Dental implant, implant tool for dental implant, and combination of dental implant and implant tool

Abstract

A dental implant is provided for implantation into the bone tissue of a patient. [Solution] A dental implant 1 for implantation into a patient's bone tissue, the dental implant including a core body 2 having a root apex 4, a crown end and an outer surface extending longitudinally between the root apex and the crown end, and at least one thread 12 extending outward from the core body, wherein cutting grooves 46 are arranged in the threaded region of the implant, and with respect to their position in the longitudinal direction of the implant, the cutting grooves are positioned by movement relative to their adjacent cutting grooves, so that at that position the cutting grooves follow the inclination of the threads.

Description

Technical Field

[0001] The present invention relates to a dental implant, in particular for implantation into a patient's bone tissue, comprising a core having a root tip, a crown end and an outer surface extending longitudinally between the root tip and the crown end, and at least one thread disposed on at least the threaded portion of the outer surface and extending outwardly from the core. The present invention further relates to a dental implant, in particular for implantation into a patient's bone tissue, comprising a core having a root tip and a crown end, the core including a channel that is open with respect to the crown end and extends in the longitudinal direction of the implant from the crown end towards the root tip. The present invention further relates to an implantation tool for implanting a dental implant into a patient's bone tissue. The present invention also relates to a combination of such an implant and such an implantation tool.

Background Art

[0002] Dental implants are widely used in reconstructive treatment to compensate for tooth loss. They are usually implanted into the jawbone at the site of a pulled or missing tooth to hold a prosthetic portion that functions as a dental prosthesis or crown after a healing period of about 4 to 12 weeks. For this purpose, such dental implants are usually constructed as appropriately shaped metal bodies that are implanted into the jawbone or bone tissue by screwing them into the intended location. In principle, the root tip of a dental implant includes a thread, most often a self-drilling thread by which the dental implant is implanted into a prepared implant bed.

[0003] A dental implant may be integrally configured such that, after being implanted into the jawbone, a dental prosthesis directly joins to the implant. As an alternative, in particular to facilitate implantation into the patient's mouth, and in particular to enable a particularly extensive preparation of the prosthesis, for example before fixing it to the implant prior to treatment of the patient in a dental laboratory, the dental implant system may also be of a multi-component configuration. In particular, a generally two-component structure can be provided, and the dental implant system includes a first implant component, referred to as the actual implant or abutment, and in addition thereto, a second implant component associated therewith, referred to as the attachment part or abutment, onto which a tooth prosthesis part, such as a prosthesis, can be attached.

[0004] The outer surface of the actual implant or abutment usually has a thread, which can be designed as a self-drilling thread or as something other than a self-drilling thread. The implant or abutment is usually fixed to a correspondingly prepared implant bed in the jawbone. The thread structure provided in the outer region of the dental implant is usually configured to obtain a higher-order fixation of the arrangement and a uniform transfer of the forces occurring under the chewing load of the dental implant into the jawbone.

[0005] For this purpose, various methods of constructing the thread and the implant body are known from the prior art, especially for high primary fixation after implantation of the implant into the bone tissue. It may be provided to form various thread shapes and combinations thereof, for example different thread types or threads with different thread parameters in different zones of the implant body. It is well known from International Patent Application No. WO2008 / 128757A2 that implants of the above type are characterized by additional helical grooves on the outer surface of each thread and / or on the implant body directly between two adjacent threads. In other systems, compression-type threads may be provided, which are characterized by narrow grooves. High primary fixation can also be achieved by making the holes drilled into the patient's bone at the site where the implant is provided smaller than normal. As a result, when the implant is screwed into the core of the implant together with the threads provided thereon, the surrounding bone material is compressed. However, too strong compression may create blood vessels during bone destruction, thereby preventing the recovery of the bone after implantation.

[0006] Another broad objective in the special design of the implant and the threads provided thereon is so-called secondary fixation or osseointegration, which is the regeneration of bone material in direct contact with the implant surface.

[0007] U.S. Patent No. 2007 / 0190491A1 discloses an implant design with a non-circular cross-sectional shape of the implant body. In this design, most natural teeth have a non-circular cross-section, and thus a similar cross-sectional structure of the implant body is recognized as being likely to fit well with the natural position of the blood vessels in the bone tissue, and as a result, to assist in good and rapid osseointegration.

[0008] Dental implants such as those described above are generally implanted into a patient's bone tissue by an implant tool (e.g., an implant driver). For this purpose, the distal portion of the implant tool is introduced into a socket provided in the crown portion of the implant. This distal portion cooperates with the implant socket such that the implant is screwed into the bone tissue in response to rotation of the implant tool about its longitudinal axis. To achieve a secure and accurate placement of the implant in the bone tissue, the implant tool must be fully fixed to, i.e., fully engaged with, the implant. Any mismatch or misalignment between the implant tool and the dental implant can complicate the implantation of the implant into the bone tissue and can cause a risk of improper placement of the implant.

[0009] Furthermore, the implant tool may be used to pick up the implant and transport it to an implantation site where it is to be implanted into the bone tissue. In this case, if a mismatch or misalignment occurs between the tool and the implant, the implant may fall out of the implant tool before it reaches the desired location. Such an event can also pose a significant risk to the patient's health if the implant is swallowed or aspirated.

[0010] To achieve a friction fit between the implant tool and the implant, U.S. Patent No. 7,131,840 B2 teaches the use of an O-ring at the distal portion of the implant driver. However, with the configuration taught in this specification, it cannot be reliably determined whether the implant tool and the implant fit properly together or not by the clinician.

[0011] Another method of improving the connection between the implant tool and the implant using a retention portion for connecting the implant tool to the implant is disclosed in U.S. Patent No. 8,864,494 B2. After the implant has been implanted into the bone tissue, the retention portion must be removed from the implant. Thus, this method requires the use of an additional dental element in the form of the retention portion, which requires an additional step for the clinician and as a result complicates and burdens the implant implantation procedure.

[0012] Accordingly, there remains a need for a reliable, efficient, and simple method for attaching an implant tool (e.g., an implant driver) to a dental implant. It provides a clear indication as to whether the implant tool and the dental implant are properly attached to each other.

[0013] Furthermore, there remains a need for an implant tool that provides for secure implantation of the implant into bone tissue while minimizing the risk of damage or breakage to the implant, particularly its socket.

[0014] There also remains a need for a dental implant that provides for secure implantation into bone tissue while minimizing the risk of damage or breakage to the implant, particularly its socket or channel.

[0015] As described above, dental implants are typically implanted into a patient's jawbone or bone tissue by screwing them into the intended location. For this purpose, the root tip of a dental implant typically includes a self-tapping thread by which the dental implant is screwed into an implant bed that has been correspondingly prepared.

[0016] The thread plays an important role in ensuring the secure and accurate placement and fitting of the implant into the jawbone or bone tissue. In particular, the thread must enable the smooth and accurate implantation of the implant into the jawbone or bone tissue and ensure a stable fit between the implant and the jawbone or bone tissue after implantation.

[0017] For this purpose, International Patent Application No. WO2016 / 125171 teaches the use of a screw-shaped dental implant having a recess in the root tip surface of the thread that extends proximally toward the crown surface of the thread. However, in the configuration disclosed in this specification, it provides improved implant placement and stability only for a limited range of thread angles, i.e., thread angles greater than about 15 degrees. Therefore, there remains a need for a dental implant that enables reliable and accurate placement and fitting in jawbone or bone tissue, particularly at a wide variety of implant thread angles, especially small thread angles.

SUMMARY OF THE INVENTION

[0018] In view of these aspects as described above, it is an object of the present invention to provide excellent characteristics for dental implants of the type described above with respect to primary and secondary fixation. It is a further object of the present invention to provide reliable embedding in bone tissue while minimizing the risk of damage or breakage of the implant, particularly its socket or channel. Furthermore, the present invention aims to provide a dental implant that enables reliable and accurate placement and fitting in jawbone or bone tissue, particularly at a wide variety of implant thread angles, especially small thread angles.

[0019] Furthermore, it is an object of the present invention to provide an implant tool for implanting a dental implant into a patient's bone tissue that efficiently provides a reliable indication of whether the implant tool and the dental implant are properly attached to each other. The present invention also aims to provide an implant tool for implanting a dental implant into a patient's bone tissue that enables reliable implantation while minimizing the risk of damage or breakage of the implant, particularly its socket or channel. The present invention also provides a combination of such an implant tool and a dental implant.

[0020] These objects are achieved by a dental implant having the technical features of claim 1, by a dental implant having the technical features of claim 4, by a dental implant having the technical features of claim 8, by a dental implant having the technical features of claim 24, by a dental implant having the technical features of claim 32, by an implant tool having the technical features of claim 41, by an implant tool having the technical features of claim 42, by an implant tool having the technical features of claim 43, and by a combination with the technical features of claim 54. Preferred embodiments of the present invention are obtained from the dependent claims. Specifically, according to the present invention, the following configurations [1] to

[54] are provided. [1] A dental implant (1) especially for implantation into a patient's bone tissue, wherein the dental implant (1) has - a core body (2) having a root tip (4), a crown end (6) and an outer surface (8) extending longitudinally between the root tip (4) and the crown end (6); - at least one thread (12) extending outwardly from the core body (2); and - a specific implant volume defined by the core body (2) or by a thread outer volume (28) defined by the thread (12), the cross-section of the specific implant volume being characterized by an eccentricity parameter defined as the ratio of the maximum distance from the center of this cross-section to the contour of this cross-section to the minimum distance from the center of this cross-section to the contour of this cross-section for each value of a parameter specific to the longitudinal coordinates of the implant; wherein the specific volume has - at least one crown zone, wherein the eccentricity parameter has a maximum, preferably constant value, and the crown zone extends along the longitudinal axis of the implant over a length of at least 10% of the total length of the implant; - at least one apical zone, where the eccentricity parameter has a minimum, preferably constant value, and the apical zone extends along the longitudinal axis of the implant over a length of at least 30% of the total length of the implant; and - at least one transition zone disposed between the crown zone and the apical zone, where the eccentricity parameter varies continuously, preferably linearly, as a function of a parameter characteristic of the longitudinal coordinate, from a minimum value adjacent to the apical zone to a maximum value adjacent to the crown zone, and the transition zone extends along the longitudinal axis of the implant over a length of at least 10% of the total length of the implant; a dental implant (1) comprising. [2] The dental implant (1) according to [1], wherein in the apical zone, the cross-section of the specific implant volume has a substantially circular shape. [3] The dental implant (1) according to any one of [1], [2], wherein in the crown zone and / or the shaping zone, the cross-section of the specific implant volume has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour has a relative maximum value, and thus a higher value than the adjacent azimuth. [4] A dental implant (1) especially for implantation into a patient's bone tissue, wherein the dental implant (1) is - a core (2) having a root tip (4), a crown end (6) and an outer surface (8) extending longitudinally between the root tip (4) and the crown end (6); and - at least one thread (12) extending outwardly from the core (2); comprising The core (2) is - a first core shaping zone (22), wherein in the first core shaping zone (22), the cross-section of the core (2) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center (50) of the cross-section and its outer contour has a relative maximum value, and thus a higher value than the adjacent azimuth; a first core shaping zone (22); - A core circular zone (20), wherein in the core circular zone (20), the cross-section of the core body (2) is basically formed into a circular shape; and - A core transition zone (26) disposed between the core forming zone (22) and the core circular zone (20), wherein in the core transition zone (26), the cross-sectional shape of the core body (2) changes continuously from a basically circular shape adjacent to the core circular zone (20) to the shape of the cross-section of the core body (2) corresponding to the cross-sectional shape of the core forming zone (22) as a function of parameters specific to the longitudinal coordinate. The dental implant (1) includes the core transition zone (26). [5] For each value of the parameter specific to the longitudinal coordinate, the dental implant (1) according to [3], wherein the cross-section of the core body (2) is characterized by an eccentricity parameter defined as the ratio of the maximum radius of this cross-section to its minimum radius. [6] In particular, the dental implant (1) according to [3], especially for implantation into a patient's bone tissue, wherein the dental implant (1) - A core body (2) having a root tip (4), a crown end (6), and an outer surface (8) extending longitudinally between the root tip (4) and the crown end (6); and - At least one thread (12) extending outwardly from the core body (2); including The core body (2) is - A first core forming zone (22), wherein in the first core forming zone (22), the cross-section of the core body (2) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center (50) of the cross-section and its outer contour reaches a relative maximum value, and thus a higher value than the adjacent azimuth. The first core forming zone (22); - A core circular zone (20), wherein in the core circular zone (20), the cross-section of the core body (2) is basically formed into a circular shape; and - A second core forming zone (26'), wherein in the second core forming zone (26'), the cross-section of the core body (2) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center (50) of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth, the second core forming zone (26'); is included, A dental implant (1) in which the core eccentricity parameter defined as the ratio of the maximum radius of the cross-section of the core body (2) to its minimum radius in the first core forming zone (22) is larger than that in the second core forming zone (26'). [7] The dental implant (1) according to any one of [1] to [3], wherein the core circular zone (20) is arranged adjacent to the root tip (4) when viewed in the longitudinal direction. [8] In particular, the dental implant (1) according to any one of [1] to [4], especially for implantation into a patient's bone tissue, wherein the dental implant (1) - A core body (2) having a root tip (4), a crown end (6), and an outer surface (8) extending longitudinally between the root tip (4) and the crown end (6); and - At least one thread (12) extending outward from the core body (2), wherein the thread (12) defines a thread outer volume (28), the thread (12); is included, The thread (12) is - A first thread forming zone (30), wherein in the thread forming zone (30), the outer cross-section of the thread outer volume (28) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth, the thread forming zone (30); - Preferably a thread circular zone (32) adjacent to the root tip (4), wherein in the thread circular zone (32), the outer cross-section of the thread outer volume (28) is basically formed into a circular shape, the thread circular zone (32); and - A thread transition zone (34) disposed between the thread forming zone (30) and the thread circular zone (32), wherein in the thread transition zone (34), the outer cross-sectional shape of the thread outer volume (28) is a function of parameters specific to the longitudinal coordinate, continuously changing from a basically circular shape adjacent to the thread circular zone (32) to the shape of the outer cross-section of the thread outer volume (28) corresponding to the outer cross-sectional shape of the thread forming zone (30); a dental implant (1) including the thread transition zone (34). [9] For each value of the parameter specific to the longitudinal coordinate, the dental implant (1) according to [4], wherein the outer cross-section of the thread outer volume (28) is characterized by a thread eccentricity parameter defined as the ratio of the maximum radius of this outer cross-section to its minimum radius.

[10] In particular, a dental implant (1) according to any one of [1] to [9], especially for implantation into a patient's bone tissue, the dental implant (1) being - A core body (2) having a root tip (4), a crown end (6), and an outer surface (8) extending longitudinally between the root tip (4) and the crown end (6); and - At least one thread (12) extending outwardly from the core body (2), the thread (12) defining a thread outer volume (28), including the thread (12); The thread (12) is - A first thread forming zone (30), wherein in the first thread forming zone (30), the outer cross-section of the thread outer volume (28) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus a higher value than the adjacent azimuth; the first thread forming zone (30); - Preferably, a thread circular zone (32) adjacent to the root tip (4), wherein in the thread circular zone (32), the outer cross-section of the thread outer volume (28) is basically circularly formed; the thread circular zone (32); and - A second thread forming zone (34'), wherein in the second thread forming zone (34'), the outer cross-section of the thread outer volume (28) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth, the second thread forming zone (34'); is included, A dental implant (1) in which a core eccentricity parameter defined as the ratio of the maximum radius of the outer cross-section of the thread outer volume (28) to its minimum radius in the first thread forming zone (30) is larger than that in the second thread forming zone (34').

[11] The dental implant (1) according to any one of [4] to

[10] , wherein the core forming zone (22) and / or the thread forming zone (30) is a top platform zone (24) adjacent to the crown end (6).

[12] The dental implant (1) according to any one of [3] to

[10] , wherein the main directions are symmetrically arranged with respect to the longitudinal central axis (64) of the core body (2).

[13] The dental implant (1) according to any one of [3] to

[11] , wherein the outer contour of the thread outer volume (28) conforms to the outer contour of the core body (2) with respect to the longitudinal central axis of the core body (2) and with respect to the maximum or minimum value.

[14] The dental implant (1) according to any one of [3] to

[12] , wherein at least a part of the core body (2) in the core forming zone (22) and / or the transition zone (26) has a triangular elliptical cross-section.

[15] The dental implant (1) according to any one of [1] to

[14] , wherein the core body (2) in the transition zone (26) preferably has a tapered shape with a conical angle in the range of 1 degree to 12 degrees.

[16] The dental implant (1) according to any one of [1] to

[15] , wherein the transition zone (26) starts at a distance of about 2 to 4 mm from the root tip (4) as viewed in the longitudinal direction.

[17] The dental implant (1) according to any one of [1] to

[16] , wherein the thread (12) is a flat thread.

[18] The dental implant (1) according to

[14] , wherein the free width (58) of the flat thread is dependent on the coordinate parameter in the longitudinal direction and continuously increases with the increase in the distance from the root tip (4) of the core (2) starting from the root tip (4) of the core (2).

[19] The dental implant (1) according to any one of [1] to

[18] , wherein a plurality of cutting grooves (46) are provided in at least one of the transition zones (26).

[20] The dental implant (1) according to

[16] , wherein the number of the cutting grooves (46) is equal to the number in the main direction.

[21] The dental implant (1) according to any one of [1] to

[20] , wherein the cutting grooves (46) are symmetrically arranged with respect to the longitudinal central axis of the core (2).

[22] The dental implant (1) according to any one of

[19] to

[21] , wherein each of the cutting grooves (46) is arranged with a given rotational deviation with respect to adjacent main directions when viewed in the orientation direction around the longitudinal central axis of the core (2).

[23] The core (2) includes a channel (10) that opens toward the crown end (6) and extends along the longitudinal direction of the implant (1) from the crown end (6) toward the root tip (4), and the core (2) has a drive zone, in which the cross-section of the channel (10) perpendicular to the longitudinal direction of the implant (1) has a plurality of radial protrusions arranged along the circumference of the cross-section, where each of the radially outermost points of the radial protrusions is on a corresponding circle around the center (50) of the cross-section, and at least two of these circles have different radii. The dental implant (1) according to any one of [1] to

[22] .

[24] A dental implant (201) particularly for implantation into a patient's bone tissue, wherein the dental implant (201) includes - a core (205) having a root tip (207) and a crown end (209), The core body (205) includes a channel (236) that opens with respect to the crown end (209) and extends along the longitudinal direction of the implant (201) from the crown end (209) toward the root tip (207), and the core body (205) has a driving zone (242), in which the cross-section of the channel (236) perpendicular to the longitudinal direction of the implant (201) has a plurality of radial protrusions arranged along the circumference of the cross-section, where each of the radially outermost points of the radial protrusions is on a corresponding circle around the center of the cross-section, and at least two of these circles have different radii, dental implant (201).

[25] The core body (205) further has a driving part (240), in which the cross-section of the channel (236) perpendicular to the longitudinal direction of the implant (201) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus a value higher than that of adjacent orientations, the dental implant (201) according to

[23] or

[24] .

[26] The driving zone (242) is arranged at the top end of the driving part (240), the dental implant (201) according to

[25] .

[27] The driving part (240) has a tapered shape, and as a result, in the driving part (240), the lateral dimension of the cross-section of the channel (236) perpendicular to the longitudinal direction of the implant (201) decreases along the direction from the crown end (209) toward the root tip (207), the dental implant (201) according to

[25] or

[26] .

[28] The number of the main directions is three or more, the dental implant (201) according to any one of

[25] to

[26] .

[29] The radially innermost points of the radial recesses are on a single circle around the center of the cross-section, the dental implant (201) according to any one of

[23] to

[28] .

[30] The radial protrusions include a first radial protrusion and a second radial protrusion, The outermost radial point of the first radial protrusion is on a single first circle around the center of the cross-section, The outermost radial point of the second radial protrusion is on a single second circle around the center of the cross-section, The second circle has a smaller radius than the first circle, and The first radial protrusion and the second radial protrusion, together with the corresponding radial recesses disposed therebetween, are alternately arranged along the circumference of the cross-section, the dental implant (201) according to any one of

[23] to

[29] .

[31] The core body (205) has an outer surface extending along the longitudinal direction of the implant (201) between the root tip (207) and the crown end (209), The implant (201) further includes at least one thread (203) extending outward from the core body (205), The thread (203) has a root tip surface facing the root tip (207) of the core body (205) and a crown surface facing the crown end (209) of the core body (205), The thread (203) has a longitudinal groove formed therein, the longitudinal groove extending from the root tip of the thread (203) toward the crown end of the thread (203), and The thread (203) has a recess formed in its crown surface at its root tip, the recess extending in a direction from the crown surface toward the root tip surface along a part of the thickness of the thread (203), the recess being open to the longitudinal groove, the dental implant (201) according to any one of

[23] to

[30] .

