KR20180093292A - Implant for bone substitute - Google Patents

Abstract

A bone substitute implant is provided. The bone substitute implant according to an embodiment of the present invention comprises: a synostosis member which comprises a body made of a bioactive crystallized glass material, and which is in contact with the surface of an adjacent bone so as to fuse therewith; an implant body to be fixed between adjacent bones; and a buffer member arranged between the synostosis member and the implant body so that the synostosis member and the implant body are spaced from each other. An embodiment of the present invention is to provide the bone substitute implant which is easy to perform a surgery and can improve the synthesis of bone and mechanical stability.

Description

Implant for bone substitute < RTI ID = 0.0 >

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a bone replacement implant, and more particularly, to a bone replacement implant which is easy to perform and can improve the compatibility with bone and mechanical stability.

In general, bone replacement implants are intended to replace bone that has been removed or lost due to lesions, and spinal implants to replace the vertebral body or the chordae are typical.

Conventionally, these bone substituting implants are made of a metal such as titanium (Ti) or a polymer material such as polyetheretherketone (PEEK), and these materials differ from each other in bone composition.

Here, such an implant material is not highly compatible with the bone, and bone graft materials are essentially used separately to overcome the low compatibility with the bone.

However, in order to apply such a bone graft material, the implant must have a structure capable of effectively receiving the bone graft material, and there is a problem in that it is troublesome to perform the bone graft material at the time of the procedure.

In addition, even when bone graft materials are used, efforts to improve the synergy between the bone graft and the implant have been performed since the low fluidity of the implant material in direct contact with the bone is not sufficient to assist the fusion between the implant and the bone , There is still no fundamental solution.

JP 2013-169465 A (Public date 2013.09.02) JP 2011-092712 A (Public date 2011.05.12)

In order to solve the problems of the prior art as described above, one embodiment of the present invention is to provide a bone substitute implant which is easy to perform and can improve the synthesis of bone and mechanical stability.

According to an aspect of the present invention, there is provided a bone union member including a body made of a bioactive crystallized glass material and adapted to contact and coalesce with a surface of an adjacent bone; An implant body for securing between adjacent corrugations; And a buffer member disposed between the bone union member and the implant body to separate the bone union member and the implant body from each other.

In one embodiment, the implant body is made of titanium (Ti), and the buffer member may be made of polyetheretherketone (PEEK).

In one embodiment, the bioactive glass material may include CaSiO ₃ , apatite, and Ca ₂ Mg (Si ₂ O ₇ ) in a weight ratio of 1: 0.7 to 1.5: 0.5 to 1.2.

In one embodiment, the body may be manufactured by CAD / CAM or 3D printing based on the medical image information of the patient.

In one embodiment, the bone union member is embedded in a space between an adjacent first vertebra and a second vertebra, and the body has a shape corresponding to a surface shape of each of the first vertebra and the second vertebra, And a plate fixed to the first vertebra and a plate fixed to the first vertebra, wherein a groove for engaging the buffer member is provided on a side of the body.

In one embodiment, the buffer member includes: a pair of supports for coupling to the body of the bone union member; And a center portion connecting the pair of supports, and the support portion may be inserted and coupled to the groove portion of the body of the bone union member in a fitting manner.

In one embodiment, the implant body fixes between the adjacent first and second transducers, and the body is formed in a rectangular shape, and a side surface of the body corresponds to a contact surface of each of the first transseptal and the second transseptal Wherein the implant body has a first plate for fixing to one side of the first and second transverse bows, and a second plate for fixing to the other side of the first transverse bellows and the second transverse bellows, 2 plate, and a through hole through which the shaft of the first plate and the buffer member are inserted may be provided at a central portion of the body.

In one embodiment, the cushioning members are formed in a pair, and each of the pair of cushioning members is formed in a plate shape so as to be spaced apart from the first plate or the second plate and the bending member, A plate-shaped spacing portion having a through-hole having a shape corresponding to the shaft of the first plate; And an insertion portion extending from the spacer to form a side wall of the through hole and inserted into the through hole of the bony member so as to separate the shaft and the bony member from each other.

In one embodiment, the implant body replaces any one of a plurality of vertebrae connected to each other, and the bony union member includes upper and lower bony members having a shape corresponding to the surface of the vertebra and spaced apart from each other The implant body may include a length adjuster disposed between the upper and lower bone union members and adjusting a distance between the upper and lower bone union members through a sliding movement during a user's operation to vary the overall length.

In one embodiment, the implant body is made of a hollow metal material having open top and bottom, and the upper side is fixedly coupled to the upper union member; And a second case made of a hollow metal material having an open top and a bottom, a lower side fixedly coupled to the lower union member, and a second case slidably coupled to the first case, The cushioning member is disposed between the opposing faces of the first case and the upper union member and between the opposing faces of the second case and the lower union member and is formed to protrude in one direction from the body of the upper union member and the lower member And can be coupled to the projection side.

The bone substitute implant according to an embodiment of the present invention can improve the compatibility with the bone and improve the mechanical stability by using a material having high fusion strength and strength with the bone.

In addition, the present invention provides a buffer member between a brittle union member and a high-strength implant body to suppress breakage of the bony member by an external force, thereby further improving the mechanical stability.

Further, according to the present invention, the area of the union portion can be increased to further promote fusion with the bone, and the position between the bones can be more stably fixed.

Further, since it is not necessary to provide a separate bone graft material, the present invention facilitates the procedure without the hassle of applying the bone graft material at the time of the procedure, thereby shortening the procedure time and improving convenience for patients and medical staff.

1 is a view showing a use state of a bone substitute implant according to a first embodiment of the present invention,
FIG. 2 is a view showing a use state of a bone substitute implant according to a second embodiment of the present invention,
3 is a view showing a use state of a bone substitute implant according to a third embodiment of the present invention,
Fig. 4 is a perspective view of the bone substitute implant of Fig. 1,
5 is an exploded perspective view of FIG. 5,
Figure 6 is a perspective view of the bone substitute implant of Figure 2,
FIG. 7 is a perspective view showing a state in which a part of the second plate is removed in FIG. 6,
FIG. 8 is a perspective view of the second plate in FIG. 6,
Fig. 9 is an exploded perspective view of the union unit and the buffer unit in Fig. 5,
FIG. 10 is a view showing a state before the operation tool is fastened in the bone substitute implant of FIG. 3;
11 is a view showing the separation of Fig. 10,
12 is a sectional view of Fig. 10, and Fig.
13 is a view showing a state in which the locking screw is fastened in Fig.

