RU2791007C2 - Tooth implant, instrument for insertion of tooth implant and combination of tooth implant and insertion instrument - Google Patents

Abstract

FIELD: medicine; surgical dentistry.

SUBSTANCE: group of inventions relates to medicine, namely to surgical dentistry; it is intended for use in dental implantation. A tooth implant is used to be inserted into patient’s bone tissue, containing a central part with an apical end, a coronal end, and an outer surface passing along a longitudinal direction between the specified apical and the specified coronal end, and at least one thread located on at least a threaded part of the specified outer surface and passing outwards from the specified central part. An instrument for insertion of a tooth implant into patient’s bone tissue is used for insertion of the tooth implant into patient’s bone tissue. Combinations of such an implant and such an insertion instrument are used.

EFFECT: inventions provide reliable and precise placement and engagement in jaw or bone tissue of an implant with a wide range of thread profile angles, as well as control, whether an insertion instrument and a tooth implant are correctly attached to each other, providing reliable insertion, while minimizing the risk of damage or destruction of the implant.

48 cl, 43 dwg, 1 tbl

Description

FIELD OF TECHNOLOGY

The invention relates to a dental implant, in particular for insertion into a patient's bone tissue, comprising a central part having an apical end, a coronal end and an outer surface extending along the longitudinal direction between said apical and said coronal ends, and at least one thread located at least on the threaded portion of said outer surface and extending outward from said central portion. The present invention also relates to a dental implant, in particular for insertion into a patient's bone tissue, comprising a central part having an apical end and a coronal end, the central part comprising a channel that is open to the coronal end and extends along the longitudinal direction of the implant from the coronal end along towards the apical end. In addition, the present invention relates to an insertion tool for inserting a dental implant into a patient's bone tissue. Furthermore, the present invention relates to a combination of such an implant and such an insertion tool.

BACKGROUND OF THE INVENTION

Dental implants are widely used in reconstructive therapy to replace missing teeth. They are usually inserted into the jawbone in place of an extracted or lost tooth, so that after the healing phase, for approximately four to twelve weeks, a prosthetic part is retained there, acting as a denture or crown. For this purpose, such a dental implant is usually made in the form of a metal formation of the appropriate form, inserted into the jawbone or bone tissue by screwing in the intended location. As a rule, the apical end of the dental implant contains a screw thread, in most cases a self-tapping screw thread, with which the dental implant is inserted into the corresponding prepared bone implant site.

Dental implants can be made as a one-piece design, in which the denture is attached directly to the implant after it has been inserted into the jawbone. Alternatively, in particular in order to facilitate insertion into the patient's mouth and in particular to allow particularly intensive preparation of the prosthesis before it is fixed to the implant even before the start of the patient's treatment, for example in a dental laboratory, dental implant systems can also have a multi-component configuration. . In particular, a two-piece design can be generally provided, wherein the dental prosthesis system comprises a first implant part, also referred to as an actual implant or post part, provided for insertion into the jawbone, and, in addition to this, an associated second implant part, also referred to as an element of the supporting part or an abutment, on which, in turn, a denture element, made in the form of a prosthesis or the like, can be installed.

The outer surface of the actual implant, or pin portion, is typically provided with a thread, which may be a self-tapping thread or a non-self-tapping thread. The implant or post part is usually anchored in the appropriately prepared bone bed of the jawbone implant. The design of the thread provided in the outer region of a dental implant is typically designed to provide high primary structural stability and uniform transmission of forces resulting from masticatory loading of a dental implant in the jawbone.

For this purpose, in particular for high primary stability after insertion of the implant into the bone tissue, various approaches to the configuration of the thread and the implant body are known from the prior art. Various types of thread geometries and their combinations can be provided, for example, the formation of different types of threads or threads with different thread parameters in different areas of the implant body. From WO 2008/128757 A2 an implant of the above type is known with additional screw recesses on the outer surface of the respective thread and/or directly on the implant body between two adjacent threads. Other systems may have a compression-type thread with narrow pockets. High primary stability can also be achieved by downsizing the hole drilled into the patient's bone in the area provided for the implant, such that when the implant is screwed into the central part of the implant body, the surrounding bone material is compressed along with the threads provided thereon. However, too much compression can cause the blood vessels in the bone to collapse, preventing the bone from healing after insertion.

Another common purpose of a particular implant design and the threads provided on it is the so-called secondary stability or osseointegration, which is the restoration of bone material in direct contact with the surface of the implant.

US 2007/0190491 A1 discloses an implant design with a non-circular cross-sectional geometry of the implant body. In the case of this design, it was recognized that most natural teeth are also not round in cross section, and therefore it is assumed that a similar design of the implant body cross section better matches the natural arrangement of blood vessels in the bone tissue, thus supporting reliable and rapid osseointegration.

Dental implants such as those described above are typically inserted into a patient's bone tissue using an insertion tool such as an implant driver. For this purpose, the distal part of the insertion tool is inserted into the bed provided in the coronal part of the implant. This distal part interacts with the implant bed so that after rotation of the insertion tool about its longitudinal axis, the implant is screwed into the bone tissue.

To ensure reliable and accurate placement of the implant in the bone tissue, the insertion tool must be correctly seated in the implant, i.e. fully engaged with the implant. Any inconsistencies and any misalignment between the insertion tool and the dental implant may make it difficult to insert the implant into the bone tissue and cause a risk of incorrect placement of the implant.

In addition, an insertion tool may be used to pick up an implant and deliver it to the implant site where it is to be inserted into bone tissue. In this case, if mismatches or misalignments occur between the instrument and the implant, the implant may fall out of the insertion instrument before it reaches the desired location. Such cases may even pose significant health risks to the patient if the implant is ingested or inhaled.

To match the friction between the insertion tool and the implant, US Pat. No. 7,131,840 B2 describes the use of an O-ring on the distal portion of the implant driver. However, the configuration described in this document does not allow the attending physician to reliably judge whether the insertion tool and the implant are correctly engaged with each other.

Another approach for improving the connection between the insert and the implant is disclosed in US Pat. No. 8,864,494 B2, using a retainer to connect the insert tool to the implant. After the implant is inserted into the bone tissue, the retaining element must be removed from the implant. Thus, this approach requires the use of an additional dental component in the form of a retainer and requires additional steps from the attending physician, which makes the implant insertion process difficult and time consuming.

Therefore, there is a need for a reliable, efficient, and simple approach for attaching an insertion tool, such as an implant driver, to a dental implant that provides a clear indication of whether the insertion tool and dental implant are correctly attached to each other.

Moreover, there is still a need for an insertion tool that allows the implant to be securely inserted into the bone tissue while minimizing the risk of damage or destruction of the implant, in particular its site.

In addition, there is a need for a dental implant that allows it to be securely inserted into bone tissue while minimizing the risk of damage or destruction of the implant, in particular its bed or channel.

As detailed above, a dental implant is typically inserted into a patient's jaw or bone tissue by screwing in at the intended location. For this purpose, the apical end of the dental implant contains a screw thread, in most cases a self-tapping screw thread, with which the dental implant is inserted into the respective prepared implant site.

The screw thread plays an important role in the secure and precise placement and engagement of the implant in the jaw or bone tissue. In particular, the screw thread must ensure smooth and precise insertion of the implant into the jaw or bone tissue and ensure stable engagement of the implant with the jaw or bone tissue after insertion.

To this end, WO 2016/125171 A1 describes the use of a threaded dental implant in which the apical surface of the thread has an apical surface recess extending proximally to the coronal surface of the thread. However, the configuration disclosed in this document only improves implant placement and stability over a limited range of thread profile angles, ie, thread profile angles greater than about 15°.

Therefore, there is a need for a dental implant that provides secure and accurate placement and engagement in jaw or bone tissue over a wide range of implant thread profile angles, in particular small thread profile angles.

BRIEF DESCRIPTION OF THE INVENTION

In view of these aspects explained above, the object of the invention is to provide a dental implant of the type mentioned above with even better properties in terms of primary and secondary stability. Another object of the present invention is to provide a dental implant that allows it to be securely inserted into the jaw or bone tissue, while minimizing the risk of damage or destruction of the implant, in particular its bed or channel. In addition, the present invention is directed to providing a dental implant that securely and accurately locates and engages in jaw or bone tissue over a wide range of implant thread profile angles, in particular small implant thread profile angles.

It is also an object of the present invention to provide a tool for inserting a dental implant into a patient's bone tissue, which effectively provides a reliable indication of whether the insertion tool and the dental implant are correctly attached to each other. Also, the invention is directed to providing a tool for inserting a dental implant into the bone tissue of a patient, which provides a reliable insertion, while minimizing the risk of damage or destruction of the implant, in particular, its bed or channel. The invention also provides a combination of such an insertion tool and a dental implant.

These goals are achieved by means of a dental implant with technical features according to claim 1, by means of a dental implant with technical features according to claim 4, by means of a dental implant with technical features according to claim 8, by means of a dental implant with technical features according to claim 8, by means of a dental implant with the technical features of claim 24, with a dental implant with the technical features of claim 32, with an insertion tool with the technical features of claim 41, with an insertion tool with the technical features of claim 42, with an insertion tool with technical features according to claim 43 and by combination with the technical features according to claim 54. Preferred embodiments of the invention follow from the dependent claims.

In accordance with the present invention, in an embodiment of the invention, this object is achieved by means of a dental implant (1), in particular for insertion into the patient's bone tissue, comprising:

- a central part (2) having an apical end (4), a coronal end (6) and an outer surface (8) extending along the longitudinal direction between said apical end (4) and said coronal end (6);

- at least one thread (12) extending outward from said central part (2), and

- the characteristic volume of the implant, defined by the specified central part (2) or the external volume (28) of the thread, defined by the specified thread (12), in which for each value of the parameter characteristic of the coordinate in the longitudinal direction of the implant, the cross section of the specified characteristic volume of the implant is characterized by the parameter eccentricity, defined as the ratio of the maximum distance of the contour of this cross section from its center to the minimum distance of the contour of this cross section from its center;

while the specified characteristic volume contains:

- at least one coronal zone, in which the specified eccentricity parameter has a maximum, preferably constant value, and the specified coronal zone runs along the longitudinal axis of the implant along the length of the coronal zone, constituting at least 10% of the total length of the implant;

- at least one apical zone, in which the specified eccentricity parameter has a minimum, preferably constant value, and the specified apical zone runs along the longitudinal axis of the implant along the length of the apical zone, constituting at least 30% of the total length of the implant, and

at least one transition zone located between said coronal zone and said apical zone, in which the eccentricity parameter, depending on the parameter characteristic of the coordinate in said longitudinal direction, continuously changes, preferably in a linear manner, from a minimum value next to said apical zone to the maximum value near the specified coronal zone, and the specified transition zone runs along the longitudinal axis of the implant along the length of the transition zone, constituting at least 10% of the total length of the implant.

In other words, in this embodiment, the implant, defined either by the body of its central part or by the outer volume of its thread, contains at least three functional areas, each of which has a certain minimum functional length, in order to provide its intended functionality. The first of these functional zones or regions is the coronal zone, in which the central part and/or the outer volume of the thread has a certain eccentricity in its geometry, providing a series of maximum and minimum values of the radius, as seen in cross section. The second functional zone or section is an apical zone in which the central part and/or the outer volume of the thread has a minimum eccentricity, preferably even an approximately circular cross section. The third functional zone, located between the first and second zones, is a transition zone that provides a smooth transition of the eccentricity (and, therefore, the symmetry of the cross section) along its length between the first and second zones. Due to this design, due to the low eccentricity, preferably even round cross-section of the implant at its apical end, a smooth and easy insertion of the implant into the bone material is ensured, while in the final stages of insertion, when the implant is already deeply anchored in the bone material, a relatively highly eccentric coronal the implant zone, due to its eccentricity, provides alternating phases of compression and decompression in the surrounding bone material after screwing. In turn, the transition zone provides a high degree of desired smooth transition and, therefore, after insertion, a smooth increase in alternating compression/decompression phases in the bone material.

In a preferred embodiment of the invention, in its eccentric parts, the implant is configured to oscillate particularly gently between compression and decompression phases in the bone material after screwing in. For this purpose, in a preferred embodiment of the invention, in said coronal zone and/or in said formed zone and/or in said transitional zone, the cross section of said characteristic implant volume has a number of main directions in which the radius measuring the distance between the center of the cross section and its outer contour, acquires a relative maximum value and, therefore, a higher value than in neighboring orientations.

In accordance with the present invention, in an embodiment of the invention, this object is achieved by a design in which the central part of the implant contains at least a first zone of the central part, in particular, made in the form of a formed zone of the central part, in which the first zone of the central part of the cross section of the central part has a number of main directions in which the radius, which measures the distance between the center of the cross section and its outer contour, acquires a relative maximum value and, therefore, a higher value than in neighboring orientations. In addition, in this embodiment of the invention, the central part contains a second zone of the central part, in particular, a circular zone of the central part, in which the second zone has a cross section of the central part of a generally circular shape, and the transition zone is located, as seen in the longitudinal direction of the implant, between said first, shaped zone and said second, circular zone, wherein in the transition zone, the geometry of the cross section of said central part, depending on the parameter characteristic of the coordinate in the longitudinal direction, changes from a basically circular shape located next to the second, circular zone , to a shape in which the cross section of said central part, in particular with respect to the overall geometry of the cross section and/or the values of its characteristic parameters, corresponds to the shape of the cross section in said first or formed zone.

In other words, the dental implant according to the present invention comprises a circular area with a circular or generally circular cross section, which in the preferred embodiment of the invention is located near or near the apical end of the implant. In this context, and also in the context mentioned below, "mostly round" refers to a shape that approximates a highly circular shape, resulting in minimal distortion or deviation, such as slight eccentricity, due to manufacturing tolerances, etc. This circular area, due to its circular cross-section, allows relatively easy engagement of the thread with the bone material, without applying too much stress to the bone tissue in the first moments when the implant is screwed into the bone material. Conversely, in a preferred embodiment of the invention, in another zone of the implant located closer to the central region of the implant or in close proximity to the other end of the implant, a central part is provided with a non-circular cross section having a number of protrusions or local maxima of the radius. In this area, when the central part of the implant is screwed into the bone tissue, the compressive force acting on the bone tissue oscillates between maximum compression, when (due to the rotational movement of the implant body) the local cross-sectional radius becomes maximum, and minimum compression, when local the cross-sectional radius becomes minimal. In particular, in the zone of the alveolar ridge, which has a relatively hard bone tissue, after insertion, this formed contour with local minima will lead to the formation of areas with low stress in the bone tissue in the immediate vicinity of the minima, which makes it possible to enhance the restoration of bone material and significantly minimize the negative impact of excessive compression on blood vessels.

In order to provide a smooth and expedient transition between these two different zones, the implant according to the present invention provides an additional core zone located between a pair of one circular zone and one non-circular zone. This transition zone is provided with a transitional cross-section, varying (as seen in the longitudinal direction) from a circular cross-section corresponding to the cross-section of the corresponding circular zone in a range close to the corresponding circular zone, to a non-circular, projecting cross-section corresponding to the cross-section of the corresponding zone of the non-circular cross section in a range close to this zone. Due to the presence of this transition zone, immediate and sudden changes in geometry, shear effects on the bone tissue and other destructive effects on the bone tissue can be avoided.

In combination, and in particular in the preferred embodiment of the invention, in which the annular zone is located near or near the apical end of the implant, the implant therefore allows relatively easy thread engagement with bone tissue in the first phase of screwing, with an oscillatory effect of compression on the bone tissue at later stage.

In an alternative embodiment of the invention, similar or equivalent effects can be achieved by designing the central part, in which the transition between the circular zone and the formed zone is carried out in stages. This alternative embodiment of the invention is considered inventive as such and can be used in accordance with the invention separately from or in combination with the first embodiment of the invention.

In this alternative embodiment of the invention, the object defined above is achieved by a construction in which the central part of the implant body comprises at least a first formed zone of the central part, and in the first formed zone of the central part, the cross section of the central part has a number of main directions in which the radius, measuring the distance between the center of the cross section and its outer contour, acquires a relative maximum value and, therefore, a higher value than in neighboring orientations. In addition, in this embodiment of the invention, the central part contains a second zone of the central part, in particular, a circular zone of the central part, and in the second zone, the cross-section of the said central part has a generally circular shape, which in the preferred embodiment of the invention is located near or next to the apical end of the implant, and the second formed zone of the central part, and in the second formed zone of the central part, the cross section of the central part has a number of main directions in which the radius measuring the distance between the center of the cross section and its outer contour acquires a relative maximum value and, therefore, a higher value than in neighboring orientations, and in the specified first formed zone of the central part, the parameter of the eccentricity of the central part, defined as the ratio of the maximum radius of the cross section of the specified central part to its minimum radius lower than in said second formed zone of the central portion. In other words, in this embodiment of the invention, the transition from a generally circular or circular geometry to a formed or non-circular geometry can be performed in stages by providing two or more non-circular, formed zones with different eccentricity parameters.

In yet another alternative embodiment of the invention, similar or equivalent effects can be achieved by a thread outer contour design similar to that of one or both of the embodiments of the invention as described above for the central portion. This alternative embodiment of the invention is considered inventive as such and can be used in accordance with the invention separately from or in combination with the first embodiments of the invention.

In particular, for purposes of explanation, the outer contour of a thread may be described by an outer volume or a shell volume defined by the thread. In this alternative embodiment of the invention, the above object is achieved by a construction in which the thread of the implant comprises a first thread zone, in particular in the form of a first formed thread zone, wherein in the first formed thread zone, the cross section of the outer volume enclosing the thread has a set of principal directions in which the radius, which measures the distance between the center of the cross section and its outer contour, acquires a relative maximum value and therefore a higher value than in adjacent orientations. In addition, in this embodiment of the invention, the thread contains a circular thread zone, in the preferred embodiment of the invention located near the apical end of the implant, and in the circular thread zone, the cross-section of the said external female volume is mainly circular in shape and, as seen in the longitudinal direction of the implant , a transition zone located between said first formed zone and said circular zone, wherein in the transition zone the cross-sectional geometry of said outer volume enclosing the thread, depending on the parameter characteristic of the coordinate in the longitudinal direction, changes from a mostly circular shape next to the specified by a circular thread area to a shape in which the cross section of said enclosing volume, in particular with respect to the overall geometry of the cross section and/or the values of its characteristic parameters, corresponds to the shape of the cross section in said first formed zone. Alternatively or additionally, a stepped transition can also be provided by providing a second formed thread zone with a different eccentricity than the first formed thread zone.

Preferred embodiments of the invention are the subject of the dependent claims.

In a preferred embodiment of the invention, the specified first or formed zone of the Central part and/or thread is made in the form of a platform zone of the alveolar ridge and is located near the coronal end of the implant. In particular, the area of the ridge platform can be configured to connect directly to the denture, i.e. in the case of a one-piece implant variant, or to the abutment supporting the denture, ie in the case of a two- or multi-piece implant variant. In yet another preferred embodiment of the invention, which is itself considered an independent invention, said crestal platform area formed, provided by the central part and/or outer thread contour, as seen in the longitudinal direction of the implant, has a length of at least 2.5 mm, preferably at least 3 mm. It was unexpectedly found that the formed, non-circular zone, in comparison with the contour of a circular shape, creates less or reduced stress in the bone tissue at local minima, which leads to fewer cell death and a decrease in bone tissue remodeling after implant insertion, faster apposition of new bone at implant surface and improved maintenance of the critical bone structure defined as the ridge lamina, buccal wall and lingual walls. Due to this, bone recovery as well as osseointegration is greatly improved by providing local minima of the formed zone in the region of critical bone construction, and it is believed that it is very useful for the purpose of osseointegration to provide these effects for a top layer with a thickness of at least 2.5 mm or even more preferably at least 3 mm in the ridge plate.

The cross section of the central part and/or the outer volume enclosing the thread can be characterized by an eccentricity parameter indicative of the deviation of the corresponding cross section from a circular shape. For the purposes of the present description and disclosure, and in accordance with 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 becomes 1 for a circular shape. This eccentricity parameter can be evaluated for each value of a parameter characteristic of a coordinate in a specified longitudinal direction, eg along the longitudinal axis of the implant (y). In order to ensure a particularly smooth transition between the end zone of the tip (= circular cross section, with an eccentricity parameter = 1) and the first or formed zone (= a longitudinal or non-circular cross section, with an eccentricity parameter > 1) in the preferred embodiment of the invention, the eccentricity parameter in the specified the transition zone of the central part and/or external thread has a linear dependence on the coordinate parameter in the longitudinal direction.

The main directions in the transition zone and/or in the first or formed zone of the central part and/or the thread, in which the corresponding cross-sectional radius has a local maximum, in the direction of rotation can be arranged in accordance with the desired effect on the bone tissue, in particular with individually selected corners. However, in another preferred embodiment of the invention, they are arranged symmetrically about the central longitudinal axis of said central part or said outer enclosing volume, respectively (axial symmetry). This design provides a relatively smooth and constant change in the amount of compression exerted on the surrounding bone tissue due to the screwing process.

