JP5449292B2 - 2-part dental implant - Google Patents

Description

  The present invention relates to a two-part dental implant. The distal implant portion is configured as an artificial root for implantation in the jawbone and the proximal implant portion holds an artificial crown.

  The present invention relates in particular to the connection between the distal and proximal implant parts, hereinafter also referred to as the implant-abutment-bond and schematically shown in IAV. The proximal end of the distal implant portion and the distal end of the proximal implant portion are configured to geometrically match each other and with the shaft implanted therein Touch the boundary.

  Dental implants are used to replace lost teeth. In dental implants, a distinction is made between single systems and two-part systems. The present invention relates to a two-part system. Such a two-part system has distal and proximal implant portions. The distal implant portion is inserted into the jawbone where it merges with the bone. The proximal implant part—also called an abutment—projects into the oral cavity several millimeters and forms an artificial stump. The proximal implant portion receives various forms of replacement teeth, such as the annulus, and couples it to the jaw via the distal implant portion.

  The distal implant portion and the proximal implant portion are typically joined together in the longitudinal direction by a longitudinally extending screw pin. The geometric shape of the coupling region between the distal and proximal implant portions is selected such that the coupling between both implant portions is a shape and / or a frictional connection.

  The most important requirements for the bond between the distal and proximal implant parts are as follows. That is, the joint must be stable because it is exposed to a very high bite force. The mating part must be machined very accurately and cannot have a gap when joined. The superstructure should be separated from the implant at any time so that it can be reconnected. Both implant parts must be rigid and free of play in the combined state and ensure that they do not pivot about the implant axis. This is of particular importance when it is desired to receive a structure in which a plurality of implants are inserted into the jaw and the individual implants are fully connected, for example a screwed immobile implant bridge. Only by using accurate anti-rotation, such ingrowth structures can be manufactured with an exact fit. For example, rotation prevention can be omitted when a plurality of implant superstructures are joined together, as in the case of a subweb structure that normally holds a removable denture. In addition to the requirements already mentioned, other requirements are imposed on the web building structure provided for this use. The web superstructure can be mounted on and coupled to the implant without any problem even if the superstructures connected to each other are not normally inserted into the bone parallel to each other. It must give a possibility.

  Known two-part dental implants do not meet the above requirements as desired. A particular problem with many known bipartite implants is the transition between both implant parts. For example, the solutions disclosed in EP0842643, US5919043, EP1371342 or US6152737 are not satisfactory.

EP0842643 US5919043 EP13731342 US61521737

  The object of the present invention is to provide a two-part dental implant which is improved with respect to the above-mentioned requirements.

  According to the present invention, the problem is that the mutually facing surfaces extend transversely to and parallel to the longitudinal axis of the dental implant and the distal partial shaft is proximal to the distal partial shaft. A longitudinal opening open towards the end, the longitudinal opening having an inner wall having a basic geometry with a circular cross section, and a V-shaped distal partial shaft of the inner wall A basic geometry provided with a recess open towards the proximal end, the building part shaft having a circular cross section at its distal end that fits into the longitudinal opening of the distal part shaft It has been solved by having an outer wall with a geometric shape.

  Advantageously, the distal and proximal implant parts have stop surfaces facing each other, the stop surfaces abutting each other after the dental implant has been assembled. The stopper surfaces facing each other limit the degree of proximity of both surfaces facing each other of the implant part with the sealing body between them, and the stopper surface defines the minimum distance between both surfaces of the implant parts facing each other This limits the maximum compression of the seal body. It is ensured that axial forces acting on the implant in this way, for example occlusal forces, are not absorbed by the sealing body but are transmitted by the stopper surfaces facing each other.

  In an advantageous variant of the sealing body, the sealing body has a sealing surface made of an elastic material, and when the distal and proximal implant parts are joined together, the distal and proximal sides The sealing surface is brought into close contact with the surface provided for the sealing body. The seal and the proximal and distal implant portions correspond to the seal surface of the seal body and both implant portions after the final bond is formed between the distal and proximal implant portions. Even if an occlusal force acts on the implant and a transition region from the proximal side to the distal implant portion is elastically deformed based on the occlusal force, the above surface pressure is generated. Is formed to be maintained.

  Therefore, according to the present invention, a seal body is provided as a seal between two end faces facing each other in the assembled state of the two-divided shaft and being outside in the radial direction of the shaft. The seal body is dimensioned so that it is not compressed in the axial direction of the shaft when loaded in the axial direction of the dental implant, but is always compressed to a minimum when loaded laterally. Thus, the seal is compressed to the extent necessary to join the implant, so that the implant-to-base-bonding guarantees a seal under all possible conditions. The degree of compression is related to the material and to the thickness of the material. It is believed that increasing the seal height may reduce the possibility of material compression to compensate for motion in the seal area.

  In order to attach the seal body, a seal body holding body is preferably provided, and this seal body holding body is used as a positioning body positioning means, and since the seal body can already be mounted by the seal body manufacturer, The dentist who finally installs the implant can easily install the seal body using the seal body holder.

  Experiments described in detail below have demonstrated that a seal having a seal body made of a rigid material does not guarantee the desired sealability.

  The examined implant is rigidly clamped to the holding device up to the level of the implant shoulder (proximal end of the distal implant part).

  A proximal implant portion was screwed onto the distal implant portion with a defined attachment force using a screw pin.

  A force of 100 N is applied to the proximal end face of the proximal implant part at an angle of 30 ° to the longitudinal axis of the implant, thereby inducing elastic (reversible) material deformation in the joined implant components It was done.

Obtained measurement results;
The following changes were observed during the application of force in the areas of both surfaces of both implant parts facing each other;
On the side on which the force acts, the nominal dimension (defined gap) provided for the seal increased by a value ≧ 1 μm.

  On the opposite side of the force action, the degree of the nominal dimension (defined gap) provided for the seal was reduced by the value ≧ 50 μm in the same time period.

