• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    Method for producing a dental prosthesis (Z), in particular crown, bridge or bridge, comprising the steps of producing a metallic framework (1), producing a ceramic veneer (3), applying at least one bonding layer (2) to the metallic framework (1) and or on the ceramic veneer (3), applying the ceramic veneer (3) to the metallic framework (1), wherein the joining layer (2) is arranged between the metal framework (1) and the ceramic veneer (3), and firing the joint together metallic framework (1), the joining layer (2) and the ceramic veneer (3), whereby the joining layer (2) connects the metallic framework (1) with the ceramic veneer (3).
    公开号:AT519721A1
    申请号:T50152/2017
    申请日:2017-02-24
    公开日:2018-09-15
    发明作者:Steger Heinrich
    申请人:Steger Heinrich；
    IPC主号:
    专利说明:

    Summary
    Method for producing a denture (Z), in particular crown, bridge or bar, with the steps of producing a metallic framework (1), producing a ceramic veneer (3), applying at least one joining layer (2) to the metallic framework (1) and / or on the ceramic veneer (3), applying the ceramic veneer (3) to the metallic framework (1), the joining layer (2) being arranged between the metallic framework (1) and the ceramic veneer (3), and jointly firing the metallic framework (1), the joining layer (2) and the ceramic veneer (3), whereby the joining layer (2) connects the metallic framework (1) with the ceramic veneer (3) in a cohesive manner.
    (Fig. 2) / 32
    81179 22 / eh
    The invention relates to a method for producing a dental prosthesis, in particular a crown, bridge or bar, comprising the steps of producing a metallic framework, producing a ceramic veneer, applying at least one joining layer to the metallic framework and / or to the ceramic veneer and applying the ceramic veneer onto the metallic framework, the joining layer being arranged between the metallic framework and the ceramic veneer. In addition, the invention relates to a denture produced in such a method.
    In the manufacture of dentures in the form of metal-ceramic crowns, the basic structure consists of a metallic alloy, which transfers the load to the (underlying rest) tooth and at the same time ensures the strength and stability of the denture. This metal framework is then veneered, this veneer being made with a ceramic material.
    In a known method, the ceramic is applied as a paste to the metal by hand and then fired in a ceramic furnace at a temperature of approximately 800 ° C. This can then be done in several steps in order to burn up several layers. In such a manufacturing process, manual skills are then expected from the dental technician performing the work in order to obtain an aesthetically satisfactory denture.
    Another possibility is that the metallic framework and the ceramic veneer are produced in a CNC-controlled processing machine. In this case, manual layering is not necessary in order to obtain a first veneer on the metal. The ceramic veneer in particular can then be refined using the known method of ceramic layering technology in order to obtain an even more natural-looking denture. In a next step, the veneer produced in this way is cemented onto the metallic framework. Self-curing or light-curing composite adhesives are generally used for this. However, these have the disadvantage that as soon as the two parts are glued to one another, no additional ceramic layer can be fired / 32, since the adhesive cannot withstand the temperatures during a firing process.
    Non-generic DE 10 2005 023 106 A1 is concerned with a method for producing a tooth replacement part. The dental prosthesis consists of an at least one-piece framework and a veneer. These parts can be manufactured using CAD / CAM processes. Aluminum oxide or zirconium oxide is advantageously provided as the material for the first component and feldspar ceramic for the second component. This document is foreign to the genus because only in the introduction to the description of the prior art it is described that metals are often used as core materials and then ceramics as veneering materials, but the invention described therein is not specifically designed for the use of these materials. The two parts are then attached to one another by joining, a composite material being used. Glass solder, low-melting ceramic or organic adhesive can be used as the composite material. The components to be connected are advantageously selected to match one another with regard to their expansion coefficient. It is also stated that the two components are joined together using heat treatment.
    DE 197 14 759 B4 describes a tooth replacement in the form of a tooth crown, which consists of a cap-like metallic inner part and a sintered oxidic part attached. The metallic inner part is coated with an oxidic powder, whereby an intermediate layer is formed. In particular, a pure aluminum oxide powder is applied to the inner part by thermal spraying. A plasma torch is required to apply the aluminum oxide layer, which can be seen as a complex step for the coating. Then the separately manufactured tooth ceramic is put on and sintered in the temperature range from 650 ° C to 850 ° C. To influence the color of the dentures, zirconium is used as an oxide. Titanium or titanium alloys are provided as the material for the inner part. How exactly the individual parts are manufactured is not explained in detail in this document.
    / 32
    The object of the present invention is to avoid the disadvantages mentioned and to improve the method and method compared to the prior art.
    to create an improved denture.
    This is achieved by a method with the features of claim 1. Accordingly, the step of jointly firing the metallic framework, the joining layer and the ceramic veneer is provided, as a result of which the joining layer integrally connects the metallic framework with the ceramic veneer.
    In order to make the dentures look even more natural, the further steps of applying at least one ceramic veneer layer to the ceramic veneer and jointly firing the metallic framework, the joining layer, the ceramic veneer and the veneer layer are provided. The veneer layer can only be applied to the ceramic veneer in certain areas. The entire surface of the ceramic veneer that is not adjacent to the joining layer is preferably covered with the veneer layer.
