CN107280747B - Intramedullary pin - Google Patents
Intramedullary pin Download PDFInfo
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- CN107280747B CN107280747B CN201710610631.9A CN201710610631A CN107280747B CN 107280747 B CN107280747 B CN 107280747B CN 201710610631 A CN201710610631 A CN 201710610631A CN 107280747 B CN107280747 B CN 107280747B
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- 230000000149 penetrating effect Effects 0.000 claims abstract description 13
- 238000007789 sealing Methods 0.000 claims description 7
- 208000010392 Bone Fractures Diseases 0.000 abstract description 32
- 210000000988 bone and bone Anatomy 0.000 description 27
- 210000003414 extremity Anatomy 0.000 description 9
- BGPVFRJUHWVFKM-UHFFFAOYSA-N N1=C2C=CC=CC2=[N+]([O-])C1(CC1)CCC21N=C1C=CC=CC1=[N+]2[O-] Chemical compound N1=C2C=CC=CC2=[N+]([O-])C1(CC1)CCC21N=C1C=CC=CC1=[N+]2[O-] BGPVFRJUHWVFKM-UHFFFAOYSA-N 0.000 description 5
- 229910052751 metal Inorganic materials 0.000 description 5
- 239000002184 metal Substances 0.000 description 5
- 230000006378 damage Effects 0.000 description 4
- 239000000463 material Substances 0.000 description 4
- 238000005192 partition Methods 0.000 description 4
- 210000001519 tissue Anatomy 0.000 description 4
- 230000007547 defect Effects 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 229910000831 Steel Inorganic materials 0.000 description 2
- QJVKUMXDEUEQLH-UHFFFAOYSA-N [B].[Fe].[Nd] Chemical compound [B].[Fe].[Nd] QJVKUMXDEUEQLH-UHFFFAOYSA-N 0.000 description 2
- 239000011248 coating agent Substances 0.000 description 2
- 238000000576 coating method Methods 0.000 description 2
- 238000002474 experimental method Methods 0.000 description 2
- 208000015181 infectious disease Diseases 0.000 description 2
- 208000014674 injury Diseases 0.000 description 2
- 239000000696 magnetic material Substances 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 229910001172 neodymium magnet Inorganic materials 0.000 description 2
- 230000000399 orthopedic effect Effects 0.000 description 2
- 230000035515 penetration Effects 0.000 description 2
- 239000010959 steel Substances 0.000 description 2
- 206010017076 Fracture Diseases 0.000 description 1
- 208000006670 Multiple fractures Diseases 0.000 description 1
- 206010028980 Neoplasm Diseases 0.000 description 1
- 208000006735 Periostitis Diseases 0.000 description 1
- 208000027418 Wounds and injury Diseases 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000017531 blood circulation Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 238000002513 implantation Methods 0.000 description 1
- 230000003993 interaction Effects 0.000 description 1
- 210000003460 periosteum Anatomy 0.000 description 1
- 230000002035 prolonged effect Effects 0.000 description 1
- 238000002271 resection Methods 0.000 description 1
- 238000001356 surgical procedure Methods 0.000 description 1
- 230000008733 trauma Effects 0.000 description 1
- 210000000689 upper leg Anatomy 0.000 description 1
- 230000000007 visual effect Effects 0.000 description 1
- 238000003466 welding Methods 0.000 description 1
Classifications
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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
- A61B17/7216—Intramedullary pins, nails or other devices for bone lengthening or compression
-
- 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
-
- 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
Landscapes
- Health & Medical Sciences (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Surgery (AREA)
- Life Sciences & Earth Sciences (AREA)
- Heart & Thoracic Surgery (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Neurology (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Surgical Instruments (AREA)
Abstract
The invention relates to the technical field of medical equipment, and particularly discloses an intramedullary pin, which comprises a first prosthesis and a second prosthesis; the first end of the first prosthesis is provided with a first through hole penetrating through the first prosthesis, and the second end of the first prosthesis is provided with a first cavity; the first end of the second prosthesis is provided with a second cavity and extends into the first cavity, and the second end of the second prosthesis is provided with a second through hole penetrating through the second prosthesis; the first cavity is sequentially provided with a magnetic block, a reduction gearbox and a screw rod from one end far away from the second prosthesis to one end close to the second prosthesis; the input shaft of the reduction gearbox rotates around the axis of the input shaft under the drive of the magnetic block, the screw rod rotates around the axis of the screw rod under the drive of the output shaft of the reduction gearbox, and the screw rod extends into the second cavity and is in threaded connection with the second cavity; the first prosthesis and the second prosthesis are connected in a sliding way along the extending direction of the screw rod. The intramedullary pin provided by the invention can realize bone fracture extension without secondary operation under the action of a driving magnetic field.