In a preferred embodiment of the invention, which is particularly preferred, the external profile of the implant, defined by the external contour or the female volume of the thread, with respect to the longitudinal central axis of said central part and with respect to local maxima or minima, corresponds to the external contour of said central part. In other words, in this preferred embodiment of the invention, in these orientations with respect to the longitudinal axis in which the radius of the central part has a local maximum, the outer contour of the outer volume enclosing the thread also takes on a local maximum. This contour matching can be done by overlapping the respective major directions within a tolerance range of preferably ±20°, and can be accurate in the preferred embodiment of the invention. Of particular advantage is the “matching” design, in which, when the implant is inserted into the bone tissue, the bone is compressed and decompressed in accordance with the external geometry of the implant both on the outer surface of the central part and on the outer surface of the thread. Deconsolidation of the bone tissue at minimal radii between the main directions (both on the outer surface of the central part and on the outer surface of the thread) allows for particularly close contact of the bone with the implant and improved initial stability.

Preferably, the number of main directions in the transition zone and/or in the formed zone is three, that is, the central part in the formed zone and/or transition zone has a tri-oval cross section. In combination with the preferred implementation of the symmetrical arrangement of the main directions with respect to the longitudinal direction, this tri-oval shape results in a rotation offset angle between two adjacent main directions of 120°.

The implant, in view of its transition zone, is specially designed for a smooth and expedient transition (when performing the screwing process) between the first engagement of the thread in the bone tissue (in the circular zone) with molding and direct processing of the bone tissue by changing the compression (in the formed zone, preferably in the zone of the alveolar platform). comb). The smooth transition between these zones can be further improved in a particularly preferred embodiment of the invention, in which the central part in the transition zone has a conical or tapering shape, preferably with a taper/tapering angle of 1° to 12°, preferably 4° to 8°. In a particularly preferred embodiment of the invention, the taper/taper angle is selected according to the overall length and diameter of the implant.

Considering the suitable and convenient dimensions of the implant in relation to the requirements applicable to the bone environment, in a preferred embodiment of the invention the transition zone, as seen in the longitudinal direction, begins at a distance of about 2-4 mm from the apical end of the implant. In other words, in an alternative or additional preferred embodiment of the invention, the location of the circular central part and/or the thread zone in the apical part of the implant is considered highly beneficial in order to maximize the potential for high primary stability. This is useful in general, and also more specifically in tooth sockets after extraction, and immediate loading protocols may be preferred. In order to provide significant apical engagement, the circular zone, as seen in the longitudinal direction of the implant, preferably has a length of at least 2.5 mm.

In addition to the geometric design of the central part, in a particularly preferred embodiment of the invention, the thread as such is also specifically designed to provide a reliable bond to the bone tissue with high primary stability. For this purpose, the thread is preferably a flat thread. Even more preferably, the width of the flat thread passage, depending on the coordinate parameter in the longitudinal direction of the implant and starting from the apical end of the central part, continuously increases with increasing distance from said apical end. In this design, the thread in the region close to the apical end can have a relatively incisive small outer width, thereby providing a high cutting ability when the thread enters the bone tissue. With further screwing of the implant (that is, further entry of the implant into the bone tissue) in a given position in the bone tissue, the width of the flat thread continuously increases, thereby continuously expanding the corresponding local gap in the bone tissue and constantly strengthening the contact area between the bone tissue and the implant.

Further improvement of the properties of the implant can be achieved by further modification of the thread profile in an alternative or additional preferred embodiment of the invention. In this modification, which is itself considered inventive, in particular considered an independent invention, the thread preferably has an apical surface profile and a coronal surface profile, the apical surface being oriented substantially perpendicular to the longitudinal axis of the implant, i.e. the normal of the plane of the apical surface is oriented mainly parallel to the longitudinal axis of the implant. Thanks to this design, reliable contact of the apical surface with the surrounding bone material can be maintained even when, as a consequence of the non-circular outer contour, the lateral expansion of the apical surface of the thread varies between the minimum and maximum radii. In this embodiment of the invention, the orientation of the coronal surface is preferably chosen in accordance with the loads of the surrounding bony structure. It is preferably oriented at an angle, preferably about 60°, to the longitudinal axis, i.e. the normal of the ridge surface plane is oriented at an angle, preferably about 30°, to the longitudinal axis of the implant, the thread resulting in a trapezoidal thread. Due to this inventive geometry, in particular the orientation of the apical surface, the apical surface can absorb the load of bite forces quite effectively. In turn, the ridge surface in this geometry provides a relatively small and sharp free edge, improving bone cutting and a relatively wide and large base for stronger threading and compression during implant insertion.

In particular, this thread profile design is advantageous in combination with the cross-sectional shape of the outer contour of the central portion and/or the outer volume enclosing the thread. This shaped contour, in particular the tri-oval cross section, creates an oscillatory effect when the bone is compressed in the longitudinal direction of the implant when the implant is screwed into the bone material, the effects being limited or reduced using the orientation of the apical surface.

In an alternative or additional preferred embodiment of the invention, the transition zone and/or the shaped zone of the implant is provided with a number of cutting grooves, preferably equal to the number of main directions. These cutting grooves provide improved cutting capabilities of the implant body during screwing. Preferably, these cutting grooves are arranged symmetrically about the central longitudinal axis of the central portion. In particular, in an embodiment of the invention, which is considered an independent invention and which, in accordance with the present invention, can also be used to improve other cutting groove systems, each cutting groove, as seen in the direction of orientation around the central longitudinal axis of the central part, is located at a given displacement of rotation to the adjacent main direction.

Preferably, the cutting grooves in the direction of orientation are located relative to the adjacent main direction of the central part and/or external threads, taking into account that when the implant is screwed in, the local maximum associated with the main direction will lead to maximum compression of the bone material, while decompression after passing through the maximum will allow the bone material to a certain extent return to the central axis of the implant. This deconsolidation according to this aspect of the invention is used to selectively improve the cutting effect of the cutting grooves. Preferably, the location of the cutting grooves relative to the local maxima is such that a normalizing effect of the bone is achieved. In other words, the cutting grooves are positioned in the direction of rotation so that the decompressing bone material engages the cutting groove with particularly high efficiency when cutting hard bone but not soft bone, thereby maintaining the stability of the implant in softer bone.

In a preferred inventive embodiment, this is achieved by arranging the cutting grooves with an offset angle α with respect to the respective principal directions. In this embodiment of the invention, the angle α is chosen according to a selection criterion, which is itself considered an independent invention. In accordance with this selection criterion, the cutting edge 48 should be positioned such that the radius of the cutting edge, defined by the outer limit of the radial extension of the cutting edge from the longitudinal axis of the implant, is 20-75 µm less than the maximum radius in the respective major direction. This criterion takes into account the specific elastic properties of the bone, which, depending on its density, is restored or decompressed by approximately the same amount after compression. Preferably, the radius of the cutting edge is chosen to be about 35 µm less than the maximum radius, which, in accordance with the remaining geometric parameters of the central part, is converted into a preferred offset angle α of about 106°. With regard to typical bone properties, as well as typical dimensions and rotational speeds when the implant is screwed into the jawbone, the rotational offset of the arrangement of the grooves relative to the adjacent main direction is preferably 80 to 120°, in particular about 108°.

The advantages achieved in accordance with the present invention are, in particular, that both high primary stability and high secondary stability can be achieved with a particular geometric design. The implant according to the present invention has a circular zone with a generally circular cross section, in the case of the central part and/or threads, which ensures smooth engagement of the thread with bone tissue with reduced rotation around the transverse axis or staggering of the implant in combination with a formed zone with a non-circular , preferably with a tri-oval cross-section, allowing successive compression and decompression of the bone tissue and thereby help to hold the buccal bone in the alveolar crest or coronal region. A transition zone and/or an additional shaped zone of varying eccentricity provided between these zones provides a smooth transition that allows the bone tissue to gradually adjust to the effects of compression and friction reduction, as well as undesired grinding or cutting of the bone.

In accordance with one aspect of the invention, a tool is provided for inserting a dental implant, in particular a dental implant according to the present invention, into a patient's bone tissue. The insertion tool comprises a proximal part and a distal part, the distal part being designed to interact with the implant. The distal part has a retaining element, and the retaining element contains a fastening part for attaching an insertion tool to a dental implant. The holding element is configured to be elastically deformable in at least all directions perpendicular to the longitudinal direction of the insertion tool. The fastening part contains at least one protrusion extending in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool.

The retaining member may be integrally formed with or integrally connected to the insertion tool, for example the rest of the insertion tool.

The entire holding element of the insertion tool is resiliently deformable. The holding element is made with the possibility of elastic deformation along its entire length. The length of the holding element extends along its longitudinal direction, namely its axial direction, i.e. the longitudinal direction of the insertion tool, namely the direction from the proximal part of the insertion tool to the distal part of the insertion tool.

The proximal part of the insertion tool is the part that is closest to the attending physician when using the insertion tool. The distal portion of the insertion tool is the portion closest to the implant site when the insertion tool is used.

The distal part of the insertion tool is designed to interact with the implant. In particular, the distal part can interact with a corresponding part of the coronal part of the implant, such as the bed. The distal portion may be at least partially inserted into the bed. The distal part of the insertion tool interacts with the implant, for example with the implant bed, so that after rotation of the insertion tool about its longitudinal axis, the implant is screwed into the bone tissue. Due to the compatibility or interaction between the distal portion of the instrument and the implant, a rotational force applied to the insertion instrument about its longitudinal axis, for example manually or by a motor, is transmitted to the implant in order to screw the implant into the bone tissue.

The distal part of the insertion tool may have a drive part as part of it which interacts with the implant. The drive part may comprise or be an anti-rotation structure. The anti-rotation structure is configured to avoid relative rotation between the insertion tool and the implant around the longitudinal axis of the tool when the tool and implant are engaged with each other, for example, at least partially by inserting the distal part of the tool into the implant site. Thus, the rotational force applied to the insertion tool around its longitudinal axis is transferred to the implant. The counter-rotational design of the inserter tool may have a cross section, that is, an outer cross section perpendicular to the longitudinal direction of the inserter tool, that is not rotationally symmetrical, for example, that is non-circular. The anti-rotation design of the distal portion of the insertion tool can interact with the corresponding anti-rotation design of the implant. The anti-rotational implant design may have a cross section, eg an internal cross section perpendicular to the longitudinal direction of the implant, that is not rotationally symmetrical, eg that is non-circular. The cross sections of the anti-rotation structures of the instrument and the implant may be substantially the same or may have the same or corresponding shape.

For example, the drive portion of the distal portion of the insertion tool may be a drive region and/or drive portion, as will be described in detail below. The drive area and/or the drive area of the insertion tool can interact with the drive portion and/or the drive area of the implant, respectively.

Thus, the entire retaining element can be elastically deformed in at least all directions perpendicular to the longitudinal direction of the insertion tool, i.e. in all or all transverse directions of the retaining element, i.e. all radial directions of the retaining element.

The elastic deformability of the rest of the distal part of the insertion tool in directions perpendicular to the longitudinal direction of the insertion tool may be lower than that of the retaining member. The rest of the distal portion of the insertion tool may not be elastically deformable in directions perpendicular to the longitudinal direction of the insertion tool.

The retaining element may be integrally formed with or integrally connected to the insertion element, for example by the rest of the insertion tool. Thus, the holding member can become an integral part of the insertion tool.

The fastening part of the retaining element contains at least one protrusion or protrusion extending from the outer surface of the remaining part of the retaining element in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool.

At least one projecting part or protrusion of the fastening part is made with the possibility of receiving in the corresponding cavity formed in the coronal part of the dental implant.

The insertion tool is attached to the dental implant by attaching the attachment portion of the retaining member to the dental implant.

When attaching the fastening part of the retaining element to a dental implant, the retaining element is first elastically deformed, i.e. elastically compressed, along the transverse directions, i.e. the radial directions of the retaining element, and then restored to its original shape when at least one projection or protrusion has been received into corresponding cavity of the dental implant due to the restoring force of the retaining element. Therefore, the fastening part can be attached to the dental implant by snap connection in a reliable and efficient manner. Engagement of at least one protrusion or protrusion of the anchoring part with the corresponding cavity of the dental implant provides audible and/or tactile feedback to the user, such as the attending physician or dental technician, for example in a dental laboratory, providing a clear and unambiguous indication that the retaining element and therefore also the insertion tool is properly attached to the dental implant.

The entire holding element, and not just a part of it, is made with the possibility of elastic deformation along its transverse directions. In this way, a particularly high degree of flexibility of the holding element is achieved. In addition, the entire retainer is resiliently deformed when the insertion tool is attached to the dental implant, thus minimizing the risk of wear or breakage of the retainer even if the retainer repeatedly engages and is removed from different dental implants.

Therefore, the insertion tool of the present invention provides a clear, reliable and efficient indication of whether the insertion tool is properly attached to a dental implant.

The holding element may be integral with the insertion tool, for example the rest of the insertion tool. In this context, the term "integrated" means that the holding element and the insertion tool, for example, the rest of the insertion tool, are made in an integral configuration.

The integral configuration of the holding element and the insertion tool makes it possible to manufacture the insertion tool in a particularly simple and efficient manner, for example by injection molding, milling such as CNC milling, and the like.

The retaining member may be integrally attached to the insertion tool, for example to the remainder of the insertion tool. In this context, the term "integrally attached" means that the retainer is attached to the insertion tool in such a way that the retainer cannot be detached or separated from the inserter without damage or destruction of the retainer and/or inserter.

If the holding element is integral with or integrally attached to the insertion tool, a particularly secure and stable configuration of the insertion tool is achieved.

The retaining member may be substantially cylindrical in shape, for example with a substantially circular cross section perpendicular to the longitudinal direction of the insertion tool.

At least one protrusion or protrusion of the fastening part of the retaining element extends in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool, that is, in one or more of its transverse directions. In particular, the fastening part may comprise at least one protrusion or protrusion that extends in a plurality of transverse directions of the retaining element, that is, extends along the outer surface portion of the remainder of the retaining element in the circumferential direction of the retaining element. At least one protrusion or protrusion 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 rest part of the holding element.

The insertion tool may, for example, be made of a metal such as stainless steel, a polymer, or a composite material.

The retaining member and the remainder of the insertion tool may be made from the same material or from different materials. If the holding element is made of a material that differs from that of the rest of the insertion tool, the holding force provided by the holding element can be set in a particularly simple manner.

The retaining element may have at least one portion extending from the distal end of the retaining element to the proximal end of the retaining element, with at least one portion being more flexible than the remainder of the retaining element. This flexible part of the retaining element contributes to or even ensures the elastic deformability of the retaining element. Therefore, the retaining member can be formed in an elastically deformable manner in a simple and efficient manner.

At least one portion extending from the distal end of the retaining element to the proximal end of the retaining element may be made or formed from a material that is more flexible than the material of the remainder of the retaining element. As an additional or alternative option, at least one part may have a configuration or design with a greater degree of flexibility than the configuration or design of the rest of the retaining element. For example, at least one part can be made more flexible by providing, for example, perforations, recesses, holes, or the like. Also, for example, at least one part may have a smaller thickness, i.e. wall thickness, than the rest of the retaining element.

The retainer may have two or more, three or more, or four or more portions extending from the distal end of the retainer to the proximal end of the retainer, these portions being more flexible than the remainder of the retainer.

The retaining element may have at least one cut or recessed portion extending from the distal end of the retaining element to the proximal end of the retaining element. At least one cut or recessed part contributes to or even ensures the elastic deformability of the retaining element. The formation of the retaining element with such at least one cut or recessed part provides a particularly flexible configuration of the retaining element. In addition, the holding element has a particularly simple structure.

The retaining element may be a hollow and/or tubular body, with at least one cut or recessed part penetrating into the outer wall of the retaining element. The retaining element may have an open annular shape or an open circular shape, i.e. a ring shape with a hole around its circumference, or a substantially C-shaped cross section perpendicular to the longitudinal direction of the retaining element, i.e. longitudinal direction of the insertion tool.

The retaining element may have a closed annular shape or a closed circular shape, ie a ring shape without an opening around its circumference.

The holding element may be integral with or integrally connected to the insertion tool, e.g., the rest of the insertion tool, by means of one or more connecting parts located between the holding element and the insertion tool, e.g., the rest of it. One or more connecting parts can be located between the holding element and the insertion tool in the longitudinal direction of the holding element. Each of the one or more connecting parts may extend along only a portion of the holding element in the circumferential direction of the holding element.

In this way, the holding element can be integrated with the insertion tool in a particularly simple and secure manner.

At least one or some of the one or more connecting portions 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 portions may extend along 10% or more, 20% or more, 30% or more, or 40% or more of the circumference of the holding member.

The holding element may be integral with or integrally connected to the insertion tool through a plurality of connecting parts, for example, two connecting parts, three connecting parts, four connecting parts or five connecting parts, the connecting parts being located between the holding element and the insertion tool. , for example, its rest. The connecting parts can be separated from each other in the circumferential direction of the holding element, i.e. respectively arranged so that there is a gap between adjacent connecting parts in the circumferential direction of the holding element. The connecting parts can be equally spaced apart in the circumferential direction of the retaining element or spaced apart at different intervals in the circumferential direction of the retaining element. The connecting parts may have the same or different extensions along the circumference of the holding element, ie in the circumferential direction of the holding element.

The holding element may be integral with or integrally connected to the insertion tool, eg the rest of it, via a single connecting part. The retaining element may have a single part extending from the distal end of the retaining element to the proximal end of the retaining element, and this single part is more flexible than the rest of the retaining element. The single connecting part may be located opposite the single part in the radial direction of the retaining element or next to the single part in the circumferential direction of the retaining element.

The retaining member may be integral with or integrally connected to the insertion tool via a single fitting. The retaining element may have a single notched or recessed portion extending from the distal end of the retaining element to the proximal end of the retaining element. A single connecting part may be located opposite the cut or recessed part in the radial direction of the retaining element or next to the cut or recessed part in the circumferential direction of the retaining element.

The retaining element may be integral with or integrally connected to the insertion tool through a single connecting part. A single connecting part can be located opposite at least one protrusion or one protrusion of the fastening part in the radial direction of the retaining element or at least one protruding part or one protrusion of the fastening part in the circumferential direction of the retaining element.

The holding element may be integral with or integrally connected to the insertion tool via at least two connecting parts. At least two connecting parts can be located opposite each other in the radial direction of the retaining element.

The attachment portion of the insertion tool may comprise a plurality of, for example, two or more, three or more, four or more, or five or more protrusions or protrusions, each of which extends in one or more directions substantially perpendicular to the longitudinal direction. insert tool.

The plurality of projections or projections may have the same or different extensions in the circumferential direction of the holding element. The plurality of protrusions or protrusions may have the same or different protruding heights from the outer surface of the remainder of the retaining member, that is, heights from that outer surface in one or more directions substantially perpendicular to the longitudinal direction of the insertion tool.

The plural protrusions or protrusions of the fastening part may be arranged sequentially one after the other or sequentially in the circumferential direction of the retaining element, that is, so that one protrusion is located behind the other in this circumferential direction. The multiple protrusions or protrusions may be equally spaced or separated from each other at different intervals in the circumferential direction of the holding element.

The plural protrusions or protrusions of the anchoring part are designed to be received in the corresponding cavity or corresponding cavities formed in the coronal part of the dental implant.

As described in more detail above, the retainer may have at least one portion extending from the distal end of the retainer to the proximal end of the retainer, at least one portion being more flexible than the remainder of the retainer. The retaining element may have or may define at least one cut or recessed portion extending from the distal end of the retaining element to the proximal end of the retaining element. At least one projecting part or one protrusion of the fastening part of the insertion tool can be located adjacent to at least one more flexible part or at least one cut or recessed part of the retaining element. In this way, a particularly secure and effective snap-on connection between the holding element and the dental implant can be ensured.

The insertion tool may have a visual indicator, such as a marking, which is configured to provide further indication of whether the insertion tool and the dental implant are correctly attached to each other. For example, the visual indicator may comprise or be a coating, laser marking, groove, or the like. A visual indicator may be provided on the distal portion of the insertion tool.

The retaining element may be made of a single material. The retaining element may, for example, be made of a metal such as titanium, a titanium alloy or stainless steel, a polymer or a composite material. In this way, the retaining element can be formed in an elastically deformable manner in a particularly simple and reliable manner.

The material of the retaining member may be metallic, superelastic, amorphous, etc.

The retaining member may be manufactured, for example, by injection molding, milling such as CNC milling, etc. For example, the retaining member may be injection molded using a colored plastic, for example to provide a color code as a marking. If the retaining member is made of a metal such as titanium, titanium alloy or stainless steel, the retaining member may be anodized.

