KR200188510Y1 - A supplement plug for spinal colulm - Google Patents

Abstract

The prosthetic plug for spinal prosthesis according to the present invention inserts a prosthetic plug filled with a bone growth material into a predetermined insertion space formed in an adjacent intervertebral space, thereby preventing and dislocating the intervertebral space and preventing interbody fusion. As used in, an inner passage 70 is formed in a forward direction from a rear end surface of which part or all is open, and a plurality of locking projections 20 and the outer peripheral surface which is in contact with the upper, lower, left, and right surfaces of the insertion space. A rectangular parallelepiped or polygonal pillar-shaped body 3 having a plurality of through-holes 60 communicating with the inner passage; In the prosthetic plug 1, which is connected to the front side of the body 3 and is installed to enter the insertion space for the first time; In the prosthetic plug 1 consisting of: The entry front part 2, one end is the body ( It is connected integrally with the outer peripheral surface of 3) and the other side is characterized in that the outer peripheral circumference gradually narrows toward the front, so that the final front cross section has a circular or elliptical shape, while making it easy to enter the pre-inserted space in the vertebral interval, Finally, there is an effect that the position can be stabilized by the structure and the locking projection of the polygon that the body has.

Description

A supplement plug for spinal colulm

The present invention relates to a prosthetic plug for spinal fusion.

The human spine consists of the vertebrae and fibrocartilaginous discs (sometimes called discs) between them, which are strengthened by strong ligaments and muscles from the skull to the pelvis, supporting the body and maintaining equilibrium. 1 is a side view of the lumbar vertebrae 200 of a human spine, as shown in the figure, the vertebrae include one vertebral body 220 and two pedicles 210 and two intervertebral discs. Disc) and spinous process at the back, with two transverse and upper and lower joints on both sides. Pedicle 210 is a cylindrical structure that connects the front and rear of the spine is slightly different in position and angle. Recently, as the use of pedicle screws increases in the thoracolumbar region, the importance thereof increases.

On the other hand, the intervertebral disc (part of what is called 'disc') 230 is composed of the annulus fibrosus and the nucleus pulposus, and the shape and size vary depending on the location. Because there are no blood vessels in the intervertebral discs of adults, the cells in them are supplied with nutrients by diffusion through the hole in the center of the vertebral disc, and the movement and weight of the vertebrae are thought to aid the diffusion.

On the other hand, lower back pain is usually caused by rupture or deterioration of the lumbar disc. Sciatica is caused by compression of the spinal nerve roots by damaged discs between the vertebrae, and lower back pain is caused by most of the weight being sustained through the destruction of the disc and the damaged unstable vertebral joint. The treatment of sciatica and lower back pain generally includes: 1) removing sciatica, sciatica and leg pain, 2) disc ablation by late fusion, and 3) anterior body. Disc ablation by fusion, 4) disc ablation by fusion between posterior lumbar vertebrae, and the like.

In this procedure, a rigid bone-bonded object is used between the vertebral bodies to relieve the pain of the degenerative disc to further prevent the disc from collapsing. At this time, because their bones are difficult to obtain a large amount, usually the same type of graft bones are used a lot, but these implanted bones take a long time to grow, and they themselves are not enough to carry a suitable load, and fixation It takes a long time and has about three times the failure rate than surgery with the patient's own bone.

Thus, U.S. Patent No. 4,743,256 provides a permanent weight support strut that maintains the distance of the disc, and is placed in a predetermined position in the spine to integrate the implant into the spine and has a rigid graft with a surface that promotes internal growth of the bone. Improved surgical methods have been described to maintain the distance of the disc between the sieve and the adjacent vertebrae to eliminate pain such as the spine caused by degeneration or rupture of the vertebral disc. The implant is a rigid implant with a tool receiving end face that facilitates insertion into a predetermined position and has a rough surface geometry on the outer periphery to enhance internal growth of the bone. This predetermined position is formed by a drill surrounded by a drill guide having projecting teeth embedded in the later end of the adjacent spine to form a channel in the opposite face of the adjacent spine. This channel preferably does not extend completely through the anterior side of the spine.