Description
Technical Field
The invention relates to the technical field of medical equipment, in particular to an intramedullary pin.
Background
Clinically, the conditions of unequal length of the developmental limb, severe trauma, bone defect after tumor resection and the like often need to be corrected by operation. Current methods of orthopedic treatment are external and internal bone fixation.
Medical devices required for external fixation of bone include a connecting rod, a first fixation needle, and a second fixation needle. The connecting rod is arranged outside the human body, one end of the first fixing needle is fixedly connected with the first end of the connecting rod, and the other end of the first fixing needle penetrates through skin tissues of the human body and is further fixedly connected with the first broken bone in the human body; one end of the second fixing needle is fixedly connected with the second end of the connecting rod, and the other end of the second fixing needle penetrates through skin tissues of a person and is further fixedly connected with a second broken bone in the person. After the connection is completed, the connecting rod can be prolonged, so that the skeleton in the human body is driven to stretch (the distance between the first broken bone and the second broken bone is increased), when the bone is pulled to a preset length, periosteum at the fracture of the first broken bone and the second broken bone is gradually mature, a marrow cavity structure is formed, and after blood circulation is established, the outer frame and the metal fixing needle are removed. Although bone stretching is easily achieved in the external bone fixation, there are also a number of problems such as inconvenience in life of the patient due to connection of the connecting rod, and easiness in infection of needle tracks of the first and second fixing needles.
Medical devices commonly used in intraosseous fixation include intramedullary nails, first fixation needles, and second fixation needles. The intramedullary pin is arranged in the human body, one end of the intramedullary pin is inserted into the first broken bone, and the intramedullary pin is fixedly connected with the first broken bone through the first fixing pin; the other end of the fixing needle is inserted into the second broken bone and is fixedly connected with the second broken bone through the second fixing needle. Although the intraosseous fixation can avoid the problems of inconvenient life caused by the external connecting rod and needle tract infection caused by the penetration of the fixed needle through the human body, the intraosseous fixation also has larger problems. Over time, the body will grow and the limb will lengthen, so the length of the original intramedullary pin implanted into the body will be insufficient, requiring a secondary operation to remove the original intramedullary pin and implant a new intramedullary pin of longer length. This would undoubtedly bring greater injury and more inconvenience to the human body.
Thus, there is a need for an intramedullary pin that can achieve extension of a fractured bone without requiring a secondary procedure.
Disclosure of Invention
One object of the present invention is to: provided is an intramedullary pin which can realize bone fracture extension without secondary operation under the action of a driving magnetic field.
To this end, the present invention provides an intramedullary pin comprising a first prosthesis and a second prosthesis;
a first through hole penetrating through the first prosthesis is formed in the first end of the first prosthesis, and a first cavity is formed in the second end of the first prosthesis; the first end of the second prosthesis is provided with a second cavity and extends into the first cavity, and the second end of the second prosthesis is provided with a second through hole penetrating through the second prosthesis;
the first cavity is sequentially provided with a magnetic block, a reduction gearbox and a screw rod from one end far away from the second prosthesis to one end close to the second prosthesis; the input shaft of the reduction gearbox rotates around the axis of the input shaft under the drive of the magnetic block, the screw rod rotates around the axis of the screw rod under the drive of the output shaft of the reduction gearbox, and the screw rod extends into the second cavity and is in threaded connection with the second cavity;
the first prosthesis is connected with the second prosthesis in a sliding manner along the extending direction of the screw rod.
Specifically, an intramedullary pin is implanted in the human body: inserting the first end of the first prosthesis into the first broken bone along the extending direction of the first broken bone, and penetrating the first through hole by using a first fixing needle so as to fixedly connect the first broken bone with the first prosthesis; inserting the second end of the second prosthesis into the second fractured bone along the extending direction of the second fractured bone, and penetrating the second penetrating hole by using the second fixing needle so as to fixedly connect the second fractured bone with the second prosthesis. Over time, the human body will grow, and therefore, it is necessary to properly lengthen the overall length of the intramedullary pin to achieve bone stretching (increase the distance between the first fractured bone and the second fractured bone). At this time, the limb implanted with the intramedullary pin is required to be placed in an alternating magnetic field, the S pole and the N pole of the alternating magnetic field can be continuously and alternately changed, and the magnetic block can rotate around the axis of the magnetic block at a high speed under the action of the alternating magnetic field. The magnetic block rotating at high speed drives the input shaft of the reduction gearbox to rotate, so that the output shaft drives the screw rod to rotate. Because the first prosthesis and the second prosthesis can only be connected in a sliding way along the extending direction of the screw rod, relative rotation perpendicular to the extending direction of the screw rod cannot occur, when the screw rod is connected with the second cavity in a threaded way, the second cavity is far away from the reduction gearbox along the extending direction of the screw rod, and finally the increase of the whole length of the intramedullary pin is realized, so that the distance between the first broken bone and the second broken bone is increased. Of course, according to this principle, the second cavity may be also made to approach the reduction gearbox along the extending direction of the screw rod, so as to finally achieve reduction of the overall length of the intramedullary pin, and further reduce the distance between the first broken bone and the second broken bone.
