Implant drills, especially dental implant drills

Abstract

Implant drill (1), in particular dental implant drill, comprising a mounting area (10) and a machining area (30), wherein the implant drill (1) extends in a longitudinal direction (L), wherein the distal end regions in the longitudinal direction (L) of the implant drill (1) are formed in particular by the mounting area (10) and the machining area (30), wherein the processing area (30) has at least two processing structures (32), wherein the processing area (30) is designed in such a way as to be characterized by the processing structures (32), that it can remove bone material during a positive rotation around the longitudinal direction (L) and that it can compact bone material during a negative rotation around the longitudinal direction (L), wherein the machining area (30) is limited in the longitudinal direction (L) by a stop flange (60), wherein the processing area (30) has different processing sections (B1, B2, B3, B4) along the longitudinal direction (L), wherein the implant drill (1) has at least three processing sections (B1, B2, B3, B4), wherein the machining sections (B1, B2, B3, B4) form different outer contour slope angles (α1, α3) with the longitudinal direction (L) or are cylindrical around the longitudinal direction (L), wherein the implant drill (1), in particular the machining area (30), has a transition machining section (B3), wherein the transition machining section (B3) forms an outer contour slope angle (α3) with the longitudinal direction (L), and wherein the outer contour slope angle (α3) of the transition machining section (B3) is in a range of 7° to 15°.

Description

[0001] The invention relates to an implant drill, in particular a dental implant drill.

[0002] Implants are already known from the prior art. They usually support a prosthesis and are firmly anchored in the surrounding bone. To insert an implant into the bone, a cavity must be created. Depending on the condition of the surrounding bone, a decision must be made whether the cavity is created by drilling or by compaction. In the prior art, these two processes are achieved using different tools: a drill or a set of drills, and one or more compaction tools, such as a chisel. Having multiple tools available can lead to confusion and also increase the workload.

[0003] WO 2020 / 097144 A1 discloses a rotating osteotome. One body of the osteotome has a tapered end with spirally arranged grooves. Furthermore, WO 2021 / 030317 A1 describes a depth stop for a drill tool to create a hole of a predetermined depth.

[0004] US 2018 / 0161124A1 describes a surgical instrument arrangement for forming holes in bone at precise locations and controlled depths. The drill has a front apical tip and a shank. The shank includes an annular groove at a predetermined distance from the apical tip. An adjustable stop gauge is connected to the shank. The stop gauge includes an indexing adapter that telescopically supports a tubular collar.

[0005] It is therefore the object of the present invention to provide a simple and reliable way to create a recess for an implant in a bone, such as a jawbone, in particular of a human.

[0006] This problem is solved with an implant drill according to claim 1. Further features, advantages and embodiments will become apparent from the dependent claims, the description and the figures.

