KR102205986B1 - trephine drill for implant - Google Patents

Abstract

In order to improve the precision of the procedure, the present invention provides a trapine drill for implants that forms a perforation for placement of a fixture, comprising: a shank portion having a mounting portion coupled to a dental handpiece at one end thereof; A guide rod portion extending from the inner end of the shank portion and having a diameter corresponding to the alignment hole so as to be inserted into and guided into a cylindrical alignment hole formed by an initial drill in the alveolar bone corresponding to the fixture placement area; And it is connected to the shank portion and rotated at the same time, the inner diameter is formed larger than the outer diameter of the guide rod portion, so that the bone fragment receiving space is formed so that the bone cutting material is guided between the outer periphery of the guide rod portion, and the circumferential direction at the end edge Accordingly, it provides a trapine drill for implants including a rotary cutting portion in which a plurality of cutting edges are formed.

Description

Trephine drill for implant

The present invention relates to a trefine drill for implants, and more particularly, to a trefine drill for implants with improved treatment precision.

In general, an implant refers to a substitute that can replace human tissue when the original human tissue is lost, but in dentistry, it means implanting an artificial tooth. In other words, it is a treatment method in which a fixture made of titanium, which has no rejection reaction to the human body, is implanted in the alveolar bone from which the tooth has been pulled out to replace the lost root, and then the artificial tooth is fixed to restore the function of the tooth.

In the case of a general prosthesis or denture, the surrounding teeth and bones are damaged over time, but the implant can prevent damage to the surrounding dental tissue and can be used stably because there are no secondary caries. In addition, since the implant has the same structure as a natural tooth, there is no pain or foreign body sensation in the gums, and it can be used semi-permanently if it is well managed.

1 is a flow chart showing a conventional implant procedure.

As shown in Figure 1, the conventional implant procedure is the first procedure (s1, s2, s3, s4) in which a fixture is placed in the alveolar bone, and the time when the fixture is bone fused to the alveolar bone (3-6 months). ), and then fixing the final prosthesis (s5, s6).

First, the first procedure is a gingival removal step (s1) to open the gums in the part where the teeth are missing, a multi-stage drilling step (s2) to form a perforation in which a fixture is to be placed, and a fixture placement step (s3), and an implanted fix. It consists of a step (s4) of coupling the temporary teeth to the chure.

In detail, in the gum removal step (s1), the gum is removed through a tissue punch or the like, and the alveolar bone at the position where the fixture is placed is exposed. Then, through a multi-stage drilling step (s2) on the exposed portion of the alveolar bone, a perforation for fixture placement is formed.

In this case, the multi-stage drilling step (s2) may include forming an initial hole, expanding the hole, forming a thread inside the hole, and removing the remaining alveolar bone inside the hole. It can be made in various ways depending on the type of drill used and the drilling method.

In addition, when the fixture is placed in the perforation formed through the multi-stage drilling step (s2) (s3), and the temporary teeth are coupled to the placed fixture (s4), the first procedure is completed. Here, the fixture placed in the perforation serves as the root of the artificial tooth. Therefore, it is very important to form an accurate perforation in the multi-stage drilling step (s2) in order to rapidly and stably recover the alveolar bone forming bone fusion with the fixture, and to provide a stable bonding force between the alveolar bone and the fixture after bone fusion. It will determine the completeness of the artificial tooth formation through the implant procedure.

On the other hand, the maxillary sinus is a space filled with air on the upper side of the molar root on both sides of the maxilla, and the alveolar bone on the maxillary side in contact with the maxillary sinus has a thin thickness and low bone density. Therefore, when the teeth of the maxillary sinus are extracted and the fixture is placed, there is a problem in that it cannot be firmly placed. In order to solve this problem, after performing a bone graft to reinforce the remaining bone on the inner surface of the alveolar bone on the maxillary sinus, the fixture is placed.

At this time, inside the maxillary sinus, there is a maxillary sinus membrane that controls the humidity in the nasal cavity in connection with the respiratory tract and controls resonance during vocalization. If the maxillary sinus membrane is torn during the drilling work to place the fixture, the inside of the maxillary sinus is exposed to pathogens and a fatal secondary infection to the maxillary sinus and respiratory tract may occur, so careful work is required.

Meanwhile, the conventional maxillary ipsilateral implant placement is performed in the following process.

First, the thickness of the alveolar bone at the fixture placement location is measured through CT imaging, and a stopper capable of limiting the insertion depth of the drill corresponding to the measured alveolar bone is provided on the outer periphery of the drill, and a hole is formed by drilling. Subsequently, water or a lifting tool is inserted through a perforation to elevate the maxillary sinus membrane from the inner surface of the maxillary sinus alveolar bone. In addition, when the maxillary sinus membrane is elevated from the inner surface of the alveolar bone, a bone graft layer having a sufficient thickness and density to place a fixture may be formed as the bone graft material is injected and bone fused inside.