Hereinafter, exemplary embodiments of the present invention will be described in detail with reference to the accompanying drawings, which will be readily apparent to those skilled in the art to which the present invention pertains. The present invention may be embodied in many different forms and is not limited to the embodiments described herein. In order to clearly illustrate the present invention, parts not related to the description are omitted, and the same or similar components are denoted by the same reference numerals throughout the specification.

Hereinafter, a bone substitute implant according to an embodiment of the present invention will be described in detail with reference to the drawings.

1 to 3, the bone replacement implant 100, 200, 300 according to the embodiment of the present invention includes the bone union members 110, 210, 310 to 320, the implant bodies 120, 220 to 230, 330 to 370 and the buffer members 130,

Here, the bone replacement implant 100 as shown in FIG. 1 is a first embodiment of the present invention, and may be an implant for replacing a chordal body such as liver cartilage or the like. The bone substitute implant 100 is embedded in a space between the adjacent first and second vertebrae 11 and 12.

The bone substitute implant 200 as shown in Fig. 2 is a second embodiment of the present invention for fixing between adjacent gyroscopes, and may be a gyroscopic implant. The bone substitute implant 200 is inserted between the adjacent first and second spacer rings 21 and 22 and fixed to both sides of the first spacer ring 21 and the second spacer ring 22.

The bone substitute implant 300 as shown in FIG. 3 is a third embodiment of the present invention for performing a role of a vertebral body substituted for any one of a plurality of vertebrae connected to each other, . Here, the replaced vertebral body may be a vertebral body in which damage or loss due to a lesion has occurred.

The bone union members 110, 210, and 310 to 320 are for contacting the surface of the adjacent bone and fusing with the bone, and may include a body made of a bioactive crystallized glass material. Bioactive crystallized glass materials may include CaSiO _3. The biologically active glass material is Ca ₁₀ (PO ₄ ) ₆ A (wherein A is an oxygen atom) and Ca ₁₀ (PO ₄ ) 6 B ₂ (wherein B is a hydroxyl group, a fluorine atom or a chlorine atom). ) And Ca ₂ Mg (Si ₂ O ₇ ). Here, the Sans body active crystallization glass material may include CaSiO ₃ , apatite, and Ca ₂ Mg (Si ₂ O ₇ ) in a weight ratio of 1: 0.7 to 1.5: 0.5 to 1.2.

Since such a bioactive crystallized glass material has bone fusion characteristics and a large strength, it can effectively replace defective tissue defects of a living body or promote skeletal and fusion when it is implanted in a living body.

Therefore, since there is no need to provide a separate bone graft material, it is easy to perform the procedure without the hassle of applying the bone graft material at the time of the procedure, thereby shortening the procedure time, thereby improving convenience for patients and medical staff.

The body of the union members 110, 210, 310 to 320 may have a shape corresponding to the surface shape of the contacted bones. For example, the body of the union members 110, 210, 310 to 320 may be manufactured by CAD / CAM or 3D printing based on medical image information of the patient. The body of the union members 110, 210, and 310 to 320 may be inclined or curved in contact with the contacting corrugations.

Accordingly, the bony members 110, 210, and 310 to 320 can be manufactured to be substantially similar or identical to the shape of the bone of the patient, thereby minimizing the anatomical mismatch between the vertebrae.

The implant bodies 120, 220 to 230, and 330 to 370 are for fixing between adjacent bones and may have various structures depending on the application region of the bone substitute implants 100, 200, and 300. The implant bodies 120, 220 to 230, and 330 to 370 may have a structure for replacing the intervertebral body, replacing the vertebral body, or fixing the intervertebral body.

Here, the implant bodies 120, 220 to 230, and 330 to 370 may be made of titanium (Ti). For example, the implant bodies 120 and 330 to 370 may be made of titanium, and the implant bodies 220 and 230 may be made of a Ti-6Al-4V material.

The cushioning members 130, 240 and 380 are made of polyetheretherketone (PEEK), and are disposed between the bone union members 110, 210 and 310 to 320 and the implant bodies 120, 220 to 230, and 330 to 370 to form the bone union members 110, 210, and 310 to 320 and the implant body 220-230, 330-370).

The cushioning members 130, 240 and 380 are used to separate the bony union members 110, 210 and 310 to 320 and the metal implant bodies 120, 220 to 230 and 330 to 370 from each other. The bony members 110, 210 and 310 to 320 and the implant bodies 120, 220 to 230 and 330 370 are directly in contact with each other, it can be prevented from being damaged by an external force applied from the human body or adjacent corrugations.

4 and 12, the bone substitute implant 100, 200, 300 according to the embodiment of the present invention will be described in more detail.

The bone substitute implant 100 in the first embodiment of the present invention includes a bone union member 110, a plate 120, and a cushioning member 130, as shown in Figs. Here, the plate 120 corresponds to the implant body.

The bone substitute implant 100 may be coupled to the first vertebra 11 by a first screw 140a and may be coupled to the second vertebra 12 by a second screw 140b.

At this time, the bony union member 110 is embedded between the first and second bones 11 and 12, and the plate 120 is fixed to one end of the first bones 11 and the second bones 12 Can be fixed.

The union member 110 may include a body 110a made of a bioactive crystallized glass material. The body 110a may have a shape corresponding to the respective surface shapes of the first and second vertebrae 11 and 12. For example, the body 110a may be manufactured by CAD / CAM or 3D printing based on medical image information of the patient. The body 110a may be formed such that the surfaces thereof contacting the first and second vertebrae 11 and 12 are inclined.

Here, the body 110a may have grooves 111a, 111b, and 111c along its sides. At this time, the support portion 131 of the buffer member 130 may be inserted into the groove portion 111a on both sides of the body 110a.

