CA2531541C - Surgical nail - Google Patents
Surgical nail Download PDFInfo
- Publication number
- CA2531541C CA2531541C CA2531541A CA2531541A CA2531541C CA 2531541 C CA2531541 C CA 2531541C CA 2531541 A CA2531541 A CA 2531541A CA 2531541 A CA2531541 A CA 2531541A CA 2531541 C CA2531541 C CA 2531541C
- Authority
- CA
- Canada
- Prior art keywords
- insert
- transverse bore
- nail
- transverse
- bore
- 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 - Fee Related
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
- A61B17/72—Intramedullary pins, nails or other devices
-
- 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
- A61B17/72—Intramedullary pins, nails or other devices
- A61B17/7233—Intramedullary pins, nails or other devices with special means of locking the nail to the bone
- A61B17/7241—Intramedullary pins, nails or other devices with special means of locking the nail to the bone the nail having separate elements through which screws pass
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00004—(bio)absorbable, (bio)resorbable, resorptive
Abstract
The invention relates to a surgical nail (1), in the form of an intramedullary nail with a central axis (2), consisting of a material M having a tensile strength F z, compression strength F d, density p2 and modulus of elasticity E. Said nail has a transverse bore (3) extending transversely to the central axis (2) and has a cross-sectional profile F and a transverse axis (4), the transverse cross-sectional profile F having a maximum length a in the direction of the central axis and a maximum width b that runs perpendicular to the length. An insert (10) with a longitudinal axis (13), made from material m and having a modulus of elasticity e that is smaller than the modulus of elasticity E of material M, can be introduced into the transverse bore (3). In addition, the insert (10) has a length L in the direction of the longitudinal axis (13) that satisfies the condition L > 0.2 D.
Description
12.6.2003 CA 02531541 2006-O1-05 English translation of the International Patent Application No. PCT/CH03/00376 "Surgical Nail" in the name of Synthes AG Chur Surgical Nail The invention concerns a surgical nail, in particular an intramedullary nail according to the preamble of patent claim 1.
The locking of intramedullary nails is state-of-the-art. The introduction of locking screws or locking bolts (in the following only the term locking screw will be used that, however, includes also the term locking bolt) into the transverse bores of a intramedullary nail is carried out either with the aid of an imaging process (X-ray control) or a more or less complicated aiming device. A certain aiming accuracy cannot be avoided in either cases, i.e. the tip of the screw cannot be exactly aligned coaxially with the central axis of the transverse bore, rather it deviates from it by a certain amount. So that the locking screw would enter into the transverse bore despite this aiming error and could pass through it, the outside diameter of the screw is so dimensioned, that it will be below that of the diameter of the transverse bore. If the aiming accuracy remains within the limit of this underdimensioning, the locking screw can be guided, despite the aiming error, through the transverse bore without any problem. In any case, as a result of the underdimensioning, the locking screw has a certain clearance relative to the transverse bore..
This clearance defines as to what extent the main bone fragments, fixed by means of locking screws in the corresponding locking hole, can move relative to the nail and thus due to the rigidity of the nail also relative to the other main bone fragments, fastened with the same nail. To guarantee the usefulness of the locking for the surgeons, while this play is essential, in the case of some indications (e.g. in the case of metaphysial fragments) it is clinically undesirable.
Even nails with a solid cross-section, that may have an internal thread in the locking hole, are not without clearance. The internal thread merely prevents the axial displacement of the nail on the locking screw.
'2 From US 6,296,645 Hover et al., a hollow, intramedullary nail from metal is known, that in the diametrally opposed openings on the jacket of the transverse bore, described as windows, has one or two plastic inserts, through which the locking screw can be introduced. A disadvantage of this known intramedullary nail is that the window-like plastic inserts can be easily pushed in, so that its desired function is lost. Even with a careful manipulation the two plastic inserts can be pushed out from their "windows", what also leads to a loss of the function.
This is where the invention wants to provide remedy. The object of the invention is to produce a surgical nail, in particular an intramedullary nail, with which the clearance between it and the locking screw can be eliminated without any risk and an improved holding force as well as an improved guiding can be achieved between the locking screw and the intramedullary nail.
The invention achieves the objective stated with a surgical nail having the features of claim 1.
The following advantages can be achieved with it:
a) the aiming accuracy during the insertion of the locking screw is unimpaired,;
b) the doctor is in the position to decide during the operation whether he uses an angularly stable locking of the locking screw or not, while the term "angularly stable" stands for a certain limitation of the degree of freedom;
c) the feasibility of an angularly stable fixing of the bone fragments in certain directions for a certain amount of the load; and d) the nail and the insert can be packed separately in a sterile manner and the surgeon can choose whether he uses the nail without or with the insert. In the latter case the surgeon himself can insert the insert into the nail and, if necessary, remove it. If the surgeon uses the nail without an insert, it remains in the sterile package for the next occasion.
In the case of a particular embodiment the length L of the insert satisfies the condition L > 0.5 D and preferably L = D.
In the case of a further embodiment the insert is basically congruent with the transverse bore.
In the case of a particular embodiment the insert can have a bore that is coaxial with its longitudinal axis so that to facilitate the introduction of the locking screw.
The material m of the insert has a tensile strength fZ < FZ, a compression strength fd < Fd and modulus of elasticity a < 0.8 E, preferably a < 0.7 E.