    Facing is not necessarily understood to mean elements that cover a metallic part and thus “blend”. This can also be understood to mean elements that simply have to be attached to a metallic component. To put it simply, it can be said that the production of a dental prosthesis means that a metallic element (in this case, a framework) and a ceramic element (in this case, a veneer) are joined together.
    According to a preferred embodiment, it is provided that the metallic framework is manufactured, preferably milled, in a CNC processing machine. As an alternative or in addition, the ceramic veneer can also be produced, preferably milled, in a CNC processing machine.
    Furthermore, it is preferably provided that the ceramic veneer is densely sintered in a sintering furnace before the joining layer is applied. Additionally or alternatively, it can be provided that the metallic framework is densely sintered in a sintering furnace prior to the application / 32 of the joining layer. The sealing sintering takes place at a suitable sintering temperature for the respective material.
    In general, the joining layer can be applied to the metallic framework or to the ceramic veneer or to both parts before joining.
    It is particularly preferably provided that the joining layer consists of, preferably silicate, glass ceramic. Such a joining layer withstands the baking temperatures of the ceramic firing. It is therefore also possible to carry out at least one further firing process - especially after the veneer layer has been applied - without the risk that the veneer undesirably detaches from the framework.
    The metallic framework can also consist of only a single metal or of a metal alloy. It is preferably provided that the metallic framework consists of titanium or a titanium alloy. Other metals can also be added. In particular, the proportion of titanium or the titanium alloy in the metallic framework is over 80%, preferably over 88%, weight percent. According to a preferred embodiment, titanium 5 (ASTM standard) with the following properties is used as the material for the metallic framework:
    Density: 4.43 g / cm 3
    Vickers hardness: 341 HV
    Thermal expansion coefficient (25 - 500 ° C) 9.7 · 10 -6 · Κ -1 Thermal conductivity: 6.7 W / (mK)
    Chemical composition (%): titanium (approx. 90%), aluminum (approx. 6%),
    Vanadium (approx. 4%), iron and
    Oxygen (minor in each case
    Shares)
    Tensile strenght:
    Stretch limit:
    Expansion:
    Modulus of elasticity:
    Shear modulus:
    860 MPa
    790 MPa%
    114 GPa
    GPa / 32
    Poisson:
    0.342
    Ceramic for veneering is an inorganic non-metallic material. In general, all ceramics or ceramic mixtures that are suitable for dental applications can be used. It is preferably provided that the ceramic veneer has zirconium dioxide as the main component. This means that the zirconium dioxide content is at least 50 percent by weight. It is preferably provided that the zirconium dioxide content is over 85% by weight.
    According to a first exemplary embodiment, a material with the following properties is used for the ceramic veneer:
    Zirconium dioxide (ZrO 2 )
    Yttrium oxide (Y 2 O 3 )
    Aluminum oxide (Al 2 O 3 )
    Silicon dioxide (SiO 2 )
    Iron (III) oxide (Fe 2 O 3 )
    Density (g / cm 3 ):
    Bending strength:
    Vickers hardness (HV10)
    Weibull modulus
    Thermal expansion coefficient:
    Main component (over 50% by weight) Share of <12% by weight Share of <1% by weight Share max. 0.02 percent by weight max. 0.02% by weight ~ 6.0 g / cm 3
    670 MPa
    1250 HV10 ~ 5 ~ 10.0-10 ' 6 -K' 1
    In addition, hafnium oxide can also be contained in this material.
    According to a second exemplary embodiment, a can be used for the ceramic veneer
    Material with the following properties can be used:
    Zirconium dioxide (ZrO2)
    Yttrium oxide (Y2O3) aluminum oxide (Al2O3)
    Silicon dioxide (SiO2)
    Iron (III) oxide (Fe2O3)
    Main component
    4 - 6 percent by weight
    Proportion of <1 percent by weight
    Max. 0.02 percent by weight
    Max. 0.01% by weight / 32
    Sodium oxide (Na 2 O)
    Density:
    Flexural strength (at R.T.)
    Vickers hardness:
    Max. 0.04% by weight ~ 6.0 g / cm 3
    1000 - 1200 MPa
    1250 HV10
    Weibull modulus:
    CTE (coefficient of thermal expansion) ~ 15 ~ 10.0 · 10 -6 · Κ -1
    This material may also contain hafnium oxide.
    In order to avoid cracks in the dentures or the breaking of the dentures due to (repeated) firing, it is preferably provided that the coefficient of thermal expansion of the joint layer should be a maximum of 2.0 · 10 -6 · Κ -1 , preferably a maximum of 1.0 · 10 -6 · Κ -1 , from the thermal expansion coefficients of both the metallic framework and the ceramic veneer. Due to these relatively small differences in thermal expansion, the risk of jumps is also lower than with large differences.