The center portion 132 of the buffer member 130 is inserted into the groove portion 111b in front of the body 110a and the end of the support portion 131 of the buffer member 130 is inserted into the groove portion 111c at the rear, . That is, the body 110a may be formed by inserting the buffer member 130 into the groove portions 111a, 111b, and 111c and enclosing the buffer member 130.

The bony member 110 can be coupled to the plate 120 for fixing to the first and second vertebrae 11 and 12 through the buffer member 130. [

A plurality of protrusions 112 may be provided on the upper surface and the lower surface of the body 110a, that is, the surfaces contacting the first and second vertebrae 11 and 12, respectively, in one direction. Each of the protrusions 112 may have a predetermined thickness and length from the surface of the body 110a and may be provided at regular intervals from each other.

By this, it is possible to further promote the fusion with the bone by increasing the fusion area to be joined to the first and second vertebrae 11 and 12, and the fusion with the first vertebrae 11 and the second vertebrae 12 can be further promoted, The position of the body 110a between the corrugations can be more stably fixed.

In addition, the projecting portion 112 and the first and second reinforcement ribs 11 and 12 can improve the fixing force of the body 110a by friction between the first and second reinforcement ribs 11 and 12.

The plate 120 includes a body 121 made of titanium (Ti) and is fixed to the first vertebra 11 and the second vertebra 12 by a first screw 140a and a second screw 140b .

The plate 120 may have a first receiving hole 122a for accommodating the first screw 140a and a second receiving hole 122b for accommodating the second screw 140b on both sides of the body 121 have. The first receiving hole 122a and the second receiving hole 122b may be inclined at different angles. That is, since the first screw 140a and the second screw 140b are coupled to the first and second vertebrae 11 and 12 at different angles to each other, the first screw 140a and the second screw 140b, The first receiving hole 122a and the second receiving hole 122b may be inclined so that the first receiving hole 122a and the second receiving hole 122b are different from each other at an angle at which the first receiving hole 140b is inserted into the plate 120. [

The first receiving hole 122a and the second receiving hole 122b may be provided with threads for fastening the first screw 140a and the second screw 140b selectively.

The plate 120 also receives a locking screw 129 for locking the first screw 140a and the second screw 140b at a central portion between the first receiving hole 122a and the second receiving hole 122b A pair of receiving grooves 124 may be provided.

Here, the pair of receiving grooves 124 are separated from each other by the partition walls, and a communicating portion 125 communicating with the first receiving hole 122a and the second receiving hole 122b is provided at one side thereof . That is, the pair of receiving grooves 124 and the first receiving holes 122a and the second receiving holes 122b are overlapped with each other so that a part of them are communicated with each other.

This allows the head portion of the locking screw 129 to block a part of the first receiving hole 122a and the second receiving hole 122b in the communicating portion 125 so that the first screw 140a and the second screw 140b may not be released to the outside.

At this time, the locking screw 129 may include a first portion 129a, which is partly inwardly flanked on one side. Here, the first portion 129a may be formed in a shape corresponding to the communicating portion 125. That is, when the locking screw 129 is integrally provided on the plate 120, the first portion 129a is rotated so as to be positioned on the communicating portion 125, whereby the first receiving hole 122a and the second receiving hole The first screw 140a and the second screw 140b can be inserted into the first receiving hole 122a and the second receiving hole 122b without being blocked by the locking screw 129 have.

The plate 120 may be provided with at least one wedge portion 123 at a surface contacting the first vertebra 11 and at a surface contacting the second vertebra 12. 5, the plate 120 includes at least one wedge portion 123 (see FIG. 5) at positions symmetrical to each other on the lower surface of the first receiving hole 122a and the upper surface of the second receiving hole 122b, May be provided.

Here, the wedge portion 123 may be provided at a position opposite to the fastening direction of the first screw 140a and the second screw 140b. 4, when the first screw 140a is coupled to the upper side of the union member 110, the wedge portion 123 is disposed on the lower side of the first receiving hole 122a, The wedge part 123 can be disposed on the upper side of the second receiving hole 122b when the first receiving part 140b is coupled to the lower side of the union member 110. [

However, it is needless to say that the forming position of the wedge portion 123 can be changed according to the fastening direction of the first screw 140a and the second screw 140b.

The plurality of wedges 123 may be spaced apart from each other by a predetermined distance and may have a pointed tip such that one end thereof is fixed to the first or second vertebrae 11 or 12.

Accordingly, it is possible to suppress or minimize the torsion of the bone substitute implant 100 that may occur according to the movement of the patient, thereby further improving the structural stability. Therefore, it is possible to extend the service life of the bone substitute implant 100 have.

The plate 120 may have fastening protrusions 127 corresponding to the fastening grooves 135 of the buffer member 130 on both sides. The fastening protrusion 127 may be formed on the back side of the plate 120, that is, on the buffer member 130 side. Here, the fastening protrusion 127 may have one end bent toward the inside of the body 121. That is, the fastening protrusion 127 may be formed in the shape of a letter "A" on the rear surface of the body 121.

Thus, the plate 120 can be coupled to the buffer member 130 by a simple structure. Therefore, since the plate 120 can be formed to have a small thickness, the volume of the plate 120 can be minimized to increase the volume of the bone union member 110, .

The cushioning member 130 is made of polyetheretherketone (PEEK), and is disposed between the bending member 110 and the plate 120 to couple the bending member 110 and the plate 120 together. Here, the buffer member 130 may include a pair of support portions 131 and a central portion 132.

The pair of supporting portions 131 are for engaging with the body 110a of the bony union member 110 and can be inserted into the groove portion 111a of the body 110a. At this time, one end of the support portion 131 may include a bent portion 133 bent inward. Here, the bent portions 133 may be inserted into both sides of the groove portion 111c of the body 110a of the union member 110. [

The center portion 132 connects between the pair of support portions 131 and can be inserted into the groove portion 111b of the body 110a of the bone union member 110. [

The support portion 131 and the center portion 132 of the buffer member 130 are inserted into the groove portions 111a, 111b and 111c of the union member 110 respectively and can be inserted and coupled in a fitting manner.

A pair of guide grooves 134 are formed on both sides of the center portion 132 so that the first screw 140a and the second screw 140b are coupled to the first and second vertebrae 11 and 12 at a predetermined angle. . That is, since the first screw 140a and the second screw 140b are obliquely connected to the first and second vertebrae 11 and 12 as shown in FIG. 1, The center portion 132 of the buffer member 130 disposed in the buffer member 130 may be interfered with.