In accordance with one aspect of the invention, a tool is provided for inserting a dental implant, in particular a dental implant according to the present invention, into a patient's bone tissue. The insertion tool comprises a proximal part and a distal part, the distal part being designed to interact with the implant. The distal part has a drive region, and in the drive region, the cross section of the distal part, perpendicular to the longitudinal direction of the insertion tool, has a number of main directions in which the radius measuring the distance between the center of the cross section and its outer contour acquires a relative maximum value and, therefore, more higher value than in neighboring orientations.

The drive region of the distal insertion tool interacts with the implant. The drive region is an anti-rotation structure, such as the anti-rotation structure described above. The drive region is designed to avoid relative rotation between the insertion tool and the implant around the longitudinal axis of the tool when the tool and implant are engaged with each other, for example at least partially by inserting the distal part of the tool into the implant site.

The cross-sectional shape of the drive region, as detailed above, ensures efficient, reliable and uniform transmission of the rotational force applied to the insertion tool around its longitudinal axis to the implant. Thus, the insertion tool ensures a secure insertion of the implant into the patient's bone tissue, while minimizing the risk of damage or destruction of the implant, in particular its site.

The drive area of the distal part of the insertion tool is designed to interact with the corresponding anti-rotation structure, in particular with the drive part, of the implant. In the drive part of the implant, the cross section, i.e. the internal cross section of the implant bed or channel, perpendicular to the longitudinal direction of the implant, has a number of main directions in which the radius, which measures the distance between the center of the cross section and its outer contour, acquires a relative maximum value and, therefore , a higher value than in adjacent orientations. The cross sections of the drive region of the insertion tool and the drive portion of the implant can be substantially the same.

The cross section of the drive region of the insertion tool may have an eccentricity parameter characteristic of the deviation of the corresponding cross section from a circular shape. For the purposes of this description and disclosure, and in accordance with the present invention, this eccentricity parameter is defined as the ratio of the maximum cross-sectional radius to its minimum radius, such that the eccentricity parameter takes on the value 1 for a circular shape. The eccentricity parameter of the cross section of the drive region of the insertion tool is greater than 1. The eccentricity parameter can be, for example, in the range of 1.1 to 1.6, 1.2 to 1.5, or 1.3 to 1.4.

This eccentricity parameter can be estimated for each parameter value specific to the coordinate in the longitudinal direction of the insert tool. The eccentricity parameter of the drive region may be constant in the longitudinal direction of the insertion tool. Alternatively, the drive region eccentricity parameter may vary in the longitudinal direction of the insertion tool, such as decreasing from the proximal end of the tool to the distal end of the tool. The eccentricity parameter of the drive region may have a linear relationship with the coordinate parameter in the longitudinal direction of the insert tool.

In some embodiments of the invention, the main directions in the drive region of the insertion tool, in which the corresponding cross-sectional radius has a local maximum, are located symmetrically, in particular axially symmetrically with respect to the central longitudinal axis of the insertion tool.

The number of major directions in the drive area of the insertion tool may be three or more, four or more, five or more, or six or more.

In some embodiments of the invention, the number of major directions in the drive region of the insertion tool is three, i.e. the drive region has a tri-oval cross section. Combined with the symmetrical arrangement of the major directions with respect to the longitudinal direction of the insertion tool, as detailed above, this tri-ovality results in a rotation offset angle between two adjacent major directions of 120°.

The drive region may have a conical configuration such that, in the drive region, lateral dimensions or cross-sectional elongations of the distal portion perpendicular to the longitudinal direction of the insertion tool decrease along the direction from the proximal end of the insertion tool to the distal end of the insertion tool.

In the drive region, the cross-sectional area of the distal portion perpendicular to the longitudinal direction of the insertion tool, that is, the cross-sectional area of the distal portion, may decrease along the direction from the proximal end of the insertion tool to the distal end of the insertion tool.

In accordance with one aspect of the invention, a tool is provided for inserting a dental implant, in particular a dental implant according to the present invention, into a patient's bone tissue. The insertion tool comprises a proximal part and a distal part, the distal part being designed to interact with the implant. The distal part has a drive section. In the drive section, the cross section of the distal portion perpendicular to the longitudinal direction of the insertion tool has a plurality of radially convex portions and a plurality of radially concave portions which are arranged alternately around the perimeter of the cross section. Each of the radially outermost points of the radially convex portions is located on a respective circle around the center of the cross section. At least two of these circles have different radii from each other.

The drive section of the distal insertion tool interacts with the implant. The drive section is an anti-rotation structure, such as the anti-rotation structure detailed above. The drive section is configured to avoid relative rotation between the insertion tool and the implant about the longitudinal axis of the tool when the tool and implant are engaged with each other, for example at least partially by inserting the distal part of the tool into the implant site.

The cross-sectional shape of the drive section, as detailed above, ensures efficient, reliable and uniform transmission of the rotational force applied to the insertion tool about its longitudinal axis to the implant. Thus, the insertion tool ensures a secure insertion of the implant into the patient's bone tissue, while minimizing the risk of damage or destruction of the implant, in particular its site.

The drive section of the distal part of the insertion tool is designed to interact with the corresponding anti-rotation structure, in particular with the drive area of the implant. In the implant drive zone, the cross-section, i.e. the internal cross-section, of the implant bed or channel, perpendicular to the longitudinal direction of the implant, has a plurality of radially convex portions and a plurality of radially concave portions that are alternately arranged around the circumference of the cross-section, with each of the radially outermost points of the radially convex parts is located 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 cross sections of the drive section of the insertion tool and the drive area of the implant may be substantially the same or match.

The radially innermost points of the radially concave portions may be on the same circle around the center of the cross section. Thus, all the radially innermost points of the radially concave portions can be on the same circle around the center of the cross section. Alternatively, at least two of the radially innermost points of the radially concave portions may be on different circles around the center of the cross section having different radii from each other.

The cross section of the distal portion of the insertion tool in the drive section may have the same number of radially convex portions and radially concave portions. The number of radially convex portions and/or radially concave portions may be 2 or more, 3 or more, 4 or more, 5 or more, 6 or more, 7 or more, 8 or more, or 9 or more. In a particularly preferred embodiment of the invention, the cross section has 6 radially convex parts and 6 radially concave parts.

The radially convex portions may include one or more first radially convex portions and one or more second radially convex portions, all of the one or more radially outermost points of the one or more first radially convex portions being located on the same first circle around the center of the cross section and all of one or more radially outermost points of one or more second radially convex portions are on one second circle around the center of the cross section.

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

The first radially convex portions and the second radially convex portions may be alternately disposed around the circumference of the cross section with respective radially concave portions disposed therebetween.

The number of the first radially raised portions may be the same as the number of the second radially raised portions.

The radially convex cross-sectional portions of the distal portion of the insertion tool in the drive section may comprise only the first radially convex portions and the second radially convex portions, i.e. apart from the first and second radially convex portions, additional radially convex portions may be absent in the cross section.

Each of the radially convex portions and/or the radially concave portions of the cross section of the drive section may have a curved shape, such as at least partially circular shape, at least partially elliptical shape, at least partially oval shape, or the like.

The radially convex portions and the radially concave portions of the cross section of the drive section may be located directly next to each other or in close proximity to each other. The radially convex portion may be located directly next to or in close proximity to the two radially concave portions and vice versa.

The distal portion of the insertion tool of the present invention may have a drive region and a drive section as described above. The drive region may be located in the proximal direction from the drive section.

By providing the distal part of the insertion tool with both a drive region and a drive section, any damage or destruction of the implant, in particular its seat, can be particularly reliably prevented when the implant is inserted into bone tissue. In particular, due to the presence of two anti-rotation structures on the distal part of the insertion tool, i.e. the drive area and the drive section, which can interact with two corresponding anti-rotation structures on the implant, for example, the drive section and the drive area, the rotational force or load applied to the implant when inserted into bone tissue, they can be distributed between two structures. Therefore, any damage to either of these two structures in the implant can be minimized. Thus, one or both of these structures in an implant can be reliably and effectively used as a marker of an abutment, an indicator post, an impression post, or the like after the implant has been inserted into the bone tissue.

The distal portion of the insertion tool of the present invention may comprise a retaining element and a drive region, as detailed above. The drive region may be located in the proximal direction from the holding element.

The distal portion of the insertion tool of the present invention may comprise a retaining element and a drive section, as detailed above. The drive section may be located in the distal direction from the holding element.

The distal portion of the insertion tool of the present invention may comprise a retaining member, a drive region, and a drive section, as detailed above. The drive section may be located in the distal direction from the holding element. The drive region may be located in the proximal direction from the holding element. The drive section, the retaining member, and the drive region may be arranged in this order in a direction from the distal end of the insertion tool to the proximal end of the insertion tool.

The insertion tool may consist of a single piece of material. In this case, all components of the insert tool are integral with each other.

The insertion tool may consist of two separate parts, for example a distal part and a proximal part, which are attached to each other, in particular detachably attached to each other.

The two separate parts of the insertion tool can be permanently attached to each other.

For example, the distal portion of the insertion tool may have a protrusion that fits into a corresponding recess in the proximal portion of the insertion tool. The distal part and the proximal part can be attached to each other, in particular, attached to each other with the possibility of detachment, by inserting the protrusion into the recess.

The protrusion and recess may have appropriate anti-rotation features or structures so as to prevent any rotation of the distal portion and the proximal portion relative to each other about the longitudinal axis of the insertion tool.

The distal counter-rotation structure may have a cross section, such as an outer cross section of the protrusion perpendicular to the longitudinal direction of the insertion tool, that is not rotationally symmetrical, such as that is non-circular, such as elliptical, oval, polygonal, such as rectangular, square, or hexagonal, or the like. The anti-rotation design of the distal portion of the insertion tool may cooperate with the corresponding anti-rotation design of the proximal portion of the inserter. The counter-rotational design of the proximal portion of the insertion tool may have a cross-section, e.g., an inner cross-section of the recess perpendicular to the longitudinal direction of the insertion tool, that is not rotationally symmetrical, e.g., which is non-circular, e.g., elliptical, oval, polygonal, e.g. or hexagonal, or the like. The cross sections of the anti-rotation structures of the distal portion and the proximal portion may be substantially the same.

Providing the insertion tool as two separate parts, such as a distal part and a proximal part, as detailed above, makes the production of the insertion tool, in particular the production of the holding member, simpler and easier. This applies in particular if the holding element is provided in the proximal part of the insertion tool. For example, the production of the retaining element can be performed by milling.

One of the two separate parts of the insertion tool, in particular the distal part, may comprise a drive section, and the other of the two separate parts, in particular the proximal part, may comprise a holding element and a drive region. Thus, the production of the insertion tool, in particular the production of the holding member, can be further simplified.

The retaining element can be made in one piece with another of two separate parts, in particular with the proximal part.

The retaining element can be made in one piece with another of two separate parts, in particular with the proximal part.

Furthermore, the invention provides a combination of a dental implant according to the present invention and an insertion tool according to the present invention.

The above explanations, features and definitions for a dental implant and an insertion tool according to the present invention are fully applicable to the combination of the invention.

The combination of the invention provides the effects and advantages already described in detail above for a dental implant and an insertion tool according to the invention.

The dental implant may have at least one cavity formed in its coronal portion to receive at least one protrusion or one protrusion of the fastening part of the retaining element.

In accordance with one aspect of the invention, a dental implant is provided, in particular for insertion into the bone tissue of a patient, comprising a central portion having an apical end and a coronal end. The central part contains a channel or bed which is open to the coronal end and extends along the longitudinal direction of the implant from the coronal end to the apical end. The central part contains 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 radially convex parts located along the circumference of the cross section. Each of the radially outermost points of the radially convex portions is located on a respective circle around the center of the cross section. At least two of these circles have different radii from each other. The internal cross section of the implant site or channel, perpendicular to the longitudinal direction of the implant, may have a plurality of radially convex portions and a plurality of radially concave portions that are alternately arranged around the circumference of the cross section.

The longitudinal direction of the dental implant runs from the coronal end of the implant to the apical end of the implant. The cross section of the channel, perpendicular to the longitudinal direction of the implant, is the internal cross section of the channel.

The drive zone of the central part of the implant interacts with the insertion tool, in particular the insertion tool according to the present invention detailed above, ie with its drive section. The drive zone is an anti-rotation structure, such as the anti-rotation structure detailed above. The drive zone is configured to prevent relative rotation between the insertion tool and the implant around the longitudinal axis of the tool when the tool and the implant are engaged with each other, for example, at least partially, by inserting the distal part of the tool into the channel or implant bed.

The cross-sectional shape of the drive zone, as detailed above, ensures efficient, reliable and uniform transmission of the rotational force applied to the insertion tool about its longitudinal axis to the implant. Thus, the implant allows it to be reliably inserted into the jaw or bone tissue of the patient, while minimizing the risk of damage or destruction of the implant, in particular, its channel or bed.

The drive zone of the implant is configured to interact with the corresponding anti-rotation structure, in particular with the drive section, of the distal part of the insertion tool. The cross sections of the drive zone of the implant and the drive section of the insertion tool may be substantially the same.

The radially innermost points of the radially concave portions of the channel cross section in the drive zone may be on the same circle around the center of the cross section. Thus, all the radially innermost points of the radially concave portions can be on the same circle around the center of the cross section. Alternatively, at least two of the radially innermost points of the radially concave portions may be on different circles around the center of the cross section having different radii from each other.

The cross section of the channel in the drive zone may have the same number of radially convex parts and radially concave parts. The number of radially convex portions and/or radially concave portions may be 2 or more, 3 or more, 4 or more, 5 or more, 6 or more, 7 or more, or 8 or more. In a particularly preferred embodiment of the invention, the cross section has 6 radially convex parts and 6 radially concave parts.

The radially raised portions may comprise one or more first radially raised portions and one or more second radially raised portions, wherein all of the one or more radially outermost points of the one or more first radially raised portions are located on the same first circle around the center of the cross section and all from one or more radially outermost points, one or more second radially convex portions are located on one second circle around the center of the cross section.

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

At least one or more of the radially outermost points of one or more of the first radially convex portions may be located at an angular position corresponding to the relative maximum angular position of the dental implant center portion within an angular tolerance range. The tolerance range may be about ±10°, preferably about ±5°. The radially outermost points of the one or more first radially convex portions may be located at the same (or substantially the same) angular position as the relative maximum of the dental implant center portion.

The number of radially outermost points of one or more of the first radially convex parts may be the same as the number of relative maximum of the central part of the implant.

At least one of the one or more radially outermost points of the one or more second radially convex portions may be located at an angular position corresponding to the angular position of the minima of the dental implant center portion within an angular tolerance range. The tolerance range may be about ±10°, preferably about ±5°. The radially outermost points of the one or more second radially convex portions may be located at the same (or substantially the same) angular position as the relative maximum of the dental implant center portion.

The above configuration of the outermost points of the drive zone ensures that between said outermost points and the periphery of the central part of the implant, a maximum of material is present in a given cross section.

The first radially convex portions and the second radially convex portions may alternately be disposed around the circumference of the cross section with respective radially concave portions disposed therebetween.

The number of the first radially raised portions may be the same as the number of the second radially raised portions.

The radially convex portions of the channel cross-section in the drive zone may include only the first radially convex portions and the second radially convex portions, i.e. apart from the first and second radially convex portions, additional radially convex portions may be absent in the cross section.

The radially convex portions and/or the radially concave portions of the channel cross-section in the drive zone may be curved, for example at least partially circular, at least partially elliptical, at least partially oval, or the like.

The radially convex portions and the radially concave portions of the cross-section of the channel in the drive zone can be located directly next to each other and in close proximity to each other. The radially convex portion may be located directly next to or in close proximity to the two radially concave portions and vice versa.

The central part may additionally comprise a drive part, wherein in the drive part the cross section of the channel, perpendicular to the longitudinal direction of the implant, has a number of main directions in which the radius measuring the distance between the center of the cross section and its outer contour takes a relative maximum value and, therefore, more higher value than in adjacent orientations.

The driving part of the central part of the implant interacts with the insertion tool, in particular with the insertion tool according to the present invention, as described in detail above, ie with its driving region. The driving part is an anti-rotation structure, such as the anti-rotation structure detailed above. The drive part is configured to prevent relative rotation between the insertion tool and the implant around the longitudinal axis of the tool when the tool and the implant are engaged with each other, for example, at least partially, by inserting the distal part of the tool into the channel or implant bed.

The cross-sectional shape of the drive portion, as detailed above, ensures efficient, reliable and uniform transmission of the rotational force applied to the insertion tool about its longitudinal axis to the implant. Thus, the implant allows it to be reliably inserted into the jaw or bone tissue of the patient, while minimizing the risk of damage or destruction of the implant, in particular, its channel or bed.

The drive part of the implant is designed to interact with the corresponding anti-rotation structure, in particular with the drive area, of the distal part of the insertion tool. The cross sections of the drive portion of the implant and the drive area of the insertion tool may be substantially the same.

The cross section of the drive part of the implant can be characterized by an eccentricity parameter characteristic of the deviation of the corresponding cross section from a circular shape. For the purposes of this description and disclosure, and in accordance with the present invention, this eccentricity parameter is defined as the ratio of the maximum cross-sectional radius to its minimum radius, such that the eccentricity parameter takes on a value of 1 for a circular shape. The eccentricity parameter of the cross section of the drive part of the implant is greater than 1. The eccentricity parameter can be, for example, in the range from 1.1 to 1.6, from 1.2 to 1.5 or from 1.3 to 1.4.

This eccentricity parameter can be estimated for each value of the parameter characteristic of the coordinate in the longitudinal direction of the dental implant. The drive part eccentricity parameter can be constant in the longitudinal direction of the implant. Alternatively, the drive portion eccentricity parameter may vary in the longitudinal direction of the implant, eg decrease from the coronal end of the implant towards the apical end of the implant. The drive part eccentricity parameter may have a linear dependence on the coordinate parameter in the longitudinal direction of the implant.

In some embodiments of the invention, the main directions in the drive part of the implant, in which the corresponding cross-sectional radius has a local maximum, are located symmetrically, in particular axially symmetrically, relative to the central longitudinal axis of the implant.

The number of main directions in the drive portion of the implant may be three or more, four or more, five or more, or six or more.

In some embodiments of the invention, the number of main directions in the drive part of the implant is three, that is, the drive part has a tri-oval cross section. Combined with the symmetrical arrangement of the main directions with respect to the longitudinal direction of the implant, as detailed above, this tri-ovality results in a rotation offset angle between two adjacent main directions of 120°.

The drive portion may have a conical configuration such that, in the drive portion, the lateral dimensions or elongations of the cross section of the channel perpendicular to the longitudinal direction of the implant decrease in the direction from the coronal end of the core to the apical end of the core.

In the drive portion, the cross-sectional area of the canal perpendicular to the longitudinal direction of the implant, ie the cross-sectional area of the canal, may decrease in the direction from the coronal end of the central part to the apical end of the central part.

Thus, the central part of the implant according to the present invention may have a drive zone and a drive part, as described in detail above. The drive zone may be located in the apical direction from the drive part.

By providing the central part of the implant with both the drive zone and the drive part, any damage or destruction of the implant, in particular its channel or bed, can be particularly reliably prevented when the implant is inserted into the jawbone or bone tissue. In particular, due to the presence of two anti-rotation structures in the central part of the implant, that is, the drive zone and the drive part, which can interact with two corresponding anti-rotation structures in the distal part of the insertion tool, for example, the drive section and the drive region, the rotational force or load applied to the implant when it is inserted into the bone tissue, can be distributed between the two structures. Therefore, any damage to either of these two structures in the implant can be minimized. Thus, one or both of these structures in an implant can be reliably and effectively used as a marker of an abutment, indicator post, impression post, or the like after the implant has been inserted into the jaw or bone tissue.

The central part may have an outer surface extending along the longitudinal direction of the implant between the apical end and the coronal end.

In addition, the dental implant may include at least one thread extending outward from the central portion, wherein the thread has an apical surface facing the apical end of the central portion and a coronal surface facing the coronal end of the central portion.

The thread may have a groove, ie a cutting groove, formed therein, the groove extending from the apical end of the thread towards the coronal end of the thread.

The thread may have, in its apical part, a recess formed on its coronal surface, the recess extending in a direction from the coronal surface to the apical surface along a part of the thickness of the thread, the recess being open to the groove, i.e. opens to the groove.

In accordance with one aspect of the invention, a dental implant is provided, in particular for insertion into the bone tissue of a patient, comprising a central part having an apical end, a coronal end and an outer surface extending along the longitudinal direction of the implant between the apical end and the coronal end. The implant further comprises at least one thread extending outward from the central portion. The thread has an apical surface facing the apical end of the central part and a coronal surface facing the coronal end of the central part. The thread has a groove, i.e. a cutting groove formed therein. The groove extends from the apical end of the thread to the coronal end of the thread. The thread has in its apical part a recess formed on its coronal surface, the recess extending in the direction from the coronal surface to the apical surface along a part of the thickness of the thread. The recess is open to the groove, i.e. opens to the groove.