  The experiment was conducted using titanium alloy (Ti6Al4V) and ceramic (ZrO2) as materials.

  This measurement supported the perception that the present invention is based, ie, that a rigid or plastically deformable seal does not prevent bacteria from entering this area.

  Seals based on the principle of permanent deformation of the sealing body only work in the case of a connection in which no force is applied to the components.

  Dental implants are used to replace lost occlusal mechanisms, absorb forces, so-called occlusal forces, and are permanently exposed to this occlusal force. Already a slight external axial force and a force that exceeds the mounting force of the screw connection creates a gap that cannot be closed again when a rigid or ductile seal is used. Therefore, this bond is not bacterially dense.

  The force required for the surface pressure between the seal body and each implant part can be generated in two ways. For one thing, if the type of coupling—for example, axial thread coupling—and the type and arrangement of the seals are properly selected, the seal body will allow for the coupling of the proximal and distal implant portions. It can be elastically compressed between both implant parts. In this case, an arrangement in which the sealing body has the shape of a disc with a central through-opening and is arranged between the two radially extending surfaces of the distal and proximal implant parts is advantageous. It is.

  On the other hand, the seal can also have a seal body that expands after the bond between the distal side and the proximal side is formed. Such an arrangement provides a short, sometimes distal, intermediate chamber that needs to be filled with a seal between the proximal and distal implant parts with the surfaces of both implant parts facing radially. This is best achieved by filling with a sealing body having a tube shape that tapers towards the end on the side. Advantageously, the sealing body has the elastic properties already described or is inserted into the proximal or distal implant part in a contracted state, for example by cooling, and then each other implant part is first It is coupled with the implant part and then the seal body expands, for example on the basis of heating. The same principle can also be used for seals in which the seal body has the shape of a disc with a central through opening.

  Suitable materials for the sealing body are biocompatible plastics, in particular elastomers or duromas. This also includes a particularly suitable mixture of rubber and PTFE. This mixture preferably contains carbon black as filler. Also, thermoplastic elastomers and elastomer alloys (eg, polypropylene from the group of polyolefins), thermoplastics (eg, Perfluoroelastomere (PTFE, FKM, FFKM, FFPM) and polyetheretherketone (PEEK)) and duroplast (Amino- or Phenolplast) or silicon is targeted as an elastic plastic for the sealing body. Of these elastomers, FFKM containing PTFE as a base material is particularly suitable as silicic acid as a filler. The black coloration of the elastomer is achieved with carbon black and the white coloration with titanium dioxide or value sulfate. Already silicic acid can provide sufficient white coloration.

  Particularly suitable are seal bodies made mostly of elastomers. This sealing body is coated with thermoplast or duroma on the outside and with PTFE. In this case, the elastomer maintains the stress continuously, and PTFE has oral stability and seals continuously.

Another coating material is Diapralylen, also known as Dimer, eg, Parylene, which can be applied to the surface to be coated by the plasma coating process. A suitable layer thickness is between 0.5 and 50 μm. Particularly suitable are layer thicknesses between 1 and 5 μm, for example 3 μm. In the following, the structural form of such a coating material is shown as an example;

  The surface of the Parylene coating layer can additionally be provided with a nano-coating consisting of a metal, such as titanium or silver—even in combination with a ceramic. This coating has a neutral aspect to cellular tissue as well as bacterial seal.

  The coated surface is advantageously poled in order to increase the adhesion for the coating layer. Such polarization of the surface can be carried out using the plasma method in a manner known in principle.

  It is also advantageous to polarize the surface of the implant or its constituent parts, in particular the surface facing away from the sealing body, to increase the resistance of the object. Polarization prevents bordering tissues, such as bone and gingiva, from rejecting or not rejecting the covering layer.

  For seal bodies that are partially coated in some cases, it is significant that the coated surface does not have sharp edges. Rather, it is desired that all coated edges are rounded so that tearing of the coating layer is avoided when the seal body is deformed.

  It is advantageous that the elastic material of the sealing body is elastically expandable or compressible by at least 5%, better 20% or more. In one embodiment, for example, the spacing provided by the stopper surface between the mutually facing surfaces of both implant parts is 250 μm and the seal has a nominal dimension of 250 μm. In this case, the seal body is made larger than the nominal size (250 μm) of the seal by, for example, 50 μm, and it is desired that compression (20% compression) of 50 μm already occurs after assembly. This size is the ideal dimension desired. The constructed height of the seal is as small as possible, and for aesthetic reasons it is desired not to give the constructed height for the later crown. In particular, nominal dimensions are between 0.1 mm and 3 mm. For sizing, the seal can only be deformed in the elastically deformable region of the seal, even under the action of an occlusal force, and in a partial region, for example, always compressed to the smallest dimension when subjected to lateral loads. It is important to stay. This ensures that the seal body is compressed only as much as necessary when joining the implants, ensuring a seal in all situations where implant-abutment-bonding is possible. The degree of compression is related to material and material thickness. If the seal height is large, the compressibility of the material is minimal to compensate for motion in the seal area.

  For sealing bodies that expand under temperature, plastics with a thermal expansion coefficient greater than 75 × 10 −6 / K at 20 ° C. are advantageous.

  It is advantageous that at least one outer surface of the sealing body forming the outer surface of the implant is coated in the manner described above with a metal or ceramic layer. In this case, the metal, Parylene or ceramic layer prevents bacteria from entering the seal component covered with the metal or ceramic layer. Particularly suitable is, for example, nano-coating using titanium particles. The sealing surface itself can consist of a directly biocompatible plastic or can be coated in the manner described above. Particularly suitable materials for the metal layer are titanium, silver or gold, possibly in the form of alloy components. All surface materials of the seal are oral resistant and antibacterial and do not absorb water or absorb very little.