As a preferred embodiment, the magnetic block is fixed on the input shaft of the reduction gearbox, and the axis of the magnetic block is in a straight line with the axis of the input shaft of the reduction gearbox;
the output shaft of the reduction gearbox is fixedly connected with the screw rod, and the axis of the output shaft of the reduction gearbox and the axis of the screw rod are on the same straight line.
Preferably, the magnetic block is fixed on a first shaft, and the first shaft is connected with an input shaft of the reduction gearbox through a gear, a belt or a chain.
Preferably, the output shaft of the reduction gearbox is connected with the screw rod through a gear, a belt or a chain.
As a preferred embodiment, the inner wall of the first cavity is provided with a boss, the outer surface of the first end of the second prosthesis is provided with a chute, and the boss is inserted into the chute and is in sliding connection with the chute;
the extending direction of the sliding groove is parallel to the extending direction of the screw rod.
As a preferred embodiment, the inner wall of the first cavity is provided with a chute, the outer surface of the first end of the second prosthesis is provided with a boss, and the boss is inserted into the chute and is in sliding connection with the chute;
the extending direction of the sliding groove is parallel to the extending direction of the screw rod.
As a preferred embodiment, the magnetic block is a permanent magnet.
Specifically, the magnetic blocks are arranged to be permanent magnets, so that the risk of demagnetizing the magnetic blocks can be avoided.
As a preferred implementation manner, one end of the first prosthesis, which is close to the magnetic block, is provided with a plurality of through grooves, and the through grooves are communicated with the first cavity and the external space of the first prosthesis;
the through groove is filled with a plastic sealing plate.
Preferably, the number of the through grooves is 2.
Specifically, because the intramedullary pin is implanted into the human body, a patient has a large impact load when walking, standing or running, the main body part of the intramedullary pin (comprising a first prosthesis, a second prosthesis and the like) generally adopts a metal structure to increase the strength of the intramedullary pin, but the metal structure can cause shielding effect on a magnetic field, so that a through groove is required to be formed on the first prosthesis around the magnetic block, and a plastic sealing plate made of plastic material is implanted, so that the intramedullary pin not only can play a role of coating and protecting the magnetic block, but also can ensure that an external alternating magnetic field can act on the magnetic block through the plastic sealing plate.
As a preferred embodiment, the reduction gearbox further comprises a reduction gear set, and the input shaft of the reduction gearbox and the output shaft of the reduction gearbox are connected through the reduction gear set through gears.
Preferably, the ratio of the rotational speed of the input shaft of the reduction gearbox to the rotational speed of the output shaft of the reduction gearbox is greater than or equal to 1000:1.
specifically, the magnetic block is of a cylindrical structure and is magnetized along the radial direction, and the material is neodymium iron boron magnetic material. The main purpose of the design of the reduction gearbox is to obtain larger output torque so as to rotate the screw rod. A large number of experiments show that when the reduction ratio is above 1000:1, the intramedullary pin can effectively overcome the tension between human tissue structures, and the output torque can be smoother through the linear driving force of the second prosthesis converted by the lead screw.
As a preferred embodiment, the pitch of the screw is 0.8mm or more and 1.2mm or less.
Preferably, the pitch of the screw is 1mm. The pitch of the screw is designed to be 1mm, and if necessary, it can be extended twice a day by 0.5mm each time. Such a rate of extension is acceptable to the human body because the patient also needs to adapt slowly to the discomfort caused to himself when extending, and the slow extension does not cause additional damage to the patient's body.
As a preferred embodiment, a nut is installed at one end of the second cavity near the reduction gearbox, the axis of the nut is on the same line with the axis of the output shaft of the reduction gearbox, and the nut is in threaded connection with the screw rod.
As a preferred embodiment of the present invention,
the diameter of the first prosthesis is above 8.5mm and below 12.5 mm;
the second end of the second prosthesis has a diameter of 8.5mm or more and 12.5mm or less.
