Source: https://patents.google.com/patent/JP4185361B2/en
Timestamp: 2020-01-18 06:20:46
Document Index: 770012979

Matched Legal Cases: ['Application No. 0856293', 'art 5', 'art 7', 'art 5', 'art 7', 'art 181', 'art 181', 'arts 183']

JP4185361B2 - Bone screw - Google Patents
JP4185361B2
JP4185361B2 JP2002557291A JP2002557291A JP4185361B2 JP 4185361 B2 JP4185361 B2 JP 4185361B2 JP 2002557291 A JP2002557291 A JP 2002557291A JP 2002557291 A JP2002557291 A JP 2002557291A JP 4185361 B2 JP4185361 B2 JP 4185361B2
JP2002557291A
JP2004528061A (en
イムラン タウヒード スィッディーキー
2002-01-17 Application filed by ジンテーズ ゲゼルシャフト ミト ベシュレンクテル ハフツング filed Critical ジンテーズ ゲゼルシャフト ミト ベシュレンクテル ハフツング
2004-09-16 Publication of JP2004528061A publication Critical patent/JP2004528061A/en
2008-11-26 Publication of JP4185361B2 publication Critical patent/JP4185361B2/en
The present invention relates to an implant for providing compression between different regions of matter. In particular, the present invention relates to a compression bone screw suitable for stabilizing broken bone.
The treatment of many bone disorders involves, for example, stabilizing the bone by applying compression between different regions of the bone, thereby bringing the regions together to promote healing. Typically, bone screws, such as those described in Augagneur US Pat. No. 6,001,101 (Patent Document 1) and Diebold et al. Published Patent Application EP 0 856 293 (Patent Document 2) , Compression was established using threaded sections with different pitches or leads. For example, the compression effect of Augagneur's screw device is that the movement of the distal portion is higher than the proximal portion, so that the proximal portion is pushed by an integral distal portion that provides compression. However, removal of known compression screws tend to produce Ri generally opposing force or polarization from the compression obtained during insertion (bias), which can destabilize regions of bone. Another disadvantage of the known compression screw is that it provides insufficient surface area or purchase to prevent bone withdrawal or damage at large lead lengths.
There is therefore a need for an improved bone screw.
US Pat. No. 6,001,101 European Patent Application No. 0856293
The present invention relates to an implant for insertion in a substance. The implant preferably includes a longitudinal axis, a proximal portion, and a distal portion. The proximal portion and the distal portion preferably have a proximal thread and a distal thread, respectively. If the shaft is the about the longitudinal axis is rotated in one direction a first region and a second region of the material was polarized et respect to each other that (in bias) apply a compressive therebetween, the proximal thread and the distal Preferably, the screw threads are shaped to be screwably engaged with the first and second spaced areas of the material, respectively. When the shaft is rotated in the opposite direction about its longitudinal axis, the proximal thread (to bias) polarized Selle first region between substantially suppressed to first and second regions that It is preferable to have a shape that substantially prevents the tension.
Preferably, at least a portion of the proximal thread is tapered. For example, the tapered portion of the proximal thread preferably forms an angle of at least about 20 degrees with respect to the longitudinal axis of the shaft. In a preferred embodiment, the tapered portion of the proximal thread disengages the proximal thread from the first region of material with less than about one-half rotation of the opposite shaft longitudinal axis.
In a preferred embodiment, the implant is a compression bone screw, and the first and second regions of material are the first and second regions of bone, respectively. In this embodiment, the graft is preferably shaped to stabilize the areas by providing compression between the bone areas, and after removal of the graft, the graft is destabilized in the bone area. Or it is made into the shape which suppresses distraction.
In another embodiment, the proximal thread and the distal thread form a proximal lead and a distal lead, respectively, and the distal lead is larger than the proximal thread. The proximal and distal portions are preferably substantially fixed relative to each other and are spaced apart by an intermediate portion.
The proximal portion of the implant preferably includes a proximal surface that forms a recessed area, which includes a drive structure therein for receiving a drive device.
The distal thread preferably forms a proximal surface and a distal surface to engage the surrounding material. The proximal and distal surfaces form a first angle and a second angle with respect to the longitudinal axis, respectively. The second angle is preferably smaller than the first angle.
