for each turn. Assuming a drilling machine with a normal rotational speed of about 600 to 800 r.p.m., typically employed in bone surgery is used to drive the tap, this results in an advance of more than a meter per minute. The extraordinarily intense pressure on the bone caused by this advance to the tap tip can result in spontaneous tears or fractures in the bone. The principal disadvantage of having too rapid an advance is evident primarily when the tip has passed through the proximal corticalis and the medullary space and encounters the inner side of the counter-corticalis. There the tip has no chance of centering itself and producing a so-called channel. Instead of the bone being drilled through, it is thrust away by the tip. This leads inevitably to a splitting of the counter-corticalis. If the screw is inserted near the fracture, the applied pressure is dispersed through longitudinal fissures of the counter-corticalis.
Efforts to reduce the axial pressure by reducing the drill r.p.m. are not possible, since the advance is preset by the thread pitch of the screw.
The manipulation procedures for the insertion of bone screws are also extended. The scre~r hole ~nu~t first be bored out with an initial instrument, and then a second instrument must be used to cut the thread. Finally, in a third procedure, the bone screw is screwed in. It is also not uncommon to have a typical bone screw tightened to the limit of its retention force, in order to fix longitudinal support rods or bone plates on the bone.
This is necessary since there is no stable connection between bone screws and the support rods or plates. Owing to the often very high initial stress, up to the retention force limit, screws can tear loose from the bone.
In addition, during the procedure described above, errors can accumulate, resulting in a poor fixation.
Wires can be inserted into bone without large-scale preliminary work, but they damage the bone owing to the associated high temperatures which arise from friction between bone and wire. In addition, the axial stability of bone fragments fixed with wires is not very great, so that the result may be a loss of positioning.
Summary Of The Invention In accordance with the invention, these difficulties are met by a bone fixation device having a tip shaped like a drill.
Specifically, the invention comprises a bone fixation device comprising a shaft having a head and a tip, the part of said shaft adjacent said tip being shaped as a spiral drill and at least a part of the shaft adjacent the head being threaded.
According to the invention there is provided a bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft. with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part shaped as a drill is self-drilling and self-cutting.
Further, the invention provides a bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part shaped as a drill is shaped as a spiral drill.
Additionally, the invention provides a bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part of the shaft adjacent to the tip is shaped as a double-lipped drill.
Stated another way, the first part (i.e. the part near the tip) of a device according to the invention is shaped as a self-cutting, self-drilling, double lipped spiral drill. Its exterior is at most the diameter of the root of the threaded portion. The front part is advantageously 3-l8mm, preferably 4-l2mm long.
3a Brief Description Of The Drawings The invention will be further described with reference to the accompanying drawing in which:
Fig. 1 is a schematic representation of a bone-fixation device according to the invention.
Fig. 2 is an axial view of the bone fixation device according to Fig. 1.
Fig. 3 is a longitudinal section detail through the winding of the bone fixation device according to Fig. 1.
Fig. 4 is a cross section along the line A-A of Fig. 1.
The bone fixation device shown in Figs. 1-4 essentially consists of a head part 1, a shaft 3 provided with a thread 2, and a front part 4 with a tip 5.
The front part 4 is shaped as a self-cutting, self-drilling, double-lipped spiral drill, whose exterior diameter is smaller than the core diameter of thread 2. The drill shape extends the full length of front part 4. Front part 4 most preferably has a length of 7-9mm, depending on the total length of the device.
The head end 1, as shown in Fig. 2, is provided with a central indentation 6 in the form of a hexagonal socket; this serves for admission of an instrument for screwing the device in a bone. The thread 2 may be a self-tapping thread.
The dimensions of the spiral drill are prpfer~bly as follows:
Point angle 60-120°, preferably 80-90°
Rake or helix angle 10-40°, preferably 20-30°
Margin 0.2-l.Omm, preferably 0.3-0.6mm ;137393 Screw height 0.3-l.5mm, preferably 0.6-0.8mm Drill core 0.1-0.6, preferably 0.3-0.5 times the outside diameter The bone fixation device can have a multiplicity of applications. For example, it can be used for fixation of bone plates or as an attachment component for external fixation systems comprising support rods and clamps used in osteosynthesis.
In use the device according to the invention is applied as one would apply a normal self-tapping screw, driving the device in manually with a suitable screwdriver.
Claims (9)
1. A bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part shaped as a drill is self-drilling and self-cutting.
2. The bone plate assembly according to claim 1 wherein the thread has a minor diameter and the part shaped as a drill has a maximum exterior diameter which is at most equal to the minor diameter of the thread.
3. The bone plate assembly according to claim 2 wherein the part shaped as a drill is from 3 to 18 mm long.
4. The bone plate assembly according to claim 3 wherein the part shaped as a drill is from 4 to 12 mm long.
5. The bone plate assembly according to claim 2 wherein the thread extends out into the part of the shaft.
6. The bone plate assembly according to claim 2 and comprising a central indentation in said head for admitting an instrument for screwing the device into a bone.