In an embodiment the material m of the insert is a biocompatible material, preferably a polyethylene or a high-molecular polyethylene (HMWPE), that has the advantage, that the synthetic material will not disintegrate into unknown decomposing products.
According to a preferred development the insert is made from a material of lesser hardness, a bioabsorbable polymer, preferably a polylactide. The result of this execution is an initial clearance-free transverse locking of the intramedullary nail, that with the increasing absorption of the polymer is successively discontinued, so that the transverse locking screws will become again mobile relative to the intramedullary nail and consequently also the bone fragments involved. Thus following the consolidation of the fracture a dynamisation of the bone fragments takes place. The bioabsorbable material has the advantage that the splinters caused by screwing in the locking screw into the nail can be decomposed by the body. A further advantage is the possibility to realise, as time passes, a different strength of the angularly stable locking of the locking screw, i.e. to achieve a gradual reduction of the holding force.
The transverse bore of the intramedullary nail can be either a circular bore, whereby the cross-section F has the maximum lengths a = b (i.e. a = b is the diameter of the transverse bore), or a slotted hole, whereby the cross-section F
has the maximum lengths a > b.
The material m of the insert has preferably a lower density p, than the material M
with density p2, while preferably p~ < 0.8 p2.
j4 The locking screws or locking bolts, that can be passed through the insert, should preferably have a shaft with a diameter of d (maximum diameter that includes a possible external thread), that satisfies the condition a > d < b. At the same time the diameter d of the external thread should preferably be at feast 5% smaller than the smaller of the two dimensions a, b.
In the case of a special execution the transverse bore expands towards the surface of the nail, preferably in the form of a tapered section. The advantage of this is that an insert having a corresponding tapered section that is inserted into it cannot be axially displaced in the direction of insertion.
The invention and developments of the invention are explained in detail based on the partially schematic illustrations of several embodiments.
They show in:
Fig.1 - a perspective view of a intramedullary nail with a continuous cannula with a transverse bore and an insert fitting it as well as a transverse locking screw, Fig.2 - a longitudinal section through the intramedullary nail according to Fig.1, Fig.3 - a longitudinal section through the intramedulfary nail according to Fig.1, rotated by 90°, Fig.4 - an enlarged schematic view of the section of the transverse bore of the intramedullary nail according to Fig.1, Fig.5 - a single-piece insert with a longitudinal bore for the transverse bore in the intramedullary nail, that after insertion is approximately aligned with the nail's cannula, ' ' " 5 Fig.6 - a partial longitudinal section through a further, modified intramedullary nail with a modified single-piece insert, and Fig.7 - a partial longitudinal section through a further, modified intramedullary nail with a modified single-piece insert.
The surgical nail 1 illustrated in Figs.1-3 is an intramedullary nail for hollow bones with a central axis 2, that is made from a metal or a metal alloy, i.e. a material with relatively high strength (tensile strength FZ, compression strength Fd and modules of elasticity E). The nail 1 has a transverse bore 3, having a transverse axis 4 and extending as a slotted hole with the cross-section F towards the central axis 2. As illustrated in Fig:4, the transverse bore 3 has a cross-section F, that has its maximum length a in the direction of the central axis 2 and right angle to it the maximum width b. The nail can have further, not illustrated, transverse bores (circular or oval).
As illustrated in Fig.1, an insert 10 is provided to be introduced into the transverse bore 3. The dimensions of the insert 10 are congruent with that of the transverse bore 3 or are so chosen that its insertion results in a press fit, thus preventing the falling out of the insert from the transverse bore 3. The insert 10 is made from a material m with lesser strength, in particularly with a lower E modules (when compared with the material M of the intramedullary nail).
As illustrated in Fig.S, the insert 10 can have a longitudinal bore 14 that is coaxial with its longitudinal axis 13 and a transverse bore 24, that after its insertion into the intrameduflary nail at right angle, corresponds with the nail's cannula.
In Fig.6 a version of the single-piece insert 10 is illustrated that comprises a pin 17 with a tapered expanding head 18.
In Fig.7 a further version of a single-piece insert 10 is illustrated, that comprises a pin 19 with a bore centrally passing through it as well as a plurality of tapered expansions 20 provided on the circumference, that in the form of a click lock can ~6 engage corresponding cavities 21 or the longitudinal bore 23 in the region of the transverse bore 3.
The locking of intramedullary nails is state-of-the-art. The introduction of locking screws or locking bolts (in the following only the term locking screw will be used that, however, includes also the term locking bolt) into the transverse bores of a intramedullary nail is carried out either with the aid of an imaging process (X-ray control) or a more or less complicated aiming device. A certain aiming accuracy cannot be avoided in either cases, i.e. the tip of the screw cannot be exactly aligned coaxially with the central axis of the transverse bore, rather it deviates from it by a certain amount. So that the locking screw would enter into the transverse bore despite this aiming error and could pass through it, the outside diameter of the screw is so dimensioned, that it will be below that of the diameter of the transverse bore. If the aiming accuracy remains within the limit of this underdimensioning, the locking screw can be guided, despite the aiming error, through the transverse bore without any problem. In any case, as a result of the underdimensioning, the locking screw has a certain clearance relative to the transverse bore..