  In addition to elastic plastic, the sealing body can include individual plastic elements made of metal springs or other plastics, for example PEEK. The spring element can for example have the shape of a disc spring or ring with a U-shaped inwardly open cross section, ensuring a continuous elasticity and stress of the sealing body. Metal springs are particularly advantageous in the case of sealing bodies in which the elastic plastic is at least partly made of polytetrafluoroethylene (PTFE, Teflon, polypropylene (PP) or polyetheretherketone (PEEK)). .

  The present invention is based on the recognition that a bipartite dental implant does not have a microgap in the region of the bone protrusion. This is because there is an implant-abutment-joint (IAV) in the region, that is, a joint between the proximal and distal implant parts. This bond is the cause of the microgap, which is the subject of the discussion at this point. As long as the implant-abutment-bond is precisely located at the bone height, it is known that the bone absorbs about 0.5 mm below the implant-abutment-bond. This was evidenced by inflammation of the tissue (gingiva and bone) adjacent to the implant-abutment-connection. In particular, proof is done with polynuclear leukocytes, which are preferred in the process induced by bacteria. As the cause of this phenomenon, the incompatibility of IAV and the contamination of IAV by bacteria are discussed.

  The result of a bone defect is a gingival recession with the result of a longer tooth (implant crown). In areas that are aesthetically demanding, such as the anterior tooth area, bone loss is a major problem.

  The sealing body preferably has the shape of a ring and is arranged between two stop faces which run perpendicular to the longitudinal axis of each implant part and serves for a bacteria-tight seal. Such a seal body or seal preferably consists of a plastic material having a greater elasticity or lower hardness than the material of both implant parts. Both implant parts are preferably made of metal, ceramic or plastic that the human body can withstand.

  In an advantageous embodiment of the two-part dental implant, the surfaces of both implant parts facing each other, between which the sealing bodies are arranged, are transverse to the longitudinal axis of the dental implant, ie radially and parallel to each other It extends to. Such a surface is particularly suitable for interposing a sealing body in the form of a disc having a central through opening. The central through-opening allows the proximal and distal sides and the implant portion to be joined using screw pins that extend in the axial direction of the implant. The screw pins also help to sufficiently compress the seal body and achieve the desired surface pressure between the sealing surface and the surface of the implant. In this case, the surface pressure is limited by the stopper surfaces that are in contact with each other. For certain applications, it is advantageous if the sealing body is thicker in the outer edge area than in the central area of the seal. In this manner, the seal body is such that when the proximal and distal implant portions are joined at its edge region, the seal surface of the seal body will contact the surfaces of both implants accurately. Transformed into However, in alternative embodiments, the sealing bodies can have sealing surfaces extending parallel to each other or can be configured in the form of O-rings.

  The geometry of the proximal and distal partial shafts is preferably at the transition between both shaft parts, advantageously the coupling between both shaft parts causes the occlusal force to partly move from the partial shafts. It is configured not only to transmit directly to the shaft but also to prevent rotation.

  According to an advantageous variant embodiment, the distal part shaft forming the distal implant part has a longitudinal opening which opens towards its proximal end. The inner wall of the longitudinal opening has a geometric shape with a circular cross section and is V-shaped, extending at least approximately in the longitudinal direction of the partial shaft and opening toward the proximal end of the partial shaft Has been inserted. The superstructure part shaft forming the proximal implant part was provided with a basic geometry at the distal end with a circular cross-section that matched the longitudinal opening of the distal part shaft. It has an outer wall.

  Advantageously, the outer wall of the superstructure shaft has a V-shaped projection at its distal end. This protrusion is adapted to the V-shaped recess of the distal partial shaft and cooperates with the side section of the V-shaped recess of the distal partial shaft so that the V-shaped protrusion of the superstructured structural shaft is It is pushed into the V-shaped recess of the distal partial shaft like a wedge. This indentation causes the two sides of the V-shaped projection and the two sides of the V-shaped recess to contact each other, and in this manner the relative position of the distal partial shaft and the superstructure partial shaft is determined in the axial direction. Both in the rotational direction and in the direction of rotation, the distal part shaft and the superstructure part shaft are connected to each other or are connected until they are fixed without play. The side surfaces that are in contact with each other form a defined height stopper as a stopper surface. The height stop is indicated by the defined geometric shape of the implant part itself. As a result, the force acting on the proximal implant portion (proximal partial shaft) from above is transmitted only to the distal implant portion (distal partial shaft). If the acting force is derived through the seal rather than through the described height stopper, the seal is considered to be broken during the period of use.

  In this case, the configuration of the distal partial shaft can receive a superstructure partial shaft that does not have a V-shaped projection, while the partial shafts coupled together are most accurately fixed in the axial direction. However, it is not fixed in the direction of rotation. This is particularly advantageous when the shaft is used for fixing the web. In this case, no separate element is required to receive the web. The processor need only screw-couple the only element that is coupled during the procedure to the implant fixator in the patient's mouth.

  The sides of the V-shaped projections or recesses preferably extend radially outward with respect to a transverse plane extending perpendicular to the longitudinal axis of the implant and thus extend perpendicular to the circumferential direction. As a result, no radial force is transmitted through the contacting side after installation of the implant, which can break the distal partial shaft, for example made of ceramic.

  If the distal partial shaft is made of a tensile-resistant material, such as metal, especially titanium, the side faces will be superstructured partial shafts (ie the proximal side) relative to the exact radial orientation described above. The side surfaces belonging to the respective recesses of the respective protrusions of the implant portion) or the distal portion shaft (distal implant portion) can be inclined so as to intersect each other in the outward direction. For example, the side surface can be inclined by 45 ° with respect to the radial direction and thus also in the circumferential direction. As a result, the side surface has a centering action not only in the rotational direction but also in the lateral direction.

  The basic geometric shape of the outer wall of the superstructure part shaft is preferably conical at least in the region of the V-shaped projections. In a correspondingly advantageous manner, the basic geometry of the longitudinal opening of the distal partial shaft is also conical at least in the region of the V-shaped recess.

