CN111529032A - Reinforced torsion-resistant interlocking intramedullary nail suite - Google Patents
Reinforced torsion-resistant interlocking intramedullary nail suite Download PDFInfo
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- CN111529032A CN111529032A CN202010491422.9A CN202010491422A CN111529032A CN 111529032 A CN111529032 A CN 111529032A CN 202010491422 A CN202010491422 A CN 202010491422A CN 111529032 A CN111529032 A CN 111529032A
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- locking hole
- intramedullary nail
- static locking
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- 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
- A61B17/725—Intramedullary pins, nails or other devices with special means of locking the nail to the bone with locking pins or screws of special form
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- 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
- A61B17/74—Devices for the head or neck or trochanter of the femur
- A61B17/742—Devices for the head or neck or trochanter of the femur having one or more longitudinal elements oriented along or parallel to the axis of the neck
- A61B17/744—Devices for the head or neck or trochanter of the femur having one or more longitudinal elements oriented along or parallel to the axis of the neck the longitudinal elements coupled to an intramedullary nail
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- 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
- A61B2017/564—Methods for bone or joint treatment
Abstract
The invention discloses a reinforced torsion-resistant interlocking intramedullary nail suite, which comprises a first intramedullary nail, a second intramedullary nail and a third intramedullary nail; first intramedullary nail, second intramedullary nail and third intramedullary nail all contain rod head section and shaft section, the proximal end static locking hole has been seted up to the proximal end portion of rod head section, distal end static locking hole has been seted up to the distal end portion of shaft section, first near-end dynamic locking hole has still been seted up on the rod head section of first intramedullary nail, first far-end static locking hole has still been seted up on the shaft section of first intramedullary nail, second near-end static locking hole and second far-end static locking hole have still been seted up on the shaft section of second intramedullary nail, third near-end static locking hole and third far-end dynamic locking hole have still been seted up on the shaft section of third intramedullary nail. The invention adjusts the stress distribution around the fracture part by changing the distribution position and the type of the locking holes of the intramedullary nail, improves the local mechanical environment and enhances the anti-rotation capability of the intramedullary nail on the basis of maintaining the axial stability of the intramedullary nail.
Description
Technical Field
The invention belongs to the technical field of medical instruments, and particularly relates to a reinforced torsion-resistant interlocking intramedullary nail suite.
Background
The femur is the longest tubular bone in a human body, and the femoral shaft comprises a shaft 2-5 cm below the tuberosity to 2-5 cm above the femoral condyle. When the femoral shaft is fractured, an interlocking intramedullary nail is adopted for fixation at present, static locking screw holes are respectively formed in the most proximal end and the most distal end of the interlocking intramedullary nail, and the most proximal end and the most distal end of the femoral shaft are fixed through screw interlocking respectively. The traditional interlocking intramedullary nail fixing method with the structure has the following defects: the specific occurrence position and type of femoral shaft fracture are not subdivided, and one cutting tool is fixed by adopting a static force type, so that the stress around the fracture part is concentrated, the screw distances at two ends of the fracture part are far, the local mechanical environment is poor, the anti-rotation capability is poor, and the fracture healing is not facilitated.
Disclosure of Invention
In view of the deficiencies of the prior art, it is an object of the present invention to provide a reinforced torsion-resistant cross-locked intramedullary nail kit.