The thickness of the thread extends in the direction from the coronal surface of the thread to the apical surface of the thread. The thread width extends in a radially outward direction from the central portion. The thread length extends in the longitudinal direction of the implant.

By providing a groove and recess thread, as detailed above, the implant becomes self-tapping. In addition, the location of the groove and recess helps to reduce the torque during implant placement, or the rotational force required to insert the implant into jaw or bone tissue. This is particularly advantageous in the case of hard bone. When inserting an implant, no axial pressure is required to be applied to it. Instead, the implant is effectively and securely drawn into the implant site as it rotates.

The recess has a cutting function, that is, a function of cutting bone tissue. Thus, the recess helps to effectively cut and remove bone material and furthermore transport the removed bone material towards the coronal end of the core.

In particular, when inserting an implant at an implant site, such as an extraction site where the implant must be cut from the side, for example, due to an oblique or angular position between the implant and the bone tissue, the implant of the present invention ensures its smooth and precise placement in bones. In addition, the recess greatly facilitates the insertion of the implant into an insufficiently prepared hole in the bone tissue or into a post-extraction tooth socket (or bed), the bone wall being inhomogeneous and, therefore, it is not possible to create a cylindrical osteotomy, which is usually the result of drilling.

Thus, the implant according to the invention allows it to be inserted into bone tissue with reduced force and with a high degree of precision. In this way, a particularly stable and reliable connection or engagement of the implant with the bone tissue, i.e. high implant stability, can be achieved.

By positioning the recess on the coronal surface of the thread, the above preferred effects can be achieved over a wide range of implant thread profile angles, i.e. essentially all implant thread profile angles, in particular for small implant thread profile angles.

Therefore, the invention provides a dental implant that ensures its secure and precise placement and engagement in the jaw or bone tissue over a wide range of implant thread profile angles, in particular small implant thread profile angles.

The dental implant contains at least one thread. A dental implant may contain a plurality of threads, such as two or more threads, three or more threads, or four or more threads.

At least one thread has at least one groove, ie at least one cutting groove, formed therein. At least one groove extends in the length direction of at least one groove from the apical end of the thread to the coronal end of the thread. Thus, at least one groove starts at the apical end of the thread and extends from there towards the coronal end of the thread. The at least one groove may extend more than 20% or more, 30% or more, 40% or more, 50% or more, or 60% or more of the thread length.

The at least one groove may extend in a direction substantially parallel to the longitudinal direction of the implant, or in a direction oblique or oblique with respect to the longitudinal direction of the implant. In the latter case, the angle between the direction of extension of the at least one groove and the longitudinal direction of the implant may be in the range of 2° to 20°, 5° to 15° or 8° to 12°.

At least one groove extends in the width direction of the at least one groove along a portion of the circumference of the central portion. The at least one groove may extend from 10% to 30%, from 15% to 25%, or from 18% to 22% of the circumference of the central portion.

The thread may have a plurality of grooves, that is, a plurality of cutting grooves formed therein. One of the plurality of grooves extends from the apical end of the thread towards the coronal end of the thread. The thread may have two or more grooves, three or more grooves, or four or more grooves formed therein.

The plurality of grooves may be staggered or offset along the length of the thread and/or along the circumference of the thread, ie the circumference of the central portion.

The thread has at least one recess formed on its coronal surface, and at least one recess extends in the direction from the coronal surface to the apical surface along a portion of the thickness of the thread. The at least one recess thus starts at the coronal surface and extends from there towards the apical surface. At least one recess does not fully penetrate the thread in the thread thickness direction. At least one recess is open, i.e. opens, with respect to the coronal surface of the thread.

In addition, the recess is open with respect to the groove, that is, it opens with respect to the groove. The recess is provided in the vicinity of, ie immediately adjacent to or in close proximity to, the groove.

The at least one recess may extend coronally to apically 20% to 90%, 30% to 80%, 40% to 70%, or 50% to 60% of the thread thickness. In this way, it can be ensured that the recess effectively facilitates the cutting process of the bone while maintaining sufficient stability of the implant.

If the first threads are allowed to cut into the bone, in the case of small volumes of available bone (e.g. post-extraction alveolus), the drilled hole can be reduced to provide greater stability to the implant derived from the incisal edge of the instrument.

The expansion of at least one recess in the direction from the coronal surface to the apical surface, that is, the depth of at least one recess, may be constant along directions parallel to the coronal surface or the apical surface.

The expansion of at least one recess in the direction from the coronal surface to the apical surface, that is, the depth of at least one recess, may vary along directions parallel to the coronal surface or the apical surface. In this case, the greatest expansion of at least one recess in the direction from the coronal surface to the apical surface may be in the range from 20% to 90%, from 30% to 80%, from 40% to 70%, or from 50% to 60% of the thickness. threads. The greatest expansion of at least one recess in the direction from the coronal surface to the apical surface may be present in the region of the recess, which is located immediately adjacent to the groove.

The expansion of at least one recess in the direction from the coronal surface to the apical surface may decrease along the circumferential direction from the groove to which the recess opens. In this way, a particularly efficient recess cutting function can be achieved.

At least one recess may have a curved shape. For example, at least one recess may be in the form of a portion or segment of a sphere or ellipsoid, such as a quarter sphere or a fourth ellipsoid. Such a curved shape of the at least one recess makes it possible to produce the recess, and hence the implant, in a particularly simple and economical manner.

The at least one recess may extend in a recess width direction of 50% to 90%, 60% to 80%, or 65% to 75% of the thread width.

At least one recess may be located on the ascending side of the groove in the direction of rotation of the implant. The direction of rotation of the implant is the direction in which the implant is screwed into the bone tissue.

At least one recess may be formed on the coronal surface of the thread during the first full or complete turn of the thread. The first full or whole turn of the thread is the first full turn in the case where the full turns are counted starting from the apical end of the thread and towards the coronal end of the thread. Thus, the first complete turn of the thread represents the most apical complete turn of the thread. Such an arrangement of the at least one recess ensures a particularly stable and firm engagement of the implant with the jaw or bone tissue.

At least one recess may be formed on the coronal surface of the thread at the second full or full turn of the thread. At least one recess may be formed on the coronal surface of the thread at the third full or full turn of the thread.

The thread may have a plurality of depressions formed on its coronal surface. For example, one of a plurality of dimples may be formed on each of the coronal surfaces of the thread at the first and second full or whole turns of the thread. One of the plurality of recesses may be formed on each of the coronal surfaces of the thread at the first, second and third full or whole thread rotations.

The thread profile angle, that is, the angle of the thread profile with respect to a plane perpendicular to the longitudinal direction of the implant, may be 25° or less, 20° or less, 15° or less, 12° or less, or 10° or less. In a particularly preferred embodiment of the invention, the thread profile angle is 10° or less.

Such small thread profile angles provide the advantage that the implant is inserted into the bone tissue more slowly, ie with less forward movement per implant rotation, which results in particularly smooth and precise placement of the implant.

As indicated above, the implant recess of the present invention works particularly well in combination with thread types having such small thread profile angles. In particular, the location of the recess on the coronal surface of the thread can provide a local increase in the angle of the thread profile due to the presence of the recess. For example, the angle of the thread profile can be locally increased to 20-40° or up to 25-35°.

Therefore, the indentation can greatly contribute to the cutting of the bone tissue.

The above and other features of the present disclosure will become more apparent from the following description and the appended claims, taken in conjunction with the accompanying drawings. Given that these drawings illustrate only a few embodiments in accordance with the invention and should not be construed as limiting its scope, the invention will be described with additional specifications and detail using the accompanying drawings.

BRIEF DESCRIPTION OF GRAPHICS

In FIG. 1 illustrates a side perspective view of a dental implant in accordance with one embodiment of the invention.

In FIG. 2 illustrates a side perspective view of an alternative dental implant in accordance with the present invention.

In FIG. 3 illustrates a side view of an embodiment of a dental implant according to the invention with areas highlighted.

In FIG. 4 illustrates a longitudinal sectional view of the implant illustrated in FIG. 3.

In FIG. 5 is a longitudinal sectional view of the implant illustrated in FIG. 2.

In FIG. 6-12 illustrate views of various embodiments of implants in accordance with the present invention.

In FIG. 13-18 illustrate side views of various embodiments of implants in accordance with the present invention equipped with cutting grooves.

In FIG. 19 illustrates a side perspective view of the coronal portion of the preferred embodiment of the implant illustrated in FIG. eleven.

In FIG. 20 illustrates a side view of a dental implant in accordance with an embodiment of the invention.

In FIG. 21 schematically illustrates a cross section of the implant illustrated in FIG. 20.

In FIG. 22 is a longitudinal sectional view of the implant illustrated in FIG. 1, 2 and 11.

In FIG. 23 is an enlarged view of the part illustrated in FIG. 22.

In FIG. 24 illustrates a longitudinal section of a portion of the implant illustrated in FIG. 1, 2 and 11 after insertion into the bone material.

In FIG. 25 illustrates two views of the implant illustrated in FIG. 1, 2 and 11, from the top view.

In FIG. 26 is a perspective view in longitudinal section of the implant illustrated in FIG. 1, 2 and 11.

In FIG. 27 is a perspective view in longitudinal section of the upper portion of the implant illustrated in FIG. 1, 2 and 11 showing the inner connection.

In FIG. 28 is a perspective view in longitudinal section of the upper portion of a dental implant according to another embodiment of the invention, showing an alternative internal connection of the implant.

In FIG. 29 illustrates a side perspective view of a coronal portion of a dental implant in accordance with another embodiment of the invention.

In FIG. 30 is a perspective side view of the dental implant illustrated in FIG. 29.

In FIG. 31 is a side view of the dental implant illustrated in FIG. 29.

In FIG. 32 illustrates a side view of a portion of the tip of a dental implant in accordance with another embodiment of the invention.

In FIG. 33 illustrates a bottom perspective view of a dental implant in accordance with another embodiment of the invention.

In FIG. 34 illustrates a side perspective view of a dental implant in accordance with another embodiment of the invention.

In FIG. 35 is a graph showing the possible change in eccentricity for certain parts of the implant along the longitudinal axis of the implant.

In FIG. 36 illustrates an insertion tool according to the first embodiment of the present invention, wherein FIG. 36(a) is a side view of the entire insertion tool, FIG. 36(b) illustrates an enlarged side view of the distal insertion tool, and FIG. 36(c) is a perspective view of the distal portion of the insertion tool.

In FIG. 37 illustrates an insertion tool according to the first embodiment of the present invention, wherein FIG. 37(a) is an expanded perspective view of the distal portion of the insertion tool; in fig. 37(b) illustrates a developed side view of the distal portion of the insertion tool; in fig. 37(c) is a developed cross-sectional view of the distal portion of the insertion tool; in fig. 37(d) is a cross-sectional view showing a state in which a portion of the distal portion of the insertion tool is inserted into the dental implant.

In FIG. 38 illustrates an insertion tool according to the first embodiment of the present invention, wherein FIG. 38(a) is a side view of the entire insertion tool, FIG. 38(b) illustrates a cross-sectional view of the distal insertion tool taken along line C-C in FIG. 38(a), FIG. 38(c) is a side view of the distal insertion tool; in fig. 38(d) illustrates a cross-sectional view of the distal portion of the insertion tool taken along line A-A in FIG. 38(c), in FIG. 38(e) illustrates a cross-sectional view of the distal portion of the insertion tool taken along line A-A in FIG. 38(c) for modifying the first embodiment of the insertion tool, and FIG. 38(f) illustrates a cross-sectional view of the distal insertion tool taken along line B-B in FIG. 38(c).

In FIG. 39 illustrates a combination of an insertion tool according to the first embodiment of the present invention and a dental implant, wherein FIG. 39(a) is a side view of this combination in a state in which an insertion tool is attached to an implant, FIG. 39(b) illustrates a cross-sectional view of the distal portion of the insertion tool and the coronal portion of the implant, taken along line D-D in FIG. 39(a), and in FIG. 39(c) is a cross-sectional view of the coronal part of the implant taken along line E-E in FIG. 39(b).

In FIG. 40 illustrates an insertion tool according to a second embodiment of the present invention, wherein FIG. 40(a) and (b) illustrate perspective views of the distal portion of the insertion tool taken from different angles.

In FIG. 41 illustrates a dental implant in accordance with an embodiment of the present invention, wherein FIG. 41(a) illustrates a side view of the implant, FIG. 41(b) illustrates a bottom view of the implant, and FIG. 41(c) illustrates a cross-sectional view of the implant taken along line H-H in FIG. 41(b).

In FIG. 42 illustrates a dental implant in accordance with an embodiment of the present invention, wherein FIG. 42(a) illustrates a side view of the apical part of the implant in the direction of the arrow K illustrated in FIG. 41(c), in FIG. 42(b) illustrates a side view of the apical part of the implant in the direction of the arrow J illustrated in FIG. 41(c), in FIG. 42(c) is an enlarged view of the surrounded area M illustrated in FIG. 41(c), and in FIG. 42(d) is an enlarged view of the surrounded area G illustrated in FIG. 41(b).

In FIG. 43 illustrates a dental implant in accordance with another embodiment of the present invention, wherein FIG. 43(a) illustrates a side view of the implant, FIG. 43(b) illustrates a cross-sectional view of the implant taken along line B-B in FIG. 43(a), and in FIG. 43(c) illustrates a top view of an implant.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Preferred embodiments of the present invention will be described below with reference to the accompanying drawings.

Identical parts are designated by the same reference numerals throughout the figures. Individual features, as illustrated, may be combined in additional embodiments of the invention, all of which are considered to fall within the scope of the present invention.

The dental implant 1 illustrated in FIG. 1 is provided for use in the jawbone of a patient at the site of an extracted or lost tooth to hold there a prosthetic portion serving as a denture or crown. In an exemplary embodiment of the invention, as illustrated, the dental implant 1 is provided for use in a so-called multi-component configuration and is designed as a so-called pin part for insertion into the patient's bone tissue. The dental implant system in which the dental implant 1 is intended to be used also includes a second implant part (not illustrated) associated with it, also referred to as an anchor element or abutment, which is designed to attach a denture element or any other prosthetic component that can interact with implant 1. However, as an alternative and still in accordance with the present invention, the dental implant 1 can also be configured to be used in a one-piece dental implant system, in which the dental implant 1 also contains a means for direct attachment in its upper region denture element or prosthetic component.

The implant 1 comprises, as a main body, a central part 2 having an apical end 4, a coronal end 6 and an outer surface 8 extending along the longitudinal direction of the central part 2 between the apical end 4 and the coronal end 6. In a single element configuration, the coronal end 6 of the central part 2 can be properly made so that the denture can be attached properly and with high mechanical stability. However, in the illustrated example, due to the multi-component configuration of the dental implant system, the coronal end 6 is configured to form a connection with high mechanical stability to the second implant part or abutment. In order to achieve such a high mechanical stability, after the denture element or prosthesis is properly fixed on the fastener element or abutment, the implant 1 comprises a receiving channel 10 into which a corresponding abutment pin can be inserted. By pushing the connecting pin into the receiving channel 10, the implant 1 and the abutment are mechanically connected to each other. The mechanical connection of the implant 1 and the abutment is carried out with the help of a corresponding connecting screw, the external thread of which is screwed into the internal thread provided in the implant 1, whereby the screw head of the connecting screw presses the abutment against the implant 1.

On its outer surface 8, the central part 2 of the implant 1 is provided with an external thread 12 extending outward from the central part 2. The thread 12 is designed, in particular in the area close to the apical end 4, as a self-tapping screw thread with which the implant 1 can be inserted. into the jawbone, screwing it into the intended location. The thread pitch 12 may be uniform or variable.

The implant 1, containing its thread 12, is specially designed, in particular, taking into account the required high primary and secondary stability and the uniform direction of the forces arising from the masticatory load on the dental implant 1 into the jawbone. For this purpose, the implant contains a number of special zones or sections, each of which is designed to specifically promote either high primary stability or high secondary stability.

Firstly, the central part 2 of the dental implant 1 comprises a circular zone 20 in the preferred embodiment of the invention, which, as illustrated, is located near the apical end 4. In the circular zone 20 of the central part, the central part 2 of the implant 1 is made with the possibility of relatively easy thread engagement 12 with bone material without exerting excessive stress on the bone tissue in the first moments of time when the implant 1 is screwed into the bone material. For this purpose, in the circular zone 20 of the central part, the central part 2 has a circular cross section. The location of the circular area 20 of the Central part in the apical part of the implant 1 is considered to be highly desirable in order to maximize the potential for high primary stability. This is useful in general, but more specifically in post-extraction dental sockets, and immediate loading protocols may be preferred. In order to provide significant apical engagement, the circular zone 20, as seen in the longitudinal direction of the implant, in the illustrated embodiment has a length of at least 2.5 mm.

On the contrary, and also secondly, the central part 2 contains the formed zone 22 of the central part. In the embodiment of the invention illustrated in FIG., the formed zone 22 of the central part is located in close proximity to the other end of the implant 2, that is, near the coronal end 6, and thus represents the zone of the platform of the alveolar ridge 24, but, as alternatively, it can also be located in some middle or intermediate range of the central part 2. In this zone 22 in the embodiment of the invention illustrated near the coronal end 6, which is configured to be attached to the abutment bearing the denture, the central part 2 is made with a non-circular cross section having a number of principal directions in which the radius measuring the distance between the center of the cross section and its outer contour takes on a relative maximum value and therefore a higher value than in adjacent orientations.

Due to this cross-sectional design, in this formed core zone 22, when the core 2 is screwed into the bone tissue, the compressive force acting on the bone tissue oscillates between the maximum compression when (due to the rotational movement of the implant body) the local radius of the transverse section becomes maximum, and minimum compression when the local radius of the cross section becomes minimum. Therefore, when the implant body is screwed in, the surrounding bone tissue in this area is subjected to an oscillatory compression that varies between periods of high compression and periods of decompression as the compression decreases. In the illustrated preferred embodiment of the invention, the formed zone 22 is located at the end of the ridge of the implant 1. Therefore, after the insertion of the implant 1, the formed zone 22 will rest on the ridge zone of the patient's jaw, which has a relatively hard bone tissue. Once inserted, this minima-shaped contour will result in areas of low stress in the bone in close proximity to the minima, which will improve bone recovery and greatly minimize the negative effects of overcompression on blood vessels. As a result, bone recovery as well as osseointegration is greatly improved by providing local minima of the formed zone 22 in the region of critical bone construction, and it is considered to be quite appropriate for the purpose of osseointegration to ensure that these effects affect the top layer at least 2 long. 5 mm or more preferably at least 3 mm in the ridge plate. Accordingly, the first formed zone 22, as seen in the longitudinal direction of the implant, in the illustrated embodiment has a length of at least 2.5 mm.

Thirdly, the central part 2 of the implant 1 comprises a transition zone 26 located, as seen in the longitudinal direction of the implant 1, between the circular zone 20 of the central part and the formed zone 22 of the central part. To ensure a smooth and expedient transition between the zones 20, 22, a transition zone 26 is provided with a transitional cross section varying (as seen in the longitudinal direction) from a circular cross section corresponding to the cross section of the circular zone 20 of the central part in a range close to the circular zone 20 the central part, to a non-circular, lobulated cross-section, corresponding to the cross-section of the formed zone 22 in a range close to the formed zone 22. Due to this transitional zone 26, immediate and sudden changes in geometry, shearing effects on bone tissue and other damaging effects can be avoided on bone tissue.

An alternative embodiment of the present invention is illustrated in FIG. 2. This embodiment may be used alone or in combination with the embodiment illustrated in FIG. 1. In this alternative embodiment of the invention, the dental implant 1', similar to the embodiment illustrated in FIG. 1 is also provided with a central part 2 comprising a circular central part zone 20 and a shaped central part zone 22. However, instead of or in addition to the transition zone 26, the dental implant 1' comprises a second formed center zone 26', wherein in the second formed zone 26' of the central part, as in the first formed zone 22 of the central part, the cross section of the central part 2 has a set of principal directions in which the radius, which measures the distance between the center of the cross section and its outer contour, takes on a relative maximum value and therefore a higher value than in neighboring orientations. The second formed zone 26' of the central part is located, as seen in the longitudinal direction of the implant 1, between the zones 20, 22. the central part, defined as the ratio of the maximum radius of the cross section of the central part 2 to its minimum radius, is greater than in the second formed zone 26' of the central part. Obviously, as a further option, this second shaped zone 26' may also itself consist of a sequence or a number of individual shaped zones of this type having different eccentricities.

In FIG. 3 illustrates a schematic representation of the implant 1, 1' in FIG. 1, 2, in which zones 20, 22, 26, 26' are recognizably identified. In the illustrated example, the transition zone 26, as seen in the longitudinal direction, starts at a distance of about 2-3 mm from the apical end 4 of the implant 1.