  For a given use case and in particular when the distal partial shaft is made of ceramic, the basic geometry of the outer wall of the superstructure partial shaft as well as the basic geometry of the inner wall of the longitudinal opening of the distal partial shaft It is advantageous if the geometric shape is cylindrical at least in the region of the V-shaped recess.

  In any case, the fit between the outer wall of the superstructure part shaft and the inner wall of the distal part shaft is preferably an idle fit, at least in the region of the V-shaped recess. Furthermore, the distal part shaft and the superstructure part shaft are each preferably provided with four V-shaped recesses or V-shaped projections distributed evenly on the outer circumference of each shaft part. In this manner, a precisely defined positioning possibility is obtained between the partial shaft distal to the superstructure and the partial shaft in the rotational direction. Optionally, a larger or smaller number of protrusions and recesses can advantageously be provided in a substantial number equally divided over the outer circumference of each partial shaft. A suitable number is, for example, 3, 6 or 8.

  It is also advantageous to provide protrusions having a large open V-shape (a sharp V angle) in association with the corresponding recesses in the distal partial shaft.

  As the V angle (open angle of each V shape), an angle between 10 ° and 170 ° is advantageous. For structures that are automatically centered, the V angle is advantageously smaller than the apex angle of each friction cone that results from the material pair of the V-shaped protrusions or recesses on the side surfaces facing each other.

  The concept of the present invention, which can be realized in a form different from that described in detail so far, is that of the distal and proximal partial shafts that can abut each other when joining both partial shafts. Of the end faces, before both partial shafts assume their final position relative to one another, any end face lies in a plane extending perpendicular to the longitudinal axis of both partial shafts. A known two-part shaft for dental implants with anti-rotation devices, in which the partial shafts are rotated relative to each other before both partial shafts are fitted in and out to the desired position. In the case of shafts having end faces extending perpendicular to the longitudinal direction that collide with each other when being applied, the proximal superstructure shaft has been pivoted to the distal partial shaft Fixed in position, the result is that the shaft resulting from this misassembly has a length greater than expected. This is because in this case both partial shafts have not yet finally been fitted in and out. The final fittings originally provided to limit the relative axial positions of both partial shafts are not yet in contact with each other in this case. This is because, based on the fact that both partial shafts rotate relative to each other, first the other surface extending perpendicular to the longitudinal axis of each partial shaft is essentially on the axis of the first partial shaft. The reason is that engagement with a vertically extending end face is not planned, and the respective parts collide with the opposite face of the other partial shaft. Also, automatic correction of the rotation angle error is not performed in this case. This is because both surfaces colliding with each other in this way slide on each other in the form of inclined surfaces, so that the rotation angle cannot be removed automatically again.

  In the case of known shafts for dental implants, the treating physician or engineer should take care that both partial shafts are fitted in and out without rotation angle error and that both partial shafts are not locked in the wrong position relative to each other. I need to pay.

  In the shaft of the present invention, the above problem is that the end surface extending perpendicularly to the longitudinal axis of each partial shaft is not provided except for the surface provided for the final longitudinal stop. Was avoided by. This was achieved by a V-shaped recess or V-shaped protrusion. However, other geometric solutions are possible.

  Said solution is that the surface that serves as a longitudinal termination stop is located at a different radius than the other end surface that is useful for positioning in the rotational direction, which is actually formed by V-shaped projections and recesses. Based on thought.

  When both the partial shafts are fitted inside and outside, the V-shaped concave portions or the V-shaped projections facing each other collide with each other on an inclined plane. When the partial shafts are further fitted, the side surfaces that collide slide relative to each other until the partial shafts are in the axial relative terminal position and have the correct rotation angle with respect to each other.

  A suitable material for the distal and proximal implants is steel or titanium, but can also be ceramic or plastic.

  In order to produce a geometrically accurate shaft in the preferred form, the proximal and distal partial shafts are preferably by metal injection molding (MIM), or hot plastic Manufactured by press working.

  Metal injection casting makes it possible to give the final geometry, which is the only working step, filling the injection mold, almost arbitrarily complex to the entire component.

  For metal injection casting, solid metal bodies are not used, but fine powder is used as the starting material for the component to be fabricated. This powder is mixed with a binder containing plastic and kneaded into a so-called feedstock. The feedstock is press-fitted into an injection mold (tool) having a negative shape of each partial shaft on a commercial injection molding machine at about 100 ° C. under high pressure. The green piece of the proximal or distal part shaft thus generated already has the desired final geometry, but in subsequent steps the binder is used to obtain a pure metal part. Must be released from again. For this purpose, the binder is removed in a multi-stage chemical and thermal process and at the same time the components are fired by sintering at about 1200 ° C. In this case, titanium is preferably used as the metal.

  If the implant part is made of ceramic rather than a gold layer, the preferred manufacturing method is Ceramic-lnjection-Molding (CIM). The CIM-method works in the same way as the MIM-method with some differences in material usage. In this case, a feedstock having ceramic powder is used instead of metal powder. Correspondingly, according to an alternative embodiment, ceramic components of implants made of CIM, in particular ceramic partial shafts, are advantageous.

  Alternatively, both partial shafts can be produced by cold or room temperature or hot plastic pressing.

  In order to selectively manufacture the proximal and distal partial shafts by hot plastic pressing, all the implant geometries that produce the implant-abutment-bonded joint region Two deformation tools must be manufactured.

  The first deforming tool is manufactured for hot plastic pressing.

  In the case of hot plastic pressing, titanium is brought into the region of dynamic recrystallization (which means that it is heated to a temperature between 700 ° C. and 900 ° C.).

  The deformation process of the superstructure structure portion (proximal partial shaft) is called room temperature actual forward plastic pressing or hot inner actual forward plastic pressing.

  The deformation process of the implant (partial shaft on the distal side) is called hot nap retraction plastic pressing or hot nap retraction plastic pressing.