In order to solve this problem, a pair of guide grooves 134 may be formed in communication with the first receiving hole 122a and the second receiving hole 122b. At this time, the pair of guide grooves 134 may be disposed at positions symmetrical to each other on both sides of the central portion 132.

That is, the guide groove 134 corresponding to the first receiving hole 122a is disposed on the upper side in the center portion 132, and the guide groove 134 corresponding to the second receiving hole 122b is disposed on the lower side As shown in FIG.

Here, the guide groove 134 may be provided at the same position as the fastening direction of the first screw 140a and the second screw 140b. 4, when the first screw 140a is coupled to the upper side of the union member 110, the guide groove 134 corresponding to the first receiving hole 122a extends from the center 132 to the upper side And when the second screw 140b is coupled to the lower side of the union member 110, the guide groove 134 corresponding to the second receiving hole 122b may be disposed at the lower side of the central portion 132. [

However, the shape of the first receiving hole 122a, the second receiving hole 122b, and the pair of guide grooves 134 may be changed depending on the fastening direction or fastening manner of the first screw 140a and the second screw 140b Of course, be deformed.

The guide groove 134 may be opened upward or downward from the central portion 132. For example, the guide groove 134 may have a hemispherical shape.

This makes it possible to easily assure a variable coupling angle of the first screw 140a and the second screw 140b coupled to the first and second vertebrae 11 and 12.

The buffer member 130 may be provided with a coupling groove 135 for coupling the plate 120 to both sides of the central portion 132. The fastening groove 135 may be formed in a shape corresponding to the fastening protrusion 127 of the plate 120.

For example, the coupling groove 135 may be formed inwardly from one side of the support portion 131 on both sides of the central portion 132, as shown in Fig. The lower end 135a of the fastening groove 135 may extend from the support 131 so that the lower surface of the fastening protrusion 127 of the plate 120 is supported.

The plate 120 is coupled to the front surface of the cushioning member 130 and the joint member 110 is coupled to the rear surface of the cushioning member 130 so that the plate 120 and the joint unit 110 are spaced apart from each other And can be stably bonded.

6 to 9, the bone substitute implant 200 according to the second embodiment of the present invention includes a bone union member 210, a first plate 220, a second plate 230, and a cushioning member 240 ). Here, the first plate 220 and the second plate 230 correspond to the implant body.

The bone substitute implant 200 is adjusted by adjusting the length of the bone substitute implant 200 with respect to the second plate 230 through the thread 226 provided on the shaft 224 of the first plate 220, The first impeller 21 and the second impeller 22 can be pressed and fixed to both sides of the first impeller 21 and the second impeller 22, respectively.

At this time, the union member 210 may be embedded in the space between the first transducer 21 and the second transducer 22 so as to be in close contact with the mutually facing side surfaces of the first transducer 21 and the second transducer 22 .

The bony union member 210 may include a body 211 made of a bioactive crystallized glass material. The body 211 may have a shape corresponding to the shape of each of the first transducer 21 and the second transducer 22. For example, the body 211 can be manufactured by CAD / CAM or 3D printing based on the medical image information of the patient.

9, the body 211 has a concave shape at a position corresponding to the contact surfaces of the first transducer 21 and the second transducer 22 on the side surface of the body 211, A portion 212 may be provided. That is, the concave portion 212 may be provided on the side surface of the body 211 so that the side surfaces opposite to each other of the first transducer 21 and the second transducer 22 easily contact each other.

The concave portion 212 may be provided with a thread portion 212a having a thread structure. That is, a plurality of grooves or protrusions may be continuously formed at predetermined intervals in the recess 212 to have a thread structure.

As a result, the fusion with the bone can be further promoted by increasing the fusion area to be bonded to the first transducer 21 and the second transducer 22, and the first transducer 21, the second transducer 22, The position of the body 211 between the corrugations can be more stably fixed by the portion 212a.

In addition, the side surfaces of the thread portion 212a, the first separator 21 and the second separator 22 can further improve the fixing force of the body 211 by friction between them.

8, a through hole 213 into which the shaft 224 of the first plate 220 is inserted may be provided at a central portion of the body 211. As shown in FIG. In the through hole 213, a buffer member 240 separating the first plate 220 and the second plate 230 from the bony union member 210 may be inserted.

The through holes 213 extend in a shape corresponding to the shape of the buffer member 240, and can be formed into a substantially circular shape. The shaft 224 of the first plate 220 can be inserted into the through hole 243 of the buffer member 240 after the pair of buffer members 240 are inserted into the through hole 213 first.

Accordingly, the bony member 210 can be coupled to the first plate 220 and the second plate 230 with the buffer member 240 interposed therebetween.

The first plate 220 includes a body 221 made of titanium and is fixed to one side of the first transducer 21 and the second transducer 22. Here, the body 221 may be made of a Ti-6Al-4V material.

The first plates 220 may be formed as a pair, as shown in FIG. That is, the first plate 220 can be spaced apart from the second plate 230 according to the shapes of the first and second spacer members 21 and 22.

At this time, each of the pair of first plates 220 may be integrally provided with a shaft 224 inserted into the through hole 213 of the union member 210. Here, the shaft 224 may be provided on the center side in the pair of first plates 220. That is, the pair of first plates 220 may be provided with a shaft 224 on the side opposite to each other.

In addition, since the first plates 220 are formed as a pair, different shapes can be adopted depending on the part of the patient to be performed. For example, when the bone substitute implant 200 is inserted into the pelvis region, the first plate 220 disposed at the lower portion is formed in a shape suitable for the joint surface of the pelvis bone, and the first plate 220, May be provided in a shape suitable for the joint surface on the spinning wheel.

Here, the thread 226 may be provided in the sun region at one end of the shaft 224. These threads 226 may be serrated. At this time, the thread 226 is linearly moved by engaging with the thread of the gap adjusting member 236 of the second plate 230, as shown in FIG. 7, so that the gap between the first plate 220 and the second plate 230 Can be adjusted.

