• 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 planning a sintering of a dental prosthesis part the present invention relates to a method for planning the heat treatment of a dental prosthesis part (1), in which a 3d model (9) of the dental prosthesis part to be produced (1) already exists. a temperature profile (16) for the heat treatment of the dental prosthesis part (1) is automatically determined by a computer (17) according to the geometric parameters determined (10, 11, 12, 13) of the dental prosthesis part to be produced (1) and / or parameters of a particular material of the part of the dental prosthesis to be produced (1).
    公开号:BR112016012960B1
    申请号:R112016012960-1
    申请日:2014-12-18
    公开日:2021-04-27
    发明作者:Peter Fornoff；Christian Schmidt
    申请人:Sirona Dental Systems Gmbh；
    IPC主号:
    专利说明:

    FIELD OF THE INVENTION
    [001] The present invention relates to a method for planning the sintering of a dental prosthesis part, and a 3D model of the dental prosthesis part to be produced has already been designed. PREVIOUS TECHNIQUE
    [002] Various methods for planning sintering processes are known in the prior art. Before sintering in a sintering oven, the user can select a specific program with a temperature profile suitable for the part of the dental prosthesis to be produced, the user taking into account the materials used and the dimensions of the dental prosthesis part .
    [003] DE 10 2011 056 211 B3 describes equipment and a sintering method, particularly dental structures, a tray being covered by a closing element, the tray structure being connected to an inert gas supply. The heating rate, the maintenance temperature, as well as a cooling time can be adjusted manually.
    [004] EP 2 620 733 A1 describes a dental device, such as a dental oven with at least one operating program, with a memory and with at least one capturing device, such as a camera. The object can be captured by means of the camera and presented in the form captured by means of a display unit. Several predetermined reference objects are deposited in a database. If a certain number of characteristics of a reference object match the image of the captured object, a corresponding operation program is started.
    [005] US 2009/0079101 A1 describes a sintering furnace with a thermally insulated camera and a temperature measurement device. A temperature profile has a heating rate of 140 ° C per minute, a maintenance temperature of 1400 ° C and a cooling rate of 50 ° C per minute.
    [006] DE 10 2008 013 555 A1 describes a sintering oven for the production of dental prosthesis parts, and the sintering of the dental prosthesis parts is carried out along a sintering line. At the same time that it passes through this sintering line, the parts of dental prosthesis are exposed to different temperatures. The sintering line is thus divided into individual segments of the sintering line, which can be adjusted for different temperatures. The supports that transport the dental prosthesis parts are moved along the sintering line by means of a slide. Each segment of the sintering line can be adjusted to different temperatures. By these means, different temperature progressions for sintering different ceramics can be adjusted.
    [007] A disadvantage of this method is the fact that, due to operator errors, he can set up incorrect temperature profiles, which can lead to manufacturing defects in the part of the dental prosthesis to be produced. A temperature profile with a heating rate that is too high can, in the case of oxide ceramics, for example, cause cracks on the surface of the dental prosthesis part.
    [008] The present invention is based on the task of providing a method for planning a sintering in such a way that such operating errors are avoided. DESCRIPTION OF THE INVENTION
    [009] The invention relates to a method for planning the heat treatment of a dental prosthesis part, and a 3D model of the dental prosthesis part to be produced already exists. Depending on certain geometric parameters of the dental prosthesis part to be produced and certain parameters of the material of the dental prosthesis part to be produced, a temperature profile for heat treatment such as sintering, crystallization or vitrification of the dental prosthesis part is determined automatically by computer, and the material parameters of a material that was selected for the manufacture of the dental prosthesis part consist of thermal conductivity, resistance to thermal shock, heating speed and / or temperature limit value for the phase transformation of the material .
    [0010] In the case of an increase in the thermal conductivity of the material used, the dental prosthesis part can be sintered more quickly, so that the maintenance time of the temperature profile can be reduced.
    [0011] In the case of high resistance to thermal shock of the material, the heating rate can also be increased without causing damage to the dental prosthesis part during sintering.
    [0012] According to the present method, a theoretical maximum heating rate for the respective part of dental prosthesis can be established or determined. To determine this maximum heating rate, mechanical coefficients of the material in question can be used, such as a linear expansion coefficient, an elastic modulus, strength, Poisson's ratio, fracture resistance, initial crack length or form factor, as well as thermal capacity related to volume or heat conductivity, in addition to geometric parameters of the part of dental prosthesis.