This clearance defines as to what extent the main bone fragments, fixed by means of locking screws in the corresponding locking hole, can move relative to the nail and thus due to the rigidity of the nail also relative to the other main bone fragments, fastened with the same nail. To guarantee the usefulness of the locking for the surgeons, while this play is essential, in the case of some indications (e.g. in the case of metaphysial fragments) it is clinically undesirable.
Even nails with a solid cross-section, that may have an internal thread in the locking hole, are not without clearance. The internal thread merely prevents the axial displacement of the nail on the locking screw.
'2 From US 6,296,645 Hover et al., a hollow, intramedullary nail from metal is known, that in the diametrally opposed openings on the jacket of the transverse bore, described as windows, has one or two plastic inserts, through which the locking screw can be introduced. A disadvantage of this known intramedullary nail is that the window-like plastic inserts can be easily pushed in, so that its desired function is lost. Even with a careful manipulation the two plastic inserts can be pushed out from their "windows", what also leads to a loss of the function.
This is where the invention wants to provide remedy. The object of the invention is to produce a surgical nail, in particular an intramedullary nail, with which the clearance between it and the locking screw can be eliminated without any risk and an improved holding force as well as an improved guiding can be achieved between the locking screw and the intramedullary nail.
The invention achieves the objective stated with a surgical nail having the features of claim 1.
The following advantages can be achieved with it:
a) the aiming accuracy during the insertion of the locking screw is unimpaired,;
b) the doctor is in the position to decide during the operation whether he uses an angularly stable locking of the locking screw or not, while the term "angularly stable" stands for a certain limitation of the degree of freedom;
c) the feasibility of an angularly stable fixing of the bone fragments in certain directions for a certain amount of the load; and d) the nail and the insert can be packed separately in a sterile manner and the surgeon can choose whether he uses the nail without or with the insert. In the latter case the surgeon himself can insert the insert into the nail and, if necessary, remove it. If the surgeon uses the nail without an insert, it remains in the sterile package for the next occasion.
In the case of a particular embodiment the length L of the insert satisfies the condition L > 0.5 D and preferably L = D.
In the case of a further embodiment the insert is basically congruent with the transverse bore.
In the case of a particular embodiment the insert can have a bore that is coaxial with its longitudinal axis so that to facilitate the introduction of the locking screw.
The material m of the insert has a tensile strength fZ < FZ, a compression strength fd < Fd and modulus of elasticity a < 0.8 E, preferably a < 0.7 E.
In an embodiment the material m of the insert is a biocompatible material, preferably a polyethylene or a high-molecular polyethylene (HMWPE), that has the advantage, that the synthetic material will not disintegrate into unknown decomposing products.
According to a preferred development the insert is made from a material of lesser hardness, a bioabsorbable polymer, preferably a polylactide. The result of this execution is an initial clearance-free transverse locking of the intramedullary nail, that with the increasing absorption of the polymer is successively discontinued, so that the transverse locking screws will become again mobile relative to the intramedullary nail and consequently also the bone fragments involved. Thus following the consolidation of the fracture a dynamisation of the bone fragments takes place. The bioabsorbable material has the advantage that the splinters caused by screwing in the locking screw into the nail can be decomposed by the body. A further advantage is the possibility to realise, as time passes, a different strength of the angularly stable locking of the locking screw, i.e. to achieve a gradual reduction of the holding force.
The transverse bore of the intramedullary nail can be either a circular bore, whereby the cross-section F has the maximum lengths a = b (i.e. a = b is the diameter of the transverse bore), or a slotted hole, whereby the cross-section F
has the maximum lengths a > b.
The material m of the insert has preferably a lower density p, than the material M
with density p2, while preferably p~ < 0.8 p2.
j4 The locking screws or locking bolts, that can be passed through the insert, should preferably have a shaft with a diameter of d (maximum diameter that includes a possible external thread), that satisfies the condition a > d < b. At the same time the diameter d of the external thread should preferably be at feast 5% smaller than the smaller of the two dimensions a, b.
In the case of a special execution the transverse bore expands towards the surface of the nail, preferably in the form of a tapered section. The advantage of this is that an insert having a corresponding tapered section that is inserted into it cannot be axially displaced in the direction of insertion.
The invention and developments of the invention are explained in detail based on the partially schematic illustrations of several embodiments.
They show in:
Fig.1 - a perspective view of a intramedullary nail with a continuous cannula with a transverse bore and an insert fitting it as well as a transverse locking screw, Fig.2 - a longitudinal section through the intramedullary nail according to Fig.1, Fig.3 - a longitudinal section through the intramedulfary nail according to Fig.1, rotated by 90°, Fig.4 - an enlarged schematic view of the section of the transverse bore of the intramedullary nail according to Fig.1, Fig.5 - a single-piece insert with a longitudinal bore for the transverse bore in the intramedullary nail, that after insertion is approximately aligned with the nail's cannula, ' ' " 5 Fig.6 - a partial longitudinal section through a further, modified intramedullary nail with a modified single-piece insert, and Fig.7 - a partial longitudinal section through a further, modified intramedullary nail with a modified single-piece insert.
The surgical nail 1 illustrated in Figs.1-3 is an intramedullary nail for hollow bones with a central axis 2, that is made from a metal or a metal alloy, i.e. a material with relatively high strength (tensile strength FZ, compression strength Fd and modules of elasticity E). The nail 1 has a transverse bore 3, having a transverse axis 4 and extending as a slotted hole with the cross-section F towards the central axis 2. As illustrated in Fig:4, the transverse bore 3 has a cross-section F, that has its maximum length a in the direction of the central axis 2 and right angle to it the maximum width b. The nail can have further, not illustrated, transverse bores (circular or oval).