    Resistance to cracks is particularly good when the coefficient of thermal expansion of the joint layer lies between the coefficient of thermal expansion of the metallic framework and the coefficient of thermal expansion of the ceramic veneer. Of course, the coefficient of thermal expansion of the joining layer can also be - preferably slightly - above or below the coefficient of thermal expansion of the metallic framework and the ceramic veneer. In particular, it is preferably provided that the coefficient of thermal expansion of the joint layer is at most 1.7 · 10 -6 · Κ -1 lower than the coefficient of thermal expansion of the ceramic veneer. In addition, it can preferably be provided that the coefficient of thermal expansion of the joining layer deviates by a maximum of 1.5 · 10 -6 · Κ -1 coefficient of thermal expansion of the metallic framework.
    Precisely, it can be provided that the metallic framework has a coefficient of thermal expansion of approximately 9.7 · 10 -6 · Κ -1 . The ceramic veneer should have a coefficient of thermal expansion of 10.0 · 10 -6 · Κ -1 . The coefficient of thermal expansion of the joining layer is preferably in a range between 8.0 and 10.5-10 -6 -K -1 . It goes without saying that these values can also deviate from the ranges specified here. However, it should be ensured that the differences between the coefficients are permissible
    Comply with differences.
    The manufacturer's specifications for the individual components on the associated data sheets apply to the coefficients of thermal expansion. If no such information is available, the coefficient of thermal expansion can also be measured. A dilatometer can generally be used to measure the coefficient of thermal expansion. An example of this is the dilatometer with the brand name "DIL 402 C" from NETZSCH-Gerätebau GmbH. For ceramic materials in the field of dentistry, the coefficient of thermal expansion can be measured on the basis of DIN EN ISO 6872 in the version from 2015. The measurement of the linear coefficient of thermal expansion is described in Section 7.4 of this standard. For the measurement of metallic materials in the field of dentistry, the DIN EN ISO 22674 in the version of 2016 should be used. The test method for measuring the linear thermal expansion is described under point 8.13.
    If the joining layer consists of a silicate glass ceramic, it is preferably provided that it consists of more than 60 percent by weight, preferably 60 to 68 percent by weight, of silicon dioxide and less than 12 percent by weight, preferably between 5 to 12 percent by weight, of aluminum oxide. In addition, it can also be provided that this joining layer has a potassium oxide content between 4 and 9 weight percent and a sodium oxide content between 5.5 and 12 weight percent.
    The joining layer is primarily used to ensure a good material connection with the ceramic veneer. In addition, the joining layer should also have suitable optical properties. In order to ensure that the underlying metallic framework is not clearly recognizable, one possible embodiment provides that the joining layer is connected to the metallic framework via at least one covering layer. So the / 32
    Joining layer is only indirectly bonded to the metallic framework via this cover layer. The same also applies if at least one cover layer is applied to the ceramic veneer. As a result, the joining layer is indirectly bonded to the ceramic veneer via the cover layer. This cover layer should be relatively opaque. Specifically, a silicate glass ceramic can also be used for this cover layer. It can also be provided that several of these cover layers are applied before the ceramic veneer is fired. The composition of these individual layers can then also differ from one another.
    Protection is also sought after for a denture, in particular a crown, bridge or bar, produced in a process according to the invention, with a metallic framework, a ceramic veneer and a joining layer connecting the framework and the veneer. In this regard, it should also be mentioned that the method according to the invention works in all dental work. Thus, the invention should not be limited to crowns, bridges and bars. For example, circular work or telescopic work can also be produced using this method, to name just a few examples. At least one area of the veneer layer is preferably also applied to the ceramic veneer. All of the exemplary embodiments and preferred variants described herein also apply to the dental prosthesis, provided this makes logical sense.
    Further details and advantages of the present invention are explained in more detail below with reference to the description of the figures and with reference to the exemplary embodiments illustrated in the drawings. In it show:
    1 schematically shows the structure of a denture,
    Fig. 2 shows schematically the individual steps of the manufacturing process of this
    dentures,
    3 schematically shows a metallic framework in the form of four tooth stumps with an applied ceramic veneer,
    Fig. 4 is a perspective view of an abutment and
    Fig. 5 front views of scaffolding in the form of titanium bases.
    / 32
    The innermost part of the dental prosthesis Z is the metallic framework 1. The joining layer 2 is layered on this metallic framework 1. This is followed by the ceramic veneer 3. On this is again one (or more)
    Facing layer 4 applied.
    In the first variant shown in FIG. 1, the metallic framework 1, which mainly consists of titanium or a titanium alloy, is veneered with a second part (ceramic veneer 3) made of zirconium dioxide. Both parts are modeled and manufactured using a CAD-CAM device. The two parts, also referred to as the joining process, are joined using a joining compound (joining layer 2). Basically, materials can be used as joining materials which have a coefficient of thermal expansion which is similar to the coefficient of thermal expansion of the two components to be joined.