[32] A dental implant (401) particularly for implantation into a patient's bone tissue, the dental implant (401) comprising: - A core body (402) having a root tip (404), a crown end (406), and an outer surface (408) extending along the longitudinal direction of the implant (401) between the root tip (404) and the crown end (406); and, - At least one thread (412) extending outward from the core body (402); The thread (412) has a root tip surface (414) facing the root tip (404) of the core (402) and a crown surface (416) facing the crown end (406) of the core (402). The thread (412) has a longitudinal groove (418) formed therein, the longitudinal groove (418) extending from the root tip of the thread (412) towards the crown end of the thread (412), and The thread (412) has, at its root tip portion, a recess (420) formed in its crown surface (416), the recess 420 extending in a direction from the crown surface (416) towards the root tip surface (414) along a part of the thickness of the thread (412), the recess (420) being open to the longitudinal groove (418), dental implant (401).

[33] The dental implant (401) according to

[31] or

[32] , wherein the recess (420) extends in a direction from the crown surface (416) towards the root tip surface (414) along 20% to 90% of the thickness of the thread (412).

[34] The dental implant (401) according to any one of

[31] to

[33] , wherein the extension of the recess (420) in the direction from the crown surface (416) towards the root tip surface (414) decreases along the direction away from the longitudinal groove (418) in the circumferential direction where the recess (420) is open.

[35] The dental implant (401) according to any one of

[31] to

[34] , wherein the recess (420) extends over 50% to 90% of the width of the thread (412) in the width direction of the recess (420).

[36] The dental implant (401) according to any one of

[28] to

[32] , wherein the recess (420) is formed in the crown surface (416) of the thread (412) by a complete rotation at the most root tip of the thread (412).

[37] The dental implant (401) according to any one of

[31] to

[34] , wherein the thread angle is 15 degrees or less.

[38] The crown surface (100) of the implant (1'''') has a wavy contour with highest and lowest points of the crown surface (100) arranged alternately along the circumference of the crown end (6) of the implant (1''''). Also, At the highest point of the crown surface (100), the crown end (6) of the implant (1'''') has a tapered shape, such that the transverse dimension of the cross-section of the crown end (6) perpendicular to the longitudinal direction of the implant (1'''') decreases along the direction from the root tip (4) of the implant (1'''') towards the crown end (6) of the implant (1''''). The dental implant (1'''') according to any one of [1] to

[37] .

[39] The core body (502) includes a channel (510) that opens towards the crown end (506) and extends along the longitudinal direction of the implant (501) from the crown end (506) towards the root tip (504). Also, the channel (510) includes a conical portion (514). The dental implant (501) according to any one of [1] to

[38] .

[40] The conical portion (514) is arranged to extend from the crown end (506) of the implant (501) along the longitudinal direction of the implant (501). The dental implant (501) according to

[36] .

[41] An implant tool (200) for implanting a dental implant, in particular the dental implant (1, 201, 401) according to any one of [1] to

[40] , into a patient's bone tissue, The implant tool (200) includes a proximal portion (202) and a distal portion (204), and the distal portion (204) is for cooperating with the implant (1, 201, 401). The distal portion (204) has a holding element (206). The holding element (206) includes an attachment portion (208) for attaching the implant tool (200) to the dental implant (1, 201, 401). The holding element (206) is at least elastically deformable in all directions perpendicular to the longitudinal direction of the implant tool (200), and The implant tool (200) wherein the attachment portion (208) includes at least one protrusion (210) extending in one or more directions substantially perpendicular to the longitudinal direction of the implant tool (200).

[42] An implant tool (200) for implanting a dental implant into a patient's bone tissue, in particular the dental implant (1, 201, 401) according to any one of [1] to

[40] , The implant tool (200) includes a proximal portion (202) and a distal portion (204), the distal portion (204) being for cooperating with the implant (1, 201, 401), and The distal portion (204) has a drive region (214), in the drive region (214), the cross-section of the distal portion (204) perpendicular to the longitudinal direction of the implant tool (200) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour becomes a relative maximum value, and thus becomes a higher value than the adjacent azimuths. The implant tool (200).

[43] An implant tool (200) for implanting a dental implant into a patient's bone tissue, in particular the dental implant (1, 201, 401) according to any one of [1] to

[40] , The implant tool (200) includes a proximal portion (202) and a distal portion (204), the distal portion (204) being for cooperating with the implant (1, 201, 401), and The distal portion (204) has a drive section (216), in the drive section (216), the cross-section of the distal portion (204) perpendicular to the longitudinal direction of the implant tool (200) has a plurality of radially convex portions (218) and a plurality of radially concave portions (220) arranged alternately along the circumference of the cross-section, where each of the radially outermost points (222, 224) of the radially convex portions (218) is in a corresponding circle around the center of the cross-section, and at least two of these circles have different radii from each other. The implant tool (200).

[44] The distal portion (204) further has a drive region (214), and in the drive region (214), the cross-section of the distal portion (204) perpendicular to the longitudinal direction of the implant tool (200) has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth. The implant tool (200) according to

[41] .

[45] The drive region (214) has a tapered shape, and as a result, in the drive region (214), the transverse dimension of the cross-section of the distal portion (204) perpendicular to the longitudinal direction of the implant tool (200) decreases along the direction from the proximal end of the implant tool (200) to the distal end of the implant tool (200). The implant tool (200) according to

[42] or

[44] .

[46] The number of main directions is three or more. The implant tool (200) according to any one of

[42] ,

[44] , and

[45] .

[47] The distal portion (204) further has a drive section (216), and in the drive section (216), the cross-section of the distal portion (204) perpendicular to the longitudinal direction of the implant tool (200) has a plurality of radially projecting portions (218) and a plurality of radially recessed portions (220) that are alternately arranged along the circumference of the cross-section, where each of the radially outermost points (222, 224) of the radially projecting portions (218) is on a corresponding circle around the center of the cross-section, and at least two of these circles have different radii from each other. The implant tool (200) according to any one of

[41] and

[44] to

[46] .

[48] The drive section (216), the holding element (206), and the drive region (214) are arranged in this order in the direction from the distal end of the implant tool (200) to the proximal end of the implant tool (200). The implant tool (200) according to

[47] which is dependent on any one of

[41] to

[43] .

[49] The distal portion (204) further has a drive section (216), and in the drive section (216), the cross-section of the distal portion (204) perpendicular to the longitudinal direction of the implant tool (200) has a plurality of radially projecting portions (218) and a plurality of radially recessed portions (220) that are alternately arranged along the circumference of the cross-section, where each of the radially outermost points (222, 224) of the radially projecting portions (218) is on a corresponding circle around the center of the cross-section, and at least two of these circles have different radii, the implant tool (200) according to any one of

[42] ,

[45] , and

[46] .

[50] The implant tool (200) consists of two separable parts (230, 232), which are attached to each other, in particular removably attached to each other, the implant tool (200) according to any one of

[41] to

[49] .

[51] One of the two separable parts (230) includes the drive section (216), and the other of the two separable parts (232) includes the holding element (206) and the drive region (214), the implant tool (200) according to

[50] dependent on

[47] or

[45] .

[52] The holding element (206) has at least one notch extending from the distal end to the proximal end of the holding element (206), the implant tool (200) according to any one of

[41] and

[44] to

[51] .

[53] The holding element (206) is a hollow body, and the at least one notch penetrates the outer wall of the holding element (206), the implant tool (200) according to

[52] .

[54] A combination of a dental implant (1, 201, 401) according to any one of [1] to

[40] and an implant tool (200) according to any one of

[41] to

[53] .

[0021] According to the present invention, in an embodiment, the object is - A core body (2) having a root tip (4), a crown end (6), and an outer surface (8) extending longitudinally between the root tip (4) and the crown end (6); - at least one thread (12) extending outwardly from the core body (2); and - a specific implant volume defined by the core body (2) or by the thread outer volume (28) defined by the thread (12); which is achieved, in particular, by a dental implant (1) for implantation into a patient's bone tissue. Therein, for each value of a parameter specific to the longitudinal coordinate of the implant, the cross-section of the specific implant volume is characterized by an eccentricity parameter defined as the ratio of the maximum distance from the center of this cross-section to the contour of this cross-section to the minimum distance from the center of this cross-section to the contour of this cross-section. The specific volume is - at least one crown zone, in which the eccentricity parameter has a maximum, preferably constant value, and the crown zone extends along the longitudinal axis of the implant over a length of the crown zone of at least 10% of the total length of the implant; - at least one root tip zone, in which the eccentricity parameter has a minimum, preferably constant value, and the root tip zone extends along the longitudinal axis of the implant over a length of the root tip zone of at least 30% of the total length of the implant; and at least one transition zone arranged between the crown zone and the root tip zone, in which the eccentricity parameter varies continuously, preferably linearly, as a function of a parameter specific to the longitudinal coordinate, from the minimum value adjacent to the root tip zone to the maximum value adjacent to the crown zone, and the transition zone extends along the longitudinal axis of the implant over a length of the transition zone of at least 10% of the total length of the implant, including a transition zone.

[0022] In other words, in the present embodiment, the implant defined by the core body or the outer thread volume thereof includes at least three functional parts, each of which has a specific minimum functional length to provide the assigned function. The first of these functional zones or parts is the crown zone where the core body and / or the outer thread volume has a specific eccentricity in its shape, with many maximum and minimum values in the radius as shown in the cross-section. The second functional zone or part is the root tip zone where the core body or the outer thread volume has a minimum eccentricity distance, preferably a substantially circular cross-section. The third functional zone located between the first and second zones is a transition zone (and thus cross-sectionally symmetric) that provides a smooth transition of the eccentricity distance over its length between the first and second zones. This design facilitates the smooth and easy implantation of the implant into the bone material due to the low eccentricity, preferably the uniform circular cross-section of the implant at the tip of its root. In contrast, at the final stage of implantation, when the implant is deeply fixed in the bone material, due to its eccentricity, the relatively high eccentricity crown zone of the implant provides alternating compression and relaxation periods to the surrounding bone material when being screwed in. Similarly, the transition zone provides a highly desirable smooth transition and thus a smooth increase in the alternating compression / relaxation periods of the bone material during implantation.

[0023] In a preferred embodiment, at the eccentric part, the implant is designed for particularly smooth vibrations during the compression and relaxation phases of the bone material when being screwed in. For this purpose, in a preferred embodiment of the crown zone and / or the shaping zone and / or the transition zone, the cross-section of the specific implant volume has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus a value higher than that of the adjacent azimuth. According to the present invention, in one embodiment, this object is achieved by design, including that the core of the implant includes at least a first core zone, particularly designed as a shaped core zone. In the first core zone, the cross-section of the core has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus a value higher than that of the adjacent azimuth. Further, in this embodiment, the core includes a second core zone, particularly a circular core zone. In the second zone, the cross-section of the core is basically circular, and it is a transition zone arranged between the first shaping zone and the second circular zone when viewed in the longitudinal direction of the implant. In the transition zone, the cross-sectional shape of the core changes from a basically circular shape adjacent to the second circular zone as a function of parameters specific to the longitudinal coordinate to a shape corresponding to the cross-sectional shape of the first or shaping zone, particularly with respect to the general shape of the cross-section and / or the value of its specific parameters.

[0024] In other words, the dental implant according to the present invention includes a circular zone having a circular or substantially circular cross-section, and in a preferred embodiment, it is arranged close to or adjacent to the tooth root tip of the implant. In this context and further in the following content, "substantially circular" defines a shape that is close to a highly circular shape, allowing for minimal distortion or deviation, such as a slight eccentricity, due to tolerances etc. This circular zone resulting from its cross-sectional circularity enables a relatively easy fit between the thread and the bone material without applying excessive stress to the bone tissue during the first time when the implant is screwed into the bone material. In contrast, in another zone of the implant, in a preferred embodiment arranged closer to the central region of the implant or near the other end of the implant, the core is designed to have a non-circular cross-section characterized by many rounded protrusions or maxima of the radius. In this region, when the implant body is screwed into the bone tissue, the compressive force applied to the bone tissue varies in an oscillating manner between a maximum compression when the local radius of the cross-section is at its maximum (due to the rotational movement of the implant body) and a minimum compression when the local radius of the cross-section is at its minimum. Particularly in the apical zone characterized by relatively hard bone tissue, after implantation, this shaped contour characterized by minima results in a region of low bone stress near the minimum value, thereby enabling enhanced regeneration of the bone material and significantly minimizing the adverse effects of overly strong compression on blood vessels.

[0025] To enable a smooth and useful transition between two different ones of these zones, the implant according to the invention provides an additional zone of the core body located between a pair of one circular zone and one non-circular zone. This transition zone has a temporary cross-section (seen in the longitudinal direction) that varies from a circular cross-section that conforms to the cross-section of each circular zone in the area proximate to each circular zone, to a cross-section with a non-circular protrusion that conforms to the cross-section of each non-circular zone in the area proximate to this zone. Due to this transition zone, an immediate and sudden change in shape, a shearing effect on the bone tissue, and other damaging effects on the bone tissue can be avoided. In combination, and particularly in the preferred embodiment where the circular zone is disposed adjacent to or near the tooth root tip of the implant, the implant thus provides a relatively simple fit between the first-stage bone tissue and the threads that can be screwed in by the oscillatory compression effect on the bone tissue at a subsequent stage.

[0026] In an alternative embodiment of the invention, a similar or equivalent effect can be achieved by a design of the core body in which the transition between the circular zone and the shaped zone is carried out stepwise. This alternative embodiment is thus considered to be inventive and may be used according to or in combination with the invention separated from the first embodiment.

[0027] In this alternative embodiment of the invention, the object made clear above is achieved by a design in which the implant core includes at least a first shaped core zone. In the first shaped core zone, the cross-section of the core has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth. Further in this embodiment, the core includes a second core zone, in particular a circular core zone. In the second zone, the cross-section of the core is basically circular, and in a preferred embodiment, it is arranged close to or near the root tip of the implant and the second core shaping zone. In the second core shaping zone, the cross-section of the core has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth. The core eccentricity parameter defined as the ratio of the maximum radius to the minimum radius of the cross-section of the core in the first core shaping zone is larger than that in the second core shaping zone. In other words, in this embodiment, the transition from a basically circular or round shape to a shaped or non-circular shape can be carried out step by step by providing two or more non-circular shaping zones with different eccentricity parameters.

[0028] In yet another alternative embodiment of the invention, a similar or equivalent effect can be achieved by a design of the outer contour of the thread similar to one or both of the designs of the core described above. This alternative embodiment is thus considered to be innovative and may be used according to or in combination with the invention separated from the first embodiment.

[0029] For the sake of special explanation, the outer contour of the thread can be described using the outer volume or the envelope volume defined by the thread. In this alternative embodiment of the invention, the object revealed above is achieved by design, where the thread of the implant includes a first thread zone, which is designed especially as a first thread forming zone. In the first thread forming zone, the outer volume surrounding the thread has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth. Further, in this embodiment, the thread includes a thread circular zone, and in a preferred embodiment, it is arranged adjacent to the root tip of the implant. In the thread circular zone, the cross-section of the outer surface surrounding volume is basically circular, and it is a transition zone arranged between the first forming zone and the circular zone when viewed in the longitudinal direction of the implant. In the transition zone, the cross-sectional shape of the outer volume surrounding the thread changes from a basically circular shape adjacent to the thread circular zone to a shape corresponding to the cross-sectional shape of the first forming zone, as a function of parameters specific to the longitudinal coordinate, especially with respect to the general shape of the cross-section and / or the value of its specific parameters. As another or further alternative, a stepwise transition can also be provided by providing a second thread forming zone with an eccentricity different from that of the first thread forming zone.

[0030] Advantageous embodiments of the invention are the subject of the dependent claims.

[0031] In a preferred embodiment, the first or shaping zone of the core body and / or the thread is configured as a top platform zone and is arranged adjacent to the crown end of the implant. In particular, the top platform zone may be designed to connect directly to a dental prosthesis, i.e., for an integral type of implant, or to connect directly to an abutment holding the dental prosthesis, i.e., for a two-piece or multi-piece type of implant. In a further preferred embodiment, which is considered an independent invention in itself, the formed top platform zone provided by the outer contour of the core body and / or the thread has a length of at least 2.5 mm, preferably at least 3 mm, as seen in the longitudinal direction of the implant. Surprisingly, the shaped non-circular zone induces a minimal or reduced stress in the bone tissue compared to the circular-shaped contour, resulting in less cell death and less bone remodeling after implantation of the implant, rapid bone attachment and improved conservation of the important bone structures defined by the top plate, the buccal wall and the lingual wall. As a result, the regeneration of bone material and, furthermore, osseointegration are significantly improved by providing a minimum of the shaping zone in the region of the important bone structures. For the purpose of osseointegration, it is considered very useful to provide these effects in the uppermost layer of the top plate of at least 2.5 mm or preferably at least 3 mm.

[0032] The cross-section of the outer volume surrounding the core body and / or the thread can be characterized by an eccentricity parameter specific to the deviation of each cross-section from the circular shape. For the purposes of this description and disclosure and according to the present invention, this eccentricity parameter is defined as the ratio of the maximum radius of the cross-section to its minimum radius, and as a result, the eccentricity parameter has a value of 1 in the circular shape. This eccentricity parameter can be evaluated for each parameter value specific to the coordinates of the longitudinal direction, for example the longitudinal axis (y) of the implant. In a preferred embodiment, the eccentricity parameter of the transition zone of the core body and / or the outer thread has a linear dependence on the longitudinal coordinate parameter in order to provide a particularly smooth transition, in particular between the tip zone (= circular cross-section, eccentricity parameter = 1) and the first or shaping zone (= protruding or non-circular surface, eccentricity parameter > 1).

[0033] The main directions of the transition zone in the rotational direction, and / or of the core body and / or of the thread, in which each radius of the cross-section has a maximum value, can be arranged, depending on the desired effect on the bone tissue, in particular at individually selected angles. However, in another preferred embodiment, they are arranged symmetrically (axially symmetric) with respect to the longitudinal central axis of the core body or of the outer surrounding volume. This design enables a relatively smooth and regular change in the degree of compression exerted on the surrounding bone tissue as a result of the screwing-in process.

[0034] In an embodiment considered particularly preferred, the outer profile of the implant, defined as the outer shape of the thread or the outer surrounding volume, with respect to the longitudinal central axis of the core body and with respect to the maximum or minimum value, conforms to the outer contour of the core body. In other words, in this preferred embodiment, in the orientation of the core body's radius with respect to the longitudinal axis having a maximum value, the outer contour of the outer volume surrounding the thread also takes on a maximum value. This conformity can preferably be achieved by an overlap of each main direction within a tolerance range of + / - 20 degrees and can be exact in a preferred embodiment. The "conforming" design has specific advantages in that, when the implant is implanted into the bone tissue, the bone condenses and relaxes in accordance with the outer shape of the implant on both the outer surface of the core body and the outer surface of the thread. The relaxation of the bone tissue on the minimum radius between the main directions (both on the outer surface of the core body and the outer surface of the thread) enables particularly high bone-to-implant contact and enhanced initial stability.

[0035] Conveniently, the number of main directions of the transition zone and / or the forming zone is three, i.e., the core body of the forming zone and / or the transition zone has a triangular-elliptical cross-section. In combination with the preferred embodiment of a symmetric arrangement of the main directions with respect to the longitudinal direction, this triangular-elliptical shape results in a rotational offset angle between two adjacent main directions of 120 degrees.

[0036] Due to its transition zone, the implant is specifically designed for a smooth and useful transition (during the screwing-in process) between the shaping of bone tissue and the first fitting of the thread of the bone tissue (in the circular zone) into direct treatment by changing the compression (in the shaping zone, preferably in the apical platform zone). The smooth transition between these zones can be further improved in particularly advantageous embodiments, where the core of the transition zone is preferably conical or tapered, preferably with a cone / taper angle between 1 degree and 12 degrees, more preferably between 4 degrees and 8 degrees. In a particularly preferred embodiment, the cone / taper angle is selected according to the overall length and diameter of the implant.

[0037] Taking into account the appropriate and convenient dimensions of the implant with respect to the requirements of the bone environment, in a preferred embodiment, the transition zone starts at a distance of about 2 - 4 mm from the root tip of the implant when viewed longitudinally. In other words, in an alternative or additional preferred embodiment, the positioning of the circular core and / or the thread zone at the root tip of the implant is considered to be very useful in order to maximize the possibility of high primary fixation. This is generally useful, but more specifically in the extraction socket, where an immediate loading protocol may be preferred. To provide a significant root tip fit, the circular zone preferably has a length of at least 2.5 mm when viewed longitudinally of the implant.

