KR101170468B1 - Implant Apparatus - Google Patents

Abstract

The present invention relates to an implant apparatus, and relates to an implant apparatus formed with a promoter infusion tube for administering a bone tissue growth accelerator so that the implant can be quickly and firmly adhered to the bone tissue after implantation.
The present invention is an implant body; An injection tube formed at one end of the implant body for injecting bone tissue growth promoter into the implant body; And a plurality of discharge pipes communicating with the injection pipe for discharging the bone tissue growth promoter injected from the injection pipe to the side of the implant body, wherein the discharge pipe has a shape in which the cross-sectional area increases toward the discharge port.

Description

Implant Apparatus {Implant Apparatus}

The present invention relates to an implant apparatus, and relates to an implant apparatus formed with a promoter infusion tube for administering a bone tissue growth accelerator so that the implant can be quickly and firmly adhered to the bone tissue after implantation.

In general, implants are used in artificial dental procedures used to cope with lost teeth. Unlike conventional prosthetics or dentures, implants do not damage surrounding tooth tissue, and their function or shape is similar to natural teeth, but with a relatively long lifespan. It has a high-tech procedure that is currently in the spotlight.

Such an implant is an implant body made of a screw thread embedded in the alveolar bone of the site where the tooth is lost, the abutment and the abutment coupled to the upper side of the implant body and used as a pillar for covering an artificial crown on the exterior. It is composed of an artificial crown that is fixed in the oral cavity by a treatment to reproduce the same shape and function as natural teeth.

1A is a cross-sectional view for explaining such a conventional implant.

Referring to FIG. 1A, a conventional implant 100 includes an implant body 110, an abutment 120, and a screw 130, and an artificial crown is inserted into the upper portion of the abutment but is not shown. .

The implant body 110 is inserted into the alveolar bone and the thread 112 is protruded perpendicularly to the longitudinal direction to be screwed. An abutment coupling part 114 is formed on the implant body 110.

The abutment 120 is positioned at the bottom and inserted into the abutment coupling portion 114 of the fixture 110, the inside is formed in a hollow so that the artificial crown (not shown) is inserted, fixed.

The screw 130 is fastened to the fixture 110 by penetrating the abutment 120, and the screw 130 penetrates the lower end of the abutment 120 and is inserted into the upper end of the implant body 110. As such, the abutment 120 is fixed to the implant body 110.

When the implant body 110 of the implant 100 configured as described above elapses in the state of being implanted in the alveolar bone of the operator, bone adhesion progresses while the osteoblast cells of the alveolar bone cling to the thread 112, and the alveolar bone It is fixed.

However, conventional implants have difficulty in initial fixation due to low adhesion to bone tissue at the initial placement.

Therefore, in order to solve this problem, disclosed in the Patent Publication No. 10-2010-005286 discloses an implant device for promoting adhesion to bone tissue after implantation.

Looking at the patent with reference to Figure 1b, the accelerator injection tube 15 is formed through the interior of the implant body in the interior of the implant body 10, the outer peripheral surface of the implant body 10 in communication with the accelerator discharge pipe Bone tissue growth accelerator introduced into the promoter injection tube 15 is discharged through the discharge tube to form a coating layer on the outside of the implant body. The outer circumferential surface of the implant body 10 is formed with a screw thread 11 to be helically coupled to the alveolar bone.

The implant body 10 is formed with a plurality of accelerator reinforcing holes 15 penetrating from the outer end to the side of the implant body 10 through the inside of the implant body 10. The stopper 30 may be installed at an outer end portion, that is, the inlet, of the accelerator reinforcing hole 15 to prevent the leakage and loss of the accelerator by blocking the accelerator reinforcing hole 15 after the bone tissue growth accelerator is injected.

In this way, the implants placed in the bone tissues are implanted in the bones of the body, and the bone tissue growth promoters are coated on the surface of the implants to promote the adhesion and growth of the bones. have.

The implant body 10 has an injection tube into which the bone tissue growth promoter is injected and four discharge tubes on the side for discharging. The maximum stress increases with respect to the maximum load generated when the teeth are used, and ends of the four discharge tubes The concentration of maximum stress at the outlet was found by performing COMSOL, a finite element modeling. Stresses concentrated at these outlets can cause the outlet to rupture.

