WO2014185264A1 - Implant driver and implant - Google Patents

Abstract

An implant driver (80) is provided with a tapered alignment shaft part (83), the outside diameter of which decreases toward a distal end thereof, and a rotation-transmitting shaft part (84) formed so as to be non-circular. The alignment shaft part (83) is formed in a center hole of a fixture (10), and is fitted in a tapered fitting hole part (14), the inside diameter of which decreases in a depth direction of the fitting hole part (14). The rotation-transmitting shaft part (84) is fitted in a rotation-preventing hole part (17) formed in the center hole of the fixture (10) in order to prevent rotation of an abutment connected to the fixture (10).

Description

Implant driver and implant

The present invention relates to an implant driver and an implant. For example, the present invention relates to a dental implant and an implant driver that are embedded in a jaw bone when a root of a permanent tooth is lost.
This application claims priority based on Japanese Patent Application No. 2013-105377 filed in Japan on May 17, 2013, the contents of which are incorporated herein by reference.

Implants embedded in the body (particularly dental implants) have attracted attention. A dental implant inserts and fixes a fixture in a hole provided in an alveolar bone when the root of a permanent tooth is lost due to decay or damage.
This dental implant is generally composed of a fixture that is fixed to the alveolar bone and an abutment that is screwed to the fixture and can be fitted with an artificial crown.

When the fixture is embedded in the alveolar bone, a device called an implant mount driver or the like (implant driver) is used.
The implant driver has a rotation transmission shaft portion formed in a non-circular shape such as a polygon at the tip thereof. The rotation of the implant driver can be transmitted to the fixture by fitting the rotation transmission shaft portion into a rotation transmission hole formed in the center hole of the fixture.

JP 2003-047621 A JP 2004-202049 A

In the conventional implant driver, the rotation transmission shaft portion only fits into the rotation transmission hole portion of the fixture. For this reason, when it embeds, rotating a fixture with respect to an alveolar bone etc., the attitude | position of a fixture tends to become unstable. If the center axis (rotation axis) of the implant driver and the fixture do not coincide with each other, the fixture will be embedded in the bone while wobbling. For this reason, there exists a problem of putting an excessive burden on a human body.

An object of the present invention is to provide an implant driver and an implant that can stabilize the posture of a fixture when the fixture is embedded in a bone.

A first embodiment of an implant driver according to the present invention is an implant driver that is inserted into a central hole formed in the fixture and transmits a rotational force from a drive source when the fixture is embedded in a bone. A tapered alignment shaft portion whose outer diameter decreases toward the tip, and a non-circular rotation transmission shaft portion, the alignment shaft portion having an inner diameter out of the center hole Is fitted in a tapered fitting hole portion that is reduced in the depth direction, and the rotation transmission shaft portion prevents rotation of an abutment connected to the fixture among the center hole. Fit into the part.

A second embodiment of an implant driver according to the present invention includes, in the first embodiment, a variable diameter portion capable of changing an outer diameter, and the variable diameter portion is configured to drop the abutment out of the center hole. Engage with retaining hole to prevent.

In a third embodiment of the implant driver according to the present invention, in the first or second embodiment, the alignment shaft portion and the rotation transmission shaft portion are formed at different positions in the axial direction.

In the fourth embodiment of the implant driver according to the present invention, in the first or second embodiment, the alignment shaft portion and the rotation transmission shaft portion are formed at the same position in the axial direction.

The first embodiment of the implant according to the present invention is a fixture in which a tapered fitting hole portion whose inner diameter decreases in the depth direction and a non-circular anti-rotation hole portion are formed in a part of the center hole. And an abutment unit formed with a tapered fitting shaft portion that fits into the fitting hole portion and a rotation prevention shaft portion that fits into the rotation prevention hole portion, and the fixture is When implanting in a bone, an implant driver that transmits a rotational force from a driving source is inserted into the center hole, and a centering shaft portion having the same shape as the fitting shaft portion is fitted into the fitting hole portion. The rotation transmission shaft portion having the same shape as the rotation prevention shaft portion is fitted into the rotation prevention hole portion.

A second embodiment of the implant according to the present invention is the abutment according to the first embodiment, wherein the abutment unit includes the fitting shaft portion, the rotation prevention shaft portion, and a through hole formed along the axial direction. And a shaft main body portion inserted through the through hole, a retaining shaft portion having a diameter larger than that of the shaft main body portion, and a rotation restricting hole portion formed in the center hole to rotate around its own axis. A clamper pin having a follow-up restricting shaft portion that is restricted, a lock bush that engages with the through hole and the shaft main body portion, and a retaining shaft portion and a retaining hole portion, And a clamper for restricting movement with respect to the fixture.

According to a third embodiment of the implant according to the present invention, in the first or second embodiment, the pressure-resistant portion including the fitting hole portion and the fitting shaft portion, the rotation prevention hole portion, and the rotation prevention shaft portion. The rotation preventing portion is formed at a different position in the axial direction.

According to a fourth embodiment of the implant according to the present invention, in the first or second embodiment, the pressure-resistant portion including the fitting hole portion and the fitting shaft portion, the rotation prevention hole portion, and the rotation prevention shaft portion. The anti-rotation portion is formed at the same position in the axial direction.

The present invention can stabilize the posture of the fixture when it is embedded in the bone while rotating the fixture. Therefore, an excessive burden on the human body can be avoided.

It is a figure which shows the usage example in the dental field | area of the implant which concerns on 1st embodiment of this invention. It is a disassembled perspective view of the implant which concerns on 1st embodiment of this invention. It is a longitudinal cross-sectional view of the implant which concerns on 1st embodiment of this invention. 2A and 2B are diagrams showing a fixture, where FIG. 1A is a top view and FIG. 1B is a longitudinal sectional view (IVb-IVb cross section). It is a figure which shows an abutment, Comprising: It is (a) side view, (b) bottom view, (c) longitudinal cross-sectional view (Vc-Vc cross section). It is a figure which shows a clamper pin, Comprising: It is (a) side view and (b) bottom view. It is a figure which shows a clamper, Comprising: It is (a) bottom view, (b) longitudinal cross-sectional view (VIIb-VIIb cross section). It is a figure which shows a lock nut, Comprising: (a) Bottom view, (b) Longitudinal section (VIIIb-VIIIb section). 1A and 1B are views showing an implant mount driver according to a first embodiment of the present invention, where FIG. 1A is a side view, FIG. 1B is a bottom view, and FIG. 2C is a partial sectional view (IXc-IXc cross section). It is a figure which shows the use condition of the implant mount driver which concerns on 1st embodiment of this invention. It is a longitudinal cross-sectional view of the implant which concerns on 2nd embodiment of this invention. 2A and 2B are diagrams showing a fixture, wherein FIG. 1A is a top view, and FIG. 2B is a side sectional view (XIIb-XIIb cross section). It is a figure which shows an abutment, Comprising: It is (a) side view, (b) longitudinal cross-sectional view (XIIIb-XIIIb cross section), (c) bottom view. It is a figure which shows a clamper pin, Comprising: (a) Side view, (b) is a bottom view. It is a figure which shows a lock nut, Comprising: (a) Top view, (b) is a longitudinal cross-sectional view (XVb-XVb cross section). It is a figure which shows the implant mount driver which concerns on 2nd embodiment of this invention, Comprising: (a) Side view, (b) Bottom view, (c) Partial sectional view (XVIc-XVIc cross section). It is a figure which shows the use condition of the implant mount driver which concerns on 2nd embodiment of this invention.

