KR20110037542A - Stent for implant and method for manufacturing the same - Google Patents

Abstract

PURPOSE: A stent for an implant and a manufacturing method thereof are provided to precisely and securely guide a perforation drill. CONSTITUTION: A stent for an implant comprises: a supporting part covering narrow region, tongue region, and occlusion region of teeth; a main body(115) which is extended from the supporting part, is arranged in a site where an implant is planted, and is equipped with a surgical operation part having a penetration hole; guide bushings(150,150') which are inserted in the penetration hole and guide the alveolar bone perforation drill; and a resin frame(145) covering the side of the guide bushing.

Description

Stent for implant and method for manufacturing same

The present invention is an implant stent and a method for manufacturing the same, the guide bushing is fixed to the body by a resin frame formed of a resin can be accurately and firmly guided drill drill, when inserting the implant stent into the tooth It effectively absorbs vibrations caused by the drill for drilling the implant while improving the adhesion between the undercut of the tooth and the inner surface of the stent without causing pain to the patient or causing damage to the tooth surface or the stent itself. The present invention relates to a implantable stent and a method for manufacturing the same.

Implant is a prosthesis used to replace a badly damaged tooth. An artificial root made of a special metal (usually titanium or titanium alloy) is implanted in the alveolar bone and entangled with the alveolar bone tissue. By using the artificial teeth to form a dental treatment method that allows you to live a daily life with a sense almost the same as the original one of their own teeth or the artificial teeth that have been treated in this way.

These implants have recently gained much attention as they have advantages such as long life and very similar to natural teeth, without damaging the surrounding teeth except for the teeth that need to be treated, compared to the methods using dentures and bridges. .

If the implant method described above is briefly described, first, the gingival (gum) of the patient to be implanted is cut to expose the alveolar bone. Next, the position of the implant to be inserted among the exposed alveolar bone is determined, and a hole for implantation is formed by deleting a portion of the alveolar bone at the position using a drilling tool such as a drill. Next, the implant including the fixture and the abutment is placed in the formed hole, and the implant installation is completed by covering the gingiva.

On the other hand, when implanting the gingival bone by exposing the gingival bone during implantation, and using a direct drill or the like on it, it is usually difficult to accurately determine the exact position and direction to perform the drilling operation. I use an assistive device called.

In the case of such a stent, the upper and / or lower jaw of the subject is obtained using an impression material such as a rubber material before the implant procedure, and then plaster is poured on the sound to the upper and / or lower jaw of the subject. Make a plaster model that mimics the shape.

The gypsum model is then coupled to an articulator and the jaw and upper and lower teeth, almost similar to those of the subject, are reproduced outside the mouth.

Then, after curing by applying a resin of a transparent material so as to cover the cavity and the teeth missing teeth, the resin portion filled in the cavity missing teeth to form a through hole through which the drill for drilling the implant can pass.

The transparent resin product made through this process is a stent, and the cavity made in the same shape as the tooth that the transparent resin is wrapped at the time of manufacture is inserted into the actual tooth to serve as a support for supporting the entire stent.

Recently, according to the development of 3D imaging technology, instead of the plaster model, a rapid prototyping (RP) based on 3D image data is used to produce a model that simulates the maxillary and / or mandible of the subject. Only the manufacturing process of the model is different, but the process of making the implant stent is the same.

However, when using this stent to drill perforated dental or edentulous subjects, it was considerably improved compared to the case without the stent. However, the stent itself was shaken to maintain the position originally intended. There were many problems such as holding the stent and manipulating the drilling tool with the other hand.

The reason why the stent fixed to the teeth does not maintain the initial position is largely due to the structure of the stent, because the close contact between the outer surface of the stent and the inner surface of the stent is limited by the maximum abundance of the teeth.

1 is a view of a conventional stent and the teeth of the operator to which the stent is inserted, and FIG. 2 is a schematic cross-sectional view taken along line AA in the state in which the stent of FIG. As can be seen, there is a lack of close contact between the undercut portion (U) below the maximum abundance (H) of the tooth and the inner surface of the stent.

This is because when the stent is inserted into the tooth, the opening of the stent is allowed to be somewhat larger than the actual undercut size of the tooth so that the stent can pass flexibly through the maximum ridge. If the stent is made without such a margin, it will cause pain to the operator when the stent is inserted into the tooth, and in severe cases, damage to the tooth surface or the stent itself.