In order to achieve the purpose, the invention adopts the following technical scheme: a reinforced torsion-resistant cross-locked intramedullary nail kit, comprising:
the first intramedullary nail is used for fixing 1/3 fracture parts on the femoral shaft; the first intramedullary nail comprises a first rod head section and a first rod body section which are distributed from near to far in sequence, a first proximal static locking hole is formed in the proximal end portion of the first rod head section, and a first distal static locking hole is formed in the distal end portion of the first rod body section; the first rod head section is further provided with a first near-end dynamic locking hole, the first near-end dynamic locking hole is positioned at the far end part of the first rod head section, the first rod body section is further provided with a first far-end static locking hole, and the center distance between the first closest-end static locking hole and the first far-end static locking hole is 1/3 of the center distance between the first closest-end static locking hole and the first far-end static locking hole;
a second intramedullary nail for fixation of 1/3 fractures in the femoral shaft; the second intramedullary nail comprises a second rod head section and a second rod body section which are distributed from near to far in sequence, a second proximal static locking hole is formed in the proximal end portion of the second rod head section, and a second distal static locking hole is formed in the distal end portion of the second rod body section; the second rod body section is further provided with a second near-end static locking hole and a second far-end static locking hole which are distributed in sequence from near to far, the center distance between the second nearest-end static locking hole and the second near-end static locking hole is 1/3 of the center distance between the second nearest-end static locking hole and the second far-end static locking hole, the center distance between the second near-end static locking hole and the second far-end static locking hole is 1/3 of the center distance between the second nearest-end static locking hole and the second far-end static locking hole, and the center distance between the second far-end static locking hole and the second far-end static locking hole is 1/3 of the center distance between the second nearest-end static locking hole and the second far-end static locking hole;
a third intramedullary nail for fixing 1/3 fracture under femoral shaft; the third intramedullary nail comprises a third rod head section and a third rod body section which are distributed from near to far in sequence, a third proximal static locking hole is formed in the proximal end portion of the third rod head section, and a third distal static locking hole is formed in the distal end portion of the third rod body section; the third rod body section is further provided with a third near-end static locking hole and a third far-end dynamic locking hole which are distributed from near to far in sequence, the third far-end dynamic locking hole is located at the far end part of the third rod body section, and the center distance between the third near-end static locking hole and the third farthest static locking hole is 1/3 of the center distance between the third nearest static locking hole and the third farthest static locking hole.
Preferably, the center distance between the third distal dynamic locking hole and the third distal-most static locking hole is 1/10-1/7 of the center distance between the third proximal static locking hole and the third distal-most static locking hole.
Preferably, the distance between the two end faces of the first intramedullary nail is 360-420 mm, the distance between the two end faces of the second intramedullary nail is 360-420 mm, and the distance between the two end faces of the third intramedullary nail is 360-420 mm.
Preferably, the centre distance between the first nearest static locking hole and the first farthest static locking hole is 360-390 mm, the centre distance between the second nearest static locking hole and the second farthest static locking hole is 360-390 mm, and the centre distance between the third nearest static locking hole and the third farthest static locking hole is 360-390 mm.
Preferably, the length of the first head section is 70-90 mm, the length of the second head section is 70-90 mm, and the length of the third head section is 70-90 mm; the outer major diameter of the first rod body section is 9-13 mm, the outer major diameter of the second rod body section is 9-13 mm, and the outer major diameter of the third rod body section is 9-13 mm. Preferably but not limited to 80 mm.
Preferably, the distance from the center of the first farthest static locking hole to the farthest end face of the first shaft section is 7-8 mm, the distance from the center of the second farthest static locking hole to the farthest end face of the second shaft section is 7-8 mm, and the distance from the center of the third farthest static locking hole to the farthest end face of the third shaft section is 7-8 mm.
Preferably, the first shaft head section is cylindrical, the first shaft body section is curved, the diameter of the first shaft head section is larger than the outer major diameter of the first shaft body section, the distal end of the first shaft head section is provided with a first transition frustum part in smooth transition connection with the first shaft body section, the distal end of the first shaft body section is provided with a first end frustum part in smooth transition, and the end edge of the first end frustum part is provided with a first fillet; the second rod head section is cylindrical, the second rod body section is bent, the diameter of the second rod head section is larger than the outer major diameter of the second rod body section, a second transition frustum part in smooth transition connection with the second rod body section is arranged at the far end of the second rod head section, a second tail end frustum part in smooth transition is arranged at the far end of the second rod body section, and a second fillet is arranged at the tail end edge of the second tail end frustum part; the third shaft head section is cylindrical, the third shaft body section is crooked, the diameter of third shaft head section is greater than the outer major diameter of third shaft body section, the distal end of third shaft head section is provided with the third transition frustum portion of being connected with third shaft body section smooth transition, the distal end of third shaft body section is provided with smooth transition's third end frustum portion, the terminal edge of third end frustum portion is provided with the third radius angle.