Here, one end 225 of the shaft 224 may have a pointed shape. That is, the shaft 224 may have a pointed shape through a chamfer at one end of the opposite side of the body 221, as shown in FIG.

In this way, the operation of inserting the first plate 220 into the space between the first transducer 21 and the second transducer 22 can be facilitated.

In addition, as shown in FIGS. 6 and 7, the body 221 may be provided with a receiving hole 223 for receiving a bone morphogenetic protein (BMP). The receiving hole 223 is formed to penetrate both sides of the body 221, thereby providing a pathway through which osseous protein (BMP) or fluid can move.

Thus, fusion between the bone substitute implant 200 and bone can be improved between the first transseptal 21 and the second transseptal 22.

The body 221 may be provided with a plurality of protrusions 222 on the inner surface of the shaft 224 on the side contacting the first oscillating ring 21 and the second oscillating ring 22. Here, as shown in FIG. 6, the first plate 220 may have a plurality of protrusions 222 on the inner side and the outer side. That is, the protrusion 222 may be provided on the opposite side of the body 221 on which the shaft 224 is provided.

The projecting portion 222 may have a pointed tip so as to be fixed to the first worm wheel 21 and the second worm wheel 22. At this time, the shape of the protrusion 222 may be different from each other depending on the portion to be fixed to the first transducer 21 and the second transducer 22.

Accordingly, it is possible to suppress or minimize the distortion of the bone substitute implant 200 that may occur according to the movement of the patient, thereby further improving the structural stability and thus extending the service life of the bone substitute implant 200 .

The second plate 230 includes a body 230a made of titanium and is fixed to the other side of the first transducer 21 and the second transducer 22. Here, the body 230a may be made of a Ti-6Al-4V material.

The second plate 230 may be integrally formed with the body 230a and the center of the body 230a may have a receiving hole 233 through which the shaft 224 of the first plate 220 is inserted.

7, a space adjusting member 236 is inserted into the space 235. The space adjusting member 236 is inserted into the space 235 at the upper side of the receiving hole 233, . At this time, the gap adjusting member 236 may be provided at the lower side with a thread having a shape corresponding to the thread 226 provided on the shaft 224 of the first plate 220.

A locking screw 237 for fixing the gap adjusting member 236 is provided on the upper side of the gap adjusting member 236. A fixing pin 239 for fixing the locking screw is fixed to one side of the locking screw 237, And a lock pin 238 for fixing the lock pin 239 may be provided.

The shaft 224 of the first plate 220 is inserted into the receiving hole 233 of the second plate 230 and then the distance adjusting member 236 is inserted into the receiving hole 233 of the shaft 224 The distance between the first plate 220 and the second plate 230 can be fixed by rotating the locking screw 237 and then inserting the locking pin 238 so as to be fixed to the thread 226 at that position .

Also, the body 230a may be provided with an extension guide 234 for guiding the receiving hole 233 to extend to the wrong side. The extension guide 234 may protrude outward from the body 230a, that is, on the opposite side of the first plate 220 to the outside.

The momentum can be received in the shaft 224 of the first plate 220 inserted into the receiving hole 233 and projecting to the outside of the second plate 230 to further improve the mechanical stability .

In addition, as shown in FIG. 8, the second plate 230 may be provided with a receiving hole 232 for receiving a bone morphogenetic protein (BMP). The receiving hole 232 is formed to penetrate both sides of the body 230a, thereby providing a passage through which the osteogenic protein (BMP) or the fluid can move.

Thus, fusion between the bone substitute implant 200 and bone can be improved between the first transseptal 21 and the second transseptal 22.

The body 230a may be provided with a plurality of protrusions 231 on a surface contacting the first oscillating ring 21 and the second oscillating ring 22, that is, on the inner surface facing the first plate 220 . Here, as shown in FIG. 8, the second plate 230 may have a plurality of protrusions 231 on the outer side in the inner side. That is, the protrusion 231 may be provided on both sides of the receiving hole 233 in the body 2310a.

The projecting portion 231 may have a sharp tip such that the protrusion 231 is fixed to the first transducer 21 and the second transducer 22. At this time, the shape of the protrusion 231 may be different from each other depending on a portion to be fixed to the first transducer 21 and the second transducer 22.

Accordingly, it is possible to suppress or minimize the distortion of the bone substitute implant 200 that may occur according to the movement of the patient, thereby further improving the structural stability and thus extending the service life of the bone substitute implant 200 .

Since the first plate 220 and the second plate 230 can be detachably coupled to each other, the bone replacement implant 200 can be easily removed without removing ligaments of the first and second wings 21 and 22, So that the recovery time of the patient can be shortened.

The cushioning member 240 is made of polyetheretherketone (PEEK) and is disposed between the bending member 210 and the first and second plates 220 and 230 to form the bending member 210 and the first plate 220, Thereby separating the second plate 220 and the second plate 230 from each other. Here, the buffer member 240 may include the spacing portion 241 and the insertion portion 242.

The spacing part 241 may be formed in a plate having a predetermined thickness so as to be spaced apart from the first plate 220 or the second plate 230 and the bony union member 210. That is, the spacing portion 241 may be formed in a plate shape such that both side surfaces of the buffer member 240 are spaced apart from the first plate 220 and the second plate 230, as shown in FIG.

At this time, the cushioning member 240 is separated from the first plate 220 and the second plate 230 and the bony member 210, and the shaft 224 of the first plate 220 is inserted into the cushioning member 240, Shape. Here, the outer diameter of the cushioning member 240 may be smaller than the width of the bony union member 210, and the inner diameter may be larger than the through-hole 213 of the bony union member 210.

The cushioning member 240 should be spaced from the shaft 224 of the first plate 220 within the through-hole 213 of the cushioning member 240 as shown in Fig. That is, the buffer member 240 should be inserted into the through hole 213 of the bony union member 210. The cushioning member 240 may be inserted into the through hole 213 of the joint unit 210 because the cushion member 241 is larger than the inner diameter of the through hole 213 of the joint member 210. In this case, . At this time, each of the pair of buffer members 240 may be inserted at both sides of the bony member 210, as shown in FIG.