[0007] According to the invention, an implant drill, in particular a dental implant drill, is provided. Advantageously, the implant drill comprises a mounting area and a machining area, wherein the implant drill extends, in particular in or along a longitudinal direction, wherein the distal end areas in the longitudinal direction of the implant drill are formed, in particular by the mounting area and the machining area, wherein the machining area can have at least two machining structures, wherein the machining area, in particular by the machining structures, is designed such that it can remove bone material during positive rotation about the longitudinal direction and that it can compact bone material during negative rotation about the longitudinal direction. The implant drill serves to create a recess or hole in a bone, in particular in the jaw of a person, by means of a rotational movement.This hole serves to accommodate an implant, particularly a dental implant. The implant drill includes a mounting area designed to secure the drill in a machine tool, machining tool, or hand tool. This securing mechanism allows for the transmission of rotary motion, especially a positive locking mechanism, to the implant drill and / or enables the drill to be held in its longitudinal direction, also positive locking. Advantageously, the mounting area of ​​the implant drill incorporates positive locking structures that allow for the positive transmission of torque around the longitudinal direction and / or a holding force along the longitudinal direction. This can be achieved, for example, by a circumferential groove and / or a sectional surface, which can also be described as a flattened area.In addition to the mounting area, the implant drill also has a working area. This working area is specifically the part of the implant drill that comes into direct contact with the bone material during processing, in order to create the recess or hole in the jawbone or bone material. In other words, the working area of ​​the implant drill serves to create the hole. The implant drill extends in a longitudinal direction, which is expediently the direction in which the implant drill rotates during processing. Alternatively, or preferably, the longitudinal direction can also be the direction in which the implant drill has its largest main dimension.Advantageously, one of the distal end regions of the implant drill is formed longitudinally by the mounting area and / or, particularly on the opposite side, by the machining area. The positive longitudinal direction of the machining area is advantageously directed from the mounting area to the machining area or vice versa. Forming the machining area as the distal end region of the implant drill in the longitudinal direction allows for particularly easy machining of the implant drill. Forming a distal end region in the longitudinal direction, particularly on the opposite side, by the mounting area allows for particularly easy mounting of the implant drill in a tool holder, especially a drill, milling cutter, machine tool, or hand tool. The machining area of ​​the implant drill advantageously has at least two machining features.These machining structures are, in particular, those surfaces, edges, or other structures of the machining area that cause bone reshaping and / or bone removal, especially when the drill is rotated. In other words, the planar or linear machining structures can cause reshaping and / or removal of bone material, whereby this machining or shape change can be achieved by rotating the implant drill around its longitudinal axis. The machining area is designed, particularly by the machining structures, such that it can remove bone material during positive rotation around its longitudinal axis and can compact bone material during negative rotation around its longitudinal axis.In other words, the working area of ​​the implant drill can be designed such that when the drill rotates around its longitudinal axis in one direction, bone material is removed, as is the case with a milling cutter or drill bit. However, if the drill rotates in the opposite direction around its longitudinal axis, the working area is designed to compact the bone material being worked, particularly through direct contact of inclined surfaces with the bone material. This design of the implant drill allows for different working options, enabling both bone removal and bone compaction with a single tool. The implant drill is therefore expediently designed to be...The processing area, and in particular the processing structures, are designed such that during positive rotation around the longitudinal direction, they can only remove bone material, and during negative rotation around the longitudinal direction, they can only compact bone material. In other words, the implant drill can be designed such that during rotation around the longitudinal direction, for example, during positive rotation around the longitudinal direction, only bone material is removed, in particular through exclusive contact of geometrically defined cutting edges with the bone material, and that during opposite rotation around the longitudinal direction, only bone-compacting processing structures come into contact with the bone, so that during such rotation, only bone compaction takes place.

[0008] Advantageously, the machining area has at least two, preferably at least three, spiral grooves, wherein the spiral grooves at least partially form and / or delimit the machining structures or some of the machining structures. A spiral groove is understood to be a groove that is spirally formed around the longitudinal direction in the implant drill. The inclusion of a spiral groove allows for a particularly compact design of the machining structure, especially drilling structures. Furthermore, the spiral grooves can also be easily used to provide a receiving space for removed bone material.By providing at least two, preferably at least three, spiral grooves, a high cooling effect can be achieved, and furthermore, this type of design can also achieve a particularly homogeneous intervention characteristic of the processing area with bone material during processing, so that the vibrations occurring during the processing of the bone material by the implant drill can be reduced.

[0009] Advantageously, the spiral groove forms at least part of the machining structures or some of them and / or limits them, particularly in a circumferential direction. This circumferential direction is specifically formed around the longitudinal direction. By utilizing the spiral grooves in such a way that they partially form and / or limit the machining structures, a particularly compact design of the implant drill can be achieved.

[0010] According to the invention, the machining area has different machining sections along the longitudinal direction, wherein the implant drill has at least three machining sections, the machining sections forming different outer contour helix angles with the longitudinal direction, or at least one of the machining sections, preferably all, are cylindrical around the longitudinal direction. An outer contour helix angle is understood to be the angle that a cone has which can just surround the machining section and wherein the axis of rotational symmetry of this cone lies on the longitudinal direction. Advantageously, the outer contour helix angle is constant over the respective machining section. This allows for particularly simple machining or manufacturing of the respective machining section.A cylindrical design around the longitudinal direction of the machining sections means, in particular, that the outer contour of the cone, which surrounds the machining section and whose axis of rotational symmetry lies on the longitudinal direction, can only intersect the longitudinal direction itself at infinity. In other words, the outer contour is not enclosed by a cone but by a cylinder. The advantage of a cylindrical design lies in the fact that it allows for particularly simple manufacturing. The advantage of the different angles of the various machining sections, which can also be referred to as machining sections, lies in the fact that this enables the creation of the implant recess in the bone material without tool changes using the drill. This is especially true due to the different machining sections, or...The implant drill can therefore be designed in such a way that, with the exception of possible pre-drilling, the cavity in the bone for the implant can be created using only this one drill. This eliminates time-consuming tool changes and prevents or at least reduces the risk of tool mix-ups. Advantageously, the implant drill is designed so that machining sections with an external contour angle and machining sections with a cylindrical shape are arranged alternately along the longitudinal direction. Each machining section is advantageously designed (in itself) such that it can remove bone material during positive rotation around the longitudinal direction and compact bone material during negative rotation around the longitudinal direction.In other words, the processing sections may differ from each other solely in terms of their geometric design, but be equivalent in their functionality.