Preferably, the convex side of the distal end part of the first rod body segment is provided with a first stress reduction groove, the convex side of the distal end part of the second rod body segment is provided with a second stress reduction groove, and the convex side of the distal end part of the third rod body segment is provided with a third stress reduction groove; a first decompression inclined plane is symmetrically arranged at the front side and the rear side of the far end part of the first club head section, and the first decompression inclined plane extends from the first club head section to the far end of the first transition frustum part; a second decompression inclined plane is symmetrically arranged at the front side and the rear side of the distal end part of the second club head section, and the second decompression inclined plane extends from the second club head section to the distal end of the second transition frustum part; and a third decompression inclined plane is symmetrically arranged at the front side and the rear side of the distal end part of the third club head section, and the third decompression inclined plane extends from the third club head section to the distal end of the third transition frustum part.
Preferably, the cross section of the first shaft section is circular, quincunx, tooth-shaped or V-shaped, the cross section of the second shaft section is circular, quincunx, tooth-shaped or V-shaped, and the cross section of the third shaft section is circular, quincunx, tooth-shaped or V-shaped; the first intramedullary nail is made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy, the second intramedullary nail is made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy, and the third intramedullary nail is made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy.
Preferably, the reinforced torsion-resistant cross-locked intramedullary nail kit further comprises at least four screws, which are mated with corresponding locking holes.
Compared with the prior art, the invention has the following beneficial effects: according to the fracture of 1/3 on/in/under the femoral shaft, the intramedullary nails with corresponding locking hole distribution are respectively designed, the stress distribution around the fracture part is adjusted by changing the distribution position and the specific type of the locking holes of the intramedullary nails, the local mechanical environment is improved, the anti-rotation capability of the intramedullary nails is enhanced on the basis of maintaining the axial stability of the intramedullary nails, the occurrence of rotation, shortening and angulation deformity is effectively prevented, the stability of the fracture end is improved, the active osteogenesis of a bone healing unit is facilitated, and the occurrence of bone nonunion is reduced.
Drawings
Fig. 1 is a schematic structural view of a first intramedullary nail in an embodiment of the present invention.
Fig. 2 is a schematic illustration of a first intramedullary nail in use in an embodiment of the present invention.
Fig. 3 is a structural schematic view of a second intramedullary nail in accordance with an embodiment of the present invention.
Fig. 4 is a schematic illustration of a second intramedullary nail in use in accordance with an embodiment of the present invention.
Fig. 5 is a schematic structural view of a third intramedullary nail in accordance with an embodiment of the present invention.
Fig. 6 is a schematic view of a third intramedullary nail in accordance with an embodiment of the present invention.
The labels in the figure are: 100. a first intramedullary nail; 101. a first proximal-most static locking hole; 102. a first distal-most static locking hole; 103. a first proximal power locking aperture; 104. a first distal static locking hole; 110. a first club head section; 111. a first transition frustum portion; 112. a first reduced-pressure inclined plane; 120. a first shaft section; 121. a first end cone portion; 122. a first stress relief groove; 200. a second intramedullary nail; 201. a second proximal-most static locking hole; 202. a second distal-most static locking hole; 203. a second proximal static locking hole; 204. a second distal static locking hole; 210. a second head section; 211. a second transition frustum portion; 212. a second reduced-pressure inclined plane; 220. a second shaft section; 221. a second distal frustum portion; 222. a second stress-reducing groove; 300. a third intramedullary nail; 301. a third proximal static locking hole; 302. a third distal-most static locking hole; 303. a third proximal static locking hole; 304. a third distal power locking aperture; 310. a third club head section; 311. a third transition frustum portion; 312. a third reduced-pressure inclined plane; 320. a third shaft section; 321. a third tip frustum portion; 322. a third stress-reducing groove; 400. a screw; 500. the femoral shaft.
Detailed Description
In order to make the aforementioned and other features and advantages of the invention more comprehensible, embodiments accompanied with figures are described in detail below.