  For this purpose, a round bar is cut into a predetermined length, heated and placed in a deforming tool. Deformation takes place at high press pressure.

  In the first transformation step, an outcome very close to the achievable final outcome is already achieved.

  Already after the first deformation step, the full geometry of the implant part forming the implant-abutment-bond is given. There is still no manufacturing error based on the thermal contraction of the workpiece being cooled. In addition, the surface is still dull due to the intense heating of the workpiece required for hot plastic pressing. In the case of titanium, there is no fear of adhesion (titanium adhesion to the tool).

  A smooth, glossy surface in the region of the implant-abutment-joint between the final shape and both partial shafts is then achieved in another deformation step.

  A second deforming tool is used for the second deforming step. Depending on the tool, cold calibration or room temperature calibration of the workpiece (proximal or distal partial shaft) is implemented.

  The second deformation step can be performed during a cooling period when the workpiece still has a temperature between about 400 ° C. and 450 ° C. at a time point defined.

  For the second deformation step, the workpiece is removed automatically from the first deformation tool and placed in the second deformation tool.

  The change in geometric shape due to the second deformation step is very slight. This is because titanium, which is an advantageous material, is extremely difficult to deform in a cold state and a heated state. As the titanium material lattice begins to flow in a short time and locally, the material lattice becomes brittle very rapidly upon further deformation. Too strong cold or hot deformation destroys the titanium structure. However, with very little deformation, in addition to the defined final shape of the workpiece in the region of implant-abutment-bonding, an increase in hardness due to local cooling of the workpiece is still achieved.

  Each deformation process ends after the second deformation step and the geometric shape between the two partial shafts for the implant-abutment-joint between the two partial shafts described above is Complete.

  For hot plastic pressing with both deformation steps described above, a tool set consisting of two deformation tools each is required to deform one implant component.

  In order to manufacture a deformable tool, a graphite body is first manufactured by a 5-axis-micro-milling. To produce a deformable tool, the graphite body is spark eroded and eroded into a block of hardened steel. The surface of the deformed tool generated in this way, which is later stamped into the series part, must be polished by hand in a very laborious process.

  In some cases it may be necessary to further process one or both workpieces (proximal or distal partial shaft) in the region outside the implant-abutment-joint.

  In some cases, the necessary shaping up to the required final shape is achieved by cutting. This shaping is due to the superstructure partial shaft corresponding to the proximal partial region of the proximal partial shaft, for example the geometrical shape required for the crown as well as the distal of the distal partial shaft. It is a geometric shape necessary to obtain an artificial tooth root in a partial region on the side.

  In order to give such a shape by cutting, the workpiece must be fastened to the workpiece holder of the corresponding machine. To this end, it is proposed to hold the workpiece in the correct geometric shape produced by hot plastic pressing and hold it during cutting.

  In order to eliminate inaccuracies, each workpiece is clamped only once for cutting.

  As a machine for imparting a shape by cutting, a machining center, that is, a machine in which all necessary machining steps by cutting are performed one after the other is suitable.

  In order to achieve the final shape of the superstructure and the implant, both a stationary tool (in the case of machining) and a rotating tool (in the case of milling) are usually required. Also, an axial through hole in the proximal partial shaft, as well as an axial hole with an internal thread that receives a screw pin connecting both partial shafts, is formed in this process.

  In the following, an embodiment of a shaft of a dental implant according to the present invention will be described with reference to the drawings together with a slightly modified embodiment of a seal body and an embodiment of a seal body holder as an auxiliary tool for assembling both partial shafts.

FIG. 6 is a perspective view of an overlaid shaft as a proximal implant portion. FIG. 3 is a perspective view of a distal partial shaft as a distal implant portion. FIG. 5 shows a shaft having a distal partial shaft and an overlaid partial shaft integrated with each other (the distal partial shaft is shown partially transparent). The perspective view which showed the partial shaft of the distal side, and the upper part partial shaft by the exploded projection method. The longitudinal cross-sectional view of a shaft. FIG. 6 is a cross-sectional view of the shaft along the line DD in FIG. 5. FIG. 3 is an exploded view showing the shaft with all the components of the shaft, i.e., the proximal and distal partial shafts, the seal body and the screw pins connecting the partial shaft to the shaft. FIG. 8 is a longitudinal sectional view showing the shaft shown in FIG. 7 in an assembled state. The longitudinal cross-sectional view of the partial shaft of a distal side. FIG. 9 is another longitudinal sectional view showing the distal partial shaft rotated by 30 ° with respect to FIG. 8. The longitudinal cross-sectional view of the partial shaft of the proximal side. FIG. 9 is a cross-sectional view similar to FIG. 8 shown without a sealing member. FIG. 3 is a cross-sectional view showing the advantageous shape of the distal partial shaft, the proximal superstructured partial shaft and the seal ring, located outwardly with respect to the longitudinal axis of the shaft. FIG. 5 is a perspective view from the outside of an advantageous transition outline from a proximal side to a distal partial shaft. FIG. 9 is an enlarged view of a modified embodiment of a superstructure partial shaft according to the embodiment shown in FIGS. 7 and 8; FIGS. 4A and 4B are diagrams showing the principle of stopper surfaces facing each other that limit the maximum compression of the seal. The figure which showed the advantageous ring-shaped sealing body which consists of an elastomer. The enlarged view from FIG. The figure which showed the sealing body by which it covered by the nano upper surface coating layer shown by FIG. 17 and 18 partially. FIG. 19 shows a seal body similar to the seal body of FIGS. 17 and 18 with a concentric outer peripheral surface. The figure which showed the sealing body in the state assembled and compressed between the partial shafts of the proximal side and the distal side. The figure which showed the selective seal body. FIG. 23 illustrates the selective seal of FIG. 22 assembled and compressed between the proximal and distal partial shafts. FIG. 23 shows a selective seal from FIG. 22 with a nano-coating layer. FIG. 3 is a cross-sectional view of a second selective seal body having a nano-coating layer and an integrated metal spring. FIG. 26 is an enlarged view of a portion of the second optional seal body of FIG. 25. FIG. 27 shows the selective seal of FIGS. 25 and 26 in a compressed state assembled between the proximal and distal partial shafts. FIG. 27 shows the second selective seal shown in FIGS. 25 and 26 with a nano-coating layer. The figure which showed the selective 1 change Example of the seal | sticker. The perspective view of a seal body holder. FIG. 31 is an enlarged partial view of a seal body receiving portion of the seal body holder in the perspective view of FIG. 30. The longitudinal cross-sectional view of the seal body holding body of FIG. FIG. 33 is an enlarged partial view of a seal body receiving portion of the seal body holder shown in the longitudinal sectional view of FIG. 32. The figure which showed the seal body holding body with the received seal body. FIG. 35 is an enlarged partial view of a perspective view of a seal body holder having the received seal body shown in FIG. The longitudinal cross-sectional view of the seal body holding body which receives the seal body shown in FIG. FIG. 38 is an enlarged partial view of a longitudinal sectional view of a seal body holding body that receives the seal body shown in FIG. 36. The figure which showed the state in the case of mounting the sealing body on the shaft part of a proximal side the sealing body holding body which has the received sealing body shown to FIGS. 30-37.

