KR20030083157A - Osseo-integrated dental implant - Google Patents

Abstract

PURPOSE: An osseo-integrated dental implant is provided to reduce stress produced in compact and cancellous bones as low as possible, and to prevent collapse and breakdown of the bones. CONSTITUTION: The osseo-integrated dental implant comprises a compact bone bonding portion(32), a cancellous bone adhesion bonding portion(34), and a lower end curved surface portion(36). The compact bone bonding potion is provided with a tapered surface having a diameter increasing upward, and a screw(32a) formed at the tapered surface and having a first pitch. The cancellous bone bonding portion extends downward from the compact bone bonding portion and is formed with a screw(34a) having a second pitch thicker than the first pitch. The lower end curved surface portion is formed at the lower end of the cancellous bone bonding portion by a certain curvature.

Description

Osseo-Integrated Dental Implant

The present invention relates to a dental bone adhesion implant, and more particularly, to a dental bone adhesion implant that can prevent the bone fracture and bone fracture of the surrounding bone to minimize the stress generated around the implant (Osseo-Integrated Dental Implant ).

Dental osteoadhesive implants are increasing in clinical application due to their high clinical success rate and superior chewing ability. The types of dental osteoadhesion implants currently used are intraosseous, subperiosteal, and osteoporotic. The most widely used dental osteosynthetic implants are intraosseous. Intraosseous dental implants are made of chromium-cobalt, carbon, ceramics, titanium, and the like. Screws, cylinders, and mixtures of screws and cylinders are available. Recently, a screw-type dental osteoadhesion implant mainly made of titanium is being used.

This dental osteoadhesive implant is implanted in the upper and lower alveolar bones (C: hereinafter, "alveolar bone"), as shown in Figure 1, wherein the dental osteoadhesion implant (1) has a high bone density Passed through the dense bone (C1) is embedded into the sponge bone (C2) having a low bone density.

On the other hand, dental bone adhesion implants implanted in the alveolar bone (C), unlike natural teeth that are coupled to the bone tissue through the periodontal ligament does not have a physiological movement of the bone by being directly attached to the bone tissue. Therefore, the load (low pressure) received from the outside is transferred to the peripheral bones C1 and C2 intact, and thus a large stress is generated in the peripheral bones C1 and C2 receiving the external load. In particular, the bone density is high and the rigid dense bone (C1) has a greater stress due to the characteristics of the material, and as such a large stress is continuously applied to the dense bone (C1) has been pointed out the problem that bone fracture and bone fracture occurs. .

On the other hand, there is a method for minimizing the stress of the peripheral bone by increasing the length and diameter of the implant to increase the depth of implantation of the implant and the adhesion surface with the surrounding bone, there is a method of increasing the adhesion efficiency while dispersing the generated stress. However, this method is not able to increase the length and diameter of the implant in a limited space indefinitely, it is pointed out that there is a limit in reality.

Accordingly, the present invention has been made to solve the conventional problems as described above, the object is to minimize the stress generated in the peripheral bones without increasing the length and diameter of the implant to minimize bone fractures and bone fractures of the peripheral bones To provide a dental osteoadhesion implant configured to prevent.

Another object of the present invention is to provide a dental osteoadhesion implant configured to prevent bone collapse and bone fracture by minimizing the stress of high bone density and hard dense bone.

1 is a front view of a conventional screw-type dental bone adhesion implant,

Figure 2 is a front view showing the configuration of the dental bone adhesion implants according to the present invention,

3 is a cross-sectional view showing a state in which the dental bone adhesion implant is implanted in the alveolar bone,

4 is a graph showing the stress change of the dense bone with or without the taper formation of the dense bone joint;

Figure 5 is a graph showing the stress change of the dense bone with or without the formation of fine screws of the dense bone joints,

6 is a graph showing the stress change of the dense bone with or without the formation of coarse thread of the sponge bone joint,

7 is a cross-sectional view showing a modification of the dental osteoadhesion implant according to the present invention,

8 is a graph showing the change in stress of the sponges with or without the formation of coarse screws of the sponge bone joints,

9 is a front view showing a modification of the dental osteoadhesion implant according to the present invention.