    [0013] This method assumes that the dental prosthesis part has already been designed, so that a 3D model of the dental prosthesis part exists. The dental prosthesis part can, for example, be a complete prosthesis for an implant, a dental prosthesis, a complete crown, a partial crown, a bridge of several whole teeth or an inlay. Based on certain selection criteria, the appropriate temperature profile is determined depending on geometric parameters and / or material parameters of the selected material. Determining the temperature profile can, for example, be carried out by automatically selecting the temperature profile from multiple temperature profiles stored in a database or by computing an individual temperature profile. The temperature profile can contain at least one heating step or several heating steps, and it is crucial that a maximum heating rate is not exceeded; the rate of heating depends on the material used and substantially on the thickness of the wall of the dental prosthesis part. This could result in the formation of cracks on the surface of the dental prosthesis part or flaking of the upper layers of the dental prosthesis part. During the sintering process, the outer layer of the dental prosthesis part may shrink more quickly than the inner layers of it, resulting in mechanical stresses. After heating the dental prosthesis part according to the established heating speed, a maintenance temperature is maintained for a certain maintenance period, with a cooling phase following. The cooling phase, for example, can be started by opening the door of the used sintering furnace, so that cold air can flow into it. The maintenance temperature and the maintenance time are selected so that the part of the dental prosthesis to be produced is completely sintered, but that excessive sintering does not occur. In the case of excessive sintering, the grain size of the material to be sintered can exceed an established limit value, which can result in reduced resistance of the dental prosthesis part.
    [0014] This method has the advantage of excluding operational errors during manual selection of an appropriate temperature profile, thus avoiding manufacturing defects.
    [0015] An additional advantage of this method is the fact that, considering the geometric parameters and / or the parameters of the material, an appropriate temperature profile can be selected combining the shortest possible duration with the highest possible heating rate and the shortest possible maintenance time, so that the total duration of the heat treatment of the dental prosthesis part is reduced.
    [0016] Preferably, the geometric parameters of the dental prosthesis part can be maximum thickness of the lateral wall, maximum thickness of the occlusal wall, a ratio of maximum thickness of the occlusal wall to the maximum thickness of the lateral wall, maximum cross section of the part of dental prosthesis, total volume of the dental prosthesis part, maximum total length of the dental prosthesis part and / or maximum change in the cross section of the dental prosthesis part.
    [0017] The maximum thickness of the lateral wall refers to the thickness of the wall on the side of the dental prosthesis part, for example, on the labial surfaces of the incisors or on the buccal surfaces of the molars. The maximum thickness of the occlusal wall refers to the thickness of the wall of an occlusal surface of the part of the dental prosthesis. The maximum cross section of the dental prosthesis part refers to a cross section that is vertical in relation to the tooth axis of the dental prosthesis part.
    [0018] Based on these geometric parameters, a temperature profile is selected, with a certain heating rate and a certain maintenance time at a certain maintenance temperature being determined in particular.
    [0019] Preferably, the temperature profile can be determined so that, with the increase of the maximum thickness of the lateral wall, with the increase of the maximum thickness of the occlusal wall, with the increase of the maximum cross section of the component and / or with the increase in the total volume of the part of the dental prosthesis, the rate of heating of the temperature profile decreases, the time of maintenance of the temperature profile increases and / or the temperature of maintenance of the temperature profile decreases.
    [0020] As the wall thickness increases, the mechanical stresses during the sintering process also increase, so that the heating rate has to be reduced, to prevent the dental prosthesis part from being damaged.
    [0021] With an increase in the cross section or in the total volume of the dental prosthesis part, the maintenance time increases as it takes longer to fully sinter the component.
    [0022] The temperature profile can be advantageously determined so that with increasing heat conductivity and / or increasing resistance to thermal shock, the heating rate of the temperature profile increases.
    [0023] This allows the heating rate to be increased depending on the thermal conductivity and the thermal shock resistance of the higher material, so that the total sintering duration can be reduced.
    [0024] Preferably, the heat treatment may consist of sintering, crystallization, a combination of sintering and vitrification or a combination of crystallization and vitrification.
    [0025] Sintering can be applied with oxide ceramic, such as zirconium dioxide or aluminum oxide, as well as with non-precious metal alloys such as CoCrMo alloy.
    [0026] Crystallization is carried out particularly with glass ceramic with a system of lithium disilicate materials.
    [0027] Finishing sintering is performed on dental restoration components that are made from pre-sintered oxide ceramics, particularly zirconium dioxide and aluminum oxide. Metal pellets that are pressed from powder and pre-sintered, particularly from CoCrMo alloys, must also be sintered after having been further mechanically processed by grinding or grinding.
    [0028] All basic metallic or ceramic materials can be faceted or vitrified after sintering by means of additional combustion processes. As part of a so-called surface finish, painting can also be carried out together with vitrification, which could undergo combustion in the same kiln process.
    [0029] The glass-ceramic has the additional advantage that it can be crystallized, painted and vitrified in the same combustion process.
    [0030] Preferably, the material selected to produce a dental prosthesis part can be zirconium dioxide, and the dental prosthesis part to be produced can be an individual tooth, a complete crown, a partial crown or an inlay (inlay) ). The total volume of a part of a dental prosthesis can equal, at most, the volume of a molar, with the maximum thickness of the lateral wall and / or the range of the maximum thickness of the occlusal wall being below the limit value of 6 mm. In consideration of these factors, a first temperature profile for sintering is established having a heating rate between 100 ° C / minute and 400 ° C / minute, a maintenance temperature between 1500 ° C and 1600 ° C and a maintenance between 5 minutes and 10 minutes.