    In the specific case, ceramic crowns, bridges or similar dental elements made of zirconium dioxide are used, which have a thermal expansion of approx. 10.0-10 -6 -K -1 . The metallic frameworks 1 made of titanium or titanium alloys used have a thermal expansion of approximately 9.7'10 ' 6 -K' 1 . Organic or inorganic agents can be used as the material for the joining layer 2. Materials such as glass solder, ceramics or organic glue can be used. However, a silicatic glass ceramic with a thermal expansion of approximately 10.0'10 ' 6 -K' 1 is preferably used. However, the thermal expansion coefficients can vary depending on the exact composition. In principle, however, the joining process can also be carried out with other materials which have approximately a desired coefficient of expansion. The silicatic glass ceramic has components of SiO 2 , Al 2 O 3 , K 2 O, Na 2 O, CaO and B 2 O 3 . The joining ceramic is very preferably based on leucite-free silicate sintered glasses.
    The composition of possible powders can be found in the following table (mass fractions in percent by weight).
    / 32
    components Material A Material B Material C SiO 2 63-68 60-65 58-62 Al2Ü3 5 - 8 8-12 7-11 K2O 5.5 - 9 4 - 6 5 - 8 Na 2 O 5.5 - 9 8-12 8-12 Li2O 1 - 3 - 1 - 3 CaO 1 - 3 0.1 - 2 1 - 3 SrO 1.5 - 4 - - BaO - 4 - 6 - B2O3 0-3 4 - 6 3 - 5 P2O5 <0.2 - 4 - 6 CeO2 0-2 - 0.5 - 2.5 ZnO 2 - 5 - 0.1 - 2 SnO 2 - - 0.1 - 2 MgO - 0.1 - 2 - ZrO2 0-2 - - TiO2 1 - 3 - - F 0-2 0.1 - 2 - CTE 10.0-10 -6 -K -1 8.5'10 -6 -K -1 9.0'10 -6 -K -1
    Depending on the color of the product, pigments are then added. This can account for up to 30%. In tests with 100% material A (which is more transparent than material C in the fired state) as joining layer 2, a very good material connection between the metallic framework 1 and the ceramic veneer 3 was achieved.
    Alternatively, a good cohesive connection was also achieved by first applying and firing a first layer of material C as a covering layer in order to cover the metallic framework 1, after which the material A was applied and fired with the ceramic veneer 3.
    In another experiment, material A was mixed with material C (division 50:50) and then applied directly and the crown (ceramic veneer 3) / 32 was placed over it and everything was fired. In this case, a satisfactory connection could also be achieved.
    The zirconium dioxide used as the ceramic material is also known colloquially as zirconium oxide or zirconium and is a material that is frequently used in the dental industry because it has excellent biocompatibility and also meets the aesthetic requirements for high-quality dentures Z. In addition, it also has the necessary mechanical properties, for example with regard to breaking strength or wear resistance. However, other ceramics (e.g. technical ceramics or glass ceramics) that have the necessary properties can also be used. Two preferred variants have already been mentioned above, which have a coefficient of thermal expansion of approximately 10.0-10 -6 -K -1 . The titanium grade 5 used in the tests has an expansion coefficient of approx. 9.7'10 ' 6 -K' 1 .
    The steps for the method for producing a dental prosthesis are explained in more detail below with reference to FIG. 2.
    In a first step (not shown), the data from the patient's mouth are recorded (e.g. the surface of the at least one tooth stump, the position of the implants, etc.), in order to then use suitable software to model the framework and the veneer to be able to perform. This can be done using a computer in an acquisition and modeling mode. The corresponding software is stored in a computer memory. The metallic framework is then adapted, for example, to the tooth stump taken up. The ceramic veneer is also modeled accordingly. A gap, which can be between 0.01 mm and 0.5 mm, but preferably between 0.02 mm and 0.2 mm and very preferably around 0.05 mm, is preferably already provided between the metallic framework and the ceramic veneer lies.
    After the two parts metallic framework 1 made of titanium and ceramic veneer 3 made of zircon have been produced, for example in a CAD / CAM processing device / 32 (see step i in FIG. 2, which only shows the metallic framework 1) the metallic framework 1 is covered with a first layer of glass ceramic (joining layer 2). This is shown in step ii of FIG. 2. As an alternative to the variant shown in FIG. 2, the joining layer 2 can also be applied to the ceramic veneer 3. A then thinner joining layer 2 can also be applied to both parts (1 and 3).
    Before this step ii is carried out, it is preferably provided that the surface of the metallic framework 1 is sandblasted. A wide variety of granules can be used for this. One possibility is aluminum oxide with a grain size of approx. 50-200 μm at approx. 2-3 bar. This has the advantage that the surface is roughened, as a result of which a better adhesive bond can be produced. This can be done both with the metallic framework 1 and with the ceramic veneer 2.
    Before applying the bonding layer 2, the powder is mixed with a liquid to form a spreadable paste. This is then applied to the metallic framework 1 with a thickness of approximately 0.5 mm using a brush. The applied layer thickness preferably corresponds to the gap which was provided between the two parts during the modeling. This process can also be carried out automatically, for example using a spray mechanism, using another application device or using a suitable method (for example diving). In such a case, the consistency must be adapted to the process used. With this joining layer 2, care must be taken that the entire surface of the metallic framework 1 is covered with it, so that no part underneath is visible. This joining layer 2 is then preferably selected by the composition such that it is an opaque and non-translucent material. This has the advantage that the gray structure of the metallic framework 1 is covered and thus does not shine through through the ceramic veneer 3. Optically better results can thus be achieved in the manufacture of the dental prosthesis Z.