Embodiments of the present invention will be described with reference to the drawings. The various dimensions shown in the following description are examples.

[First embodiment]
FIG. 1 is a diagram showing an example of use in the dental field of an implant 5 according to a first embodiment of the present invention.
The implant 5 includes a fixture 10 that is fixed to the alveolar bone 2, and an abutment unit 8 that can be attached to and detached from the fixture 10. An artificial crown 6 is attached to the abutment unit 8.

The center axis (longitudinal direction) of the implant 5 is taken as the Z axis (Z direction, depth direction, axial direction, vertical). Of the Z-axis, the fixture 10 side is the + Z side (+ Z direction), and the abutment 20 side is the −Z side (−Z direction). The bottom view is when viewed from the + Z direction, and the top view is when viewed from the -Z direction. The end in the + Z direction is called the base end (first end), and the end in the −Z direction is called the front end (second end).

A male screw 12 is formed on the outer peripheral surface of the fixture 10. The fixture 10 is fixed to the alveolar bone 2 by screwing the male screw 12 into a hole formed in the alveolar bone (bone) 2.
An artificial crown 6 is attached to the outer peripheral surface of the abutment unit 8 using an adhesive or the like.
A contact portion S between the fixture 10 and the abutment unit 8 is covered with the gum 4 or the alveolar bone 2. The contact surfaces of the fixture 10 and the abutment unit 8 are finished with high accuracy. The contact surfaces of the fixture 10 and the abutment unit 8 are in close contact with each other to prevent foreign matter from entering.

FIG. 2 is an exploded perspective view of the implant 5 according to the first embodiment of the present invention.
FIG. 3 is a longitudinal sectional view of the implant 5 according to the first embodiment of the present invention.

The implant 5 includes a fixture 10 and an abutment unit 8.
The abutment unit 8 is an assembly of the abutment 20, the clamper pin 30, the clamper 40, and the lock nut 50.
The abutment unit 8 includes a shaft-shaped abutment 20, a shaft-shaped clamper pin 30, a ring-shaped clamper 40, and a lock nut 50.
An artificial crown 6 is attached to the abutment 20.
The clamper pin 30 is inserted into the through hole 24 of the abutment 20 and engages with the fixture 10.
The clamper 40 is fitted to the clamper pin 30.
The lock nut 50 is screwed (locked) to the abutment 20 and the clamper pin 30.

4A and 4B are diagrams showing the fixture 10, wherein FIG. 4A is a top view, and FIG.
The fixture 10 is an axial member formed of a ceramic material such as zirconia. The fixture 10 is formed in a cylindrical shape, and a male screw 12 is formed on the outer peripheral surface thereof.
A center hole 13 is opened at the center of the end face on the −Z side of the fixture 10. In the center hole 13, a tapered hole portion 14, a reverse tapered hole portion 15, and an engagement hole portion 16 are continuously formed toward the + Z side.
The inner diameter of the tapered hole portion (fitting hole portion) 14 is gradually reduced (reduced) from the −Z side end surface toward the + Z side. The reverse tapered hole portion 15 gradually increases (increases in diameter) toward the + Z side. The engaging hole 16 is formed with two parallel surfaces (rotating restricting holes) 16A composed of two parallel inner surfaces facing each other.

The taper angle of the taper hole 14 is, for example, 8 °. The average diameter of the tapered hole portion 14 is, for example, 2 mm. The length (depth) of the tapered hole portion 14 is formed to be 1/3 or more (for example, 4 to 5 mm) of the entire length (for example, 10 mm) of the fixture 10.
A plurality of protrusions 17 are formed along the Z direction on the inner peripheral side surface of the tapered hole portion 14. The plurality of protrusions (rotation prevention hole portions) 17 are arranged at equal intervals (equal angles) in the circumferential direction of the center hole 13. The number of protrusions 17 is five. The number of protrusions 17 can be changed as appropriate.
The shape of the cross section perpendicular to the Z-axis of the protrusion 17 is a shape in which the top side (outer peripheral side) swells in a semicircular shape.

The minimum inner diameter of the reverse tapered hole 15 is smaller than the minimum inner diameter of the tapered hole 14. Therefore, a protruding portion (a retaining hole) 15A that protrudes to the inner peripheral side of the center hole 13 is formed at a connection portion between the tapered hole portion 14 and the reverse tapered hole portion 15. The taper angle of the reverse taper hole 15 is, for example, 10 °. The length (depth) of the reverse taper hole 15 is, for example, 2.5 mm.

The engaging hole portion 16 is composed of two opposing arc-shaped inner peripheral side surfaces and two parallel and opposing inner side surfaces. The two inner surfaces are parallel two surfaces 16A. The length (depth) of the engagement hole 16 is, for example, 1.2 mm. The width (two surface widths) of the two parallel two surfaces 16A is, for example, 1.1 mm.

5A and 5B are diagrams showing the abutment 20, which are (a) a side view, (b) a bottom view, and (c) a longitudinal sectional view (Vc-Vc cross section).
The abutment 20 includes a main body portion 21 and a tapered shaft portion 22.
An artificial dental crown 6 is attached to the main body 21. The taper shaft portion (fitting shaft portion) 22 extends from the base end side (+ Z side) of the main body portion 21 and is inserted into the center hole 13 of the fixture 10.
The abutment 20 is integrally formed of a white ceramic material having excellent aesthetics. Zirconia is adopted as the ceramic material.

The taper angle of the taper shaft portion 22 is, for example, 8 °. The angle is the same as that of the tapered hole portion 14 of the center hole 13 of the fixture 10.
The average inner diameter of the tapered shaft portion 22 is, for example, 2 mm. The length of the tapered shaft portion 22 is the same as or longer than that of the tapered hole portion 14. The length of the taper shaft portion 22 is, for example, 6 mm.
A plurality of groove portions 23 are formed on the outer peripheral side surface of the tapered shaft portion 22 along the Z direction. The plurality of groove portions (anti-rotation shaft portions) 23 are arranged at equal intervals (equal angles) in the circumferential direction of the taper shaft portion 22. The number of the groove parts 23 is five. The number of the groove parts 23 can be changed as appropriate. The number of the groove portions 23 is the same as the number of the protrusions 17 of the tapered hole portion 14.
The cross-sectional shape orthogonal to the Z-axis of the groove 23 is a shape in which the bottom side (inner peripheral side) is recessed in a semicircular arc shape. That is, the groove portion 23 has a shape opposite to that of the protrusion 17 formed on the inner peripheral side surface of the tapered hole portion 14.