In addition, Korean Patent Publication No. 92-3405 by the same applicant as the US patent discloses an improved plug used in the method. According to this, in a prosthetic column for a vertebral column that traverses a predetermined area opposite the disk distance between the adjacent vertebrae and the plane of the adjacent vertebrae, each plug intersects the predetermined area to facilitate internal growth of the bone from the spine. It has a rough surface that locks, and each plug has an end face and tool-receiving means fitted into the plug to securely mount the plug in an end direction on the tool to facilitate insertion of the plug into the end in a predetermined area. It is equipped with side-by-side, rigid, inert rigid plugs that are sized and shaped to maintain the required disc distance between adjacent vertebrae and to form a transverse column located in a predetermined area of the adjacent vertebrae. Figure 2 shows that such a prosthetic plug is inserted in a predetermined position on the spine, Figure 3 is a perspective view showing an example of a conventional prosthetic plug.

The plug 100 is not screwed into an inter-disk disc-shaped hole, but is used in a form of being directly inserted into an insertion space formed in the vertebral space. That is, in order to support the spine itself as a support, the tool is inserted into the insertion space by using a tool, and the tool is removed from the plug without moving the plug to facilitate internal growth of the bone from the spine near the surface. do. In this case, in general, the protrusion 110 is formed on the outer circumferential surface of the plug, so that the plug can be fixed within the vertebral spacing.

The plugs used in this procedure are inserted directly between the vertebrae, not by screwing by male or female female threads, so the moment of first entering the insertion space becomes important. That is, the moment when the front end of the plug enters for the first time, the insertion space between the vertebrae is unnecessarily destroyed, or if the insertion operation is not performed smoothly, the fixing at the final fixing position may be incomplete. It may not be easy on its own. For example, the known plugs as disclosed in FIG. 3 have their front end, which is substantially parallel to the rear body, and have the same width and height, and thus cannot avoid the problems described above.

Prosthetic plug according to the present invention is intended to solve the above disadvantages, in the prosthetic plug used to directly insert and fix the insertion space in the vertebral spacing of the spine, the entry into the insertion space more smoothly, the final fixation An object of the present invention is to provide a prosthetic plug having a structure that can be stabilized in position.

In addition, it is an object of the present invention to provide a prosthetic plug having a structure that allows the inserted prosthetic plug to more effectively absorb the impact load and the fatigue load applied up and down in the vertebral body.

1 is a side view showing the side of the lumbar spine of a human spine.

Figure 2 is a side view showing the implanted position of the prosthetic plug for the spine.

3 is a perspective view showing a conventional spinal prosthetic plug

Figure 4 is a perspective view of the prosthetic plug for the spine of the present invention.

Figure 5 is a side view showing another embodiment of the prosthetic plug for the spine according to the present invention.

Figure 6 is a perspective view showing another embodiment of the prosthetic plug for the spine according to the present invention.

Figure 7 is a perspective view showing another embodiment of the prosthetic plug for the spine according to the present invention.

Figure 8 is a perspective view showing another embodiment of the prosthetic plug for the spine according to the present invention.

In order to achieve the above object, the present invention inserts a prosthetic plug filled with bone growth material into a predetermined insertion space formed in an adjacent vertebral space, thereby preventing and dislocating the intervertebral space and satisfying bone union. As used in fusion surgery, an inner passage is formed in a forward direction from a rear end surface which is partially or entirely opened, and a plurality of engaging protrusions and a plurality of communicating with the inner passage are formed on the outer circumferential surface which comes into contact with the upper, lower, left, and right surfaces of the insertion space. A rectangular parallelepiped or polygonal pillar-shaped body formed with two through holes; In the prosthetic plug for spine comprising: a front entrance portion connected to the front side of the body to enter the insertion space for the first time, the entrance front portion, one side extends integrally with the outer peripheral surface of the body and the other side is the front Outsourcing The circumference is gradually narrowed to provide a prosthetic plug for the spine, characterized in that the final front section has a circular or elliptical shape.

In addition, the present invention provides a prosthetic plug for the spine, characterized in that the body has a rectangular parallelepiped shape.

In addition, the present invention further provides a prosthetic plug for the spine, characterized in that a constant inclination is formed over the front and rear to correspond to the inclination angle between the vertebral spacing on the body.

In addition, the present invention further provides a prosthetic plug for spine, characterized in that the upper and lower impact prevention trim portion is further provided on the body side to give elasticity in the vertical direction when the intervertebral vertebrae is mounted to absorb the impact.

Hereinafter, with reference to the accompanying drawings, it will be described in detail the configuration and effect of the prosthetic plug for the spine according to the present invention.