As a solution to the problem of adhesion of the stent, it is possible to consider making the stent into a resin material having a considerably large elastic modulus. However, if the stent is manufactured from a resin material having a fairly large modulus of elasticity, the stent itself is less durable and difficult to maintain the basic shape of the initial stage. In addition, the alveolar bone is usually drilled using a drill rotating at high speed and high torque of about 10,000 RPM. This is a difficult solution to employ because there is a problem that the stent does not have rigidity enough to keep its initial position even in the punctured state.

Therefore, it has conventionally been recognized that there is an unavoidable existence of a certain gap between the implant stent surface, the undercut U portion below the maximum abundance H of the tooth, and the inner surface of the stent.

The present invention was devised to solve the above problems, the guide bushing is fixed to the main body by a resin frame formed of a resin can accurately and firmly guide the drill for drilling, inserting the implant stent into the tooth Vibration caused by the drill for drilling an implant while increasing the adhesion between the undercut portion below the maximum abutment of the tooth and the inner surface of the stent, without causing pain to the subject or damage to the tooth surface or the stent itself. It is an object of the present invention to provide a stent for implants having a novel structure and a method for manufacturing the same, which can be effectively absorbed.

Implant stent according to a preferred embodiment of the present invention to achieve the above object, the support portion surrounding the buccal and lingual and occlusal side of the tooth, and extending from the support portion is disposed on the site where the implant is to be treated and the through hole A main body having an excised surgical part; A guide bushing inserted into the through hole to guide the drill for drilling the alveolar bone; And a resin frame attached to an inner surface of the procedure part and surrounding a side of the guide bushing to fix the guide bushing.

Here, the main body is preferably made of a transparent thermoplastic resin is heated by the omni bag.

At this time, the support portion is formed so as to surround a part of the undercut of the tooth beyond the maximum wind bulge of at least one of the buccal and lingual, it is preferable that the elastic body capable of elastic deformation is attached to the inner surface of the buccal and lingual side of the support.

At this time, the elastic modulus of the elastic body is preferably larger than the elastic modulus of the support.

In addition, the elastic body is preferably a silicon material.

In addition, it is preferable that a stepped step is further formed at each lower end of the buccal side and the lingual side of the support part.

In addition, each of the buccal side and the lingual side of the support portion is preferably provided with a through hole for the separation preventing the elastic body is filled.

On the other hand, the occlusal side of the support portion is preferably formed with a discharge hole for discharging the extra elastic body to the outside.

In addition, the support portion and the surgical portion is preferably made of fiber-reinforced plastic or carbon fiber.

And, it is preferable that the outer shape of the said guide bushing is cylindrical cylinder shape.

In addition, the outer shape of the guide bushing is preferably an ellipsoidal cylinder shape.

Furthermore, it is preferable that at least one or more truncated cone-shaped fixing bases are formed in the supporting part or the surgical part through which a passing hole through which the fixing screw inserted into the alveolar bone passes along the longitudinal direction is fixed to the support part or the surgical part. .

According to another aspect of the invention, the guide bushing fixing step of fixing the guide bushing with a resin in the position to be perforated alveolar bone in the plaster model of the maxillary or mandibular structure of the subject; Resin heating step for heating by putting a transparent thermoplastic resin in the omni bag; A resin covering step of covering the thermoplastic resin heated by the omni bag on the gypsum model to which the guide bushing is fixed and the resin on the gypsum model; A vacuum suction step of vacuum suction from the lower side by the omni bag so that the thermoplastic resin contacts the gypsum model and the resin outer surface; And a finishing step of removing a portion in which the guide bushing is located in the thermoplastic resin to open the hollow of the guide bushing.

Here, the guide bushing fixing step, after placing the guide bushing on the gypsum model, it is preferable to build up (built up) surrounding the side of the guide bushing with the resin to fix the guide bushing.

In the implant stent and the method for manufacturing the same according to the present invention, the guide bushing is fixed to the main body by a resin frame formed of a resin, so that the drilling drill can be accurately and firmly guided.

On the other hand, the support portion surrounding the buccal and lingual and occlusal side of the tooth is formed to cover a portion of the undercut of the tooth over the maximum abundance of at least one of the buccal and lingual side, the elastic deformation is on the inner surface of the buccal and lingual side of the support. It has a configuration in which elastic bodies are attached as much as possible. Therefore, the process of inserting the stent into the teeth by the elastic deformation of the elastic body proceeds smoothly, and the elastic body that is contracted when passing through the maximum bulge of the tooth is elastically restored at the undercut bulge, The inner surface is in close contact with each other via the elastic body to improve the fixing of the stent.