Therefore, due to the accelerator injection pipe and the accelerator discharge pipe formed inside the implant body, stress concentrations are generated in a plurality of accelerator discharge pipes, and thus the maximum stress value is increased, which may cause the implant to rupture.

KR 10-2010-0005286 A

Accordingly, it is an object of the present invention to provide an implant apparatus having improved durability by reducing the maximum stress by minimizing the stress concentration of the accelerator infusion tube and the accelerator discharge tube for administering bone tissue growth accelerator to the implant body.

According to an aspect of the present invention for achieving the above object, an implant body; An injection tube formed at one end of the implant body for injecting bone tissue growth promoter into the implant body; And a plurality of discharge tubes communicating with the injection tube and discharging the bone tissue growth accelerator injected from the injection tube to the side of the implant body, wherein the discharge tube has a shape in which a cross-sectional area increases toward the discharge port. To provide.

The discharge pipe includes a pair of side upper discharge pipes having a cone shape inclined downward, and a pair of side lower discharge pipes having the same shape and the same cross-sectional area under the side upper discharge pipes.

The discharge pipe has a pair of side upper discharge pipes having a cone shape inclined downward, a pair of side lower discharge pipes having the same shape and the same cross-sectional area under the side upper discharge pipes, and a cone-shaped communication from an end portion to a lower surface of the injection pipe. The discharge pipe.

The discharge pipe includes a pair of side upper discharge pipes having a cone shape asymmetric to a horizontal plane, a pair of side lower discharge pipes having a cone shape inclined to a lower portion having a smaller cross-sectional area than the side upper discharge pipe under the side upper discharge pipes, and the injection pipe. It consists of a lower surface discharge pipe which communicates from the edge part of the to the lower surface in cone shape.

The discharge pipe has a pair of side upper discharge pipes having a cone shape symmetrical to a horizontal plane, a pair of side lower discharge pipes having the same shape and the same cross-sectional area under the side upper discharge pipes, and communicating from the end of the injection pipe to the bottom surface in a cone shape. The discharge pipe.

The discharge pipe may include a pair of side upper discharge pipes having a cone shape symmetrical to a horizontal plane, a pair of side lower discharge pipes having the same cross-sectional area below the side upper discharge pipe under the side upper discharge pipes, and an end portion of the injection pipe. It consists of a lower surface discharge pipe which communicates to a lower surface in cone shape.

The discharge pipe has a pair of upper side discharge pipes having a cone shape asymmetrical to a horizontal plane, a pair of side lower discharge pipes having the same shape and the same cross-sectional area under the side upper discharge pipes, and a cone-shaped communication from the end of the injection pipe to the lower surface. The discharge pipe.

The injection tube is characterized in that it has a cross-sectional area that increases in the downward direction.

Therefore, in the present invention, by optimizing the shape of the accelerator injection tube and the accelerator discharge tube for administering the bone tissue growth accelerator to the implant body, it is possible to improve the durability by minimizing the stress concentration and reducing the maximum stress.

Figure 1a is a cross-sectional view for explaining a general implant device,
Figure 1b is a cross-sectional view for explaining a conventional implant device,
Figure 2a is a cross-sectional view for explaining an implant device according to a first embodiment of the present invention,
Figure 2b is a schematic diagram showing a state in which the implant device of Figure 2a implanted in the alveolar bone,
3 is a cross-sectional view for explaining an implant device according to a second embodiment of the present invention;
4 is a cross-sectional view for explaining an implant apparatus according to a third embodiment of the present invention;
5 is a cross-sectional view for explaining an implant device according to a fourth embodiment of the present invention;
6 is a cross-sectional view for explaining an implant device according to a fifth embodiment of the present invention;
7 is a cross-sectional view for explaining an implant device according to a sixth embodiment of the present invention;

In the present invention, after implanting the implant into the alveolar bone, the bone tissue growth accelerator is injected into the accelerator injection tube into the implant body to be discharged through a plurality of accelerator outlets, wherein the stress concentration is concentrated in a plurality of accelerator outlets. It was confirmed that the maximum stress should be reduced to minimize the development of implant devices that are not load-sensitive when using teeth.

Usually, the stress is proportional to the vertical load and inversely proportional to the cross-sectional area under the assumption that the stress distribution is uniform in the cross section. Accordingly, a method of reducing stress is to increase the cross-sectional area under the same load, and even in the same cross-sectional area, stress or stress concentration can be reduced by changing the position or angle of the section where the load is concentrated.