However, when the stopper is in direct contact with the soft tissue gum, the gap between the end of the stopper and the alveolar bone changes as the gum is pressed by the force of pressing the drill. For this reason, since the insertion depth of the drill is not accurately limited, there is a serious problem in that the maxillary sinus membrane is torn due to the direct contact of the drill end to the maxillary sinus membrane.

In addition, when the gum is incised and the stopper is in contact with the outer surface of the exposed alveolar bone, the gap between the end of the stopper and the alveolar bone may be fixed, but the stopper slides along the rounded profile of the alveolar bone and the drilling position is deviated from the preset position. As a result, the placement position of the fixture is not desirable, and the accuracy of the overall implant placement is deteriorated, and there is a problem in that the maxillary sinus membrane is in contact with the end of the drill where the position has been moved and is torn. Moreover, the incision area of the gums is wide, so that the recovery period increases, the appearance of the gums is deformed after recovery, and the blood supply through the gums is not smooth, so there is a problem that the recovery period consumed for fusion and stabilization of the grafted bone increases.

In order to solve the above problem, some auxiliary devices called a surgical guide were used to guide the insertion depth and the drilling position of the drill. In such a surgical guide, at least one guide hole passes through corresponding to the placement position and direction of the fixture and substantially matches the interior of the oral cavity, thereby improving the accuracy of the drilling operation. In addition, as the stopper is supported on the outer surface of the surgical guide, the drill position can be stably guided.

However, due to the fluidity of the periodontal tissue or carelessness of the operator, drilling is performed beyond the limited insertion depth through the surgical guide, and the maxillary sinus membrane may be damaged. Accordingly, the inside of the maxillary sinus is exposed to pathogens, and a fatal secondary infection occurs in the maxillary sinus and respiratory tract, thereby deteriorating the accuracy of the procedure and the safety of the procedure.

Further, in the related art, threads are formed on the outer periphery of the shank and the inner periphery of the drill cutting edge so that the longitudinal position of the drill cutting edge is selectively adjusted, and a separate position fixing unit for fixing the drill cutting edge is further provided.

However, the conventional position fixing unit has a structure in which the shank is pressed through a hole formed on the side of the drill cutting edge, and it is difficult to use it in combination with the surgical guide, and thus, as the support power of the drill decreases, there is a problem that the treatment precision is rapidly deteriorated.

Moreover, when the pressurization of the conventional position fixing unit is released during the drilling operation, the drill cutting edge is separated in the longitudinal direction, so there is a problem that the safety of the procedure is rapidly deteriorated.

Korean Patent Registration No. 10-0619145

In order to solve the above problems, the present invention has as a solution to provide a train fine drill for implants with improved procedure precision.

In order to solve the above problems, the present invention provides a trapine drill for implants that forms a perforation for placing a fixture, comprising: a shank portion having a mounting portion coupled to a dental handpiece at one end thereof; Doedoe extending from the inner end of the shank portion, inserted into a cylindrical alignment hole formed by an initial drill in the alveolar bone corresponding to the fixture placement area, and guided by a cylinder having a diameter corresponding to the alignment hole, and integrally rotated when the shank portion is rotated A guide rod portion provided so as to be; And it is connected to the shank portion and rotated at the same time, the inner diameter is formed larger than the outer diameter of the guide rod portion, so that the bone fragment receiving space is formed so that the bone cutting material is guided between the outer periphery of the guide rod portion, and the circumferential direction at the end edge It includes a rotary cutting portion in which a plurality of cutting edges are formed according to the length of the guide rod portion is provided in excess of the length of the alignment hole, and the length of the rotary cutting portion is limited to a depth of perforation by the guide rod portion. It is formed to be less than a preset spacing range with respect to the end of the guide rod to prevent cutting, and the preset spacing range is formed to be less than the depth of the alignment hole, and inserted into the alignment hole at the end edge of the guide rod part. A round portion is formed to be rounded to prevent cutting of the alignment hole when the guide rod portion is rotated, and the edge of the round portion decreases in diameter at a preset radius reduction rate toward the end side, and the cutting edge is one surface portion corresponding to the rotation direction. And a stepped surface formed to be inclined to be inclined at the cutting slope and a stepped surface formed to be stepped perpendicularly to the cutting target surface from the end of the cutting slope on the other surface corresponding to the rotational direction, and the cutting slope and the stepped surface are the rotary cutting It provides a trapine drill for implants, characterized in that it is provided alternately in sequence along the circumferential direction at the end edge of the portion.

Here, at least one bone discharging hole is formed along the longitudinal direction so that the bone cutting material introduced into the bone piece receiving space is discharged at the side of the rotating cutting part, and the length in the longitudinal direction of the bone discharging hole is the placement position of the fixture. It is preferable that it is formed in excess of the thickness of the guide hole of the surgical guide to guide it.