Figure 4 is a perspective view showing an example of the structure of the prosthetic plug for the spine of the present invention. The prosthetic plug 1 shown in the figure consists of a body 3 of a rectangular parallelepiped and an entrance front part 2 connected integrally with the body 3. Inside the body 3 there is formed an inner passage 70 extending from the rear end to just before the front end, which is inserted into the auxiliary insertion tool when the prosthetic plug is inserted into the insertion space between the vertebral spacings. In addition to the role of losing, along with the through-hole 60 in communication with the inner passage 70 in the upper and lower left and right, and then filling the bone growth material, and serves to activate the growth of the intervertebral bone tissue. At this time, the bone growth material is charged to some extent even after the plug is inserted into the vertebral interval, but it is usually preferable to use it after filling the inner passage to some extent in advance.

At this time, the front entrance 2 is integrally connected to the front end of the body 3, and toward the front side, the width of the circumference becomes narrower, the front entrance ( The final front end 10 of 2) has a circular shape. Of course, this cross-sectional shape may be exactly circular, but may also have an elliptic shape.

The prosthetic plug may be made of an inert rigid metal such as stainless steel, cobalt-chromium-molybdenum alloy, titanium. In addition, the locking protrusion 20 may be made of the same material as the plug body 3 or may be made of another material such as a polymer resin cover. In addition, instead of the inert metal as described above, a polysulfone type such as plastic, polycarbonate, polypropylene, polyacetyl, polystyrene, glass or carbon fiber may be a well-filled iolucent material. Such plastics may be injection molded.

Effects of the prosthetic plug for the spine having the configuration as described above are as follows. When the prosthetic plug 1 is fitted in a preformed insertion space at an intervertebral interval from the dorsal side of the patient to the dorsal or abdominal to the dorsal side, the first entering front end 10 has a circular shape, which is different from the entrance of the insertion space. There is no resistance. Then, when fully inserted to the rear of the body (3), the position movement is subjected to resistance by the bone tissue in the insertion space by the angle of the perimeter of the body (3). In addition, since a plurality of locking projections 20 are formed on the side wall of the body 3, the resistance effect of such position movement can be further enhanced.

At this time, the shape of the body is preferably a rectangular parallelepiped, but may also be other polygonal column shape, the through-holes 60 communicated with the inner passage 70, the position, number, shape and size of the back of the projection, etc. It should be considered that the present invention is not necessarily limited to the contents disclosed in the drawings. That is, in the example shown in the drawings attached to the present specification, the upper surface is almost completely open, but like the side of the plug 1 of this drawing, some parts are closed and some may be formed in the form of through holes. have. In addition, although the locking projections have the shape of a triangular pyramid in the drawing, the triangular pyramids may be formed to have a predetermined angle in the front, rear, left and right, or the locking projection may be formed on the side. However, in terms of allowing more bone fragments and blood to accumulate on the bone growth material filled in the body 3, it may be preferable that the locking projection is formed at least on the upper surface.

On the other hand, the height of the body (3 ') can be configured to have a height over the front and rear. 5 is a side view showing an example in which the inclination angle θ is given to the prosthetic plug of the present invention. In this prosthetic plug 1 ', the inclination angle is set based on the inclination of the upper and lower surfaces of the interbody space. In general, the vertebrae that form the human spine are often formed at a certain angle rather than being completely parallel to each other. In supporting the intervertebral body, when the existing prosthetic plug of the up and down parallel shape is used, there may be a case in which more space than necessary is required to form an insertion space within the intervertebral space, and the upper and lower weights are supported. In terms of efficiency, efficiency may be reduced.

However, when the prosthetic plug 1 'having the inclination corresponding to the angle between the vertebrae is used as described above, the smoothing effect of the insertion and the synergistic effect of the bearing force will be obtained at the same time. Of course, even in this case, the shape of the inclination shown in FIG. 5 is merely exemplary, and the scope of the present invention is not limited to this shape. In addition, the manufacturing of the prosthetic plug having such an inclined shape may measure the angle in the vertebral spacing and set it accordingly, but some types of prosthetic plugs may be standardized, and then suitable ones may be selected and used.