As illustrated in Fig.1, an insert 10 is provided to be introduced into the transverse bore 3. The dimensions of the insert 10 are congruent with that of the transverse bore 3 or are so chosen that its insertion results in a press fit, thus preventing the falling out of the insert from the transverse bore 3. The insert 10 is made from a material m with lesser strength, in particularly with a lower E modules (when compared with the material M of the intramedullary nail).
As illustrated in Fig.S, the insert 10 can have a longitudinal bore 14 that is coaxial with its longitudinal axis 13 and a transverse bore 24, that after its insertion into the intrameduflary nail at right angle, corresponds with the nail's cannula.
In Fig.6 a version of the single-piece insert 10 is illustrated that comprises a pin 17 with a tapered expanding head 18.
In Fig.7 a further version of a single-piece insert 10 is illustrated, that comprises a pin 19 with a bore centrally passing through it as well as a plurality of tapered expansions 20 provided on the circumference, that in the form of a click lock can ~6 engage corresponding cavities 21 or the longitudinal bore 23 in the region of the transverse bore 3.
Claims (16)
1. An intramedullary nail comprising:
an elongate body having a longitudinal central axis and formed of a material M
having a tensile strength F z, compressive strength F d, density .rho.2 and modulus of elasticity E;
at least one transverse bore extending transversely to the central axis, the transverse bore having a cross-section F and a transverse axis;
an insert formed of a bioabsorbable material configured and dimensioned for insertion into the transverse bore, the insert having a longitudinal axis and a plurality of projections provided on an outer surface of the insert for engaging the nail body adjacent to the transverse bore and holding the insert in position within the transverse bore, the insert including a central bore coaxial with the transverse axis.
an elongate body having a longitudinal central axis and formed of a material M
having a tensile strength F z, compressive strength F d, density .rho.2 and modulus of elasticity E;
at least one transverse bore extending transversely to the central axis, the transverse bore having a cross-section F and a transverse axis;
an insert formed of a bioabsorbable material configured and dimensioned for insertion into the transverse bore, the insert having a longitudinal axis and a plurality of projections provided on an outer surface of the insert for engaging the nail body adjacent to the transverse bore and holding the insert in position within the transverse bore, the insert including a central bore coaxial with the transverse axis.
2. The device of claim 1, wherein the insert is formed of a material m having a modulus of elasticity e<E.
3. The device of claim 1, wherein the transverse cross-section F of the transverse bore has a maximum length a in the direction of the central axis and a maximum width b perpendicular to the length a, the intramedullary nail has a diameter D at the transverse bore, and the insert has a length L in the direction of its longitudinal axis that satisfies the condition L>0.2 D.
4. The device of claim 3, wherein the insert has a length L>0.5 D.
5. The device of claim 1, wherein the insert has substantially the same shape as the transverse bore.
6. The device of claim 2, wherein the modulus of elasticity of the insert, e<0.8 E.
7. The device of claim 2, wherein the material m has a tensile strength f z<F
z.
z.
8. The device of claim 2, wherein the material m has a compressive strength f d<F d.
9. The device of claim 1, wherein the bioabsorbable material includes one of a polyethylene, a high-molecular polyethylene (HMWPE), and another biocompatible synthetic material.
10. The device of claim 1, wherein the bioabsorbable material is one of a polymer and a copolymer.
11. The device of claim 3, wherein the transverse bore in the nail has a substantially circular cross-section F, with maximum lengths a=b.
12. The device of claim 3, wherein the transverse bore in the nail has a substantially slotted cross-section F, where the maximum length a>b.
13. The device of claim 2, wherein the density .rho.1 of material m is less than the density .rho.2 of material M.
14. The device of claim 1, further comprising a locking screw adapted for insertion through the insert in the transverse bore, the locking screw having a shaft with an outer diameter d satisfying the conditions a>d<b.
15. The device of claim 1, wherein the nail has an outer surface adjacent the transverse bore, and the transverse bore expands towards the outer surface of the nail to form a depression in the outer surface of the nail.
