CA2076939C - Anchoring member - Google Patents
Anchoring member Download PDFInfo
- Publication number
- CA2076939C CA2076939C CA002076939A CA2076939A CA2076939C CA 2076939 C CA2076939 C CA 2076939C CA 002076939 A CA002076939 A CA 002076939A CA 2076939 A CA2076939 A CA 2076939A CA 2076939 C CA2076939 C CA 2076939C
- Authority
- CA
- Canada
- Prior art keywords
- anchoring member
- cutting
- bone tissue
- cutting edge
- screw
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C8/00—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools
- A61C8/0018—Means to be fixed to the jaw-bone for consolidating natural teeth or for fixing dental prostheses thereon; Dental implants; Implanting tools characterised by the shape
- A61C8/0022—Self-screwing
Abstract
The present invention relates to a screw-shaped titanium anchoring member for permanent anchorage in bone tissue, specifically permanent anchorage of artificial teeth or tooth bridges in the jaw-bone. The tip of the anchoring member comprises at least one cavity (4). The edges of the cavities on the outer cylindrical surface form cutting edges (5) to provide self-tapping when the anchoring member is screwed into the bone tissue. The total volume of the cavities is adapted to contain the scraped-off bone tissue material, i.e.
all the scraped-off bone tissue material can be housed in the screw in the volume formed by the cavities. Behind the cutting edges (5) the anchoring member has a clearance surface (9), i.e. behind each cutting edge the surface of the anchoring member is slightly bevelled towards the center of the anchoring member. By means of such clearance surface any squeezing effect which might occur in the cutting portion of the fixture when it is screwed into hard bone tissue can be avoided.
all the scraped-off bone tissue material can be housed in the screw in the volume formed by the cavities. Behind the cutting edges (5) the anchoring member has a clearance surface (9), i.e. behind each cutting edge the surface of the anchoring member is slightly bevelled towards the center of the anchoring member. By means of such clearance surface any squeezing effect which might occur in the cutting portion of the fixture when it is screwed into hard bone tissue can be avoided.
Description
~:,~.,. ~, ... y Case 3259 Anchoring member The present invention relates to a screw-shaped anchoring member made of titanium for permanent anchorage in bone tissue, specifically permanent anchorage of artificial teeth and tooth bridges in the jaw bone. The tip of the anchoring member comprises at least one cavity.
The edges of the cavities on the outer cylindrical surface form cutting edges to provide self-tapping when the anchoring member is screwed into the bone tissue. The total volume of the cavities is adapted to contain the scraped-off bone tissue material, i.e. the bone tissue material is contained within the volume formed by said cavities.
An anchoring member of this type, a so-called fixture, is previously known by EP 0 23? 505. In this case the cavities are formed by two perpendicular through holes which are perpendicular to the longitudinal axis of the fixture or by three not through-going cavities formed on the outer, circular surface of the anchoring member so that cutting edges having a positive cutting angle are formed.
The advantage of a self-tapping fixture is the fact that the fixture can be more easily installed in the jaw-bone. In the normal procedure for installing a fixture a hole is drilled in the jaw-bone. Then drills with successively increasing drilling diameters are used until the hole diameter corresponds to the root diameter of the threaded fixture. In the normal surgical method indicated by Dr Br~nemark a screw tap is used to form the internal thread into which the threaded part of the fixture is inserted. When using a self-tapping fixture of the above-mentioned type the installation can be carried out without any screw tap.
The hardness of the bone (jaw-bone) into which the fixtures are installed varies to a big extent. Some of the patients has a very thin outer bone layer, corticalis, which is hard, but the rest of the bone, the inner spongious bone, is very soft. Por some patients on the other hand all the bone through the entire section is hard.
The edges of the cavities on the outer cylindrical surface form cutting edges to provide self-tapping when the anchoring member is screwed into the bone tissue. The total volume of the cavities is adapted to contain the scraped-off bone tissue material, i.e. the bone tissue material is contained within the volume formed by said cavities.
An anchoring member of this type, a so-called fixture, is previously known by EP 0 23? 505. In this case the cavities are formed by two perpendicular through holes which are perpendicular to the longitudinal axis of the fixture or by three not through-going cavities formed on the outer, circular surface of the anchoring member so that cutting edges having a positive cutting angle are formed.