In another embodiment, the invention includes a proximal portion having at least one thread shaped to be received within the first region of material, and at least three shaped and configured to be received within the second region of material. And a distal portion having a thread start (start start point). In relation to the insertion of the implant, it is preferred that the proximal and distal threads are threadably engaged with the first region and the second region, respectively, to provide compression therebetween. The distal thread preferably provides sufficient force to substantially prevent damage to the second region of material. In a preferred embodiment, the proximal portion includes at least two thread starts, more preferably at least three thread starts. In another preferred embodiment, the distal portion preferably includes at least four thread starts.
Preferred embodiments of the invention are described below in connection with the accompanying drawings. With reference to FIGS. 1-7, the implant 1 is contained within a substance having at least a first region and a second region, for example by positioning and / or fixing them relative to each other. It is preferable that the shape be stabilized. Implant, for example, by causing polarized et them relatively toward one another, it is preferably shaped to provide compression between the regions. Polarized rehabilitation, it is preferable that along the longitudinal axis 3 of implant 1 comprising providing a compressive force which tends to promote towards each other region. If the regions are fixed at least slightly relative to each other, for example, bone regions that are only partially separated due to incomplete breakage, the absolute movement or translation of the regions may be negligible, A compressive force that tends to stabilize will be established between them based on the placement of the implant 1. In some cases, the first region and the second region of material may be separated by at least a third region of material (which is preferably not screwably engaged by the implant 1). In these cases, it is preferred that the first region and the second region are related to the insertion of the implant 1 and the third region is compressed therebetween.
The present invention advantageously allows the insertion and removal of the implant 1 in brittle and / or fragile materials without causing material damage. Preferred materials for use according to the present invention include bone, masonry, stone, cement, calcined gypsum or plaster, etc., but the implant is suitable for use in any material capable of housing the implant.
In a preferred embodiment, the implant of the present invention is at least partially unintentional, such as by breakage or rupture, so that the opposite portion of the bone region is sufficiently adjacent to promote bone healing and / or stabilization. A compression bone screw shaped to provide compression between areas or pieces of bone to be stabilized. More preferably, the implant of the present invention is sized and shaped for insertion into a bone associated with the hand or wrist, such as a ship-like bone, or a bone associated with the foot or ankle. However, it should be understood that the present invention is also suitable for stabilizing other bones, such as long bones including femurs, tibias, or humerus. Therefore, the implant of the present invention may be formed from any biocompatible material, such as titanium, chromium alloys, and stainless steel. Any biodegradable and / or bioabsorbable material may also be used, such as calcium phosphate or hydroxyapatite.
In a preferred embodiment, the implant 1 comprises a shaft 2 having a proximal thread 5 and a proximal part 5 and a distal part 7 including distal threads 11a and 11b, respectively. Preferably, the proximal portion 5 includes at least a single thread start and the distal portion 7 includes at least two thread starts. The number of thread starts represents the number of thread forms of the preferably helical formed on the shaft. In the following, the distal threads 11a and 11b are represented by a common reference number 11. The pitch of the distal thread 11 is preferably the same as the pitch of the single proximal thread 9. The proximal portion 5 and the distal portion 7 are fixed with respect to each other, and the proximal thread 9 and the distal thread 11 are received in and threadably engaged with the first and second regions of material, respectively. It is preferred that they be separated by a distance sufficient to make it possible. However, it should be understood that the preferred distance separating the proximal portion 5 and the distal portion 7 depends on the size and spacing of the region of the material that receives the implant.
The shaft 2 of the graft 1 is interposed between the proximal part 5 and the distal part 7, spaced apart them, and in relation to the insertion of the graft 1, a first region and a second region of material. It is preferable to include an intermediate portion 25 shaped to bridge the gap. Intermediate portion 25 is shaped to allow the different regions of substantially prevented to substances that proximal portion 5 and a distal portion 7 is the same area and each engaging the material is polarized et against each other, and Preferably it is sized. Further, the intermediate portion 25 is substantially free to translate relative to the area around the material based on the insertion or removal graft 1 and / or rotating the intermediate portion 25 is added to Ri polarization around the material It is preferable to have a shape that substantially prevents this.
Referring to FIG. 1, the intermediate portion 25 includes a smooth region such as a cylinder 27 that does not include threads. Cylinder 27 may have an outer diameter that is smaller than the diameter of either proximal thread 9 or distal thread 11. Also, the intermediate portion 25 may be tapered, bent inward, or form any other shape that is shaped to facilitate translation and / or rotation of the intermediate portion 25 with respect to surrounding material. The intermediate portion 25 may also form a thread or thread-shaped region having a height or surface area that is insufficient to obtain a substantial increase or engagement with the surrounding material.