[0011] Advantageously, the implant drill, and in particular its working area, is longitudinally limited by an axial machining section. This axial machining section forms an outer contour angle with the longitudinal direction, wherein the outer contour angle of the axial machining section is in the range of 60° to 87°, and / or wherein the longitudinal length of the axial machining section is in the range of 0.2 mm to 0.4 mm. By providing an axial machining section whose primary function is axial penetration into bone material, a particularly good penetration into the jawbone can be achieved if this section also longitudinally limits the working area.If the axial machining section forms an outer contour angle with the longitudinal direction that lies in the range of 60° to 87°, this allows for particularly fast yet effective axial penetration of the implant drill into the bone material. If the length of the axial machining section in the longitudinal direction is in the range of 0.2 mm to 0.4 mm, this allows for a particularly compact design of the axial machining section, resulting in a particularly easy-to-handle implant drill. This can be crucial, especially for dental implant drills, as the handling area for a drill is particularly limited in the dental field.

[0012] Advantageously, the implant drill, and in particular its working area, has a main working section, wherein the main working section forms an outer contour angle with the longitudinal direction, the outer contour angle of the main working section being in the range of 0.2° to 9°, or wherein the main working section is cylindrical around the longitudinal direction. The main working section is, in particular, the working section of the implant drill that has the greatest or longest longitudinal length. The main working section primarily serves to ensure the final shaping of the implant receiving hole or bone recess to be created by the implant drill. Therefore, the main working section preferably forms a distal end of the bone recess.If the main machining section forms an outer contour slope angle with the longitudinal direction, preferably in the range of 0.2° to 9°, this allows for particularly easy and reliable assembly, especially of self-tapping implants, or additionally or alternatively, preferably dental implants. However, if the main machining section is cylindrical around the longitudinal direction, this allows for particularly simple manufacturing of the drill and, moreover, ensures good retention force for the implant in the bone.

[0013] Advantageously, the implant drill, particularly the machining area, and especially preferably the main machining section, has circumferential cooling grooves, which in particular form closed rings around the longitudinal direction. The provision of grooves or cooling grooves increases the available surface area and also reduces the cutting surface of the machining structures, especially the drilling structures, with both of these effects contributing to cooling. Providing sufficient cooling is fundamentally important to prevent overheating-related trauma to the bone material being machined. The cooling grooves extend in closed rings around the longitudinal direction. A closed ring is understood to mean that the cooling grooves or...The imaginary extension of the cooling grooves is closed in itself and advantageously circular. In other words, the cooling groove can be interrupted along its path, for example, by spiral grooves or machining features, but the cooling groove continues behind this interruption, and at least the cooling groove path, in conjunction with the imaginary path, forms a closed structure, in particular a circular one. The closed rings of the cooling groove allow for particularly simple and fast manufacturing. Advantageously, the plane of extension of these closed rings lies perpendicular to the longitudinal direction. This further simplifies the manufacturing of the cooling grooves.Alternatively or additionally, preferably, the center point around which the cooling groove or grooves are formed can lie on the longitudinal direction in order to achieve fast, easy and precise manufacturing.

[0014] Advantageously, the implant drill, and in particular the machining area, has a cylindrical machining section, wherein the cylindrical machining section is cylindrical around its longitudinal axis. Advantageously, the cylindrical machining section is formed longitudinally between the axial machining section and the main machining section. It is particularly advantageous if the cylindrical machining section is formed longitudinally adjacent to the axial machining section. The cylindrical design of the cylindrical machining section allows for particularly good radial guidance of the drill. This guiding effect of the cylindrical machining section can be increased by arranging the cylindrical machining section longitudinally directly adjacent to the axial machining section and / or at least longitudinally between the axial machining section and the main machining section.