The first embodiment is as follows: as shown in fig. 1 to 6, the present embodiment provides a reinforced torsion-resistant cross-locked intramedullary nail kit, comprising:
a first intramedullary nail 100 for fixation of 1/3 fracture on the femoral shaft 500; the first intramedullary nail 100 comprises a first rod head section 110 and a first rod body section 120 which are distributed from near to far in sequence, a first proximal static locking hole 101 is formed in the proximal end portion of the first rod head section 110, and a first distal static locking hole 102 is formed in the distal end portion of the first rod body section 120; the first rod head segment 110 is further provided with a first proximal dynamic locking hole 103, the first proximal dynamic locking hole 103 is located at the distal end portion of the first rod head segment 110, the first rod body segment 120 is further provided with a first distal static locking hole 104, and a center distance B1 between the first proximal static locking hole 101 and the first distal static locking hole 104 is 1/3 of a center distance a1 between the first proximal static locking hole 101 and the first distal static locking hole 102;
a second intramedullary nail 200 for fixation of 1/3 fractures in the femoral shaft 500; the second intramedullary nail 200 comprises a second rod head section 210 and a second rod body section 220 which are distributed from near to far in sequence, a proximal end part of the second rod head section 210 is provided with a second proximal-most static locking hole 201, and a distal end part of the second rod body section 220 is provided with a second distal-most static locking hole 202; the second shaft body section 220 is further provided with a second proximal static locking hole 203 and a second distal static locking hole 204 which are distributed from near to far in sequence, the center distance B2 between the second most proximal static lock hole 201 and the second proximal static lock hole 203 is 1/3 of the center distance a2 between the second most proximal static lock hole 201 and the second most distal static lock hole 202, the center distance C2 between the second proximal and distal static lock holes 203 and 204 is 1/3 of the center distance a2 between the second proximal most static lock hole 201 and the second distal most static lock hole 202, the center distance D2 between the second distal static locking hole 204 and the second distal-most static locking hole 202 is 1/3 of the center distance a2 between the second proximal-most static locking hole 201 and the second distal-most static locking hole 202;
a third intramedullary nail 300 for fixing 1/3 fracture under femoral shaft 500; the third intramedullary nail 300 comprises a third rod head section 310 and a third rod body section 320 which are distributed from near to far in sequence, a proximal end part of the third rod head section 310 is provided with a third nearest static locking hole 301, and a distal end part of the third rod body section 320 is provided with a third farthest static locking hole 302; the third shaft section 320 is further provided with a third proximal static locking hole 303 and a third distal dynamic locking hole 304 which are distributed from near to far in sequence, the third distal dynamic locking hole 304 is located at the distal end portion of the third shaft section 320, and a center distance B3 between the third proximal static locking hole 303 and the third distal static locking hole 302 is 1/3 of a center distance A3 between the third proximal static locking hole 301 and the third distal static locking hole 302.
When 1/3 on the femoral shaft 500 is fractured, the first intramedullary nail 100 is selected for use; when 1/3 fractures in the femoral shaft 500, the second intramedullary nail 200 is selected for use; the third intramedullary nail 300 is selected for use when the femoral shaft 500 is fractured at 1/3. By adopting the first nearest static locking hole 101, the first farthest static locking hole 102, the second nearest static locking hole 201, the second farthest static locking hole 202, the second near static locking hole 203, the second far static locking hole 204, the third nearest static locking hole 301 and the third farthest static locking hole 302, the two ends are interlocked and fixed, static type fixation is realized, better axial and rotary fixing effects are achieved, fracture displacement after fixation is prevented, and the application range of the device is expanded. One end of the first proximal dynamic locking hole 103, the first distal static locking hole 104, the third proximal static locking hole 303 and the third distal dynamic locking hole 304 is locked and fixed, and the other end of the first proximal dynamic locking hole is slid, so that dynamic fixation is realized, and the healing of bones can be promoted; wherein the first proximal dynamic locking hole 103 is preferably an oblong locking hole extending along the length of the first stem head section 110, such that the first intramedullary nail 100 can slide up and down at the first proximal dynamic locking hole 103; the third distal dynamic locking hole 304 is preferably an oblong locking hole extending along the length of the third shaft section 320 such that the third intramedullary nail 300 can slide up and down at the third distal dynamic locking hole 304; the length G of the oblong locking hole is preferably, but not limited to, 10-14 mm, such as 11-13 mm, and more specifically, 12 mm.