16. The device of claim 1, wherein the insert is a pin having a tapered expanded head.
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| PCT/CH2003/000376 WO2004110291A1 (en) | 2003-06-12 | 2003-06-12 | Surgical nail |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2531541A1 CA2531541A1 (en) | 2004-12-23 |
| CA2531541C true CA2531541C (en) | 2011-05-10 |
Family
ID=33546137
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2531541A Expired - Fee Related CA2531541C (en) | 2003-06-12 | 2003-06-12 | Surgical nail |
Country Status (15)
| Country | Link |
|---|---|
| US (1) | US9737347B2 (en) |
| EP (1) | EP1631206B1 (en) |
| JP (1) | JP4357478B2 (en) |
| CN (1) | CN100457058C (en) |
| AR (1) | AR044330A1 (en) |
| AT (1) | ATE375125T1 (en) |
| AU (1) | AU2003232567B2 (en) |
| BR (1) | BR0318327B1 (en) |
| CA (1) | CA2531541C (en) |
| CL (1) | CL2004000867A1 (en) |
| DE (1) | DE50308380D1 (en) |
| ES (1) | ES2294372T3 (en) |
| NZ (1) | NZ544074A (en) |
| TW (1) | TWI323169B (en) |
| WO (1) | WO2004110291A1 (en) |
Families Citing this family (32)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE20300987U1 (en) | 2003-01-23 | 2003-04-10 | Stryker Trauma Gmbh | Implant for osteosynthesis |
| WO2004071356A2 (en) * | 2003-02-10 | 2004-08-26 | Smith & Nephew, Inc. | Resorbable devices |
| WO2004078049A1 (en) * | 2003-03-07 | 2004-09-16 | Synthes Ag Chur | Locking screw for an intramedullary nail |
| BRPI0318150B8 (en) * | 2003-03-21 | 2021-06-22 | Synthes Ag | intramedullary claw |
| DE50312960D1 (en) * | 2003-06-12 | 2010-09-16 | Synthes Gmbh | SURGICAL NAIL |
| ATE418923T1 (en) * | 2003-07-30 | 2009-01-15 | Synthes Gmbh | SURGICAL NAIL |
| CN100479775C (en) * | 2003-08-29 | 2009-04-22 | 斯恩蒂斯有限公司 | Intramedullary nail |
| NZ546545A (en) * | 2003-10-21 | 2008-11-28 | Synthes Gmbh | Intramedullary nail |
| GB0329654D0 (en) | 2003-12-23 | 2004-01-28 | Smith & Nephew | Tunable segmented polyacetal |
| AU2004320725A1 (en) * | 2004-06-22 | 2005-12-29 | Synthes Gmbh | Intramedullary nail |
| CA2571672C (en) * | 2004-06-24 | 2012-08-28 | Synthes (U.S.A.) | Intramedullary nail |
| US8066706B2 (en) * | 2004-06-30 | 2011-11-29 | Synthes Usa, Llc | Surgical nail |
| WO2007020432A2 (en) * | 2005-08-18 | 2007-02-22 | Smith & Nephew, Plc | High strength devices and composites |
| US9005201B2 (en) | 2006-04-06 | 2015-04-14 | Halifax Biomedical Inc. | Intramedullary rod with vent |
| CA2679365C (en) | 2006-11-30 | 2016-05-03 | Smith & Nephew, Inc. | Fiber reinforced composite material |
| JP5416090B2 (en) | 2007-04-18 | 2014-02-12 | スミス アンド ネフュー ピーエルシー | Expansion molding of shape memory polymer |
| US9770534B2 (en) | 2007-04-19 | 2017-09-26 | Smith & Nephew, Inc. | Graft fixation |
| EP2142227B1 (en) | 2007-04-19 | 2012-02-29 | Smith & Nephew, Inc. | Multi-modal shape memory polymers |
| EP2142122A1 (en) * | 2007-04-27 | 2010-01-13 | Synthes GmbH | Implant devices constructed with metallic and polymeric components |
| CN101677831B (en) | 2007-05-25 | 2011-07-20 | 齐默尔有限公司 | Reinforced intramedullary nail |
| US8668695B2 (en) | 2008-10-15 | 2014-03-11 | Zimmer Gmbh | Intramedullary nail |
| FR2968373B1 (en) * | 2010-12-07 | 2013-01-04 | Skf Ab | BEARING FOR TILT ROLLING DEVICE AND TENDERING GAUGE |
| US20130053847A1 (en) | 2011-08-31 | 2013-02-28 | Mark Siravo | Implant Devices Constructed with Metallic and Polymeric Components |
| KR101415316B1 (en) | 2012-06-01 | 2014-07-04 | 유앤아이 주식회사 | A wire-type nail assembly |
| DE102013005414A1 (en) * | 2013-03-28 | 2014-10-02 | Dietmar Wolter | Osteosynthesis system for the multidirectional, angularly stable treatment of fractures of long bones including an intramedullary nail and bone screws |
| US9526542B2 (en) | 2014-05-07 | 2016-12-27 | Acumed Llc | Hip fixation with load-controlled dynamization |
| US10080596B2 (en) | 2013-12-09 | 2018-09-25 | Acumed Llc | Hip fixation with load-controlled dynamization |
| US9463055B2 (en) | 2013-12-09 | 2016-10-11 | Acumed Llc | Plate-based compliant hip fixation system |
| ES2805053T3 (en) | 2013-12-09 | 2021-02-10 | Acumed Llc | Nail-based elastic hip fixation system |