The advantage of a self-tapping fixture is the fact that the fixture can be more easily installed in the jaw-bone. In the normal procedure for installing a fixture a hole is drilled in the jaw-bone. Then drills with successively increasing drilling diameters are used until the hole diameter corresponds to the root diameter of the threaded fixture. In the normal surgical method indicated by Dr Br~nemark a screw tap is used to form the internal thread into which the threaded part of the fixture is inserted. When using a self-tapping fixture of the above-mentioned type the installation can be carried out without any screw tap.
The hardness of the bone (jaw-bone) into which the fixtures are installed varies to a big extent. Some of the patients has a very thin outer bone layer, corticalis, which is hard, but the rest of the bone, the inner spongious bone, is very soft. Por some patients on the other hand all the bone through the entire section is hard.
Self-tapping fixtures have previously been used primarily for softer bone-types, i.e. bone in the over-denture. Self-tapping fixtures for harder bone types must have very good cutting characteristics in order to limit the torsional force so that the fixture itself or the surrounding bone tissue will not be damaged. Very hard requirements on the fixture design as well as on the cutting sharpness then must be fulfilled.
In another and more simple method for using a self-tapping fixture the hole in the jaw bone is drilled big enough to allow only the outer part of the threading to contact the bone. This is a risky method, however, as the initial stability of the fixture in the bone is reduced.
The object of the present invention is to provide a self-tapping anchoring member (fixture? with good properties even when installed in hard bone qualities.
According to the invention the good properties have been achieved by providing the anchoring member with a clearance behind the cutting edges, i.e. the outer surface of the anchoring member, seen in a section through the cutting part of he anchoring member, is slightly bevelled behind each cutting edge. By means of such clearance surface the squeezing effect on the anchoring member in the cutting zone when screwed into the bone can be eliminated. This squeezing effect otherwise contributes to a big extent to the torque transmitted o the anchoring member when installed in the bone.
Accordingly, in one aspect of the invention there is provided a screw-shaped titanium anchoring member having a forward lip for permanent anchorage in bone tissue, specifically permanent anchorage of artificial teeth or 2a tooth bridges in the jaw-bone, comprising at least one cavity located on the forward tip of the screw-shaped member, the edges of said at least one cavity on an outer threaded cylindrical surface forming a cutting portion having a cutting tooth with a cutting edge to provide self-tapping when the anchoring member is screwed into a bored hole in the bone tissue and the total volume of said at least one cavity being adapted to contain scraped-off bone tissue material wherein said cutting edge is provided with a clearance surface defined on the outer surface of the anchoring member, which when seen in a cross-section through a cutting part of the anchoring member, is slightly bevelled a short distance behind said threaded cutting edge.
In a second aspect, there is provided a screw-shaped titanium anchoring member for permanent anchorage in bone tissue, comprising: a plurality of cavities located at the forward tip of the member, the edge of each cavity on an outer threaded cylindrical surface of the anchoring member forming a cutting tooth with a cutting edge to provide self-tapping when the anchoring member is screwed into a bored hole in the bone tissue, the total volume of tissue material, wherein the anchoring member on the outer threaded cylindrical surface, a short distance behind each said cutting edge of each said cutting tooth is provided with a clearance surface which, when seen in a cross-section through a cutting part of the anchoring member, is slightly bevelled a short distance behind its respective threaded cutting edge and whereby a distance from the center to the periphery of the anchoring member is larger at each cutting edge than at each clearance surface.
In a preferred embodiment of the invention the clearance is made as a plane surface but it can also be curved.
2b In the following the invention will be described more in detail in connection with the accompanying drawing in which Fig. 1 is a side view of the threaded part of the anchoring member and Fig. 2 a section through the cutting part of the anchoring member.
As illustrated in figure 1 the anchoring member comprises a cylindrical screw 1 (fixture) with an external thread 2. The screw is intended to be inserted in a bored hole in the jaw bone for permanent r~,~_, a :..~_..~~ 23260-4'?0 anchoring of artificial teeth and tooth-bridges. The neck portion of the screw is therefore intended to be attached with a spacer element, coupling element or the like. These elements take no part of this invention, however, and are therefore not described in any detail here. The anchoring member is preferably made of commercially pure titanium with a surface structure according to SE-PS 7902035-0.