    After the glass ceramic (joining layer 2) has been applied, the previously made ceramic veneer 3 is then placed over it (see step iii in Fig.
    / 32
    2). It can happen that too much applied material from the
    Joining gap is pushed out. This is then removed. It should then be ensured that the ceramic veneer 3 is pressed onto the position provided on the metal frame 1.
    This “three-way network” is then fired or sintered. To do this, the composite is only exposed to air for approx. 5 min. dried. Then the composite is in about 5 min. entered the kiln S (see step iv in FIG. 2), which has a standby temperature of approx. 400 ° C. and then heats to 800 ° C. in a vacuum with an increase of approx. 55 K / min. As a rule, there is a hold time of one minute. The furnace S is then opened slowly, also in steps, and the joined parts are slowly moved out. This ensures that controlled cooling takes place. This step takes about ten minutes. The process described here is a preferred variant and can also be carried out with other time and temperature parameters.
    The advantage of such a treatment is that this bonded composite can then be coated and refined with additional ceramic (veneer layer 4; see step v in FIG. 2). Thereupon, so-called glaze firings can be carried out in the furnace S (see step vi in FIG. 2) without endangering the adhesive bond between the metallic framework 1 and the ceramic veneer 3 given by the joining layer 2.
    In the prior art, the veneers were previously coated with the ceramic paste, and this was fired again and again in order to maintain the strength of the ceramic. This was carried out until the desired result was achieved. This veneered with ceramic was then connected to the metal frame using cement, for example a composite adhesive. If this denture was then placed in the patient's mouth and it was found that the color did not quite match the previous teeth, then the bond had to be loosened again in order to be able to make further adjustments to the ceramic in terms of color, since the stove was fired again the glue would burn.
    / 32
    When using the joining layer 2, preferably in the form of a silicate glass ceramic, these problems are eliminated and adjustments can be made as often as desired. The ceramic layer materials of the joining layer 2 can then be selected with any pigmentation, advantageously according to the VITA color scale A1-D4.
    Under certain circumstances, the ceramic veneer 3 itself can already be colored. This is carried out with so-called liquids, with which the ceramic veneer 3 is colored before the sealing sintering. The sealing sintering of the veneer 3 in the case of zirconium dioxide takes place at approximately 1400 ° -1500 ° C. However, this temperature range can vary. This sealing sintering of the ceramic veneer takes place in a sintering furnace (not shown) before the joining. It can also be provided that 3 multilayer blocks are used for the ceramic veneer, which already have different layers of color and do not necessarily have to be colored. Pressed blanks are generally used to produce the ceramic veneer 3, which are then densely sintered after processing, as described above. However, it can also be provided that ceramic blanks are used which already have their final density and no longer have to be densely sintered. These are then only processed superficially, preferably by grinding.
    In a second variant, based on the first variant shown in FIG. 2, provision can also be made for a first layer of the silicate glass ceramic (joining layer 2) to be applied to the metallic framework 1. Subsequently, the metallic framework 1 is then fired with this first applied layer, without the ceramic veneer 3 being attached.
    Then the metallic framework 1 together with the joining layer 2 is then scanned with a scanner in order to obtain the new geometric data of the surface. The ceramic veneer 3 can then be modeled based on this data. A gap can then be provided here between the two parts.
    / 32
    In theory, it is also possible that the scanning process is omitted and the previously modeled veneer 3 is placed on the already fired joining layer 2 and then this composite is fired again. However, the veneer 3 can also be adjusted in this case using a scan.
    If this does not take place, a joining layer 2 of the silicate glass ceramic can be applied again in the next step. In this case, the jointing compound can also differ from the first compound used. It is not mandatory that the same mass be used.
    In theory, this applied layer can now be fired again, then scanned using a scanner and the modeling carried out again. Normally, however, before this second applied layer is fired, the veneer 3 is put on and then the entire composite is fired again. This is done according to the procedure previously described.
    In a third variant, provision can also be made for the metallic framework 1 to be captured digitally using a scanner before it is coated with the joining layer 2. In some cases, it may happen that adjustments have to be made manually to the metal frame 1, for example parallelization of the walls. These changes must then of course be digitized again in order to be able to model the connection of the ceramic veneer 3 accordingly.
    After this step has taken place, the first or second variant can then be continued.
    If it is assumed that the titanium of the metallic framework 1 has a lower thermal expansion coefficient than the ceramic veneer 3, then when applying several joining layers 2 it can be provided that the individual layers also differ in their thermal expansion coefficient, and so that the titanium slowly adapts to the veneer. For example, titanium has a coefficient of thermal expansion of 9.0 · 10 -6 · Κ -1 and zircon has a coefficient of 10.5 · 10 -6 · Κ -1 . So / 32 two layers could be provided, the first layer on the titanium having a thermal expansion of 9.5'10 ' 6 -K' 1 and the second layer of
    10.0'10 ' 6 -K' 1 . A smooth transition can thus be created. You can also work with multiple layers here.