| US9433451B2 (en) | 2013-12-09 | 2016-09-06 | Acumed Llc | Hip fixation system with a compliant fixation element |
| EP3740145A1 (en) | 2018-01-15 | 2020-11-25 | GLW, Inc. | Hybrid intramedullary rods |
| US11617604B2 (en) | 2020-04-15 | 2023-04-04 | DePuy Synthes Products, Inc. | Intramedullary nail assembly |
Family Cites Families (92)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US2834342A (en) | 1956-08-29 | 1958-05-13 | Clyde E Yost | Surgical device for the fixation of fractured bones |
| US3112743A (en) | 1960-09-01 | 1963-12-03 | Orthopaedic Specialties Corp | Method for treatment of bone fractures |
| US3433220A (en) | 1966-12-30 | 1969-03-18 | Robert E Zickel | Intramedullary rod and cross-nail assembly for treating femur fractures |
| US4095591A (en) | 1977-01-27 | 1978-06-20 | Richards Manufacturing Co., Inc. | Compression screw system |
| US4103683A (en) | 1977-06-03 | 1978-08-01 | Neufeld John A | Sub-trochanteric nail |
| US4172452A (en) | 1978-05-15 | 1979-10-30 | Howmedica, Inc. | Fracture nail plate assembly |
| US4274163A (en) | 1979-07-16 | 1981-06-23 | The Regents Of The University Of California | Prosthetic fixation technique |
| US4494535A (en) | 1981-06-24 | 1985-01-22 | Haig Armen C | Hip nail |
| US4438762A (en) | 1981-12-30 | 1984-03-27 | Richard F. Kyle | Orthopedic hip fixation device |
| DE3332642A1 (en) | 1983-09-09 | 1985-04-04 | Ortopedia Gmbh, 2300 Kiel | DEVICE FOR DETECTING CROSS HOLES INTRAMEDULLA IMPLANTS |
| CH668173A5 (en) | 1984-05-14 | 1988-12-15 | Synthes Ag | DEVICE FOR FIXING TUBE BONE FRACTURES WITH A BONE MARBLE NAIL AND AT LEAST ONE CROSS-BOLT LOCKING. |
| US4657001A (en) | 1984-07-25 | 1987-04-14 | Fixel Irving E | Antirotational hip screw |
| US4612920A (en) | 1984-11-06 | 1986-09-23 | Zimmer, Inc. | Compression hip screw |
| US4697585A (en) | 1985-01-11 | 1987-10-06 | Williams Michael O | Appliance for fixing fractures of the femur |
| US4622959A (en) | 1985-03-05 | 1986-11-18 | Marcus Randall E | Multi-use femoral intramedullary nail |
| DE3534747A1 (en) | 1985-09-28 | 1987-04-09 | Hasselbach Christoph Von | THIGH NECK IMPLANT |
| US4754749A (en) | 1986-04-29 | 1988-07-05 | Tsou Paul M | Surgical screw with counter-rotation prevention means |
| US4776330A (en) | 1986-06-23 | 1988-10-11 | Pfizer Hospital Products Group, Inc. | Modular femoral fixation system |
| US5312406A (en) | 1986-12-30 | 1994-05-17 | Smith & Nephew Richards Inc. | Method of treating an intertrochanteric fracture |
| US5167663A (en) | 1986-12-30 | 1992-12-01 | Smith & Nephew Richards Inc. | Femoral fracture device |
| US4978270A (en) * | 1987-07-31 | 1990-12-18 | Akh, Inc. | Headless rivet |
| GB8722370D0 (en) | 1987-09-23 | 1987-10-28 | Halder S C | Fixating device |
| US5176681A (en) | 1987-12-14 | 1993-01-05 | Howmedica International Inc. | Intramedullary intertrochanteric fracture fixation appliance and fitting device |
| CH674613A5 (en) | 1988-03-14 | 1990-06-29 | Synthes Ag | |
| US4973332A (en) | 1988-09-12 | 1990-11-27 | Hospital For Joint Diseases | Attachment for femur sliding screw plate |
| US5066296A (en) | 1989-02-02 | 1991-11-19 | Pfizer Hopsital Products Group, Inc. | Apparatus for treating a fracture |
| US4978349A (en) | 1989-08-03 | 1990-12-18 | Synthes (U.S.A.) | Fixation plate |
| US5032125A (en) | 1990-02-06 | 1991-07-16 | Smith & Nephew Richards Inc. | Intramedullary hip screw |
| US5120171A (en) | 1990-11-27 | 1992-06-09 | Stuart Surgical | Bone screw with improved threads |
| CH682300A5 (en) | 1990-12-17 | 1993-08-31 | Synthes Ag | |
| GB9113578D0 (en) * | 1991-06-24 | 1991-08-14 | Howmedica | Intramedullary intertrochanteric fracture fixation appliance |
| DE9109883U1 (en) | 1991-08-09 | 1991-09-26 | Howmedica Gmbh, 2314 Schoenkirchen, De | |
| DE4205118C1 (en) * | 1992-02-13 | 1993-07-29 | Dietmar Dr.Med. Priv. Doz. 5000 Koeln De Pennig | |
| DE4318150C2 (en) | 1993-06-01 | 1996-08-01 | Endocare Ag | Osteosynthesis tools for the treatment of subtrochanteric and pertrochanteric fractures as well as fractures of the femoral neck |
| US5484439A (en) | 1992-09-16 | 1996-01-16 | Alphatec Manufacturing, Inc. | Modular femur fixation device |