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In addition, the central portion of the shank portion is integrally formed with a stopper step extending radially outward along the circumferential direction, and the rotary cutting portion is preferably connected to the inner end of the stopper step.

Through the above solution means, the present invention provides the following effects.

First, since the guide rod protruding from the inner end of the shank is inserted into the alignment hole previously formed in the alveolar bone by the initial drill to guide the perforation direction for the placement of the fixture during drilling, the procedure precision can be significantly improved.

Second, the rotating cutting part connected to the shank part is rotated and supported in the guide hole of the surgical guide, and the guide rod part is inserted into the alignment hole to guide the double alignment support structure. Since it is possible to form a precise perforation corresponding to the diameter, the treatment precision can be remarkably improved.

Third, since the end of the guide rod portion inserted into the alignment hole formed in the alveolar bone to guide the perforation direction is formed to be rounded, cutting of the inner circumferential surface of the alignment hole guiding the perforation direction when the guide rod portion is rotated is prevented in advance, thereby maintaining a solid support force. The safety of the procedure and the precision of the procedure can be remarkably improved.

Fourth, since the length of the rotational cutting part is formed to be less than a predetermined distance range with respect to the end of the guide rod inserted into the alignment hole, the puncturing depth is limited, so that cutting of the maxillary sinus membrane is prevented in advance, so that surgical safety can be significantly improved. have.

Fifth, unlike the prior art where the lengthwise position of the cutting edge is variable and fixed by the position fixing unit, the rotating cutting unit is integrally fixed and rotated on the shank, so that the support power is increased during cutting to improve the treatment precision, and Since the deviation of the blade in the longitudinal direction is prevented in advance, the safety of the procedure can be improved.

1 is a flow chart showing a conventional implant procedure.
Figure 2 is a perspective view showing a trepine drill for implants according to an embodiment of the present invention.
Figure 3 is a side view showing a trefine drill for implants according to an embodiment of the present invention.
Figure 4 is a cross-sectional view showing a trefine drill for implants according to an embodiment of the present invention.
Figure 5 is an example of the use of a trefine drill for implants according to an embodiment of the present invention.
Figure 6 is a usage example showing a first modified example of a trefine drill for implants according to an embodiment of the present invention.
Figure 7 is a use example showing a second modified example of a trefine drill for implants according to an embodiment of the present invention.

Hereinafter, a train fine drill for implants according to a preferred embodiment of the present invention will be described in detail with reference to the accompanying drawings.

2 is a perspective view showing a trepine drill for implants according to an embodiment of the present invention, Figure 3 is a side view showing a trepine drill for implants according to an embodiment of the present invention. And, Figure 4 is a cross-sectional view showing a trepine drill for implants according to an embodiment of the present invention, Figure 5 is an example of use of the trepine drill for implants according to an embodiment of the present invention.

As shown in Figures 1 to 5, the implant train drill 100 according to an embodiment of the present invention includes a shank portion 10, a guide rod portion 20, and a rotational cutting portion (30). .

Here, the implant trepine drill 100 is used in the procedure of multi-stage drilling to form a perforation for the placement of the fixture during the implant procedure, and perforation in the alveolar bone 4 at the position where the fixture is placed in the oral cavity. It is a device for cutting and removing the alveolar bone 4 so that it is formed.

And, in an embodiment of the present invention, a case where the trefine drill 100 for implant is used for the maxillary jaw in which the maxillary sinus membrane 5 is present is shown and described as an example, but it is equally applicable to the mandible. It is desirable to understand that.

This implant trepine drill 100 is a guide rod portion 20 to be described later is inserted into a cylindrical alignment hole 6 formed by an initial drill (not shown) in the alveolar bone 4 corresponding to the fixture placement area to be drilled. It is preferred that the direction is guided. At the same time, the implant train 100 is rotated by inserting the outer circumference of the rotary cutting unit 30 to be described later into the guide hole 2 of the surgical guide 1 that guides the placement position of the fixture. I can.

Here, the alignment hole 6 may be formed by the initial drill (not shown) separately provided in the initial stage of the multi-stage drilling step of forming a hole in which the fixture is to be placed. Here, the alignment hole 6 is preferably formed to a depth smaller than the depth from the surface of the gum 3 to the maxillary sinus membrane 5, and between the inner end of the alignment hole 6 and the maxillary sinus membrane 5 It is preferable that they are formed to be spaced apart at predetermined intervals.

For example, when the total depth of the alveolar bone 4 at the fixture placement position measured through CT, that is, the depth from the surface of the gum 3 to the maxillary sinus membrane 5 is 8.0 mm, the alignment hole 6 ) May be formed to a depth of 5.0mm from the surface of the gum (3).

On the other hand, it is preferable that the shank portion 10 has a mounting portion 11 coupled to a dental handpiece (not shown) at one end thereof. Here, the dental handpiece (not shown) is a hand drill device used to provide rotational force to the implant train 100.