The screw has a conical, downwardly tapered part 3 to facilitate the insertion of the screw into the bored hole in the bone tissue. The cone angle at the tip of the fixture is a parameter which effects the cutting properties. A small cone angle at the tip of the fixture has a positive effect with respect to the guiding and engagement of the screw thread into the threaded bore hole, but it has also a negative effect as an essential part of the important load carrying threaded surface then is removed. In the present embodiment the cone angle is in the range of 15~-40~.
The base of the screw is provided with three openings 4 on the cylindrical surface of the screw. The edges 5 of the openings on the cylindrical surface form - sharp cutting edges and the total volume of the openings is big enough to room the scraped-off bone tissue material.
The openings 4 are longitudinal and extend in the longitudinal direction of the screw close to the end surface 6 of the screw. In this way all scraped-off bone tissue material is collected within the cavities and is stored there and the fixture has a plane, unbroken circular bottom surface 6 without any openings. As illustrated in EP 0 237 505 this is an advantage as the collected bone tissue material promotes newly formed bone tissue to grow into the holes and further prevents any tendencies of screwing out the screw after insertion.
The cutting edge 5 comprises a long, straight edge parallel to the longitudinal axis of the screw. In order to obtain a stable insertion of the screw at least three cutting edges are required, which edges are symmetrically arranged about the periphery of .the cylindrical surface of the screw.
In another and more simple method for using a self-tapping fixture the hole in the jaw bone is drilled big enough to allow only the outer part of the threading to contact the bone. This is a risky method, however, as the initial stability of the fixture in the bone is reduced.
The object of the present invention is to provide a self-tapping anchoring member (fixture? with good properties even when installed in hard bone qualities.
According to the invention the good properties have been achieved by providing the anchoring member with a clearance behind the cutting edges, i.e. the outer surface of the anchoring member, seen in a section through the cutting part of he anchoring member, is slightly bevelled behind each cutting edge. By means of such clearance surface the squeezing effect on the anchoring member in the cutting zone when screwed into the bone can be eliminated. This squeezing effect otherwise contributes to a big extent to the torque transmitted o the anchoring member when installed in the bone.
Accordingly, in one aspect of the invention there is provided a screw-shaped titanium anchoring member having a forward lip for permanent anchorage in bone tissue, specifically permanent anchorage of artificial teeth or 2a tooth bridges in the jaw-bone, comprising at least one cavity located on the forward tip of the screw-shaped member, the edges of said at least one cavity on an outer threaded cylindrical surface forming a cutting portion having a cutting tooth with a cutting edge to provide self-tapping when the anchoring member is screwed into a bored hole in the bone tissue and the total volume of said at least one cavity being adapted to contain scraped-off bone tissue material wherein said cutting edge is provided with a clearance surface defined on the outer surface of the anchoring member, which when seen in a cross-section through a cutting part of the anchoring member, is slightly bevelled a short distance behind said threaded cutting edge.
In a second aspect, there is provided a screw-shaped titanium anchoring member for permanent anchorage in bone tissue, comprising: a plurality of cavities located at the forward tip of the member, the edge of each cavity on an outer threaded cylindrical surface of the anchoring member forming a cutting tooth with a cutting edge to provide self-tapping when the anchoring member is screwed into a bored hole in the bone tissue, the total volume of tissue material, wherein the anchoring member on the outer threaded cylindrical surface, a short distance behind each said cutting edge of each said cutting tooth is provided with a clearance surface which, when seen in a cross-section through a cutting part of the anchoring member, is slightly bevelled a short distance behind its respective threaded cutting edge and whereby a distance from the center to the periphery of the anchoring member is larger at each cutting edge than at each clearance surface.
In a preferred embodiment of the invention the clearance is made as a plane surface but it can also be curved.
2b In the following the invention will be described more in detail in connection with the accompanying drawing in which Fig. 1 is a side view of the threaded part of the anchoring member and Fig. 2 a section through the cutting part of the anchoring member.
As illustrated in figure 1 the anchoring member comprises a cylindrical screw 1 (fixture) with an external thread 2. The screw is intended to be inserted in a bored hole in the jaw bone for permanent r~,~_, a :..~_..~~ 23260-4'?0 anchoring of artificial teeth and tooth-bridges. The neck portion of the screw is therefore intended to be attached with a spacer element, coupling element or the like. These elements take no part of this invention, however, and are therefore not described in any detail here. The anchoring member is preferably made of commercially pure titanium with a surface structure according to SE-PS 7902035-0.