[0038] In addition to the geometric design of the core body, in a particularly preferred embodiment, the thread is also specifically designed to assist in ensuring fitting with bone tissue in high primary fixation. For this purpose, the thread is preferably a flat thread. Even more advantageously, the free width of the flat thread depends on the longitudinal coordinate parameter of the implant and starting from the root tip of the core body, continuously increases with the increase in the distance from the root tip. In this design, the thread in the region close to the root tip can be characterized by a relatively acute angle and a small outer width, thereby providing high cutting ability when the thread enters the bone tissue. In the process of screwing the implant into a specific position of the bone tissue (i.e., the implant entering deeper bone tissue), the width of the flat thread continuously increases, thereby continuously widening each local gap of the bone tissue and constantly strengthening the contact area between the bone tissue and the implant. Further improvement in the properties of the implant may be obtained by additional deformation of the thread profile in alternative or additional preferred embodiments. In this deformation, which is considered to be innovative in itself and particularly as an independent invention, the thread preferably has a profile with a root tip surface and a crown surface. The root tip surface is arranged so as to be basically orthogonal to the longitudinal axis of the implant, that is, the surface normal of the root tip surface is oriented basically parallel to the longitudinal axis of the implant. With this design, reliable contact between the root tip surface and the surrounding bone material can be maintained as a result of the non-circular outer surface contour - even when the lateral extension of the root tip surface of the thread varies between the minimum radius and the maximum radius. In this embodiment, the crown surface is preferably selected according to the requirements of the surrounding bone structure. Preferably, it is oriented at an angle to the longitudinal axis, preferably about 60 degrees, that is, the surface normal of the top surface is oriented at an angle to the longitudinal axis of the implant, preferably about 30 degrees, thereby causing the entire thread to form a buttress thread. Due to the shape of this invention, especially the orientation of the root tip surface, the root tip surface can absorb the load of the biting force very efficiently. Similarly, with this shape, the top surface provides a relatively small and sharp free end that improves the process of cutting bone, and a relatively wide and large base for a stronger thread that provides compression when the implant is inserted.

[0039] In particular, this design of the thread profile is useful when combined with the cross-sectional shape of the outer contour of the core body and / or the outer volume surrounding the thread. This shaped profile, in particular the triangular-elliptical cross-section, produces a vibratory effect of bone compression in the longitudinal direction of the implant when the implant is screwed into the bone material. The effect may be limited or reduced using the orientation of the tooth root apex. In an alternative or additional preferred embodiment, a plurality of cutting grooves, preferably equal in number to the number of main directions, are provided in the transition zone and / or the shaping zone of the implant. These cutting grooves enable an enhanced cutting ability of the implant body when being screwed in. Preferably, these cutting grooves are arranged symmetrically with respect to the longitudinal central axis of the core body. In particular, considered as an independent invention and in embodiments according to the present invention, it can also be used to improve other cutting groove systems. Each cutting groove is arranged with a given rotational displacement with respect to the adjacent main direction when viewed in the orientation direction around the longitudinal central axis of the core body.

[0040] Preferably, the cutting grooves in the orientation direction are arranged with respect to the adjacent main directions of the core body and / or the outer thread, taking into account that the maximum values associated with the main directions result in maximum compression of the bone material when the implant is screwed in. On the other hand, the relaxation after passing the maximum enables the bone material to return backwards towards the central axis of the implant to a certain extent. The relaxation according to this aspect of the present invention is used to selectively improve the cutting effect of the cutting grooves. Preferably, the position of the cutting grooves associated with the maximum values is for achieving the bone normalization effect. In other words, by arranging the cutting grooves in the rotational direction, as a result, relaxing the bone material is fitted by cutting, especially efficiently, when cutting hard bone rather than cartilage, and thus the stability of the implant with more flexible bone properties is maintained.

[0041] In a preferred embodiment of the invention, this is achieved by arranging the cutting grooves at an offset angle α with respect to each main direction. In this embodiment, the angle α is selected according to a selection criterion which is considered an independent invention in itself. According to this selection criterion, the cutting edge 48 must be arranged such that the radius of the cutting tip, defined by the outer limit of the radial extension of the cutting tip from the longitudinal axis of the implant, is between 20 and 75 μm less than the maximum radius in the corresponding main direction. This criterion takes into account the specific elasticity of the bone by this approximate amount after compression, by which its density returns or relaxes. In a preferred embodiment, the radius of the cutting tip is selected to be approximately 35 μm less than the maximum radius, where it is converted to a preferred offset angle α of approximately 106 degrees according to the remaining shape parameters of the core. When screwing the implant into the jawbone, the rotational displacement of the arrangement of the longitudinal grooves with respect to the adjacent main direction is preferably between 80 degrees and 120 degrees, particularly approximately 108 degrees, with respect to the normal properties, normal dimensions and rotational speed of the bone tissue.

[0042] The advantages achieved in the present invention, particularly including both high primary fixation and high secondary fixation, can be achieved by a specific geometric design. The implant according to the present invention is characterized by a circular zone having a substantially circular cross-section for the core and / or the thread. It is combined with a shaped zone having a non-circular, preferably triangular-elliptical cross-section, which enables continuous compression and relaxation of the bone tissue, thereby helping to retain the buccal bone in the apical or crown region, allowing for a smooth fit between the thread and the bone tissue with reduced rotation or wobbling of the implant. The transition zone and / or additional shaped zones provided between these zones, having different eccentricities, enable a smooth transition, allow the bone tissue to gently adapt to the compression effect, and reduce bone friction and unnecessary grinding or cutting.

[0043] According to one aspect of the present invention, there is provided an implant tool for implanting a dental implant, particularly a dental implant according to the present invention, into a patient's bone tissue. The implant tool includes a proximal portion and a distal portion, and the distal portion is for cooperating with the implant. The distal portion has a retaining element, and the retaining element includes an attachment portion for attaching the implant tool to the dental implant. The retaining element is at least elastically deformable in all directions perpendicular to the longitudinal direction of the implant tool. The attachment portion includes at least one protrusion extending in one or more directions substantially perpendicular to the longitudinal direction of the implant tool.

[0044] The retaining element may be integrally formed with (e.g., the remainder of) the implant tool or may be integrally attached thereto.

[0045] The entire retaining element of the implant tool is elastically deformable. The retaining element is elastically deformable along its entire length. The length of the retaining element extends along its longitudinal direction (i.e., its axial direction), that is, along the longitudinal direction of the implant tool (i.e., the direction from the proximal portion of the implant tool to the distal end of the implant tool).

[0046] The proximal portion of the implant tool is the portion closer to the clinician when using the implant tool. The distal portion of the implant tool is the portion closer to the implantation site when using the implant tool.

[0047] The distal portion of the implant tool is for cooperation with the implant. In particular, the distal portion may cooperate with a corresponding portion (e.g., a socket) of the crown portion of the implant. The distal portion may be at least partially introduced into the socket. The distal portion of the implant tool cooperates with the implant, e.g., the implant socket, such that the implant is screwed into the bone tissue in response to rotation of the implant tool about its longitudinal axis. Due to the cooperation or interaction between the distal tool portion and the implant, a rotational force applied manually or using a motor, for example, around its longitudinal axis is transferred to the implant to screw the implant into the bone tissue.

[0048] The distal portion of the implant tool may have a drive part as the part that cooperates with the implant. The drive part may or may not include an anti-rotation structure. The anti-rotation structure is configured to avoid relative rotation between the implant tool and the implant around the longitudinal axis of the tool when the tool and the implant fit together, for example, at least partially, by introducing the distal portion of the tool into the implant socket. In this way, the rotational force applied to the implant tool around its longitudinal axis is transferred to the implant. The anti-rotation structure of the implant tool may have a cross-section (i.e., outer cross-section) perpendicular to the longitudinal direction of the non-rotationally symmetric (e.g., non-circular) implant tool. The anti-rotation structure of the distal portion of the implant tool may cooperate with the corresponding anti-rotation structure of the implant. The anti-rotation structure of the implant may have a cross-section (e.g., inner cross-section) perpendicular to the longitudinal direction of the non-rotationally symmetric (e.g., non-circular) implant. The cross-sections of the anti-rotation structures of the tool and the implant may be substantially the same, or may have the same or corresponding shapes.

[0049] For example, the drive part of the distal portion of the implant tool may be a drive region and / or a drive part as further detailed below. The drive region and / or drive section of the implant tool can cooperate with the drive part and / or drive zone of the implant, respectively.

[0050] Therefore, the entire retaining element can be elastically deformed in all directions that are at least perpendicular to the longitudinal direction of the implant tool or along it, i.e., in the entire transverse direction (i.e., the entire radial direction) of the retaining element or along it.

[0051] The elastic deformability of the remainder of the distal portion of the implant tool in a direction perpendicular to the longitudinal direction of the implant tool may be lower than that of the retaining element. The remainder of the distal portion of the implant tool may not be elastically deformable in a direction perpendicular to the longitudinal direction of the implant tool.

[0052] The retaining element may be formed integrally with the implant tool (e.g., the remainder of the implant tool) or may be attached integrally thereto. Thus, the retaining element may form an integral part of the implant tool.

[0053] The attachment portion of the retaining element includes at least one protrusion or convexity extending from the outer surface of the remainder of the retaining element in one or more directions substantially perpendicular to the longitudinal direction of the implant tool.

[0054] At least one protrusion or convexity of the attachment portion is configured to be received in a corresponding cavity formed in the crown portion of the dental implant.

[0055] The implant tool is attached to the dental implant by attaching the attachment portion of the retaining element to the dental implant.

[0056] When attaching the attachment portion of the retaining element to the dental implant, the retaining element first elastically deforms, i.e., is elastically compressed, along the transverse direction of the retaining element, i.e., along the radial direction, such that when at least one protrusion or convexity is received in the corresponding cavity of the dental implant, due to the restoring force of the retaining element, it then returns to its original shape. Thus, the attachment portion can be attached to the dental implant by a snap fit in a reliable and efficient manner. The fitting of at least one protrusion or convexity of the attachment portion with the corresponding cavity of the dental implant provides audible and / or tactile feedback to the user (e.g., a clinician or technician in a dental laboratory) that the retaining element and thus the implant tool are properly attached to the dental implant in an obvious and clear manner.

[0057] The entire retaining element is elastically deformable along its transverse direction rather than just that portion. In this way, a particularly high degree of flexibility of the retaining element is obtained. Further, the entire retaining element elastically deforms during the attachment of the implant tool to the dental implant, and thus even when the retaining part is repeatedly fitted to and then removed from different dental implants, the risk of wear or breakage of the retaining element is minimized.

[0058] Therefore, the implant tool of the present invention provides a reliable and efficient indication as to whether the implant tool is properly attached to the dental implant.

[0059] The retaining element may be integrally formed with the implant tool (e.g., the remainder of the implant tool). As used herein, the term "integrally formed" means that the retaining element and the implant tool (e.g., the remainder of the implant tool) are formed in a one-piece configuration. Forming the retaining element and the implant tool in a one-piece configuration enables the implant tool to be manufactured in a particularly simple and efficient manner, such as by injection molding, milling (e.g., CNC milling), etc. The retaining element may be integrally attached to the implant tool (e.g., the remainder of the implant tool). As used herein, "integrally attached" means that the retaining element is attached to the implant tool such that the retaining element cannot be removed or separated from the implant tool without damaging and / or destroying the retaining element and / or the implant tool.

[0060] When the retaining element is integrally formed with or integrally attached to the implant tool, a particularly robust and stable configuration of the implant tool is obtained.

[0061] The retaining element may have a substantially cylindrical shape, for example, with a substantially circular cross-section with respect to the longitudinal direction of the implant tool.

[0062] At least one or more protrusions or convex portions of the attachment portion of the retaining element extend in one or more directions that are substantially perpendicular to the longitudinal direction of the embedding tool, i.e., in one or more transverse directions thereof. In particular, the attachment portion can include at least one protrusion or convex portion that extends in a plurality of transverse directions of the retaining element, i.e., along a part of the outer surface of the remaining portion of the retaining element in the circumferential direction of the retaining element. The at least one protrusion or convex portion may extend along 1% or more, 1.5% or more, 2% or more, 5% or more, 10% or more, 20% or more, or 30% or more of the outer circumference of the remaining portion of the retaining element.

[0063] The embedding tool may be made of, for example, metal (such as stainless steel), polymer, or composite material.

[0064] The retaining element and the remaining portion of the embedding tool may be made of the same material or different materials. When the retaining element is made of a material different from the remaining portion of the embedding tool, the retaining force provided by the retaining element can be set in a particularly simple manner.

[0065] The retaining element may have at least one portion that extends from the distal end of the retaining element to the proximal end of the retaining element, and the at least one portion is more flexible than the remaining portion of the retaining element. This flexible portion of the retaining element contributes to or provides the elastic deformability of the retaining element. Thus, the retaining element can be configured in an elastically deformable manner in a simple and efficient way.

[0066] At least one portion that extends from the distal end of the retaining element to the proximal end of the retaining element can be made of or formed from a material that is more flexible than the material of the remaining portion of the retaining element. Alternatively or additionally, the at least one portion can have a configuration or structure that has a higher degree of flexibility than the configuration or structure of the remaining portion of the retaining element. For example, the at least one portion can be made more flexible, for example, by providing perforations, recesses, openings, etc. therein. Also, for example, the at least one portion may have a thinner thickness (i.e., wall thickness) than the remaining portion of the retaining element.

[0067] The retaining element may have two or more, three or more, or four or more portions extending from the distal end to the proximal end of the retaining element, and these portions are more flexible than the remainder of the retaining element.

[0068] The retaining element may have at least one notch or recess extending from the distal end to the proximal end of the retaining element. The at least one notch or recess contributes to or provides the elastic deformability of the retaining element. Forming a retaining element with such at least one notch or recess particularly provides a flexible structure for the retaining element. Further, the retaining element has a particularly simple structure.

[0069] The retaining element may be hollow and / or tubular, and the at least one notch or recess penetrates the outer wall of the retaining element. The retaining element can have an open annular or circular shape (i.e., an annular shape having an opening in its circumference, or substantially a C shape) in a cross-section perpendicular to the longitudinal direction of the retaining element (i.e., the longitudinal direction of the implant tool).

[0070] The retaining element may have a closed annular or circular shape (i.e., an annular shape without an opening in its circumference).

[0071] The retaining element may be integrally formed with or integrally attached to an implant tool (e.g., the remainder of the implant tool) by one or more connecting portions disposed between the retaining element and the implant tool (e.g., its remainder). The one or more connecting portions may be disposed between the retaining element and the implant tool in the longitudinal direction of the retaining element. Each of the one or more connecting portions may extend along only a part of the retaining element in the circumferential direction of the retaining element.

[0072] In this way, the retaining element can be integrated with the implant tool in a particularly simple and reliable manner.

[0073] At least one or some of the one or more connecting parts may extend along 1% or more, 1.5% or more, 2% or more, 5% or more, 10% or more, 20% or more, 30% or more, or 40% or more of the circumference of the holding element. Each of the one or more connecting parts may extend along 10% or more, 20% or more, 30% or more, or 40% or more of the circumference of the holding element.

[0074] The holding element may be integrally formed with or integrally attached to the embedding tool by a plurality of connecting parts, for example, two connecting parts, three connecting parts, four connecting parts, or five connecting parts, and the connecting parts are arranged between the holding element and the embedding tool (for example, the rest thereof). The connecting parts may be separated from each other in the circumferential direction of the holding element such that there is a gap between adjacent connecting parts in the circumferential direction of the holding element, that is, they may be arranged respectively. The connecting parts may be separated from each other at equal distances in the circumferential direction of the holding element, or may be separated from each other at different intervals in the circumferential direction of the holding element. The connecting parts can have the same or different extensions along the circumference of the holding element, that is, in the circumferential direction of the holding element.

[0075] The holding element may be integrally formed with or integrally attached to the embedding tool (for example, the rest thereof) by a single connecting part. The holding element may have a single part extending from the distal end to the proximal end of the holding element, and the single part is more flexible than the rest of the holding element. The single connecting part may be arranged opposite to a single part in the radial direction of the holding element, or may be arranged adjacent to a single part in the circumferential direction of the holding element.

[0076] The holding element may be integrally formed with or integrally attached to the embedding tool by a single connecting part. The holding element may have a single notch or recess extending from the distal end to the proximal end of the holding element. The single connecting part may be arranged opposite to the notch or recess in the radial direction of the holding element, or may be arranged adjacent to the notch or recess in the circumferential direction of the holding element.

[0077] The retaining element may be formed integrally with the implant tool by a single connecting portion or may be attached integrally thereto. The single connecting portion may be arranged opposite to at least one notch or recess of the radial mounting portion of the retaining element, or may be arranged adjacent to at least one notch or recess of the circumferential mounting portion of the retaining element.

[0078] The retaining element may be formed integrally with the implant tool by at least two connecting portions or may be attached integrally thereto. The at least two connecting portions may be arranged opposite to each other in the radial direction of the retaining element.

[0079] The mounting portion of the implant tool may include a plurality of, for example, two or more, three or more, four or more, or five or more protrusions or convex portions, each extending in one or more directions substantially perpendicular to the longitudinal direction of the implant tool.

[0080] The plurality of protrusions or convex portions may have the same or different extensions in the circumferential direction of the retaining element. The plurality of protrusions or convex portions may have the same or different raised heights from the outer surface of the remainder of the retaining element, that is, the height from this outer surface in one or more directions substantially perpendicular to the longitudinal direction of the implant tool.

[0081] The plurality of protrusions or convex portions of the mounting portion may be arranged sequentially or continuously in the circumferential direction of the retaining element, that is, as a result, one is arranged behind the other in this circumferential direction. The plurality of protrusions or convex portions may be separated from each other at equal distances or at different intervals in the circumferential direction of the retaining element.

[0082] The plurality of protrusions or convex portions of the mounting portion are configured to be received in corresponding cavities (plural) formed in the crown portion of the dental implant.

[0083] As described above, the retention element may have at least one portion extending from the distal end to the proximal end of the retention element, and the at least one portion is more flexible than the remainder of the retention element. The retention element may have, or may define, at least one notch or recess extending from the distal end to the proximal end of the retention element. At least one protrusion or convexity of the attachment portion of the implant tool may be disposed adjacent to at least one flexible portion, or at least one notch or recess, of the retention element. In this way, a particularly secure and effective snap-fit connection between the retention element and the dental implant can be ensured.

[0084] The implant tool may have a visual indicator (e.g., a marking), which is configured to provide further indication as to whether the implant tool and the dental implant are properly attached to each other. For example, the visual indicator may include, or may be, a coating, a laser mark, a groove, etc. The visual indicator may be provided at the distal portion of the implant tool.

[0085] The retention element can be formed from a single material. The retention element may be made of, for example, a metal (e.g., titanium, a titanium alloy or stainless steel), a polymer or a composite material. In this way, the retention element can be configured to be elastically deformable in a particularly simple and reliable manner.

[0086] The material of the retention element may be a metal, superelastic, amorphous, etc.

[0087] The retention element may be manufactured, for example, by injection molding, milling (e.g., CNC milling), etc. For example, the retention element may be manufactured by injection molding using a colored plastic so as to provide color-coding as a label, for example. When the retention element is made of a metal (e.g., titanium, a titanium alloy or stainless steel), the retention element may be anodized.

[0088] According to one aspect of the present invention, there is provided an implant tool for implanting a dental implant, in particular a dental implant according to the present invention, into a patient's bone tissue. The implant tool includes a proximal portion and a distal portion, and the distal portion is adapted to cooperate with the implant. The distal portion has a driving region, and in the driving region, the cross-section of the distal portion perpendicular to the longitudinal direction of the implant tool has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour becomes a relative maximum value, and thus becomes a higher value than the adjacent azimuth.

[0089] The driving region of the distal portion of the implant tool cooperates with the implant. The driving region constitutes an anti-rotation structure, for example, the anti-rotation structure described above. The driving region is configured to avoid relative rotation between the tool and the implant around the longitudinal axis of the tool when the tool and the implant are fitted to each other, for example, at least partially, by introducing the distal portion of the tool into the implant socket.

[0090] The cross-sectional shape of the driving region described above enables efficient, reliable and uniform transfer of the rotational force applied to the implant tool around its longitudinal axis to the implant. Thus, the implant tool can minimize the risk of damage or breakage of the implant, especially its socket, along with reliable implantation of the implant into the patient's bone tissue.

[0091] The driving region of the distal portion of the implant tool is configured to cooperate with a corresponding anti-rotation structure of the implant, especially the driving portion. In the driving portion of the implant, the cross-section of the implant socket or channel perpendicular to the longitudinal direction of the implant, that is, the inner cross-section, has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour becomes a relative maximum value, and thus becomes a higher value than the adjacent azimuth. The cross-sections of the driving region of the implant tool and the driving portion of the implant may be substantially the same.