The shaft 2 may include a cannula insertion 47 that extends along the longitudinal axis 3 from the distal tip 31 to the proximal surface 37 of the implant 1. The distal tip 31 of the graft 1 includes a cutting element 33 that is shaped to cut material when the graft 1 is inserted. Further, the distal tip 31 may have a smooth tip shape such as a hemispherical tip.
The distal portion 7 preferably includes a self-cutting channel or groove 29 disposed proximal to the distal tip 31 to prepare the material for the distal thread 11 during insertion and cut the internal thread. Thus, in a preferred embodiment, the implant 1 is both self-drilling and self-tapping so that a leading hole having a depth greater than or equal to the length of the implant 1 is as described below. Is not required to insert. FIGS. 8 and 9 illustrate an embodiment of an implant 50 having a proximal portion 52 with a proximal cutting groove 35 for preparing bone for the proximal thread 9 during insertion and cutting an internal thread. Except for the proximal groove 35, the implant 50 is substantially similar to the implant 1. As will be appreciated by those skilled in the art, the penetration of proximal cutting groove 35 and distal cutting groove 29 as determined by the depth, angle, and number of grooves appears to be suitable for the properties of the material that will receive the implant. You may adjust it.
Returning to the embodiment of FIGS. 1-7, the proximal surface 37 of the graft 1 is centrally located, such as a slot or socket 39, to receive a drive tool for applying torque to the graft 1 during insertion and removal. A driven structure is formed. The socket 39 is preferably disposed within the concave hemispherical depression 41 so that the proximal or upper edge 43 of the socket is disposed below or distal to the rim 45 of the proximal surface 37. Thus, the rim 45 preferably forms the most proximal portion or end of the implant. In use, the hemispherical recess 41 advantageously guides the drive tool toward the socket 39 to prevent the drive tool from being laterally displaced by the surrounding material.
For example, in preparation for insertion of the implant 1 into a bone having a first region and a second region, it is preferred that a guide wire is placed in the bone along a predetermined insertion axis. If required, the cannulated cone and / or cannulated countersink guided by the guide wire should form a relatively shallow leading hole and a larger diameter concentric countersink in the bone fragment. It can then be used. In order to minimize material loss, the leading hole allows the cutting element 33 and groove 29 to engage the bone to prepare the bone for the distal thread 11 in relation to the rotation of the implant 1. Preferably it is only deep enough. Once the graft has reached a sufficient depth, the countersink allows the proximal cutting groove 35 (if included) to engage the bone to prepare the bone for the proximal thread 9. It is preferable to form a sufficient diameter.
Based on a continuous rotation of the implant 1 in a first orientation around the longitudinal axis 3, for example, clockwise, the threads 9 and 11 are threadably engaged with the first and second regions, respectively, so that the proximal portion 5 and the first region of bone are polarized et al in a first direction at a first rate relative to each other, polarized et distal portion 7 and a second region of the bone in a second direction at a second rate relative to one another Is done. In general, the proportion threaded element is engaged screwed freely engaged in the region of the material polarized et al to the area of the material, the longitudinal axis of the member area of the material is forced to translate based on one revolution of the threaded element , And is defined herein as the distance associated with the material. Proportion to polarization et a first region of the engaged material proximal threads 9 with respect to the second region of the implant 1 is engaged with the distal thread 11 material, multiplied by the pitch of the thread This corresponds to the difference in the number of proximal and distal thread starts.
It is preferred the first and second directions polarized Rino imparted by implant 1 are the same in an absolute sense. However, different to provide the desired compression between the polarization Rino proportion of proximal thread 9 and distal threads 11 and the first and second regions of material in relation to the rotation of the implant 1 Is preferred. The distal portion 7 have a number thread start is greater than the proximal portion 5 to the proximal portion 5 is polarized, et al to the second region of material at a greater rate than the rate to polarized et a first region of material Is preferred. Therefore, based on the insertion, discrimination polarized rehabilitation preferable to provide a compression of the amount sufficient to promote stabilization and healing to stabilize contact between the first region and a second region with respect to each other substances.
The proximal thread 9 and the distal thread 11 cause the thread 9, 11 to peel off, pull out, or otherwise damage the area in which the thread 1 is threadably engaged upon placement or removal of the implant 1. The shape is substantially prevented. “Substantially prevent” means that the implant 1 is inserted by applying a torque, for example, to a desired degree of compression without loss of force or engagement between the implant 1 and the substance. It means that it may be given between the area and the second area. In this way, damage to the threadably engaged material is substantially prevented so that the compression established during insertion of the implant 1 is substantially maintained after the insertion is complete.