In addition, the mounting portion 11 may be provided with a de-cut shape on one surface thereof, and an end portion of the other surface portion may be extended stepwise outward in the radial direction. Accordingly, when the mounting portion 11 is coupled to the dental handpiece (not shown), the rotational force of the handpiece (not shown) is transmitted to the shank portion 10 so that the shank portion 10 is integrated Can be rotated.

In addition, the shank portion 10 is connected to the guide rod portion 20 and the rotary cutting portion 30 to reduce the rotational force generated by the dental handpiece (not shown) to the guide rod portion 20 and the It can be transmitted to the rotary cutting unit 30.

At this time, the shank portion 10 may be formed irrespective of the diameter of the guide rod portion 20 and the rotation cutting portion 30, but is provided with a diameter smaller than the diameter of the rotary cutting portion 30 desirable. In addition, the shank portion 10 is preferably provided with a diameter larger than the diameter of the guide rod portion 20.

In addition, the shank portion 10 may be provided in a cylindrical shape, and may be provided with a metal material such as stainless steel. Accordingly, the shank portion 10 may be rigidly connected to and supported by the guide rod portion 20 and the rotating cutting portion 30 when rotating at high speed.

Through this, damage such as bending or twisting that may occur when the shank portion 10 is rotated can be prevented, thereby improving durability, as well as preventing a reduction in drilling precision due to vibration caused by rotational damage. have.

Meanwhile, it is preferable that a stopper step 12 extending radially outwardly along the circumferential direction is integrally formed at the central portion in the longitudinal direction of the shank portion 10. Here, the stopper step 12 is preferably formed integrally with the outer circumference of the longitudinal central portion adjacent to the other end of the shank portion 10 and extending radially outward along the circumferential direction. At this time, the stopper step 12 may be manufactured by a method such as SUS welding.

In detail, it is preferable that the stopper step 12 is formed with a flat seating portion perpendicular to the length direction so as to support one end of the rotary cutting portion 30. In addition, an inclined portion whose diameter decreases from the seating portion toward one side of the shank portion 10 may be formed.

Here, it is preferable that the seating portion extends stepped outward in the radial direction from the body adjacent to the other end of the central portion in the longitudinal direction of the shank portion 10 in the radial direction. In this case, it is preferable that the diameter of the stopper step 12 seating portion is greater than or equal to the diameter of the rotary cutting portion 30.

Accordingly, since the one end of the rotary cutting unit 30 is supported by the stopper step 12 during the drilling operation for forming a perforation, the deviation in the longitudinal direction of the rotary cutting unit 30 is prevented in advance, so that the operation precision and operation are performed. Safety can be significantly improved.

In addition, a cylindrical coupling portion 13 may be formed at the other end of the shank portion 10 so that the rotary cutting portion 30 is fixed. Here, the outer diameter of the coupling part 13 may be formed to correspond to the inner diameter of the rotary cutting part 30.

On the other hand, the guide rod part 20 is integrally extended from the inner end of the coupling part 13 of the shank part 10 along the longitudinal direction to be provided in a cylindrical shape, and is integrated when the shank part 10 is rotated. Can be rotated to Here, the guide rod part 20 may be made of a metal material such as stainless steel, and may be made of titanium having excellent biocompatibility in some cases.

In addition, the guide rod portion 20 is most preferably formed integrally with the shank portion 10, but in some cases, the guide rod portion 20 is provided separately from the shank portion 10 and the shank portion It may be detachably coupled to the inner end of the coupling portion 13 of (10). Accordingly, since the guide rod part 20 is separated from the shank part 10 and is easy to clean, the convenience of use may be improved.

In addition, the guide rod part 20 is preferably provided with a diameter corresponding to the alignment hole 6 so that the end of the guide rod part 20 is inserted into the alignment hole 6 to guide the perforation direction. . For example, when the diameter w1 of the alignment hole 6 is formed to be 1.5mm or 2.0mm by the initial drill (not shown), the diameter w2 of the guide rod part 20 is the alignment hole ( It may be provided with 1.5mm or 2.0mm corresponding to the diameter of 6).

Accordingly, the guide rod part 20 protruding from the inner end of the shank part 10 is inserted into the alignment hole 6 formed in advance by the initial drill (not shown) to rotate the rotation cutting part The perforation direction of 30 can be guided.

Through this, unlike the prior art in which the alignment hole 6 is not formed and the alveolar bone 4 is cut by a drill, the guide rod part 20 is inserted into the alignment hole 6 to be drilled for fixture placement. Since the direction is guided, the treatment precision can be remarkably improved.

Further, it is preferable that the length of the guide rod part 20 exceeds the length of the alignment hole 6. In addition, at the end of the guide rod part 20, the round part 21 is rounded to prevent cutting of the alignment hole 6 when the guide rod part 20 inserted into the alignment hole 6 rotates. It is preferably formed.