Preferably, the diameter of the first prosthesis is equal to the diameter of the second end of the second prosthesis. Specifically, the intramedullary pin has an outer diameter of 8.5mm, 10.5mm, 12.5mm, etc., to accommodate patients with varying bone sizes. Along with the rotation of the screw rod, the second prosthesis pushes the second broken bone to move, so that the length of the defect section is increased, and the aim of prolonging the length of the limb is fulfilled.
The beneficial effects of the invention are as follows: the intramedullary pin is provided, and the magnetic block, the reduction gearbox and the screw rod are arranged, so that the bone fracture extension operation can be completed without secondary operation under the action of a driving magnetic field.
Drawings
The invention is described in further detail below with reference to the drawings and examples.
FIG. 1 is a schematic view showing an appearance of an intramedullary pin according to a first embodiment;
FIG. 2 is a schematic cross-sectional view of an intramedullary pin according to a first embodiment;
FIG. 3 is an enlarged schematic view at A in FIG. 2;
FIG. 4 is a schematic view of the structure of a second prosthesis provided in accordance with the first embodiment;
FIG. 5 is a schematic view of a magnetic driving platform according to a second embodiment;
fig. 6 is a schematic diagram of an internal structure of a magnetic driving platform according to a second embodiment.
In the figure:
1. a first prosthesis; 101. a first through hole;
2. a second prosthesis; 201. a second through hole; 202. a boss;
3. a primary bone; 301. a first fractured bone; 302. a second fractured bone;
4. a magnetic block;
5. a reduction gearbox; 501. an input shaft; 502. an output shaft;
6. a screw rod;
7. a nut;
8. a panel;
9. a frame; 901. a first upright; 902. a second upright; 903. a third upright; 904. a fourth upright; 905. a first upper cross bar; 906. a first middle cross bar; 907. a second middle cross bar; 908. a third middle cross bar; 909. a first lower cross bar; 910. a second bottom rail; 911. a third bottom rail;
10. a first separator;
11. a display screen;
12. an alternating magnetic field generator;
13. a saddle;
14. a universal wheel;
15. a handle;
16. a first fixed needle;
17. a second fixed needle;
18. and (5) a plastic sealing plate.
Detailed Description
The technical scheme of the invention is further described below by the specific embodiments with reference to the accompanying drawings.
Example 1
As shown in fig. 1 to 4, an intramedullary pin includes a first prosthesis 1 and a second prosthesis 2. A first through hole 101 penetrating through the first prosthesis 1 is formed at a first end of the first prosthesis 1, and a first cavity is formed at a second end of the first prosthesis 1; the first end of the second prosthesis 2 is provided with a second cavity and extends into the first cavity, and the second end of the second prosthesis 2 is provided with a second through hole 201 penetrating the second prosthesis 2. The first cavity is sequentially provided with a magnetic block 4, a reduction gearbox 5 and a screw rod 6 from one end close to the second prosthesis 2 to one end far from the second prosthesis 2; the input shaft 501 of the reduction gearbox 5 rotates around the axis of the input shaft 501 under the drive of the magnetic block 4, the lead screw 6 rotates around the axis of the screw rod 6 under the drive of the output shaft 502 of the reduction gearbox 5, and the lead screw 6 extends into the second cavity and is in threaded connection with the second cavity. The first prosthesis 1 is slidingly connected with the second prosthesis 2 along the extension direction of the screw rod 6.
Specifically, the primary bone 3 in the human body is broken into a first broken bone 301 and a second broken bone 302. Implantation of an intramedullary pin into a human body: inserting the first end of the first prosthesis 1 into the first fractured bone 301 along the extending direction of the first fractured bone 301, and fixedly connecting the first fractured bone 301 with the first prosthesis 1 by penetrating the first through hole 101 with the first fixing needle 16; the second end of the second prosthesis 2 is inserted into the second fractured bone 302 in the extending direction of the second fractured bone 302, and the second fractured bone 302 is fixedly connected to the second prosthesis 2 by penetrating the second penetration hole 201 using the second fixing needle 17. Over time, the human body may grow, and thus, it is necessary to appropriately lengthen the overall length of the intramedullary pin to achieve bone stretching (increase the distance between the first broken bone 301 and the second broken bone 302). At this time, the limb into which the intramedullary pin has been implanted is placed in an alternating magnetic field, and the S pole and the N pole of the alternating magnetic field are constantly and alternately changed, and the magnetic block 4 rotates around its own axis at a high speed under the action of the alternating magnetic field. The magnetic block 4 rotating at high speed drives the input shaft 501 of the reduction gearbox 5 to rotate, and the output shaft 502 drives the screw rod 6 to rotate. Because the first prosthesis 1 and the second prosthesis 2 can only be connected in a sliding manner along the extending direction of the screw rod 6, and relative rotation perpendicular to the extending direction of the screw rod 6 cannot occur, when the screw rod 6 is in threaded connection with the second cavity, the second cavity is far away from the reduction gearbox 5 along the extending direction of the screw rod 6, and finally the whole length of the intramedullary pin is increased, so that the distance between the first broken bone 301 and the second broken bone 302 is increased. Of course, according to this principle, the second cavity may be made to approach the reduction gearbox 5 along the extension direction of the screw rod 6, and finally the overall length of the intramedullary pin is reduced, so that the distance between the first broken bone 301 and the second broken bone 302 is reduced.