The screw has a conical, downwardly tapered part 3 to facilitate the insertion of the screw into the bored hole in the bone tissue. The cone angle at the tip of the fixture is a parameter which effects the cutting properties. A small cone angle at the tip of the fixture has a positive effect with respect to the guiding and engagement of the screw thread into the threaded bore hole, but it has also a negative effect as an essential part of the important load carrying threaded surface then is removed. In the present embodiment the cone angle is in the range of 15~-40~.
The base of the screw is provided with three openings 4 on the cylindrical surface of the screw. The edges 5 of the openings on the cylindrical surface form - sharp cutting edges and the total volume of the openings is big enough to room the scraped-off bone tissue material.
The openings 4 are longitudinal and extend in the longitudinal direction of the screw close to the end surface 6 of the screw. In this way all scraped-off bone tissue material is collected within the cavities and is stored there and the fixture has a plane, unbroken circular bottom surface 6 without any openings. As illustrated in EP 0 237 505 this is an advantage as the collected bone tissue material promotes newly formed bone tissue to grow into the holes and further prevents any tendencies of screwing out the screw after insertion.
The cutting edge 5 comprises a long, straight edge parallel to the longitudinal axis of the screw. In order to obtain a stable insertion of the screw at least three cutting edges are required, which edges are symmetrically arranged about the periphery of .the cylindrical surface of the screw.
is:'~ i'~.~~~ 23260-420 Figure 2 is a sectional view of the screw which shows the form of the three cavities 4. Each cavity 4 is formed by two perpendicular surfaces, a straight, plane surface 7 with a cutting edge 5 and a concave surface 8. As in EP 0 237 505 the cavities are formed so as to provide a positive cutting edge. In order to reduce the cutting forces when installing the fixture, it is important that the cutting angle of the fixture is as large as possible. In contrast to the previously known fixture the present fixture has an additional clearance 9 behind the cutting edge, i.e. the outer surface behind the cutting edge S is slightly bevelled. This means that the distance from the center of the implant screw to the periphery of the screw in the cutting zone has its maximum through the cutting edge part S.
This means that any squeezing effect which might occur when the fixture is screwed into the bone hole can be avoided. Such a squeezing effect could otherwise be an essential contribution to the torsional moment required for installing the screw.
The additional clearance 9 might have different geometrical designs.
It might consist of a straight as well as a curved surface. In the example illustrated in the figures the clearance consists of a straight surface located a short distance behind the cutting edge 5 and is extending to the concave surface 8 in the cavity.
The cutting process can be divided into two stages, the starting process when the fixture is engaged and the rest of the process when the fixture is screwed down into the bone. By means of the clearance 9 and the positive cutting angles on the cutting edge, sufficiently good start and cutting characteristics for the fixture, even for comparatively hard bone qualities, can be achieved.
The invention is not limited to the illustrated embodiment but c;tn be varied within the scope of the accompanying claims.
This means that any squeezing effect which might occur when the fixture is screwed into the bone hole can be avoided. Such a squeezing effect could otherwise be an essential contribution to the torsional moment required for installing the screw.
The additional clearance 9 might have different geometrical designs.
It might consist of a straight as well as a curved surface. In the example illustrated in the figures the clearance consists of a straight surface located a short distance behind the cutting edge 5 and is extending to the concave surface 8 in the cavity.
The cutting process can be divided into two stages, the starting process when the fixture is engaged and the rest of the process when the fixture is screwed down into the bone. By means of the clearance 9 and the positive cutting angles on the cutting edge, sufficiently good start and cutting characteristics for the fixture, even for comparatively hard bone qualities, can be achieved.
The invention is not limited to the illustrated embodiment but c;tn be varied within the scope of the accompanying claims.
Claims (7)
1. A screw-shaped titanium anchoring member having a forward lip for permanent anchorage in bone tissue, specifically permanent anchorage of artificial teeth or tooth bridges in the jaw-bone, comprising at least one cavity located on the forward tip of the screw-shaped member, the edges of said at least one cavity on an outer threaded cylindrical surface forming a cutting portion having a cutting tooth with a cutting edge to provide self-tapping when the anchoring member is screwed into a bored hole in the bone tissue and the total volume of said at least one cavity being adapted to contain scraped-off bone tissue material wherein said cutting edge is provided with a clearance surface defined on the outer surface of the anchoring member, which when seen in a cross-section through a cutting part of the anchoring member, is slightly bevelled a short distance behind said threaded cutting edge.