In addition, since the inherent elasticity of the elastic body has an effect of absorbing vibration caused by the drill for drilling the implant, the stent of the stent can be continuously maintained even during the drilling operation.

Figure 3 is a perspective view showing a main body and a resin frame in the implant stent according to the invention, Figure 4 is a perspective view schematically showing the teeth of the implant to the implant stent and the stent according to the invention, Figure 6 4 is a cross-sectional view taken along the line BB in the state in which the implant stent and the tooth is coupled.

Referring to the drawings, the implant stent of the present invention is attached to the main body 115, the guide bushings 150, 150 'mounted on the main body 115, and the main body 115, the guide bushing 150 And a resin frame 145 fixing 150 '.

The main body 115 includes a support part 120 surrounding the buccal B, buccal, lingual, and occlusal sides of at least one tooth 100 ', and the support part. And a surgical part 140 extending from 120 and having a through hole 142 on which guide bushings 150 and 150 'are mounted.

At this time, the support portion 120 is formed so as to surround a portion of the undercut (U) of the tooth (100 ') beyond the maximum wind bulge (H) of at least one of the buccal (B) and lingual (L).

Here, it is preferable that an elastic body 130 capable of elastic deformation is attached to inner surfaces of the buccal side B and the lingual side L of the support part 120.

In addition, the support portion 120 serves to support and hold the entire implant stent 100 at a predetermined position of the tooth (100 ').

Implant stent 100 is to be made by applying a resin of a transparent material to cover the gingival model of the patient's teeth, the tooth loss 110 and the appropriate number of teeth (100 ') and harden it Thus, the support 120 has a cavity 122 of the same shape as the outline of the tooth 100 'to which the resin has been applied.

Therefore, when the cavity 122 is fitted to the tooth 100 'having a corresponding shape, the support part 120 contacts the buccal side B, the lingual side L, and the occlusal side O of the tooth 100'. The wrapping is done.

How many teeth (100 ') to wrap when making the implant stent 100, that is, how many cavities 122 to be made in the implant stent 100 in consideration of the fixing of the stent 100 is selected It cannot be decided uniformly.

As an example, the implant stent 100, as shown in Figure 4, may have a shape to wrap only the molar or premolars except for the central incisor (front teeth) in addition to the shape surrounding the entire dentition.

In addition, the surgical part 140 extends from the support part 120 and has a through hole 142 into which the guide bushings 150 and 150 ′ guide the drill 200 for alveolar bone drilling.

Since the resin applied to the gingival 110 portion where the tooth is lost in the process of making the implant stent 100 is a hardened portion, there is no structure such as the cavity 122 formed in the support 120.

Since the procedure 140 is made dependent on where there is no tooth in the teeth of the subject, it may be disposed anywhere in the middle or end of the stent 100.

The main body 115 configured as described above, that is, the support part 120 and the surgical part 140 is preferably manufactured by heating a transparent thermoplastic resin by an omni bag.

Of course, the support unit 120 and the surgical unit 140 may be made of not only a transparent resin, but also fiber reinforced plastics or carbon fibers.

Glass fiber, carbon fiber or kevlar may be used as the reinforcing material of the fiber reinforced plastic.

On the other hand, the guide bushings 150 and 150 ′ are inserted into the through holes of the main body 115 to serve to guide the alveolar bone drilling drill 200.

Here, the through-hole 142 of the main body 115 surgical section 140 is a hole through which the drill 200 for drilling the alveolar bone enters and exits, and is slightly larger than the outer diameter of the drill 200. The through hole conventionally served only as an access passage of the drill 200 as described above, and did not play a role of guiding the drilling direction of the drill 200.

In the present invention, the guide bushings 150 and 150 ′ are inserted into the through-holes 142 of the surgical part 140 to guide the drill in the drilling direction as described above.

The guide bushings 150 and 150 ′ have a hollow cylindrical shape and are in contact with the outer surface of the shank portion 210 of the alveolar bone drilling drill 200 and guide the same in a precise drilling direction. ) Is penetrating.

And another example of the guide bushing is shown in FIG.

Referring to the drawings, the guide bushing 150 ′ is ellipsoidal in shape.