[0015] According to the invention, the implant drill, and in particular the machining area, has a transition machining section, wherein the transition machining section forms an outer contour helix angle with the longitudinal direction, the outer contour helix angle of the transition section being in particular in the range of 7° to 15°. By providing a transition machining section, a simple and easily manufactured increase in the diameter of the machining area can be achieved in a particularly straightforward manner. The transition machining section is located in the longitudinal direction, in particular between the axial machining section and the main machining section. Advantageously, the transition machining section forms that part of the machining area which is formed in the longitudinal direction between the cylindrical machining section and the main machining section.By forming the transition machining section with an outer contour slope angle in a range of 7° to 15°, particularly low heat generation can be achieved during the machining of the bone material, so that overheating-related bone trauma can be avoided or at least reduced.

[0016] Advantageously, the ratio of the diameter of the cylinder machining section to the diameter of the main machining section is in the range of 0.5 to 0.9, preferably in the range of 0.72 to 0.82. The diameter of the cylinder machining section is the diameter of the cylinder directly surrounding the cylinder machining section, wherein this imaginary cylinder has an axis of rotational symmetry that is coincident with the longitudinal direction. In other words, the diameter of the cylinder machining section is the diameter of the circle that can directly surround the cylinder machining section or the main machining section in a cutting plane perpendicular to the longitudinal direction, and wherein the center of this circle lies on the longitudinal direction. This smallest possible circle in the cutting plane is, in the context of the invention, also referred to as an envelope.A ratio in the range of 0.5 to 0.9 allows for particularly simple manufacturing of the implant drill. However, if the ratio is in the range of 0.72 to 0.82, this results in particularly good guidance through the cylinder machining section.

[0017] Advantageously, the ratio of the longitudinal length of the cylindrical machining section to the longitudinal length of the main machining section is in the range of 0.1 to 0.4, preferably in the range of 0.2 to 0.3. With a ratio in the range of 0.1 to 0.4, particularly good guidance of the cylindrical machining section can be provided – even in the case of bone material compaction. However, if the ratio is in the range of 0.2 to 0.3, the applicant has surprisingly discovered that this creates a recess which can achieve particularly good implant durability.

[0018] Advantageously, the machining area has at least one compaction machining structure and one drilling machining structure. A drilling machining structure is specifically a machining structure that has a geometrically defined cutting edge. This geometrically defined cutting edge serves, in particular, to achieve machining of bone material by chip removal. Such a drilling machining structure can be achieved, for example, by an undercut between two contacting (boundary) surfaces. In other words, the drilling machining structure can be, in particular, the cutting edge of two intersecting surfaces, which can, in particular, form an undercut with each other.A compaction machining structure is, in particular, a structure designed for processing bone, which can be formed, for example, by a trailing surface that can exert pressure on the bone to displace it, especially in the direction normal to the wall of the hole to be created, and thus achieve compaction of the bone material. For example, such a compaction machining structure can be achieved by a freeform surface or a free area designed in such a way that, through rotation, it causes bone compaction or locally pushes or displaces bone material adhering to the surface outwards. This can be achieved, for example, by the freeform surface or free area forming an angle and thereby displacing the bone material outwards. In particular, this freeform surface or free area can be...The clearance surface should be designed as a surface that rises in the direction of rotation. This design, particularly during negative rotation around the longitudinal direction, ensures that the clearance surface increases in distance from the axis of rotation or the longitudinal direction. In other words, this clearance surface, or freeform surface, can be designed without undercuts, so that it does not cause bone material to be removed during rotation, especially during negative rotation around the longitudinal direction. By incorporating different machining structures, namely compaction and drilling structures, the machining area and its structures can be easily produced, achieving both compaction and bone removal.