  As can be seen from the superstructure part shaft 10 shown in FIG. 1, the superstructure part shaft 10 has a conical shape that tapers toward the distal end 14 of the superstructure part shaft 10. It has a length section 12 having a basic geometric shape. The cone angle is 10 °. In the region of this conical length section 12, the superstructure part shaft 10 has a total of four V-shaped projections 16. This protrusion 16 points at its distal end to the distal end 14 of the superstructure part shaft 10. The four V-shaped projections 16 act as triangular teeth, are symmetrical, and are spaced equidistantly around the conical longitudinal section 12 of the superstructured part shaft. In this manner, eight side surfaces 18 are produced which are inclined and directed at the distal end 14 of the superstructure shaft portion 10.

  In FIG. 2, the distal partial shaft 20 is shown in a perspective view. The partial shaft 20 has a longitudinal opening that opens toward the proximal end 22. The longitudinal opening has an inner wall 24 which likewise has a conical basic geometric shape. The inner wall 24 is provided with four V-shaped recesses 26. These recesses 26 have side surfaces 28 facing the proximal end 22 of the distal partial shaft 20.

  When the distal partial shaft 20 and the proximal superstructure partial shaft 10 are joined together (see FIG. 3), the relative positions of both partial shafts are close to each other, both axially and rotationally. Is most accurately defined by the side surface 18 or 28 that contacts the surface. The inclined side surfaces 18 or 28 of the V-shaped protrusions or recesses form a stop surface facing each other, the proximity of the surfaces 32 and 34 facing each other (see FIGS. 6 and 7), and hence the seal 30 (FIG. 6). 7)). This is shown in FIGS. 12a to 12c. In particular, FIG. 12c shows how the faces 18 and 28 come into contact and thus form a longitudinal stop when the dental implant has been assembled.

  Accurate centering of both partial shafts is done by assembly by the opposed inclined sides 18 or 28 of the V-shaped projections or recesses, respectively. When the superstructure partial shaft 10 is inserted into the longitudinal opening of the distal partial shaft 20, the inclined side surfaces 18 or 28 of the projecting portion or the concave portion abut on the inclined plane. The superstructure part shaft 10 therefore slides until it reaches its axial end position when further inserted into the longitudinal opening of the distal part shaft 20, in which case all the opposite side surfaces 18 and 28. Rotate until they touch each other evenly. Thereby, the superstructure part shaft 10 is forced to a desired end position without being prevented from sliding, and is then fixed by a screw pin 40 (see FIG. 7) extending in the longitudinal direction of the shaft. The screw pin 40 is tightened with a force of 30 Ncm.

  At the same time, the cooperating side surfaces 18 and 28, which serve as longitudinal stoppers and anti-rotation, are then advantageously entered into the longitudinal opening of the distal partial shaft 20, as in other systems. It is not located in the area of the implant shoulder. Thus, the implant shoulder can be held at exactly the same level.

  In the alternative embodiment shown in FIGS. 1 to 5, in order to configure the transition from the proximal superstructure partial shaft to the distal partial shaft in a bacteria-tight manner in the region of the outer ring of the assembled shaft. Does not show any special means.

  According to the alternative embodiment shown in FIG. 6, a seal 30 is provided for this purpose. The seal 30 is disposed between an end face 32 located outside the proximal superstructure part shaft 10 'and an end face 34 located opposite the distal part shaft 20' opposite thereto. Yes. When the shaft has been assembled, that is, when the proximal superstructure partial shaft 10 ′ and the distal partial shaft 20 ′ take a final axial relative position to each other, the seal ring 30 is axially moved. Is compressed. The seal ring 30 is made of biocompatible plastic.

  FIG. 7 shows an exploded view of the main components of the shaft of the dental implant of the present invention. That is, the proximal partial shaft, the distal partial shaft 20, the seal body 30 for sealing the transition between the proximal and distal partial shafts, and the proximal and distal portions. A screw pin 40 for screwing the partial shaft to the distal side is shown.

  The longitudinal section of the shaft according to the invention for the dental implant in FIG. 8 is shown with the seal body 30 correspondingly compressed with all the main components assembled.

  9 to 11 show the individual components in longitudinal section.

  In FIG. 12, the side surface 18 of the projection 16 in the proximal partial shaft 10 or the side surface 28 of the recess 26 in the distal partial shaft 20 is centered through the side surface and the partial shaft 10 in between. And 20 are shown to cooperate in such a way that they do not occur through the perimeter.