When the abutment 20 is inserted into the center hole 13 of the fixture 10, the tapered shaft portion 22 of the abutment 20 is fitted into the tapered hole portion 14 of the center hole 13 of the fixture 10. At this time, the five groove portions 23 formed in the tapered shaft portion 22 are inserted into the five protrusions 17 formed in the tapered hole portion 14.

A through hole 24 penetrating in the Z direction is formed at the center of the abutment 20. The part corresponding to the main body portion 21 in the through hole 24 is formed with an inner diameter of about 2.5 mm. An internal thread 25 of M2.5 is provided in a part of the through hole 24. The screw size of the inner screw 25 can be appropriately changed according to the inner diameter of the through hole 24 and the like.
A portion of the through hole 24 corresponding to the tapered shaft portion 22 has an inner diameter of, for example, 1 mm. The clamper pin 30 is inserted into the through hole 24 with almost no gap.

6A and 6B are diagrams showing the clamper pin 30, wherein FIG. 6A is a side view and FIG. 6B is a bottom view.
The clamper pin 30 is an elongated shaft-shaped member. The clamper pin 30 is made of titanium or a titanium alloy. The diameter of the clamper pin 30 is, for example, 1 mm.
The clamper pin 30 includes an elongated main body portion (shaft main body portion) 30A and an engaging portion 31 formed on the base end side (+ Z side) of the main body portion 30A. The diameter of the main body 30A is, for example, 1 mm. The engaging portion 31 is fitted into the engaging hole portion 16 formed at the deepest portion of the center hole 13 of the fixture 10.
The engaging part 31 is composed of a tapered part 31A and two parallel surfaces 31B. The outer diameter of the tapered portion (retaining shaft portion) 31A gradually increases (expands) toward the + Z side. The parallel two surfaces (spinning restriction shaft portions) 31B are two outer surfaces that are formed on the outer surface of the tapered portion 31A and are parallel and facing away from each other. The angle of the tapered portion 31A is about 30 °. The width (two-surface width) of the parallel two surfaces 31B is 1.1 mm, for example.

An outer thread 32 of M1 is provided on the tip side (−Z side) of the clamper pin 30. The screw size of the external screw 32 can be appropriately changed according to the diameter of the clamper pin 30 and the like.
The length of the clamper pin 30 is such that when the implant 5 is assembled, the outer screw 32 is substantially in the same position as the inner screw 25 at the end (−Z side) of the through hole 24 of the abutment 20.

7A and 7B are diagrams showing the clamper 40, where FIG. 7A is a bottom view and FIG. 7B is a longitudinal sectional view (VIIb-VIIb cross section).
The clamper 40 is a ring-shaped member. The clamper 40 is made of titanium or a titanium alloy. The outer diameter of the clamper 40 is, for example, 1.5 mm. The outer diameter of the clamper 40 is slightly smaller than the minimum inner diameter of the reverse tapered hole portion 15 of the center hole 13 of the fixture 10. The outer diameter of the clamper 40 may be slightly larger than the minimum inner diameter of the reverse tapered hole portion 15 and may be inserted into the reverse tapered hole portion 15.
The inner diameter of the clamper 40 is, for example, 1 mm. The inner diameter of the clamper 40 is fitted on the clamper pin 30. The clamper 40 is disposed at a position where it is caught by the engaging portion 31 of the clamper pin 30.
The clamper 40 is disposed so as to be received in the reverse tapered hole portion 15 of the center hole 13 of the fixture 10 when the implant 5 is assembled.

In the clamper 40, three comb teeth 41 are formed on the base end side (+ Z side). The number of the comb teeth 41 can be changed as appropriate. When the clamper 40 rides on the engaging portion 31 of the clamper pin 30, the comb teeth 41 are elastically deformed and spread toward the outer peripheral side. The comb teeth 41 of the clamper 40 operate in the same manner as a so-called collet chuck.
When the comb teeth 41 of the clamper 40 spread toward the outer peripheral side, the diameter becomes larger than the minimum inner diameter of the tapered hole portion 14. The clamper 40 is hooked (intervenes) at the projecting portion 15A projecting to the inner peripheral side at the upper end of the reverse tapered hole portion 15 of the center hole 13 of the fixture 10. Thereby, the movement of the clamper 40 and the clamper pin 30 to the −Z side is restricted.

FIGS. 8A and 8B are views showing the lock nut 50, where FIG. 8A is a bottom view and FIG. 8B is a longitudinal sectional view (VIIIb-VIIIb cross section).
The lock nut (lock bush) 50 is a ring-shaped member. The lock nut 50 has an outer screw 51 of M2.5 on the outer peripheral surface and an inner screw 52 of M1 on the inner peripheral surface. The lock nut 50 is formed of titanium or a titanium alloy. The screw dimensions of the outer screw 51 and the inner screw 52 can be appropriately changed corresponding to the inner screw 25 and the outer screw 32.
A pair of wrench grooves 53 having two parallel and back surfaces are provided on the end surface of the lock nut 50 on the −Z side. A lock nut 50 can be rotated by engaging an unillustrated instrument (such as a wrench) with the two parallel surfaces of the wrench groove 53.
The outer screw 51 is screwed into an inner screw 25 formed in a part of the through hole 24 of the abutment 20. The inner screw 52 is screwed to the outer screw 32 formed on the tip side (−Z side) of the clamper pin 30. When the lock nut 50 is rotated clockwise while the implant 5 is assembled, the clamper pin 30 moves to the −Z side with respect to the abutment 20.

(Two implant treatment methods (a treatment method that requires two operations))
The assembly of the implant 5 is performed according to the following procedure.

(First surgery)
First, the fixture 10 is implanted in the patient's alveolar bone 2.
When the fixture 10 is embedded in the alveolar bone 2, an implant mount driver 80 is used.

FIG. 9 is a view showing the implant mount driver 80 according to the first embodiment of the present invention, where (a) a side view, (b) a bottom view, and (c) a partial cross-sectional view (IXc-IXc cross section). is there.
FIG. 10 is a diagram showing a usage state of the implant mount driver 80 according to the first embodiment of the present invention.
In the implant mount driver 80, the end in the + Z direction is referred to as the distal end (first end), and the end in the −Z direction is referred to as the proximal end (second end).

The implant mount driver (implant driver) 80 is an elongated shaft-shaped member, and is formed of stainless steel or the like. The implant mount driver 80 is used in a state where it is connected to a surgical motor (not shown).
In the implant mount driver 80, a motor connection portion 81 connected to a surgical motor (drive source) is formed on the base end side (−Z side). The implant mount driver 80 is formed with an implant coupling portion 82 that is inserted into and fitted into the center hole 13 of the fixture 10 on the distal end side (+ Z side).