2. The anchoring member according to claim 1 wherein the clearance surface is a planar surface.
3. The anchoring member according to claim 1 wherein the clearance surface is a curved surface.
4. The anchoring member according to claim 1 wherein said tip is a conical tip having a cone angle of 15°-40°, and wherein said at least one cavity as well as said clearance surface extend down into said conical tip.
5. The anchoring member according to claim 4 wherein an upper threaded portion of the member forms a non-cutting portion and the thread diameter of the non-cutting portion of the member is less than the thread diameter of the cutting portion of the member.
6 6. The anchoring member according to claim 1 wherein three cutting edges and three clearance surfaces are symmetrically distributed about the periphery of the outer cylindrical surface of the anchoring member.
7. A screw-shaped titanium anchoring member for permanent anchorage in bone tissue, comprising:
a plurality of cavities located at the forward tip of the member, the edge of each cavity on an outer threaded cylindrical surface of the anchoring member forming a cutting tooth with a cutting edge to provide self-tapping when the anchoring member is screwed into a bored hole in the bone tissue, the total volume of tissue material, wherein the anchoring member on the outer threaded cylindrical surface, a short distance behind each said cutting edge of each said cutting tooth is provided with a clearance surface which, when seen in a cross-section through a cutting part of the anchoring member, is slightly bevelled a short distance behind its respective threaded cutting edge and whereby a distance from the center to the periphery of the anchoring member is larger at each cutting edge than at each clearance surface.
a plurality of cavities located at the forward tip of the member, the edge of each cavity on an outer threaded cylindrical surface of the anchoring member forming a cutting tooth with a cutting edge to provide self-tapping when the anchoring member is screwed into a bored hole in the bone tissue, the total volume of tissue material, wherein the anchoring member on the outer threaded cylindrical surface, a short distance behind each said cutting edge of each said cutting tooth is provided with a clearance surface which, when seen in a cross-section through a cutting part of the anchoring member, is slightly bevelled a short distance behind its respective threaded cutting edge and whereby a distance from the center to the periphery of the anchoring member is larger at each cutting edge than at each clearance surface.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| SE9102451A SE468154B (en) | 1991-08-27 | 1991-08-27 | SCREW SIZE TITAN MOUNTING FOR PERMANENT ANCHORING IN BONE TISSUE. |
| SE9102451-3 | 1991-08-27 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2076939A1 CA2076939A1 (en) | 1993-02-28 |
| CA2076939C true CA2076939C (en) | 2004-05-25 |
Family
ID=20383547
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002076939A Expired - Fee Related CA2076939C (en) | 1991-08-27 | 1992-08-26 | Anchoring member |
Country Status (10)
| Country | Link |
|---|---|
| US (1) | US5269685A (en) |
| EP (1) | EP0530160B1 (en) |
| JP (1) | JP2627385B2 (en) |
| AT (1) | ATE136207T1 (en) |
| CA (1) | CA2076939C (en) |
| DE (1) | DE69209592T2 (en) |
| DK (1) | DK0530160T3 (en) |
| ES (1) | ES2085612T3 (en) |
| GR (1) | GR3019974T3 (en) |
| SE (1) | SE468154B (en) |
Families Citing this family (58)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5695336A (en) * | 1992-03-03 | 1997-12-09 | Implant Innovations, Inc. | Dental implant fixture for anchorage in cortical bone |