[0092] The cross-section of the drive region of the insert tool can be characterized by an eccentricity parameter specific to the deviation of each cross-section from a circular shape. For the purposes of this description and disclosure and according to the present invention, this eccentricity parameter is defined as the ratio of the maximum radius of the cross-section to its minimum radius, such that the eccentricity parameter has a value of 1 in a circular shape. The eccentricity parameter of the cross-section of the drive region of the insert tool is greater than 1. The eccentricity parameter may be, for example, in the range of 1.1 to 1.6, 1.2 to 1.5 or 1.3 to 1.4.

[0093] This eccentricity parameter can be evaluated for each value of the parameter specific to the longitudinal coordinate of the insert tool. The eccentricity parameter of the drive region may be constant in the longitudinal direction of the insert tool. Alternatively, the eccentricity parameter of the drive region may vary in the longitudinal direction of the insert tool, for example decreasing in the direction from the proximal end of the tool towards the distal end of the tool. The eccentricity parameter of the drive region may have a linear dependence on the longitudinal coordinate parameter of the insert tool.

[0094] In some embodiments, the main directions of the drive region of the insert tool, in which each radius of the cross-section has a maximum value, are arranged symmetrically with respect to the longitudinal central axis of the insert tool, in particular axially symmetrically.

[0095] The number of main directions of the drive region of the insert tool may be three or more, four or more, five or more or six or more.

[0096] In some embodiments, the number of main directions of the drive region of the insert tool is three, i.e. the drive region has a triangular elliptical cross-section. In combination with the symmetric arrangement of the main directions with respect to the longitudinal direction of the insert tool as described above, this triangular ellipse results in a rotational offset angle between two adjacent main directions of 120 degrees.

[0097] The drive region may have a tapered shape, such that in the drive region, the lateral dimension or extent of the cross-section of the distal portion perpendicular to the longitudinal direction of the insert tool decreases along the direction from the proximal end of the insert tool towards the distal end of the insert tool.

[0098] In the driving region, the cross-sectional area of the distal portion perpendicular to the longitudinal direction of the implant tool, i.e., the cross-sectional area of the distal portion, may decrease along the direction from the proximal end to the distal end of the implant tool.

[0099] According to one aspect of the present invention, there is provided an implant tool for implanting a dental implant, particularly a dental implant according to the present invention, into a patient's bone tissue. The implant tool includes a proximal portion and a distal portion, and the distal portion is for cooperating with the implant. The distal portion has a driving section. In the driving section, the cross-section of the distal portion perpendicular to the longitudinal direction of the implant tool has a plurality of radially protruding portions and a plurality of radially recessed portions that are alternately arranged along the circumference of the cross-section. Each of the radially outermost points of the radially protruding portions is on a corresponding circle around the center of the cross-section. At least two of these circles have different radii.

[0100] The driving section of the distal portion of the implant tool cooperates with the implant. The driving section constitutes an anti-rotation structure, such as the anti-rotation structure described above. The driving section is configured to avoid relative rotation between the tool and the implant around the longitudinal axis of the tool when the tool and the implant are fitted to each other, for example, at least partially, by introducing the distal portion of the tool into the implant socket. The cross-sectional shape of the driving section described above enables efficient, reliable, and uniform transfer of the rotational force applied to the implant tool around its longitudinal axis to the implant. Thus, the implant tool can minimize the risk of damage or breakage of the implant, particularly its socket, while ensuring reliable implantation of the implant into the patient's bone tissue.

[0101] The drive section of the distal portion of the implant tool is configured to cooperate with a corresponding anti-rotation structure of the implant, particularly the drive section. In the drive zone of the implant, the cross-section of the socket or channel of the implant perpendicular to the longitudinal direction of the implant, i.e., the inner cross-section, has a plurality of radial protrusions and a plurality of radial recesses that are alternately arranged along the circumference of the cross-section. Each of the radially outermost points of the radial protrusions is on a corresponding circle around the center of the cross-section, and at least two of these circles have different radii. The cross-section of the drive section of the implant tool and the drive zone of the implant may be substantially the same or corresponding to each other. The radially innermost points of the radial recesses may be on a single circle around the center of the cross-section. Thus, all of the radially innermost points of the radial recesses may be on the same circle around the center of the cross-section. Alternatively, at least two of the radially innermost points of the radial recesses may be on different circles around the center of the cross-section having different radii from each other.

[0102] The cross-section of the distal portion of the implant tool of the drive section may have the same number of radial protrusions and radial recesses. The number of radial protrusions and / or radial recesses may be two or more, three or more, four or more, five or more, six or more, seven or more, eight or more, or nine or more. In a particularly preferred embodiment, the cross-section has six radial protrusions and six radial recesses.

[0103] The radial protrusions may include one or more first radial protrusions and one or more second radial protrusions. Thus, all of the radially outermost points of the one or more first radial protrusions are on a single first circle around the center of the cross-section, and all of the radially outermost points of the one or more second radial protrusions are on a single second circle around the center of the cross-section.

[0104] The second circle may have a smaller radius than the first circle. The first radial protrusions and the second radial protrusions, together with the corresponding radial recesses arranged therebetween, are alternately arranged along the circumference of the cross-section.

[0105] The number of the first radial protrusions may be the same as the number of the second radial protrusions.

[0106] The radial protrusions of the cross-section of the distal portion of the embedding tool of the drive section may include only the first radial protrusions and the second radial protrusions. That is, other than the first and second radial protrusions, no more radial protrusions may be present in the cross-section.

[0107] The radial protrusions and / or radial recesses of the cross-section of the drive section may each have a curved shape, for example, at least partially circular shape, at least partially elliptical shape, at least partially oval shape, etc.

[0108] The radial protrusions and radial recesses of the cross-section of the drive section may be arranged directly or immediately adjacent to each other. The radial protrusion may be directly or immediately adjacent to two radial recesses, and vice versa.

[0109] The distal portion of the embedding tool of the present invention may have a drive region and a drive section as described above. The drive region may be arranged proximal to the drive section.

[0110] By providing both a drive region and a drive section in the distal portion of the embedding tool, any damage or breakage to the implant, particularly to its socket, can be particularly reliably avoided when implanting the implant into the bone tissue. In particular, due to the presence of two anti-rotation structures (i.e., the drive region and the drive section) in the distal portion of the embedding tool that can cooperate with two corresponding anti-rotation structures of the implant (e.g., the drive region and the drive section), when implanting it into the bone tissue, the rotational force or load applied to the implant can be shared by the two structures. Therefore, any damage to either of these two structures of the implant can be minimized. Thus, one or both of these structures of the implant can be reliably and efficiently used as an indicator for abutments, scan posts, impression posts, etc. after implanting the implant into the bone tissue.

[0111] As described above, the distal portion of the implant tool of the present invention may have a retaining element and a drive region. The drive region may be disposed proximal to the retaining element.

[0112] As described above, the distal portion of the implant tool of the present invention may have a retaining element and a drive section. The drive section may be disposed distal to the retaining element.

[0113] As described above, the distal portion of the implant tool of the present invention may have a retaining element, a drive region, and a drive section. The drive section may be disposed distal to the retaining element. The drive region may be disposed proximal to the retaining element. The drive section, the retaining element, and the drive region may be arranged in this order in a direction from the distal end to the proximal end of the implant tool.

[0114] The implant tool may consist of a single piece of material. In this case, all elements of the implant tool are integrally formed with each other.

[0115] The implant tool may consist of two separate parts, for example a distal part and a proximal part, which are attached to each other, in particular removably attached to each other.

[0116] The two separate parts of the implant tool may be permanently attached to each other.

[0117] For example, the distal portion of the implant tool may have a convex portion that fits into a corresponding concave portion of the proximal portion of the implant tool. The distal portion and the proximal portion may be attached to each other, in particular removably attached to each other, by inserting the convex portion into the concave portion. The convex portion and the concave portion may have corresponding anti-rotation shapes or structures to prevent any rotation of the distal portion and the proximal portion relative to each other around the longitudinal axis of the implant tool.

[0118] The anti-rotation structure of the distal portion may have a cross-section (e.g., the outer cross-section of the convex portion) perpendicular to the longitudinal direction of the implant tool that is not rotationally symmetric, and for example it is non-circular, such as elliptical, oval, polygonal (e.g., rectangular, square, hexagonal), etc. The anti-rotation structure of the distal portion of the implant tool can cooperate with the corresponding anti-rotation structure of the proximal portion of the implant tool. The anti-rotation structure of the proximal portion of the implant tool may have a cross-section (e.g., the inner cross-section of the concave portion) perpendicular to the longitudinal direction of the implant tool that is not rotationally symmetric, and for example it is non-circular, such as elliptical, oval, polygonal (e.g., rectangular, square, hexagonal), etc. The cross-sections of the anti-rotation structures of the distal and proximal portions may be substantially the same.

[0119] Providing the implant tool in the form of two separate parts as described above, for example the distal and proximal portions, makes the manufacture of the implant tool, especially the manufacture of the retaining element, simpler and easier. This is especially true when the retaining element is provided in the proximal portion of the implant tool. For example, the manufacture of the retaining element can be carried out by milling.

[0120] One of the two separate parts of the implant tool, especially the distal portion, may include a drive section, and the other of the two separate parts, especially the proximal portion, may include a retaining element and a drive region. In this way, the manufacture of the implant tool, especially the manufacture of the retaining element, can be further simplified.

[0121] The retaining element may be integrally formed with the other of the two separate parts, especially the proximal portion.

[0122] The retaining element may be integrally attached to the other of the two separate parts, especially the proximal portion.

[0123] The present invention further provides a combination of a dental implant according to the present invention and an implant tool according to the present invention.

[0124] The descriptions, features and definitions provided above for the dental implant and implant tool of the present invention apply fully to the combination of the present invention.

[0125] The combination of the present invention provides the effects and advantages already described above for the dental implant and the implant tool of the present invention.

[0126] The dental implant can have at least one cavity formed in its crown portion for receiving at least one protrusion or convex portion of the mounting portion of the retaining component.

[0127] According to one aspect of the present invention, there is provided a dental implant including a core body having a root tip and a crown end, particularly for implantation into a patient's bone tissue. The core body includes a channel and a socket that open towards the crown end and extend in the longitudinal direction of the implant from the crown end towards the root tip. The core body has a drive zone, and in the drive zone, the cross-section of the channel perpendicular to the longitudinal direction of the implant has a plurality of radial protrusions arranged along the circumference of the cross-section. Each of the radially outermost points of the radial protrusions is on a corresponding circle around the center of the cross-section. At least two of these circles have different radii. The inner cross-section of the socket or channel of the implant perpendicular to the longitudinal direction of the implant can have a plurality of radial protrusions and a plurality of radial recesses arranged alternately along the circumference of the cross-section.

[0128] The longitudinal direction of the dental implant extends from the crown end of the implant towards the root tip of the implant. The cross-section of the channel perpendicular to the longitudinal direction of the implant is the inner cross-section of the channel.

[0129] The drive zone of the core body of the implant cooperates with an implant tool, particularly the implant tool of the present invention described above, i.e., its drive section. The drive zone constitutes an anti-rotation structure, for example, the anti-rotation structure described above. The drive zone is configured to avoid relative rotation between the tool and the implant around the longitudinal axis of the tool when the tool and the implant fit together, for example, at least partially, by introducing the distal portion of the tool into the channel or socket of the implant.

[0130] The cross-sectional shape of the drive zone described above enables the efficient, reliable, and uniform transfer of the rotational force applied to the implant tool around its longitudinal axis to the implant. Thus, the implant, together with its reliable implantation into the patient's jawbone or bone tissue, makes it possible to minimize the risk of damage or breakage of the implant, especially its channels or sockets.

[0131] The drive zone of the implant is configured to cooperate with a corresponding anti-rotation structure at the distal part of the implant tool, especially the drive section. The cross-sections of the drive zone of the implant and the drive section of the implant tool may be substantially the same.

[0132] The radially innermost points of the radial recesses of the channel cross-section of the drive zone may be on a single circle around the center of the cross-section. Thus, all the radially innermost points of the radial recesses may be on the same circle around the center of the cross-section. Alternatively, at least two of the radially innermost points of the radial recesses may be on different circles around the center of the cross-section having different radii from each other.

[0133] The cross-section of the channel of the drive zone may have the same number of radial protrusions and radial recesses. The number of radial protrusions and / or radial recesses may be two or more, three or more, four or more, five or more, six or more, seven or more, or eight or more. In a particularly preferred embodiment, the cross-section has six radial protrusions and six radial recesses.

[0134] The radial protrusions may include one or more first radial protrusions and one or more second radial protrusions. Thus, all of the radially outermost points of the one or more first radial protrusions are on a single first circle around the center of the cross-section, and all of the radially outermost points of the one or more second radial protrusions are on a single second circle around the center of the cross-section.

[0135] The second circle may have a smaller radius than the first circle.

[0136] At least one of the one or more radially outermost points of the one or more first radial protrusions can be located at an angular position that conforms to the angular position of the maximum value of the core of the dental implant within an angular tolerance range. The tolerance range can be about ±10 degrees, preferably ±5 degrees. The radially outermost points of the one or more first radial protrusions can be located at the same (or substantially the same) angular position as the maximum value of the core of the dental implant.

[0137] The number of the radially outermost points of the one or more first radial protrusions can be the same as the number of the maximum values of the implant core.

[0138] At least one of the one or more radially outermost points of the one or more second radial protrusions can be located at an angular position that conforms to the angular position of the minimum value of the core of the dental implant within an angular tolerance range. The tolerance range can be about ±10 degrees, preferably ±5 degrees. The radially outermost points of the one or more second radial protrusions can be located at the same (or substantially the same) angular position as the maximum value of the core of the dental implant.

[0139] The above-described configuration of the outermost points of the drive zone ensures that the maximum amount of material exists between the outermost points of a given cross-section and the periphery of the implant core.

[0140] The first radial protrusions and the second radial protrusions, together with the corresponding radial recesses disposed therebetween, are alternately arranged along the circumference of the cross-section.

[0141] The number of the first radial protrusions may be the same as the number of the second radial protrusions.

[0142] The radial protrusions of the cross-section of the channel of the drive zone may include only the first radial protrusions and the second radial protrusions. That is, there may be no more radial protrusions in the cross-section other than the first and second radial protrusions.

[0143] The radial protrusions and / or radial recesses of the cross-section of the channel in the drive zone may each have a curved shape, for example, at least partially circular, at least partially elliptical, at least partially oval, etc.

[0144] The radial protrusions and radial recesses of the cross-section of the channel in the drive zone may be arranged directly adjacent to each other. The radial protrusion may be directly adjacent to two radial recesses, and vice versa.

[0145] The core may further have a drive portion, and in the drive portion, the cross-section of the channel perpendicular to the longitudinal direction of the implant has a plurality of main directions. In these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth.

[0146] The drive portion of the core of the implant cooperates with an implanting tool, particularly the implanting tool of the present invention described above, i.e., its drive region. The drive portion constitutes an anti-rotation structure, such as the anti-rotation structure described above. The drive portion is configured to avoid relative rotation between the tool and the implant around the longitudinal axis of the tool when the tool and the implant are fitted to each other, for example, at least partially, by introducing the distal portion of the tool into the channel or socket of the implant.

[0147] The cross-sectional shape of the drive portion described above enables efficient, reliable, and uniform transfer of the rotational force applied to the implanting tool around its longitudinal axis to the implant. Thus, the implant can minimize the risk of damage or breakage to the implant, particularly its channel or socket, along with its reliable implantation into the patient's jawbone or bone tissue.

[0148] The drive portion of the implant is configured to cooperate with a corresponding anti-rotation structure of the distal portion of the implanting tool, particularly the drive region. The cross-sections of the drive portion of the implant and the drive region of the implanting tool may be substantially the same.

[0149] The cross-section of the drive part of the implant can be characterized by an eccentricity parameter specific to the deviation of each cross-section from a circular shape. For the purposes of this description and disclosure and according to the present invention, this eccentricity parameter is defined as the ratio of the maximum radius of the cross-section to its minimum radius, such that the eccentricity parameter has a value of 1 in a circular shape. The eccentricity parameter of the cross-section of the drive part of the implant is greater than 1. The eccentricity parameter may be, for example, in the range of 1.1 to 1.6, 1.2 to 1.5 or 1.3 to 1.4.

[0150] This eccentricity parameter can be evaluated for each value of a parameter specific to the longitudinal coordinates of the dental implant. The eccentricity parameter of the drive part may be constant in the longitudinal direction of the implant. Alternatively, the eccentricity parameter of the drive part may vary in the longitudinal direction of the implant, for example decreasing in the direction from the crown end of the implant towards the root tip of the implant. The eccentricity parameter of the drive part may have a linear dependence on the longitudinal coordinate parameter of the implant.

[0151] In some embodiments, the main direction of the drive part of the implant, in which each radius of the cross-section has a maximum value, is arranged symmetrically, in particular axially symmetrically, with respect to the longitudinal central axis of the implant.

[0152] The number of main directions of the drive part of the implant may be three or more, four or more, five or more or six or more.

[0153] In some embodiments, the number of main directions of the drive part of the implant is three, i.e. the drive part has a triangular elliptical cross-section. In combination with the symmetrical arrangement of the main directions with respect to the longitudinal direction of the implant as described above, this triangular ellipse results in a rotational offset angle between two adjacent main directions of 120 degrees.

[0154] The drive part may have a tapered shape, such that in the drive part, the lateral dimension or extent of the cross-section of the channel perpendicular to the longitudinal direction of the implant decreases along the direction from the crown end of the core body towards the root tip of the core body.

[0155] In the drive part, the area of the cross-section of the channel perpendicular to the longitudinal direction of the implant, i.e., the cross-sectional area of the channel, may decrease along the direction from the crown end of the core body to the root tip end of the core body.

[0156] The core body of the implant according to the present invention may thus have a drive zone and a drive part as described above. The drive region may be arranged at the tip of the drive part.

[0157] By providing both a drive zone and a drive part on the core body of the implant, any damage or breakage to the implant, particularly to its channel or socket, can be particularly reliably avoided when the implant is implanted into the jawbone or bone tissue. In particular, due to the presence of two anti-rotation structures (i.e., the drive zone and the drive part) of the core body of the implant that can cooperate with two corresponding anti-rotation structures (e.g., the drive section and the drive region) of the distal part of the implant tool, the rotational force or load applied to the implant during its implantation into the bone tissue can be shared by the two structures. Thus, any damage to either of these two structures of the implant can be minimized. Then, one or both of these structures of the implant can be reliably and efficiently used as an indicator for abutments, scan posts, impression posts, etc. after the implant is implanted into the jawbone or bone tissue.

[0158] The core body may have an outer surface extending along the longitudinal direction of the implant between the root tip end and the crown end.

[0159] The dental implant may further include at least one thread extending outward from the core body, and the thread has a root tip surface facing the root tip end of the core body and a crown surface facing the crown end of the core body.

[0160] The thread may have a longitudinal groove, i.e., a cutting groove, formed therein, and the longitudinal groove extends from the root tip end of the thread to the crown end of the thread.

[0161] The thread may have a recess formed in the crown surface at the tip of the tooth root, and the recess extends in a direction from the crown surface toward the root tip surface along a part of the thickness of the thread. The recess is open to the longitudinal groove, that is, open to the longitudinal groove.

[0162] According to one aspect of the present invention, there is provided a dental implant, particularly for implantation into a patient's bone tissue, comprising a core having an outer surface extending along the longitudinal direction of the implant at the root tip, the crown end, and between the root tip and the crown end. The implant further includes at least one thread extending outwardly from the core. The thread has a root tip surface facing the root tip of the core and a crown surface facing the crown end of the core. The thread has a longitudinal groove, that is, a cutting groove, formed therein. The longitudinal groove extends from the root tip of the thread toward the crown end of the thread. The thread has a recess formed in the crown surface at the tip of the tooth root, and the recess extends in a direction from the crown surface toward the root tip surface along a part of the thickness of the thread. The recess is open to the longitudinal groove, that is, open to the longitudinal groove.

[0163] The thickness of the thread extends in a direction from the crown surface of the thread toward the root tip surface of the thread. The width of the thread extends radially outward from the core. The length of the thread extends in the longitudinal direction of the implant.

[0164] As described above, by providing the longitudinal groove and the recess in the thread, the implant becomes self-drilling. Further, the arrangement of the longitudinal groove and the recess helps to reduce the insertion torque or rotational force required to insert the implant into the jawbone or bone tissue. This is particularly advantageous in the case of hard bone. When inserting the implant, axial pressure is not required. Rather, the implant efficiently and reliably inserts itself into the implantation site in response to its rotation.

[0165] The recess has a cutting function, that is, a function of cutting bone tissue. Therefore, the recess helps to efficiently cut and remove bone material and transport the removed bone material further toward the crown end of the core.