7. The bone plate assembly of claim 6 wherein the indentation is a hexagonal socket.
8. A bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part shaped as a drill is shaped as a spiral drill.
9. A bone plate assembly comprising a bone plate having screw holes and a bone fixation device in a screw hole of said plate, said bone fixation device having a shaft with a head and a tip, a part of the shaft adjacent the tip being shaped as a drill and another part of the shaft having a thread, wherein the part of the shaft adjacent to the tip is shaped as a double-lipped drill.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CH03643/93-8 | 1993-12-07 | ||
| CH03643/93A CH688222A5 (en) | 1993-12-07 | 1993-12-07 | Bone fixation element. |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2137393A1 CA2137393A1 (en) | 1995-06-08 |
| CA2137393C true CA2137393C (en) | 2004-06-15 |
Family
ID=4260399
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002137393A Expired - Lifetime CA2137393C (en) | 1993-12-07 | 1994-12-06 | Bone fixation element |
Country Status (10)
| Country | Link |
|---|---|
| US (1) | US6059785A (en) |
| EP (1) | EP0657142B1 (en) |
| JP (1) | JP3701995B2 (en) |
| AT (1) | ATE200404T1 (en) |
| AU (1) | AU689140B2 (en) |
| CA (1) | CA2137393C (en) |
| CH (1) | CH688222A5 (en) |
| DE (1) | DE59409725D1 (en) |
| ES (1) | ES2156888T3 (en) |
| RU (1) | RU94042915A (en) |
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| US4537185A (en) * | 1983-06-10 | 1985-08-27 | Denis P. Stednitz | Cannulated fixation screw |
| CH663347A5 (en) * | 1984-01-19 | 1987-12-15 | Synthes Ag | FIXATEUR FOR FIXING BONE PIECES. |
| DE3418490A1 (en) * | 1984-05-18 | 1985-11-21 | Aesculap-Werke Ag Vormals Jetter & Scheerer, 7200 Tuttlingen | Spiral drill for working on bones |
| DE3622676A1 (en) * | 1985-08-28 | 1987-03-12 | Werner Scholz | Surgical drill |
| CH671150A5 (en) * | 1986-10-13 | 1989-08-15 | Jaquet Orthopedie | |
| IL80705A0 (en) * | 1985-11-28 | 1987-02-27 | Jaquet Orthopedie | Transcutaneous pin for fixation of a bone part or fragment |
| US5098435A (en) * | 1990-11-21 | 1992-03-24 | Alphatec Manufacturing Inc. | Cannula |
| DE9017101U1 (en) * | 1990-12-19 | 1991-04-11 | Gerhard Hug Gmbh, 7801 Umkirch, De | |
| US5242447A (en) * | 1992-02-06 | 1993-09-07 | Howmedica Inc. | Pin with tapered root diameter |
| US5334204A (en) * | 1992-08-03 | 1994-08-02 | Ace Medical Company | Fixation screw |
-
1993
- 1993-12-07 CH CH03643/93A patent/CH688222A5/en not_active IP Right Cessation
-
1994
- 1994-11-15 US US08/340,905 patent/US6059785A/en not_active Expired - Lifetime
- 1994-11-21 ES ES94118274T patent/ES2156888T3/en not_active Expired - Lifetime
- 1994-11-21 DE DE59409725T patent/DE59409725D1/en not_active Expired - Lifetime
- 1994-11-21 AT AT94118274T patent/ATE200404T1/en active
- 1994-11-21 EP EP94118274A patent/EP0657142B1/en not_active Expired - Lifetime
- 1994-11-30 AU AU79105/94A patent/AU689140B2/en not_active Ceased
- 1994-12-06 CA CA002137393A patent/CA2137393C/en not_active Expired - Lifetime
- 1994-12-06 RU RU94042915/14A patent/RU94042915A/en unknown
- 1994-12-06 JP JP32979594A patent/JP3701995B2/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| EP0657142A1 (en) | 1995-06-14 |
| AU689140B2 (en) | 1998-03-26 |
| CA2137393A1 (en) | 1995-06-08 |
| AU7910594A (en) | 1995-06-15 |
| JPH07194631A (en) | 1995-08-01 |
| EP0657142B1 (en) | 2001-04-11 |
| ES2156888T3 (en) | 2001-08-01 |
| DE59409725D1 (en) | 2001-05-17 |
| ATE200404T1 (en) | 2001-04-15 |
| US6059785A (en) | 2000-05-09 |
| RU94042915A (en) | 1996-10-10 |
| CH688222A5 (en) | 1997-06-30 |
| JP3701995B2 (en) | 2005-10-05 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKEX | Expiry |
Effective date: 20141208 |