    As already mentioned, the present invention can be used not only for individual work, but also for larger work. For example, according to FIG. 3 it can be provided that the metallic framework 1 comprises a structure which has four individual tooth stumps, via which the individual ceramic veneers 3 can then be joined. These facings 3 can be present individually or can be designed as a coherent part. This denture Z can then be veneered again with a veneer layer 4 after the joining. The lower, still exposed titanium part, which would also be visible in the patient's mouth, can then be veneered with a ceramic veneer layer 4, for example to imitate the gums. Ceramic materials with an aesthetically appropriate pigmentation are then used for this.
    Alternatively, its web can also be manufactured, which can be used completely in the veneer 3 and then nothing more can be seen of the metallic framework 1, or only very small areas which can be veneered again with ceramic.
    In general, it is also possible for the metallic frameworks 1 and also the ceramic veneers 3 to be produced in a different way, for example by means of various casting processes known in the dental industry.
    Other dental alloys can also be used which have a coefficient of thermal expansion which is similar to the veneer and the joining agent. A chromium-cobalt alloy (CrCo), for example, would be suitable as a metal for dental applications.
    In a preferred embodiment variant, the metallic framework 1 is machined / milled out of a solid block. Alternatively, a sintered metal block / 32 can also be used. In this case, the metallic frame 1 must then, before the
    Joining layer 2 is applied, densely sintered.
    It is also possible for the ceramic veneer 3 to be manually coated with a veneer layer 4 before it is added to the metallic framework 1 and to be fired beforehand before this complete veneer (3 and 4) is then added to the metallic framework 1 , In this way, the optical adaptation to the remaining steps would already take place in a first process step, i.e. before the joining process. Afterwards, after the joining process, refinements can still be made.
    The firing or sintering process can then be adapted to the precisely used materials as required. For example, a slower heating rate can be used to generate less stress in the material or to adjust the start and end temperature.
    With the masses used for the joining layer 2, it is also possible for different powders to be mixed. For example, a powder can aim to hide the framework structure and is accordingly opaque (cover layer). This is then mixed with a powder that is translucent to thereby generate a less opaque powder. This powder is then again mixed with a liquid to form a paste that can be applied and can then be layered and processed using the methods already described above.
    Of course, there is always a possibility that one of the two parts to be joined, or both, are manufactured manually and then joined. If one is made manually, it can be captured by a scanner and the second part is then adapted / modeled and manufactured accordingly.
    Furthermore, it can also be the case that the veneer 3 itself has a multilayer structure and the individual layers are connected / joined to one another. These individual layers can then in turn be generated automatically using a CAD / CAM device.
    / 32
    In addition to material-removing processes, material-building, additive processes can also be used for the production. Milling, grinding, additive manufacturing processes, etc. are also possible. Generally everyone can
    Manufacturing processes are used, which result from DIN 8580 and through which the individual components can be manufactured.
    The attachment in the patient's mouth is described below as a final step (not shown).
    A dental prosthesis Z as shown in FIG. 1 can then, when it is finished, be cemented onto a tooth stump in the patient's mouth. For this purpose, the natural tooth in the patient's mouth may have been processed so that the denture Z can then be put on. As already described at the beginning, the situation in the patient's mouth must be digitally recorded in order to create the dental prosthesis Z. A wide variety of methods can be used for this. On the one hand, recording via an intraoral scanner is conceivable. However, impressions can also be taken, which in turn are then recorded digitally. A wide variety of methods are known to the dental technician.
    It may also be that the patient has an implant in the jawbone and an abutment 5 is fixed on it. Such an abutment 5 is shown in FIG. 4. This abutment 5 has the shape of a stump on which the dental prosthesis Z (not shown here) can then be placed / cemented. The abutment 5 is then connected in a rotationally secure manner to the implant in the jawbone via its connecting region 6 and fixed to the implant by means of a screw. However, there is also the possibility that the denture Z is connected to the implant via a screw connection. It is also possible that a commercially available titanium base 7 is used as the metallic framework 1, onto which the veneer 3 is then added. Possible configurations of titanium bases 7 are shown in FIG. 5. These titanium bases 7 generally have a screw seat and can then be connected to the implant via a screw. Alternatively, the metallic framework 1 can also have a connection which is compatible with a titanium base 7/32. In such variants, it may then be necessary for the ceramic
    Facing 3 has a through hole, which then the
    Screw can be inserted to fix the denture Z in the patient's mouth.
    In principle, there are still many different ways to fix a denture Z in a patient's mouth. The fact that they are not all described here does not mean that the invention does not work in such a combination, but rather that these practices are known to a dental technician and not all need to be listed.