In this embodiment, the magnetic block 4 is fixed on the input shaft 501 of the reduction gearbox 5, and the axis of the magnetic block 4 is on the same line with the axis of the input shaft 501 of the reduction gearbox 5; the output shaft 502 of the reduction gearbox 5 is fixedly connected with the screw rod 6, and the axis of the output shaft 502 of the reduction gearbox 5 is in the same straight line with the axis of the screw rod 6. In other embodiments, the magnetic block 4 is fixed on a first shaft, and the first shaft is connected with the input shaft 501 of the reduction gearbox 5 through a gear, a belt or a chain; the output shaft 502 of the reduction gearbox 5 is connected with the screw rod 6 through a gear, a belt or a chain.
In this embodiment, a chute is provided on the inner wall of the first cavity, a boss 202 is provided on the outer surface of the first end of the second prosthesis 2, and the boss 202 is inserted into the chute and slidingly connected with the chute; the extending direction of the sliding groove is parallel to the extending direction of the screw rod 6. In other embodiments, the inner wall of the first cavity is provided with a boss 202, the outer surface of the first end of the second prosthesis 2 is provided with a chute, and the boss 202 is inserted into the chute and is in sliding connection with the chute; the extending direction of the sliding groove is parallel to the extending direction of the screw rod 6, so that the first prosthesis 1 and the second prosthesis 2 are in sliding connection along the extending direction of the screw rod 6.
In this embodiment, the magnet 4 is a permanent magnet. Specifically, setting the magnet 4 as a permanent magnet can avoid the risk of the magnet 4 being demagnetized. In other embodiments, the magnet 4 may be a common magnet.
In the embodiment, 2 through grooves are formed in one end, close to the magnetic block 4, of the first prosthesis 1, and the through grooves are communicated with the first cavity and the external space of the first prosthesis 1; the through grooves are filled with plastic closure plates 18. Specifically, after the intramedullary pin is implanted into a human body, a patient has a large impact load when walking, standing or running, so that the main body part of the intramedullary pin (including the first prosthesis 1, the second prosthesis 2 and the like) generally adopts a metal structure to increase the strength of the intramedullary pin, but the metal structure can cause shielding effect on a magnetic field, therefore, a through groove is required to be formed on the first prosthesis 1 around the magnetic block 4, and a plastic sealing plate 18 made of plastic material is implanted, so that the intramedullary pin not only can play a role of coating and protecting the magnetic block 4, but also can ensure that an external alternating magnetic field can act on the magnetic block 4 through the plastic sealing plate 18. In other embodiments, the number of through slots may be 1, 3, 4, or more.
In this embodiment, the reduction gearbox 5 further includes a reduction gear set, and the input shaft 501 of the reduction gearbox 5 and the output shaft 502 of the reduction gearbox 5 are connected through the reduction gear set; the ratio of the rotation speed of the input shaft 501 of the reduction gearbox 5 to the rotation speed of the output shaft 502 of the reduction gearbox 5 is equal to 1000:1. in other embodiments, the ratio of the rotational speed of the input shaft 501 of the reduction gearbox 5 to the rotational speed of the output shaft 502 of the reduction gearbox 5 is equal to 1100: 1. 1200: 1. 1300:1 or even greater. Specifically, the magnetic block 4 is in a cylindrical structure and is magnetized along the radial direction, and the material is neodymium iron boron magnetic material. The main purpose of the design of the reduction gearbox 5 is to obtain a large output torque and thus turn the screw 6. A large number of experiments show that when the reduction ratio is above 1000:1, the intramedullary pin can effectively overcome the tensile force between human tissue structures, and the output torque can be smoother through the linear driving force of the second prosthesis 2 converted by the lead screw.