The threads 9, 11 form at least about 1 full rotation around the implant 1, more preferably at least about 1.5 full rotations, between the threads 9, 11 and the surrounding material. It is preferable to increase the engagement. As best seen in FIG. 7, the proximal thread 9 includes a proximal face 14 and a distal face 16, which act to transmit forces between the thread 9 and the surrounding material. The proximal surface 14 and the distal surface 16 form angles 18 and 20 with respect to the longitudinal axis 3 of the implant 1, respectively. Angle 18 may be greater than angle 20 to provide a more effective transmission of force between the threads 9 of the implant 1 and the surrounding material during insertion to reduce damage to the surrounding material during compression. preferable.
FIG. 1 shows that the proximal face 22 and the distal face 24 of the distal thread 11 are shaped similarly to the proximal face 14 and the distal face 16 of the proximal thread 9. In order to further enhance the engagement of the distal thread 11 with the surrounding material, the root diameter 26 of the distal thread 11 may be smaller than the diameter 28 of the intermediate portion 25. Thus, because the outer diameter of the distal thread 11 is greater than the intermediate diameter 28, the proximal surface 22 and the distal surface 24 exhibit a greater surface area relative to the surrounding material.
For example, in relation to removal by applying torque to the implant 1 in a direction opposite to the torque applied during insertion, the implant 1 propels the first and second regions of material away from each other. is the Ri polarization that tends to a shape substantially eliminated. Such polarization Ri puts graft undesirably under compression, a first region and a second region placed under tension, which first and second regions are separated relative to each other, or destabilization Increase the tendency to become. The proximal thread 9 is preferably disengaged from the first region of material by less than about 1/2 rotation of the implant 1, more preferably less than 1/4 rotation. Outside and is meant to stop giving proximal thread 9 as rotation and removal progresses Ri polarized in a first region of material substantially. Thus, in a preferred embodiment, the graft 1 substantially prevents forces that tend to distract or destabilize the healed or stabilized bone, so that the compressed piece of bone becomes a part of the graft 1. It remains stabilized or adjacent after removal.
With reference to FIG. 1, the proximal thread 9 includes an outwardly tapered apex 13 having a proximal end 15 and a distal end 17. Proceeding along the apex 13 from the distal end 17 toward the proximal end 15, at least a portion of the apex 13 is generally outwardly tapered such that the proximal end 15 is distal end. A diameter greater than 17 is formed. It is preferred that all of the proximal threads are tapered. The outward taper of the proximal thread 9 is preferably sufficient to disengage from the surrounding material after removal as previously described. The apex 13 preferably includes at least two adjacent protrusions 19, 21 that form an angle 23 with respect to the longitudinal axis 3 of the shaft 2 of at least about 15 °, preferably at least about 20 °, more preferably at least about 25 °. Adjacent tips 19, 21 are preferably separated from one another by one full rotation of the thread 9 around the shaft 2. The position 21 is preferably separated from the distal end 17 by at least about one full rotation of the thread 9 around the shaft 2. The distal end 17 and the adjacent tip 20 of the thread crest 13 preferably form an angle of at least about 30 ° with respect to the longitudinal axis of the shaft 2.
The proximal thread 9 preferably extends far enough towards the proximal surface 37 into which the implant 1 can be inserted so as to prevent any protrusion of the implant 1 above the surface of the material. Thus, for example, the present invention can be inserted into a region, such as a joint, adjacent to a different bone without disturbing the relative motion of the bone.
With reference to FIGS. 6 a-6 c, the implant 1 has a first region 53 and a second region 55 associated with an unstable region, such as a fracture 57, and is illustrated for insertion into a ship-like bone 51. Shown in use. Prior to complete insertion of the implant 1, the breakage 57 typically separates the first region 53 and the second region 55 as shown in FIG. At this stage, the proximal and distal threads are threadably engaged with the first region 53 and the second region 55 of the ship-like bone 51, respectively. Polarized continuous rotation of implant 1 towards the first region 53 and second region 55 each other Selle. The graft 1 can be applied to the hull 51 to a depth sufficient to stabilize the unstable region, for example by providing sufficient compression and substantially closing the fracture 57, as shown in FIG. 6b. Inserted. Substantial sealing of the breakage 57 provides the adjacent region 59 where the first region 53 and the second region 55 are located sufficiently close to facilitate stabilization, for example, by healing or adhesion of the breakage 57. FIG. 6 c shows the graft in a partially removed state, where the proximal thread 9 is removed from the first region 53 of the ship-like bone 51 leaving a gap 58 therebetween, and the proximal thread 9 is to prevent giving Ri polarized to a region 53. Therefore, after complete removal, the first region 53 and the second region 55 will remain stably adjacent.