    LIST OF REFERENCE NUMBERS
    Z dentures
    S Kiln metallic framework
    Joining layer ceramic veneer
    veneering
    abutment
    connecting area
    titanium Base
    Innsbruck, February 24, 2017/32
    81179 22 / eh
    权利要求:
    Claims (17)
    [1]
    claims
    1. A method for producing a denture (Z), in particular crown, bridge or bar, with the steps
    - manufacture of a metallic framework (1),
    - producing a ceramic veneer (3),
    - applying at least one joining layer (2) to the metallic framework (1) and / or to the ceramic veneer (3),
    - Applying the ceramic veneer (3) to the metallic framework (1), the joining layer (2) being arranged between the metallic framework (1) and the ceramic veneer (3), and
    - Common firing of the metallic framework (1), the joining layer (2) and the ceramic veneer (3), whereby the joining layer (2) connects the metallic framework (1) with the ceramic veneer (3) integrally.
    [2]
    2. The method according to claim 1, with the subsequent steps:
    - Applying at least one ceramic veneer layer (4) to the ceramic veneer (3) and at least in regions
    - Common firing of the metallic framework (1), the joining layer (2), the ceramic veneer (3) and the veneer layer (4).
    [3]
    3. The method according to at least one of the preceding claims, wherein the metallic framework (1) and / or the ceramic veneer (3) are / is produced in a CNC processing machine.
    [4]
    4. The method according to at least one of the preceding claims, wherein the ceramic veneer (3) and / or the metallic framework (1) are / are densely sintered in a sintering furnace (S) before the application of the joining layer (2).
    [5]
    5. The method according to at least one of the preceding claims, wherein the metallic framework (1) consists of titanium or a titanium alloy, the
    21/32
    Joining layer (2) consists of, preferably silicate, glass ceramic and the veneering ceramic (3) consists of zirconium dioxide.
    [6]
    6. The method according to at least one of the preceding claims, wherein the thermal expansion coefficient of the joining layer (2) by a maximum of 2.0'10 ' 6 ' K · 1 , preferably by a maximum of '1.0-10 6 -K · 1 , of the Thermal expansion coefficient of both the metallic framework (1) and the ceramic veneer (3) differs.
    [7]
    7. The method according to at least one of the preceding claims, wherein the coefficient of thermal expansion of the joining layer (2) lies between the coefficient of thermal expansion of the metallic framework (1) and the coefficient of thermal expansion of the ceramic veneer (3).
    [8]
    8. The method according to at least one of the preceding claims, wherein the coefficient of thermal expansion of the joining layer (2) is at most 1.7-10 ' 6 -K · 1 lower than the coefficient of thermal expansion of the ceramic veneer (3).
    [9]
    9. The method according to at least one of the preceding claims, wherein the thermal expansion coefficient of the joining layer (2) deviates by a maximum of 1.5-10 ' 6 -K · 1 from the thermal expansion coefficient of the metallic framework (1).
    [10]
    10. The method according to at least one of the preceding claims, wherein the metallic frame (1) has a thermal expansion coefficient of 9.7-10 ' 6 -K · 1 .
    [11]
    11. The method according to at least one of the preceding claims, wherein the ceramic veneer (3) has a coefficient of thermal expansion of 10.0-10 ' 6 -K' 1 .
    [12]
    12. The method according to at least one of the preceding claims, wherein the joining layer (2) has a coefficient of thermal expansion of 10.0-10 ' 6 -K · 1 .
    22/32
    [13]
    13. The method according to at least one of the preceding claims, wherein the joining layer (2) consists of more than 60 percent by weight, preferably 60 to 68 percent by weight, of silicon dioxide and less than 12 percent by weight, preferably between 5 to 12 percent by weight, of aluminum oxide.
    [14]
    14. The method according to claim 13, wherein the joining layer (2) has a proportion of potassium oxide between 4 and 9 percent by weight and a proportion of sodium oxide between 5.5 and 12 percent by weight.
    [15]
    15. The method according to at least one of the preceding claims, wherein the joining layer (2) via a cover layer with the metallic framework (1) and / or with the ceramic veneer (3) is connected.
    [16]
    16. dentures (Z), in particular crown, bridge or bridge, produced in a method according to any one of claims 1 to 15, with
    - a metallic framework (1),
    - A ceramic facing (3) and
    - A joining layer (2) connecting the framework (1) and the veneer (3).
    [17]
    17. Dental prosthesis according to claim 16, wherein at least one veneer layer (4) is applied to the ceramic veneer (3) at least in regions.
    Innsbruck, February 24, 2017
    23/32
    Heinrich Steger
    81179
    24/32
    P (6.