In this embodiment, the screw pitch of the screw 6 is 1mm, and if necessary, it may be extended twice a day by 0.5mm each time. Since the reduction ratio is 1000 or more, it takes 1000 rotations or more of the magnet 4 per 1mm of movement of the second prosthesis 2, and the alternating frequency of the external driving magnetic field is 50Hz (3000 RPM), it takes about 3.5 minutes per 1mm of movement of the second prosthesis 2. Such a drive speed and extension time is acceptable for limb extension because the patient also needs to adapt slowly to the discomfort caused to him or herself while extending, without additional damage to the patient's body. In other embodiments, the pitch of the screw 6 is 0.8mm, 0.9mm, 1.1mm or 1.2mm.
In this embodiment, a nut 7 is installed at one end of the second cavity near the reduction gearbox 5, the axis of the nut 7 is on the same line with the axis of the output shaft 502 of the reduction gearbox 5, and the nut 7 is in threaded connection with the screw rod 6. Thereby realizing a threaded connection of the second cavity with the screw 6. In other embodiments, the threads may be directly machined into the second cavity, thereby achieving threaded connection of the second cavity to the screw 6.
In this embodiment, the diameter of the first prosthesis 1 is equal to the diameter of the second end of the second prosthesis 2 is equal to 10mm. Specifically, the outer diameter of the intramedullary pin (i.e., the outer diameter of the first prosthesis 1 and the outer diameter of the second end of the second prosthesis 2) may also be 8.5mm, 10.5mm, 12.5mm, etc. to accommodate patients with different bone sizes. As the lead screw 6 rotates, the second prosthesis 2 pushes the second fractured bone 302 to move, increasing the length of the defect segment, and achieving the purpose of extending the length of the limb. In other embodiments, the diameter of the first prosthesis 1 is 8.5mm and the diameter of the second prosthesis 2 is 9mm.
Example two
The embodiment provides a magnetic drive platform which can be matched with the intramedullary pin in the first embodiment to work so as to provide a driving magnetic field for the intramedullary pin, thereby realizing bone fracture extension without secondary operation.
As shown in fig. 5 to 6, a magnetic drive platform comprises a frame 9 and a panel 8 covering the frame 9. The frame 9 comprises a first upright 901, a second upright 902, a third upright 903 and a fourth upright 904, all arranged vertically; the lengths of the first upright 901 and the second upright 902 are equal, the lengths of the third upright 903 and the fourth upright 904 are equal, and the length of the first upright 901 is greater than the length of the second upright 902; the upper end of the third vertical rod 903 is connected with the first vertical rod 901 through a first upper cross rod 905, the upper end of the third vertical rod 903 is connected with the upper end of the fourth vertical rod 904 through a second upper cross rod, and the upper end of the fourth vertical rod 904 is connected with the second vertical rod 902 through a third upper cross rod; the middle part of the third vertical rod 903 is connected with the first vertical rod 901 through a first middle cross rod 906, the middle part of the third vertical rod 903 is connected with the middle part of the fourth vertical rod 904 through a second middle cross rod 907, and the middle part of the fourth vertical rod 904 is connected with the second vertical rod 902 through a third middle cross rod 908; the lower end of the third upright 903 is connected to the first upright 901 by a first lower cross bar 909, the lower end of the third upright 903 is connected to the lower end of the fourth upright 904 by a second lower cross bar 910, and the lower end of the fourth upright 904 is connected to the second upright 902 by a third lower cross bar 911. An alternating magnetic field generator 12 is arranged between the first upper cross bar 905 and the first middle cross bar 906, two support rods with the extending direction parallel to that of the second middle cross bar 907 are arranged on the first middle cross bar 906 and the third middle cross bar 908, a saddle 13 is arranged on the support rods, and the alternating magnetic field generator 12 is fixed on the saddle 13. The alternating magnetic field generator 12 comprises a housing and a coil positioned inside the housing, and a cylindrical treatment channel is arranged in the middle of the alternating magnetic field generator 12, and the axis of the treatment channel is parallel to the extending direction of the second middle cross bar 907. The two side surfaces of the panel 8 perpendicular to the axis of the treatment channel are provided with treatment through holes, the axis of the treatment through holes and the axis of the treatment channel are on the same straight line, and the treatment through holes are communicated with the external space of the panel 8 and the treatment channel.