In other words, the inventors of the present invention increase the size and number of the plurality of accelerator outlets in which stress concentration occurs in the implant, increase the contact area with the sponges of alveolar bone, and improve the shape and position of the accelerator outlet in view of such stress characteristics. In order to alleviate stress concentration and reduce maximum stress, a highly durable implant device was developed through various simulations.

 Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings.

Figure 2a is a cross-sectional view for explaining the implant device according to the first embodiment of the present invention, Figure 2b is a schematic diagram showing a state in which the implant device of Figure 2a implanted in the alveolar bone.

2A and 2B, the implant device according to the present invention has a generally cylindrical implant body 20 that is placed in the alveolar bone. The implant body 20 may be formed in a tapered shape so as to be narrowed at a predetermined angle from the top to the bottom thereof, and the shape of the implant body 20 is not limited.

The implant body 20 is made of a metal material, preferably titanium or a titanium alloy, but may be configured using various materials such as a bio-friendly ceramic.

The implant body 20 is formed with an injection tube 21 for injecting bone tissue growth promoter from the outer upper injection port 21a through the central axis up and down inside the implant body 20, and communicating from the injection tube 21. Thus, the side discharge pipes 22a, 22b, 23a, and 23b having the same shape are formed of four pairs of upper and lower pairs for discharging the bone tissue growth accelerator injected from the injection pipe 21 to the side of the implant body 20. .

The discharge pipes 22a, 22b, 23a, and 23b are formed in a cone shape in which the cross-sectional area increases toward each discharge port 21b. The top of the injection port 21a may be equipped with a stopper 20a for preventing the leakage and loss of the accelerator.

The bone tissue growth promoter may be made of, for example, a material such as hydroxyapatite (HAp: Hydroxyapatite), but in addition to any other material that has biocompatibility and helps adhesion and growth with bone tissue, Can be used.

As such, when the injection tube 21 is formed to penetrate the implant body 20 and the bone tissue growth promoter 20b is injected, the discharge pipes 22a, 22b, 23a, and 23b are discharged through the outlet on the outer circumference of the implant body 20. The bone tissue growth promoter 20b flows out to the outer surface of the implant body 20 to form a promoter coating layer 20c on part or all of the implant body 20. In this way, the promoter coating layer 20c formed on the outer surface of the implant body 20 promotes adhesion and growth of bone tissue to act to quickly and firmly adhere the implant to bone tissue.

In order to minimize the stress concentration of the implant body according to the first embodiment as described above by varying the shape and size of the injection pipe and the discharge pipe will be described with reference to various embodiments below. In the following embodiments, reference numerals of the inlets and outlets given in FIG. 2A will be omitted.

In the stress analysis used in the following examples, the COMSOL method, which is well known as a FEM tool, was used.

The load was applied to a higher value than the actual tooth use. The vertical direction was 400N / m downward and 75N / m horizontally to the right, and these loads were applied with a uniform distribution load on the upper part of the implant.

The analytical method was a static analysis in which loads and constraints did not change over time and the maximum value of von mises stress (σ _v ) was obtained. The value of each stress indicates the load per area received by each point as shown in Equation 1 below, and consists of three vertical stresses (σ _ii ) and three shear stresses (σ _ij ).

In the following embodiments, since the functions of the injection pipe and the discharge pipe are the same as in the first embodiment, a detailed description thereof will be omitted and described with reference to various simulation processes for minimizing stress concentration. do.

Injection tube
Diameter (mm) Side top
outlet
Diameter (mm) Lower side
outlet
Diameter (mm) if
outlet
Diameter (mm) Outlet
Total cross section
(mm ² ) Stress
(MPa) Comparative example 0.2 0.2 0.2 - 0.13 3.809 First Embodiment 0.2 0.8 0.8 - 2.01 2.916 Second Embodiment 0.4 1.0 1.0 1.0 3.93 1.348 Third Embodiment 0.4 1.6 1.0 1.0 6.38 1.114 Fourth embodiment 0.4 1.0 1.0 1.0 3.93 1.403 Fifth Embodiment 0.4 2.0 1.0 1.0 8.64 1.991 Sixth embodiment 0.4 1.6 1.6 1.6 10.05 1.113

The comparative example is the diameter of the injection tube and the discharge tube of the implant body (see Fig. 1b) disclosed in the patent 10-2010-0005286 referred to in the prior art of the present invention and the diameter of the injection tube and the discharge tube are all equal to 0.2mm In the case of the example, the cross section of the discharge pipe affecting the stress concentration was 0.13mm ² and the maximum stress was 3.089MPa.