    Heinrich Steger
    81179
    25/32
    Heinrich Steger
    81179
    26/32
    Heinrich Steger
    81179
    27/32 Austrian
    Patent Office
    类似技术:
    公开号 | 公开日 | 专利标题
    EP3453686B1|2020-12-30|Use of a lithium silicate glass ceramic with zro2 content
    EP3366260B1|2020-01-01|Method for producing a dental prosthetic
    WO2007028787A1|2007-03-15|Ceramic tooth replacement and method for the production thereof
    EP2765119B1|2021-07-28|Blank for dental purposes
    DE102005042091A1|2007-03-15|Ceramic dental prosthesis, preferably composite ceramic crown or bridge, comprises two independent components, which are manufactured by a computer-aided procedure and are connected by a ceramic connector mass
    DE102005023106A1|2006-11-16|Production of artificial denture part involves division of artificial denture part into first and further structural parts in automatic dismantling process according to construction algorithms, producing 3D data records of structural parts
    DE19852516A1|2000-05-25|Ceramic dental restoration
    EP3050856A1|2016-08-03|Lithium silicate diopside glass ceramic
    DE102015122861A1|2017-06-29|Method for producing a blank, blank and a dental restoration
    WO2017032745A1|2017-03-02|Lithium silicate low quartz glass ceramics
    DE102004010138B4|2006-04-06|Reinforced, pressable ceramic compositions for dental purposes
    WO2016142234A1|2016-09-15|Substance mixture, sprayable ceramic veneer composition, method for coating dental restorations of zirconium dioxide, and dental restorations of zirconium dioxide
    EP1167311B1|2004-04-14|Low sintering apatite glass ceramics
    DE102016119934A1|2018-05-03|Method for producing a blank, blank and a dental restoration
    DE102020103720A1|2021-08-19|Use of a blank with holder for the production of dental restorations
    EP2045218B1|2016-12-28|Glaze for coating of surfaces
    WO2007014571A1|2007-02-08|Glass-crystalline compound for the treatment of surfaces
    EP3733618A1|2020-11-04|Low-melting glass ceramic
    EP3189826A1|2017-07-12|Conditioning of the surface of dental components
    DE102015106424A1|2016-10-27|Process for producing dentures with a plastic core
    WO2020025795A1|2020-02-06|Multicolored blank for dental purposes
    DE102015204186A1|2016-09-15|Mixture of substances, method for producing a dental restoration and dental restoration
    DD278918A3|1990-05-23|CERAMIC MATERIAL WITH CORDIERITE CRYSTAL PHASE AND ITS APPLICATION
    同族专利:
    公开号 | 公开日
    EP3366260B1|2020-01-01|
    ES2781999T3|2020-09-09|
    AT519721B1|2019-02-15|
    EP3366260A1|2018-08-29|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    CH608183A5|1976-09-24|1978-12-29|Sumitomo Chemical Co|Porcelain-coated metal crown as dental prosthesis|
    DE3144859A1|1980-11-12|1982-08-12|Four Brain K.K., Hiroshima|Method of bonding metal and ceramic, prosthetic teeth made by this bonding method and composite primary plating materials for use in the bonding method|
    EP0055383A2|1980-12-09|1982-07-07|Etablissement Dentaire IVOCLAR|Base material for firing in order to prepare an intermediate layer between a high melting dental alloy and a tooth porcelain|
    US5314334A|1990-12-18|1994-05-24|American Thermocraft Corporation Subsidiary Of Jeneric/Pentron Incorporated|Dental procelain bond layer for titanium and titanium alloy copings|
    DE19714759A1|1997-04-10|1998-10-15|Castolin Sa|Dental prosthesis with good bond between metal oxide on metal core, suitable for partly automatic production|
    DE102005023106A1|2005-05-13|2006-11-16|Sirona Dental Systems Gmbh|Production of artificial denture part involves division of artificial denture part into first and further structural parts in automatic dismantling process according to construction algorithms, producing 3D data records of structural parts|
    WO2007028787A1|2005-09-05|2007-03-15|Ivoclar Vivadent Ag|Ceramic tooth replacement and method for the production thereof|
    US20120193823A1|2009-09-30|2012-08-02|Martin Goetzinger|Systems and methods for making layered dental appliances|
    DE102011051594A1|2011-07-06|2013-01-10|Smilden Biotechnology Co., Ltd.|Highly connected dental structure for dental prostheses, has ceramic layer which is applied on the inner and outer surfaces of metal cap using a plasma spray process|
    FR2318842B1|1975-07-21|1981-09-25|Sumitomo Chemical Co|DE102018128566A1|2018-11-14|2020-05-14|Bredent Gmbh & Co. Kg|Process for fitting a ceramic outer shell|
    CN109820610A|2019-01-31|2019-05-31|上海慧丰牙科技术有限公司|A kind of fixed denture and processing technology|
    EP3733617A1|2019-05-03|2020-11-04|VITA-ZAHNFABRIK H. Rauter GmbH & Co. KG|Low-melting glass ceramic|
    法律状态:
    优先权:
    申请号 | 申请日 | 专利标题
    ATA50152/2017A|AT519721B1|2017-02-24|2017-02-24|Process for producing a dental prosthesis|ATA50152/2017A| AT519721B1|2017-02-24|2017-02-24|Process for producing a dental prosthesis|
    EP18157873.3A| EP3366260B1|2017-02-24|2018-02-21|Method for producing a dental prosthetic|
    ES18157873T| ES2781999T3|2017-02-24|2018-02-21|Method for the manufacture of a dental prosthesis|
    [返回顶部]