The implant connecting portion 82 includes a tapered alignment shaft portion 83 whose outer diameter decreases toward the tip, a rotation transmission shaft portion 84 formed in a non-circular shape, and a clamper 85 capable of changing the outer diameter. The alignment shaft portion 83 and the rotation transmission shaft portion 84 are integrally formed. That is, the alignment shaft portion 83 and the rotation transmission shaft portion 84 are formed at the same position in the Z direction (axial direction).
The aligning shaft portion 83 is a portion that fits into the tapered hole portion 14 of the center hole 13 of the fixture 10. The alignment shaft portion 83 is formed in the same shape as the tapered shaft portion 22 of the abutment 20 of the abutment unit 8.

The rotation transmission shaft portion 84 is a portion that fits into the protrusion 17 of the center hole 13 of the fixture 10. The rotation transmission shaft portion 84 has a groove portion 84A. The rotation transmission shaft portion 84 (groove portion 84 </ b> A) is formed in the same shape as the groove portion 23 of the abutment 20.
The clamper (variable diameter portion) 85 is a portion that engages with the reverse tapered hole portion 15 (projecting portion 15 </ b> A) of the center hole 13 of the fixture 10. The clamper 85 (clamp body 87) is formed in substantially the same shape as the clamper 40 of the abutment unit 8.

The implant connecting portion 82 of the implant mount driver 80 is formed in the same shape as a portion of the abutment unit 8 that is inserted into the center hole 13 of the fixture 10.
For this reason, when the implant coupling part 82 of the implant mount driver 80 is inserted into the center hole 13 of the fixture 10, functions similar to those of the pressure-resistant part 60 and the rotation prevention part 70 described later can be exhibited.
Specifically, in a state where the implant mount driver 80 is inserted into the center hole 13 of the fixture 10, the alignment shaft portion 83 and the tapered hole portion 14 are fitted (contacted), so the implant mount driver 80 and the fixture The ten central axes (rotating axes) coincide with each other, and the posture of the fixture 10 is restricted (suppressed). Further, since the groove portion 84A of the rotation transmission shaft portion 84 and the projection 17 are engaged with each other, the rotation of the fixture 10 relative to the implant mount driver 80 is restricted (suppressed).

The clamper 85 includes a thin shaft portion 86 formed in the implant connecting portion 82 and a clamp body 87 that fits with a small gap with respect to the thin shaft portion 86. The clamp body 87 is a C-shaped ring member formed of a synthetic resin such as PEEK (polyetheretherketone).
The outer diameter of the clamp body 87 is slightly larger than the minimum inner diameter of the reverse tapered hole portion 15 of the center hole 13 of the fixture 10. For this reason, the clamper 85 can be put into the reverse taper hole 15 of the center hole 13 of the fixture 10. Since the clamp body 87 is a C-shaped ring member and a slight gap is provided between the clamp body 87 and the thin shaft portion 86, the outer diameter of the clamp body 87 is small when the clamp body 87 comes into contact with the protruding portion 15A. It will be elastically deformed. When the clamper 85 is inserted into the reverse tapered hole portion 15, the elastic deformation of the clamp body 87 is recovered, and the clamper 85 engages with the protruding portion 15A. For this reason, the fixture 10 is prevented from falling off from the implant mount driver 80.

When the fixture 10 is embedded in the alveolar bone 2, the groove portion 84 </ b> A of the rotation transmission shaft portion 84 and the protrusion 17 mesh with each other, so that the rotational force of the surgical motor is reliably applied to the fixture 10 via the implant mount driver 80. Communicated. Further, since the aligning shaft portion 83 and the tapered hole portion 14 are fitted, the fixture 10 is embedded in the alveolar bone 2 in a stable posture without wobbling. Therefore, by using the implant mount driver 80, an excessive burden on the human body can be avoided.

Since the male screw 12 of the fixture 10 has a threading function, the fixture 10 is embedded while cutting the screw directly into the alveolar bone 2. For this reason, the operation time can be shortened, and reliable initial fixation can be obtained.

After embedding the fixture 10 in the alveolar bone 2, the implant mount driver 80 is pulled in the −Z direction to be separated from the fixture 10. At this time, the clamp body 87 comes into contact with the protruding portion 15A and is elastically deformed so that the outer diameter becomes small. Since the clamp body 87 is elastically deformed only by a slight pulling force, an excessive load is not applied to the human body, and the fixture 10 does not fall out of the alveolar bone 2.

After separating the implant mount driver 80 from the fixture 10, the gums 4 are sewn together. The alveolar bone 2 and the fixture 10 are brought into close contact with the bone over about 3 to 6 months, although there are individual differences.

(Preparation for the second surgery)
Separately from the fixture 10, the abutment unit 8 is assembled. The abutment unit 8 is assembled by the abutment 20, the clamper pin 30, the clamper 40 and the lock nut 50. The abutment unit 8 is sold in an assembled form.

In assembling the abutment unit 8, first, the clamper 40 is externally fitted to the clamper pin 30. Next, the lock nut 50 is attached to the abutment 20. The outer screw 51 of the lock nut 50 is screwed into the inner screw 25 formed in a part of the through hole 24 of the abutment 20.

Next, the clamper pin 30 is inserted from the + Z side of the through hole 24 of the abutment 20. When the tip end side (−Z side) of the clamper pin 30 comes into contact with the lock nut 50 attached to the abutment 20, the clamper pin 30 is rotated clockwise. By the clockwise rotation of the clamper pin 30, the outer screw 32 of the clamper pin 30 is screwed into the inner screw 52 of the lock nut 50. The clamper pin 30 is rotated clockwise until immediately before the tip end side (−Z side) of the clamper 40 fitted on the clamper pin 30 contacts the −Z side end of the abutment 20.
Thereby, the assembly of the abutment unit 8 is completed.

(Second surgery)
The abutment unit 8 is inserted into the center hole 13 of the fixture 10 embedded in the alveolar bone 2 of the patient. The tapered shaft portion 22 of the abutment 20 is fitted into the tapered hole portion 14 of the center hole 13 of the fixture 10 in a wedge shape.
The engagement portion 31 on the base end side (+ Z side) of the clamper pin 30 is inserted into the engagement hole portion 16 on the bottom (+ Z side) of the center hole 13 of the fixture 10. The parallel two surfaces 31B of the engaging portion 31 of the clamper pin 30 and the parallel two surfaces 16A of the engaging hole portion 16 of the fixture 10 are in close contact (fitting).