As shown in Table 1, in the embodiments to be described below, the diameter of the inlet and outlet tubes is increased, and the shape of the outlet tube is changed to a cone shape as in the first embodiment, and the outlet of the lower surface is further configured to have a cross-sectional area of the outlet tube. As it increases, the maximum stress decreases.

2A, the implant body 20 has four side discharge pipes 22a, 22b, 23a, and 23b having a diameter of 0.2 mm and a cone shape inclined downward. Each discharge pipe is in communication with the injection pipe so that the diameter increases toward the discharge port so that the cross-sectional area is increased toward the discharge port to minimize stress concentration, and the diameter of the discharge ports of the four side discharge pipes is 0.8 mm, respectively. In this way, when the area of the outlet was enlarged, the maximum stress of the comparative example was reduced from 3.089 MPa to the maximum stress of 2.916 MPa of the first example, thereby reducing the stress concentration of 23% compared to the comparative example, and the stress contour zooming. It was confirmed that the stress concentration is reduced to the four outlet (21b) by the).

Referring to the second embodiment of FIG. 3, the implant body 30 increases the diameter of the injection tube 31 to 0.4 mm and has a cone-shaped side upper discharge tube 32a and 32b that is inclined downward with an outlet of the same diameter. In addition to the lower side discharge pipes 33a and 33b, it is the same as the implant body 20 of the first embodiment except that a lower discharge pipe 34 is further formed in communication with the bottom surface.

Further, when all of the five discharge pipe diameter is formed to 1mm wider than the first embodiment of the implant body 20, the maximum stress as the first cross-sectional area it is increased 144% as compared to the first embodiment of 2.01mm ² to 3.93mm ² It can be seen that the reduced 1.348MPa than the embodiment, all the stress concentration portion generated at each contact disappeared, it was confirmed that the stress concentration is weakly generated only in the side upper discharge pipe (32a, 32b).

Here, the injection pipe 31 was increased in diameter to 0.4mm in order to smoothly discharge the bone tissue growth accelerator without the bottleneck in the five discharge pipe.

Referring to the third embodiment of Figure 4, the implant body 40 is formed in the center axis of the injection tube 41, the side upper discharge pipe (42a, 42b) has a cone shape asymmetrical in the horizontal plane of the discharge port Except for increasing the diameter to 1.6mm, the lower side discharge pipes 43a and 43b and the lower discharge pipe 44 are the same as in the second embodiment. Here, the cone shape asymmetrical to the horizontal plane refers to a shape in which one side symmetry plane is removed from the cone shape symmetrical to the horizontal plane about the horizontal plane.

The implant body 40 of the third embodiment has a cross-sectional area of 6.38 mm ^{2, which} is relatively higher than 3.93 mm ² of the second embodiment, with a maximum stress of 1.114 MPa, which is 17% less than the maximum stress of the second embodiment and the stress in the discharge pipe. It can be seen that the effect of reducing concentration is excellent. Therefore, it can be seen that it is also effective to increase the cross-sectional area of the side upper discharge pipe in order to reduce the maximum stress.

Referring to the fourth embodiment of Figure 5, the implant body 50 forms the injection tube 51 on the central axis, the shape of the side upper discharge pipe (52a, 52b) and the side lower discharge pipe (53a, 53b) in the horizontal plane It is the same as the second embodiment except that it is formed in a symmetrical cone shape. As a result, it can be seen that the cross-sectional area is 3.93 mm ² and the same as that of the second embodiment, so that the maximum stress is 1.403, which is similar to that of the second embodiment.

Referring to the fifth embodiment of FIG. 6, the implant body 60 forms the injection tube 61 on the central axis, and maximizes the cross-sectional areas of the side upper discharge pipes 62a and 62b to form a cone symmetrical in the horizontal plane. Except that the diameter was increased to 2mm, the lower side discharge pipes 63a and 63b and the lower discharge pipe 64 are the same as in the fourth embodiment.