[0019] Advantageously, at least one compaction processing structure, preferably all compaction processing structures, is formed by a free surface and / or the compaction processing structure(s) form an angle in a range of 10° to 45°, preferably in a range of 12° to 40°, with a tangent in a cutting plane perpendicular to the longitudinal direction. The relevant tangent is the tangent to the envelope of the processing area at which the (even if imaginary) extended course of the compaction processing structure intersects the envelope of the processing area of ​​the implant drill. The envelope of the implant drill or the processing area is the smallest possible circle whose center lies on the longitudinal direction and which can just encircle the implant drill or the processing area in the cutting plane.In other words, the enclosing element can also be formed by a circle lying in a cutting plane perpendicular to the longitudinal direction, where the circle is precisely the smallest possible circle that can enclose the processing area in the cutting plane. If the angle of the compaction processing structure is in the range of 10° to 45°, a particularly easy-to-manufacture compaction processing structure can be achieved. However, if the angle is in the range of 12° to 40°, a particularly good bone compaction capability can be achieved, which nevertheless prevents overheating of the bone material during compaction and / or at least significantly reduces the probability of this occurring.

[0020] Advantageously, the compaction processing structure is designed to be free of undercuts from directly adjacent structures, particularly in a cutting plane perpendicular to the longitudinal direction. This undercut-free design with adjacent structures prevents, in particular, the separation of bone material during rotation around the longitudinal direction by the compaction processing structure(s).

[0021] Advantageously, the angle of the compaction processing structure is variable along its longitudinal path. In other words, the angle formed by the compaction processing structure can differ in different cutting planes along the longitudinal direction. This allows the compaction effect of the compaction processing structure to be adapted to the outer diameter of the drill bit. This is particularly advantageous because different diameters require different angles of attack for bone compaction. However, it is expedient that the angle of the compaction processing structure along its longitudinal path remains constant in the respective processing sections. This simplifies the manufacturing of the drill bit. In other words, the angle can be constant, for example, in the main processing section and / or in each individual processing section.However, the angle can change at the transition from one processing section to the next, so that it is not constant "global" but variable, especially along the longitudinal direction.

[0022] Advantageously, the angle of the compaction machining structure, preferably of all compaction machining structures, lies in the axial machining section and / or in the cylindrical machining section in a range of 12° to 18°. This allows for a particularly good compaction effect with small drill diameters, while still preventing or at least significantly reducing overheating of the bone material.

[0023] Advantageously, the angle of the compaction machining structure, preferably of all compaction machining structures, lies in the range of 30° to 40° in the main machining section and / or in the transition machining section. Especially with large machining surfaces or machining structures that primarily do not result in axial machining, an angle in the range of 30° to 40°, particularly preferably in the range of 33° to 37°, has a particularly good compaction effect, while at the same time bone overheating can be avoided and / or at least reduced.

[0024] Advantageously, the angle of the compaction machining structure, preferably of all compaction machining structures, is predominantly constant. "Predominantly constant" means that the angle is only varied in small sections along the longitudinal direction. In other words, while the angle of the compaction machining structure may be variable along the longitudinal direction, the sum of the constant sections constitutes 70%, preferably at least 80%, and particularly preferably at least 90% of the longitudinal length of the compaction machining structure in order to be considered predominantly constant within the meaning of the invention. For example, except for a sharp transition, the angle can assume a first value in the axial machining section and / or in the cylindrical machining section and a second value in the main machining section and / or in the transition machining section.These different angular ranges are specifically delimited by a sharp transition region, or this sharp transition region itself exhibits a variable angle. Preferably, the sharp transition region can be formed as an edge, resulting in an abrupt transition. Alternatively, and more preferably, the transition region can extend longitudinally over a length range of 0.01 to 0.4 mm, preferably over a range of 0.02 to 0.1 mm. In other words, the angle can be constant section by section, except for the transition region.

[0025] Preferably, the spiral flutes, and preferably all spiral flutes, are circumferentially bounded by a compaction machining structure and / or by a drilling machining structure and / or by a transition chamfer. In other words, the spiral flute, particularly circumferentially around the longitudinal direction in the positive and / or negative circumferential direction, can be bounded by a compaction machining structure, a drilling machining structure, and / or a transition chamfer. This allows for a small implant drill size. A transition chamfer is a short chamfer, particularly with an edge length in the range of 0.02 to 0.1 mm, which provides a transition to a compaction machining structure. This transition chamfer, in particular, prevents undercutting, thus ensuring that the compaction machining structure and the surrounding area do not have a bone-removing effect.