[0166] Particularly when implanting the implant into an implantation site, for example, an extraction site, due to, for example, an inclined or angled arrangement between the implant and the bone tissue, the implant must be cut laterally there, and the implant of the present invention ensures its smooth and accurate arrangement in the bone. Furthermore, the recess is very useful for implanting the implant into a hole or extraction socket with insufficient bone tissue preparation where the bone wall is not uniform and thus a cylindrical bone cut resulting from normal perforation cannot be made.

[0167] The implant of the present invention can thus implant into bone tissue with reduced force and high precision. In this way, a particularly stable and robust connection or fitting between the implant and the bone tissue, that is, high implant stability can be achieved.

[0168] Due to the arrangement of the recess on the threaded crown surface, the above-mentioned effects can be achieved over a wide range of implant thread angles, that is, for substantially all implant thread angles, particularly for small implant thread angles.

[0169] Therefore, the present invention provides a dental implant that enables reliable and accurate placement and fitting of the jawbone or bone tissue at a variety of implant thread angles, particularly small thread angles. The dental implant includes at least one thread. The dental implant may include a plurality of threads, for example, two or more threads, three or more threads, or four or more threads.

[0170] At least one thread has at least one longitudinal groove, i.e., at least one cutting groove, formed therein. The at least one longitudinal groove extends in the longitudinal direction of the at least one longitudinal groove from the root tip of the thread to the crest end of the thread. Thus, the at least one longitudinal groove starts at the root tip of the thread and extends therefrom towards the crest end of the thread. The at least one longitudinal groove may extend over 20% or more, 30% or more, 40% or more, 50% or more, or 60% or more of the length of the thread.

[0171] The at least one longitudinal groove may extend in a direction substantially parallel to the longitudinal direction of the implant or in a direction inclined or slanted with respect to the longitudinal direction of the implant. In the latter case, the angle between the extending direction of the at least one longitudinal groove and the longitudinal direction of the implant may be in the range of 2 degrees to 20 degrees, 5 degrees to 15 degrees, or 8 degrees to 12 degrees.

[0172] The at least one longitudinal groove extends along a part of the circumference of the core in the width direction of the at least one longitudinal groove. The at least one longitudinal groove may extend over 10% to 30%, 15% to 25%, or 18% to 22% of the circumference of the core. The thread may have a plurality of longitudinal grooves, i.e., a plurality of cutting grooves, formed therein. One of the plurality of longitudinal grooves extends from the root tip of the thread to the crest end of the thread. The thread may have two or more longitudinal grooves, three or more longitudinal grooves, or four or more longitudinal grooves formed therein.

[0173] The plurality of longitudinal grooves may be arranged in a staggered or offset arrangement along the length of the thread and / or along the circumference of the thread, i.e., along the circumference of the core.

[0174] The thread has at least one recess formed in its crown surface, and the at least one recess extends in a direction from the crown surface toward the root tip surface along a part of the thickness of the thread. Thus, the at least one recess starts at the crown surface of the thread and extends therefrom toward the root tip surface of the thread. The at least one recess does not completely penetrate the thread in the thickness direction of the thread. The at least one recess is open to, i.e., opens to, the crown surface of the thread.

[0175] Furthermore, the recess is open to, i.e., opens to, the longitudinal groove. The recess is provided adjacent to, i.e., directly or immediately adjacent to, the longitudinal groove.

[0176] The at least one recess may extend in a direction from the crown surface toward the root tip surface along 20% - 90%, 30% - 80%, 40% - 70% or 50% - 60% of the thickness of the thread. In this way, while maintaining sufficient stability of the implant, it can be ensured that the recess can effectively serve in the bone cutting process.

[0177] When the available bone is of low volume (e.g., extraction socket), when the first thread cuts into the bone, the drilling hole may be small, and as a result, good stability of the implant obtained from the tip can be obtained. The extension of the at least one recess in the direction from the crown surface toward the root tip surface (i.e., the depth of the at least one recess) may be constant along a direction parallel to the crown or root tip surface.

[0178] The extension of the at least one recess in the direction from the crown surface toward the root tip surface (i.e., the depth of the at least one recess) may vary along a direction parallel to the crown or root tip surface. In this case, the maximum extension of the at least one recess in the direction from the crown surface toward the root tip surface may be in the range of 20% - 90%, 30% - 80%, 40% - 70% or 50% - 60% of the thickness of the thread. The maximum extension of the at least one recess in the direction from the crown surface toward the root tip surface may be present in the portion of the recess disposed directly adjacent to the longitudinal groove.

[0179] The extension of at least one recess in the direction from the crown surface towards the root tip surface of the thread may decrease along a direction away from the longitudinal groove in which the recess is open in the circumferential direction. In this way, a particularly effective cutting function of the recess can be obtained.

[0180] At least one recess may have a curved shape. For example, at least one recess may have the shape of a part or portion of a sphere or an ellipsoid, for example a quarter sphere or a quarter ellipsoid. Such a curved shape of at least one recess enables the recess and thus further the implant to be manufactured in a particularly simple and cost - efficient manner.

[0181] At least one recess may extend in the width direction of the thread over 50% - 90%, 60% - 80%, or 65% - 75% of the width of the thread.

[0182] At least one recess may be arranged on the upstream side of the longitudinal groove in the rotational direction of the implant. The rotational direction of the implant is the direction in which the implant is screwed into the bone tissue.

[0183] At least one recess may be formed on the crown surface of the thread at the first complete or maximum rotation of the thread. The first complete or maximum rotation of the thread is the first complete rotation when a complete rotation is counted starting from the root tip of the thread and proceeding towards the crown end of the thread. The first complete rotation of the thread is thus the complete rotation at the most tooth root tip of the thread. Such an arrangement of at least one recess enables a particularly stable and robust fitting of the implant with the jawbone or bone tissue.

[0184] At least one recess may be formed on the crown surface of the thread at the second complete or maximum rotation of the thread. At least one recess may be formed on the crown surface of the thread at the third complete or maximum rotation of the thread.

[0185] The thread has a plurality of recesses formed on its crest surface. For example, one of the plurality of recesses may be formed on each of the crest surfaces of the thread at the first and second complete or maximum rotations of the thread. One of the plurality of recesses may be formed on each of the crest surfaces of the thread at the first, second, and third complete or maximum rotations of the thread.

[0186] The thread angle, that is, the inclination angle of the thread with respect to a plane perpendicular to the longitudinal direction of the implant, may be 25 degrees or less, 20 degrees or less, 15 degrees or less, 12 degrees or less, or 10 degrees or less. In a particularly preferred embodiment, the thread angle is 10 degrees or less.

[0187] Such a small thread angle provides the advantage that the implant, which enables a particularly smooth and accurate placement of the implant, is introduced into the bone tissue more slowly, that is, with less forward movement per rotation of the implant.

[0188] As described above, the recesses of the implant of the present invention work particularly well in combination with a thread having such a small thread angle. In particular, the arrangement of the recesses on the crest surface of the thread can provide a local increase in the thread angle due to the presence of the recesses. For example, the thread angle may increase locally to 20 degrees to 40 degrees, or 25 degrees to 35 degrees.

[0189] Therefore, the recesses can greatly contribute to the cutting of bone tissue.

[0190] The above and other features of the present disclosure will become even more fully apparent from the following description and the appended claims, when considered in conjunction with the accompanying drawings. These drawings merely illustrate some embodiments according to the present disclosure and are not to be regarded as limiting the scope of the present disclosure. With this understanding, the present disclosure will be described more specifically and in detail with reference to the accompanying drawings.

Brief Description of the Drawings

[0191]

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Mode for Carrying Out the Invention

[0192] Preferred embodiments of the present invention will be described with reference to the accompanying drawings.

[0193] The same parts are denoted by the same reference numerals in all the figures. As shown, individual features may be incorporated into further modifications, all of which are considered to be within the scope of the present invention.

[0194] The dental implant 1 shown in FIG. 1 is provided for use in a patient's jawbone at the site of a pulled or missing tooth to hold a prosthetic portion that functions as a dental prosthesis or crown. As shown in the exemplary embodiment, the dental implant 1 is designed for a so-called multi-component configuration and is configured as a so-called strut portion for implantation into the patient's bone tissue. A dental implant system for the purpose of using the dental implant 1, also referred to as an attachment portion or abutment, includes a second implant component (not shown) associated therewith, provided for fixing a dental prosthetic portion or any other prosthetic element that can cooperate with the implant 1. However, alternatively and further according to the present invention, the dental implant 1 may also be configured for use in an integrated dental implant system, where the dental implant 1 in its top region also has means for directly attaching a dental prosthetic portion or prosthetic element.

[0195] The implant 1 includes, as its body, a core 2 having a root tip 4, a crown end 6, and an outer surface 8 extending longitudinally between the root tip 4 and the crown end 6. In an integrated configuration, the crown end 6 of the core 2 can be appropriately designed so that a dental prosthesis can be attached with appropriate and high mechanical stability. However, in the example shown, due to the multi-component configuration of the dental implant system, the crown end 6 is designed to form a highly mechanically stable connection with a second implant component or abutment. After appropriately fixing the dental prosthesis part or the prosthesis to the attachment part or abutment, in order to provide such high mechanical stability, the implant 1 is characterized by a receiving channel 10 into which a corresponding connection pin of the abutment can be inserted. By pushing the connection pin into the receiving channel 10, the implant 1 and the abutment are mechanically connected to each other. The mechanical connection between the implant 1 and the abutment is achieved via a relevant connection screw, the male thread of which is screwed into the female thread provided on the implant 1, whereby the screw head of the connection screw presses the abutment onto the implant 1.

[0196] On its outer surface 8, the core 2 of the implant 1 is provided with an external thread 12 extending outward from the core 2. The thread 12 is configured in a zone close to the root tip 4, in particular as a self-drilling thread, whereby the implant 1 can be inserted into the jawbone by screwing it into the intended location. The pitch of the thread 12 can be uniform or variable.

[0197] The implant 1 including the thread 12 is specifically designed, particularly taking into account the desired high primary and secondary fixation, as well as the uniform transfer of forces occurring under the chewing load of the dental implant 1 into the jawbone. For this purpose, the implant includes a number of specific zones or sections, each of which is shown to specifically contribute to high primary fixation or high secondary fixation.

[0198] First, the core body 2 of the dental implant 1, in the preferred embodiment as shown, includes a circular zone 20 located adjacent to the tooth root tip 4. In the core circular zone 20, the core body 2 of the implant 1 is designed for a relatively simple fit between the thread 12 and the bone material without applying excessive stress to the bone tissue during the first time when the implant 1 is screwed into the bone material. For this purpose, in the core circular zone 20, the core body 2 has a circular cross-section. The positioning of the core circular zone 20 at the tooth root tip of the implant 1 is considered very useful to maximize the possibility of high primary fixation. Although this is useful in principle, more specifically, it is in the extraction socket and an immediate loading protocol may be preferred. To provide a significant tooth root tip fit, the circular zone 20 has a length of at least 2.5 mm as seen in the longitudinal direction of the implant in the embodiment shown.

[0199] Second, the core body 2 includes a core shaping zone 22. In the embodiment shown in the figure, the core shaping zone 22 is arranged near the other end of the implant 2, that is, adjacent to the crown end 6, thereby constituting the top platform zone 24, or it may also be arranged in some central or intermediate ranges of the core body 2. In the embodiment shown adjacent to the crown end 6 designed to connect to an abutment for holding a dental prosthesis, in this zone 22, the core body 2 is designed with a non-circular cross-section characterized by a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value and thus a higher value than the adjacent azimuths.

[0200] Due to the cross-sectional design of this core forming zone 22, when the core 2 is screwed into the bone tissue, the compressive force applied to the bone tissue changes in an oscillating manner between a maximum compression when the local radius of the cross-section is at its maximum (due to the rotational movement of the implant body) and a minimum compression when the local radius of the cross-section is at its minimum. Thus, when the implant body is screwed in, in this zone, the surrounding bone tissue is subjected to fluctuating compression that varies between periods of high compression and periods of relaxation when the compression decreases. In the preferred embodiment shown, the forming zone 22 is located at the top end of the implant 1. Thus, after implantation of the implant 1, the forming zone 22 stops in the top zone of the patient's jaw, which is characterized by relatively hard bone tissue. After implantation, this forming profile, which features a minimum value, results in a region of low bone stress near the minimum value, thereby enabling enhanced regeneration of bone material and significantly minimizing the adverse effects of overly strong compression on blood vessels. As a result, the regeneration of bone material, and thus osseointegration, is significantly improved by providing the minimum value of the forming zone 22 in the region of the important bone structure. For the purpose of osseointegration, it is considered very useful to provide these effects in the uppermost layer of the top plate of at least 2.5 mm or preferably at least 3 mm. Thus, the first forming zone 22 has a length of at least 2.5 mm in the longitudinal direction of the implant, as shown in the illustrated embodiment.

[0201] Thirdly, the core 2 of the implant 1 includes a transition zone 26 located between the core circular zone 20 and the core forming zone 22 when viewed in the longitudinal direction of the implant 1. To enable a smooth and useful transition between zones 20 and 22, the transition zone 26 has a temporary cross-section (viewed in the longitudinal direction) that changes from a circular cross-section that conforms to the cross-section of the core circular zone 20 in the vicinity of the core circular zone 20 to a cross-section with a non-circular protrusion that conforms to the cross-section of the forming zone 22 in the vicinity of the forming zone 22. Due to this transition zone 26, an immediate and sudden change in shape, a shearing effect on the bone tissue, and other damaging effects on the bone tissue can be avoided.

[0202] An alternative embodiment of the present invention is shown in FIG. 2. This embodiment can be used separately or in combination with the embodiment of FIG. 1. In this alternative embodiment, a dental implant 1' similar to the embodiment of FIG. 1 also includes a core body 2 including a core circular zone 20 and a core forming zone 22. However, instead of or in addition to the transition zone 26, the dental implant 1' includes a second core forming zone 26'. Similar to the first core forming zone 22, in the second core forming zone 26', the cross-section of the core body 2 has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the value of the adjacent azimuth. The second core forming zone 26' is located between the zones 20 and 22 when viewed in the longitudinal direction of the implant 1. In this embodiment of the first core forming zone 22, in order to enable a desired smooth and useful transition between the zones 20 and 22, the core eccentricity parameter defined as the ratio of the maximum radius to the minimum radius of the cross-section of the core body 2 is larger than that of the second core forming zone 26'. As a further option, clearly this second forming zone 26' itself may be composed of an arrangement or number of individual forming zones of this type having different eccentricities.

[0203] FIG. 3 shows a schematic view of the implants 1, 1' of FIGS. 1 and 2, where the zones 20, 22, 26, 26' are distinguishable and identified. In the example shown, the transition zone 26 begins at a distance of about 2-3 mm from the tooth root tip 4 of the implant 1 when viewed in the longitudinal direction.

[0204] This design concept of the core body 2, namely providing the three zones 20, 22 and 26 or 26' respectively, is considered as one first possible group of embodiments for the concept of the present invention. Separate from or in combination with the embodiments of the first group, in an alternative separate second group of embodiments for the concept of the present invention, useful cutting characteristics and similar or equivalent effects for bone treatment can be achieved by the design of the outer contour of the thread 12 similar to the design described above for the core body 2. In FIG. 4, an embodiment of the implant 1 is shown to feature both of these alternative groups of embodiments of the present invention in combination, but they may equally be used independently of each other. For a better explanation of the design of the outer contour of the thread 12, hereinafter it is referred to as the "outer volume", or the enclosed volume 28 defined by the outer contour of the thread 12 as clearly represented in the longitudinal cross-sectional view according to FIG. 4.

[0205] In the shown combined embodiment, the thread 12 of the implant 1 also includes a first or shaped thread zone 30. Thus, the outer volume 28 surrounding the thread 12 has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus a value higher than the adjacent azimuths. Further in this embodiment, the thread 12 includes a thread circular zone 32, and in the shown preferred embodiment, it is also arranged adjacent to the root tip 4 of the implant 1. Thus, the cross-section of the outer surface enclosed volume 28 is basically circular, and when viewed in the longitudinal direction of the implant, it is a thread transition zone 34 arranged between the first shaped zone 30 and the second circular zone 32. Thus, the cross-sectional shape of the outer volume 28 surrounding the thread 12 changes from a basically circular shape adjacent to the circular zone 32 as a function of parameters specific to the longitudinal coordinates, to a shape corresponding to the cross-sectional shape of the first or shaped zone 30, particularly with respect to the general shape of the cross-section and / or the values of its specific parameters.

[0206] An alternative embodiment of this group of embodiments of the present invention is shown in FIG. 5. This embodiment can be used separately or in combination with the embodiment of FIG. 4. In this alternative embodiment, a dental implant 1' similar to the embodiment of FIG. 4 also features an enclosed volume 28 of a thread 12 that includes a threaded circular zone 32 and a thread-forming zone 30. However, instead of or in addition to the thread transition zone 34, the dental implant 1' includes a second thread-forming zone 34'. Similar to the first thread-forming zone 30, in the second thread-forming zone 34', the cross-section of the outer volume 28 has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus a higher value than adjacent orientations. The second thread-forming zone 34' is located between zones 30 and 32 when viewed in the longitudinal direction of the implant 1. In this embodiment of the first thread-forming zone 30, in order to enable a desired smooth and useful transition between zones 30 and 32, the thread eccentricity parameter defined as the ratio of the maximum radius to the minimum radius of the cross-section of the outer volume 28 is greater than that of the second thread-forming zone 34'. As a further option, clearly this second forming zone 34' itself may be composed of an arrangement or number of individual forming zones of this type having different eccentricities.

[0207] Due to their transition zones 26, 26', 34, 34', the implants 1, 1' are specifically designed for a smooth and useful transition (during the screwing process) during the first fitting of the thread 12 of the bone tissue (in the core circular zone 20 and / or the threaded circular zone 32) to the shaping and direct treatment of the bone tissue (in the shaping zones 22, 30) by changing the compression. To further improve the smooth transition between these zones, the core 2 of the transition zone 26 is in a conical or tapered shape with a cone / taper angle especially between 1 degree and 12 degrees, preferably between 4 degrees and 8 degrees.

[0208] The cross-section of the core 2 can be characterized by an eccentricity parameter defined as the ratio of the maximum radius to the minimum radius of the cross-section. The eccentricity parameter, which is 1 for a circular shape, is characteristic of the deviation of each cross-section from the circular shape. In order to provide a particularly smooth transition between the core circular zone 20 with a circular cross-section and the core shaping zone 22 with a non-circular cross-section, this eccentricity parameter of the transition zone 26 has a linear dependence on the coordinate parameters of the longitudinal implant 1. In the example shown, the core 2 of the core shaping zone 22 has an eccentricity value of approximately 1.1. The same concept can be used for the transition zone 34 of the thread 12 and the eccentricity parameter of the outer volume 28 of the thread shaping zone 30.

[0209] Hereinafter, various considerations regarding the individual elements and components of the implants 1, 1' and their shape parameters will be considered by referring to the group of embodiments with the implant 1. Obviously, they may equally apply to the group of embodiments with the implant 1', or to combinations of these groups of example embodiments.

[0210] The positions and boundaries of the various core zones 20, 22, 26 (or 26' respectively) and the various thread zones 30, 32, 34 (or 34' respectively) in the longitudinal direction of the implant 1 may vary in different embodiments, seven of which are shown as general examples in FIGS. 6 to 9. In each of these displays, FIGS. 6a, 7a, 8a, 9a show perspective views of each implant 1, and FIGS. 6b, 7b, 8b, 9b show longitudinal cross-sectional views of each implant 1. FIGS. 6c to 6e, 7c to 7e, 8c to 8e and 9c to 9e show cross-sections of the outer contour of the core 2 and the outer contour of the surrounding volume 28.

[0211] In the embodiment of FIG. 6, the core 2 and the surrounding volume 28 of its cross-section are three-sided ellipses from the apical central part to the crown end 6 in order to increase the buccal bone and assist in the normalization of the bone.

[0212] In contrast, in the embodiment of FIG. 7, in the apical zone 42 above the transition line 4, the cross-section of the core 2 is circular (as shown in FIG. 7c) having the outer contour of the three-sided elliptical surrounding volume 28. This is done in order to maintain the outer three-sided elliptical shape for the bone normalization effect and increased buccal bone, as well as to improve torque and initial stability and implant strength during implantation.

[0213] In the embodiment shown in FIG. 8, the cross-section of the core 2 is circular over the entire length of the implant 1, and only the outer contour of the surrounding volume 28 changes from circular near the root tip to three-sided elliptical near the crown end 6.

[0214] FIG. 9 shows an embodiment in which the cross-section of the core 2 in the center of the implant 1 (FIG. 9d) is circular but three-sided elliptical in the apical zone 42. As shown in FIG. 9d, in the central region, the region having the circular cross-section of the core 2 overlaps with the region of the three-sided elliptical cross-section of the surrounding volume 28.