A second embodiment of the implant 100 shown in FIG. 10 includes a proximal portion 102 and a distal portion 106. Proximal portion 102 and distal portion 106 include a single proximal thread form 104 and a single distal thread form 108. Proximal threads 104 of the implant 100 is preferably formed a sufficient outward taper to prevent Ri undesired polarization based on removed as previously described.
The proximal portion 102 and the distal portion 106 of the implant 100 are shaped as described above to be received and compressed or tensioned within the first and second regions of material, respectively. However, since the proximal portion 102 and the distal portion 106 each have only a single thread start, the pitch of the proximal thread 104 is preferably different from the pitch of the distal thread 108, so that Proximal portion 102 is propelled to travel at a different speed than distal portion 106 relative to the surrounding material in relation to rotation of implant 100. The pitch of the distal thread 108 is preferably greater than the pitch of the proximal thread 104 to provide compression based on the insertion of the implant 100. The implant 100 preferably includes features substantially similar to those described above for the implant 1 except that the implant 100 includes only a single distal thread 108 start.
A third embodiment of the implant 150 shown in FIG. 11 includes a proximal portion 152 and a distal portion 154. The distal portion 154 of the graft 150 is sufficient to prevent damage to the surrounding material and to increase the engagement and augmentation of the distal thread with the surrounding material to maintain compression after placement of the graft 150. Preferably, it includes a number of distal thread starts. The distal portion 154 preferably includes at least three distal thread forms 158a-158c having at least three thread starts, more preferably at least four thread starts. The proximal thread 156 of the proximal portion 152 preferably includes at least one proximal thread start. Implant 150 may also include features similar to those described above, for example, a proximal taper, an intermediate portion, and a cutting groove.
In addition to providing greater boost with the surrounding material, the inclusion of additional threads in the proximal and distal portions allows greater accuracy and choice when choosing the degree of compression for a given application To. For example, Table 1 shows the absolute compression (unit: mm) obtained for an implant having a proximal and distal thread pitch of 0.25 mm, and Table 2 shows 0.67 mm proximal and distal screws. Figure 3 shows the absolute compression obtained for an implant with a crest pitch. Here, absolute compression is defined as the distance translated by the proximal portion minus the distance translated by the distal portion based on one rotation of the implant. Therefore, absolute compression is the separation of the freely translating region of the material engaged with the proximal portion relative to the second freely translating region of the material engaged with the distal portion based on one complete rotation of the implant. This corresponds to the relative change in distance.
The positive values in Tables 1 and 2 indicate the combination of proximal and distal thread start where compression is obtained based on graft insertion, while the negative value indicates tension is graft insertion. The region that occurs based on By changing the number of distal and proximal thread starts, compression can be varied. For example, referring to Table 2, an implant with three distal thread starts with a pitch of 0.67 mm and two proximal thread starts has an absolute compression of 0.67 mm for each rotation of the implant. give. FIG. 12 shows an implementation of an implant 175 having a proximal portion 177 including a first proximal thread start 181a and a second proximal thread start 181b and a distal portion 179 including three distal thread starts 183a-183c. The form is shown. The embodiment of FIG. 12 will obtain and maintain a sufficient amount of compression and provide a significantly greater boost than an implant with fewer threads. Thus, according to the present invention, the implant may include 1-7 distal threads and 1-6 proximal threads shaped to provide compression.
It will be appreciated that those skilled in the art can devise many improvements and embodiments. The claims are intended to cover all such modifications and embodiments that fall within the true spirit and scope of the invention. For example, the implant, for example, by causing polarized et away based on regions of a substance to the insertion of the implant may be shaped to provide tension between the regions of the material. In this case, the graft may be shaped to prevent compression of the spaced area based on removal of the graft.
It is a side view of 1st embodiment of the graft of this invention. FIG. 2 is a distal end view of the implant shown in FIG. FIG. 2 is a proximal end view of the implant shown in FIG. 1. FIG. 2 is a distal perspective view of the implant shown in FIG. 1. FIG. 2 is a proximal perspective view of the implant shown in FIG. 1. FIG. 2 shows a cross-sectional side view of a graft implanted in a partially inserted ship-like bone. FIG. 2 shows a cross-sectional side view of a graft implanted in a fully inserted ship-like bone. FIG. 6 shows a cross-sectional side view of a graft implanted in a ship-like bone with partial removal. FIG. 2 shows a partial side view of the implant shown in FIG. 1 including a proximal partial cut section. It is a side view of 2nd embodiment of the graft of this invention. FIG. 9 is a distal end view of the implant shown in FIG. 8. FIG. 6 shows a side view of a third embodiment of the implant of the present invention. It is a side view of 4th embodiment of the graft of this invention. It is a side view of 5th embodiment of the graft of this invention.