In detail, as the guide rod part 20 rotates when the guide rod part 20 is rotated, the end edge side of the guide rod part 20 to which a substantial external force is applied to the alignment hole 6 may be formed to be rounded. That is, the diameter of the rim of the round part 21 may be reduced at a preset radius reduction rate toward the end.

Accordingly, since the end of the guide rod part 20 is formed to be rounded, cutting of the inner circumferential surface of the alignment hole 6 guiding the perforation direction when the guide rod part 20 is rotated can be prevented in advance. Through this, since a solid support force of the alignment hole 6 guiding the perforation direction is maintained, the safety of the procedure and the precision of the procedure can be remarkably improved.

On the other hand, the rotation cutting part 30 is preferably provided connected to the shank part 10 so as to rotate simultaneously with the shank part 10. In detail, the rotary cutting part 30 may be made of a metal material such as stainless steel having a hollow cylindrical shape, and one end may be connected to an inner end of the seating part of the stopper step 12. In this case, a recessed groove 34 that is recessed radially inwardly along the circumferential direction may be formed at the edge of the one end side of the rotating cutting part 30.

In addition, the rotation cutting part 30 is most preferably integrally fixed to the shank part 10 so that it rotates simultaneously when the shank part 10 rotates, but may be provided separately and fixed to each other in some cases.

Therefore, unlike the conventional case where the lengthwise position of the drill cutting edge is variable and fixed by the position fixing unit, the rotational cutting unit 30 is integrally fixed to and rotated by the shank unit 10, so that the holding force increases during cutting. Therefore, the accuracy of the procedure can be remarkably improved.

In addition, since the rotational cutting part 30 is integrally fixed to the shank part 10 and rotated, the deviation of the cutting edge 31 in the longitudinal direction is prevented in advance, so that the safety of the procedure can be significantly improved.

In addition, it is preferable that the rotary cutting unit 30 is provided with a plurality of different lengths so as to be sequentially used for each procedure of multi-stage drilling, and is integrally fixed to the shank unit 10. That is, it is preferable that the rotary cutting unit 30 provided with a plurality of different lengths is provided integrally with the shank unit 10.

Accordingly, since a plurality of trapine drills for implants provided with the rotating cutting unit 30 of the length required in each procedure of multi-stage drilling are provided, a rapid procedure can be performed, thereby improving work efficiency and procedure safety. .

In addition, the length of the rotary cutting part 30 is preset based on the end of the guide rod 20 so that the depth of the perforation is limited by the guide rod part 20 to prevent cutting of the maxillary sinus membrane 5. It is preferably formed to be less than the interval range (h2).

Here, the predetermined spacing range (h2) is preferably formed to be less than the depth (h1) of the alignment hole (6). At this time, the alignment hole (6) is formed to a depth (h1) smaller than the length from the surface of the gum (3) to the maxillary sinus membrane (5), the inner end of the alignment hole (6) and the maxillary sinus membrane (5) It is desirable to understand that it is formed by being spaced apart.

For example, when the depth h1 of the alignment hole 6 is formed to be 5.0 mm, and the length of the guide rod part 20 is provided as 17.0 mm, the length of the rotary cutting unit 30 is 14.0 mm. It can be provided. That is, the length of the rotation cutting part 30 may be formed as small as 3.0 mm from the end of the guide rod 20. Of course, the length of the rotation cutting unit 30 may be provided longer than the length of the guide rod unit 20, a detailed description will be described later.

Accordingly, when the guide rod part 20 is inserted into the alignment hole 6 and rotated, the alveolar bone 4 is rotated by a difference between the predetermined distance range h2 from the depth h1 of the alignment hole 6 This can be cut to form a perforation. At this time, as in an embodiment of the present invention, when the length of the rotary cutting unit 30 is smaller than the length of the guide rod unit 20, the alveolar bone 4 is cut to a depth smaller than the target drilling depth to be cut. It is desirable to understand it.

Through this, when the length of the rotary cutting part 30 is provided smaller than the length of the guide rod part 20 inserted into the alignment hole 6, the depth of the perforation is limited, so that the maxillary sinus membrane 5 is cut. Since it is prevented in advance, the safety of the procedure can be remarkably improved. That is, since the rotational cutting unit 30 is rotated while the guide rod part 20 of the present invention is inserted into the alignment hole 6, the drilling direction is guided and the drilling depth for fixture placement is limited. The configuration is markedly different from the prior art.

Therefore, since the length of the rotary cutting part 30 is formed to be less than a predetermined interval range h2 with respect to the end of the guide rod 20, the depth of perforation is limited, so that the cutting of the maxillary sinus membrane 5 is prevented. Therefore, the safety of the procedure can be remarkably improved.