| US5364268A (en) * | 1992-03-03 | 1994-11-15 | Implant Innovations, Inc. | Method for installing a dental implant fixture in cortical bone |
| US5709547A (en) * | 1992-03-03 | 1998-01-20 | Implant Innovations, Inc. | Dental implant for anchorage in cortical bone |
| US5527183A (en) * | 1993-08-18 | 1996-06-18 | Collaborative Enterprises, Inc. | Endosseous implant system |
| US5642996A (en) * | 1993-10-20 | 1997-07-01 | Nikon Corporation | Endosseous implant |
| SE506279C2 (en) * | 1993-12-20 | 1997-12-01 | Nobel Biocare Ab | Screw-shaped fasteners of titanium for permanent anchoring in bone tissue |
| US5816812A (en) * | 1994-07-22 | 1998-10-06 | Osteomed Corporation | Dental implant fixture |
| US5628630A (en) * | 1994-12-15 | 1997-05-13 | Univ. Of Alabama At Birmingham | Design process for skeletal implants to optimize cellular response |
| US5927979A (en) * | 1994-12-15 | 1999-07-27 | Biohorizons Implants Systems, Inc. | Abutment-mount system for dental implants |
| ES2283003T3 (en) * | 1995-07-18 | 2007-10-16 | Implant Innovations, Inc. | DENTAL IMPLANT OF THE SCREW AND SELF-TYPE TYPE. |
| US5727943A (en) * | 1995-07-18 | 1998-03-17 | Implant Innovations, Inc. | Self-tapping, screw-type dental implant |
| JP3881025B2 (en) * | 1996-01-18 | 2007-02-14 | インプラント・イノヴェーションズ・インコーポレーテッド | Low friction screw dental implant |
| SE9600517D0 (en) * | 1996-02-13 | 1996-02-13 | Astra Ab | Screw thread implant |
| SE506596C2 (en) * | 1996-05-17 | 1998-01-19 | Nobel Biocare Ab | Self-tapping anchoring elements for tooth screw ice |
| US5752830A (en) * | 1996-06-20 | 1998-05-19 | Suarez; Omar F. | Removable dental implant |
| US6068480A (en) * | 1996-07-18 | 2000-05-30 | Biohorizons Implant Systems, Inc. | Abutment-mount with square driving surface |
| IT1283471B1 (en) * | 1996-07-19 | 1998-04-21 | Lucia Biemmi | SUBMERSIBLE OR SEMI-SUBMERGED SCREW DENTAL IMPLANT AND RELATIVE DRILL FOR THE PREPARATION OF THE IMPLANT SEAT |
| FR2753368B1 (en) | 1996-09-13 | 1999-01-08 | Chauvin Jean Luc | EXPANSIONAL OSTEOSYNTHESIS CAGE |
| FR2759282B1 (en) * | 1997-02-10 | 1999-05-07 | Eos Medical | BREAKABLE SCREW DEVICE FOR OSTEOSYNTHESIS PLATE OR FOR COAPTATION OF TWO BONE FRAGMENTS |
| US5951287A (en) * | 1997-04-17 | 1999-09-14 | Hawkinson; Roy T. | Dental implant failed fastener recovery systems, devices and methods |
| EP0984737B1 (en) | 1997-05-24 | 2004-09-22 | Straumann Holding AG | Support for sustaining and/or forming a dental prosthesis |
| US5961329A (en) * | 1997-07-02 | 1999-10-05 | Stucki-Mccormick; Suzanne U. | Combination distraction dental implant and method of use |
| WO1999011177A2 (en) * | 1997-09-05 | 1999-03-11 | Deslauriers Richard J | Self-retaining anchor track and method of making and using same |
| US5842865A (en) * | 1997-09-12 | 1998-12-01 | Sulzer Calcitek Inc. | Self-tapping implant with multiple concave tapping channels |
| US5897319A (en) * | 1997-09-12 | 1999-04-27 | Sulzer Calcitek Inc. | Self-tapping implant with helical flutes |
| SE516917C2 (en) | 1997-11-11 | 2002-03-19 | Nobel Biocare Ab | Device for providing reliable anchoring of threaded implants in bone |
| US6048204A (en) | 1998-02-03 | 2000-04-11 | Lifecore Biomedical, Inc. | Self tapping screw type dental implant |
| US6086371A (en) * | 1998-02-05 | 2000-07-11 | Sulzer Orthopedics Inc. | Dental implant delivery system having driver mount with removable flange |
| AU2043799A (en) | 1998-02-05 | 1999-08-23 | Institut Straumann Ag | Endo-osseal dental implant with a self-cutting screw |
| US6076660A (en) * | 1998-02-05 | 2000-06-20 | Sulzer Calcitek Inc. | Vial for dental implant delivery system |