[0215] As an example, FIG. 10 shows an embodiment of the implant 1 together with input data that may be for CNC machining of each shape. In FIG. 10a, the implant 1 is shown in a longitudinal cross-sectional view, while FIG. 10b shows the implant 1 in a side view. FIG. 10c is a longitudinal cross-sectional view of the outer volume 28 of the thread of the implant 1 embodiment, and the implant is present on the side with the minimum radius. The contour of the outer volume 28 may be obtained by CNC machining with a tool contour that conforms to at least one of the lines shown in FIG. 10c. After machining the raw material into this shape, the thread 12 is machined by engraving a thread groove, the depth of which is imparted by the contour as shown in FIG. 10d. This results in the final shape of the core 2 as described above.

[0216] The three - elliptical shape of the implant 1 design may be obtained by CNC machining, where the circular mode is shown in FIG. 10f. As can be seen from FIG. 10f, the differential elliptical parameter e is an alternative definition for the shape of the core 2 / outer volume 28, defined by the difference between the maximum radius and the minimum radius of the cross - section, and is preferably selected to be about 0.23 mm at a normal diameter of about 4 mm.

[0217] FIG. 10c also shows a plurality of longitudinal coordinates / positions Y01 - Y05 along the axis y (the implant longitudinal axis) that defines a zone along the said axis y. Y01 is the position of coordinate 0 mm. In the embodiment shown in FIG. 10c, the value of the elliptical parameter e varies according to the coordinate y along the said axis. For example, in the first zone Y01 - Y02, the elliptical parameter e can have a constant value included in / selected from between 0.10 and 0.50 mm, more preferably between 0.20 and 0.25 mm. Further, the said zone Y1 - Y2 (outer zone 1 or the first outer zone) can be a zone with a certain eccentricity. In the said zone Y1 - Y2, the maximum diameter OD of the outer volume 28 can be constant and may have a value of 4 mm. Within the zone Y2 - Y3 (outer zone 2 or the second outer zone), the elliptical parameter e may have a value that varies from a value included in / selected from between 0.20 and 0.30 mm at position Y2 and a value of 0 mm at position Y03. In the said zone Y02 - Y03, the maximum diameter OD of the outer volume 28 may vary between 4 and 3.54 mm. The deviation of the elliptical parameter and / or the change in the eccentricity distance defined above may be linear in the said zone Y2 - Y3. Finally, the elliptical parameter e may have a value of 0 mm between positions Y03 and Y05. As a non - limiting example, the outer volume 28 can have a conical shape between positions Y03 and Y04 (outer zone 3 or the third outer zone) with a diameter varying between 3.54 and 3.40 mm. The outer volume 28 can also have a conical shape between positions Y04 and Y05 (outer zone 4 or the fourth outer zone) with a diameter varying between 3.40 and 1.80 mm.

[0218] Obviously, the length of each zone depends on the overall length of the implant. As a non-limiting example for an implant having an overall length of 13 mm, Y2 can be located 2.30 mm from Y1, Y3 can be located 5 mm from Y1, Y4 can be located 11.70 mm from Y1, and Y5 can be located 13 mm from Y1.

[0219] FIG. 10d shows a longitudinal cross-section of the core 2 of the implant 1 of FIG. 10a. FIG. 10d also shows a plurality of longitudinal coordinates / positions Y6 to Y09 located along the axis y. Said positions further define zones along said axis y. Y1 is the position of coordinate 0 mm. In the embodiment shown in FIG. 10d, the value of the elliptical parameter e varies according to the coordinate y along said axis. For example, in the first region Y1 to Y6, the elliptical parameter e can have a constant value included in / selected from between 0.10 and 0.50 mm. In said first zone, the maximum core diameter OD varies between 4 and 3.60 mm along the longitudinal axis. Said zone Y1 to Y6 (core zone 1 or first core zone) can have a constant eccentricity. Within the zone Y6 to Y7 (outer zone 2 or second outer zone), the elliptical parameter e can have a value that varies from a value included in / selected from between 0.10 and 0.50 mm at position Y6 and a value of 0 mm at position Y7. The deviation of the elliptical parameter can be linear in said zone Y6 to Y7. In said zone Y6 to Y7, the maximum core diameter OD can vary between 3.30 and 2.70 mm. Finally, the elliptical parameter e can have a value of 0 mm between positions Y07 and Y09. As a non-limiting example, the core 2 has a conical shape (core zone 3 or third core zone) between positions Y07 and Y08 with a core diameter varying between 2.70 and 2.2 mm, and a conical shape between positions Y08 and Y09 (core zone 4 or fourth core zone) with a core diameter varying between 2.2 and 1.6 mm.

[0220] Obviously, the length of each zone depends on the total length of the implant. As a non-limiting example for an implant having a total length of 13 mm, Y6 can be positioned 2.30 mm from Y1, Y7 can be positioned 5 mm from Y1, Y8 can be positioned 11.70 mm from Y1, and Y9 can be positioned 13 mm from Y1.

[0221] Yet another embodiment of the present invention is shown in FIG. 11. This embodiment can be used separately or in combination with the embodiments of FIGS. 1 and / or 2. In this alternative embodiment shown in FIG. 11, a dental implant 1'' similar to the embodiments of FIGS. 1 and / or 2 also comprises a core body 2 including a concentric zone 20, a core shaping zone 22, a circular thread zone 32 and a thread shaping zone 30, although this alternative embodiment may be used without one or more of these zones. In this alternative embodiment, the thread 12 of the crown portion overlaps with an additional groove 38 defined by the outer width or surface of the thread 12. This additional groove promotes bone attachment to the implant. This groove 37, by its groove depth, defines a bottom level at its bottom. In a better explanation of the design of the alternative embodiment, hereinafter it is referred to as the "bottom volume" defined by the bottom level of the groove 38 of the thread 12. In other words, this "bottom" volume (also referred to as the "groove core volume") is the volume passing through the innermost points of all the grooves, or all the points of the grooves closest to the longitudinal axis of the implant 1''. In the combined embodiment shown in FIG. 11, the groove 38 of the thread 12 of the implant 1 similarly includes a first or shaping groove zone 40. Thus, the cross-section of the bottom volume of the thread 12 has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus a higher value than the adjacent azimuths.

[0222] Similar to FIG. 10, as an example, FIG. 12 shows the input data that may be used for CNC machining of the respective shapes in implant 1''. In particular, FIG. 12a shows a right side view of the outer volume 28. FIG. 12b is a longitudinal cross-sectional view of the outer volume 28. FIG. 12c is a left side view of the outer volume 28. FIG. 12d is a right side view of the core 2. FIG. 12e is a longitudinal cross-sectional view of the core 2. FIG. 12f is a left side view of the core 2. FIG. 12g is a right side view of the bottom volume. FIG. 12h is a longitudinal cross-sectional view of the bottom volume. FIG. 12i is a left side view of the bottom volume. FIG. 12j is the circular mode of CNC machining. As can be seen from FIG. 12j, the differential elliptical parameter is an alternative definition for the shape of the core 2 / outer volume 28 / bottom volume, defined by the difference between the maximum radius and the minimum radius of the cross-section, and at a normal maximum diameter of about 4.20 mm, is preferably selected between about 0.10 and 0.50, and more preferably can be about 0.23 mm.

[0223] In the embodiment of FIG. 12, the change in the elliptical parameter e and thus the eccentricity parameter for the core 2 / outer volume 28 / bottom volume along the longitudinal axis y of the implant is similar to that described with respect to FIG. 10, and reference is made to the said description. The main differences between the embodiments of FIGS. 10 and 12 are the length of the implant and the presence of the grooves in the embodiment of FIG. 12. As a non-limiting example, the implant of FIG. 12 may have an overall length of 9 mm and coordinates from Y01 to the following, - For the outer volume 28 (see FIG. 12b), Y02 of 2.30 mm, Y03 of 4.5 mm, Y04 of 8.10 mm and Y05 of 9 mm; - For the core, Y07 of 2.30 mm, Y08 of 5 mm, Y09 of 7 mm and Y10 of 9 mm; - For the "bottom volume" or "groove core volume", it may have positions with Y11 of 0.75 mm, Y12 of 2.30 mm, Y13 of 4.50 mm and Y14 of 7.90 mm.

[0224] As a non-limiting example, between positions Y01 and Y02, the implant may have a maximum outer diameter OD of 4.20 mm. Between positions Y02 and Y03, the implant may have a maximum outer diameter OD that varies between 4.20 and 3.80 mm. Between positions Y03 and Y04, the implant may have a conical shape with an outer diameter that varies between 3.80 and 3.57 mm, and between positions Y04 and Y05, the implant may have an outer diameter that varies between 3.57 and 1.90 mm.

[0225] As a further non-limiting example, between positions Y01 and Y07, the implant may have a maximum core diameter OD that varies between 4.20 and 3.78 mm. Between positions Y07 and Y08, the implant may have a maximum core diameter that varies between 3.78 and 2.84 mm. Between positions Y08 and Y09, the implant may have an outer diameter that varies between 2.84 and 2.31 mm, and between positions Y09 and Y10, the implant may have an outer diameter that varies between 2.31 and 1.68 mm.

[0226] Furthermore, the "bottom" volume or "groove core" volume may have a differential elliptical parameter e that varies along the y-axis. As a non-limiting example, the elliptical parameter e may have a constant or varying value included in / selected from between 0.10 and 0.50 mm. In one embodiment, the "bottom" volume or "groove core" volume may have a parameter that varies as follows. - From Y1 to Y11 (the first bottom volume zone), the differential elliptical parameter e may have a value (e.g., a constant) included in between 0.10 and 0.50 mm, and the eccentricity may be constant. - From Y11 to Y12 (the second bottom volume zone), e may vary from a starting value selected between 0.20 and 0.30 mm to a final value of 0 mm, the variation may be linear, and the eccentricity may also vary linearly. - From Y12 to Y13 (the third bottom volume zone), e may have a value of 0 mm, and the "bottom" volume or "groove core" volume may have a conical shape that tapers along the y-axis. - From Y13 to Y14 (the fourth bottom volume zone), e may have a value of 0 mm, and the "bottom" volume or "groove core volume" may have a conical shape.

[0227] It should be noted that the differential elliptical parameter e (and thus the eccentricity) can vary for each of the core 2, the outer volume 28, and / or the bottom volume at a given cross-section. The elliptical parameter e can have a value included in and / or selected from between 0.10 and 0.50 mm. In some embodiments, the elliptical parameter e can have a value of 0.15, 0.20, 0.23, or 0.30 mm.

[0228] The implant according to the invention thus - Have at least one crown zone (also called the first shaping zone) or portion extending along the longitudinal axis y of the implant having a maximum, for example constant, eccentricity, and can include the surrounding volume 21 and / or the core 2 and / or the groove core volume. The maximum eccentricity can be included between 1.05 and 1.2 and can extend, for example, between 0 and 80% of the total length of the implant. In some embodiments, the crown zone extends to about 30%, 45%, 60%, or 70% of the total length of the implant, - At least one transition zone or portion extends along the longitudinal axis y of the implant having an eccentricity that varies between the maximum and minimum eccentricities, and the variation can be linear, - At least one tooth root tip zone (also called the circular zone) or portion extends along the longitudinal axis y of the implant having the maximum constant eccentricity.

[0229] The implant according to the invention thus - It can include an enveloping volume 21 and / or a core body 2 and / or a groove core volume, having at least one crown zone (also called the first shaping zone) or portion extending along the longitudinal axis y of the implant with a maximum, for example a constant eccentricity. The maximum eccentricity can be included between 1.05 and 1.2. The crown zone can extend at least 10%, at least 15%, at least 20%, or at least 25% of the total length of the implant. - At least one transition zone or portion extends along the longitudinal axis y of the implant having an eccentricity that varies between the maximum and minimum eccentricities, and the variation can be linear. The transition zone can extend at least 10%, at least 15%, at least 20%, or at least 25% of the total length of the implant. - At least one tooth root tip zone (also called the circular zone) or portion extends along the longitudinal axis y of the implant having the maximum constant eccentricity. The tooth root tip zone can extend at least 30%, at least 35%, at least 40%, at least 45% or at least 50% of the total length of the implant.

[0230] The following table shows different non-limiting possible values for the lengths of the respective zones of the implant depending on the total length of the implant. JPEG0007702983000001.jpg74166

[0231] Figure 35 is a graph showing different values (variations or deployments) of eccentricity of the core 2 and / or the thread surrounding volume 28 and / or the groove forming zone 40 depending on the position along the longitudinal axis of the implant in a particular embodiment. As can be seen in Figure 35, the root tip zone of the core 2 and / or the thread surrounding volume 28 and / or the groove forming zone 40 can have a constant minimum eccentricity equal to 1 between position A and position B. The core 2 and / or the thread surrounding volume 28 and / or the groove forming zone 40 can also have a transition zone starting at position B, and the eccentricity varies from the constant minimum eccentricity to the maximum eccentricity value at position C. After position C, the core 2 and / or the thread surrounding volume 28 and / or the groove forming zone 40 can have a crown zone, where the eccentricity has a constant maximum value. As described above, the constant maximum eccentricity can be included between 1.05 and 1.2.

[0232] In some embodiments, particularly for the core 2 and / or the thread surrounding volume 28, position A can represent the root tip of the implant and the crown end of the implant, and position D can represent the crown end of the implant. Positions A, B, C, and D do not necessarily have the same coordinates of the core 2, the thread surrounding volume 28, or the groove forming zone 40. Position A should be understood as the most root tip position of the core 2, the thread surrounding volume 28, or the groove forming zone 40. As can be seen in Figure 35, the shape of the eccentricity curve has no sharp corners and it is a solid line having only one tangent at all positions.

[0233] In addition to the geometric design of the core 2 and / or the thread 12 as described above, which is also considered an independent invention in its details, in a preferred alternative embodiment, further means may be provided to assist in ensuring a secure fit with bone tissue in high primary fixation. For this purpose, in the embodiments shown in FIGS. 13 to 18, cutting grooves 46 are provided in the threaded portions of the implants 1, 1', 1''. FIGS. 13 to 18 each show a perspective view of each implant, and the various core / thread zones 20, 22, 26, 30, 32, 34 are shown with hatching lines to indicate changes. In these embodiments, in selected portions, or in all of the cores 2 and threads 12, a plurality of cutting grooves 46, preferably equal in number to the main direction of the core 2 and / or the thread 12, may be provided in the transition zone 26 of the implant 1 and / or in other zones 20, 22. Each of these cutting grooves 46 is characterized by a cutting edge 48 (see FIG. 19) that removes bone material when the implant 1 is screwed in, thereby enabling an enhanced cutting ability of the implant 1 during screwing. Clearly, the groove 38 is not shown in the embodiments of FIGS. 13 to 18, but in another alternative embodiment, any of those shown may include the groove 38. With respect to the arrangement and / or design, the cutting grooves 46 are considered an independent invention and, as shown in the figures, together with the features of the implant 1 and / or implant 1' and / or implant 1'' as described above, or may be used with a conventional implant or screw system and have specific features.

[0234] FIGS. 13 to 15 show embodiments of the implant 1 of FIG. 1 in which the position and / or length of the cutting grooves vary preferably according to the specific requirements of an individual implant design. These embodiments form variations according to the number of cutting grooves 46 that extend longitudinally along a part of the transition zones 28, 34 and a part of the shaping zones 22, 30.

[0235] In the embodiment shown in FIG. 13, the core 2 and the outer thread are configured such that both the core circular zone 20 and the threaded circular zone 32 are arranged, i.e., to conform to the outer contour adjacent to the tooth root tip 4. Adjacent to these, both the core transition zone 26 and the thread transition zone 34 are arranged in an overlapping manner. Adjacent to the tooth crown end 6, the core forming zone 220 is arranged together with the thread forming zone 30, and both have a triangular elliptical cross-section in this embodiment.

[0236] In contrast, FIG. 14 shows an embodiment in which zones of different types and cross-sections partially overlap. In particular, adjacent to the tooth root tip 4, both the core circular zone 20 and the thread circular zone 32 are arranged, each starting from the tooth root tip 4. In the core 2, as indicated by the change in the hatching lines - when viewed longitudinally, while the thread 12 is still within its circular zone 32, the transition from the core circular zone 20 to the core transition zone 26 is arranged at 43. At the intersection position 43a, the core transition zone 26 ends and the core forming zone 22 starts, and at the position within the core forming zone 22, the thread circular zone 32 crosses within the thread transition zone 34. At a position further towards the tooth crown end 10, at the intersection position 43b, the core forming zone 22 ends again and transitions to another transition zone 26. At the same intersection position 43b, the thread transition zone 34 transitions into the thread forming zone 30. Thus, in this present embodiment, the various zones of the core and the thread partially overlap with each other in various combinations.

[0237] FIG. 15 again shows an embodiment in which the core 2 and the outer thread 12 are configured such that both the core circular zone 20 and the threaded circular zone 32 are arranged, i.e., to conform to the outer contour adjacent to the tooth root tip 4. Adjacent to these, both the core transition zone 26 and the thread transition zone 34 are arranged in an overlapping manner. Adjacent to the tooth crown end 10, the core forming zone 22 is arranged together with the thread forming zone 30, and both have a triangular elliptical cross-section in this embodiment.

[0238] As shown in the example according to FIGS. 16 to 18, the cutting groove 46 may have various orientations such as being basically parallel to the longitudinal axis of the implant 1 (example in FIG. 16), being inclined with respect to the longitudinal axis of the implant 1 (as in FIG. 17), or being curved and wound around the outer surface 8 of the core body 2 as shown in FIG. 18.

[0239] Another preferred embodiment is shown in FIG. 19 based on the basic implant design of the implant 1''. FIG. 19 shows a side view of the top or crown portion of the implant 1''. Clearly, with regard to the number and arrangement of the cutting grooves 46, the concept shown may similarly be used for any other preferred implant concept or for a conventional implant / screw design. Further, in the embodiment shown in FIG. 19 which is considered an independent invention in itself, the cutting grooves 46 are arranged in the threaded region of the implant 1''. With respect to their arrangement in the "z - direction", i.e., the longitudinal direction of the implant 1'', they are arranged by the movement with respect to their adjacent cutting grooves 46, such that, in that position, the cutting grooves 46 follow the inclination of the thread 12. By this design, when screwing the implant 1'' into the bone tissue, it can be ensured that fitting the individual threads 12 into the bone tissue provides the cutting effect on the same bone zone by the continuous cutting edges 46.

[0240] FIG. 20 shows the implant 1 of FIG. 1 in a variation according to the number of cutting grooves 46 extending longitudinally along a part of the transition zones 28, 34 and a part of the shaping zones 22, 30. FIG. 21 shows a cross-section (schematically) of the implant 1 of FIG. 20 in the position shown in FIG. 20. As can be seen in FIG. 21, the cross-section of the core 2 and its outer surface 8 has a triaxial ellipse. In other words, in its core shaping zone 22, the cross-section of the core 2 (and the cross-section of the enveloping volume 28 of the thread 12) has a plurality of (i.e., three) main directions. In these main directions, the radius corresponding to the distance between the center 50 of the cross-section and its outer contour becomes a relative maximum value ("maximum radius"), and thus a higher value than the adjacent azimuth. In the figure of FIG. 21, one of these main directions is oriented parallel to the vertically upward direction represented by the line 52. The maximum value of the radius of the outer contour of the core 2 in this main direction is at position 54. Due to the symmetric arrangement of the main directions with respect to the center 50, the other two main directions are at an angle of 120 degrees with respect to the line 52.

[0241] The cutting grooves 46 in this example are also symmetrically arranged around the center 50, i.e., the angle between two adjacent cutting grooves is also 120 degrees. The rotationally oriented cutting grooves 46 are appropriately arranged to maximize the cutting efficiency of the bone material in consideration of the relaxation effect of the bone tissue after the maximum value of the radius has been exceeded during the screwing process. For this purpose, each cutting groove 46 is arranged with a given rotational offset with respect to the adjacent main direction as seen in the orientation direction around the center 50 or the longitudinal central axis of the core 2. In FIG. 21, the core 2 is shown from above (where the core is rotated in the right-hand direction (or clockwise) during implantation), and the rotational offset is represented by the angle α between the main maximum represented by the line 52 and the dotted line 56 pointing towards the respective cutting end 48 of the cutting groove 46 and the next successive cutting end 46.

[0242] In the shown embodiment, this angle α is selected according to a selection criterion that is considered an independent invention in itself. According to this selection criterion, the cutting edge 48 should be arranged such that the radius of the cutting edge, defined by the intersection of the dotted line 56 and the outer surface 8, i.e., the outer limit of the radial extension of the cutting end from the center 50, is between 20 and 75 μm less than the maximum radius. This criterion takes into account the specific elasticity of the bone, which, after compression, returns to or relaxes to its original density by this approximate amount. In the shown embodiment, the radius of the cutting end is selected to be approximately 35 μm less than the maximum radius, whereupon, according to the remaining shape parameters of the core, it is converted to a preferred angle α of approximately 106 degrees.