In addition, the inner diameter of the rotating cutting part 30 is formed larger than the outer diameter of the guide rod part 20, and the outer diameter of the rotating cutting part 30 is preferably formed to correspond to the inner diameter of the guide hole 2 Do.

Here, the rotating cutting part 30 is provided with an outer diameter corresponding to the inner circumference of the guide hole 2 so as to be inserted into the guide hole 2 of the surgical guide 1 to guide the fixture placement position and supported for rotation. This is desirable.

In detail, in the implant procedure, an auxiliary device called a surgical guide 1 is used because it is difficult to grasp the exact position and direction to be performed when forming the perforation in which the fixture is placed. Here, the surgical guide 1 is formed as a profile inside the oral cavity. In addition, the surgical guide 1 is fixed by wrapping and fixing periodontal tissues such as teeth and gums of a dental jaw or edentulous patient, and a plurality of guide holes 2 are formed for each position where an implant is required.

In addition, the guide hole 2 is provided as a cylindrical hole, it is preferably provided to support the rotation of the drill device inserted into the inside and guide up and down. At this time, the rotating cutting part 30 is inserted into the inner circumference of the guide hole 2 and is guided by being slid in the longitudinal direction, but it is supported by rotation inside the guide hole 2, so that the user corresponds to the fixture placement position. The exact part of the gum can be easily removed.

In addition, the guide hole 2 may be provided with various diameters according to the type of natural teeth to be replaced with an implant. For example, the fixture that becomes the root of an artificial tooth is provided with a diameter of 3.5mm, 4.0mm, 4.5mm, 5.0mm, or the like. In addition, the outer diameter of the guide hole 2 and the rotary cutting part 30 may be formed to be about 3.0mm, 3.5mm, 4.0mm, 4.5mm, etc. corresponding to the chikyeong of the fixture. That is, the guide hole 2 may be selected and provided in a size corresponding to the diameter of the fixture, and the rotating cutting part 30 may be provided corresponding to the diameter of the guide hole 2. In this case, the rotation cutting part 30 is preferably provided with an outer diameter that is slightly smaller than the inner circumference of the guide hole 2 so that it can be inserted and rotated in the guide hole 2.

Accordingly, the rotation cutting part 30 is provided with a double alignment support structure in which the guide rod part 20 is inserted into the alignment hole 6 and guided at the same time while the rotation cutting part 30 is supported by the guide hole 2. Therefore, since it is possible to form a precise perforation corresponding to the diameter of the fixture in the alveolar bone 4 on the side of the fixture placement area, the procedure precision can be remarkably improved.

Moreover, referring to FIG. 5, an auxiliary stopper 40 for adjusting the insertion depth of the rotary cutting unit 30 may be further provided. These auxiliary stoppers 40 may be standardized in unit length and provided in plural.

Here, the auxiliary stopper 40 may be selectively provided with one end contacting the seating portion of the stopper step 12 and the other end contacting one end of the guide hole 22. In addition, the auxiliary stopper 40 may be disposed to surround an outer surface of one side of the rotary cutting unit 30.

Through this, abrasion or tearing of the maxillary sinus membrane 5 due to the contact of the end of the cutting edge 30 with the maxillary sinus membrane 5 while the perforation is formed in the alveolar bone 4 at the correct position can be prevented in advance. I can.

In addition, the inner diameter of the rotating cutting part 30 is formed larger than the outer diameter of the guide rod part 20, so that the rotating cutting part 30 is spaced apart and enclosed by the guide rod part 20 by a predetermined distance. It is preferably provided with.

In addition, between the inner circumference of the rotation cutting unit 30 and the outer circumference of the guide rod unit 20, a bone piece receiving space 32 through which a bone cutting material is guided is preferably formed. In addition, at least one bone discharge hole (33a, 33b) is formed in the side portion of the rotating cutting part (30) in communication with the outside so that the bone cutting material introduced into the bone piece receiving space (32) is discharged. This is desirable.

At this time, it is preferable to understand that the bone cutting material generated during the drilling process may be introduced into the bone piece receiving space 32, and the bone cutting material means the alveolar bone removed from the implant placement position.

In addition, the bone cutting material may be discharged to the outside through the bone discharge holes 33a and 33b communicated with the bone piece receiving space 32. At this time, the length of the bone discharge holes (33a, 33b) in the longitudinal direction is preferably formed to exceed the thickness of the guide hole (2).

For this reason, the rotational cutting part 30 is inserted into the inner circumference of the guide hole 2 to remove the alveolar bone 4 in a rotationally supported state, and when inserted, one of the longitudinal ends of the bone discharging holes 33a, 33b At least one side may be exposed to the outside of the guide hole 2.