On the other hand, Figures 6 to 8 shows a case where the upper and lower impact prevention trimming part 4 is formed in the side portion of the body (1 ''). This trim 4 is formed over the left and right and rear surfaces of the body, as shown in Figure 6, or formed over the left and right and front cross-section of the body, as shown in Figure 7, or the front cross section as shown in Figure 8 It may be formed from a portion over a portion of the rear surface via the left or right side of the body. In any case, in order to have elasticity up and down, the upper and lower ends cut by the trimming part 4 should be able to be moved close to each other by the impact in the vertical direction and then move away again. The effect of the provision of such a configuration is as follows.

Bone remodeling can also be caused by physical forces or micro electrical stimuli, where stresses, ie areas under high stress (force per unit area) and appropriate mechanical stumulations, such as micromotion, occur. Where bones are produced, bones are absorbed at sites with less load (load). According to this bone remodeling mechanism, firm fixation can change bone remodeling, and cause osteplysis of surrounding bone tissue due to differences in hardness between bone tissue and metal. For example, steel is ten times stronger than bone tissue. In the case of fixing with a metal of such a high strength, when a load is applied, normal stress is not transmitted to the bone tissue, and bone absorption occurs locally. Because of this, the structure of the generated bone is weakened, so there is a high risk of fracture. This phenomenon is called stress shielding. In addition, a large difference in strength between the bone and the prosthetic device is likely to cause loosening between the bone tissue and the prosthetic fixture fixation.

At this time, as shown in Figures 6 to 8 of the present invention, in the case where the trimming portion 4 is formed on the side wall surface of the plug, the elasticity and flexibility of the plug structure is increased even when an impact is applied to the spine in the vertical direction. This allows some degree of deformation in the structure. This property allows sufficient load and appropriate mechanical stimulus to be transferred to the bone pieces filled in the plug, creating an environment favorable for the aforementioned bone remodeling. That is, the spine is one of the places where the body is subjected to a large load, and the main form of the load applied is also instantaneous (impact load) and repetitive (fatigue load), and thus the performance of the plug structure against shock and fatigue is very high. One of the important characteristics is that the provision of the trim 4 according to the present invention is to be able to effectively eliminate the adverse effect of this load on bone growth.

As described above, the prosthetic plug according to the present invention enters into the pre-formed insertion space in the vertebral spacing by having the outer circumference gradually narrower toward the front and the final front end face having a circular or elliptical shape. While easy to achieve, there is an effect that can be stabilized by the angled structure and the locking projection that the body finally has.

In addition, by providing a predetermined inclination angle to the outer peripheral surface of the prosthetic plug, it is possible to cope with the inclination angle formed basically between the adjacent vertebrae, has the advantage of increasing the support efficiency, and by forming a portion for preventing the up and down impact on a part of the plug By applying an elastic force there is an advantage to effectively absorb the impact load applied to the spine.

Claims (4)

By inserting a prosthetic plug filling bone growth material into a predetermined insertion space formed in an adjacent vertebral space, it is used for interbody fusion to prevent dislocation and satisfy bone union while restoring and maintaining the intervertebral spacing. An inner passage 70 is formed in a forward direction from a rear end surface of which part or all is open, and a plurality of locking protrusions 20 and the inner passage 70 are formed on the outer circumferential surface which comes into contact with the top, bottom, left and right surfaces of the insertion space. Polygonal columnar body (3,3 ', 3' ') formed with a plurality of through-holes 60 in communication with; In the prosthetic plug for the spine consisting of: the front and rear portions (2, 2 ', 2' ') connected to the front side of the body (3, 3', 3 ``) to enter the insertion space for the first time: The entrance front part 2, 2 ', 2' ', one end is integrally connected to the outer circumferential surface of the body (3, 3', 3 '') and the other side is gradually narrower around the outer circumference toward the front end Prosthetic plug (1,1 ', 1' ') for the front end surface, characterized in that the circular or elliptical shape. The prosthetic plug (1,1 '') according to claim 1, characterized in that the body (3, 3 '') has a rectangular parallelepiped shape. The prosthetic plug (1 ') according to claim 1, wherein a constant inclination is formed in the body (3') in front and rear to correspond to the inclination angle between the vertebral intervals. According to any one of claims 1 to 2, wherein the side of the body (3 ') to the upper and lower impact prevention trimming part (4) to give elasticity in the vertical direction when mounting between the vertebral vertebrae to absorb the impact Spinal prosthetic plug (1 ''), characterized in that is further formed.