Next, a tool (not shown) (such as a wrench) is fitted in the wrench groove 53 of the lock nut 50 and rotated clockwise. The lock nut 50 moves while rotating in the + Z direction. At the same time, the clamper pin 30 moves in the −Z direction.
At this time, since there is a difference in the pitch between the outer screw 51 and the inner screw 52 of the lock nut 50 (M2.5: 0.35P, M1: 0.2P), compared to the amount of movement of the lock nut 50 in the + Z direction. The amount of movement of the clamper pin 30 in the −Z direction increases.
Since the engaging portion 31 of the clamper pin 30 is inserted into the engaging hole portion 16 of the fixture 10, the parallel two surfaces 31 </ b> B of the engaging portion 31 and the parallel two surfaces 16 </ b> A of the engaging hole portion 16 are in close contact (fitting). The rotation of the clamper pin 30 is restricted (suppressed). The clamper pin 30 does not rotate with the lock nut 50 and moves in the −Z direction.

When the clamper pin 30 is moved in the −Z direction, the tip end side (−Z side) of the clamper 40 fitted on the clamper pin 30 comes into contact with the + Z side end of the abutment 20, and the clamper 40 moves in the + Z direction. Is regulated (deterred).
When the clamper pin 30 is further moved in the + Z direction, the tapered portion 31A of the engaging portion 31 of the clamper pin 30 is inserted into the inner peripheral side of the clamper 40 (the clamper 40 rides on the tapered portion 31A). Thereby, the three comb teeth 41 on the + Z side of the clamper 40 are elastically deformed and spread toward the outer peripheral side.
Therefore, the clamper 40 is caught by the protruding portion 15A protruding to the inner peripheral side at the upper end of the reverse tapered hole portion 15 of the center hole 13 of the fixture 10, and the movement of the clamper 40 and the clamper pin 30 to the −Z side is restricted.

In a state where movement of the clamper 40 and the clamper pin 30 to the −Z side is restricted, the lock nut 50 is further rotated clockwise. As a result, the abutment 20 moves in the + Z direction. The abutment 20 further moves toward the fixture 10, and the tapered shaft portion 22 of the abutment 20 is further inserted in a wedge shape into the tapered hole portion 14 of the center hole 13 of the fixture 10.

In this way, the implant 5 is assembled robustly without rattling.
Thereafter, the artificial dental crown 6 is attached to the −Z side outer peripheral surface of the abutment 20 of the implant 5 using an adhesive or the like.

In the implant 5, the tapered shaft portion 22 and the tapered hole portion 14 are fitted (inserted) to function as a pressure-resistant portion 60 that receives an external force (occlusion pressure F) acting on the abutment 20 (see FIG. 1). .
In particular, the pressure-resistant portion 60 has a sufficiently large area for receiving the occlusal pressure F because the tapered shaft portion 22 and the tapered hole portion 14 have sufficiently longer lengths in the Z direction than the conventional one, and have high pressure-resistant performance.
Therefore, for example, when the implant 5 is used as an anterior tooth, even if the occlusal pressure F is received from the direction intersecting the Z-axis direction with respect to the abutment 20, the occlusal pressure F is reliably received. Therefore, the abutment 20 and the fixture 10 are not cracked or chipped.

When inserting the abutment 20 into the center hole 13 of the fixture 10, the five grooves 23 of the tapered shaft portion 22 are inserted into the five protrusions 17 of the tapered hole portion 14 of the center hole 13. Since the protrusion 17 on the inner peripheral side surface of the tapered hole portion 14 and the groove portion 23 on the outer peripheral side surface of the tapered shaft portion 22 mesh with each other, the rotation of the abutment 20 relative to the fixture 10 is restricted (suppressed). The protrusion 17 of the tapered hole portion 14 and the groove portion 23 of the tapered shaft portion 22 function as the rotation preventing portion 70.

In the implant 5, a pressure-resistant portion 60 (taper shaft portion 22 and taper hole portion 14) that receives the occlusal pressure F and a rotation prevention portion 70 (projection 17 and groove portion 23) are integrally formed. That is, the pressure | voltage resistant part 60 and the rotation prevention part 70 are formed in the same position in a Z direction (axial direction).
For this reason, the pressure | voltage resistant part 60 can be formed longer (deeply) than before. The length of the pressure-resistant portion 60 (the tapered shaft portion 22 and the tapered hole portion 14) can be set to one third or more of the entire length of the fixture 10.
Therefore, the implant 5 can reliably receive the strong occlusal pressure F without causing cracks and chipping in the abutment 20 and the fixture 10.

[Second Embodiment]
FIG. 11 is a longitudinal sectional view showing an implant 105 according to the second embodiment of the present invention.
In the implant 105, the same members as those in the implant 5 according to the first embodiment are denoted by the same reference numerals, and the description thereof is omitted.

The implant 105 includes a fixture 110 that is fixed to the alveolar bone 2 and an abutment unit 108 that can be attached to and detached from the fixture 110. An artificial crown 6 is attached to the abutment unit 108.

The central axis (longitudinal direction) of the implant 105 is taken as the Z axis (Z direction, depth direction, axial direction, vertical). Of the Z-axis, the fixture 110 side is the + Z side (+ Z direction), and the abutment 120 side is the −Z side (−Z direction). The bottom view is when viewed from the + Z direction, and the top view is when viewed from the -Z direction. The end in the + Z direction is called the base end (first end), and the end in the −Z direction is called the front end (second end).

The abutment unit 108 is an assembly of the abutment 120, the clamper pin 130, the clamper 40 and the lock nut 150.
The abutment unit 108 includes a shaft-shaped abutment 120, a clamper pin 130, a clamper 40, and a lock nut 150.
An artificial crown 6 is attached to the abutment 120.
The clamper pin 130 is inserted into the through hole 124 of the abutment 120 and engages with the fixture 110.
The clamper 40 is fitted to the clamper pin 130.
The lock nut 150 engages with the abutment 120 and is screwed into the clamper pin 130.

In the implant 5 according to the first embodiment, the pressure-resistant portion 60 (taper shaft portion 22 and tapered hole portion 14) that receives the occlusal pressure F and the rotation prevention portion 70 (projection 17 and groove portion 23) are integrated (the same in the Z direction). Position).
On the other hand, in the implant 105, the pressure-resistant portion 160 (taper shaft portion 122 and taper hole portion 114) that receives the occlusal pressure F and the rotation prevention portion 170 (rotation prevention hole portion 117 and rotation prevention shaft portion 123) are different (different in the Z direction). Position).

12A and 12B are diagrams showing the fixture 110, where FIG. 12A is a top view and FIG. 12B is a partial cross-sectional side view (XIIb-XIIb cross section).
The fixture 110 is a shaft-shaped member formed of a ceramic material such as zirconia, and a male screw 12 is formed on the outer peripheral surface.
A center hole 113 is opened at the center of the −Z side end face of the fixture 110. In the center hole 113, a tapered hole portion 114, a rotation prevention hole portion 117, a reverse tapered hole portion 15, and an engagement hole portion 16 (parallel two surfaces 16A) are continuously formed toward the + Z side.
The inner diameter of the tapered hole portion 114 is gradually reduced (reduced) from the end surface on the −Z side toward the + Z side. The rotation prevention hole 117 is formed in a non-circular shape.