Accordingly, the bone cutting material introduced into the bone piece receiving space 32 is not accumulated in the inside of the bone piece receiving space 32 and can be smoothly discharged outward through the bone discharge holes 33a and 33b. . Moreover, the accumulation of the bone cutting material and the flow accordingly can prevent the bone cutting material from being entangled with the gums or alveolar bone that are not to be removed. Therefore, the alveolar bone at the implant placement position can be smoothly and accurately removed, and additional work such as removing and scraping the entangled bone cut through a separate tool or procedure is not required, so work efficiency can be significantly improved.

In addition, it is preferable that a plurality of cutting edges 31 are formed along the circumferential direction so as to cut the alveolar bone 4 at the fixture placement position at the end edge of the rotary cutting part 30. In detail, an end of the rotation cutting part 30 is opened to communicate with the bone piece receiving space 32, and the cutting edge 31 may be formed along the edge of the rotation cutting part 30. In this case, the cutting blade 31 is most preferably provided integrally with the rotating cutting unit 30, and may be individually provided and combined in some cases.

Here, it is preferable that the cutting edge 31 includes a plurality of cutting inclined surfaces which are formed on one surface corresponding to the rotational direction, but are increased in length along the circumferential direction and are formed to be inclined. In addition, it is preferable that the cutting edge 31 includes a plurality of stepped surfaces formed on the other surface corresponding to the opposite rotational direction and formed to be stepped perpendicularly to the cutting target surface from the end of the cutting slope. In this case, the cutting target surface is preferably understood as a cutting surface of the alveolar bone 4 that is cut corresponding to the fixture placement area.

In addition, it is preferable that each of the cutting inclined surfaces and each of the stepped surfaces are sequentially alternately provided along the circumferential direction on the edge of the end of the rotary cutting unit 30. Accordingly, the cutting edge 31 is in direct contact with the alveolar bone 4 between the fixture placement position to cut the alveolar bone 4 when rotating. At this time, the alveolar bone 4 contacted by the cutting edge 31 may be cut and introduced into the bone piece receiving space 32.

In addition, the cutting edge 31 is inserted into the alveolar bone 4 and cuts the alveolar bone 4 to separate it from the entire tissue. At this time, the rotating cutting part 30 pushes the alveolar bone 4 outside the cutting edge 31 to the outside as the cutting edge 31 is inserted toward the alveolar bone 4, and the outer surface is outside the cutting edge 31 It is in close contact with the alveolar bone (4).

Accordingly, the alveolar bone 4 separated from the entire tissue through the cutting edge 31 and the bone cutting material decomposed by friction due to the rotation of the cutting edge 31 to the outside of the rotating cutting part 30 It can flow smoothly toward the bone piece receiving space 32 without leakage.

On the other hand, Figure 6 is a usage example showing a first modified example of a trefine drill for implants according to an embodiment of the present invention. Since the trapine drill 100A for implant according to the first modified example of the present invention has the same basic configuration as that of the above-described embodiment except for the length of the rotary cutting unit 30A, a detailed description of the same configuration will be omitted.

As shown in Figure 6, the length of the rotation cutting part (30A) is the guide so that a hole for the placement of the fixture is formed as the alveolar bone 4 is cut by a depth corresponding to the alignment hole 6 It is preferable that it is formed corresponding to the length of the rod part 20.

For example, when the depth h1 of the alignment hole 6 is formed to be 5.0 mm, and the length of the guide rod part 20 is provided as 17.0 mm, the length of the rotary cutting unit 30A is 17.0 mm. It can be provided. Accordingly, when the guide rod part 20 is inserted into the alignment hole 6 and rotated, the alveolar bone 4 is cut by the depth h1 of the alignment hole 6 to form a perforation.

Here, it is understood that the implant trefine drill 100A according to the first modification of the present invention is inserted into the perforation of the fixture placement region first cut by the implant trefine drill 100 of the above-described embodiment. desirable. That is, it is preferable to understand that the alveolar bone 4 in the fixture placement region is cut step by step by a predetermined depth by a plurality of train trains for implants having different lengths of rotational cutting portions.

On the other hand, Figure 7 is a use example showing a second modified example of the trefine drill for implants according to an embodiment of the present invention. Since the trapine drill 100B for implant according to the second modified example of the present invention has the same basic configuration as that of the above-described embodiment except for the length of the rotary cutting unit 30B, a detailed description of the same configuration will be omitted.

As shown in FIG. 7, it is preferable that the length of the rotation cutting part 30B is formed to exceed a preset length h3 from the length of the guide rod part 20. In this case, the preset length is preferably formed to be smaller than the depth between the maxillary sinus membrane 5 at the inner end of the alignment hole 6 so as to prevent cutting of the maxillary sinus membrane 5.

For example, when the depth from the surface of the gum 3 to the maxillary sinus membrane 5, that is, the total depth of the alveolar bone 4 is 8.0 mm, the depth h1 of the alignment hole 6 is formed to be 5.0 mm Can be. Accordingly, the depth between the maxillary sinus membrane 5 at the inner end of the alignment hole 6 may be set to 3.0 mm. In addition, when the length of the guide rod part 20 is 17.0 mm, the length of the rotary cutting part 30B may be formed to exceed 17.0 mm and less than 20.0 mm. That is, the length of the rotation cutting part 30B is a sum of a length less than the length of the guide rod part 20 and the length corresponding to the depth between the maxillary sinus membrane 5 at the inner end of the alignment hole 6 It can be formed in length.