Specifically, the limb (upper arm, lower arm, thigh, shank, etc.) into which the intramedullary pin has been implanted is extended into the treatment channel, and then the magnetic drive platform is activated. The alternating magnetic field generator 12 generates an alternating magnetic field at the periphery of the limb, and the magnetic block 4 can rotate around the axis of the alternating magnetic field at a high speed under the action of the alternating magnetic field. The magnetic block 4 rotating at high speed drives the input shaft 501 of the reduction gearbox 5 to rotate, and the output shaft 502 drives the screw rod 6 to rotate. Because the first prosthesis 1 and the second prosthesis 2 can only slide along the extending direction of the screw rod 6 and cannot rotate relatively perpendicular to the extending direction of the screw rod 6, when the screw rod 6 is in threaded connection with the second cavity, the second cavity is far away from the reduction gearbox 5 along the extending direction of the screw rod 6, and finally the overall length of the intramedullary pin is increased. Of course, according to this principle, it is also possible to bring the second cavity close to the reduction gearbox 5 in the direction of extension of the screw rod 6, eventually achieving a reduction of the overall length of the intramedullary pin. The axis of the treatment channel is horizontally arranged, so that a human body can conveniently sit to extend hands into the treatment channel or can conveniently lie to extend feet into the treatment channel. Therefore, the purpose of prolonging broken bones without secondary operation can be achieved. Furthermore, the basic principle of the magnetic drive platform is that alternating current is converted into alternating magnetic field, non-contact remote driving can be realized on the magnetic blocks 4 in the magnetic field range, especially in the field of medical surgery including orthopedics, the magnetic drive platform can remotely drive the magnetic blocks 4 in a human body to rotate in a non-contact state, and further non-invasive extension prosthesis operation without secondary operation is realized. Specifically, the frame 9 adopts an integral welding steel structure design, the panel 8 is made of bent steel plates, and the structure is compact and firm and is not easy to damage.
In this embodiment, the first top rail 905 and the third top rail are provided with a first partition board 10 disposed horizontally; the control device is fixed on the first partition board 10 through bolts, and the control device is electrically connected with the alternating magnetic field generator 12. Specifically, the control device comprises a DSP digital chip, a PID closed-loop control system, a PLC control unit and the like. The control device can intelligently control the power supply voltage, the power supply frequency, the magnetic field intensity, the magnetic field frequency and the like, and can correspondingly adjust according to actual requirements so as to achieve the optimal operation effect.
The display screen 11 is arranged on the panel 8, and the distance from the upper part of the display screen 11 to the first upright 901 is smaller than the distance from the lower part of the display screen 11 to the first upright 901; the display screen 11 is used for providing a man-machine interaction interface, and the display screen 11 is electrically connected with the control device. Specifically, setting the display screen 11 obliquely upward facilitates the patient or medical person to view the display screen 11 from top to bottom and to perform operations on the display screen 11. The user can directly read the working state of the magnetic drive platform through the display screen 11, including the working state and working parameters such as battery voltage, battery current, magnetic field intensity, magnetic field frequency, and the like, and can set and adjust the parameters according to actual needs. In this embodiment, the display screen 11 is a touch screen. Specifically, the touch screen is convenient and quick, easy to use, simple and visual. In other embodiments, the display screen 11 is a non-touch screen, and works in cooperation with physical keys electrically connected to the control device.
The first lower cross bar 909 and the third lower cross bar 911 are provided with a second partition plate horizontally arranged; the power supply system is fixed on the second partition board; a power system is located between the first bottom rail 909 and the first middle rail 906, the power system being electrically connected to the control means. In this embodiment, the power system includes a rectifying device, a dc power distribution device, a battery pack, a dc converter, and a rack power device. Specifically, the power supply system may convert the direct current of the battery pack into alternating current, thereby obtaining alternating current. The magnetic drive platform with the storage battery can be moved to any medical position at will without being limited by the position of the socket, and is convenient to use. In other embodiments, the power supply system may not be equipped with a battery pack, and may directly convert 220V household ac power into high-frequency exchange current.
In this embodiment, four universal wheels 14 are provided at the bottom of the frame 9, and handles 15 are provided at the front and rear of the panel 8. Specifically, four universal wheels 14 are additionally arranged at the bottom of the frame 9 so as to facilitate the integral movement, and a handle 15 is arranged on the panel 8 so as to facilitate the push-pull of the magnetic drive platform.
The terms "first," "second," "third," and the like herein are merely used for descriptive purposes and are not intended to be limiting.
It should be noted that the specific features described in the above embodiments may be combined in any suitable manner, and in order to avoid unnecessary repetition, the present invention will not be described in any detail with respect to the possible combinations.
Moreover, any combination of the various embodiments of the invention can be made without departing from the spirit of the invention, which should also be considered as disclosed herein.