An advantage of the guide bushing 150 ′ having an elliptic cylinder shape is that the guide bushing 150 ′ fixed to the stent 100 is rotated at high speed while the drill 200 is guided along the guide surface 152 ′. ) Is that the cross-sectional shape in the direction perpendicular to the drilling direction of the drill 200 is elliptical, it is possible to suppress the guide bushing 150 'to rotate together with the rotation of the drill 200.

The guide bushings 150 and 150 ′ are basically for guiding the drilling direction of the drill 200, and have a cylindrical shape having an outer diameter larger than the diameter of the drill 200 at an appropriate position of the drill shank 210. If the induction part 220 is formed and a stopper is formed on the lower end of the induction surfaces 152 and 152 'of the guide bushings 150 and 150' or the upper surface of the induction part 220, the drilling depth may also be controlled.

That is, the guide surface of the guide bushings 150, 150 ′ of the guide bushings 150, 150 ′ is appropriately selected and the stopper prevents the guide portion 220 from moving forward. 152 ') the lower end or the upper surface of the induction part 220, the lower surface of the induction part 220 until the contact with the stopper of the guide bushings 150 and 150' or the stopper of the induction part 220 is guide bushing The drilling depth can be limited by advancing the drill 200 only until it contacts the upper surface of the 150 and 150 '.

Examples of the shape that can be used as the stopper include placing the stepped portion at the lower end of the guide surfaces 152 and 152 'of the guide bushings 150 and 150', and the diameter thereof on the upper surface of the guide portion 220 of the drill 200. And forming a disk-shaped jaw protruding along the direction.

In addition, the resin frame 145 is attached to the inner surface of the surgical part 140, and is configured to surround side portions of the guide bushings 150 and 150 ′ to fix the guide bushings 150 and 150 ′.

When the guide bushings 150 and 150 'are fitted into the through-holes 142 of the surgical part 140 without the resin frame 145, the guide bushings 150 and 150' for external force may be due to the flexibility of the surgical part 140. Since the position fixing is not well made, the guide bushings 150 and 150 'may be moved in the process of drilling the alveolar bone with the drill 200.

In order to prevent such a point, the resin frame 145 is attached to the inner surface of the treatment unit 140 of the main body 115, the lower surface of the surgical unit 140 in the lower body main body 115 as shown in FIG. 4, The side surfaces of the guide bushings 150 and 150 'fitted in the through holes 142 are wrapped to fix the guide bushings 150 and 150'.

A method of manufacturing the implant stent as described above will be described with reference to FIG. 5.

First, in the gypsum model of the maxillary or mandibular structure of the subject, the guide bushings 150 and 150 'are fixed to the position at which the alveolar bone is to be punctured (S100). Here, the resin is cured to form the resin frame 145.

Specifically, the guide bushing fixing step (S100), after placing the guide bushings 150, 150 'on the gypsum model, guide bushings 150 with resin to fix the guide bushings 150, 150' The resin frame 145 is built up on the gypsum model by enclosing the sides of the cavities 150 '.

Then, the transparent thermoplastic resin is put into the omni bag (S110).

At this time, the edge of the thermoplastic resin is fixed to the omni bag and then heated to make the resin flexible.

Subsequently, the thermoplastic resin heated by the omnibag is covered with the gypsum model to which the guide bushings 150 and 150 'are fixed and the resin frame 145 on the gypsum model (S120).

Next, the thermoplastic resin is sucked under vacuum by the omnibag so as to contact the outer surface of the plaster model and the resin frame 145 (S130).

Finally, the portion in which the guide bushings 150 and 150 'are positioned is removed from the thermoplastic resin so that the hollows of the guide bushings 150 and 150' are opened (S140).

Meanwhile, other technical features of the present invention will be described.

In the support part 120, except for the occlusal side (O), the elastic body 130 that is elastically deformable is attached to the inner surface of the buccal side (B) and the lingual side (L).

6 is a cross-sectional view taken along the line BB in the state in which the stent 100 and the tooth 100 'of FIG. 4 are coupled to each other, as shown in FIG. H) the undercut U portion below and the inner surface of the stent 100 are in close contact with each other via the elastic body 130.

The elastic body 130 is made of a material free of elastic deformation, for example, silicon material, the elastic modulus of the elastic body 130 is configured to be larger than the elastic modulus of the support portion 120.

Therefore, in the process of inserting the stent 100 into the tooth 100 ′, since the elastic body 130 first causes elastic deformation before the support 120 is elastically deformed, the elastic deformation of the support part 120 is minimized. While the stent 100 is able to be gently inserted into the tooth (100 ').