[0243] This preferred offset angle may further vary depending on the value of the maximum radius in order to reliably account for the elasticity of the bone material. Due to the preferred tapered shape design of the core 2 and / or the outer volume 28, this maximum radius may vary as a function of the longitudinal coordinate of the implant 1, thereby further providing a preferred offset angle that depends on this longitudinal coordinate. As a result, the resulting cutting groove 46 may be helical around the core 2 of the implant 1.

[0244] In principle, the thread 12 may be of any convenient thread profile, particularly a flat thread. The free width 58 of the thread 12 continuously increases with the increase in the distance from the root tip 4 at each position along the longitudinal direction of the implant 1. With this design, the thread 12 in the region close to the root tip 4 can be characterized by a relatively acute angle and a small outer width, thereby providing high cutting ability when the thread 12 enters the bone tissue. In the process of screwing the implant 1 into a specific position of the bone tissue (i.e., an implant that enters deeper bone tissue), the width 58 of the thread 12 continuously increases, thereby continuously widening each local gap of the bone tissue and constantly strengthening the contact area between the bone tissue and the implant.

[0245] In the embodiments of the invention shown in the figures, the thread 12 is designed to have a specific profile in order to usefully interact with the non-circular cross-section of the core 2 and / or the thread 12. In this variant, which is also considered to be inventive in itself, in particular as an independent invention, as can be seen in the enlarged views of FIGS. 22 and 23, the thread 12 preferably has a profile comprising a root face 60 and a crown face 62. The root face 60 is thus arranged essentially perpendicular to the longitudinal axis 64 of the implant 1, i.e., the surface normal of the root face 60 is oriented essentially parallel to the longitudinal axis 64 of the implant 1. Furthermore, the crown face 62 is oriented at an angle of approximately 60 degrees with respect to the longitudinal axis 64, i.e., the surface normal of the crown face 62 is oriented at an angle of approximately 30 degrees with respect to the longitudinal axis 64 of the implant 1. This angle is represented by line 66. In other words, the thread 12 as a whole forms a so-called buttress thread.

[0246] The potential effect of the non-circular, for example, triangular-elliptical shape, due to a specific choice of orientation of the root face 60, which is considered an independent invention in itself, may be corrected. This effect is the vibration of the bone with which the thread 12 comes into contact when inserted. This means that when the implant 1 is implanted, the thread 12 is only in contact with the bone at intervals.

[0247] By making the root side of the thread 12 90 degrees with respect to the longitudinal axis, the root face will have improved contact over the full length of the thread after implantation. This is shown in the enlarged section according to FIG. 24. The longitudinal section of FIG. 24 shows a part of the implant 1 after being implanted in the bone material 70.

[0248] In a preferred embodiment, which is considered an independent invention in itself, the depth of the thread 12 at the tooth root tip surface 60 is selected for enhanced primary fixation after implantation. For this purpose, this preferred embodiment takes into account that, in order to absorb masticatory forces, after implantation, at the core and / or thread forming zones 22, 30 and / or at the core and / or thread transition zones 26, 34, ideally, the thread at the tooth root tip surface 60 must physically contact the bone material 70 to the greatest extent possible. In this regard, the zone of the minimum radius of the forming / transition zone estimates the final position after implantation where the previous maximum value has passed, thereby creating a cavity 72 into which the bone tissue is extruded. Nevertheless, the depth of the thread 12 at the tooth root tip surface 60 is preferably selected to be at least twice as large as the difference between the maximum and minimum radii of the outer contour of the surrounding volume 28 in order to provide a reliable platform 74 on the bone material on which the tooth root tip surface 60 of the thread can rest on a part of the bone material 70.

[0249] In yet another preferred embodiment, which is considered an independent invention in itself, the implant 1 (similarly the implants 1', 1'') comprises a state-of-the-art connection system 80 for mechanically connecting the abutments associated with the implant 1 to each other. Below, various embodiments of the state-of-the-art connection system 80 are described with reference to the implant 1. Obviously, all embodiments may be used equally advantageously for any other implant type, for example, by the implants 1'', 1''' as described above.

[0250] The connection system 80 is characterized in that the implant 1 has a receiving channel 10 into which the corresponding connection pins of the abutment can be inserted. Figures 25a and 25b show the upper surface of the implant 1 from the direction represented by the arrow 82 in Figure 4. As can be seen in Figure 25, the cross-section or outer contour of the non-circular zones 22, 30 of the implant 1 is three-sided elliptical, thereby providing three main directions in the transition zones 26, 34 and the shaping zones 22, 30 respectively. These main directions, each radius of the cross-section having a maximum value, are arranged symmetrically with respect to the longitudinal central axis of the core 2. As is also apparent from the representation in Figure 25, the outer profile of the implant 1 defined by the outer contour of the thread 12 conforms to or "follows" the outer contour of the core 2. Thus, in its orientation where the radius of the core 2 has a maximum value, the outer contour of the thread 12 likewise has a maximum value. Furthermore, due to the conical or tapered shape of the core 2 in the transition zone 26, the minimum radius of the core 2 in the shaping zone 22 is larger than the radius of the outer contour of the thread 12 in the circular zone 20.

[0251] Furthermore, the receiving channel 10 also has an external profile or external contour that conforms to or "follows" both the outer contour of the thread 12 of the implant 1 and the outer contour of the core body 2. Thus, in the orientation where the radius of the core body 2 and the outer contour of the thread 12 have their maximum values, the contour of the receiving channel 10 also takes on a minimum value, i.e., it is also three-sided elliptical. Furthermore, the receiving channel 10 also tapers, and its cross-section becomes narrower as it approaches the bottom end 84. Due to this shape, together with its associated connection pins of the abutment, the receiving channel 10 provides a so-called indexing structure that ensures the correct rotational flexibility of the abutment when implanted. As can also be seen in the longitudinal cross-sectional views of the implant 1 according to FIGS. 25 as well as FIGS. 26 and 27, in the proper assembly of the abutment, the receiving channel 10 at its lower or bottom end 84 has an indexing contour 86. This "second indexing" of the preferred embodiment shown in FIGS. 26 and 27 has a Torx®-like cross-section and may be used to conduct the torque required for implanting the implant by inserting an appropriate tool. Due to the indexing contour 86, this torque can be applied without affecting the indexing contour of the actual receiving channel 10.

[0252] As shown in FIG. 28, in an alternative embodiment of the implant 1''' with a second indexing, the second indexing contour may be integrated with the first indexing contour such that it is provided by the receiving channel 10 with its non-circular cross-section. This is achieved, according to the illustrated embodiment, by a number of pores 88 that are cut into the tapered sidewalls of the receiving channel 10. To apply the torque required to implant the implant 1''' into the bone material, a tool corresponding to a screwdriver method may be applied to fit into the pores 88, thereby ensuring that there is no load on the inner surface of the receiving channel 10 and thus it cannot be damaged during implantation. With respect to the three-sided elliptical cross-section of the receiving channel 10 in the illustrated embodiment, the pores 88 can be arranged "conformingly" in the cross-section, i.e., it may be arranged in the main direction characterized by the maximum value of the radius, or it may be arranged at a certain offset with respect to the main direction.

[0253] As shown in FIGS. 26 to 28, in all preferred embodiments, the implants 1, 1', 1'', 1''' further have a more highly useful function and, further, are considered an independent invention either by themselves or in combination with any number of the functions described above. According to this feature, the implants 1, 1', 1'', 1''' as part of their inner connection system 80 include a feedback structure 90 that conveys feedback to the user after appropriately and completely fitting a connection pin, such as that of a related second implant part (e.g., abutment), into the receiving channel of the implants 1, 1', 1''. To provide this feedback, the feedback system 90 includes pores or grooves 92 disposed on the inner surface of the receiving channel that, in the embodiment shown at its bottom end 84, circularly surround the receiving channel 10. This circular groove 92 can interact with or receive one or more corresponding protrusions of a dental fitting, such as those described in European Patent Application No. 16151231.4, and / or protrusions of a retaining element, such as those described in European Patent Application No. 15178180.4 by the same applicant, both applications being incorporated herein by reference. As soon as the connection pin is fully and adequately embedded in the receiving channel 10, these protrusions snap into the groove 92 with an audible "click", thereby allowing the user to confirm that the proper embedding of the connection pin into the receiving channel 10 has been completed.

[0254] In yet another alternative embodiment of the implant 1'''', as shown in FIGS. 29, 30, and 31 (side views), the crown end 6 has a specific shaped design. This feature, which is considered an independent invention either by itself or in combination with any number of the functions described above, provides an improved positional orientation of the implant 1'''', along with improved overall system strength during implantation. This is achieved by the fact that the width of the top / upper or crown surface 100 of the implant 1'''', i.e., the wall width of the implant 1'''', varies with an inverse gradient and as a result of the top and valley portions, such that it is larger at the valley portion and smaller at the peak portion, as shown in FIGS. 29 and 30.

[0255] Specifically, the crown surface 100 of the implant 1’’’’ has a wavy, corrugated or sinusoidal profile with a highest point and a lowest point of the crown surface 100. That is, the maximum height and the minimum height in the longitudinal direction of the implant 1’’’’ are alternately arranged along the circumference of the crown end 6 of the implant 1’’’’. At the highest point of the crown surface 100, preferably near these highest points, the crown end 6 of the implant 1’’’’ has a tapered shape or configuration, that is, an inverse taper shape or configuration. As a result, the lateral dimension or extent of the cross-section of the crown end 6 perpendicular to the longitudinal direction of the implant 1’’’’ decreases along the direction from the root tip 4 of the implant 1’’’’ towards the crown end 6 of the implant 1’’’’ (see FIGS. 29 and 30).

[0256] Due to this wavy, corrugated or sinusoidal profile and the inverse taper shape or configuration of the implant 1’’’’, the wall width of the implant 1’’’’, that is, the width of the wall of the implant 1’’’’ at the crown end 6, also varies. Specifically, the wall width is larger at the lowest point of the crown surface 100 and smaller at the highest point of the crown surface 100.

[0257] Either by itself or in combination with any number of the above functions, the above-described features of the crown surface 100 are considered an independent invention. These features enable a particularly reliable and simple identification of the orientation of the implant. In the embodiment shown in FIG. 29, due to the preferred design that conforms to the contour of its core forming zone 22 and further the thread forming zone 30 - the implant 1’’’’ has a triangular-elliptical cross-section, that is, each cross-section is characterized by three main directions where the radius is at a maximum value. In synchronization with this cross-sectional shape, at positions conforming to these main directions, the crown end 6 is further at a maximum as shown in a direction parallel to the longitudinal axis of the implant 1’’’’. In other words, the crown surface 100 of the implant 1’’’’ is not a flat surface, but rather has a wavy, sinusoidal structure with its highest points arranged in the main directions defined by the forming zones 22, 30 as described above.

[0258] In yet another preferred embodiment of the implant 1’’’’’, the tip or root tip 4 may be specifically designed to facilitate implantation into the bone material, particularly with respect to the external thread 12 of this section. For this purpose, at least the tooth tip of the thread 12 may be serrated as can be seen in FIG. 32. In this embodiment, a plurality of grooves 102 having at least a cutting end may be defined at the tooth tip and / or the crown surface of the thread 12.

[0259] FIG. 33 shows an embodiment of an implant according to the invention having at least one interrupted tooth tip cutting groove 104, which can be defined (or crushed or cut) at least at the tooth tip half of the thread 12. As can be seen in FIG. 33, the cutting groove does not extend into the core of the implant. An implant according to this embodiment can also have two or more of such cutting grooves. Also in this embodiment, the thread can be considered a serrated thread.

[0260] The serrated thread helps the implant to be implanted into the hole when used in the patient's extraction socket. Since the angle of the socket wall is not perpendicular to the axis of the implant, one side of the wall first contacts the implant and affects the positioning of the implant. To help reduce this effect, the serrated thread cuts the bone on the side of the implant.

[0261] Furthermore, these features, either by themselves or in combination with any number of the above-described functions, are considered independent inventions.

[0262] The implants 1, 1’, 1’’, 1’’’, 1’’’’, 1’’’’’ of any of the above-described embodiments, or any combination thereof, are preferably designed according to the specific requirements given by the individual treatment of the patient over their entire overall length. In the embodiments shown in the figures above, the normal “standard” value of the overall length of each implant can be about 13 mm. In other embodiments, the implant may be designed in a “short version” having an overall length of, for example, about 7 mm. An example of this embodiment is shown in FIG. 34.

[0263] FIG. 36 shows an implant tool 200 according to a first embodiment of the present invention.

[0264] The implant tool 200 is an implant tool for implanting a dental implant into a patient's bone tissue. The implant tool 200 includes a proximal portion 202 and a distal portion 204 as shown in FIG. 36(a). The distal portion 204 is configured to cooperate with the implant to screw the implant into the bone tissue.

[0265] The distal portion 204 has a holding element 206. The holding element 206 includes an attachment portion 208 for attaching the implant tool 200 to a dental implant. The holding element 206 is at least elastically deformable in all directions perpendicular to the longitudinal direction of the implant tool 200, that is, along all transverse directions of the holding element 206. The attachment portion 208 includes one protrusion 210 (see FIG. 36(b)) extending along a plurality of directions substantially perpendicular to the longitudinal direction of the implant tool 200, that is, along a plurality of transverse directions of the holding element 206.

[0266] The holding element 206 is formed integrally with one of the two parts of the implant tool 200, that is, the proximal part (see FIGS. 37(a) and (b)). Specifically, the holding element 206 is formed integrally with the proximal part of the implant tool 200 by two connecting parts 212 arranged between the holding element 206 and the proximal part in the longitudinal direction of the holding element 206 (see FIGS. 36(c) and 37(a)). Each of the connecting parts 212 extends along only a part of the circumferential direction of the holding element 206, as schematically shown in FIGS. 37(a) and (b) for example. The connecting parts 212 are arranged substantially opposite to each other in the radial direction of the holding element 206.

[0267] The retaining element 206 has a substantially cylindrical shape with a substantially circular cross-section with respect to the longitudinal direction of the retaining element 206 (see Fig. 37(a)). The retaining element 206 is formed as a hollow tubular body. The retaining element 206 has a closed annular or closed circular ring shape (i.e., an annular shape without an opening in its circumference). The elastic deformability of the retaining element 206 along all its transverse directions is provided by appropriately selecting the material and wall thickness of the retaining element 206.

[0268] The retaining element 206 may be made of, for example, a metal (such as titanium, a titanium alloy or stainless steel), a polymer or a composite material. The retaining element 206 can be elastically compressed in its transverse direction when the implant tool 200 is attached to the dental implant (see Figs. 37(d) and 39).

[0269] The protrusion 210 of the attachment portion 208 enables the implant tool 200 to be attached to the dental implant by snap fit, as will be described in detail below with reference to Figs. 37(d) and 39.

[0270] As shown in Fig. 37(a), the protrusion 210 of the attachment portion 208 is provided between two connecting portions 212. In this way, a particularly reliable and effective snap fit between the attachment portion 208 and the dental implant can be ensured.

[0271] The distal portion 204 of the implant tool 200 has a drive region 214 (see Figs. 36 - 38). In the drive region 214, the cross-section of the distal portion 204 perpendicular to the longitudinal direction of the implant tool 200 has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus a higher value than the adjacent azimuths (see Fig. 38(d)).

[0272] The drive region 214 of the distal portion 204 of the implant tool 200 cooperates with the implant. The drive region 214 constitutes an anti-rotation structure. The drive region 214 is configured to avoid relative rotation between the implant tool 200 and the implant around the longitudinal axis of the tool 200 when the tool 200 and the implant fit together, for example, by partially introducing the distal portion 204 of the tool 200 into the implant socket.

[0273] The drive region 214 is configured to cooperate with a corresponding anti-rotation structure of the implant, i.e., a drive portion, as will be described in more detail below (see FIGS. 37(d) and 39).

[0274] The main directions of the drive region 214 of the implant tool 200, each radius of the cross-section having a maximum value, are arranged axially symmetrically with respect to the longitudinal central axis of the implant tool 200 (see FIG. 38(d)). The number of main directions of the drive region 214 is three, i.e., the drive region 214 has a three-sided elliptical cross-section as shown in FIG. 38(d). In combination with the symmetric arrangement of the main directions with respect to the longitudinal direction of the implant tool 200, this three-sided ellipse results in a rotational offset angle between two adjacent main directions of 120 degrees.

[0275] The drive region 214 has a tapered shape, such that in the drive region 214, the lateral dimension or extent of the cross-section of the distal portion 204 perpendicular to the longitudinal direction of the implant tool 200 decreases along the direction from the proximal end of the implant tool 200 towards the distal end of the implant tool 200 (see FIGS. 36, 37 and 38).

[0276] The drive region 214 is arranged proximal to the retaining element 206.

[0277] The cross-sectional shape of the drive region 214 enables an efficient, reliable and uniform transfer of the rotational force applied to the implant tool 200 around its longitudinal axis to the implant.

[0278] In a modification of the first embodiment of the implant tool 200 shown in FIG. 38(e), the tool 200 has no drive region. Rather, as shown in FIG. 38(e), the cross-section along line A-A of FIG. 38(c) has a circular shape.

[0279] The distal portion 204 of the implant tool 200 further has a drive section 216, and the cross-section of the distal portion 204 perpendicular to the longitudinal direction of the implant tool 200 has a plurality of radial protrusions 218 and a plurality of radial recesses 220 that are alternately arranged along the circumference of the cross-section (see FIG. 38(f)). Each of the radially outermost points 222, 224 of the radial protrusions 218 is on a corresponding circle around the center of the cross-section, as shown in FIG. 38(f).

[0280] The cross-section of the distal portion 204 of the implant tool 200 of the drive section 216 has the same number, that is, six radial protrusions 218 and radial recesses 220 respectively.

[0281] The radial protrusions 218 include a first radial protrusion and a second radial protrusion. Thus, all of the radially outermost points 222 of the first radial protrusion are on a single first circle around the center of the cross-section, and all of the radially outermost points 224 of the second radial protrusion are on a single second circle around the center of the cross-section. The second circle has a smaller radius than the first circle (see FIG. 38(f)). The first radial protrusion and the second radial protrusion, together with the corresponding radial recesses 220 arranged therebetween, are alternately arranged along the circumference of the cross-section. The number of the first radial protrusions is the same as the number of the second radial protrusions.

[0282] The radial protrusions 218 and / or the radial recesses 220 of the cross-section of the drive section 216 each have a curved shape, for example, at least partially circular shape, at least partially elliptical shape, at least partially oval shape, etc. The radial protrusions 218 and the radial recesses 220 are arranged directly adjacent to each other.

[0283] The radially innermost point 226 of the radial recess 220 is on a single circle 228 around the center of the cross-section. Thus, all the radially innermost points 226 of the radial recess 220 are on the same circle 228 around the center of the cross-section.

[0284] The drive section 216 may have a length in the longitudinal direction of the implant tool in the range of 0.5 to 1.2 mm.

[0285] The drive section 216 of the distal portion 204 of the implant tool 200 cooperates with the implant. The drive section 216 constitutes an anti-rotation structure. The drive section 216 is configured to avoid relative rotation between the implant tool 200 and the implant around the longitudinal axis of the tool 200 when the tool 200 and the implant fit together, for example, by at least partially introducing the distal portion 204 of the tool 200 into the implant socket.

[0286] The drive section 216 is configured to cooperate with a corresponding anti-rotation structure of the implant, namely a drive zone, as will be described in more detail below (see FIGS. 37(d) and 39).

[0287] Thus, the distal portion 204 of the implant tool 200 according to the first embodiment of the present invention has a drive region 214 and a drive section 216. The drive region 214 is arranged proximal to the drive section 216 (see FIGS. 36 to 38).

[0288] Due to the presence of two anti-rotation structures (i.e., a drive region and a drive section) in the distal portion 204 of the implant tool 200 that can cooperate with two corresponding anti-rotation structures of the implant (i.e., the drive region and the drive section), when the implant is implanted into bone tissue, the rotational force or load applied to the implant can be shared by the two structures. Thus, any damage to either of these two structures of the implant can be minimized. Then, one or both of these structures of the implant can be reliably and efficiently used as an indicator for abutments, scan posts, impression posts, etc. after the implant has been implanted into bone tissue.

[0289] The drive region 214 and the drive section 216 are further useful for accurately positioning the implant tool 200 relative to the implant. Due to the cross-sectional shape of these elements, only three relative rotational positions between the tool 200 and the implant are possible.

[0290] The distal portion 204 of the implant tool 200 further has a retaining element 206 as described above. The drive section 216, the retaining element 206, and the drive region 214 are arranged in this order in a direction from the distal end of the implant tool 200 towards the proximal end of the implant tool 200.

[0291] The implant tool 200 consists of two separate parts, namely a distal part 230 and a proximal part 232, which are attached to each other as shown in FIGS. 37(a)-(c).