The concept of this design for the central part 2, ie the provision of three zones 20, 22 and 26 or 26', respectively, is considered the first of the possible groups of embodiments of the invention for the concept of the present invention. Alternatively, an independent second group of embodiments of the concept of the present invention, which can be used independently or in combination with an embodiment of the invention from the first group, similar or equivalent effects on beneficial properties of cutting and bone processing can be achieved by developing the outer contour of the thread 12, of a similar construction as described above for the central part 2. FIG. 4 illustrates an embodiment of the implant 1 showing both of these alternative groups of embodiments in combination, but they can also be used independently. For a better explanation of the design of the outer contour of the thread 12, it is hereinafter referred to as the "outer volume" or enclosing volume 28 defined by the outer contour of the thread 12, as clearly represented by the longitudinal sectional view of FIG. 4.

In a combined embodiment of the invention, as illustrated, the thread 12 of the implant 1 also comprises a first or formed thread zone 30, wherein the cross section of the outer volume 28 enclosing the thread 12 has a number of principal directions in which a radius measuring the distance between the center of the cross section and its outer contour, takes on a relative maximum value and, therefore, a higher value than in neighboring orientations. In addition, in this embodiment, the thread 12 comprises a circular thread area 32 in the preferred embodiment, as illustrated, adjacent to the apical end 4 of the implant 1, the outer enclosing volume 28 having a generally circular cross-section and, as seen in the longitudinal direction of the implant, a thread transition zone 34 located between said first, formed zone 30 and said second, circular zone 32, in which the cross-sectional geometry of said outer volume 28 enclosing the thread 12, as a function of a parameter characteristic of the coordinate in the longitudinal direction, changes from a generally circular shape next to said circular zone 32 to a shape in which the cross section of said enclosing volume 28, in particular with respect to the overall geometry of the cross section and/or the values of its characteristic parameters, correspond to the cross sectional shape in said first or formed zone 30 .

An alternative embodiment of the invention from this group of embodiments of the present invention is illustrated in FIG. 5. This embodiment may be used alone or in combination with the embodiment illustrated in FIG. 4. In this alternative embodiment of the invention, the dental implant 1', similar to the embodiment illustrated in FIG. 4 also has a female thread volume 28 12 comprising a circular thread zone 32 and a formed thread zone 30. However, instead of or in addition to the thread transition zone 34, the dental implant 1' comprises a second formed thread zone 34', wherein in the second formed thread zone 34', as in the first formed thread zone 30, the cross section of the outer volume 28 has a number of main directions, in which the radius, which measures the distance between the center of the cross section and its outer contour, takes on a relative maximum value and therefore a higher value than in adjacent orientations. The second formed thread zone 34' is located, as seen in the longitudinal direction of the implant 1, between the zones 30, 32. In this embodiment, in the first formed thread zone 30, the thread eccentricity parameter determined by as the ratio of the maximum radius of the cross-section of the outer volume 28 to its minimum radius, greater than in the second formed zone 34' of the thread. Obviously, as a further option, this second shaped zone 34' may itself also consist of a sequence or number of separate shaped zones of this type having different eccentricities.

The implant 1, 1', thanks to its transition zones 26, 26', 34, 34', is specially designed for a smooth and expedient transition (during the screwing process) between the first engagement of the thread 12 in the bone tissue (in the circular zone 20 of the central part and/or the circular thread zone 32) for shaping and direct processing of bone tissue by changing the compression (in the formed zone 22, 30). To further improve the smooth transition between these zones, the central part 2 in the transition zone 26 is tapered or tapered, in particular with a taper/taper angle in the range of 1° to 12°, preferably 4° to 8°.

The cross section of the central part 2 can be characterized by the eccentricity parameter, defined as the ratio of the maximum radius of the cross section to its minimum radius. This eccentricity parameter, which takes on a value of 1 for a circular shape, is characteristic of the deviation of the respective cross section from the circular shape. To ensure a particularly smooth transition between the circular region 20 of the central part with a circular cross section and the formed zone 22 of the central part with a non-circular cross section, this eccentricity parameter in the transition zone 26 has a linear dependence on the coordinate parameter of the implant 1 in the longitudinal direction. In the illustrated example, the central part 2 has an eccentricity value of about 1.1 in its formed zone 22 of the central part. The same concept can be used for the transition zone 34 of the thread 12 and the eccentricity parameter of the outer volume 28 in the formed thread zone 30 .

In the following, various considerations regarding the individual elements and components of the implant 1, 1' and their geometry parameters are described with reference to the group of embodiments of the invention according to the implant 1. Obviously, they can also be applied to the group of embodiments of the invention according to the implant 1 ' or a combination of these groups of embodiments of the invention.

The positions and boundaries of the various zones 20, 22, 26 (or 26', respectively) of the central part and the various zones 30, 32, 34 (or 34', respectively) of the central part in the longitudinal direction of the implant 1 may differ in various embodiments of the invention, seven of which are illustrated as general examples in FIG. 6-9. In each of these representations in FIG. 6a, 7a, 8a and 9a show a perspective view of the respective implant 1, FIG. 6b, 7b, 8b and 9b illustrate a longitudinal sectional view of the respective implant 1, and FIG. 6c-6e, 7c-7e, 8c-8e and 9c-9e illustrate cross sections of the outer contour of the central part 2 and the outer contour of the enclosing volume 28.

In the embodiment of the invention illustrated in FIG. 6, the central portion 2 and the enclosing volume 28 are tri-oval in their cross sections from the medial portion of the alveolar ridge to the coronal end 6 in order to enlarge the buccal bone plate and promote bone regeneration.

Conversely, in the embodiment of the invention illustrated in FIG. 7, in the area of the ridge 42 above the transition line 4, the cross section of the central part 2 is circular (as illustrated in FIG. 7c), with the outer contour of the enclosing volume 28 being tri-oval. This is done to improve the torques as well as the initial stability and strength of the implant during insertion while maintaining the external tri-oval shape to achieve the effect of bone repair and enlargement of the buccal bone plate.

In the embodiment of the invention illustrated in FIG. 8, the cross section of the central part 2 is circular along the entire length of the implant 1, and only the outer contour of the enclosing volume 28 changes from round near the apical end 4 to tri-oval near the coronal end 6.

In FIG. 9 illustrates an embodiment of the invention in which the cross section of the central part 2 in the middle of the implant 1 (FIG. 9d) is circular, being tri-oval in the area 42 of the alveolar ridge. In the middle range, as illustrated in FIG. 9d, the circular cross-sectional area of the central part 2 is covered by the tri-oval cross-sectional area of the enclosing volume 28.

In FIG. 10 illustrates an exemplary embodiment of the invention of the implant 1, together with possible input data for CNC processing of the respective shapes. In FIG. 10a the implant 1 is illustrated in longitudinal section, while in FIG. 10b illustrates the implant 1 in side view. In FIG. 10c shows a longitudinal cross-section of the outer thread volume 28 of an embodiment of the implant 1, said implant being located on the minimum radius side. The profile of the outer volume 28 may be CNC machined with a tool profile corresponding to at least one of the lines illustrated in FIG. 10s. After the starting material has been processed into this shape, the thread 12 is machined by cutting recesses in the thread, the depth of which is given by the profile, as illustrated in FIG. 10d. This results in the final shape of the central part 2 as described above.

The three-ovality design of the implant 1 can be obtained by CNC machining, the circular modes of which are illustrated in FIG. 10f. As can be seen in FIG. 10f, the differential ovality parameter e, which is an alternative definition of the shape of the central part 2/outer volume 28 and which is determined by the difference between the maximum radius of the cross section and its minimum radius, for a typical diameter of about 4 mm, a value of about 0.23 mm is preferably chosen.

In FIG. 10c also illustrates a plurality of longitudinal coordinates/points from Y01 to Y05 along the y-axis (the longitudinal axis of the implant) defining zones along said y-axis. Y01 is the point with coordinate 0 mm. In the embodiment of the invention illustrated in FIG. 10c, the value e of the ovality parameter changes depending on the y coordinate along the indicated axis. For example, in the first zone Y01-Y02, the ovality parameter e may have a constant value of/selected from a value in the range of 0.10 to 0.50 mm, and more preferably 0.20 to 0.25 mm. Moreover, said zone Y1-Y2 (outer zone 1 or first outer zone) may be a constant eccentricity zone. In said zone Y1-Y2, the maximum diameter ∅D of the outer volume 28 can be constant and have a value of 4 mm. Within zone Y2-Y3 (outer zone 2 or second outer zone), the ovality parameter can have a value ranging from a value constituting a value/selected from a value in the range of 0.20 to 0.30 mm at point Y2 to a value of 0 mm at point Y03. In said zone Y02-Y03, the maximum diameter ∅D of the outer volume 28 can vary from 4 to 3.54 mm. The change in the ovality parameter and/or the change in eccentricity, as mentioned above, may be linear in said zone Y2-Y3. Finally, the ovality parameter e can have a value of 0 mm between points Y03 and Y05. As a non-limiting example, outer volume 28 may be conical between Y03 and Y04 (outer zone 3 or third outer zone) with a diameter ranging from 3.54 to 3.40 mm. The outer volume 28 may also have a conical shape between points Y04 and Y05 (outer zone 4 or fourth outer zone) with a diameter varying from 3.40 to 1.80 mm.

Obviously, the length of each zone depends on the overall length of the implant, but as a non-limiting example for an implant with a total length of 13 mm, Y2 may be 2.30 mm from Y1, Y3 may be 5 mm from Y1, Y4 may be 11.70mm from Y1 and Y5 can be 13mm from Y1.

In FIG. 10d illustrates a longitudinal cross-section of the central part 2 of the implant 1 illustrated in FIG. 10a. In FIG. 10d also illustrates a plurality of longitudinal coordinates/points Y6-Y09 along the y-axis. The specified points also define zones along the specified y-axis. Y1 is the point with coordinate 0 mm. In the embodiment of the invention illustrated in FIG. 10d, the value e of the ovality parameter varies depending on the y coordinate along the indicated axis. For example, in the first zone Y1-Y6, the ovality parameter e may have a constant value of/selected from a value in the range of 0.10 to 0.50 mm. In said first zone, the maximum diameter of the central part ∅D can vary along the longitudinal axis from 4 to 3.60 mm. Said area Y1-Y6 (center area 1 or first center area) may have a constant eccentricity. In the zone Y6-Y7 (zone 2 of the central part or the second zone of the central part), the parameter e-ovality can have a value varying from a constant value of / selected from the range from 0.10 to 0.50 mm at point Y6, to a value of 0 mm at point Y7. The change in the ovality parameter may be linear in the specified zone Y6-Y7. In said zone Y6-Y7, the maximum diameter ∅D of the central part can vary from 3.30 to 2.70 mm. Finally, the ovality parameter e can have a value of 0 mm between points Y07 and Y09. As a non-limiting example, the center portion 2 may be tapered between points Y07 and Y08 with a center portion diameter varying from 2.70 to 2.2 mm (center portion zone 3 or center portion third zone), and a conical shape between points Y08 and Y09 (core zone 4 or core zone 4) with core diameter varying from 2.2 to 1.6 mm.

Obviously, the length of each zone depends on the overall length of the implant, but as a non-limiting example for an implant with a total length of 13 mm, Y6 may be 2.30 mm from Y1, Y7 may be 5 mm from Y1, Y8 may be 11.70 mm from Y1, and Y9 can be 13 mm from Y1.

Another alternative embodiment of the present invention is illustrated in FIG. 11. This embodiment may be used alone or in combination with the embodiments illustrated in FIG. 1 and/or FIG. 2. In this alternative embodiment of the invention illustrated in FIG. 11, a dental implant 1'' similar to the embodiments illustrated in FIG. 1 and/or FIG. 2 is also provided with a central portion 2 comprising a circular central region 20, a formed central region 22, a circular threaded region 32, and a formed threaded region 30, however this alternative embodiment may also be used without one or more of these regions. In this alternative embodiment of the invention, the threads 12 in the coronal section are applied over an additional recess 38, defined by the outer width or surface of the threads 12. This additional recess assists in the attachment of the bone to the implant. This recess 38, in accordance with the depth of the recess, defines the lower level with its bottom. For a better explanation of the design of an alternative embodiment of the invention, hereinafter, this refers to the "lower volume" defined by the lower levels of the recess 38 in the thread 12. In other words, this "lower" volume (also referred to as the "center volume of the recess") is the volume passing through through all the innermost points of the recesses or through all the points of the recesses closest to the longitudinal axis of the implant 1″. In the combined embodiment of the invention illustrated in FIG. 11, the recess 38 in the thread 12 of the implant 1 also comprises a first or formed recess zone 40 in which the cross section of the lower volume in the thread 12 has a series of principal directions in which the radius, measuring the distance between the center of the cross section and its outer contour, assumes a relative maximum value and therefore a higher value than in neighboring orientations.

By analogy with FIG. 10, fig. 12 shows by way of example possible input data for CNC processing of the respective figures for a 1″ implant. In particular, in FIG. 12a is a right side view of the outer volume 28, FIG. 12b illustrates the profile of the outer volume 28, FIG. 12c illustrates a left side view of the outer volume 28. FIG. 12d is a correct size view of the central part 2, FIG. 12e illustrates the profile of the central part 2, FIG. 12f is a left side view of the central part 2, FIG. 12g illustrates a right side view of the lower volume, FIG. 12h illustrates the profile of the lower volume, FIG. 12i illustrates a left side view of the lower volume, and FIG. 12j illustrates circular modes for CNC machining. As can be seen in FIG. 12j, the differential ovality parameter e, which is an alternative definition of the shape of the central part 2/outer volume 28/bottom volume and which is determined by the difference between the maximum radius of the cross section and its minimum radius for a typical maximum diameter of about 4.20 mm, is preferably selected from range from 0.10 to 0.50 and more preferably may be about 0.23 mm.

In the embodiment of the invention illustrated in FIG. 12, the change in the ovality parameter e and hence the eccentricity parameter for the central part 2/outer volume 28/lower volume along the longitudinal axis y of the implant is similar to what has been explained in connection with FIG. 10, and reference is made to said explanation. The main differences between the embodiments of the invention illustrated in FIG. 10 and 12 are the length of the implant and the presence of recesses in the embodiment of the invention illustrated in FIG. 12. As a non-limiting example, the implant illustrated in FIG. 12 may have a total length of 9 mm and have points with the following coordinates from Y01:

- for the outer volume 28 (see Fig. 12b): Y02 at a distance of 2.30 mm, Y03 at a distance of 4.5 mm, Y04 at a distance of 8.10 mm and Y05 at a distance of 9 mm;

- for the central part: Y07 at a distance of 2.30 mm, Y08 at a distance of 5 mm, Y09 at a distance of 7 mm and Y10 at a distance of 9 mm;

- for the "lower" volume or "centre recess volume": Y11 at a distance of 0.75 mm, Y12 at a distance of 2.30 mm, Y13 at a distance of 4.50 mm and Y14 at a distance of 7.90 mm.

As a non-limiting example, between points Y01 and Y02, the implant may have a maximum outer diameter ∅D of 4.20 mm. Between points Y02 and Y03, the implant can have a maximum outer diameter ∅D varying from 4.20 to 3.80 mm. Between points Y03 and Y04, the implant may have a conical shape with an outer diameter varying from 3.80 to 3.57 mm, and between points Y04 and Y05, the implant may have an outer diameter varying from 3.57 to 1.90 mm.

In addition, and as a non-limiting example, between points Y01 and Y07, the implant may have a maximum central portion diameter ∅D varying from 4.20 to 3.78 mm. Between points Y07 and Y08, the implant can have a maximum diameter of the central part, varying from 3.78 to 2.84 mm. Between Y08 and Y09, the implant may have an outer diameter ranging from 2.84 to 2.31 mm, and between Y09 and Y10, the implant may have an outer diameter ranging from 2.31 to 1.68 mm.

In addition, the "bottom" volume or "center volume" may have a differential ovality parameter e varying along the y-axis. As a non-limiting example, the ovality parameter may have a constant or variable value of/selected from a value in the range of 0.10 to 0.50 mm. In one embodiment of the invention, the "lower" volume or "volume of the central part of the recess" may have parameters that vary as follows:

- from Y1 to Y11 (the first zone of the lower volume) the differential ovality parameter e can have a value, for example, a constant, in the range from 0.10 to 0.50 mm, and the eccentricity can be a constant,

- from Y11 to Y12 (second zone of the lower volume) e can change from an initial value selected from the range from 0.20 to 0.30 mm to a final value of 0 mm, the change can be linear, and the eccentricity can also change linearly,

- from Y12 to Y13 (third zone of the lower volume) e may have a value of 0 mm, and the "lower" volume or "volume of the central part of the recess" may have a conical shape tapering down towards the y-axis,

- Y13 to Y14 (fourth zone of the lower volume) e may have a value of 0 mm, and the "lower" volume or "volume of the central part of the recess" may have a conical shape.

It should be noted that the differential ovality parameter e (and hence the eccentricity value) may be different in a given cross section for each of the central portion 2, the outer volume 28 and/or the lower volume. The ovality parameter e may have a value that is/selected from a value in the range of 0.10 to 0.50 mm. In a certain embodiment of the invention, the ovality parameter may have a value of 0.15, 0.20, 0.23, or 0.30 mm.

The implant according to the invention may therefore comprise a female volume 21 and/or a central portion 2 and/or a recess central volume having:

- at least one coronal zone (also called the first formed zone) or part, passing along the longitudinal axis y of the implant with a maximum, for example constant, eccentricity. Said maximum eccentricity may range from 1.05 to 1.2 and may extend, for example, from 0 to 80% of the total length of the implant. In some embodiments, the coronal zone extends about 30%, 45%, 60%, or 70% of the total length of the implant;

at least one transitional zone or portion extending along the longitudinal axis y of the implant with an eccentricity varying between a specified maximum eccentricity and a minimum eccentricity, said change may be linear, and

- at least one apical zone (also called a circular zone) or part, passing along the longitudinal axis y of the implant with the specified minimum constant eccentricity.

The implant according to the invention may therefore comprise a female volume 21 and/or a central portion 2 and/or a recess central volume having:

- at least one coronal zone (also called the first formed zone) or part, passing along the longitudinal axis y of the implant with a maximum, for example constant, eccentricity. The specified maximum eccentricity can be from 1.05 to 1.2. The coronal zone may 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 part, passing along the longitudinal axis y with an eccentricity varying from the specified maximum eccentricity to the minimum eccentricity, and the specified change may be linear, the transition zone may extend at least 10%, at least 15 %, at least 20% or at least 25% of the total length of the implant,

- and at least one apical zone (also called a circular zone) or a part extending along the longitudinal axis of the implant with the specified minimum permanent eccentricity. The apical zone may extend at least 30%, at least 35%, at least 40%, at least 45%, or at least 50% of the total length of the implant.

The table below shows different non-limiting possible lengths for each implant zone depending on the overall length of the implant.

Abutment length in mm: 13 End of coronal zone in mm End of transition zone in mm Apical end in mm 13 2.35 5 13 % external shape of the implant 18.07692308 20.38461538 61.53846154 2.3 5.7 13 % internal shape of the implant 17.69230769 26.15384615 56.15384615 Implant length in mm: 9 2.35 5 9 9 26.11111111 29.44444444 44.44444444 internal 2.3 5.7 9 25.55555556 37.77777778 36.66666667 Implant length in mm: 11 eleven 2.35 5 eleven % external shape of the implant 21.36363636 24.09090909 54.54545455 2.3 5.7 eleven % internal shape of the implant 20.90909091 30.90909091 48.18181818

In FIG. 35 is a graph showing the different values (change or further development) of the eccentricity of the central part 2 and/or the female thread volume 28 and/or the formed recess zone 40 depending on the position along the longitudinal axis of the implant in some embodiments of the invention. As can be seen in FIG. 35, the apical zone of the central part 2 and/or the female volume 28 of the thread and/or the formed recess zone 40 may have a constant minimum eccentricity of 1 between point A and point B. The central part 2 and/or the female volume 28 of the thread and/or formed recess zone 40 may also have a transition zone starting at point B, wherein the eccentricity changes from a specified constant minimum eccentricity to a maximum eccentricity value at point C. Beyond point C, the central portion 2 and/or the enclosing thread volume 28 and/or the formed zone 40 the recess may have a coronal zone, while the eccentricity has a constant maximum value. As mentioned earlier, the specified constant maximum eccentricity value can be from 1.05 to 1.2.

In some embodiments of the invention, and in particular for the central part 2 and/or for the female volume 28 of the thread, point A may represent the apical end of the implant, and point D the coronal end of the implant. Points A, B, C and D do not always have the same coordinate for the central part 2, for the female volume 28 of the thread or the formed zone 40 of the notch. Point A should be considered the most apical point of the central part 2, the enclosing volume 28 of the thread or the formed zone 40 of the notch. As can be seen in FIG. 35, the shape of the eccentricity curve has no sharp corners, it is a solid line with one tangent at each point.