♣ Explanation of symbols for the main parts of the drawing ♣

10: implant 20: head

30: body 32: dense bone joint

32a: fine screw 34: spongy bone joint

34a: coarse screw 34b: lower surface

34c: upper surface 36: lower curved portion

36a: screw

In order to achieve the above object, the present invention, in the dental bone adhesion implant embedded in the dense bone and the cancellous bone of the alveolar bone, has a tapered surface gradually increasing in diameter toward the top, the thin screw of the first pitch is Dense bone junction formed; A spongy bone joint extending downward from the dense bone joint and having a thick screw having a second pitch larger than the thin screw on an outer surface thereof; Characterized in that it consists of a lower surface portion formed with a predetermined curvature at the lower end of the sponge bone joint.

Hereinafter, with reference to the accompanying drawings a preferred embodiment of the dental osteoadhesion implant according to the present invention will be described in detail.

Figure 2 is a front view showing the configuration of the dental bone adhesion implant according to the present invention, Figure 3 is a cross-sectional view showing a state in which the dental bone adhesion implant is embedded in the alveolar bone. First, as shown in Figure 2, the bone adhesion implant 10 of the present invention is composed of the upper hexagonal head 20 and the lower columnar body 30, the lower body 30 is the upper dense bone again Consisting of the joint 32, the interfacial cancellous bone joint 34 and the lower lower curved portion 36. Here, the upper head 20 is configured to be fixed to the prosthesis 22, as shown in Figure 3, the lower body 30 is configured to be embedded in the alveolar bone (C). In particular, the dense bone joint 32 of the body 30 is configured to be bonded to the dense bone (C1) of the alveolar bone (C), the spongy bone joint 34 and the lower surface portion 36 of the body 30 is the alveolar bone (C) It is configured to bond with the spongy bone (C2).

Meanwhile, as shown in FIGS. 2 and 3, the dense bone junction 32 of the body 30 is configured so that its diameter is gradually enlarged and tapered toward the head 20, and a fine screw is formed around the tapered outer surface. screw thread: 32a) is formed. The dense bone joint 32 in which the tapered and thin screws 32a are formed increases the contact area with the dense bone C1 to maximize the joint ratio between the implant 10 and the dense bone C1 and is transferred from the top. The load (low pressure) is evenly distributed in the circumferential dense bone C1 to minimize the stress generated in the dense bone C1. In particular, the narrow screw 32a formed in the dense bone joint 32 increases the bonding rate of the dense bone C1 with the fine bone tissue, thereby inducing complete bone fusion of the implant 10 and the dense bone C1 and loading the upper load. By evenly dispersing the circumference of the dense bone (C1) serves to lower the maximum stress (Maxinum Equivalent Stress) of the dense bone (C1).

Here, the taper value of the dense bone junction 32 may vary depending on the length of the implant 10, the implantation position of the implant 10, and the state of the dense bone C1, but it is shown that it is preferably about 1 / 1.5. That is, the taper value is a large diameter (b)-small diameter (a) / length (ℓ), for example, the length (L) of the dense bone joint 32 is 1.5mm, the lower diameter of the dense bone joint 32 When (a) is 4mm, it is preferable that the top diameter b of the dense bone joint 32 should be 5mm. And the pitch of the fine screw 32a formed in the dense bone joint 32 and the height of the acid may vary depending on the length of the implant 10, the position of the implant 10, the state of the dense bone (C1), about 0.25mm to It has been found to be preferred to have a pitch in the range of 0.35 mm and a height of the mountain in the range of 0.1 mm to 0.2 mm.

According to the present invention, a stress analysis was performed using a finite element method for the implant having the dense bone joint 32 formed on the body 30 of the implant 10. That is, the dense bone joint 32 is formed on the body 30, but tapered to 1 / 1.5, and the outer surface has a thin screw having a pitch of 0.25 mm to 0.35 mm and a height of 0.1 mm to 0.2 mm in height. A model with 32a) and a tapered and non-screwed model are placed in the mandible, and a vertical load of 400 N (maximum gripping force that can be applied by humans) is applied to the upper apex of the implant as a static load. It was. According to the finite element analysis, as shown in FIG. 4, an implant having a taper of 1 / 1.5 generates significantly lower stress in the dense bone C1 than an implant without a taper. In particular, the maximum stress concentration in the dense bone (C1) at the top of the implant (10), that is, the dense bone (C1) at the top of the dense bone junction (32) is approximately compared to the implant having no taper Was lower than 7.5 MPa. In addition, as shown in FIG. 5, an implant having a fine screw 32a having a pitch in the range of 0.25 mm to 0.35 mm and a height of a peak in the range of 0.1 mm to 0.2 mm is more dense than the implant having no fine screw ( C1) showed significantly lower stress, and the maximum stress generated in the dense bone (C1) at the top of the dense bone joint 32, which is the maximum stress concentration, was approximately 25 MPa or less compared to an implant without a thin screw. You can see that it appears low.