| SE9802571D0 (en) * | 1998-07-17 | 1998-07-17 | Astra Ab | Implant |
| EP0997651A1 (en) * | 1998-10-27 | 2000-05-03 | Chao-Wei Lin | Screw |
| CA2386809C (en) | 1999-10-14 | 2009-06-09 | Robert L. Schroering | Dental implant having a dual-textured exterior surface |
| EP1182986A1 (en) | 2000-01-24 | 2002-03-06 | Chang, ang-Kohn | Dental implant system |
| US6679701B1 (en) * | 2000-03-23 | 2004-01-20 | Gordon D. Blacklock | Anchor having threads opposing unthreading |
| SE523765C2 (en) * | 2000-07-12 | 2004-05-18 | Entific Medical Systems Ab | Screw-shaped anchoring element for permanent anchoring of leg anchored hearing aids and ear or eye prostheses in the skull |
| UA75347C2 (en) * | 2000-09-19 | 2006-04-17 | Assembly of denture carrier | |
| US6382976B1 (en) | 2001-02-05 | 2002-05-07 | Sulzer Dental Inc. | Dental implant having round bottom with fluid directing channels |
| US7160109B2 (en) * | 2001-09-17 | 2007-01-09 | Sulzer Dental Inc. | Torque limiting implant drive system |
| US7137816B2 (en) * | 2001-09-17 | 2006-11-21 | Zimmer Dental Inc. | Impression post and temporary abutment and method of making dental restoration |
| US8651863B2 (en) * | 2003-04-01 | 2014-02-18 | Robert Schroering | Band of connective tissue grooves for use with a dental implant or a separate abutment for a dental implant |
| DE10350424B4 (en) * | 2003-10-29 | 2006-03-30 | Ulrich Gmbh & Co. Kg | bone screw |
| US8277218B2 (en) * | 2005-10-20 | 2012-10-02 | D Alise David D | Screw-type dental implant |
| US9173042B2 (en) * | 2007-07-20 | 2015-10-27 | Cochlear Limited | Bone anchor fixture for a medical prosthesis |
| DE102008063397B4 (en) * | 2008-12-30 | 2019-02-21 | Holger Zipprich | Dental implant screw |
| IL201902A (en) | 2009-11-03 | 2012-12-31 | Ben-Zion Karmon | Dental implant |
| ES2371804B1 (en) * | 2010-06-14 | 2012-08-03 | Juan Manuel Aviñó Bolinches | PERFECTION IN THE OBJECT OF THE PATENT N. P-200902041 SELF-FLOWING AND SELF-THROWING IMPLANT. |
| CN103458822B (en) * | 2011-04-14 | 2016-08-24 | 登士伯Ih有限公司 | Fixator and fixator group |
| EP2931169B1 (en) | 2012-12-11 | 2018-07-18 | Huwais Ip Holding Llc | Condensing implant |
| US9387027B2 (en) | 2012-12-13 | 2016-07-12 | Jonathon Yigal Yahav | Implantable fixture |
| GB2509136A (en) | 2012-12-21 | 2014-06-25 | Nobel Biocare Services Ag | Dental component with metal adapter |
| GB2509138A (en) | 2012-12-21 | 2014-06-25 | Nobel Biocare Services Ag | Dental component with screw fixation |
| GB2509135A (en) | 2012-12-21 | 2014-06-25 | Nobel Biocare Services Ag | An abutment with conical metal adapter |
| US11240613B2 (en) | 2014-01-30 | 2022-02-01 | Cochlear Limited | Bone conduction implant |
| JP6263314B2 (en) | 2014-06-04 | 2018-01-17 | ヴェンツェル スパイン，インコーポレイテッド | Interbody fusion device that expands bilaterally |
| JP6959653B2 (en) | 2016-02-07 | 2021-11-02 | ヒューワイス アイピー ホールディング，エルエルシー | Anchor screw with compression characteristics |
| US11219531B2 (en) | 2019-04-10 | 2022-01-11 | Wenzel Spine, Inc. | Rotatable intervertebral spacing implant |
| US11786343B2 (en) | 2020-07-09 | 2023-10-17 | Southern Implants (Pty) Ltd | Dental implants with stepped threads and systems and methods for making the same |
Family Cites Families (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS597046B2 (en) * | 1979-12-29 | 1984-02-16 | 有限会社新城製作所 | drill screw |
| DE3241963C1 (en) * | 1982-11-12 | 1984-04-26 | Feldmühle AG, 4000 Düsseldorf | Helical jaw implant |
| US4781506A (en) * | 1984-10-05 | 1988-11-01 | W. A. Deutsher Pty. Ltd. | Self-drilling screw |
| US4730969A (en) * | 1985-02-12 | 1988-03-15 | Nisco Inc. | Self-drilling screw |