In this embodiment, the center distance H3 between the third distal dynamic locking hole 304 and the third distal-most static locking hole 302 is 1/10-1/7 of the center distance A3 between the third proximal static locking hole 303 and the third distal-most static locking hole 302. Further, the center distance H3 between the third distal dynamic locking hole 304 and the third distal-most static locking hole 302 is preferably 1/9 to 1/8 times, such as 0.12 times, specifically 10 to 20mm, and preferably, but not limited to, 15mm of the center distance A3 between the third proximal static locking hole 303 and the third distal-most static locking hole 302.
In the embodiment, the distance L1 between the two end faces of the first intramedullary nail 100 is 360-420 mm, preferably but not limited to 380mm, 400 mm; the distance L2 between the two end faces of the second intramedullary nail 200 is 360-420 mm, preferably but not limited to 380mm and 400 mm; the distance L3 between the two end faces of the third intramedullary nail 300 is 360-420 mm, preferably but not limited to 380mm, 400 mm. Specifically, the lengths of the first intramedullary nail 100, the second intramedullary nail 200 and the third intramedullary nail 300 can be selected according to male, female, adult and child patients, the length of the male can be 380-420 mm, the length of the female can be 360-400 mm, and the distance from the greater tuberosity tip of the limb-strengthening femur to the upper edge of the patella can be measured through a standard X-ray, namely the length of the intramedullary nail.
In the present embodiment, the center distance A1 between the first nearest static locking hole 101 and the first farthest static locking hole 102 is 360-390 mm, preferably but not limited to 370-380 mm, such as 376.8 mm; the center distance A2 between the second most proximal static locking hole 201 and the second most distal static locking hole 202 is 360-390 mm, preferably but not limited to 370-380 mm, such as 376.8 mm; the center distance A3 between the third nearest static locking hole 301 and the third farthest static locking hole 302 is 360-390 mm, preferably but not limited to 370-380 mm, such as 376.8 mm. Wherein the center distance B1 between the first nearest static locking hole 101 and the first far static locking hole 104 is 120-130 mm, preferably but not limited to 125.6 mm; the center distance B2 between the second nearest static locking hole 201 and the second proximal static locking hole 203, the center distance C2 between the second proximal static locking hole 203 and the second distal static locking hole 204, and the center distance D2 between the second distal static locking hole 204 and the second farthest static locking hole 202 are all 120-130 mm, preferably, but not limited to 125.6 mm; the center distance B3 between the third proximal static locking hole 303 and the third distal-most static locking hole 302 is 120-130 mm, preferably, but not limited to 125.6 mm.
In the present embodiment, the length F1 of the first club head segment 110 is 70 to 90mm, preferably but not limited to 80 mm; the length F2 of the second head section 210 is 70-90 mm, preferably but not limited to 80 mm; the length F3 of the third head section 310 is 70-90 mm, preferably but not limited to 80 mm; the outer major diameter R1 of the first shaft section 120 is 9-13 mm, preferably but not limited to 10-12 mm, specifically 11 mm; the outer major diameter R2 of the second shaft section 220 is 9-13 mm, preferably but not limited to 10-12 mm, specifically 11 mm; the outer major diameter R3 of the third shaft section 320 is 9-13 mm, preferably but not limited to 10-12 mm, specifically 11 mm. Specifically, the outer major diameters of the first shaft section 120, the second shaft section 220 and the third shaft section 320 can be selected according to male, female, adult and child patients, the diameter of a male can be selected to be 10-13 mm, the diameter of a female can be selected to be 9-12 mm, the transverse diameter of the narrowest part of the medullary cavity of a patient can be measured through a standard X-ray, and the thickness of the intramedullary nail is obtained by subtracting 10% from the transverse diameter.