  The transition between the superstructured partial shaft 10 'and the distal partial shaft 20', shown in perspective and partially enlarged in FIG. 13, is the contour of the assembled shaft. However, it has been shown that in the transition region from the superstructure partial shaft 10 'to the distal partial shaft 20', a clump-shaped space is formed and bacteria are not continuously accumulated in this space.

  This is also obtained from the appearance of the transition between the superstructure part shaft 10 'and the distal part shaft 20' shown in FIG.

  FIG. 15 is an enlarged perspective view of the proximal erected structure part shaft. Similar to the V-shaped protrusion 16 already described in connection with FIGS. 1 to 6, the seat 36 of the sealing body 30 is well identified.

  FIG. 16 shows how the side surfaces 18 and 28 act as stopper surfaces in the longitudinal direction and are useful for compressing the sealing body 30 (see FIG. 12).

  17 and 18 show in cross section an advantageous sealing body 30 'made of an elastomer, for example FFKM. From this drawing, it can be seen that the sealing surface 36 of the sealing body 30 ′ is not flat but protrudes in the axial direction of the implant at the outer edge of the sealing body 30 ′ to form raised portions 42 and 44. The ridges 42 and 44 are deformed upon fastening of the proximal and distal implant portions to form a secure seal.

  FIG. 19 shows the sealing body 30 ′ shown in FIGS. 17 and 18 having a covering layer of Parylene as described at the beginning. Furthermore, it can be seen from FIG. 19 that the coated edge of the sealing body 30 ′ is rounded to avoid rupturing of the coating layer in the region of the coated edge.

  FIG. 20 shows that the outer peripheral surface 50 of the seal body can be formed in a concavity. As a result, after assembly of the shaft according to the invention for a dental implant, the outer peripheral surface of the sealing body extends as nearly as straight as possible due to the compression of the sealing body.

  FIG. 21 shows the roundness given to the locations indicated by the arrows at the edges of the seal body 30 and the partial shafts 10 and 20.

  FIGS. 22-24 show an optional seal body 30 ″ having an O-ring shaped elastomer body 60 and inserted into a ring element 62 having an open U-shaped cross section therein.

  In FIG. 22, an optional seal body 30 ″ is shown in cross-section. FIG. 23 is an enlarged partial view showing that the optional seal body 30 ″ has a distal portion shaft 10 and a distal portion. It is shown in an assembled state with the shaft 20 on the side. FIG. 24 shows that this optional sealing body 30 ″ can also have a covering layer made of, for example, Parylene.

  Figures 25 to 27 show by way of example another alternative sealing body 30 "'having a metal spring 48 therein. The metal spring 48 is configured in a ring shape and is U-shaped outward. Located in an elastic plastic body 46 having an open cross section, the plastic body 46 is preferably made of PTFE and the metal spring 48 is made of stainless steel, as shown in FIG. May have a covering layer 38, for example made of Parylene, on the outside, the plastic body 46 is a layer 38 several nanometers thick, which in the preferred embodiment illustrated contains titanium particles inside. It is covered with a layer 38. The thickness of the layer 38 is shown greatly exaggerated so that this layer 38 is visible. It can, moreover can be provided independently of the outer shape of the seal body.

  In alternative embodiments, the spring can also consist of other spring materials, such as titanium or plastic, such as PEEK. Moreover, as long as a spring exhibits a spring action in the longitudinal direction shown by the broken line of the sealing body, it can have other shapes (see FIG. 25).

  FIG. 28 shows a sealing body in which a ring-shaped plastic body, for example made of PTFE, has a U-shaped cross section and is partially filled with elastomer 64.

  FIG. 29 shows a seal having a seal ring 30 "" made of an expandable material, such as an expandable metal or a high coefficient of thermal expansion plastic. The seal body 30 "shown in Fig. 29 has the shape of a tube section. The corresponding space between the proximal and distal implant portions 10" "or 20" " Is formed.

  30 to 38 show a seal body holder 70 used as a tool for attaching the seal body 30 to the partial shaft 10 on the proximal side. The seal body holding body 70 has a groove 72 opened inward at one end, and the seal body 30 can be inserted into the groove 72. Advantageously, the seal body holder 70 is fitted with a seal body by the seal body manufacturer immediately after the seal body 30 is manufactured. This simplifies handling by the doctor and improves treatment. In this case, the grip area 74 with a small groove facilitates handling.

  10 Overstructure part shaft, 12 Length section, 14 End, 16 Protrusion, 18 Side, 20 Partial shaft, 22 End, 24 Inner wall, 26 Recess, 28 Side, 30 Seal, 32 End face, 34 End face, 36 Seat Part, 42 raised part, 44 raised part, 46 plastic body, 48 metal spring, 50 peripheral surface, 60 elastomer body, 62 ring element, 64 elastomer, 70 seal body holder, 72 groove, 74 grip region

Claims (32)