In addition to the geometry of the central portion 2 and/or the threads 12 as described above, in a preferred alternative embodiment of the invention, the elements of which are also considered independent inventions, additional means may be provided to ensure reliable engagement with bone tissue with high primary stability. For this purpose, in the embodiments of the invention illustrated in FIGS. 13-18, cutting grooves 46 are provided in the threaded part of the implant 1, 1', 1''. On each of the FIGS. 13-18 illustrate a perspective view of the respective implant, in which the different zones 20, 22, 26, 30, 32, 34 of the central part/thread are indicated by hatching changes. In these embodiments of the invention, in selected segments or in the entire central part 2 and thread 12, a certain number of cutting grooves 46 can be provided, preferably equal to the number of main directions of the central part 2 and/or thread 12, in the transition zone 26 and/or in other zones. 20, 22 of the implant 1. These cutting grooves 46 comprise a cutting edge 48 (see FIG. 19) which removes bone material when the implant 1 is screwed in, thereby improving the cutting capability of the implant 1 when screwed in. It will be appreciated that although notch 38 is not illustrated in the embodiments of the invention in FIGS. 13-18, in another alternative embodiment of the invention, any of these images can also be provided with a notch 38. With regard to the layout and/or design, the cutting grooves 46 have special features that are considered an independent invention and can be used, as illustrated in FIG. , together with features of implant 1 and/or implant 1' and/or implant 1'' as described above, or in other conventional implant or fixation systems.

In FIG. 13-15 illustrate embodiments of the invention of the implant 1 illustrated in FIG. 1, in which the position and/or length of the cutting grooves are changed, preferably in accordance with the specific requirements of the individual implant design. These embodiments form a variation with multiple cutting grooves 46 that extend longitudinally along parts of the transition zones 28, 34 and parts of the formed zones 22, 30.

In the embodiment of the invention illustrated in FIG. 13, the central part 2 and the external thread are configured to have corresponding external contours, that is, both the circular region 20 of the central part and the circular region 32 of the thread are located near the apical end 4. Next to them, both the transition zone 26 of the central part and the transition zone 34 of the thread are located so as to overlap each other. Proximate the coronal end 6, the central portion formed zone 22 is located together with the thread formed zone 30, both zones in this embodiment having a tri-oval cross section.

In contrast to the above, in FIG. 14 illustrates an embodiment of the invention in which zones of different types and cross sections partially overlap. In particular, near the apical end 4 are located both the circular region 20 of the central part and the circular region 32 of the thread, each starting from the apical end 4. As indicated by the change in hatching, for the central part 2, as seen in the longitudinal direction, the transition from the circular zone 20 of the central part to the transition zone 26 of the central part is in the transition position 43, while the thread 12 is still within its circular zone 32. In the transition position 43a, the transition zone 26 of the central part ends and the formed zone 22 of the central part begins part zone, and in a position inside the formed zone 22 of the central part, the circular zone 32 of the thread passes into the transition zone 34 of the thread. At a position still farther towards the coronal end 10, at the transition position 43b, the formed region 22 of the central part ends again and passes into another transition zone 26. At the same transition position 43b, the transitional zone 34 of the thread passes into the formed zone 30 of the thread. Therefore, in this embodiment of the invention, the different zones for the central part and the threads partially overlap each other in various combinations.

In FIG. 15 again illustrates an embodiment of the invention in which the central portion 2 and the outer thread 12 are configured to have corresponding outer contours, i.e., both the circular region 20 of the central portion and the circular region 32 of the thread are located near the apical end 4. Next to them, both the transition zone 26 of the central part and the transition zone 34 of the thread are located so that they overlap each other. Proximate the coronal end 10, the formed zone 22 of the central part is located together with the formed zone 30 of the thread, both zones in this embodiment of the invention have a tri-oval cross-section.

As illustrated in the examples according to FIG. 16-18, the cutting grooves 46 may have various orientations, such as being generally parallel to the longitudinal axis of the implant 1 (example in FIG. 16), inclined with respect to the longitudinal axis of the implant 1 (as in FIG. 17), or curved and wrapped around the outer surface 8 the central part 2, as illustrated in FIG. 18.

In FIG. 19 illustrates another preferred embodiment of the invention based on the basic design of the implant 1''. In FIG. 19 illustrates a side view of the top or coronal section of a 1″ implant. Obviously, with respect to the number and arrangement of the cutting grooves 46, the illustrated concept can also be used in the case of any other preferred implant concept or for typical implant/screw fixation designs. In the embodiment of the invention illustrated in FIG. 19, which is considered an invention in itself, the cutting grooves 46 are located in the threaded region of the implant 1″. As regards their position in the "z-direction", i.e. in the longitudinal direction of the implant 1'', they are positioned offset from the adjacent cutting groove 46 so that in their positions the cutting grooves 46 follow the thread pitch 12. According to this the design makes it possible to make sure that when the implant 1'' is screwed into the bone tissue, a separate thread 12 engaging with the bone material will provide a cutting effect in the same area of the bone using successive cutting grooves 46.

In FIG. 20 illustrates the implant 1 illustrated in FIG. 1, in a variant with a certain number of cutting grooves 46, which in the longitudinal direction extend along parts of the transition zones 28, 34 and parts of the formed zones 22, 30. In FIG. 21 shows (schematically) a cross section of the implant 1 illustrated in FIG. 20 in the position shown in FIG. 20. As can be seen in FIG. 21, the cross-section of the central part 2 and its outer surface 8 has a tri-oval shape. In other words, in its formed core zone 22, the cross section of the core 2 (as well as the cross section of the female volume 28 of the thread 12) has a certain number (i.e., three) principal directions in which the radius measuring the distance between the center 50 of the cross section and its outer contour takes on a relative maximum value ("maximum radius") and therefore a higher value than in adjacent orientations. In the image in Fig. 21, one of these main directions is oriented parallel to the vertical upward direction represented by line 52. The local maximum of the radius of the outer contour of the central part 2 in this main direction is at point 54. The other two main directions, due to the symmetrical arrangement of the main directions relative to the center 50, are at an angle of 120° relative to line 52.

The cutting grooves 46 in this example are also arranged symmetrically around the center 50, ie the angle between two adjacent cutting grooves is also 120°. The cutting flutes 46 in the angular orientation are appropriately positioned to maximize the efficiency of cutting the bone material, taking into account the decompaction effects in the bone tissue after the local maximum radius has been passed during the screwing process. For this purpose, each cutting groove 46, as seen in the direction of orientation around the center 50 or the central longitudinal axis of the central part 2, is located with a predetermined rotational offset with respect to the adjacent main direction. As illustrated in FIG. 21, the center portion 2 is illustrated in plan view (thus, when inserted, the center portion will be rotated in the right (or clockwise) direction, and the rotation offset is represented by the angle α between the leading maximum represented by line 52 and the adjacent rear cutting groove 46 , as illustrated by the dashed line 56 directed towards the corresponding cutting edge 48 of the cutting groove 46.

In the illustrated embodiment of the invention, this angle α is chosen according to a selection criterion which is itself considered an independent invention. In accordance with this selection criterion, the cutting edge 48 must be positioned such that the radius of the cutting edge, defined by the intersection of the dotted line 56 and the outer surface 8, that is, the outer limit of the radial extension of the cutting edge 48 from the center 50, is 20-75 microns less than the maximum radius . This criterion takes into account the specific elastic properties of the bone, which, depending on its density, is compressed or decompressed by approximately the same amount after compression. In the illustrated embodiment, the cutting edge radius is chosen to be about 35 µm less than the maximum radius, which, according to the rest of the geometry of the central portion 2, translates into a preferred angle α of about 106°.

This preferred angle of displacement can also vary depending on the value of the maximum radius in order to reliably take into account the elastic properties of the bone material. Due to the preferred conical design of the central part 2 and/or the outer volume 28, this maximum radius can vary as a function of the coordinate in the longitudinal direction of the implant 1, thereby also making it possible for the preferred offset angle to depend on this coordinate in the longitudinal direction. As a result, the resulting cutting groove 46 can wrap around the central part 2 of the implant 1.

In general, thread 12 may have any convenient thread profile, in particular flat threads. The free width 58 of the thread 12, depending on the respective position in the longitudinal direction of the implant 1, continuously increases with increasing distance from the apical end 4. In this design, the thread 12 in the area close to the apical end 4 can have a relatively steep, small outer width, thereby providing high cutting ability when the thread 12 enters the bone tissue. With the progressive screwing of the implant 1 (i.e. further entry of the implant into the bone tissue), in a given position in the bone tissue, the width 58 of the thread 12 continuously increases, thereby continuously expanding the corresponding local gap in the bone tissue and constantly increasing the contact area between the bone tissue and implant.

In an embodiment of the invention, as illustrated in the figures, the thread 12 is configured to have a specific profile to suitably interact with the non-circular cross section of the center portion 2 and/or the thread 12. In this modification, which is also considered inventive in itself, specifically regarded as an independent invention, as can be seen in FIG. 22 and in an enlarged view in FIG. 23, the thread 12 is profiled with an apical surface 60 and a coronal surface 62, with the apical surface 60 oriented generally perpendicular to the longitudinal axis 64 of the implant 1, i.e. the plane normal of the apical surface 60 is oriented substantially parallel to the longitudinal axis 64 of the implant 1. In addition, coronal surface 62 is oriented at an angle of about 60° to longitudinal axis 64, i.e., the planar surface normal of coronal surface 62 is oriented at about 30° to longitudinal axis 64 of implant 1. This angle is represented by line 66. In other words, thread 12 generally forms called trapezoidal thread.

By this particular choice of orientation of the apical surface 60, which is itself considered an independent invention, the potential effect of a non-circular, eg tri-oval, shape can be offset. This effect is the oscillation of the bone, with the thread 12 in contact when it is inserted. This means that when the implant 1 is inserted, the thread 12 will only come into contact with the bone at certain intervals.

By making the apical side of the thread 12 at 90° to the longitudinal axis, the apical surface will have improved contact along the entire length of the thread after insertion. This is illustrated in the enlarged segment according to FIG. 24. In FIG. 24 illustrates in longitudinal section an implant segment 1 after insertion into bone material 70.

In the illustrated preferred embodiment of the invention, which is itself considered an independent invention, the depth of the thread 12 on its apical surface 60 is chosen for improved primary stability after insertion. For this purpose, this preferred embodiment of the invention takes into account that in the formed zone 22, 30 of the central part and/or threads and/or in the transition zone 26, 34 of the central part and/or threads after insertion to absorb masticatory forces, ideally the apical surface 60 of the thread should be in physical contact with the bone material 70 as much as possible. In this regard, the minimum radius zones in the formed/transition zone will take on the final post-insertion positions that the previous maxima have passed, thereby creating voids 72 from which the bone is pushed out. textile. In order to nonetheless provide reliable platforms 74 in the bone material, in which the apical surface 60 of the thread can rest on a portion of the bone material 70, the depth of the thread 12 on its apical surface 60 is chosen to be greater, preferably at least twice as large, as the difference between the maximum and minimum radii of the outer contour of the enclosing volume 28.

In yet another preferred embodiment of the invention, which is itself considered an independent invention, an improved connection system 80 is provided in the implant 1 (as well as in the implants 1', 1'') for mechanically connecting the implant 1 and its associated abutment to each other. Various embodiments of the invention for the improved connection system 80 based on implant 1 are described below. Obviously, all embodiments of the invention can also be useful for any other type of implant in accordance with, for example, implants 1'', 1''', as described higher.

The connection system 80 includes a receiving channel 10 into which the corresponding connection post of the abutment can be inserted. In FIG. 25a and 25b illustrate the view of the implant 1 from the direction represented by the arrow 82 in FIG. 4. As can be seen in FIG. 25, the cross section or outer contour in the non-circular zones 22, 30 of the implant 1 is tri-oval, thereby providing three main directions in the transition zones 26, 34 and in the formed zones 22, 30, respectively. These main directions, in which the respective cross-sectional radius has a local maximum, are arranged symmetrically about the central longitudinal axis of the central part 2. In addition, as shown in FIG. 25, the outer profile of the implant 1, defined by the outer contour of the thread 12, matches or "follows" the outer contour of the central portion 2. Accordingly, in those directions in which the radius of the central portion 2 has a local maximum, the outer contour of the thread 12 also takes on a local maximum. In addition, due to the conical or tapered geometry of the central part 2 in the transition zone 26, the minimum radius of the central part 2 in the formed zone 22 is greater than the radius of the outer contour of the thread 12 in the circular zone 20.

In addition, the receiving channel 10 also has an outer profile or contour that matches or “follows” both the outer contour of the threads 12 and the outer contour of the central portion 2 of the implant 1. Accordingly, in those directions in which the radius of the central portion 2 and the outer contour threads 12 have a local maximum, the contour of the receiving channel 10 also takes on a local maximum, i.e. is also tri-oval. In addition, the receiving channel 10 also tapers, with its cross-section narrowing as it approaches its lower end 84. Due to this shape, the receiving channel 10, together with its abutment connecting post, provides a so-called intermittent circular feed design that guarantees correct angular alignment of the abutment when inserted. . As can be seen in FIG. 25, as well as in longitudinal section of the implant 1, in accordance with FIG. 26 and 27, a periodic circular feed circuit 86 is provided in the receiving channel 10 at its lower or lower end 84 to properly assemble the abutment. This "second periodic circular feed", which in the preferred embodiment of the invention illustrated in FIG. 26, 27, has a star-shaped cross section, can be used to transmit the torque required to insert the implant by inserting an appropriate tool. Due to the periodic circular feeding circuit 86, this torque can be applied without affecting the periodic circular feeding circuit of the actual receiving channel 10.

In an alternative implementation of the implant 1''' with a second periodic circular feed, as illustrated in FIG. 28, the second periodic circular feeding circuit can be integrated with the first periodic circular feeding circuit, which is provided by the receiving channel 10 with its non-circular cross section. In accordance with the illustrated embodiment of the invention, this is achieved by a series of slots 88 that are cut into the conical side wall of the receiving channel 10. can be used to engage slots 88, thereby ensuring that the inside surface of the receiving channel 10 is free from load and therefore cannot be damaged during insertion. With respect to the tri-oval cross section of the receiving channel 10 in the illustrated embodiment, slots 88 may be positioned to "match" the cross section, that is, they may be located in major directions with local radius maxima, or they may be located with a certain offset relative to the main directions.

As illustrated in FIG. 26-28, in all preferred embodiments of the invention, the implant 1, 1', 1'', 1''' is provided with another highly effective feature, which alone or in combination of any number of features disclosed above is also an independent invention. In accordance with this feature, the implant 1, 1', 1'', 1''', as part of its internal connection system 80, includes a feedback structure 90 that provides feedback to the user after a connection pin or the like in an associated part the second implant (eg abutment) has been correctly and completely inserted into the implant receiving channel 1, 1', 1'''. To provide this feedback, the feedback structure 90 includes a slot or recess 92 located on the inner surface of the receiving channel, in the embodiments of the invention illustrated at its lower end 84, circumferentially surrounding the receiving channel 10. This circular recess 92 can interact with one or more or receive one or more respective protrusions of a dental fixture such as the dental fixture described in patent application EP16151231.4 and/or projections of a retaining element such as described in patent application EP15178180.4 by the same applicant, both applications included in the present description by reference. Once the connecting pin is fully and correctly inserted into the receiving channel 10, these protrusions snap into the recess 92 with an audible “click” sound, thereby indicating to the user that proper insertion of the contact pin into the receiving channel 10 is complete.

In yet another alternative embodiment of the invention, the implant 1'''', as illustrated in FIG. 29, 30 and 31 (side view), the coronal end 6 has a particular shaped design. This feature, which alone or in combination of any number of features described above, is considered an independent invention, provides improved positional orientation of the implant 1'''' when inserted, together with improved overall system strength. This is achieved in that the width of the upper/superior or coronal surface 100 of the implant 1'''', i. e. the width of the implant wall 1'''', varies due to the presence of the posterior cone, as well as rises and falls, with the greater width falling on the falls and the smaller width falling on the rises, as illustrated in FIG. 29 and 30.

In particular, the coronal surface 100 of the implant 1'''' has an undulating, wavy or sinusoidal contour with maxima and minima of the coronal surface 100, that is, the maxima and minima of the heights in the longitudinal direction of the implant 1'''', and they are located alternately along the perimeter of the coronal end 6 of the implant 1''''. At the maxima of the coronal surface 100, and preferably also in the immediate vicinity of these maxima, the coronal end 6 of the implant 1'''' has a conical shape or configuration, i.e. a reverse conical shape or configuration, so that the lateral dimensions or cross-sectional elongations of the coronal end 6 perpendicular to the longitudinal direction of the implant 1'''' decrease along the direction from the apical end 4 of the implant 1'''' to the coronal end 6 of the implant 1'''' (see FIGS. 29 and 30).

Because of this undulating, wavy or sinusoidal contour and the posterior conical shape or configuration of the implant 1'''', the width of the implant wall 1'''', i.e. the width of the implant wall 1'''', at the coronal end 6 also varies. In particular, the wall width is larger at the 100 coronal surface minima and smaller at the 100 coronal surface maxima.

The above features of the coronal surface 100, alone or in combination with any of the features described in more detail above, are considered independent inventions. These features make it possible to determine the orientation of the implant particularly reliably and without difficulty.

In the embodiment of the invention illustrated in FIG. 29, the implant 1'''' in its formed zone 22 of the central part, and also, due to the preferred design of "coinciding contours", in its formed zone 30 of the thread has tri-oval cross-sections, that is, the corresponding cross-section has three main directions in which the radius includes local maxima. In synchronization with this cross-sectional shape in positions coinciding with these main directions, the coronal end 6, as seen in the direction parallel to the longitudinal axis of the implant 1'''', also has local maxima. In other words, the coronal surface 100 of the implant 1''''' is not a flat surface, but has an undulating, sinusoidal design, as detailed above, with its maxima located in the main directions as defined by the shaped zones 22, 30.

In yet another preferred embodiment of the implant 1''''', the tip or apical end 4, in particular with respect to the external thread 12 in this section, may be designed specifically to facilitate insertion into bone material. For this purpose, at least the apical part of the thread 12 is serrated, as can be seen in FIG. 32. In this embodiment, a plurality of notches 102 with at least a cutting edge may be defined on the apical and/or coronal surface of the thread 12.

In FIG. 33 illustrates an embodiment of an implant according to the invention that has at least one discontinuous apical cutting groove 104 that can be defined (or milled or cut) in at least the apical half of the thread 12. As can be seen in FIG. 33, said cutting groove does not extend within the central portion of the implant. The implant according to this embodiment of the invention may also have two or more such cutting grooves. Also in this embodiment of the invention, the thread can be considered as a serrated thread.

Said serrated thread assists in inserting the implant into the hole when used in a post-extraction tooth socket (bed) of a patient. Because the angle of the socket is not perpendicular to the axis of the implant, one side of the wall will touch the implant first and affect the placement of the implant. To reduce this effect, the serrated thread cuts away the bone on the side of the implant.

These features alone or in combination with any of the features disclosed above are considered independent inventions.

In the implant 1, 1', 1'', 1''', 1'''', 1''''' in any of the embodiments of the invention described above, or in any combination thereof in general, the overall length is preferably in accordance with the specific requirements set by the individual treatment of the patient. In the embodiments of the invention illustrated in the figures above, a typical "standard" overall length of the respective implant may be about 13 mm. In other embodiments of the invention, the implant can be made in the form of a "short version" with an overall length of, for example, about 7 mm. An example of this embodiment of the invention is illustrated in FIG. 34.

In FIG. 36 illustrates an insertion tool 200 according to the first embodiment of the present invention.

The insertion tool 200 is a tool for inserting a dental implant into a patient's bone tissue. The insertion tool 200 includes a proximal portion 202 and a distal portion 204 as illustrated in FIG. 36(a). The distal portion 204 is configured to interact with the implant so as to screw the implant into the bone tissue.

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

The retaining member 206 is integral with one of the two parts, namely the proximal part, of the insertion tool 200 (see FIGS. 37(a) and (b)). In particular, the retaining member 206 is integral with the proximal part of the insertion tool 200 through two connecting portions 212 located between the retaining member 206 and the longitudinally proximal portion of the retaining member 206 (see FIGS. 36(c) and 37(a). )). Each of the connecting portions 212 extends along only a portion of the retaining member 206 in the circumferential direction of the retaining member 206, as shown schematically in, for example, FIG. 37(a) and (b). The connecting parts 212 are located essentially opposite each other in the radial direction of the retaining element 206.