In addition, a through hole 243 may be formed at the center of the spacing portion 241. The through hole 243 may have a shape corresponding to the shape of the shaft 224 of the first plate 220. For example, the through hole 243 may have a rectangular shape corresponding to the rectangular shaft 224.

The insertion portion 242 may extend from the spacing portion 241 to form a side wall of the through hole 243. [ Here, the insertion portion 242 may have a length corresponding to the thickness of the bony union member 210. That is, the length of the insertion portion 242 may be a length inserted into the through hole 213 of the union member 210. In this case, when the cushioning members 240 are a pair having the same shape, the lengths of the insertion portions 242 may be the same, but they may be different from each other.

The cushioning member 240 can be separated from the first plate 220 and the second plate 230 on both sides of the bending member 210 and the through hole 213 by the external force, It is possible to prevent breakage of the battery.

At this time, the body 221 of the pair of first plates 220 and the body 130a of the second plate 230 may be formed at the same inclination of about 45 degrees on both sides so as not to interfere with each other when they are arranged successively have.

Such a transdermal implant 200 can be used successively in series of translators. That is, between the first transducer 21 and the second transducer 22 and between the second transducer 22 and the third transducer (not shown).

Accordingly, it is possible to easily perform a plurality of transdermal implants 200 according to the extent and extent of damage of the vertebrae.

In the meantime, the transdermal implant 200 according to the second embodiment of the present invention can be provided in a form in which one side and the other side are different from each other depending on the part of the patient in which the first plate 120 and the second plate 130 are to be performed have. That is, in order to maximize the area in contact with the pelvic bones, the transdermal implant 200 can change the body of one side of the integral second plate 130 and the body of one side of the pair of first plates 120 into a wing shape have.

For example, in the impeller implant 200, both the first plate 220 and the second plate 230 may be bent at one side in the "B" or "B" shape.

That is, one plate of the pair of first plates 220 is formed of the body 121 as described above, and the other plate is formed of a body (not shown) ≪ / RTI >

The "b" shaped body (not shown) on one side of the first plate 220 and the "b" shaped body (not shown) on one side of the second plate 230 are arranged to contact the pelvic bones, And the other body 221 of the first plate 220 and the body 130a of the second plate 230 can be fixed to the joint surfaces of the pawl bones 11 and 12 .

Thus, the epiphyseal implant 200 can be easily fixed to the epiphysis adjacent to the pelvic bone, and thus can be used for the spinal diseases of the pelvic region.

10 to 13, the bone substitute implant 300 according to the third embodiment of the present invention includes the bone union members 310 and 320, the length adjusters 330, 340 and 350, the case 360 and 370, and the buffer member 380 . Here, the length adjusting portions 330, 340 and 350 and the case 360 and 370 correspond to the implant body.

The union members 310 and 320 are for interconnecting the two vertebrae 32 and 34 which are in direct contact with the surface of the vertebra of which the one surface is disconnected. That is, the bony union members 310 and 320 are provided in two and can be in contact with the two vertebrae 32 and 34, respectively, which are separated from each other by spacing apart from each other through the length adjusting unit.

For this purpose, the union members 310 and 320 include an upper union member 310, which is in contact with the surface of the vertebral body 32 positioned on the upper side of the two vertebra bodies 32 and 34 that are disconnected from each other, And a lower union member 320 that is in contact with the surface 34 of the vertebral body on one side.

One of the surfaces of the union members 310 and 320 contacting the vertebral body may have a shape corresponding to the surface shape of the vertebral body. In one example, one side of the union members 310 and 320 can be manufactured by CAD / CAM or 3D printing based on the medical image information of the patient. Here, one surface of the union members 310 and 320 that are in contact with the vertebral body may have a horizontal surface or an inclined surface.

For example, the bone union members 310 and 320 may include bodies 312 and 322 having contact surfaces corresponding to one surface of the vertebral body and protrusions 314 and 324 extending a predetermined length on the opposite surface of the contact surface, A buffer member 380 described later can be fastened.

Here, the upper un-united member 310 of the union members 310 and 320 may be coupled to the power transmitting member 350 of the length adjusting unit described below, and the lower union member 320 may be coupled to the movable member 340 of the length- Lt; / RTI >

At this time, a plurality of protrusions 311 and 321 may be protruded in one direction on the contact surface side. The protrusions 311 and 321 may be formed in a predetermined pattern with a predetermined height from the surface of the contact surface.

By this, the fusion area between the vertebral bodies 32, 34 and the bone union members 310, 320 can be further promoted by increasing the fusion area to be joined to the respective vertebral bodies 32, 34, The positions of the joint members 310 and 320 can be more stably fixed between the vertebrae 32 and 34 which are disconnected from each other through the first and second connecting members 311 and 321.

In addition, the union members 310 and 320 may be formed with at least one wedge portion 390 protruding at a predetermined length on a contact surface that is in contact with the vertebral bodies 32 and 34. The wedge portion 390 may be disposed between the two vertebral bodies 32 and 34 in place of any one of the plurality of vertebrae continuously arranged in the bone substitute implant 300 according to the third embodiment of the present invention It is possible to increase the binding force by being stuck on one surface of the vertebral bodies 32 and 34 which are in contact with each other. This minimizes the risk that the respective vertebral bodies 32 and 34 and the bony union members 310 and 320 that are in contact with each other are separated through the wedge portion 390 so that the bone substitute implants 300 according to the third embodiment of the present invention The two separated vertebra bodies 32 and 34 can be supported more stably.

Here, the wedge portion 390 may be integrally formed with the bodies 312 and 322, but may be inserted into the seating recesses 313 and 323 formed at a predetermined depth inward from the contact surfaces of the bodies 312 and 322. In addition, the wedge portion 390 may have a shape in which the cross-sectional area gradually decreases toward the outer side from the contact surface of the bodies 312 and 322 so that the wedge portion 390 can improve the coupling with the vertebral bodies 32 and 34 and the tightness. In one example, the wedge portion 390 may be conical. The wedge portion 390 may be made of the same material as the bony union members 310 and 320, but may be made of polyetheretherketone (PEEK).