A two-part dental implant having a distal partial shaft or distal implant portion and a proximal building partial shaft or proximal implant portion, the distal and proximal sides The surfaces of the implant portions are bound to each other at least indirectly at the binding site in a state of being bonded to each other and face each other in the region of the binding site;
A seal body is provided between the surfaces of the distal and proximal implant portions facing each other, the seal body having a seal surface facing the surface, and both implant portions are finally joined together In such a state, the surfaces facing each other are in close contact with the sealing surfaces facing each surface ,
The distal and proximal implant portions are provided with stopper surfaces facing each other, the stopper surfaces abut against each other in the assembled state of the dental implant, and the seal body is disposed between the implant portions. In a type that limits the degree to which both surfaces facing each other approach and defines a minimum spacing between both facing surfaces of the implant portion, the minimum spacing being bridged by a seal body,
Mutually facing surfaces extend transversely to and parallel to the longitudinal axis of the dental implant,
An inner wall having a basic geometry with a longitudinal opening that opens towards the proximal end of the distal partial shaft, the longitudinal opening having a circular cross section And a V-shaped recess in the inner wall is provided that opens toward the proximal end of the distal partial shaft,
The end of the construction part shaft thereof distally, has an outer wall having a basic geometry Matogata shape having a matching circular cross-section in the longitudinal opening of the distal portion the shaft,
The outer wall of the building part shaft has a V-shaped protrusion in the region of its distal end, the V-shaped protrusion being fitted into the V-shaped recess of the distal part shaft, When the shaft and the building part shaft are joined together, the side sections of the V-shaped recess and the V-shaped projection contact and cooperate with each other to provide opposing stopper surfaces that limit compression of the seal. A two-part dental implant characterized in that it is formed .   The dental implant according to claim 1, wherein the seal body is at least partially made of an elastic material.   The dental implant according to claim 1, wherein the mutually facing surfaces are conical, have the same cone angle, and are arranged concentrically with each other and concentrically with the longitudinal axis of the dental implant.   4. Dental implant according to claim 1, wherein the sealing body has the shape of a disc with a central through opening.   The sealing body has an end surface formed in a concurve, and the material thickness of the sealing body as measured by the longitudinal axis of the implant is at least in the relaxed state in the peripheral region of the sealing body is larger than the central region of the sealing body The dental implant according to any one of claims 1 to 4. 6. Dental implant according to any one of claims 2 to 5, wherein the elastic material of the sealing body is elastically compressible by at least 5% in the direction of expansion. The dental implant according to any one of claims 2 to 6, wherein the elastic material of the sealing body is plastic.   The dental implant according to claim 7, wherein the plastic is an elastomer, a thermoplast or a duroma mixture. Besides the seal body is plastic, a metal or ceramic component is an integrated component of the metal or ceramic component starve Lumpur body, according to claim 7 or 8 teeth implant according.   To a sealing component in which at least one outer surface of the sealing body forming the outer surface of the implant is coated with a metal or ceramic or plastic layer, and the metal, ceramic or plastic layer is coated with a metal or ceramic or plastic layer The dental implant according to claim 9, which prevents invasion of bacteria. Or metal layer contains titanium, silver and / or gold, or plastic layer contains a PTFE, tooth implant according to claim 10, wherein.   The dental implant according to any one of claims 1 to 9, wherein at least the sealing surface of the sealing body is made of an elastic, biocompatible, oral stable, sterilizable plastic. The dental implant according to any one of claims 7 to 12, wherein the plastic has a thermal expansion coefficient of 75 * ^10-6 / K or more at 20C. Seal body to check in the radial direction between the distal and proximal implant portions of the surface are arranged, complete radial dimension of the seal body implants portion between the distal side and the proximal side 4. A dental implant according to claim 1 or 3, wherein the dental implant is larger than the space between the distal and proximal implant portions when coupled to each other. A distal partial shaft as a distal implant portion and a proximal constructed partial shaft as a proximal implant portion having a longitudinally divided shaft and for implantation in a jawbone; An artificial crown is built on the construction part shaft,
The proximal end of the distal partial shaft and the distal end of the building partial shaft are configured to geometrically fit each other and interface with each other with the shaft implanted. The dental implant of claim 1. The distal partial shaft has four V-shaped recesses, the V-shaped recesses are evenly distributed around the inner wall, and the construction partial shaft is correspondingly divided into four V-shaped recesses. has a projection, the projection of the V-shape is likewise evenly distributed over the circumference of the outer wall, the tooth implant according to claim 1, wherein. It is conical in the region of the projections of the outer wall basic geometry V-shaped construction part shaft, tooth implant according to claim 1, wherein. 18. Dental implant according to claim 17 , wherein the basic geometric shape of the inner wall of the longitudinal opening of the distal partial shaft is conical in the region of a V-shaped recess. A seal body is disposed between and acts as a seal between the two end faces located outside the radial direction of the shaft facing each other in the assembled state, and the distal partial shaft and the proximal side shaft 19. The sealing body according to any one of claims 15 to 18 , wherein the sealing body is designed such that the sealing body is compressed in the axial direction of the shaft when the building part shaft assumes a final axial relative position to each other. The dental implant according to Item. 20. Dental implant according to claim 19 , wherein the sealing body has the shape of a circular seal ring with a rectangular material cross section. 21. A dental implant according to claim 19 or 20 , wherein the seal body is made from a biocompatible plastic. 22. Dental implant according to any one of claims 15 to 21 , wherein the distal partial shaft and / or the proximal building partial shaft are made from a biocompatible metal. 23. A dental implant according to claim 22 , wherein the metal is titanium or a titanium-containing alloy. 22. Dental implant according to any one of claims 15 to 21 , wherein the distal partial shaft and / or the proximal partial shaft are made of ceramic. 25. Dental implant according to claim 24 , wherein the ceramic is HIPed and / or polished. The ceramic is ZrO ₂ , ZrO ₂ / Al ₂ O ₃ / Y ₂ O ₃ (ATZ), ZrO ₂ / Y ₂ O ₃ (TZP) or ZrO ₂ / Y ₂ O ₃ / Al ₂ O ₃ (TZP-A). The dental implant according to claim 24 or 25 , which is contained. 22. Dental implant according to any one of claims 15 to 21 , wherein the distal partial shaft and / or the proximal partial shaft are made of plastic. 28. Dental implant according to claim 27 , wherein the plastic contains polyetheretherketone (PEEK). The dental implant of claim 1, wherein the V-shaped projection is pointed at a distal end of the building part shaft. The dental implant of claim 1, wherein the V-shaped recess has a side facing the proximal end of the distal partial shaft. 31. A dental implant according to claim 30, wherein the side surfaces simultaneously function as a longitudinal stopper and a locking means to prevent rotation. When the distal partial shaft and the building partial shaft are connected or connected, the relative positions of the distal partial shaft and the building partial shaft are fixed without play in either the axial direction or the rotational direction. The dental implant according to claim 1.

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