The retaining member 206 has a substantially cylindrical shape with a substantially circular cross section perpendicular to the longitudinal direction of the retaining member 206 (see FIG. 37(a)). The holding element 206 is made in the form of a hollow tubular element. The retaining member 206 has a closed annular shape or a closed circular shape, that is, a ring shape without a hole in its circumference. The elastic deformability of the retaining element 206 in all of its transverse directions is provided by an appropriate choice of material and wall thickness of the retaining element 206.

The retainer 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 member 206 may be resiliently compressed in its transverse direction when the insertion tool 200 is attached to the dental implant (eg, as in FIGS. 37(d) and 39).

The protrusion 210 of the attachment portion 208 allows the insertion tool 200 to be snap-attached to the dental implant, as will be described in detail below with reference to FIG. 37(d) and 39.

As illustrated in FIG. 37(a), a protrusion 210 of the fastening part 208 is provided between the two connecting parts 212. Thus, a particularly secure and effective latch for the fastening part 208 and the dental implant can be provided.

The distal portion 204 of the insertion tool 200 has a drive region 214 (see, for example, FIGS. 36-38). In the drive region 214, the cross section of the distal portion 204, perpendicular to the longitudinal direction of the insertion tool 200, has a number of principal directions in which the radius, measuring the distance between the center of the cross section and its outer contour, takes on a relative maximum value and therefore a higher value, than in adjacent orientations (see Fig. 38(d)).

The drive region 214 of the distal portion 204 of the insertion tool 200 engages with the implant. The drive region 214 is an anti-rotation structure. The drive region 214 is designed to avoid relative rotation between the insertion tool 200 and the implant about the longitudinal axis of the tool 200 when the tool 200 and the implant are engaged with each other, for example, by partially inserting the distal portion 204 of the tool 200 into the socket ) of the implant.

The drive region 214 is configured to interact with the corresponding anti-rotation structure, ie the drive portion, of the implant (see FIGS. 37(d) and 39), as will be explained in more detail below.

The main directions in the drive region 214 of the insertion tool 200, in which the corresponding cross-sectional radius has a local maximum, are axially symmetrical about the central longitudinal axis of the insertion tool 200 (see FIG. 38(d)). The number of major directions in the drive region 214 is three, that is, the drive region 214 has a tri-oval cross section as illustrated in FIG. 38(d). In combination with the symmetrical arrangement of the major directions with respect to the longitudinal direction of the insertion tool 200, this tri-ovality creates a rotation offset angle between two adjacent major directions of 120°.

The drive region 214 has a conical configuration such that, in the drive region 214, the transverse dimensions or elongations of the cross section of the distal portion 204 perpendicular to the longitudinal direction of the insertion tool 200 decrease along the direction from the proximal end of the insertion tool 200 to the distal end of the insertion tool 200 (see Fig. 36, 37 and 38).

The drive region 214 is located in the proximal direction from the holding element 206.

The cross-sectional shape of the drive region 214 ensures efficient, reliable and uniform transmission of the rotational force applied to the insertion tool 200 around its longitudinal axis to the implant.

In a modification of the first embodiment of the invention, the insertion tool 200 illustrated in FIG. 38(e), tool 200 does not include a drive region. Rather, as illustrated in FIG. 38(e) is a cross section taken along line A-A in FIG. 38 (c), has a circular shape.

The distal portion 204 of the insertion tool 200 further has a drive section 216. In the drive section 216, a cross section of the distal portion 204 perpendicular to the longitudinal direction of the insertion tool 200 has a plurality of radially convex portions 218 and a plurality of radially concave portions 220 that are arranged alternately around the perimeter of the transverse section (see Fig. 38 (f)). Each of the radially outermost points 222, 224 of the radially raised portions 218 is on a respective circle around the center of the cross section, as illustrated in FIG. 38(f).

The cross section of the distal portion 204 of the insertion tool 200 in the drive section 216 has the same number of radially convex portions 218 and radially concave portions 220, namely 6 of each type.

The radially convex portions 218 include first radially convex portions and second radially convex portions, wherein all radially outermost points 222 of the first radially convex portions are on the same first circle around the center of the cross section, and all radially outermost points 224 of the second radially convex portions are on one 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 radially convex portions and the second radially convex portions are arranged alternately around the perimeter of the cross section with respective radially concave portions 220 disposed therebetween. The number of the first radially convex parts is the same as the number of the second radially convex parts.

Each of the radially convex portions 218 and the radially concave portions 220 of the cross-section of the drive section 216 has a curved shape, for example, at least partially, a circular shape, at least partially, an elliptical shape, at least partially, an oval shape, or the like. The radially convex portions 218 and the radially concave portions 220 are directly adjacent to each other.

The radially innermost points 226 of the radially concave portions 220 are on the same circle 228 around the center of the cross section. Thus, all radially innermost points 226 of the radially concave portions 220 are on the same circle 228 around the center of the cross section.

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

The drive section 216 of the distal portion 204 of the insertion tool 200 engages with the implant. The drive section 216 is an anti-rotation design. The drive section 216 is designed to avoid relative rotation between the insertion tool 200 and the implant about the longitudinal axis of the tool 200 when the tool 200 and the implant are engaged with each other, for example, at least partially, by inserting the distal portion 204 of the tool 200 in the implant bed.

The drive section 216 is configured to interact with the corresponding anti-rotation structure, ie the drive area of the implant (see FIGS. 37(d) and 39), as will be explained in more detail below.

The distal portion 204 of the insertion tool 200 according to the first embodiment thus has a drive region 214 and a drive section 216. The drive region 214 is positioned proximal to the drive section 216 (see FIGS. 36-38).

Because of the presence of two anti-rotation structures on the distal portion 204 of the insertion tool 200, i.e., the drive region 214 and the drive section 216, which can interact with two corresponding anti-rotation structures on the implant, i.e., the drive portion and the drive zone, the rotational force or load applied to the implant when it is inserted into the bone tissue, can be distributed between the two structures. Thus, any damage to either of these two structures in the implant can be minimized. Therefore, one or both of these structures in an implant can be reliably and efficiently used as a marker of an abutment, an indicator post, an impression post, or the like after the implant has been inserted into the bone tissue.

The drive region 214 and the drive section 216 further assist in accurately positioning the insertion tool 200 relative to the implant. Due to the cross-sectional shapes of these elements, only three relative angular positions are possible between the instrument 200 and the implant.

The distal portion 204 of the insertion tool 200 further has a holding member 206, as detailed above. The drive section 216, the retaining member 206, and the drive region 214 are arranged in this order in a direction from the distal end of the insertion tool 200 to the proximal end of the insertion tool 200.

The insertion tool 200 consists of two separate parts, ie, a distal part 230 and a proximal part 232, which are attached to each other as illustrated in FIG. 37(a)-(c).

The distal portion 230 of the insertion tool has a protrusion that fits into a corresponding recess of the proximal portion 232 of the insertion tool 200 (see FIGS. 37(c) and (d)). The distal portion 230 and the proximal portion 232 are attached to each other by inserting a protrusion into a recess. The protrusion is held in place within the recess by friction using the molded shoulder 234 of the distal portion 230 distally from the protrusion (see FIG. 37(b)). The pressed shoulder 234 additionally has the function of sealing against liquids.

The protrusion and recess have respective anti-rotation structures to prevent any rotation of the distal portion 230 and the proximal portion 232 relative to each other about the longitudinal axis of the insertion tool 200. The anti-rotation structure of the distal portion 230 has a cross section, that is, an outer cross section of the protrusion perpendicular to the longitudinal direction of the insertion tool 200, which is non-circular, namely substantially square (see FIG. 37(a)). The anti-rotation structure of the distal portion 230 of the insertion tool 200 can interact with the corresponding anti-rotation design of the proximal portion 232 of the insertion tool 200. The counter-rotational structure of the proximal portion 232 of the insertion tool 200 has a cross section, that is, an inner cross section of the recess perpendicular to the longitudinal direction of the insertion tool 200, which is non-circular, namely substantially square. The cross sections of the anti-rotation structures of the distal portion 230 and the proximal portion 232 are substantially the same.

The distal portion 230 includes a drive section 216, and the proximal portion 232 includes a retention member 206 and a drive region 214. Thus, the manufacture of the insertion tool 200, in particular the manufacture of the retention member 206, can be greatly simplified.

The retaining element 206 is integral with the proximal portion 232.

In FIG. 37(d) and 39 illustrate the combination of the insertion tool 200 according to the first embodiment of the present invention and the dental implant 201 according to the embodiment of the present invention in a state in which the distal portion 204 of the insertion tool 200 is inserted into the implant 201. In the state illustrated in these drawings, the insertion tool 200 is fully engaged with the implant 201.

The dental implant 201 is made of metal such as titanium, titanium alloy or stainless steel.

The dental implant 201 is designed to be inserted into a patient's bone tissue. The dental implant 201 includes a central portion 205 having an apical end 207 and a coronal end 209 as illustrated in FIG. 39(a).

The dental implant 201 has a bed or channel 236 (see FIGS. 37(d) and 39(b)) formed in the coronal portion of the implant 201 to receive a portion of the distal portion 204 of the insertion tool 200 comprising the retaining member 206. The central portion 205 contains a channel 236. The channel 236 is open with respect to the coronal end 209 and runs along the longitudinal direction of the implant 201 from the coronal end 209 to the apical end 207 (see Fig. 39 (a) and (b)).

The coronal portion of the implant 201 is formed with an annular cavity 238 (see FIGS. 37(d) and 39(b)) to receive the protrusion 210 of the attachment portion 208 of the retaining member 206. Therefore, the attachment portion 208 of the retaining member 206 can be securely held within the coronal portion of the implant. 201 latch.

In addition, the dental implant 201 has an external threaded portion 203 for screwing the implant 201 into the patient's jawbone tissue (see FIGS. 39(a) and (b)).

When the insertion tool 200 is attached to the dental implant 201, a portion of the distal portion 204 of the insertion tool 200 is inserted into the channel 236 of the implant 201 so that the protrusion 210 of the attachment portion 208 of the retaining member 206 is received in the annular cavity 238 formed in the coronal portion of the implant 201. Therefore, the retainer 206 is securely held within this coronal portion by a latch, thereby securely attaching the insertion tool 200 to the implant 201.

In the process of attaching the insertion tool 200 to the implant 201, the retaining member 206 first elastically deforms, i.e., resiliently compresses, in its transverse directions when the retaining member 206 is inserted into the channel 236 and then recovers to its shape immediately after the protrusion 210 is received. in the annular cavity 238. This “click-in” process of the protrusion 210 provides audible and tactile feedback to the user of the insertion tool 200, such as a clinician or dental technician, such as in a dental laboratory, indicating that the insertion tool is properly seated in the implant 201 (see Fig. 37 (d) and 39).

In this fully engaged state of the insertion tool 200, the insertion tool 200 can be used to pick up the implant 201 and transport it to the implant site, whereby it must be inserted into the bone tissue. By securely engaging the tool 200 with the implant 201, any risk of the implant 201 falling out of the insertion tool 200 before it reaches the desired location can be safely avoided.

Furthermore, in this fully engaged state of the insertion tool 200, the drive region 214 and the drive section 216 of the distal portion 204 of the insertion tool 200 are engaged with the drive portion 240 and the drive region 242 of the implant 201, respectively, as illustrated in FIG. 39(b) and (c). The central portion 205 of the implant 201 has a drive portion 240 and a drive area 242. The drive area 242 is positioned apically with respect to the drive portion 240, as illustrated in FIG. 39(b).

In the drive portion 240 of the implant 201, the cross-section, i.e. the internal cross-section, of the channel 236 of the implant 201, perpendicular to the longitudinal direction of the implant 201, has a number of main directions in which the radius, measuring the distance between the center of the cross-section and its outer contour, takes on a relative maximum value and hence a higher value than in adjacent orientations. The cross sections of the drive region 214 of the insertion tool 200 and the drive portion 240 of the implant 201 are essentially the same.

The drive portion 240 has a conical configuration such that, in the drive portion 240, the cross-sectional dimensions of the channel 236 perpendicular to the longitudinal direction of the implant 201 decrease along the direction from the coronal end 209 to the apical end 207, as illustrated in FIG. 39(b).

In the drive zone 242 of the implant 201, the cross-section, i.e., the inner cross-section, of the channel 236 of the implant 201, perpendicular to the longitudinal direction of the implant 201, has a plurality of radially convex portions, and may have a plurality of radially concave portions that are arranged alternately around the perimeter of the cross-section, each of the radially outermost points of the radially convex portions is on a corresponding circle around the center of the cross section, as illustrated in FIG. 39(c).

The cross section of the channel 236 of the implant 201 in the drive zone 242 has the same number of radially convex parts and radially concave parts, namely 6 of each type (see Fig. 39 (c)).

The radially convex portions of the drive zone 242 include first radially convex portions and second radially convex portions, wherein all of the radially outermost points of the first radially convex portions are on the same first circle around the center of the cross section, and all of the radially outermost points of the second radially convex portions are on one second circle around the center of the cross section. The second circle has a smaller radius than the first circle. The first radially convex portions and the second radially convex portions are arranged alternately around the perimeter of the cross section of the drive zone 242 with respective radially concave portions disposed therebetween. The number of the first radially raised parts is the same as the number of the second radially raised parts.

Each of the radially convex portions and the radially concave portions of the cross section of the drive zone 242 has a curved shape, for example, at least partially, a circular shape, at least partially, an elliptical shape, at least partially, an oval shape, or the like. The radially convex portions and the radially concave portions are located directly next to each other.

The radially innermost points of the radially concave portions are on the same circle around the center of the cross section. Thus, all the radially innermost points of the radially concave portions are on the same circle around the center of the cross section.

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.

The cross sections of the drive section 216 of the insertion tool 200 and the drive zone 242 of the implant 201 are substantially the same.

Therefore, the implant 201 can be screwed into bone tissue by matching or interaction between the drive region 214 and the drive section 216 of the distal portion 204 of the insertion tool 200 and the drive portion 240 and the drive area 242 of the implant 201, respectively. As mentioned above, due to the presence of the drive region 214 and the drive section 216, which can interact with the drive portion 240 and the drive area 242, the rotational force or load applied to the implant 201 when it is inserted into the bone tissue can be distributed between the two structures. which minimizes the risk of damage to the implant 201.

In FIG. 40 illustrates an insertion tool 300 according to a second embodiment of the present invention. The insertion tool 300 according to the second embodiment differs from the insertion tool 200 according to the second embodiment, inter alia, in that the insertion tool 300 consists of a single piece of material. Thus, all components of the insertion tool 300 are integrally formed.

The overall design and functionality of the insertion tool 300 is essentially the same as that of the insertion tool 200 . In particular, the insertion tool 300 has a proximal portion (not illustrated) and a distal portion 304. The distal portion 304 includes a drive section 316, a holding member 306, and a drive region 314 that are arranged in that order in a direction from the distal end of the insertion tool 300 toward the proximal end of the insertion tool 300 as illustrated in FIG. 40(a) and (b). In addition, the insertion tool 300 includes a cut-out portion 320 in the drive section 316, which facilitates the manufacture of the insertion tool 300, in particular with respect to the manufacture of the retaining member 306.

In FIG. 41 and 42 illustrate a dental implant 401 in accordance with an embodiment of the present invention.

The 401 dental implant is a self-tapping dental implant for insertion into a patient's jaw or bone tissue. The dental implant 401 includes a central portion 402 having an apical end 404, a coronal end 406, and an outer surface 408 extending along the longitudinal direction of the implant 401 between the apical end 404 and the coronal end 406, as illustrated in FIG. 41(a).

The dental implant 401 is made of metal such as titanium, titanium alloy or stainless steel.

The implant 401 further comprises a thread 412 extending outward from the central portion 402 (see FIGS. 41(a) and (c) and FIGS. 42(a) and (b)). Thread 412 has a thread profile angle of about 10°.

The thread 412 has an apical surface 414 facing the apical end 404 of the central portion 402 and a coronal surface 416 facing the coronal end 406 of the central portion 402. The thread 412 has a first groove 418, a first cutting groove 418 formed therein (see FIG. 41(a) and (b) and Fig. 42(b)). The first groove 418 extends from the apical end of the thread 412 toward the coronal end of the thread 412. As illustrated in FIG. 42(b), the first groove 418 extends over the first three full turns of the thread 412.

The thread 412 has in its apical portion a recess 420 formed on its coronal surface 416, the recess 420 extending in the direction from the coronal surface 416 to the apical surface 414 along a portion of the thickness of the thread 412. The recess 420 is open towards the first groove 418, as illustrated in fig. 41(a) and 42(b). The recess 420 is provided adjacent to, that is, directly adjacent to, the first groove 418. The recess 420 has a cutting function, that is, a bone tissue cutting function.

The thread 412 further has a second groove 418' and a third groove 418'' (see FIGS. 41(a) and (b) and FIGS. 42(a) and (d)). The first to third grooves 418, 418', 418'' are staggered or staggered along the length of the thread 412 and along the circumference of the thread 412. In particular, the second groove 418' is staggered or offset from the first groove 418 along the length and circumference. threads 412 as illustrated in FIG. 41(a). The third groove 418'' is located opposite the first groove 418 in the radial direction from the implant 401 and is located essentially in the same position in height or length as the thread 412 (see Fig. 41 (b) and 42 (a ) and (b)). The first to third grooves 418, 418', 418'' and recess 420 make the implant 401 self-tapping.

The first and third grooves 418, 418'' extend in a direction inclined or at an angle relative to the longitudinal direction of the implant 401 (see Fig. 42 (a) and (b)). The second groove 418' extends in a direction substantially parallel to the longitudinal direction of the implant 401 (see FIG. 41(a)).

The first to third grooves 418, 418', 418'' extend in the groove width directions along a portion of the circumference of the center portion 402.

The extension of recess 420 in the direction from coronal surface 416 to apical surface 414, i.e. the depth of recess 420, varies along directions parallel to coronal surface 416 (see FIGS. 41(c) and 42(b) and (c)). In particular, the depth of recess 420 decreases along the circumferential direction from the first groove 418, as illustrated in FIG. 42(b). In this way, a particularly efficient cutting function of the recess 420 is achieved.

Thus, the deepest recess 420 exists in the portion of the recess 420 that is immediately adjacent to the first groove 418.

In particular, recess 420 has the approximate shape of a quarter sphere, as illustrated in FIG. 41(c) and 42(b) and (c). This shape of recess 420 allows recess 420, and hence implant 401, to be manufactured in a particularly simple and economical manner.

The recess 420 is located on the ascending side of the first groove 418 in the direction of rotation of the implant 401 (see Fig. 42 (b)).

Recess 420 is formed on the coronal surface 416 of thread 412 at the first complete turn of thread 412, i.e., the most apical portion of a full turn of thread 412, as illustrated in FIG. 41(a) and (c) and 42(b). This arrangement of the recess 420 provides a particularly stable and reliable engagement of the implant 401 with jaw or bone tissue.

The indentation 420 assists in effectively cutting and removing bone material and further transporting the removed bone material towards the coronal end 406 of the central portion 402.

The implant 401 of the present embodiment allows it to be inserted into bone tissue with reduced force and with a high degree of precision. In this way, a particularly stable and reliable connection or engagement of the implant 401 with the bone tissue, i.e. high implant stability, can be achieved.

By positioning recess 420 in coronal surface 416 of thread 412, these benefits can be achieved for essentially all implant thread profile angles, in particular for small implant thread profile angles, such as about 10° thread profile angle of thread 412.

In FIG. 43 illustrates a dental implant 501 in accordance with an embodiment of the present invention.

The 501 dental implant is a self-tapping dental implant for insertion into a patient's jaw or bone tissue. The dental implant 501 includes a central portion 502 having an apical end 504, a coronal end 506, and an outer surface 508 extending along the longitudinal direction of the implant 501 between the apical end 504 and the coronal end 506, as illustrated in FIG. 43(a). The implant 501 further includes a thread 512 extending outward from the central portion 502 (see Fig. 44 (a) and (b)).

The dental implant 501 is made of metal, such as titanium, titanium alloy, or stainless steel.

The external configuration of the dental implant 501 may be substantially the same as any of the dental implants disclosed above, such as dental implant 1, which is illustrated in FIG. 1, 3, 6 and 7.

In particular, the dental implant 501 may have a first formed core region in which the cross section of the core 502 has a number of major directions in which the radius measuring the distance between the center of the cross section and its outer contour takes on a relative maximum value and therefore more higher value than in adjacent orientations. In particular, the center portion 502 in the first formed area of the center portion may have a three-oval cross section (see FIG. 43(c)).

The dental implant 501 may have a circular core region in which the cross section of the core 502 is generally circular.

The dental implant 501 may have a central portion transition zone located between the formed central portion zone and the circular central portion region, wherein, in the central portion transition zone, the cross-sectional geometry of the central portion 502 as a function of a parameter characteristic of the longitudinal direction coordinate varies continuously from basically circular shape next to the circular area of the Central part to the shape in which the cross section of the Central part 502 corresponds to the shape of the cross section in the first formed area of the Central part. In particular, the center portion 502 in the transition zone of the center portion may have a tri-oval cross section.