Here, it is understood that the implant trefine drill 100B according to the second modification of the present invention is inserted into the perforation of the fixture placement area secondly cut by the implant trefine drill 100A of the first modification described above. This is desirable. That is, it is preferable to understand that the alveolar bone 4 in the fixture placement region is cut step by step by a predetermined depth by a plurality of train trains for implants having different lengths of rotational cutting portions.

Accordingly, the length of the rotation cutting part 30B may be provided longer than the length of the guide rod part 20. In addition, the difference between the end of the guide rod part 20 facing the alveolar bone 4 and the end of the rotating cutting part 30B is the depth between the maxillary sinus membrane 5 at the inner end of the alignment hole 6 It can be formed smaller. Through this, when cutting the alveolar bone 4 in the fixture placement area, the maxillary sinus membrane 5 can be treated precisely as long as the cutting is prevented, so that the treatment precision can be remarkably improved.

Therefore, since the length of the rotary cutting part 30B is formed within a predetermined distance range with respect to the end of the guide rod 20, the drilling depth is limited to prevent cutting of the maxillary sinus membrane 5 in advance. Safety can be significantly improved.

At this time, the terms such as "include", "comprise" or "have" described above mean that the corresponding component may be present unless otherwise stated, excluding other components. It should not be construed as being able to include other components. All terms, including technical or scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art, unless otherwise defined, to which the present invention belongs. Terms generally used, such as terms defined in the dictionary, should be interpreted as being consistent with the meaning of the context of the related technology, and are not interpreted as ideal or excessively formal meanings unless explicitly defined in the present invention.

As described above, the present invention is not limited to each of the above-described embodiments, and it is possible to be modified and implemented by those of ordinary skill in the art without departing from the scope claimed in the claims of the present invention. And, these modifications are within the scope of the present invention.

100,100A,100B: Implant Trefine Drill 1: Surgical Guide
2: guide hole 3: gum
4: alveolar bone 5: maxillary sinus membrane
6: alignment hole 10: shank portion
11: mounting part 12: stopper step
13: extension part 20: guide rod part
21: Round part 30,30A,30B: Rotary cutting part
31: cutting edge 32: space for bone pieces
33a, 33b: bone extraction hole 34: recessed groove
40: auxiliary stopper

Claims (5)

In the trapine drill for implants to form a perforation for fixture placement,
A shank portion having a mounting portion coupled to the dental handpiece formed at one end thereof;
Doedoe extending from the inner end of the shank portion, inserted into a cylindrical alignment hole formed by an initial drill in the alveolar bone corresponding to the fixture placement area, and guided by a cylinder having a diameter corresponding to the alignment hole, and integrally rotated when the shank portion is rotated A guide rod portion provided so as to be; And
It is connected to the shank portion and rotated at the same time, the inner diameter is formed larger than the outer diameter of the guide rod portion, so that the bone fragment receiving space is formed so that the bone cutting material is guided between the outer periphery of the guide rod portion, Including a rotary cutting unit in which a plurality of cutting edges are formed,
The length of the guide rod part is provided in excess of the length of the alignment hole, and the length of the rotary cutting part is preset based on the end of the guide rod so that the depth of the perforation is limited by the guide rod part to prevent cutting of the maxillary sinus membrane. It is formed to be less than the spacing range, the predetermined spacing range is formed to be less than the depth of the alignment hole,
At the edge of the guide rod portion, a round portion is formed to be rounded so as to prevent cutting of the alignment hole when the guide rod portion inserted into the alignment hole is rotated, and the diameter of the round portion decreases toward the end at a preset radius reduction rate. Become,
The cutting edge includes a cutting inclined surface formed to be inclined on one surface portion corresponding to the rotation direction, and a stepped surface formed to be stepped vertically from the end of the cutting slope to the cutting target surface on the other surface corresponding to the rotational direction, Trapine drill for implants, characterized in that the cutting inclined surface and the stepped surface are sequentially alternately provided along the circumferential direction at the end edge of the rotary cutting unit. delete delete The method of claim 1,
At least one bone discharging hole is formed in the side portion of the rotating cutting part along the longitudinal direction so that the bone cutting material introduced into the bone piece receiving space is discharged,
The lengthwise length of the bone discharging hole exceeds the thickness of the guide hole of the surgical guide for guiding the placement position of the fixture. The method of claim 1,
A stopper step extending radially outward along a circumferential direction is integrally formed at the central portion of the shank portion, and the rotation cutting portion is connected to the inner end of the stopper step.

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