An implant for insertion in a substance,
The implant includes a shaft including a longitudinal axis, a proximal portion, and a distal portion, the proximal portion and the distal portion having a proximal thread and a distal thread, respectively;
When the shaft is rotated in one direction about its longitudinal axis to bias the first and second regions of material relative to each other to provide compression therebetween, the proximal and distal threads are The proximal thread is configured to threadably engage the first and second spaced regions of the material, respectively, and the shaft rotates in an opposite direction about its longitudinal axis. In an implant configured to substantially prevent tension between the first region and the second region ,
At least a portion of the proximal thread is tapered; and
A) the tapered portion of the proximal thread forms an angle of at least 20 degrees with respect to the longitudinal axis of the shaft;
B) The implant wherein the tapered portion of the proximal thread disengages the proximal thread from the first region of material with a rotation of less than about half of the longitudinal axis of the shaft. .
The implant of claim 1, wherein the proximal thread and the distal thread have the same pitch.
The implant of claim 1, wherein the proximal thread and the distal thread have different pitches.
4. Implant according to any one of claims 1 to 3, characterized in that the proximal thread is tapered.
5. The implant of any one of claims 1 to 4, further comprising an intermediate portion disposed between and spaced from the proximal portion and the distal portion .
The implant is a compression bone screw, and the first and second regions of material are the first and second regions of bone, respectively, and when the implant is inserted, the implant Is shaped to stabilize the bone region by applying compression between them, and when the graft is removed, the graft is shaped to inhibit destabilization of the bone region. The implant according to any one of claims 1 to 5, characterized in that
Wherein comprises at least two distal thread starts the distal portion, according to any one of claims 1 to 6, wherein the distal threads and forming a larger lead the proximal threads Graft.
8. The implant of any one of claims 1 to 7, wherein the proximal portion and the distal portion are substantially fixed relative to each other .
9. The implant of any one of claims 1 to 8, wherein the proximal portion includes a proximal surface, and the proximal surface includes a recessed region forming a drive structure therein .
The distal thread forms a proximal surface and a distal surface, the proximal surface forms a first angle relative to the longitudinal axis, and the distal surface is a second, smaller angle relative to the longitudinal axis. The implant according to any one of claims 1 to 9, characterized in that
An implant for insertion in a substance ,
A) the proximal thread has at least one thread start;
B) the distal thread has at least three thread starts;
C) In insertion of the graft by rotation, the proximal thread and the distal thread are threadably engaged with the first region and the second region, respectively, to provide compression therebetween, 11. Implant according to any one of the preceding claims, characterized in that the distal thread provides sufficient force to substantially prevent damage to the second region of material .
12. An implant according to any one of the preceding claims, wherein the proximal portion includes at least two threaded starts .
13. Implant according to any one of the preceding claims, wherein the proximal portion comprises at least three thread starts .
14. The implant of any one of claims 1 to 13, wherein the distal portion includes at least four threaded starts .
The implant forms a longitudinal axis, the distal thread forms a proximal surface and a distal surface, the proximal surface forms a first angle with respect to the longitudinal axis, and the distal surface; 15. The implant according to any one of the preceding claims , wherein forms a second, smaller angle with respect to the longitudinal axis .
JP2002557291A 2001-01-17 2002-01-17 Bone screw Expired - Fee Related JP4185361B2 (en)
JP2004528061A JP2004528061A (en) 2004-09-16
JP4185361B2 true JP4185361B2 (en) 2008-11-26
JP2002557291A Expired - Fee Related JP4185361B2 (en) 2001-01-17 2002-01-17 Bone screw
DK1105058T3 (en) * 1998-08-21 2002-10-14 Synthes Ag Tapping hulcylinderisk bone anchoring element
EP2370004A1 (en) * 2008-12-09 2011-10-05 Mazor Surgical Technologies Ltd. Double threaded orthopedic screw
WO2018195377A1 (en) * 2017-04-21 2018-10-25 DePuy Synthes Products, Inc. Angled flutes in cannulated bone screws
NO20033221D0 (en) 2003-07-16