The length adjuster adjusts the distance between the two bone union members 310 and 320 to vary the overall length of the bone substitute implant 300. Accordingly, when connecting the two vertebrae 32, 34, which are disconnected from each other, by replacing any of the plurality of vertebrae continuously arranged on the bone-implant implant 300 according to the third embodiment of the present invention, The upper and lower bony members 32 and 34 and the lower bony member 320 can be disposed in a completely close contact with each other to secure a stable supporting force.

Such a length adjuster can be applied to any known method as long as the gap between the two union members 310 and 320 can be varied through a sliding method during a user's operation.

For example, the length adjusting unit applied to the third embodiment of the present invention may be provided with a driving force through a known bevel gear method when the user operates the apparatus, so that the distance between the two bony union members 310 and 320 can be adjusted.

Specifically, the length adjuster may include a movable member 330 rotated by gear engagement with the work tool 30 during a user's operation, and a drive unit 330 for providing a driving force for moving the movable member 330 when the movable member 330 rotates And a power transmission member 350 that transmits the driving force generated by the relative movement of the movable member 330 and the movable member 340 toward the upper joint member 310. [

The movable member 330 may be provided in a hollow cylindrical shape having a predetermined length and may include a plurality of gear grooves 321 formed along the circumferential direction at an upper end thereof so as to be gear- (331) may be formed. Here, the movable member 330 can perform a role of a driven gear by engaging with a driving gear formed on the working tool 30 through the gear groove 331 (see FIG. 10).

Accordingly, when the user rotates the work tool 30 in one direction, the movable member 330 can be rotated clockwise or counterclockwise by providing the driving force through the gear engagement.

The movable member 330 may have a first screw portion 332 formed along an outer circumferential surface of the movable member 330 and a second screw portion 342 corresponding to the first screw portion 332 along the inner circumferential surface of the movable member 340. [ May be formed. Accordingly, the movable member 330 can be screwed through relative movement with the movable member 340 during rotation by gear engagement.

The movable member 340 may be provided in a hollow cylindrical shape having a predetermined length to accommodate the movable member 330 and having a second screw portion 342 formed on the inner peripheral surface thereof, Can be fixed to the member (320).

When the movable member 330 is rotated in a state where the movable member 340 is fixed, the movable member 330 is moved by the first screw portion 332 along the second screw portion 342, (Not shown).

The power transmitting member 350 may have a predetermined length and may have an upper end fixed to the upper joint member 310 and a lower end adjacent to the upper side of the movable member 330. For example, the movable member 330 can be supported by the step 333 on the lower edge side of the power transmitting member 350 by forming the step 333 on the upper side where the gear groove 331 is formed.

The power transmitting member 350 supported by the step portion 333 of the movable member 330 when the movable member 330 is rotated through the relative movement with respect to the movable member 340, Can be moved upward together with the upper union member 310 or can be moved downward. Thereby, the two bone union members 310 and 320 are spaced apart or narrowed from each other, so that the overall length of the bone substitute implant 300 can be adjusted (see FIGS. 12 and 13).

An insertion groove 352 is formed at one side of the power transmitting member 350 so that the end of the working tool 30 can be inserted and supported thereby to allow the user to operate the working tool 30 The work tool 30 can be smoothly rotated around the insertion groove 352 in a state where the drive gear (not shown) and the gear groove 331 formed in the movable member 330 are engaged with each other.

Meanwhile, the bone substitute implant 300 according to the third embodiment of the present invention may include a pair of cases 360 and 370 which are provided in a hollow shape having an open top and a bottom and are slidably coupled, The case 360 and the case 360 may be fixed to one of the upper and lower union members 310 and 320, respectively.

The first case 360 of the pair of cases 360 and 370 may be fixedly coupled to the upper union member 310 and the lower case may be coupled to the lower union member 320. [ And the first case 360 may be disposed so as to be positioned inside the second case 370.

Accordingly, when the movable member 330 is screwed along the longitudinal direction of the movable member 340, the first case 360 is engaged with the upper joint member 310 by the driving force transmitted through the power transmitting member 350, The second case 370 can be slidably moved.

At this time, the pair of cases 360, 370 is formed by the movement of the user in a state where the bone substitute implant 300 according to the third embodiment of the present invention is disposed between the two disconnected vertebrae 32, Sectional shape so as to support the torsional load when twisting occurs between the first and second torsion springs 34 and 34 and may be made of a metal material to prevent breakage due to a load. For example, the pair of cases 360 and 370 may be in the shape of a hollow square pipe having open top and bottom, and may be made of titanium (Ti).

In addition, the pair of cases 360 and 370 are arranged so as to surround the outside of the length adjuster, thereby accommodating the osteogenic protein therein. Accordingly, the bone substitute implant 300 according to the third embodiment of the present invention can further promote fusion with the vertebral bodies 32 and 34 through the osteogenic proteins disposed inside the cases 360 and 370.

A plurality of through holes 362 and 372 may be formed through the pair of cases 360 and 370 and a plurality of through holes 362 and 372 may be formed through the through holes 362 and 372 in a state in which the first case 360 is slid with respect to the second case 370, The first through hole 362 and the second through hole 372 may be formed so as to always communicate with each other.

For example, the first through hole 362 and the second through hole 372 may be formed at positions corresponding to each other, and the first through hole 362 may be formed as a long hole along the height direction of the first case 360 have. Accordingly, even if the first case 360 is slid and the relative positions of the first through hole 362 and the second through hole 372 are changed, the first case 360 and the second case 370 are positioned at the overlapped positions The formed second through hole 372 can always remain in communication with the first through hole 362. The inside and the outside of the first case 360 and the second case 370 are connected to each other through the first through hole 362 and the second through hole 372, It can be smoothly performed. Thus, it is possible to prevent problems such as bacterial growth or necrosis that can occur when the body fluids are stagnated inside the cases 360 and 370.

The pair of cases 360 and 370 has openings 363 and 373 having a predetermined area so that the end side of the working tool 30 can easily enter and can be engaged with the gear groove 331 of the movable member 330 And the opening 373 formed in the second case 370 can prevent the middle portion of the opening 363 formed in the first case 360 from being clogged when sliding the first case 360 So that one side may be opened.

The bone substitute implant 300 according to the third embodiment of the present invention includes a case 360 and a crotch member 360 made of a metal and a cushioning member 310 and 320 made of a bioactive crystalline glass material, (380) may be disposed. The cushioning member 380 may be made of polyetheretherketone (PEEK), and may be coupled to the protrusions 314 and 324 of the union members 310 and 320 as described above.