The taper angle of the tapered hole portion (fitting hole portion) 114 is, for example, 8 °. The average diameter of the tapered hole 114 is, for example, 2 mm. The length (depth) of the tapered hole portion 114 is, for example, 3.5 mm.
The rotation prevention hole 117 has a plurality of grooves 117A along the Z direction. The plurality of groove portions 117 </ b> A are arranged at equal intervals (equal angles) in the circumferential direction of the center hole 113. The number of the groove portions 117A is five. The number of the groove portions 117A can be changed as appropriate. The shape of the cross section orthogonal to the Z-axis of the groove 117A is such that the bottom side (inner peripheral side) is recessed in a semicircular arc shape.

FIGS. 13A and 13B are views showing the abutment 120, where FIG. 13A is a side view, FIG. 13B is a longitudinal sectional view (XIIIb-XIIIb section), and FIG. 13C is a bottom view.
The abutment 120 includes a main body 121, a taper shaft 122, and a rotation prevention shaft 123.
An artificial dental crown 6 is attached to the main body 121. The taper shaft portion (fitting shaft portion) 122 extends from the base end side (+ Z side) of the main body portion 121 and is inserted into the center hole 113 of the fixture 10.
The abutment 120 is integrally formed of a white ceramic material having excellent aesthetics. Zirconia is adopted as the ceramic material.

The taper angle of the taper shaft portion 122 is, for example, 8 °. The angle is the same as the angle of the tapered hole 114 of the center hole 113 of the fixture 110.
The average inner diameter of the tapered shaft portion 122 is, for example, 2 mm. The length of the tapered shaft portion 122 is the same as or longer than that of the tapered hole portion 114. The length of the taper shaft portion 122 is, for example, 5 mm.
The rotation preventing shaft 123 has a plurality of protrusions 123A along the Z direction. The plurality of protrusions 123 </ b> A are arranged at equal intervals (equal angles) in the circumferential direction of the rotation prevention shaft portion 123. The number of protrusions 123A is five. The number of protrusions 123A can be changed as appropriate. The number of protrusions 123A is the same as the number of grooves 117A of the rotation prevention hole 117.
The shape of the cross section orthogonal to the Z-axis of the protrusion 123A is such that the top side (outer peripheral side) swells in a semicircular arc shape. That is, the protrusion 123A has a shape opposite to the groove 117A of the rotation prevention hole 117.

When the abutment 120 is inserted into the center hole 113 of the fixture 110, the tapered shaft portion 122 of the abutment 120 is fitted into the tapered hole portion 114 of the center hole 113 of the fixture 110. At approximately the same time, the five protrusions 123A of the rotation prevention shaft 123 are inserted into the five grooves 117A of the rotation prevention hole 117.

At the center of the abutment 120, a through hole 124 that penetrates in the Z direction is formed. Of the through hole 124, a portion corresponding to the main body 121 (the main body side through hole 124A) has an inner diameter of, for example, 2.5 mm. The lock nut 150 is inserted into the main body side through hole 124A.
Of the through hole 124, a portion corresponding to the tapered shaft portion 122 (taper shaft portion side through hole 124B) has an inner diameter of, for example, 1 mm. The main body portion 30A of the clamper pin 130 is inserted through the tapered shaft portion side through hole 124B with almost no gap.
A step surface 125 perpendicular to the Z direction is formed at the boundary between the main body side through hole 124A and the tapered shaft side through hole 124B.

14A and 14B are diagrams showing the clamper pin 130, where FIG. 14A is a side view and FIG. 14B is a bottom view.
The clamper pin 130 has substantially the same shape as the clamper pin 30. Unlike the engaging portion 31 of the clamper pin 30, a tapered portion 31A and two parallel surfaces 31B are separately provided on the base end side (+ Z side) of the clamper pin 130.

15A and 15B are diagrams showing the lock nut 150, where FIG. 15A is a top view and FIG. 15B is a longitudinal sectional view (XVb-XVb cross section).
The lock nut 150 is a ring-shaped (cylindrical) member formed of titanium or a titanium alloy.
On the inner peripheral surface of the lock nut 150, an inner screw 52 which is an M1 size right screw is provided. The screw dimension of the inner screw 52 can be appropriately changed corresponding to the outer screw 32.
An end surface 150A on the + Z side of the lock nut 150 is formed to be rotatable around a central axis (a central hole) while being in contact with the stepped surface 125 of the through hole 124 of the abutment 120.
A straight groove 153 into which a minus driver (not shown) is inserted is provided on the end surface 150B on the −Z side of the lock nut 150. The lock nut 150 can be rotated by engaging a minus driver with the linear groove 153.

The lock nut 150 is inserted into the through hole 124 (the main body side through hole 124A) of the abutment 120. A slight gap is provided between the outer peripheral surface 150S of the lock nut 150 and the main body side through hole 124A. The inner screw 52 of the lock nut 150 is screwed into the outer screw 32 of the clamper pin 130 exposed in the main body side through hole 124A.
Therefore, when the lock nut 150 is rotated clockwise while the implant 105 is assembled, the end surface 150A of the lock nut 150 contacts and slides against the step surface 125 of the through hole 124 of the abutment 120. At the same time, the clamper pin 130 screwed to the inner screw 52 can be moved to the −Z side with respect to the abutment 120.

(Two implant treatment methods (a treatment method that requires two operations))
The assembly and the like of the implant 105 are substantially the same as the assembly and the like of the implant 5 according to the first embodiment.

(First surgery)
First, the fixture 110 is implanted in the patient's alveolar bone 2.
When the fixture 110 is embedded in the alveolar bone 2, an implant mount driver 180 is used.

FIGS. 16A and 16B are views showing an implant mount driver 180 according to the second embodiment of the present invention, wherein FIG. 16A is a side view, FIG. 16B is a bottom view, and FIG. 16C is a partial cross-sectional view (XVIc-XVIc cross section). is there.
FIG. 17 is a diagram illustrating a usage state of the implant mount driver 180 according to the second embodiment of the present invention.
In the implant mount driver 180, the end in the + Z direction is referred to as the distal end (first end), and the end in the −Z direction is referred to as the proximal end (second end).

The implant mount driver (implant driver) 180 is an elongated shaft-shaped member, and is formed of stainless steel or the like. The implant mount driver 180 is used in a state of being connected to a surgical motor (not shown).
The implant mount driver 180 is formed with an implant coupling portion 182 that is inserted into and fitted into the center hole 113 of the fixture 110 on the distal end side (+ Z side).

The implant connecting portion 182 includes a tapered alignment shaft portion 183 whose outer diameter decreases toward the tip, a rotation transmission shaft portion 184 formed in a non-circular shape, a clamper 85 that can change the outer diameter, and the like. The alignment shaft portion 183 and the rotation transmission shaft portion 184 are formed separately. That is, the alignment shaft portion 183 and the rotation transmission shaft portion 184 are formed at different positions in the Z direction (axial direction).
The aligning shaft portion 183 is a portion that fits into the tapered hole portion 114 of the center hole 113 of the fixture 110. The aligning shaft portion 183 is formed in the same shape as the tapered shaft portion 122 of the abutment 120 of the abutment unit 108.