In addition, when the stent 100 is completely inserted into the tooth 100 ′, that is, when the occlusal side O of the support 120 comes into contact with the occlusal surface of the tooth 100 ′, the elastic body 130 The elasticity is restored so as to fill the gap between the undercut U portion below the maximum wind portion H of the tooth 100 'and the inner surface of the stent 100 to maintain the adhesion of the stent 100.

The role of the elastic body 130 contributes to maintaining the stability of the stent 100 not only in the static state but also in the dynamic state, which inherent elasticity of the elastic body 130 to the drill for drilling the implant (200) This is because it has an effect of absorbing the vibration caused by.

As described above, the implant stent 100 of the present invention may have an additional configuration for more effectively preventing the elastic body 130 from being detached due to reinsertion of the stent repeatedly.

The basic force for maintaining the state in which the elastic body 130 is attached to the inner side of the buccal side B and the lingual side L of the support part 120 is the adhesive force of the elastic body 130 itself. The reason why silicon is selected as the preferred material of the elastic body 130 is that not only elastic restoring force but also such adhesive force is taken into consideration.

However, the adhesive force of the elastic body 130 alone may not be sufficient to prevent the elastic body 130 from deviating from or leaving the initial position by the use of a repetitive stent. In the present invention, two additional configurations are provided to prevent separation of the elastic body 130.

The first configuration is to form step 124 at each lower end of the buccal side B and the lingual side L of the support part 120. 7 is a cross-sectional view taken along line BB in a state where the implant stent and the tooth of FIG. 4 are coupled when the jaws are formed at each lower end of the buccal side B and the lingual side L of the support. The configuration of 124 is shown well.

As can be seen intuitively, by the configuration of the step 124, the elastic body 130 has a form sandwiched between the end of the occlusal side (O) and the step 124, accordingly the elastic body 130 It is effectively suppressed to be pushed out or released out of position.

The second configuration is to form a through-hole for preventing separation 126 in the buccal side (B) and lingual side (L) of the support portion 120. FIG. 8 is a cross-sectional view when the stent 100 and the tooth 100 ′ of FIG. 4 are cut along the CC line, and the elastic body 130 is filled to the inside of the separation preventing through hole 126. Note the facts.

If the elastic body 130 is made of a silicone material having a certain degree of fluidity before curing, the silicone material is applied to the buccal side B and the lingual side L of the support part 120 to form the elastic body 130. In this process, the silicon can be filled to the inside of the separation preventing through hole 126. After the fluidity of the silicon disappears, the elastic body 130 extends into the separation preventing through hole 126. Have).

Accordingly, the completed elastic body 130 is more firmly attached by the adhesive force between the arm 126 ′ and the inner surface of the through hole 126 for preventing separation, and the arm 126 ′ has the elastic body 130 up and down. Since it can counter the shear force generated when trying to move, the fixing of the elastic body 130 is more surely guaranteed.

On the other hand, the occlusal side (O) of the support portion 120 does not include an elastic body 130, which is when the elastic body 130 is elastically behaving on the occlusal side (O) in the vertical direction of the stent 100 This is because play occurs in fixation.

Therefore, in no case should the elastic body 130 on the occlusal side (O) of the support portion 120. However, when the resin is applied to the buccal side B and the lingual side L of the support part 120 in order to form the elastic body 130, the resin is applied with a little margin, so that the extra resin is pushed up to the occlusal side O. There is a possibility of entering.

FIG. 9 is a cross-sectional view when the stent 100 and the tooth 100 ′ of FIG. 4 are cut along the DD line, and an extra elastic body 130 is provided on the occlusal side O of the support 120. It can be seen that the discharge hole 128 for discharging to the outside is formed. The discharge hole 128 is preferably formed at a position corresponding to the concave portion of the tooth occlusal surface.

Here, Figure 4 is a basic embodiment of the implant stent 100 according to the present invention, as well as the configuration of each modification, that is, step 124 and the separation prevention through-hole 126 and the discharge hole 128 at once It must be taken into account to show. That is, there is no need or limitation that the step 124, the separation prevention through-hole 126, and the discharge hole 128 have to be separately provided, respectively, and the three additional configurations may be used in combination with each other as needed. Care should be taken.

In the above description based on the configuration of the support portion 120 of the implant stent 100 according to the present invention, in addition to the unique configuration of the support portion 120, the present invention may further include some other technical features. .