The total cross-sectional area increased to 8.64mm ² only by increasing the cross-sectional area of the upper side discharge pipe, but the maximum stress was 1.991MPa. Therefore, it can be seen that the increase in the cross-sectional area of the upper discharge pipe is not the only factor that reduces the maximum stress.

Referring to the sixth embodiment of FIG. 7, the implant body 70 forms the injection tube 71 on the central axis, and the side upper discharge pipes 72a and 72b and the side lower discharge pipes 73a and 73b are asymmetrical in the horizontal plane. It was formed in the shape of a cone and formed with a diameter of the outlets of 1.6 mm each so as to have a maximum cross-sectional area of 10.05 mm ² .

Although the maximum stress at this time was most reduced to 1.113 MPa, it can be seen that the cross-sectional area is not the only factor that reduces the maximum stress, as it is similar to the third embodiment having a small cross-sectional area.

As described above, as a result of varying the shape or size of the discharge port and confirming the maximum stress according to the cross-sectional area, the shape of the discharge pipe is mainly in the shape of a cone, and in particular, the cross-sectional area of the side upper discharge pipe is cross-sectional area of the lower side discharge pipe. When larger, the most desirable maximum stress reduction result was shown.

In the above embodiments, the injection tube is the same diameter, but it is also possible to have a diameter gradually increasing downward from the injection port in order to smoothly inject the bone tissue growth promoter.

The implant device of the present invention can be applied to a variety of dental implants, as well as medical implant devices, for example, orthopedic implants.

20,30,40,50,60,70: implant body
21,31,41,51,61,71: injection tube
22a, 22b, 32a, 32b, 42a, 42b, 52a, 52b, 62a, 62b, 72a, 72b
23a, 23b, 33a, 33b, 43a, 43b, 53a, 53b, 63a, 63b, 73a, 73b
34,44,54,64,74: bottom discharge pipe

Claims (8)

Implant body;
An injection tube formed at one end of the implant body for injecting bone tissue growth promoter into the implant body; And
It includes a plurality of discharge pipes in communication with the injection pipe for discharging the bone tissue growth promoter injected from the injection pipe to the side of the implant body,
The discharge pipe is an implant device, characterized in that the cross-sectional area increases toward the discharge port. According to claim 1, wherein the discharge pipe
A pair of side upper discharge pipes having a cone shape inclined downward; And
Implant apparatus comprising a pair of side lower discharge pipe of the same shape and the same cross-sectional area to the lower side of the upper side discharge pipe. According to claim 1, wherein the discharge pipe
A pair of side upper discharge pipes having a cone shape inclined downward;
A pair of side lower discharge pipes of the same shape and the same cross-sectional area under the side upper discharge pipes; And
And a lower surface discharge tube communicating from an end portion of the injection tube to a lower surface in a cone shape. According to claim 1, wherein the discharge pipe
A pair of side upper discharge pipes having a cone shape asymmetric to the horizontal plane;
A pair of side lower discharge pipes having a lower inclined cone shape having a smaller cross-sectional area than the side upper discharge pipe under the side upper discharge pipe; And
And a lower surface discharge tube communicating from an end portion of the injection tube to a lower surface in a cone shape. According to claim 1, wherein the discharge pipe
A pair of side upper discharge pipes having a cone shape symmetrical with respect to the horizontal plane;
A pair of side lower discharge pipes of the same shape and the same cross-sectional area under the side upper discharge pipes; And
And a lower surface discharge tube communicating from an end portion of the injection tube to a lower surface in a cone shape. According to claim 1, wherein the discharge pipe
A pair of side upper discharge pipes having a cone shape symmetrical with respect to the horizontal plane;
A pair of side lower discharge pipes having the same shape below the side upper discharge pipe and having a smaller cross-sectional area than the side upper discharge pipe; And
And a lower surface discharge tube communicating from an end portion of the injection tube to a lower surface in a cone shape. According to claim 1, wherein the discharge pipe
A pair of side upper discharge pipes having a cone shape asymmetric to the horizontal plane;
A pair of side lower discharge pipes of the same shape and the same cross-sectional area under the side upper discharge pipes; And
And a lower surface discharge tube communicating from an end portion of the injection tube to a lower surface in a cone shape. The method of claim 1, wherein the injection tube
Implant apparatus, characterized in that it has a cross-sectional area that increases in the downward direction from the injection port.

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