| FR2698261B1 (en) * | 1992-11-24 | 1995-03-17 | Lacaffiniere Jean Yves De | Device for guiding a double screw of the neck of the femur for locked trochantero-diaphyseal nail. |
| IT1261494B (en) | 1993-07-30 | 1996-05-23 | Gideon Raphael Tock | ENDOMIDOLLAR NAIL AND CROSS-LINKED OSTEOSYNTHESIS, MODULAR FOR APPLICATION IN ORTHOPEDICS WITHOUT EXPOSURE TO IONIZING RAYS. |
| FR2711505B1 (en) | 1993-10-25 | 1995-12-29 | Tornier Sa | Device for synthesizing fractures of the upper end of the femur. |
| CH688222A5 (en) | 1993-12-07 | 1997-06-30 | Synthes Ag | Bone fixation element. |
| EP0668059B1 (en) | 1994-02-21 | 2000-01-05 | Collux AB | Implant for treating fractures of the femur |
| US5549610A (en) | 1994-10-31 | 1996-08-27 | Smith & Nephew Richards Inc. | Femoral intramedullary nail |
| DE4442206A1 (en) | 1994-11-19 | 1996-05-23 | Artos Med Produkte | Joint prosthesis |
| US5976141A (en) * | 1995-02-23 | 1999-11-02 | Synthes (U.S.A.) | Threaded insert for bone plate screw hole |
| US5578035A (en) | 1995-05-16 | 1996-11-26 | Lin; Chih-I | Expandable bone marrow cavity fixation device |
| IT1275300B (en) | 1995-06-05 | 1997-08-05 | Gruppo Ind Bioimpianti Srl | BLOCKED ENDOMIDOLLAR NAIL SUITABLE FOR FEMORE FRACTURES IN PARTICULAR |
| JPH0966061A (en) | 1995-08-31 | 1997-03-11 | Mizuho Ika Kogyo Kk | Intramedullary nail |
| JP3307804B2 (en) | 1995-08-31 | 2002-07-24 | 瑞穂医科工業株式会社 | Intramedullary nail |
| JP3307805B2 (en) | 1995-08-31 | 2002-07-24 | 瑞穂医科工業株式会社 | Intramedullary nail |
| US5658339A (en) | 1996-01-05 | 1997-08-19 | Wright Medical Technology, Inc. | Compression hip screw plate |
| US5976139A (en) | 1996-07-17 | 1999-11-02 | Bramlet; Dale G. | Surgical fastener assembly |
| IT1287271B1 (en) | 1996-04-05 | 1998-08-04 | Antonio Chemello | ENDOMIDOLLAR NAIL FOR THE OSTEOSYNTHESIS OF LONG BONE FRACTURES |
| DE19629011C2 (en) | 1996-07-18 | 2001-08-23 | Dietmar Wolter | Tools for osteosynthesis |
| WO1998005263A1 (en) | 1996-07-31 | 1998-02-12 | Synthes Ag Chur | Device for attaching fractured hip-joint heads |
| DE19633865A1 (en) | 1996-08-16 | 1998-02-19 | Guenter Prof Dr Med Lob | Endoprosthesis |
| IT242435Y1 (en) | 1996-10-24 | 2001-06-14 | Hit Medica Srl | NAIL FOR THE REDUCTION OF TROCANTERIC FRACTURES AND OF THE NECK DELFEMORE. |
| DE29620327U1 (en) | 1996-11-22 | 1998-03-26 | Howmedica Gmbh | Locking nail with adjustable openings for locking screws |
| US5741256A (en) | 1997-01-13 | 1998-04-21 | Synthes (U.S.A.) | Helical osteosynthetic implant |
| IT1293934B1 (en) | 1997-01-21 | 1999-03-11 | Orthofix Srl | ENDOMIDOLLAR NAIL FOR THE TREATMENT OF HIP FRACTURES |
| EP0865769A1 (en) | 1997-03-19 | 1998-09-23 | Osteo Ag | Modular intramedullary nail |
| US6228086B1 (en) | 1997-03-19 | 2001-05-08 | Stryker Trauma-Selzach Ag | Modular intramedullary nail |
| US7255712B1 (en) * | 1997-04-15 | 2007-08-14 | Active Implants Corporation | Bone growth promoting implant |
| JP3311660B2 (en) | 1997-11-12 | 2002-08-05 | 瑞穂医科工業株式会社 | Intramedullary nail |
| EP0919200A1 (en) | 1997-11-20 | 1999-06-02 | VM Tech | System for osteosynthesis of the upper extremity of the femur |
| US5935127A (en) * | 1997-12-17 | 1999-08-10 | Biomet, Inc. | Apparatus and method for treatment of a fracture in a long bone |
| JP2000051225A (en) | 1998-06-02 | 2000-02-22 | Ikushi Yamada | Intramedullary nail and distal side stopping method |
| DE19829228C1 (en) | 1998-06-30 | 1999-10-28 | Aesculap Ag & Co Kg | Bone fracture fixture with locking-nail with through-hole |
| JP2973316B1 (en) | 1998-08-05 | 1999-11-08 | 洋司 村嶋 | Fixing structure of lag screw used for nail for implant |
| US6010506A (en) | 1998-09-14 | 2000-01-04 | Smith & Nephew, Inc. | Intramedullary nail hybrid bow |
| FR2784283B1 (en) | 1998-10-07 | 2000-12-15 | Fournitures Hospitalieres Ind | MEDULAR NAIL OF OSTEOSYNTHESIS |
| US6123708A (en) | 1999-02-03 | 2000-09-26 | Pioneer Laboratories, Inc. | Intramedullary bone fixation rod |
| US6296645B1 (en) * | 1999-04-09 | 2001-10-02 | Depuy Orthopaedics, Inc. | Intramedullary nail with non-metal spacers |
| US6783529B2 (en) * | 1999-04-09 | 2004-08-31 | Depuy Orthopaedics, Inc. | Non-metal inserts for bone support assembly |