[0292] The distal part 230 of the implant tool has a convex portion that fits into a corresponding concave portion of the proximal part 232 of the implant tool 200 (see FIGS. 37(c) and (d)). The distal part 230 and the proximal part 232 are attached to each other by inserting the convex portion into the concave portion. The convex portion is held in a predetermined position inside the concave portion by friction fitting using a press fit shoulder 234 of the distal part 230 disposed distally of the convex portion (see FIG. 37(b)). The press fit shoulder 234 further has a sealing function against liquid.

[0293] The convex and concave portions have corresponding anti-rotation structures to prevent any rotation of the distal portion 230 and the proximal portion 232 relative to each other around the longitudinal axis of the implant tool 200. The anti-rotation structure of the distal portion 230 has a cross-section perpendicular to the longitudinal direction of the implant tool 200, i.e., the outer cross-section of the convex portion, which is non-circular, i.e., substantially square (see Fig. 37(a)). The anti-rotation structure of the distal portion 230 of the implant tool 200 can cooperate with the corresponding anti-rotation structure of the proximal portion 232 of the implant tool 200. The anti-rotation structure of the proximal portion 232 of the implant tool 200 has a cross-section perpendicular to the longitudinal direction of the implant tool 200, i.e., the inner cross-section of the concave portion, which is non-circular, i.e., substantially square. The cross-sections of the anti-rotation structures of the distal portion 230 and the proximal portion 232 are substantially the same.

[0294] The distal portion 230 includes a drive section 216, and the proximal portion 232 includes a holding element 206 and a drive region 214. Thus, the manufacture of the implant tool 200, particularly the manufacture of the holding element 206, can be particularly simplified.

[0295] The holding element 206 is integrally formed with the proximal portion 232. Figs. 37(d) and 39 show a combination of an implant tool according to a first embodiment of the present invention and a dental implant 201 according to an embodiment of the present invention, in which a part of the distal portion 204 of the implant tool 200 is implanted into the implant 201. In the state shown in these drawings, the implant tool 200 is fully fitted with the implant 201.

[0296] The dental implant 201 is made of metal (e.g., titanium, titanium alloy or stainless steel).

[0297] The dental implant 201 is for implantation into a patient's bone tissue. The dental implant 201 includes a core body 205 having a root tip 207 and a crown end 209, as shown in Fig. 39(a).

[0298] The dental implant 201 has a socket or channel 236 formed in the crown portion of the implant 201 for receiving a part of the distal portion 204 of the implant tool 200 that includes the retaining element 206 (see FIGS. 37(d) and 39(b)). The core 205 includes the channel 236. The channel 236 opens to the crown end 209 and extends in the longitudinal direction of the implant 201 from the crown end 209 towards the root tip 207 (see FIGS. 39(a) and (b)).

[0299] The crown portion of the implant 201 is formed with a cavity 238 for receiving the projection 210 of the attachment portion 208 of the retaining element 206 (see FIGS. 37(d) and 39(b)). Thus, the attachment portion 208 of the retaining element 206 can be securely held within the crown portion of the implant 201 by snap - fitting.

[0300] Furthermore, the dental implant 201 has an outer threaded portion 203 for screwing the implant 201 into the patient's jawbone tissue (see FIGS. 39(a) and (b)).

[0301] When the implant tool 200 is attached to the implant 201, a part of the distal portion 204 of the implant tool 200 is inserted into the channel 236 of the implant 201. As a result, the projection 210 of the attachment portion 208 of the retaining element 206 is received in the cavity 238 formed in the crown portion of the implant 201. Thus, the retaining element 206 is firmly held within this crown portion by snap - fitting, and thus the implant tool 200 is firmly attached to the implant 201.

[0302] In the process of attaching the implant tool 200 to the implant 201, when the retaining element 206 is inserted into the channel 236, the retaining element 206 first elastically deforms in its transverse direction, that is, it is elastically compressed, and then when the protrusion 210 is received in the cavity 238, it returns to its original shape. This "snap fit" process of the protrusion 210 provides audible and tactile feedback to the user of the implant tool 200 (e.g., a clinician or technician in a dental laboratory) indicating that the implant tool 200 has been properly implanted into the implant 201 (see FIGS. 37(d) and 39).

[0303] In this fully fitted state of the implant tool 200, the implant tool 200 may be used to pick up the implant 201 and transport it to the implant site where it is to be implanted into the bone tissue. Due to the secure fit between the tool 200 and the implant 201, any risk of the implant 201 coming off the implant tool 200 before it reaches the desired position can be reliably avoided.

[0304] Furthermore, in this fully fitted state of the implant tool 200, the drive region 214 and the drive section 216 of the distal portion 204 of the implant tool 200 are respectively fitted with the drive portion 240 and the drive zone 242 of the implant 201 as shown in FIGS. 39(b) and (c). The core 205 of the implant 201 has the drive portion 240 and the drive zone 242. The drive zone 242 is disposed at the top end of the drive portion 240 as shown in FIG. 39(b). In the drive portion 240 of the implant 201, the cross-section of the channel 236 of the implant 201 perpendicular to the longitudinal direction of the implant 201, that is, the inner cross-section, has a plurality of main directions. In these main directions, the radius corresponding to the distance between the center of the cross-section and its outer contour reaches a relative maximum value, and thus is higher than the adjacent azimuth values. The cross-section of the drive region 214 of the implant tool 200 and the drive portion 240 of the implant 201 are substantially the same.

[0305] The drive part 240 has a tapered shape. As a result, in the drive part 240, the lateral dimension of the cross-section of the channel 236 perpendicular to the longitudinal direction of the implant 201 decreases along the direction from the crown end 209 to the root tip 207, as shown in FIG. 39(b).

[0306] In the drive zone 242 of the implant 201, the cross-section of the channel 236 of the implant 201 perpendicular to the longitudinal direction of the implant 201, i.e., the inner cross-section, has a plurality of radial protrusions and a plurality of radial recesses that are alternately arranged along the circumference of the cross-section, and can have a plurality of radial recesses that are alternately arranged along the circumference of the cross-section. Thus, each of the outermost radial points of the radial protrusions is on a corresponding circle around the center of the cross-section, as shown in FIG. 39(c).

[0307] The cross-section of the channel 236 of the implant 201 in the drive zone 242 has the same number, i.e., six radial protrusions and radial recesses respectively (see FIG. 39(c)).

[0308] The radial protrusions in the drive zone 242 include a first radial protrusion and a second radial protrusion. Thus, all of the outermost radial points of the first radial protrusion are on a single first circle around the center of the cross-section, and all of the outermost radial points of the second radial protrusion are on a single second circle around the center of the cross-section. The second circle has a smaller radius than the first circle. The first radial protrusion and the second radial protrusion, together with the corresponding radial recesses arranged therebetween, are alternately arranged along the circumference of the cross-section of the drive zone 242. The number of the first radial protrusions is the same as the number of the second radial protrusions.

[0309] The radial protrusions and the radial recesses of the cross-section of the drive zone 242 each have a curved shape, for example, at least partially circular, at least partially elliptical, at least partially oval, etc. The radial protrusions and the radial recesses are arranged directly adjacent to each other.

[0310] The radially innermost points of the radial recesses are on a single circle around the center of the cross-section. Thus, all the radially innermost points of the radial recesses are on the same circle around the center of the cross-section.

[0311] The drive zone 242 may have a length in the longitudinal direction of the dental implant 201 in the range of 0.5 to 1.2 mm.

[0312] The cross-sections of the drive section 216 of the implant tool 200 and the drive zone 242 of the implant 201 are substantially identical.

[0313] Thus, the implant 201 can be screwed into the bone tissue by the respective cooperation or interaction between the drive region 214 and the drive section 216 of the distal portion 204 of the implant tool 200 and the drive portion 240 and the drive zone 242 of the implant 201. As described above, due to the presence of the drive region 214 and the drive section 216 that can cooperate with the drive portion 240 and the drive zone 242, when the implant 201 is implanted into the bone tissue, the rotational force or load applied to the implant 201 can be shared by the two structures, thus minimizing the risk of damage to the implant 201.

[0314] FIG. 40 shows an implant tool 300 according to a second embodiment of the present invention. The implant tool 300 according to the second embodiment is different from the implant tool 200 according to the second embodiment, especially in that the implant tool 300 is made of a single piece of material. Thus, all the elements of the implant tool 300 are integrally formed with each other.

[0315] The general structure and function of the implant tool 300 are substantially the same as those of the implant tool 200. Specifically, the implant tool 300 includes a proximal portion (not shown) and a distal portion 304. The distal portion 304 has a drive section 316, a retaining element 306, and a drive region 314, which are arranged in this order in a direction from the distal end to the proximal end of the implant tool 300, as shown in FIGS. 40(a) and (b). Further, the implant tool 300 has a notch 320 in the drive section 316 to facilitate the manufacture of the implant tool 300, particularly with respect to the manufacture of the retaining element 306.

[0316] FIGS. 41 and 42 show a dental implant 401 according to an embodiment of the present invention.

[0317] The dental implant 401 is a self-drilling dental implant for implantation into a patient's jawbone or bone tissue. The dental implant 401 includes a core body 402 having a root tip 404, a crown end 406, and an outer surface 408 extending along the longitudinal direction of the implant 401 between the root tip 404 and the crown end 406, as shown in FIG. 41(a).

[0318] The dental implant 401 is made of metal (e.g., titanium, titanium alloy, or stainless steel).

[0319] The implant 401 further includes a thread 412 extending outward from the core body 402 (see FIGS. 41(a) and (c) and FIGS. 42(a) and (b)). The thread 412 has a thread angle of about 10 degrees.

[0320] The thread 412 has a root surface 414 facing the root tip 404 of the core body 402 and a crown surface 416 facing the crown end 406 of the core body 402. The thread 412 has a first longitudinal groove 418 formed therein, i.e., a first cutting groove 418 (see FIGS. 41(a) and (b) and FIG. 42(b)). The first longitudinal groove 418 extends from the root tip to the crown end of the thread 412. As shown in FIG. 42(b), the first longitudinal groove 418 extends beyond the first three complete rotations of the thread 412.

[0321] The thread 412 has, at the tip of its tooth, a recess 420 formed in the crown surface 416 thereof, and the recess 420 extends in a direction from the crown surface 416 toward the root tip surface 414 along a part of the thickness of the thread 412. The recess 420 is open to the first longitudinal groove 418 as shown in FIGS. 41(a) and 42(b). The recess 420 is provided adjacent to, i.e., directly adjacent to, the first longitudinal groove 418. The recess 420 has a cutting function, i.e., a function of cutting bone tissue.

[0322] The thread 412 further has a second longitudinal groove 418' and a third longitudinal groove 418'' (see FIGS. 41(a) and (b) and FIGS. 42(a) and (d)). The first to third longitudinal grooves 418, 418', 418'' are arranged in a stagger arrangement or a displaced arrangement along the length of the thread 412 and along the circumference of the thread 412. Specifically, as shown in FIG. 41(a), the second longitudinal groove 418' is arranged in a stagger arrangement or a displaced arrangement with respect to the first groove 418 along the length and the circumference of the thread 412. The third longitudinal groove 418'' is arranged opposite to the first longitudinal groove 418 in the radial direction of the implant 401 and at a position of substantially the same height or length of the thread 412 (see FIGS. 41(b) and FIGS. 42(a) and (b)). The first to third longitudinal grooves 418, 418', 418'' and the recess 420 make the implant 401 a self-drilling type.

[0323] The first and third longitudinal grooves 418, 418'' extend in a direction inclined or slanted with respect to the longitudinal direction of the implant 401 (see FIGS. 42(a) and (b)). The second longitudinal groove 418' extends in a direction substantially parallel to the longitudinal direction of the implant 401 (see FIG. 41(a)).

[0324] The first to third longitudinal grooves 418, 418', 418'' extend along a part of the circumference of the core body 402 in the width direction of the longitudinal grooves.

[0325] The extension of the recess 420 in the direction from the crown surface 416 towards the root apex surface 414 varies along a direction parallel to the crown surface 416 (see FIGS. 41(c) and 42(b) and (c)). In particular, the depth of the recess 420 decreases along a direction away from the first longitudinal groove 418 in the circumferential direction, as shown in FIG. 42(b). Thus, a particularly effective cutting function of the recess 420 is achieved.

[0326] Therefore, the maximum depth of the recess 420 exists in the portion of the recess 420 that is disposed immediately adjacent to the first longitudinal groove 418.

[0327] Specifically, the recess 420 has an approximately quarter-spherical shape, as shown in FIGS. 41(c) and 42(b) and (c). This shape of the recess 420 enables the recess 420 and thus further the implant 401 to be manufactured in a particularly simple and cost-effective manner.

[0328] The recess 420 is disposed on the upstream side of the first longitudinal groove 418 in the rotational direction of the implant 401 (see FIG. 42(b)).

[0329] The recess 420 is formed on the crown surface 416 of the thread 412 at the first complete rotation of the thread 412, that is, at the complete rotation at the most root apex of the thread 412, as shown in FIGS. 41(a) and (c) and FIG. 42(b). This arrangement of the recess 420 enables a particularly stable and robust fit of the implant 401 with the jawbone or bone tissue.

[0330] The recess 420 efficiently cuts and removes bone material and helps to transport the removed bone material towards the crown end 406 of the core body 402.

[0331] The implant 401 of the present embodiment enables its implantation into the bone tissue with reduced force and high precision. Thus, a particularly stable and robust connection or fit between the implant 401 and the bone tissue, that is, high implantation stability, can be achieved.

[0332] Due to the arrangement of the recess 420 on the crown surface 416 of the thread 412, these effects can be achieved for substantially all implant thread angles of the thread 412, particularly for small implant thread angles (e.g., a thread angle of about 10 degrees).

[0333] FIG. 43 shows a dental implant 501 according to an embodiment of the present invention.

[0334] The dental implant 501 is a self - drilling dental implant for implantation into a patient's jawbone or bone tissue. The dental implant 501 includes a core body 502 having a root tip 504, a crown end 506, and an outer surface 508 extending along the longitudinal direction of the implant 501 between the root tip 504 and the crown end 506, as shown in FIG. 43(a). The implant 501 further includes a thread 512 extending outwardly from the core body 502 (see FIGS. 43(a) and (b)).

[0335] The dental implant 501 is made of a metal (e.g., titanium, titanium alloy or stainless steel).

[0336] The outer shape of the dental implant 501 may be substantially the same as any of the above - mentioned dental implants shown in FIGS. 1, 3, 6 and 7, for example, the dental implant 1.

[0337] Specifically, the dental implant 501 may have a first core - forming zone where the cross - section of the core body 502 has a plurality of main directions, and in these main directions, the radius corresponding to the distance between the center of the cross - section and its outer contour reaches a relative maximum value and thus a higher value than the adjacent azimuths. In particular, the core body 502 of the first core - forming zone may have a triangular - elliptical cross - section (see FIG. 43(c)).

[0338] The dental implant 501 may have a core - forming zone where the cross - section of the core body 502 is basically formed into a circular shape.

[0339] The dental implant 501 may have a core transition zone located between the core forming zone and the core circular zone. In the core transition zone, the cross-sectional shape of the core body 502 continuously changes from a basically circular shape adjacent to the core circular zone to a shape corresponding to the cross-sectional shape of the first core forming zone as a function of parameters specific to the longitudinal coordinates. In particular, the core body 502 of the core transition zone may have a triangular elliptical cross-section.

[0340] The dental implant 501 has a socket or channel 510 formed in the crown portion of the implant 501 (see FIGS. 43(a) to (c)). The channel 510 opens to the crown end 506 of the implant 501 and extends in the longitudinal direction of the implant 501 from the crown end 506 towards its root tip 504.

[0341] The core body 502 has a hexagonal meshing recess 515 where the cross-section of the channel 510 perpendicular to the longitudinal direction of the implant 501 is substantially hexagonal.

[0342] The channel 510 includes a conical portion 514, a hexagonal meshing recess 515, and an internally threaded portion 516 arranged in this order in the direction from the crown end 506 to the root tip 504 of the implant 501 (see FIGS. 43(b) and (c)). The conical portion 514 and the hexagonal meshing recess 515 are configured to receive the tip portions of the abutment and implant tool 200, 300, and the internally threaded portion 516 is configured to receive a connecting screw for fixing the abutment to the dental implant 501.

[0343] The conical portion 514 has a side wall that tapers inwardly with respect to the longitudinal axis of the dental implant 501 and provides a wide first opening by means of the channel 510 at the crown end 506 of the implant 501. The specific shape of the conical portion 514 defines a conical half-angle with respect to the longitudinal axis of the dental implant 501. This conical half-angle may be between about 10 degrees and about 20 degrees. That is, the angle between the inner wall of the conical portion 514 and the longitudinal centerline of the dental implant 501 may be between about 10 degrees and about 20 degrees. In one embodiment, the conical half-angle is about 12 degrees.

[0344] The ratio between the length of the conical portion 514 in the longitudinal direction of the implant 501 and the length of the hexagonal engagement recess 515 in the longitudinal direction of the implant 501 may be about 1:1. The length of the conical portion 514 may be at least about 1 mm, and the length of the hexagonal engagement recess 515 may be at least about 1 mm. The length of the conical portion 514 is the distance measured vertically from the upper surface of the implant 501 to the portion of the channel 510 where the tapered surface of the conical portion 514 ends. The length of the hexagonal engagement recess 515 is measured vertically from the end of the conical portion 514 to the end of the hexagonal engagement recess 515.

[0345] The ratio and length of the conical portion 514 and the hexagonal engagement recess 515 advantageously combine the advantages of a sufficiently long tapered shape connection to provide effective sealing and a sufficiently long hexagonal engagement recess 515. As a result, when the implant 501 is implanted into the patient's jawbone, sufficient driving torque can be transmitted to the implant 501.

[0346] The features of all embodiments of the dental implant of the present invention described above can be combined with each other or taken separately from each other. The features of all embodiments of the implant tool of the present invention described above can be combined with each other or taken separately from each other.

Description of Reference Numerals

[0347] 1, 1´, 1´´, 1´´´, 1´´´´, 201, 401, 501 Dental implants 2, 205, 402, 502 Cores 4,207,404,504 root tip 6,209,406,506 crown end 8,408,508 outer surface 10,236,510 receiving channel 12,203,412,512 thread 20 core circular zone 22 core forming zone 24 apex platform zone 26 core transition zone 26´ second core forming zone 28 enclosed volume 30 thread forming zone 32 thread circular zone 34 thread transition zone 34´ second thread forming zone 38 groove 40 groove forming zone 42 apex zone 43 intersection position 44 transition line 46 cutting groove 48 cutting end 50 center of cross-section 52 line 54 point 56 dotted line 58 free width 60 root tip surface 62 crown surface 64 longitudinal axis 66 line 70 bone tissue 72 cavity 74 platform 80 connection system 82 arrow 84 bottom end 86 scribed contour 88 pore 90 feedback structure 92 groove 100 crown surface 102 groove 104 root tip cutting groove 200,300 implant tool 202 proximal part 204,304 distal portion 206,306 holding element 208 mounting portion 210 protrusion 212 connecting portion 214,314 drive region 216,316 drive section 218 radial protrusion 220 radial recess 222,224 radially outermost points of the radial protrusion 226 radially innermost point of the radial recess 228 circle of the cross-sectional center circumference 230 distal part 232 proximal part 234 press fit shoulder 238 cavity 240 drive part 242 drive zone 320 notch 414 root thread surface 416 crown thread surface 418,418’,418’’ longitudinal groove 420 recess 514 conical portion 515 hexagonal engagement recess 516 internal threaded portion

Claims

**Claim 1** A dental implant (1'') for implantation into a patient's bone tissue, the dental implant (1'') comprising: - a core body (2) having a root tip (4), a crown end (6), and an outer surface (8) extending longitudinally between the root tip (4) and the crown end (6); and - at least one thread (12) extending outwardly from the core body (2); A cutting groove (46) is disposed in a threaded region of the implant (1''), and a line connecting a starting point on the root tip (4) side of one of the plurality of cutting grooves (46) and a starting point on the root tip (4) side of the cutting groove (46) adjacent to this cutting groove (46) is parallel to the direction in which the thread (12) of the implant extends. Dental implant (1''). **Claim 2** The cross-section of the core body (2) and its outer surface (8) has a triangular ellipse shape. In the core forming zone (22), the cross-section of the core body (2) has three main directions, and each cutting groove (46) is arranged at a given rotational misalignment angle α with respect to adjacent main directions when viewed in the orientation direction around the center (50) or the longitudinal central axis of the core body (2). The dental implant (1'') according to claim 1. **Claim 3** The dental implant (1'') according to claim 2, wherein the angle α is selected in consideration of the specific elasticity of the bone. **Claim 4** The dental implant (1'') according to claim 3, wherein the cutting groove (46) is spiral around the core body (2) of the implant (1'').

Images