[0026] Advantageously, at least one spiral groove, preferably all spiral grooves, extends through the main machining section, the transition machining section, the cylindrical machining section, and / or the axial machining section. By forming the spiral groove such that it runs longitudinally through several machining sections, in particular all machining sections, and / or extends into these areas, particularly simple manufacturing of the implant drill can be achieved. If the spiral groove extends through or into all areas of the machining section, a particularly good possibility can be created for the drill to reliably create all areas of the hole or implant recess not only during machining but also during compaction machining, while the spiral groove can simultaneously provide a cooling effect for the bone material.

[0027] The working area is limited longitudinally by a stop flange, which in particular runs around the entire circumference. This ensures that the implant drill cannot penetrate too deeply into the bone material. Therefore, such a stop flange increases the safety of the implant drill.

[0028] The implant drill is preferably made of titanium or a titanium alloy. Using titanium allows for particularly good stability and high mechanical strength, thus increasing the drill's safety and extending its service life.

[0029] The implant drill is expediently designed as a single piece. "Single piece" in this context means that the main component is essentially manufactured from a single body created in a single forming process. In other words, a single-piece design is no longer present when various components must be joined to create a base body or blank from which the implant drill is then produced. The single-piece design of the implant drill allows for particularly high drill strength, making it especially advantageous under dynamic and / or fluctuating loads.

[0030] Further advantages and features of the present invention will become apparent from the following description with reference to the figures. Individual features of the illustrated embodiments can also be used in other embodiments, unless this has been expressly excluded. The figures show: Fig. 1. A side view of an implant drill; Fig. 2 a detailed view of an implant drill in the area of ​​the machining area; Fig. 3 a section through a processing area of ​​the implant drill; Fig. 4. another cut through the working area of ​​an implant drill; Fig. 5 an isometric view of an implant drill; Fig. 6 an implant drill blank in a side view; Fig. 7 an axial view of an implant drill; and Fig. 8 A schematic view of a section of a machining area of ​​the implant drill with an envelope.

[0031] In the Fig. Figure 1 shows a side view of an implant drill 1. The distal ends in the longitudinal direction L of the implant drill 1 are formed by the mounting area 10 and by the machining area 30. In the axial direction, i.e., in the longitudinal direction L, the machining area 30 is bounded by the axial machining section B1 and by the stop flange 60. The machining area 30 can be divided into four sections, or is formed by these sections, which are arranged side by side in the longitudinal direction. These machining sections are the axial machining section B1, the cylindrical machining section B2, the transition machining section B3, and the main machining section B4.The machining area 30 has a plurality of spiral grooves 34, which extend spirally around the longitudinal direction L and from the axial machining section B1, via the cylindrical machining section B2, via the transition machining section B3, and into the main machining section B4. To achieve particularly good cooling during bone machining, the main machining section B4 has a plurality of cooling grooves 36, which are arranged in a ring around the longitudinal direction L. To secure the implant drill 1 in a drill or hand tool, the mounting area 10 has a flattened section and a circumferential groove, thus enabling a positive-locking torque transmission around the longitudinal direction to the implant drill 1 and a positive-locking axial force transmission in the direction of the longitudinal direction L.The main machining section B4 can extend up to the stop flange 60 in the longitudinal direction L.

[0032] In the Fig. Figure 2 shows a detailed view of an editing area 30. The one in the Fig. The processing area 30 shown in section 2 can in particular be used for the processing area shown in the Fig. The processing area shown in section 1 corresponds to 30. Fig. Figure 2 shows two cutting planes marked with arrows, labeled A and B. Possible configurations of these cutting planes can be found for cutting plane AA in the... Fig. 3 and BB in the Fig. 4. The machining area 30 has a plurality of spiral grooves 34. These spiral grooves 34 are circumferentially bounded around the longitudinal direction L by machining structures 32. On one side circumferentially, the spiral groove 34 is bounded by drilling machining structures 52, and on the opposite circumferential side by compaction machining structures 50. The compaction machining structures 50 can, however, be spaced from the spiral groove 34 by a transition chamfer 54. In other words, a short transition chamfer 54 can be provided at the outlet side of the spiral groove 34, into which the compaction machining structure 50 then connects circumferentially. The axial runout of the spiral groove 34 is located in the main machining section B4 in the longitudinal direction L.