That is, the cushioning member 380 serves as a spacer for separating the bony union members 310 and 320 and the metallic cases 360 and 370 from each other, thereby ensuring physical stability. If the union members 310 and 320 and the cases 360 and 370 are in direct contact with each other, the bony union members 310 and 320 having large brittleness due to an external force applied from the human body or the vertebral bodies 32 and 34 may be damaged by the cases 360 and 370 Because.

The surface of the protrusions 314 and 324 and the inner surface of the buffer member 380 are formed with a step structure corresponding to each other to prevent the buffer member 380 from being easily separated from the protrusions 314 and 324, May be fixed through a separate fixing member such as a bolt member in a state in which they are disposed so as to surround the circumference of the protrusions 314 and 324, or both of them may be applied.

The bone substitute implant 300 according to the third embodiment of the present invention includes a locking screw 392 to prevent the movable member 330 from being rotated by an external force applied from the human body or the vertebrae 32, The rotation of the movable member 330 can be restricted.

That is, after the bone substitute implant 300 according to the third embodiment of the present invention is disposed between the vertebrae 32 and 34 that are separated from each other, the respective bone union members 310 and 320 are inserted into the corresponding vertebrae The rotation of the movable member 330 can be restricted by tightening the lock screw 392 on the side of the length adjuster in a state in which it is completely in close contact with the surface of the movable member 330.

At least one fastening hole 344 may be formed in the side portion of the movable member 340 and a second through hole 374 may be formed at a position corresponding to the fastening hole 344 on the side of the second case 370. [ Can be formed through. The first case 360 has a first through hole 364 formed along the longitudinal direction at a position corresponding to the second through hole 374 so that the first case 360 is connected to the second case 370, The first passage hole 364 and the second passage hole 374 are always kept in a communicated state.

Thus, in a state where the entire length adjustment of the bone substitute implant 300 is completed through the operation of the user, the user inserts the locking screw 392 through the first passage hole 364 and the second passage hole 374 into the fastening hole 344 and the rotation of the movable member 330 can be restricted by pressing the side of the movable member 330 on the side of the end of the lock screw 392. [

Here, the locking screw 392 is rotated by the first case 360 because the middle of the length or the head portion 392a is located in the first passage hole 364, The rotation of the rotation shaft 330 can be restricted.

At this time, the fastening hole 344 may be formed with a threaded portion on the inner surface so that the fastening screw 392 can be screwed, and the second passage hole 374 may be formed such that the head 392a of the fastening screw 392 is fastened to the second May be formed to have the same or relatively larger area as the head portion 392a of the locking screw 392 so as not to protrude out of the case 370. [

While the present invention has been particularly shown and described with reference to exemplary embodiments thereof, it is to be understood that the invention is not limited to the disclosed exemplary embodiments, It will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims.

100, 200, 300: bone replacement implant
110, 210, 310 to 320:
120, 220 to 230, 330 to 370: Implant body
130, 240,

Claims (10)

A bone union member including a body made of a bio-active crystallized glass material and adapted to contact and coalesce with a surface of an adjacent bone;
An implant body for securing between adjacent corrugations; And
A buffer member disposed between the bone union member and the implant body to separate the bone union member from the implant body;
0.0 > implant. ≪ / RTI > The method according to claim 1,
The implant body is made of titanium (Ti)
Wherein the buffer member is made of polyetheretherketone (PEEK). The method according to claim 1,
Wherein the bioactive crystalline glass material comprises CaSiO ₃ , apatite, and Ca ₂ Mg (Si ₂ O ₇ ) at a weight ratio of 1: 0.7 to 1.5: 0.5 to 1.2. The method according to claim 1,
Wherein the body is manufactured by CAD / CAM or 3D printing based on medical image information of a patient. The method according to claim 1,
The bone union member is embedded in a space between the adjacent first vertebra and the second vertebra,
Wherein the body has a shape corresponding to a surface shape of each of the first and second vertebrae,
Wherein the implant body includes a plate fixed to the first vertebra and the second vertebra,
And a groove for engaging the buffer member is provided on a side surface of the body. 6. The method of claim 5,
The cushioning member,
A pair of supports for coupling to the body of the union member; And
And a central portion connecting the pair of supports,
And the support portion is inserted into the groove portion of the body of the bone union member in a fitting manner. The method according to claim 1,
Wherein the implant body fixes between the adjacent first and second wings,
The body has a rectangular shape,
Wherein a concave portion is provided on a side surface of the body at a position corresponding to a contact surface of each of the first and second impellers,
Wherein the implant body includes a first plate for fixing to one side of the first and second wings, and a second plate for fixing to the other side of the first wings and the second wings,
Wherein a shaft of the first plate and a through hole into which the buffer member is inserted are provided at the center of the body. 8. The method of claim 7,
Wherein the buffer members are formed in a pair,
A plate-shaped spacing portion having a plate-like shape so as to be spaced apart from the first plate or the second plate and the bony union member and having a through hole having a shape corresponding to the shaft of the first plate, And
And an insertion portion extending from the spacer to form a side wall of the through hole and inserted into the through hole of the bone union member to separate the shaft and the bone union member from each other. The method according to claim 1,
Wherein the implant body replaces any one of a plurality of vertebrae connected to each other,
Wherein the bony union member includes upper and lower bony members spaced apart from each other with a shape corresponding to a surface of the vertebra,
Wherein the implant body is disposed between the upper and lower bone union members and includes a length adjuster that adjusts an overall length by adjusting an interval between the upper and lower union members through a sliding movement during a user's operation. 10. The method of claim 9,
Wherein the implant body is made of a hollow metal material having an open top and a bottom, and the upper side is fixedly coupled to the upper bone union member; And
And a second case made of a hollow metal material having an open top and a bottom, a lower side fixedly coupled to the lower joint member, and a second case slidably coupled to the first case
The buffer member is disposed between the opposite surfaces of the first case and the upper union member and between the opposite surfaces of the second case and the lower union member,
And is coupled to a protruding portion protruding in one direction from a body of the upper union member and the lower union member.

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