Claims (5)
1. An intramedullary pin, which is characterized in that,
comprising a first prosthesis and a second prosthesis;
a first through hole penetrating through the first prosthesis is formed in the first end of the first prosthesis, and a first cavity is formed in the second end of the first prosthesis; the first end of the second prosthesis is provided with a second cavity and extends into the first cavity, and the second end of the second prosthesis is provided with a second through hole penetrating through the second prosthesis;
the first cavity is sequentially provided with a magnetic block, a reduction gearbox and a screw rod from one end far away from the second prosthesis to one end close to the second prosthesis; the input shaft of the reduction gearbox rotates around the axis of the input shaft under the drive of the magnetic block, the screw rod rotates around the axis of the screw rod under the drive of the output shaft of the reduction gearbox, and the screw rod extends into the second cavity and is in threaded connection with the second cavity;
the first prosthesis is connected with the second prosthesis in a sliding manner along the extending direction of the screw rod;
a plurality of through grooves are formed in one end, close to the magnetic block, of the first prosthesis, the through grooves are communicated with the first cavity and the external space of the first prosthesis, and plastic sealing plates are filled in the through grooves;
the speed reduction box further comprises a speed reduction gear set, and an input shaft of the speed reduction box is connected with an output shaft of the speed reduction box through a gear of the speed reduction gear set;
the magnetic block is fixed on the input shaft of the reduction gearbox, and the axis of the magnetic block and the axis of the input shaft of the reduction gearbox are in the same straight line;
the output shaft of the reduction gearbox is fixedly connected with the screw rod, and the axis of the output shaft of the reduction gearbox and the axis of the screw rod are on the same straight line;
the inner wall of the first cavity is provided with a boss, the outer surface of the first end of the second prosthesis is provided with a chute, and the boss is inserted into the chute and is in sliding connection with the chute;
the extending direction of the sliding groove is parallel to the extending direction of the screw rod; or alternatively, the first and second heat exchangers may be,
the inner wall of the first cavity is provided with a chute, the outer surface of the first end of the second prosthesis is provided with a boss, and the boss is inserted into the chute and is in sliding connection with the chute;
the extending direction of the sliding groove is parallel to the extending direction of the screw rod.
2. The intramedullary pin of claim 1, wherein the magnet is a permanent magnet.
3. An intramedullary pin according to claim 1, wherein a pitch of the lead screw is above 0.8mm and below 1.2mm.
4. An intramedullary pin as defined in claim 1, wherein,
and a nut is arranged at one end of the second cavity, which is close to the reduction gearbox, the axis of the nut and the axis of the output shaft of the reduction gearbox are on the same straight line, and the nut is in threaded connection with the screw rod.
5. An intramedullary pin as defined in claim 1, wherein,
the diameter of the first prosthesis is above 8.5mm and below 12.5 mm;
the second end of the second prosthesis has a diameter of 8.5mm or more and 12.5mm or less.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710610631.9A CN107280747B (en) | 2017-07-25 | 2017-07-25 | Intramedullary pin |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710610631.9A CN107280747B (en) | 2017-07-25 | 2017-07-25 | Intramedullary pin |
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| CN107280747B true CN107280747B (en) | 2024-04-02 |
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|---|---|---|---|---|
| FR2758976A1 (en) * | 1997-01-31 | 1998-08-07 | Jean Louis Herve | Femoral bone growth prosthesis |
| EP2068724A2 (en) * | 2006-10-03 | 2009-06-17 | Arnaud Soubeiran | Intracorporeal elongation device with a permanent magnet |
| CN101500501A (en) * | 2006-06-13 | 2009-08-05 | 阿诺·苏贝朗 | Device for intrabody extension with screws working in traction |
| CN105662663A (en) * | 2016-03-18 | 2016-06-15 | 王威 | Implant capable of automatically extending |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7481841B2 (en) * | 2004-06-30 | 2009-01-27 | Depuy Products, Inc. | Adjustable orthopaedic prosthesis and associated method |
| RU2016101629A (en) * | 2009-09-04 | 2018-12-04 | Нувэйсив Спешилайзд Ортопэдикс, Инк. | DEVICE AND METHOD FOR BONE EXTENSION |
| US20140052134A1 (en) * | 2012-02-08 | 2014-02-20 | Bruce Orisek | Limb lengthening apparatus and methods |
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2017
- 2017-07-25 CN CN201710610631.9A patent/CN107280747B/en active Active
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| FR2758976A1 (en) * | 1997-01-31 | 1998-08-07 | Jean Louis Herve | Femoral bone growth prosthesis |
| CN101500501A (en) * | 2006-06-13 | 2009-08-05 | 阿诺·苏贝朗 | Device for intrabody extension with screws working in traction |
| EP2068724A2 (en) * | 2006-10-03 | 2009-06-17 | Arnaud Soubeiran | Intracorporeal elongation device with a permanent magnet |
| CN105662663A (en) * | 2016-03-18 | 2016-06-15 | 王威 | Implant capable of automatically extending |
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| CN107280747A (en) | 2017-10-24 |
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