[0033] In the Fig. 3 is a possible sectional view of the [unclear] in the Fig. 2, section plane marked AA, is shown. As the Fig. The implant drill 1, which can be removed from the 3, has three circumferentially arranged spiral grooves 34. At their outer intersection with the outer surface, the spiral grooves 34 are designed to form either a compaction machining structure 50 or a drilling machining structure 52. These two types of machining structures 32 serve to create a recess or a bore in bone material, thus enabling the placement of an implant within this bone material.

[0034] In the Fig. 4 is one possible design of the in the Fig. Section 2 is shown with BB. Section BB preferably runs through the main machining section B4. In the main machining section B4, the spiral grooves 34 are also bounded circumferentially around the longitudinal direction L by drilling machining structures 32 and / or compaction machining structures 40 and / or transition phases 54. In other words, the distal end regions of the spiral groove 34 can form the machining structures 32 and / or a transition phase 54.

[0035] In the Fig. Figure 5 shows an explanatory isometric view of an implant drill 1. In the Fig. Figure 5 shows the flattened torque transmission surface in the mounting area 10 of the implant drill 1 particularly well. As the Fig. 5 can be removed, the spiral grooves 34 extend from an axial end in the longitudinal direction L of the machining area 30 over large parts of the machining area 30.

[0036] In the Fig. Figure 6 shows a blank or semi-finished product of an implant drill 1. Explanatory details are provided in the Fig. Figure 6 shows the outer contour slope angle α1 of the axial machining section B1 and the outer contour slope angle α3 of the transition machining section B3. In the Fig. No spiral grooves 34 are incorporated into the implant drill 1 or the implant drill blank shown in Figure 6, so that the implant drill 1 or the implant drill blank - as shown in the Fig. 6 is shown - without processing structures 32 is formed. However, how the Fig. As can be seen from Figure 6, the cooling grooves 36 are already incorporated into the machining section 30 of the blank, which are formed in closed rings around the longitudinal direction L. As the Fig. 6 - compared to the Fig. 1 - as can be seen, the cylinder machining section B2 and the main machining section B4 are cylindrical around the longitudinal direction L. In principle, the one in the Fig. The 6 shown implant drills 1 or the implant drill blank can be used to insert the implant into the Fig. 1, Fig. 2, Fig. 3, Fig. 4, Fig. 5 or Fig. 7 as well as, in principle, the one in the Fig. The embodiment shown in section 8 can serve as the starting workpiece. In other words, the blank can be used according to the Fig. 6 an implant drill according to the Fig. They will be trained in grades 1 to 5 and 7 to 8.

[0037] In the Fig. Figure 7 shows a view of an implant drill 1 in the longitudinal direction L. The positive longitudinal direction L can point from the mounting area 10 to the machining area 30 or from the machining area 30 to the mounting area 10. Advantageously, the implant drill 1 is designed such that it achieves a drilling operation when rotated clockwise and a compacting operation when rotated counterclockwise. Such a design can be achieved, for example, by the [missing information] in the Fig. The design shown in section 7 can be achieved.

[0038] In the Fig. Figure 8 shows a basic, albeit schematic, illustration to demonstrate the design of a compaction processing structure 50. In the Fig.Figure 8 shows a section plane perpendicular to the longitudinal direction L, which is located within the machining area 30. A spiral groove 34 is provided in the implant drill 1, penetrating the section plane in the longitudinal direction L. This groove is bounded circumferentially counterclockwise by a drilling machining structure 52. A transition chamfer 54 adjoins the spiral groove 34 in the circumferential direction, followed clockwise in the circumferential direction by a compaction machining structure 50. The machining area 30 is enclosed by the envelope 70, the center point of which lies on the longitudinal direction L. The (at least imaginary) course of the compaction machining structure 50 intersects the envelope 70 in the depicted section plane. The tangent 72 drawn at this intersection point with the envelope 70 forms an angle W1 with the compaction machining structure 50.the imagined course of the compaction processing structure 50. Reference symbol list: 1 implant drill 10 Assembly area 30 processing area 32 processing structures 34 spiral groove 36 Cooling groove 50 compaction processing structure 52 Drilling machining structure 54 Transition phase 60 Stop flange 70 Enveloping 72 Tangent B1 Axial machining section B2 Cylinder machining section B3 Transition Processing Section B4 Main processing section L Longitudinal direction W1 Angle of the compaction processing structure α1 Outer contour slope angle of the axial machining section α3 Outer contour slope angle of the transition machining section

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