| IL132742A0 (en) | 1999-05-11 | 2001-03-19 | S I N A I Medical Technologies | Osteosynthesis device for holding together in compression the parts of a fractured femur neck |
| EP1053718B1 (en) | 1999-05-12 | 2008-07-09 | Zimmer GmbH | Locking nail for the treatment of femoral shaft fractures |
| JP2000342596A (en) | 1999-06-07 | 2000-12-12 | Homuzu Giken:Kk | Intramedullary nail |
| DE19945611B4 (en) | 1999-09-23 | 2005-11-24 | Aesculap Ag & Co. Kg | Proximal Humeral Nail |
| US6926719B2 (en) | 1999-10-21 | 2005-08-09 | Gary W. Sohngen | Modular intramedullary nail |
| JP4242588B2 (en) * | 1999-12-03 | 2009-03-25 | 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 | Intramedullary nail |
| US6645209B2 (en) * | 2000-04-04 | 2003-11-11 | Synthes (Usa) | Device for rotational stabilization of bone segments |
| DE50102314D1 (en) | 2000-12-18 | 2004-06-24 | Herbert Bernsteiner | Locking screw for implants |
| GB0102488D0 (en) | 2001-01-31 | 2001-03-14 | Grampian Univ Hospitals | Bone Fixture Apparatus |
| EP1260188B1 (en) | 2001-05-25 | 2014-09-17 | Zimmer GmbH | Femoral bone nail for implantation in the knee |
| US6652528B2 (en) * | 2001-07-17 | 2003-11-25 | Biomet, Inc. | Intramedullary nail with modular sleeve |
| DE20113345U1 (en) | 2001-08-17 | 2003-01-02 | Tantum Ag | Femurfrakturnagel |
| US20030069581A1 (en) | 2001-10-04 | 2003-04-10 | Stinson David T. | Universal intramedullary nails, systems and methods of use thereof |
| US6835197B2 (en) | 2001-10-17 | 2004-12-28 | Christoph Andreas Roth | Bone fixation system |
| WO2004078049A1 (en) | 2003-03-07 | 2004-09-16 | Synthes Ag Chur | Locking screw for an intramedullary nail |
| BRPI0318150B8 (en) | 2003-03-21 | 2021-06-22 | Synthes Ag | intramedullary claw |
| DE50312960D1 (en) | 2003-06-12 | 2010-09-16 | Synthes Gmbh | SURGICAL NAIL |
| ATE418923T1 (en) | 2003-07-30 | 2009-01-15 | Synthes Gmbh | SURGICAL NAIL |
| CN100479775C (en) | 2003-08-29 | 2009-04-22 | 斯恩蒂斯有限公司 | Intramedullary nail |
| NZ546545A (en) | 2003-10-21 | 2008-11-28 | Synthes Gmbh | Intramedullary nail |
-
2003
- 2003-06-12 JP JP2005500667A patent/JP4357478B2/en not_active Expired - Fee Related
- 2003-06-12 ES ES03817232T patent/ES2294372T3/en not_active Expired - Lifetime
- 2003-06-12 CN CNB038266156A patent/CN100457058C/en not_active Expired - Fee Related
- 2003-06-12 AT AT03817232T patent/ATE375125T1/en not_active IP Right Cessation
- 2003-06-12 WO PCT/CH2003/000376 patent/WO2004110291A1/en active IP Right Grant
- 2003-06-12 CA CA2531541A patent/CA2531541C/en not_active Expired - Fee Related
- 2003-06-12 NZ NZ544074A patent/NZ544074A/en not_active IP Right Cessation
- 2003-06-12 BR BRPI0318327-0B1A patent/BR0318327B1/en not_active IP Right Cessation
- 2003-06-12 AU AU2003232567A patent/AU2003232567B2/en not_active Ceased
- 2003-06-12 EP EP03817232A patent/EP1631206B1/en not_active Expired - Lifetime
- 2003-06-12 DE DE50308380T patent/DE50308380D1/en not_active Expired - Lifetime
-
2004
- 2004-04-23 CL CL200400867A patent/CL2004000867A1/en unknown
- 2004-04-27 TW TW093111714A patent/TWI323169B/en not_active IP Right Cessation
- 2004-05-14 AR ARP040101642A patent/AR044330A1/en not_active Application Discontinuation
-
2005
- 2005-12-09 US US11/299,337 patent/US9737347B2/en active Active
Also Published As
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|---|---|
| AR044330A1 (en) | 2005-09-07 |
| ATE375125T1 (en) | 2007-10-15 |
| AU2003232567B2 (en) | 2007-12-20 |
| TW200505386A (en) | 2005-02-16 |
| EP1631206B1 (en) | 2007-10-10 |
| JP2006527004A (en) | 2006-11-30 |
| EP1631206A1 (en) | 2006-03-08 |
| US9737347B2 (en) | 2017-08-22 |
| BR0318327A (en) | 2006-07-11 |
| CN1787787A (en) | 2006-06-14 |
| CA2531541A1 (en) | 2004-12-23 |
| AU2003232567A1 (en) | 2005-01-04 |
| JP4357478B2 (en) | 2009-11-04 |
| CN100457058C (en) | 2009-02-04 |
| CL2004000867A1 (en) | 2005-01-14 |
| BR0318327B1 (en) | 2013-06-18 |
| TWI323169B (en) | 2010-04-11 |
| WO2004110291A1 (en) | 2004-12-23 |
| DE50308380D1 (en) | 2007-11-22 |
| NZ544074A (en) | 2007-10-26 |
| ES2294372T3 (en) | 2008-04-01 |
| US20060149248A1 (en) | 2006-07-06 |
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