The rotation transmission shaft portion 184 is a portion that fits into the rotation prevention hole portion 117 (groove portion 117A). The rotation transmission shaft portion 184 has a protrusion 184A. The rotation transmission shaft portion 184 (projection 184A) is formed in the same shape as the projection 123A of the rotation prevention shaft portion 123 of the abutment 120.
The clamper 85 is a part that engages with the reverse tapered hole part 15 (projecting part 15A) of the center hole 113 of the fixture 110. The clamper 85 (clamp body 87) is formed in substantially the same shape as the clamper 40 of the abutment unit 108.

The implant connecting portion 182 of the implant mount driver 180 is formed in the same shape as a portion of the abutment unit 108 that is inserted into the center hole 113 of the fixture 110. For this reason, when the implant connection part 182 of the implant mount driver 180 is inserted into the center hole 113 of the fixture 110, the same functions as those of the pressure-resistant part 160 and the rotation prevention part 170 described later can be exhibited.
Specifically, in a state where the implant mount driver 180 is inserted into the center hole 113 of the fixture 110, the alignment shaft portion 183 and the tapered hole portion 114 are fitted (contacted), so the implant mount driver 180 and the fixture are fixed. The central axes (rotating axes) of 110 coincide with each other, and the posture of the fixture 110 is restricted (suppressed). Further, since the five protrusions 184A of the rotation transmission shaft portion 184 and the five grooves 117A of the rotation prevention hole portion 117 mesh with each other, the rotation of the fixture 110 with respect to the implant mount driver 180 is restricted (suppressed).

When the fixture 10 is embedded in the alveolar bone 2, the rotation transmission shaft portion 184 (protrusion 184A) and the rotation prevention hole portion 117 (groove portion 117A) mesh with each other, so that the rotational force of the surgical motor causes the implant mount driver 180 to move. Via the fixture 110. In addition, since the aligning shaft portion 183 and the tapered hole portion 114 are fitted, the fixture 110 is embedded in the alveolar bone 2 in a stable posture without wobbling. Therefore, by using the implant mount driver 180, an excessive burden on the human body can be avoided.

After embedding the fixture 110 in the alveolar bone 2, the implant mount driver 180 is pulled in the −Z direction to be separated from the fixture 110. At this time, the clamp body 87 comes into contact with the protruding portion 15A and is elastically deformed so that the outer diameter becomes small. Since the clamp body 87 is elastically deformed only by a slight pulling force, an excessive load is not applied to the human body, and the fixture 110 does not fall out of the alveolar bone 2.

After separating the implant mount driver 180 from the fixture 110, the gums 4 are sewn together. The alveolar bone 2 and the fixture 110 are brought into close contact with the bone over about 3 to 6 months, although there are individual differences.

(Preparation for the second surgery)
Separately from the fixture 110, the abutment unit 108 is assembled. The abutment unit 108 is assembled by the abutment 120, the clamper pin 30, the clamper 40 and the lock nut 50. The abutment unit 108 is sold in an assembled form.

The assembly of the abutment unit 108 is almost the same as the assembly of the abutment unit 8.

(Second surgery)
The procedure for attaching the abutment unit 108 to the fixture 110 embedded in the alveolar bone 2 of the patient (assembly of the implant 105) and the like are almost the same as the assembly of the implant 5.

In the implant 105, the tapered shaft portion 122 and the tapered hole portion 114 are fitted (inserted) to function as a pressure-resistant portion 160 that receives an external force (occlusion pressure F) acting on the abutment 120.

When inserting the abutment 120 into the center hole 113 of the fixture 110, the five protrusions 123A of the rotation preventing shaft 123 are inserted into the groove 117A of the rotation preventing hole 117. Since the five grooves 117A and the five protrusions 123A mesh with each other, the rotation of the abutment 120 relative to the fixture 110 is restricted (suppressed). The rotation prevention hole portion 117 (groove portion 117A) and the rotation prevention shaft portion 123 (projection 123A) function as the rotation prevention portion 170.

In the implant 105, a pressure-resistant portion 160 (taper shaft portion 122 and taper hole portion 114) that receives the occlusal pressure F and a rotation prevention portion 170 (rotation prevention hole portion 117 and rotation prevention shaft portion 123) are separately formed. That is, the pressure | voltage resistant part 160 and the rotation prevention part 170 are formed in a different position in the Z direction (axial direction).
For this reason, the implant 105 can reliably receive the strong occlusal pressure F without causing cracks and chipping in the abutment 120 and the fixture 110.

The technical scope of the present invention is not limited to the above-described embodiment. In the range which does not deviate from the meaning of this invention, what added the various change to embodiment mentioned above is included. The specific materials and layer configurations described in the embodiments are merely examples, and can be changed as appropriate.

Although the case where the implant mount drivers 80 and 180 are attached to the surgical motor has been described, the present invention is not limited to this. The implant mount drivers 80 and 180 may be rotated manually without using a power source such as various motors. The drive source for applying the rotational force to the implant mount drivers 80 and 180 may be an air turbine or the like in addition to a motor and human power.

The cross-sectional shape of the rotation prevention units 70 and 170 is not limited to the above-described embodiment. The cross-sectional shape of the rotation preventing portions 70 and 170 may be a non-circular shape.
Instead of the protrusion 17, the groove 117 </ b> A, the groove 23, and the protrusion 123 </ b> A, a polygonal or elliptical hole / shaft may be used. In this case, the shape of the rotation transmission shafts 84 and 184 also needs to be a polygonal or elliptical shaft.

Although the case where the implant mount drivers 80 and 180 are formed of stainless steel or the like has been described, the present invention is not limited to this. You may form with various metal materials, such as titanium and a titanium alloy, and ceramic materials, such as an alumina and a zirconia.

In the implant mount driver 180, the case where the alignment shaft portion 183 is disposed on the proximal end side (−Z side) and the rotation transmission shaft portion 184 is disposed on the distal end side (+ Z side) is described, but the present invention is not limited thereto. The alignment shaft portion 183 may be disposed on the distal end side (+ Z side), and the rotation transmission shaft portion 184 may be disposed on the proximal end side (−Z side). In this case, in the fixture 110, the rotation prevention hole 117 is disposed on the distal end side (+ Z side), and the tapered hole portion 114 is disposed on the proximal end side (−Z side).

Although the alignment shaft portions 83 and 183 of the implant mount drivers 80 and 180 have the same shape as the tapered shaft portions 22 and 122 of the abutments 20 and 120, they are not limited thereto. The aligning shaft portions 83 and 183 may have the same shape as a part of the tapered shaft portions 22 and 122. The aligning shaft portions 83 and 183 may not be fitted to the entire tapered hole portions 14 and 114 of the fixtures 10 and 110. For example, the alignment shaft portions 83 and 183 may be shorter in the Z direction than the tapered shaft portions 22 and 122.