The part to be mentioned first relates to the through hole 142 of the surgical part 140. The through hole 142 is a hole through which the drill 200 bores the alveolar bone, and is formed slightly larger than the outer diameter of the drill 200. However, in the related art, the through hole 142 merely functions as an entrance and exit of the drill 200, but did not play a role of guiding the drilling direction of the drill 200.

In order to solve this problem, the implant stent 100 of the present invention is shown in Figure 10, for guiding the drilling direction of the alveolar bone drilling drill 200 in the through-hole 142 of the surgical section 140 A guide bushing 150 having a cylindrical cylindrical shape as shown in FIG. 4 was embedded and fixed (see FIG. 4).

The guide bushing 150 is formed through the induction surface 152 of the circular cross section in contact with the outer surface of the shank 210 of the alveolar bone drilling drill 200 to guide it in the correct drilling direction.

In addition, another example of the guide bushing is shown in FIG. 11. The characteristic of the guide bushing 150 ′ of FIG. 11 is that the outer shape is an ellipsoidal cylinder shape.

An advantage of the guide bushing 150 'in the shape of the elliptic cylinder is that the guide bushing 150' fixed to the stent 100 is rotated at high speed while the drill 200 is guided along the guide surface 152 '. Since the cross-sectional shape of the direction perpendicular to the drilling direction of the drill 200 is elliptical, it is possible to suppress the guide bushing 150 'from being rotated together with the rotation of the drill 200.

The guide bushings 150 and 150 ′ are basically for guiding the drilling direction of the drill 200, and have a cylindrical shape having an outer diameter larger than the diameter of the drill 200 at an appropriate position of the drill shank 210. If the induction part 220 is formed and a stopper is formed on the lower end of the induction surfaces 152 and 152 'of the guide bushings 150 and 150' or the upper surface of the induction part 220, the drilling depth may also be controlled.

That is, the guide surface of the guide bushings 150, 150 ′ of the guide bushings 150, 150 ′ is appropriately selected and the stopper prevents the guide portion 220 from moving forward. 152 ') the lower end or the upper surface of the induction part 220, the lower surface of the induction part 220 until the contact with the stopper of the guide bushings 150 and 150' or the stopper of the induction part 220 is guide bushing The drilling depth can be limited by advancing the drill 200 only until it contacts the upper surface of the 150 and 150 '.

Examples of the shape that can be used as the stopper include placing the stepped portion at the lower end of the guide surfaces 152 and 152 'of the guide bushings 150 and 150', and the diameter thereof on the upper surface of the guide portion 220 of the drill 200. And forming a disk-shaped jaw protruding along the direction.

In addition to the technical features of the implant stent 100 of the present invention other than the unique configuration of the support portion 120, the support base 120 is a truncated cone-shaped fixed base 160 as shown in FIG. And / or at least one embedded in the surgical unit 140.

The fixing base 160 is formed with a through hole 162 along its longitudinal direction. The fixing screw 300 for fixing the implant stent 100 more firmly in the mouth of the operator is provided with the through hole 162. ) And screwed into the alveolar bone (see FIG. 4).

The fixing screw 300 is used to obtain the fixing force of the stent 100 from the alveolar bone when the tooth state of the subject is significantly bad or the number of teeth to support the stent 100 is significantly short.

The fixed base 160 embedded in the implant stent 100 according to the present invention is pressed between the gingiva 110 and the head 310 of the fixing screw, a wide bottom surface of the upper and lower surfaces of the frustoconical gingiva (110) It is arranged to contact with. This arrangement prevents the fixing base 160 from being separated from the stent 100 by the pressing of the fixing screw 300.

As described above, although the present invention has been described by way of limited embodiments and drawings, the present invention is not limited thereto and is intended by those skilled in the art to which the present invention pertains. Of course, various modifications and variations are possible within the scope of the claims to be described.

Figure 1 is a perspective view schematically showing the teeth of the implant and the stent for the implant according to the prior art.

2 is a cross-sectional view taken along line A-A in a state in which the implant stent of FIG. 1 is coupled to a tooth.

Figure 3 is a perspective view showing the body and the resin frame in the implant stent according to the invention.

Figure 4 is a perspective view schematically showing the teeth of the implant and the implant stent according to the invention the stent.

FIG. 5 is a flowchart illustrating a method of manufacturing the implant stent of FIG. 4.