Dental implant 501 has a bed or channel 510 (see Fig. 43 (a) - (c)) formed in the coronal part of the implant 501. The channel 510 is open with respect to the coronal end 506 of the implant 501 and extends along the longitudinal direction of the implant 501 from the end 506 to its apical end 504.

The central part 502 has a hexagonal locking recess 515, in which the cross section of the channel 510, perpendicular to the longitudinal direction of the implant 501, has a substantially hexagonal shape.

Channel 510 includes a conical portion 514, a hexagonal locking recess 515, and an internally threaded portion 516 (see FIGS. 44(b) and (c)), which are located in this order in the direction from the coronal end 506 of the implant 501 to the apical end 504 of the implant. 501. The conical portion 514 and the hexagonal locking recess 515 are configured to receive the abutment and the tip portion of the insertion tool 200, 300, and the female thread portion 516 is configured to receive a connecting screw for fixing the abutment to the dental implant 501.

The conical portion 514 has a sidewall that tapers inwards relative to the longitudinal axis of the dental implant 501, providing a wider initial bore 510 at the coronal end 506 of the implant 501. The specific geometry of the conical portion 514 defines a conical half-angle relative to the longitudinal axis of the dental implant 501. This conical the half angle may be from about 10° to about 20°. In other words, the angle between the inner wall of the conical portion 514 and the longitudinal center line of the dental implant 501 may be from about 10° to about 20°. In one embodiment of the invention, the conical half angle is about 12°.

The ratio between the length of the conical portion 514 in the longitudinal direction of the implant 501 and the length of the hexagonal locking recess 515 in the longitudinal direction of the implant 501 may be about 1:1. The length of the tapered portion 514 may be at least about 1 mm, and the length of the hexagonal locking recess 515 may be at least about 1 mm. The length of the conical part 514 is the distance measured in the vertical direction from the top surface of the implant 501 to the portion of the channel 510 where the conical surfaces of the conical part 514 end. 515.

The ratios and lengths of the conical portion 514 and the hex locking recess 515 advantageously combine the benefits of a conical connection long enough to provide effective sealing and a hex locking recess 515 long enough so that sufficient torque can be transferred to the implant 501 when the implant 501 is inserted into the patient's jawbone. .

The features of all embodiments of the dental implant of this invention described above may be combined with each other or taken separately from each other. The features of all embodiments of the insertion tool of the present invention described above may be combined with each other or taken separately from each other.

List of reference positions

1, 1', 1'',

eleven'''',

201, 401,

501 - dental implant

2, 205,

402, 502 - central part

4, 207

404, 504 - apical end

6, 209

406, 506 - coronal end

8,408

508 - outer surface

10, 236

510 - receiving channel

12, 203

412, 512 - thread

20 - circular zone of the central part

22 - formed zone of the central part

24 - platform area of the alveolar ridge

26 - transition zone of the central part

26´ - the second formed zone of the central part

28 - covering volume

30 - formed thread area

32 - circular thread area

34 - thread transition zone

34´ - second formed thread zone

38 - notch

40 - formed excavation zone

42 - zone of the alveolar ridge

43 - transition position

44 - transition line

46 - cutting groove

48 - cutting edge

50 - the center of the cross section

52 - line

54 - dot

56 - dotted line

58 - free width

60 - apical surface

62 - coronal surface

64 - longitudinal axis

66 - line

70 - bone tissue

72 - emptiness

74 - platform

80 - connection system

82 - arrow

84 - lower end

86 - circuit periodic circular feed

88 - slot

90 - feedback design

92 - notch

100 - coronal surface

102 - notches

104 - apical cutting groove

200, 300 - insertion tool

202 - proximal part

204, 304 - distal part

206, 306 - holding element

208 - fastener

210 - ledge

212 - connecting part

214, 314 - drive area

216, 316 - drive section

218 - radially convex part

220 - radially concave part

222, 224 - radially outermost points of the radially convex parts

226 - radially innermost points of the radially concave parts

228 - circle around the center of the cross section

230 - distal part

232 - proximal part

234 - pressed shoulder

238 - annular cavity

240 - driving part

242 - drive zone

320 - cutout

414 - apical surface of the thread

416 - coronal thread surface

418, 418'

418'' - grooves

420 - deepening

514 - conical part

515 - hexagon lock recess

516 - part with internal thread.

Claims (96)

1. Dental implant (1) for insertion into the patient's bone tissue, containing: - a central part (2) having an apical end (4), a coronal end (6) and an outer surface (8) extending in the longitudinal direction between said apical end (4) and said coronal end (6); - at least one thread (12) extending outward from said central part (2), and - the characteristic volume of the implant, defined by the specified central part (2) or the outer volume (28) of the thread, as defined by the specified thread (12), and for each value of the parameter characteristic of the coordinate in the longitudinal direction of the implant, the cross section of the specified characteristic volume of the implant is characterized by the parameter eccentricity, defined as the ratio of the maximum distance of the contour of this cross section from its center to the minimum distance of the contour of this cross section from its center; while the specified characteristic volume contains: - at least one coronal zone, in which the specified eccentricity parameter has a maximum, constant value, and the specified coronal zone runs along the longitudinal axis of the implant along the length of the coronal zone, constituting at least 10% of the total length of the implant; - at least one apical zone in which said eccentricity parameter has a minimum constant value, and - at least one transition zone located between said coronal zone and said apical zone, in which said eccentricity parameter, as a function of a parameter characteristic of a coordinate in said longitudinal direction, continuously changes in a linear manner from a minimum value near said apical zone to a maximum values adjacent to said coronal zone, said transition zone extending along the longitudinal axis of the implant along a length of the transition zone that is at least 10% of the total length of the implant. 2. Dental implant according to claim 1, characterized in that said apical zone extends along the longitudinal axis of the implant along the length of the apical zone, which is at least 30% of the total length of the implant. 3. Dental implant (1) according to claim 1, characterized in that in said apical zone the cross section of said characteristic volume of the implant has a circular shape. 4. A dental implant (1) according to any one of the preceding claims, characterized in that in said coronal zone and/or in said shaped zone, the cross section of said characteristic volume of the implant has a number of directions in which a radius measuring the distance between the center of the cross section and its outer contour, takes on a maximum value and, therefore, a higher value than in neighboring orientations. 5. Dental implant (1) for insertion into the patient's bone tissue according to claim 4, containing: - a central part (2) having an apical end (4), a coronal end (6) and an outer surface (8) extending in the longitudinal direction between said apical end (4) and said coronal end (6); And - at least one thread (12) extending outward from said central part (2), wherein said central part (2) contains: - the first shaped zone (22) of the central part, and in the first shaped zone (22) of the central part, the cross section of the specified central part (2) has a number of directions in which the radius measuring the distance between the center (50) of the cross section and its outer contour, takes on a maximum value and therefore a higher value than in adjacent orientations, - a circular zone (20) of the central part, and in the circular zone (20) of the central part, the cross section of the specified central part (2) has a circular shape, and - a second shaped zone (26') of the central part, and in the second shaped zone (26') of the central part, the cross section of the specified central part (2) has a number of directions in which the radius measuring the distance between the center (50) of the cross section and its outer contour, takes on a maximum value and, therefore, a higher value than in neighboring orientations, in this case, in the said first shaped zone (22) of the central part, the eccentricity parameter of the central part, defined as the ratio of the maximum cross-sectional radius of the said central part (2) to its minimum radius, is greater than in the said second shaped zone (26') of the central part. 6. A dental implant (1) according to any one of the preceding claims, characterized in that said circular region (20) of the central part, when viewed in said longitudinal direction, is adjacent to said apical end (4). 7. A dental implant (1) for insertion into a patient's bone tissue according to any one of the preceding claims, comprising: - a central part (2) having an apical end (4), a coronal end (6) and an outer surface (8) extending in the longitudinal direction between said apical end (4) and said coronal end (6); And - at least one thread (12) extending outward from said central part (2), said thread (12) defining the outer volume of the thread (28), while said thread (12) contains: - the first shaped zone (30) of the thread, and in the shaped zone (30) of the thread, the outer cross-section of the specified outer volume (28) of the thread has a number of directions in which the radius measuring the distance between the center of the cross-section and its outer contour takes the maximum value and , hence a higher value than in adjacent orientations, - a circular area (32) of the thread next to the specified apical end (4), and in the circular area (32) of the thread, the outer cross-section of the specified outer volume (28) of the thread has a circular shape, and - transition zone (34) of the thread located between the specified figured zone (30) of the thread and the specified circular zone (32) of the thread, and in the transition zone (34) of the thread, the geometry of the outer cross-section of the specified outer volume (28) of the thread as a function of for a coordinate in the specified longitudinal direction, continuously changes from a circular shape next to the specified circular area (32) of the thread to a form in which the outer cross section of the specified outer volume (28) of the thread corresponds to the shape of the outer cross section in the specified figured area (30) of the thread. 8. A dental implant (1) according to any one of the preceding claims, characterized in that for each value of a parameter characteristic of a coordinate in said longitudinal direction, the outer cross section of said outer thread 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. 9. A dental implant (1) according to any one of the preceding claims, characterized in that said shaped zone (22) of the central part and/or said shaped zone (30) of the thread is an area of the platform (24) of the alveolar ridge near the specified coronal end ( 6). 10. A dental implant (1) according to any one of the preceding claims , characterized in that said directions are arranged symmetrically with respect to the central longitudinal axis (64) of said central part (2). 11. Dental implant (1) according to any of the preceding paragraphs, characterized in that the outer contour of the specified external volume (28) of the thread relative to the longitudinal central axis of the specified central part (2) and relative to local maxima or minima corresponds to the outer contour of the specified central part (2 ). 12. A dental implant (1) according to any one of the preceding claims, characterized in that said central part (2) has a tri-oval shape in said formed zone (22) of the central part and/or at least in part of said transition zone (26). cross section. 13. Dental implant (1) according to any one of the preceding claims, characterized in that said central part (2) tapers in said transition zone (26) with a taper angle ranging from 1° to 12°. 14. Dental implant (1) according to any one of the preceding claims, characterized in that said transition zone (26), when viewed in said longitudinal direction, starts at a distance of about 2-4 mm from said apical end (4). 15. Dental implant (1) according to any of the preceding claims, characterized in that said thread (12) is a flat thread. 16. Dental implant (1) according to claim 15, characterized in that the free width (58) of the flat thread, depending on the coordinate parameter in the specified longitudinal direction and starting from the apical end (4) of the specified central part (2), continuously increases with increasing distance from the specified apical end (4). 17. A dental implant (1) according to any one of the preceding claims, characterized in that a series of flutes (46) is provided in at least said transition zone (26). 18. Dental implant (1) according to claim 17, characterized in that the number of said flutes (46) is equal to the number of directions. 19. Dental implant (1) according to any one of the preceding claims, characterized in that said flutes (46) are arranged symmetrically with respect to the central longitudinal axis of said central part (2). 20. Dental implant (1) according to any one of paragraphs. 17-19, characterized in that each flute (46), when viewed in the direction of orientation around the central longitudinal axis of the specified central part (2), is located with a given angular displacement with respect to the adjacent direction. 21. A dental implant (1) according to any one of the preceding claims, characterized in that the central part (2) comprises a channel (10) which is open towards the coronal end (6) and extends in the longitudinal direction of the implant (1) from the coronal end ( 6) to the apical end (4), and the central part (2) has a drive zone, and in the drive zone, the cross section of the channel (10), perpendicular to the longitudinal direction of the implant (1), has radially convex parts located along the circumference of the cross section, with each of the radially most distant points of the radially convex parts is located on a corresponding circle around the center (50) of the cross section, and at least two of these circles have different radii from each other. 22. Dental implant (201) for insertion into the patient's bone tissue, containing: - a central part (205) having an apical end (207) and a coronal end (209), wherein the central part (205) contains a channel (236), which is open towards the coronal end (209) and extends in the longitudinal direction of the implant (201) from the coronal end (209) to the apical end (207), and the central part (205) has a drive zone (242), and in the drive zone (242) the cross section of the channel (236), perpendicular to the longitudinal direction of the implant (201), has radially convex curved parts located around the circumference of the cross section, with each of the radially outermost points of the radially convex portions of the curved shape is located on a corresponding circle around the center of the cross section, at least two of these circles having different radii from each other. 23. Dental implant (201) according to claim 22, characterized in that the central part (205) additionally has a drive part (240), and in the drive part (240) the cross section of the channel (236), perpendicular to the longitudinal direction of the implant (201), has a number of directions in which the radius measuring the distance between the center of the cross section and its outer contour, takes on a maximum value and, therefore, a higher value than in neighboring orientations. 24. Dental implant (201) according to claim 23, characterized in that the drive zone (242) is located in the apical direction from the drive part (240). 25. Dental implant (201) according to claim. 23 or 24, characterized in that the drive part (240) has a conical configuration, such that in the drive part (240) the transverse dimensions of the cross section of the channel (236), perpendicular to the longitudinal direction of the implant (201 ), decrease along the direction from the coronal end (209) to the apical end (207). 26. Dental implant (201) according to any one of paragraphs. 23-25, characterized in that the number of directions is three or more. 27. Dental implant (201) according to any one of paragraphs. 22-26, characterized in that What the points of the radially concave parts radially closest to the center are on the same circle around the center of the cross section. 28. Dental implant (201) according to any one of paragraphs. 22-27, characterized in that the radially convex curved portions comprise first radially convex curved portions and second radially convex curved portions, all radially outermost points of the first radially convex parts of the curved shape are on the same first circle around the center of the cross section, the radially outermost points of the second radially convex portions of the curved shape are on one second circle around the center of the cross section, the second circle has a smaller radius than the first circle, and the first radially convex curved portions and the second radially convex curved portions are alternately disposed around the circumference of the cross section with respective radially concave portions disposed therebetween. 29. Dental implant (201) according to any one of paragraphs. 22-28, characterized in that the central part (205) has an outer surface extending in the longitudinal direction of the implant (201) between the apical end (207) and the coronal end (209), the implant (201) further comprises at least one thread (203) extending outward from the central part (205), the thread (203) has an apical surface facing the apical end (207) of the central part (205) and a coronal surface facing the coronal end (209) of the central part (205), the thread (203) has a groove formed therein, the groove extending from the apical end of the thread (203) to the coronal end of the thread (203), and the thread (203) has in its apical part a recess formed on its coronal surface, the recess extending in the direction from the coronal surface to the apical surface along a part of the thickness of the thread (203), while the recess is open in the direction of the groove. 30. Dental implant (401) for insertion into the patient's bone tissue, containing: a central part (402) having an apical end (404), a coronal end (406) and an outer surface (408) extending in the longitudinal direction of the implant (401) between the apical end (404) and the coronal end (406); And - at least one thread (412) extending outward from the central part (402), while the thread (412) has an apical surface (414) facing the apical end (404) of the central part (402) and a coronal surface (416) facing the coronal end (406) of the central part (402), the thread (412) has a groove (418) formed therein, the groove (418) extending from the apical end of the thread (412) towards the coronal end of the thread (412), and the thread (412) has in its apical part a recess (420) formed on its coronal surface (416), wherein the recess (420) extends in the direction from the coronal surface (416) to the apical surface (414) along part of the thickness of the thread (412) , while the recess (420) is open in the direction of the groove (418) and in the front surface of the groove (418) has a cross section of the segment of the sphere. 31. Dental implant (401) for insertion into the patient's bone tissue, containing: - a central part (402) having an apical end (404), a coronal end (406) and an outer surface (408) extending in the longitudinal direction of the implant (401) between the apical end (404) and the coronal end (406); And - at least one thread (412) extending outward from the central part (402), while the thread (412) has an apical surface (414) facing the apical end (404) of the central part (402) and a coronal surface (416) facing the coronal end (406) of the central part (402), the thread (412) has a groove (418) formed therein, the groove (418) extending from the apical end of the thread (412) towards the coronal end of the thread (412), and the thread (412) has in its apical part a recess (420) formed on its coronal surface (416), wherein the recess (420) extends in the direction from the coronal surface (416) to the apical surface (414) along part of the thickness of the thread (412) , while the recess (420) is open in the direction of the groove (418) and has the shape of a quarter of a sphere. 32. Dental implant (401) according to claim 30 or 31, characterized in that the recess (420) extends in the direction from the coronal surface (416) to the apical surface (414) along 20-90% of the thickness of the thread (412). 33. Dental implant (401) according to any one of paragraphs. 30-32, characterized in that the elongation of the recess (420) in the direction from the coronal surface (416) to the apical surface (414) decreases along the circumferential direction away from the groove (418), in relation to which the recess (420) is open. 34. Dental implant (401) according to any one of paragraphs. 30-33, characterized in that the recess (420) extends in the direction of the width of the recess (420) by 50-90% of the width of the thread (412). 35. Dental implant (401) according to any one of paragraphs. 30-34, characterized in that the recess (420) is formed on the coronal surface (416) of the thread (412) at the most apical point of the full rotation of the thread (412). 36. Dental implant (401) according to any one of paragraphs. 30-35, characterized in that the thread profile angle is 15° or less. 37. Dental implant (1'''') according to any one of the preceding claims, characterized in that - the coronal surface (100) of the implant (1'''') has a wavy contour, with the maxima and minima of the coronal surface (100) located alternately along the perimeter of the coronal end (6) of the implant (1''''), and - at the maxima of the coronal surface (100), the coronal end (6) of the implant (1'''') has a conical configuration, so that the transverse dimensions of the cross section of the coronal end (6) perpendicular to the longitudinal direction of the implant (1'''') are reduced along the direction from the apical end (4) of the implant (1'''') to the coronal end (6) of the implant (1''''). 38. Dental implant (501) according to any one of the preceding claims, characterized in that the central part (502) contains a channel (510) that is open towards the coronal end (506) and extends in the longitudinal direction of the implant (501) from the coronal end (506) to the apical end (504), while the channel (510) contains a conical part (514). 39. Dental implant (501) according to claim 38, characterized in that the conical part (514) is located so as to extend from the coronal end (506) of the implant (501) in the longitudinal direction of the implant (501). 40. Tool (200) for inserting a dental implant dental implant (1, 201, 401) according to any one of paragraphs. 1-36 into the patient's bone tissue. 41. Tool (200) for inserting a dental implant dental implant (1, 201, 401), according to any one of paragraphs. 1-36 into the patient's bone tissue, characterized in that - the tool (200) for insertion contains a proximal part (202) and a distal part (204), and the distal part (204) is designed to interact with the implant (1, 201, 401), and the distal part (204) has a drive section (216), and in the drive section (216) the cross section of the distal part (204), perpendicular to the longitudinal direction of the insertion tool (200), has radially convex parts (218), which are located alternately along the perimeter cross section, wherein each of the radially outermost points (222, 224) of the radially convex parts (218) is located on a corresponding circle around the center of the cross section, and at least two of these circles have different radii from each other. 42. The tool according to claim 41, characterized in that in the drive section (216) the cross section of the distal part (204) perpendicular to the longitudinal direction of the tool (200) in addition to the said radially convex parts (218), has radially concave parts (220) , which together with said radially convex parts (218) are located alternately along the perimeter of the cross section. 43. Tool for insertion (200) according to paragraphs. 40, 41 or 42, characterized in that the distal part (204) additionally has a drive area (214), and in the drive area (214) the cross section of the distal part (204), perpendicular to the longitudinal direction of the insertion tool (200), has a row directions in which the radius, which measures the distance between the center of the cross section and its outer contour, takes on a maximum value and, therefore, a higher value than in adjacent orientations. 44. Insertion tool (200) according to claim 40 or 43, characterized in that the drive region (214) has a conical configuration so that in the drive region (214) the transverse dimensions of the cross section of the distal portion (204) perpendicular to the longitudinal direction of the tool (200) for insertion decrease in the direction from the proximal end of the insertion tool (200) to the distal end of the insertion tool (200). 45. Tool (200) for insertion according to any one of paragraphs. 43 or 44, characterized in that the number of directions is three or more. 46. Tool (200) for insertion according to any one of paragraphs. 40, 41 or 43-45, characterized in that the distal part (204) additionally has a drive section (216), and in the drive section (216) the cross section of the distal part (204), perpendicular to the longitudinal direction of the insertion tool (200), has radially convex curved parts (218) that are located along the perimeter of the cross section, and each of the radially outermost points (222, 224) of the radially convex curved parts (218) is located on a corresponding circle around the center of the cross section, and at least two of these circles have different radii from each other. 47. Tool (200) for inserting according to paragraph 46 as dependent on any of paragraphs. 43 or 45, characterized in that the drive section (216), the holding element (206) and the drive region (214) are located in this order in the direction from the distal end of the insertion tool (200) to the proximal end of the insertion tool (200). 48. The combination of a dental implant (1, 201, 401) according to any one of paragraphs. 1-36 and tool (200) for insertion according to any one of paragraphs. 40-47.

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