The biocompatible ceramic material forming the fixtures 10 and 110 and the abutments 20 and 120 is not limited to zirconia (zirconium oxide). Alumina (aluminum oxide), yttrium oxide, hafnium oxide, silicone oxide, magnesium oxide, cerium oxide, or the like may be employed.
The fixtures 10 and 110 and the abutments 20 and 120 may be formed of a metal material such as titanium or a titanium alloy.

The material forming the clamper 40 is not limited to titanium excellent in biocompatibility. A titanium alloy may be adopted. As the titanium alloy, for example, an alloy of titanium and aluminum can be adopted. The clamper 40 may be formed of an elastic material such as resin (rubber). The number of the comb teeth 41 of the clamper is not limited to three. Two or four or more may be used.

The clamp body 87 is not limited to a synthetic resin, and may be formed of an elastic material such as rubber. When the clamp body 87 is formed of rubber, it may be formed in a complete ring shape without a slit.
The clamp body 87 may be formed of a metal material. In this case, the elastic deformation in the radial direction is possible by making the clamp body 87 C-shaped and reducing the radial thickness.

The material forming the clamper pins 30 and 130 and the lock nuts 50 and 150 can be changed as appropriate.

The follow-up restricting hole portion and the follow-up restricting shaft portion are not limited to the parallel two surfaces 16A and 31B. The follow-up restricting hole portion and the follow-up restricting shaft portion may be non-circular.
Instead of the parallel two surfaces 16A and 31B, a polygonal hole and a polygonal shaft may be used.

The lock bush is not limited to the lock nut 50 in which screws 51 and 52 are formed on the outer peripheral surface and the inner peripheral surface, respectively. The lock bush may be engaged with each of the through holes 24 of the abutments 20 and 120 and the main body portion 30 </ b> A of the clamper pin 30.

In the implant 5, the outer screw 51 of the lock nut 50 is screwed (locked) to the inner screw 25 of the through hole 124 of the abutment 20, but this is not a limitation. A step surface 125 may be formed in place of the inner screw 25, and a lock nut 150 may be used in place of the lock nut 50.
In the implant 105, the end surface 150 </ b> A of the lock nut 150 abuts (latches) on the step surface 125 of the abutment 120, but is not limited thereto.
The inner screw 25 may be formed in place of the stepped surface 125, and the lock nut 50 may be used in place of the lock nut 150.

In the implant 5, a clamper pin 130 may be used instead of the clamper pin 30.
In the implant 105, the clamper pin 30 may be used instead of the clamper pin 130.

The fixtures 10 and 110 are not limited to those having a threading function at the base end (self-tapping type). The fixtures 10 and 110 may be those that do not have a threading function (normal type).

The implants 5 and 105 are not limited to use for dental treatment. The fracture treatment method using the implants 5 and 105 and the implants 5 and 105 may be used for artificial joints.

2 Alveolar bone (bone) 5 Implant 8 Abutment unit 10 Fixture 13 Center hole 14 Taper hole (fitting hole) 15A Protruding part (retaining hole) 16A Parallel two surfaces (rotation restricting hole) 17 Protrusion (Rotation prevention hole part) 20 Abutment 22 Tapered shaft part (fitting shaft part) 23 Groove part (rotation prevention shaft part) 30 Clamper pin 30A Body part (shaft body part) 31A Taper part (retaining shaft part) 31B Parallel two surfaces (Spinning restriction shaft portion) 40 Clamper 50 Lock nut (lock bush) 80 Implant mount driver (driver for implant) 83 Alignment shaft portion 84 Rotation transmission shaft portion 85 Clamper (variable diameter portion) 105 Implant 108 Abutment unit 110 Fixture Char 113 center hole 114 Tapered hole (fitting hole) 117 Anti-rotation hole 120 Abutment 122 Tapered shaft (fitting shaft)
123 Rotation prevention shaft portion 130 Clamper pin 150 Lock nut (lock bush) 180 Implant mount driver (driver for implant) 183 Alignment shaft portion 184 Rotation transmission shaft portion

Claims (8)

1. When implanting a fixture into a bone, an implant driver is inserted into a central hole formed in the fixture and transmits a rotational force from a driving source,
   A tapered aligning shaft portion whose outer diameter decreases toward the tip;
   A rotation transmission shaft formed in a non-circular shape,
   With
   The aligning shaft portion is fitted into a tapered fitting hole portion whose inner diameter is reduced in the depth direction among the center hole,
   The rotation transmission shaft portion is an implant driver that fits into a rotation prevention hole portion that prevents rotation of an abutment connected to the fixture among the center hole.
2. It has a variable diameter part that can change the outer diameter,
   2. The implant driver according to claim 1, wherein the variable diameter portion engages with a retaining hole portion that prevents the abutment from dropping out of the central hole.
3. The implant driver according to claim 1 or 2, wherein the alignment shaft portion and the rotation transmission shaft portion are formed at different positions in the axial direction.
4. The implant driver according to claim 1 or 2, wherein the alignment shaft portion and the rotation transmission shaft portion are formed at the same position in the axial direction.
5. A fixture in which a tapered fitting hole portion whose inner diameter is reduced in the depth direction and a non-circular anti-rotation hole portion is formed in a part of the center hole;
   An abutment unit formed with a tapered fitting shaft portion that fits into the fitting hole portion and a rotation prevention shaft portion that fits into the rotation prevention hole portion;
   With
   When the fixture is embedded in a bone, an implant driver that transmits a rotational force from a driving source is inserted into the center hole, and the fixture has the same shape as the fitting shaft portion with respect to the fitting hole portion. An implant in which a mandrel is fitted and a rotation transmission shaft having the same shape as the rotation prevention shaft is fitted into the rotation prevention hole.
6. The abutment unit is
   An abutment having a through hole formed along the fitting shaft portion, the rotation prevention shaft portion and the axial direction;
   Engage with the shaft main body portion inserted through the through hole, the retaining shaft portion having a larger diameter than the shaft main body portion, and the follow-up restricting hole portion formed in the center hole to restrict rotation around the own shaft. A clamper pin having a follow-up restricting shaft portion;
   A lock bush to be engaged with the through hole and the shaft main body,
   A clamper that engages with the retaining shaft portion and the retaining hole portion and restricts movement of the clamper pin relative to the fixture;
   The implant of claim 5.
7. The pressure-resistant part consisting of the fitting hole part and the fitting shaft part and the rotation prevention part consisting of the rotation prevention hole part and the rotation prevention shaft part are formed at different positions in the axial direction. The described implant.
8. 7. The pressure-resistant portion comprising the fitting hole and the fitting shaft portion and the rotation preventing portion comprising the rotation prevention hole portion and the rotation prevention shaft portion are formed at the same position in the axial direction. The implant according to 1.
   

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