In the present embodiment, the distance E1 from the center of the first most distal static locking hole 102 to the most distal end face of the first shaft segment 120 is 7-8 mm, preferably but not limited to 7.5 mm; the distance E2 from the center of the second most distal static locking hole 202 to the most distal end face of the second shaft section 220 is 7-8 mm, preferably but not limited to 7.5 mm; the distance E3 from the center of the third most distal static locking hole 302 to the most distal end face of the third shaft section 320 is 7-8 mm, preferably but not limited to 7.5 mm.
In the present embodiment, the first shaft head section 110 is cylindrical, the first shaft section 120 is curved, the diameter of the first shaft head section 110 is greater than the outer major diameter of the first shaft section 120, the distal end of the first shaft head section 110 is provided with a first transition frustum portion 111 in smooth transition connection with the first shaft section 120, the distal end of the first shaft section 120 is provided with a first end frustum portion 121 in smooth transition, and the distal end edge of the first end frustum portion 121 is provided with a first rounded corner; the second shaft head section 210 is cylindrical, the second shaft body section 220 is curved, the diameter of the second shaft head section 210 is larger than the outer major diameter of the second shaft body section 220, the distal end of the second shaft head section 210 is provided with a second transition frustum part 211 which is in smooth transition connection with the second shaft body section 220, the distal end of the second shaft body section 220 is provided with a second end frustum part 221 which is in smooth transition, and the end edge of the second end frustum part 221 is provided with a second fillet; third shaft section 310 is cylindrical, third shaft section 320 is the bending, the diameter of third shaft section 310 is greater than the outer major diameter of third shaft section 320, the distal end of third shaft section 310 is provided with third transition frustum portion 311 with third shaft section 320 smooth transition connection, the distal end of third shaft section 320 is provided with third tip frustum portion 321 of smooth transition, the terminal edge of third tip frustum portion 321 is provided with the third radius angle.
In this embodiment, the convex side of the distal end of the first shaft segment 120 is provided with a first stress-relief groove 122, the convex side of the distal end of the second shaft segment 220 is provided with a second stress-relief groove 222, and the convex side of the distal end of the third shaft segment 320 is provided with a third stress-relief groove 223; a first decompression inclined plane 112 is symmetrically arranged at the front side and the rear side of the distal end part of the first head section 110, and the first decompression inclined plane 112 extends from the first head section 110 to the distal end of the first transition frustum part 111; a second decompression inclined plane 212 is symmetrically arranged at the front side and the rear side of the distal end part of the second head section 210, and the second decompression inclined plane 212 extends from the second head section 210 to the distal end of the second transition frustum part 211; the distal end portion of the third stem head section 310 is symmetrically provided with a third decompression inclined plane 312 at the front-rear side, and the third decompression inclined plane 312 extends from the third stem head section 310 to the distal end of the third transition frustum portion 311. Wherein half of the first decompression ramp plane 112 is located on the outer surface of the first stem head section 110 and the other half of the first decompression ramp plane 112 is located on the outer surface of the first transition frustum portion 111; half of the second relief inclined plane 212 is located on the outer surface of the second head section 210, and the other half of the second relief inclined plane 212 is located on the outer surface of the second transition frustum portion 211; half of the third relief rake plane 312 is located on the outer surface of the third stem section 310 and the other half of the third relief rake plane 312 is located on the outer surface of the third transition frustum portion 311.
In this embodiment, the cross-section of the first shaft section 120 is preferably circular, quincunx (as shown), toothed, V-shaped, etc., the cross-section of the second shaft section 220 is preferably circular, quincunx (as shown), toothed, V-shaped, etc., and the cross-section of the third shaft section 320 is preferably circular, quincunx (as shown), toothed, V-shaped, etc. The first intramedullary nail 100 is preferably made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy, the second intramedullary nail 200 is preferably made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy, and the third intramedullary nail 300 is preferably made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy.
Example two: referring to fig. 1 to 6, the difference between the present embodiment and the first embodiment is: the reinforced torsion-resistant cross-locked intramedullary nail kit further comprises at least four screws 400, wherein the screws 400 are matched with the corresponding locking holes.
It should be understood, however, that the description herein of specific embodiments is not intended to limit the invention to the particular forms disclosed, but on the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the appended claims.