| SE455155B (en) * | 1986-02-12 | 1988-06-27 | Inst For Tillempad Bioteknolog | SCREW SIZE FASTENER FOR PERMANENT ANCHORING IN BONE TAPE |
| DE3626172A1 (en) * | 1986-08-01 | 1988-02-04 | Precision Fasteners | Self-tapping threaded insert |
| US4713004A (en) * | 1986-09-04 | 1987-12-15 | Vent Plant Corporation | Submergible screw-type dental implant and method of utilization |
| IT1218548B (en) * | 1987-12-04 | 1990-04-19 | Pier Luigi Mondani | SELF-THREADING PIN FOR IMPLANTING DENTAL PROSTHESES |
| DE9002823U1 (en) * | 1989-09-14 | 1990-05-17 | Nobelpharma Ab, Goeteborg, Se | |
| IL94477A0 (en) * | 1990-05-22 | 1991-03-10 | Maarachot Amlach 83 Ltd | Device for performing surgical implants |
-
1991
- 1991-08-27 SE SE9102451A patent/SE468154B/en not_active IP Right Cessation
-
1992
- 1992-07-07 DE DE69209592T patent/DE69209592T2/en not_active Expired - Lifetime
- 1992-07-07 AT AT92850168T patent/ATE136207T1/en active
- 1992-07-07 DK DK92850168.3T patent/DK0530160T3/en active
- 1992-07-07 EP EP92850168A patent/EP0530160B1/en not_active Expired - Lifetime
- 1992-07-07 ES ES92850168T patent/ES2085612T3/en not_active Expired - Lifetime
- 1992-08-21 JP JP4245741A patent/JP2627385B2/en not_active Expired - Fee Related
- 1992-08-26 CA CA002076939A patent/CA2076939C/en not_active Expired - Fee Related
- 1992-08-27 US US07/935,993 patent/US5269685A/en not_active Expired - Lifetime
-
1996
- 1996-05-20 GR GR960401349T patent/GR3019974T3/en unknown
Also Published As
| Publication number | Publication date |
|---|---|
| SE9102451D0 (en) | 1991-08-27 |
| CA2076939A1 (en) | 1993-02-28 |
| GR3019974T3 (en) | 1996-08-31 |
| DE69209592T2 (en) | 1996-09-19 |
| JP2627385B2 (en) | 1997-07-02 |
| JPH05228162A (en) | 1993-09-07 |
| DE69209592D1 (en) | 1996-05-09 |
| DK0530160T3 (en) | 1996-08-05 |
| SE9102451L (en) | 1992-11-16 |
| EP0530160B1 (en) | 1996-04-03 |
| ATE136207T1 (en) | 1996-04-15 |
| US5269685A (en) | 1993-12-14 |
| EP0530160A1 (en) | 1993-03-03 |
| SE468154B (en) | 1992-11-16 |
| ES2085612T3 (en) | 1996-06-01 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2076939C (en) | Anchoring member | |
| US5064425A (en) | Anchoring member for anchorage in bone tissue | |
| US4854873A (en) | Oral implant | |
| US5785525A (en) | Dental implant system | |
| US10398533B2 (en) | Implants for enhanced anchoring within bone | |
| US4624673A (en) | Device system for dental prosthesis fixation to bone | |
| US5427527A (en) | Dental implant method of installation | |
| US4960381A (en) | Screw-type dental implant anchor | |
| US4863383A (en) | self-taping screw-in bone implant for dental purposes | |
| EP0263274B2 (en) | Improved submergible screw-type dental implant | |
| US6227857B1 (en) | Dental and orthopedic implant system | |
| US5816812A (en) | Dental implant fixture | |
| US4932868A (en) | Submergible screw-type dental implant and method of utilization | |
| JP4278305B2 (en) | Implant | |
| CA2093900C (en) | Dental implant having cutting means | |
| US4842518A (en) | Submergible screw-type dental implant and method of utilization | |
| ES2687256T3 (en) | Self-tapping implant | |
| US20150044639A1 (en) | Arrangement for Obtaining Reliable Anchoring of a Threaded Implant in a Bone | |
| US5141435A (en) | Endosseous dental implant assembly | |
| US20110045437A1 (en) | Dental implant | |
| US5772437A (en) | Securing element | |
| US11464605B2 (en) | Dental implant | |
| US20040033469A1 (en) | Dental implant anchor having internal/external wrench engaging means | |
| KR20040081419A (en) | Implant | |
| WO2015186123A1 (en) | Universal implant-to-bone fixation system |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKLA | Lapsed |