6 is a cross-sectional view taken along the line B-B in a state in which the implant stent and tooth of FIG.

FIG. 7 is a cross-sectional view taken along line B-B in a state where the implant stent and the tooth of FIG. 4 are coupled when a stepped portion is formed at each of the lower side of the buccal side and the lingual side of the support.

8 is a cross-sectional view taken along the line C-C in a state in which the implant stent and tooth of FIG.

9 is a cross-sectional view taken along the line D-D in a state in which the implant stent and tooth of FIG.

10 is a perspective view of a cylindrical cylindrical bushing that is buried in the through-hole of the implant stent according to the present invention.

11 is a perspective view of an elliptic cylinder-shaped guide bushing embedded in a through-hole of an implant stent according to the present invention.

Figure 12 is a perspective view of a fixed base of a truncated cone-shaped embedded in the support and / or treatment of the implant stent according to the present invention.

<Explanation of symbols for the main parts of the drawings>

100: implant stent 100 ': teeth

110: gingiva 115: body

120: support part 122: cavity part

124: step 126: through hole for separation prevention

126 ': arm 128: discharge hole

130: elastic body 140: the surgical part

142: through hole 145: resin frame

150, 150 ': guide bushing 152,152': guide face

160: fixed base 162: through hole

200: drilling drill 210: shank portion of the drill

220: guide portion of the drill 300: fixed screw

310: head of the fixing screw B: buccal

L: Lingual O: Occlusal

H: Height of contour U: Undercut

Claims (14)

A main body including a support portion surrounding the buccal and lingual and occlusal sides of the tooth, and a treatment portion extending from the support portion and disposed at a portion to be implanted and having a through-hole; A guide bushing inserted into the through hole to guide the drill for drilling the alveolar bone; And A resin frame attached to an inner surface of the procedure part and surrounding a side of the guide bushing to fix the guide bushing; Implant stents comprising a. The method of claim 1, The main body is an implant stent, characterized in that the transparent thermoplastic resin is heated by the omni bag. The method of claim 1, The support portion is formed so as to surround a portion of the undercut of the tooth beyond the maximum bulge of at least one of the buccal and lingual, Implant stent, characterized in that the elastic body capable of elastic deformation is attached to the inner side of the buccal and lingual side of the support. The method of claim 3, The stent for implants, characterized in that the elastic modulus of the elastic body is greater than the elastic modulus of the support. The method according to claim 3 or 4, The stent for implants, characterized in that the elastic material is a silicon material. The method of claim 1, Implant stent, characterized in that the step is further formed on each lower end of the buccal and lingual side of the support. The method according to claim 3 or 6, wherein Implant stents, characterized in that each of the buccal and lingual side of the support portion is further formed with a separation preventing through hole filled with the elastic body. The method according to claim 3 or 6, wherein Implant stent, characterized in that the occlusal side of the support portion is further formed with a discharge hole for discharging the extra elastic body to the outside. The method of claim 1, The support and the implant portion is a stent for implants, characterized in that made of fiber-reinforced plastic or carbon fiber. The method of claim 1, Implant stent, characterized in that the outer shape of the guide bushing is cylindrical cylinder shape. The method of claim 1, Implant stent, characterized in that the outer shape of the guide bushing is an ellipsoidal cylinder shape. The method of claim 1, The support or the implant, characterized in that at least one implant is embedded in the truncated cone-shaped fixing base formed along the longitudinal direction of the passage hole through which the fixing screw inserted into the alveolar bone to fix the implant stent For stents. A guide bushing fixing step of fixing the guide bushing with a resin at a position where the alveolar bone is to be perforated in a plaster model having a maxillary or mandibular structure of the subject; Resin heating step for heating by putting a transparent thermoplastic resin in the omni bag; A resin covering step of covering the thermoplastic resin heated by the omni bag on the gypsum model to which the guide bushing is fixed and the resin on the gypsum model; A vacuum suction step of vacuum suction from the lower side by the omni bag so that the thermoplastic resin contacts the gypsum model and the resin outer surface; And A finishing step of removing a portion where the guide bushing is located in the thermoplastic resin so that the hollow of the guide bushing is opened; Implant stent manufacturing method comprising a. The method of claim 13, The guide bushing fixing step, After placing the guide bushing on the gypsum model, the implant stent manufacturing method characterized in that the built-up (built up) surrounding the side of the guide bushing with the resin to fix the guide bushing.

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