Claims (10)
1. A reinforced torsion-resistant cross-locked intramedullary nail kit, comprising:
the first intramedullary nail is used for fixing 1/3 fracture parts on the femoral shaft; the first intramedullary nail comprises a first rod head section and a first rod body section which are distributed from near to far in sequence, a first proximal static locking hole is formed in the proximal end portion of the first rod head section, and a first distal static locking hole is formed in the distal end portion of the first rod body section; the first rod head section is further provided with a first near-end dynamic locking hole, the first near-end dynamic locking hole is positioned at the far end part of the first rod head section, the first rod body section is further provided with a first far-end static locking hole, and the center distance between the first closest-end static locking hole and the first far-end static locking hole is 1/3 of the center distance between the first closest-end static locking hole and the first far-end static locking hole;
a second intramedullary nail for fixation of 1/3 fractures in the femoral shaft; the second intramedullary nail comprises a second rod head section and a second rod body section which are distributed from near to far in sequence, a second proximal static locking hole is formed in the proximal end portion of the second rod head section, and a second distal static locking hole is formed in the distal end portion of the second rod body section; the second rod body section is further provided with a second near-end static locking hole and a second far-end static locking hole which are distributed in sequence from near to far, the center distance between the second nearest-end static locking hole and the second near-end static locking hole is 1/3 of the center distance between the second nearest-end static locking hole and the second far-end static locking hole, the center distance between the second near-end static locking hole and the second far-end static locking hole is 1/3 of the center distance between the second nearest-end static locking hole and the second far-end static locking hole, and the center distance between the second far-end static locking hole and the second far-end static locking hole is 1/3 of the center distance between the second nearest-end static locking hole and the second far-end static locking hole;
a third intramedullary nail for fixing 1/3 fracture under femoral shaft; the third intramedullary nail comprises a third rod head section and a third rod body section which are distributed from near to far in sequence, a third proximal static locking hole is formed in the proximal end portion of the third rod head section, and a third distal static locking hole is formed in the distal end portion of the third rod body section; the third rod body section is further provided with a third near-end static locking hole and a third far-end dynamic locking hole which are distributed from near to far in sequence, the third far-end dynamic locking hole is located at the far end part of the third rod body section, and the center distance between the third near-end static locking hole and the third farthest static locking hole is 1/3 of the center distance between the third nearest static locking hole and the third farthest static locking hole.
2. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 1, wherein: the center distance between the third distal dynamic locking hole and the third distal-most static locking hole is 1/10-1/7 of the center distance between the third proximal static locking hole and the third distal-most static locking hole.
3. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 1, wherein: the distance between the two end faces of the first intramedullary nail is 360-420 mm, the distance between the two end faces of the second intramedullary nail is 360-420 mm, and the distance between the two end faces of the third intramedullary nail is 360-420 mm.
4. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 1, wherein: the center distance between the first nearest static locking hole and the first farthest static locking hole is 360-390 mm, the center distance between the second nearest static locking hole and the second farthest static locking hole is 360-390 mm, and the center distance between the third nearest static locking hole and the third farthest static locking hole is 360-390 mm.
5. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 1, wherein: the length of the first head section is 70-90 mm, the length of the second head section is 70-90 mm, and the length of the third head section is 70-90 mm; the outer major diameter of the first rod body section is 9-13 mm, the outer major diameter of the second rod body section is 9-13 mm, and the outer major diameter of the third rod body section is 9-13 mm.
6. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 1, wherein: the distance from the center of the first farthest static force locking hole to the farthest end face of the first rod body section is 7-8 mm, the distance from the center of the second farthest static force locking hole to the farthest end face of the second rod body section is 7-8 mm, and the distance from the center of the third farthest static force locking hole to the farthest end face of the third rod body section is 7-8 mm.
7. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 1, wherein: the first rod head section is cylindrical, the first rod body section is bent, the diameter of the first rod head section is larger than the outer major diameter of the first rod body section, a first transition frustum part in smooth transition connection with the first rod body section is arranged at the far end of the first rod head section, a first tail end frustum part in smooth transition is arranged at the far end of the first rod body section, and a first fillet is arranged at the tail end edge of the first tail end frustum part; the second rod head section is cylindrical, the second rod body section is bent, the diameter of the second rod head section is larger than the outer major diameter of the second rod body section, a second transition frustum part in smooth transition connection with the second rod body section is arranged at the far end of the second rod head section, a second tail end frustum part in smooth transition is arranged at the far end of the second rod body section, and a second fillet is arranged at the tail end edge of the second tail end frustum part; the third shaft head section is cylindrical, the third shaft body section is crooked, the diameter of third shaft head section is greater than the outer major diameter of third shaft body section, the distal end of third shaft head section is provided with the third transition frustum portion of being connected with third shaft body section smooth transition, the distal end of third shaft body section is provided with smooth transition's third end frustum portion, the terminal edge of third end frustum portion is provided with the third radius angle.
8. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 9, wherein: a first stress reduction groove is formed in the convex side of the far end part of the first rod body segment, a second stress reduction groove is formed in the convex side of the far end part of the second rod body segment, and a third stress reduction groove is formed in the convex side of the far end part of the third rod body segment; a first decompression inclined plane is symmetrically arranged at the front side and the rear side of the far end part of the first club head section, and the first decompression inclined plane extends from the first club head section to the far end of the first transition frustum part; a second decompression inclined plane is symmetrically arranged at the front side and the rear side of the distal end part of the second club head section, and the second decompression inclined plane extends from the second club head section to the distal end of the second transition frustum part; and a third decompression inclined plane is symmetrically arranged at the front side and the rear side of the distal end part of the third club head section, and the third decompression inclined plane extends from the third club head section to the distal end of the third transition frustum part.
9. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 1, wherein: the cross section of the first rod body section is circular, quincunx, tooth-shaped or V-shaped, the cross section of the second rod body section is circular, quincunx, tooth-shaped or V-shaped, and the cross section of the third rod body section is circular, quincunx, tooth-shaped or V-shaped; the first intramedullary nail is made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy, the second intramedullary nail is made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy, and the third intramedullary nail is made of stainless steel, titanium alloy, chromium-cobalt alloy or cobalt-nickel alloy.
10. The enhanced torsion resistant cross-locked intramedullary nail kit of claim 1, wherein: at least four screws are also included, which are matched with the corresponding locking holes.
Priority Applications (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010491422.9A CN111529032B (en) | 2020-06-02 | 2020-06-02 | Reinforced torsion-resistant interlocking intramedullary nail suite |
| CN202110526148.9A CN113509254B (en) | 2020-06-02 | 2020-06-02 | Interlocking intramedullary nail suite capable of improving mechanical environment |
| CN202110526204.9A CN113229916B (en) | 2020-06-02 | 2020-06-02 | Anti-rotation interlocking intramedullary nail suite |
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| CN202010491422.9A CN111529032B (en) | 2020-06-02 | 2020-06-02 | Reinforced torsion-resistant interlocking intramedullary nail suite |
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| CN202110526148.9A Division CN113509254B (en) | 2020-06-02 | 2020-06-02 | Interlocking intramedullary nail suite capable of improving mechanical environment |
| CN202110526204.9A Division CN113229916B (en) | 2020-06-02 | 2020-06-02 | Anti-rotation interlocking intramedullary nail suite |
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| CN111529032A true CN111529032A (en) | 2020-08-14 |
| CN111529032B CN111529032B (en) | 2021-06-08 |
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| CN202110526148.9A Active CN113509254B (en) | 2020-06-02 | 2020-06-02 | Interlocking intramedullary nail suite capable of improving mechanical environment |
| CN202010491422.9A Active CN111529032B (en) | 2020-06-02 | 2020-06-02 | Reinforced torsion-resistant interlocking intramedullary nail suite |
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| CN202110526148.9A Active CN113509254B (en) | 2020-06-02 | 2020-06-02 | Interlocking intramedullary nail suite capable of improving mechanical environment |
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Also Published As
| Publication number | Publication date |
|---|---|
| CN113229916B (en) | 2022-04-08 |
| CN113509254B (en) | 2022-06-21 |
| CN113509254A (en) | 2021-10-19 |
| CN111529032B (en) | 2021-06-08 |
| CN113229916A (en) | 2021-08-10 |
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