As a result, it can be seen that the stress generated in the dense bone C1 is remarkably dropped by tapering the dense bone joint 32 connected to the dense bone C1 and forming a screw 32a on the outer surface thereof. As a result, bone fracture and bone fracture of dense bone (C1) can be prevented.

2 and 3 again, the spongy bone joint 34 of the body 30 extends long with the same diameter from the lower end of the dense bone joint 32, and a thick screw 34a is formed on the outer surface thereof. . The coarse screw 34a increases the contact area of the cancellous bone (C2) to increase the bonding rate between the implant (10) and the cancellous bone (C2), and consists of a trapezoidal screw. In particular, the coarse screw 34a has a larger pitch and a higher height than the thin screw 32a of the dense bone joint 32, and is configured to have a relatively dense pitch. Here, the pitch of the thick screw 34a and the height of the peak may vary depending on the length of the implant 10, the implantation position of the implant 10, the state of the dense bone C1, and the pitch of approximately 0.7 mm to 0.9 mm. It has been shown that it is preferred to have a height of the mountain in the range of 0.4 mm to 0.6 mm.

According to the present invention, the stress analysis was performed using the finite element method for the implant having the trapezoidal coarse screw 34a formed on the spongy bone joint 34 of the body 30. That is, a model in which a trapezoidal thick screw 34a having a pitch in the range of 0.7 mm to 0.9 mm and a height of a peak in the range of 0.4 mm to 0.6 mm is formed on the sponge bone joint 34 of the body 30, and a thick screw is formed. A model with a non-molded model placed in the mandible was prepared, and a vertical load of 400 N was applied to the upper apex of the implant as a static load. According to the finite element analysis, an implant with a trapezoidal coarse thread with a pitch in the range of 0.7 mm to 0.9 mm and a height of a peak in the range of 0.4 mm to 0.6 mm is less than the spongy bone (C2) and the dense bone compared to the implant without the C1) has been shown to generate low stress. In particular, as shown in FIG. 6, the implant having the trapezoidal coarse screw was found to generate significantly lower stress in the dense bone C1 than the implant without the coarse screw.

As a result, a threaded thick screw 34a is formed in the spongy bone joint portion 34 to be joined to the spongy bone C2, but by forming relatively densely, the stress generated in the spongy bone C2 and the dense bone C1 is significantly lowered. It can be seen, and thus bone fracture and bone fracture of the implant surrounding bone can be prevented.

On the other hand, Figure 7 is a view showing a modified example of the spongy bone joint 34. According to this, the spongy bone joint 34 of the modified example is provided with a trapezoidal coarse screw 34a, but gradually lowers as the thread is directed downward, converging to the outer circumferential surface, and at the same time, the lower surface 34b of the coarse screw 34a under load. Compared with the upper surface 34c of this thick screw 34a, it has a structure which makes it incline comparatively gentle. This can cause unnecessary stress concentration in the sponge (C2) of the thick bone 34a formed in the spongy bone joint 34, bar far from the top of the spongy bone joint 34 to generate a large stress This is to avoid the unnecessary concentration of unnecessary stress in the cancellous bone (C2) by gradually reducing the thick screw (34a). In addition, the lower surface 34b of the thick screw 34a is gently formed so as to evenly distribute the load transmitted from the upper portion to the sponge bone C2 while increasing the contact area with the sponge bone C2. Here, the inclination angle of the lower surface 34b of the coarse screw 34a preferably forms an angle in the range of approximately 45 ° to 55 ° with respect to the outer surface of the cancellous bone joint portion 34.

According to the stress analysis using the finite element method, a trapezoidal coarse screw 34a is formed at the spongy bone joint 34 of the body 30, and the lower the thread is gradually lowered, the inclination angle of the lower surface 34b is decreased. The gently configured implants in the 45 ° to 55 ° range have been shown to produce lower stresses in the cancellous bone (C2) as well as even stresses throughout the cancellous bone (C2) compared to non-threaded implants. That is, a model is formed with a trapezoidal coarse screw 34a having a lower thread 34b having a gradually lowered thread and an inclined angle toward the lower part, and a model having a screwless model placed in the mandible. When a vertical load of 400 N is applied to the upper apex of the implant at a static load, the implant having a gradually lower thread and a trapezoidal coarse screw 34a of the lower surface 34b having a gentle inclination angle is shown in FIG. 8 compared to an implant without a screw. As shown, not only the low stress is generated on the cancellous bone (C2) but also the even stress is generated throughout the cancellous bone (C2).

2 and 3, the lower curved portion 36 of the body 30 has a predetermined radius of curvature and forms a gentle curve from the lower edge of the spongy bone joint 34. The lower curved portion 36 made of a gentle curve distributes and distributes the load transmitted from the upper portion to the surrounding sponges C2 evenly, thereby preventing the stress from concentrating on specific portions of the sponges around the periphery of the bone. Preventing bone collapse and bone destruction of the sponges (C2) due to concentration. Here, the lower curved portion 36 has a radius of curvature in the range of approximately 2.5 mm to 3.0 mm from the lower edge of the spongy bone junction 34 is preferably configured gently.

9 is a view showing a modified example of the lower curved portion 36. According to this, the lower curved part 36 of the modification is provided with the screw 36a connected with the coarse screw 34a of the cancellous bone joint part 34. As shown in FIG. The screw 36a of the lower curved portion 36 connected to the coarse screw 34a of the cancellous bone joint 34 increases the bone contact rate by increasing the contact area between the cancellous bone C2 and the implant 10. give. According to the stress analysis using the finite element method, the lower curved portion 36 on which the screw 36a is formed has a high bonding ratio with the cancellous bone C2 while preventing stress from concentrating on the surrounding cancellous bone C2. . Here, the screw 36a of the lower curved portion 36 extends from the coarse screw 34a of the cavernous bone joint 34, so that the screw 36a has the same pitch and peak height as the coarse screw 34a of the cavernous bone joint 34. do.

Although the preferred embodiments of the present invention have been described above by way of example, the scope of the present invention is not limited to these specific embodiments, and may be appropriately changed within the scope of the claims.

As described above, the dental osteoadhesion implant according to the present invention has a dense bone joint and a spongy bone joint and a lower curved joint joined with the dense bone, but the dense bone joint and the spongy bone joint form a screw, and the lower curved part By configuring to form a gentle curve has the effect of reducing the stress generated in the dense bone and sponge bone to a minimum, and thus has the advantage of preventing bone fracture and bone fracture of the dense bone and sponge bone. In particular, the dense bone joint formed with a thin screw is to minimize the stress generated in the dense bone to prevent bone fracture and bone fracture of the dense bone.

Claims (5)

In the dental osteoadhesion implants embedded in the dense and cancellous bone of the alveolar bone, A dense bone joint portion 32 having a tapered surface that gradually increases in diameter toward the top, and having a thin screw 32a having a first pitch on the tapered surface; A spongy bone joint portion 34 extending downward from the dense bone joint portion 32 and having a thick screw 34a having a second pitch larger than the thin screw 32a on an outer surface thereof; Dental bone adhesion implant, characterized in that consisting of the lower surface portion 36 is formed with a predetermined curvature at the lower end of the spongy bone joint portion (34). The dental osteoadhesion implant according to claim 1, wherein the coarse screw (34a) of the spongy bone joint portion (34a) is formed to have a thread gradually lowered downward. The thread of the thick screw 34a of the cavernous bone joint portion 34 is formed such that the lower surface 34b under load has a gentle inclination with respect to the upper surface 34c. Dental bone adhesion implants. The taper value of the dense bone joint portion 32 is 1 / 1.5, and the thin screw 32a of the tapered surface has a pitch in the range of 0.25 mm to 0.35 mm and a thread height in the range of 0.1 mm to 0.2 mm. Dental osteoadhesive implant, characterized in that. 2. The dental osteoadhesion implant according to claim 1, wherein the coarse screw (34a) of the spongy bone joint (34) has a pitch in the range of 0.7 mm to 0.9 mm and a thread height in the range of 0.4 mm to 0.6 mm.