    [0031] Due to the relatively small thickness of the wall and the low total volume of the dental prosthesis part, a relatively high heating rate is possible, so that the total duration is reduced. The low total volume also allows the dental prosthesis part to be sintered more quickly, so that a relatively short maintenance time can be selected, which further shortens the total sintering duration. The first temperature profile makes rapid sintering possible for relatively small dental prosthesis parts.
    [0032] Preferably, the selected material can be zirconium dioxide, and the part of dental prosthesis to be produced is a bridge consisting of a maximum of 6 connected teeth or 6 individual teeth. Taking these factors into account, a second temperature profile for sintering is established, with a heating rate between 70 C / minute and 200 ° C / minute, a maintenance temperature between 1450 ° C and 1550 ° C and a maintenance between 20 minutes and 40 minutes.
    [0033] The second temperature profile is selected for dental prosthesis parts with a total volume of no more than six teeth, and a longer maintenance time is required for sintering the dental prosthesis part than for the first temperature profile.
    [0034] Preferably, the selected material may be zirconium dioxide, the part of the dental prosthesis to be produced comprising more than 6 individual teeth, with a third temperature profile being established having a heating rate between 10 ° C / minute and 70 ° C / minute, with a maintenance temperature between 1500 ° C and 1600 ° C and a maintenance time between 100 minutes and 140 minutes.
    [0035] The third temperature profile is selected for parts of relatively large dental prostheses with a total volume of more than six teeth, the heating rate being significantly reduced compared to the first temperature profile and the second profile of temperature, to prevent cracks from forming on the surface of the dental prosthesis part. Maintenance time is significantly increased compared to the first temperature profile and the second temperature profile, to ensure complete sintering across the entire dental prosthesis.
    [0036] Preferably, the selected material can be aluminum oxide (Al2O3), with a fourth temperature profile being established having a heating rate between 10 ° C / minute and 70 ° C / minute, with a maintenance temperature between 1500 ° C and 1600 ° C and a maintenance time between 100 minutes and 140 minutes.
    [0037] The fourth temperature profile is suitable for the aluminum oxide material, and, regardless of the size of the dental prosthesis part, the heating rate and the maintenance time are selected similarly to the third temperature profile.
    [0038] Preferably, the 3D model of the dental prosthesis part to be produced can be graphically presented by means of a display device, with certain sections of the 3D model being graphically marked; these sections exceed a certain limit value in relation to the thickness of the lip or occlusal wall.
    [0039] The display device can, for example, be a monitor, which graphically shows the 3D model drawn of the part of the dental prosthesis to be produced. These sections, in which the wall thickness exceeds the limit value determined, for example, 3 mm, are graphically marked. In this way, the user can recognize which sections of the 3D model are not compatible with the geometric parameters for the first temperature profile or the second temperature profile. The user, such as a dentist or dental technician, can thus properly adjust these marked sections.
    [0040] Preferably, the user can manually adjust the marked sections using the virtual tools or the marked sections can be automatically adjusted by the computer in such a way that these sections are below the limit value for the thickness of the lip or occlusal wall. In this way, sintering for the part of the dental prosthesis to be produced according to this adjusted 3D model can be performed with the use of the first temperature profile and not with the second temperature profile.
    [0041] Consequently, the user can adjust the marked areas in such a way that they are below the limit value for the wall thickness of, for example, 3 mm. In this way, the geometric parameters for the first temperature profile are satisfied, so that sintering can be performed using the first temperature profile, which results in a shorter total sintering duration compared to sintering with the second temperature profile .
    [0042] Preferably, the determination of the appropriate temperature profile can be carried out by selecting among several temperature profiles that are stored in a database.
    [0043] For example, the different temperature profiles can be saved in a memory arranged on a microcomputer that is integrated with the sintering furnace. Alternatively, this memory can also be integrated into a computer that is arranged outside the sintering furnace.
    [0044] The characteristics of the temperature profiles such as the heating rate, the maintenance time and / or the maintenance temperature can be graphically presented by means of a display unit. The display unit can, for example, be a display that is adjusted to the sintering furnace. The choice is then made automatically by a computer, and the characteristics of the selected temperature profile can be graphically visualized.
    [0045] In a preferential scenario, the determination of the appropriate temperature profile can be performed by computing an individual temperature profile that is calculated taking into account the geometric parameters and / or the material parameters of the part of the dental prosthesis to be be produced.
    [0046] Consequently, this allows an individual temperature profile to be calculated taking into account the geometric parameters and / or the material parameter. In this context, mathematical methods known as interpolation can be used.
    [0047] The invention additionally relates to a system for carrying out a method for planning the thermal treatment of a part of dental prosthesis, by means of a sintering furnace, a system comprising a computer, being a 3D model of the part of dental prosthesis to be produced already exists. Depending on certain geometric and material parameters of the dental prosthesis part to be produced, a temperature profile for sintering the dental prosthesis part can be automatically established by a computer.
    [0048] In this way, the system allows the method described above to be performed, and the computer automatically determines an appropriate temperature profile for the respective part of the dental prosthesis depending on the geometric and material parameters.
    [0049] An advantage of this system is the fact that operational errors, which would probably occur when users such as dentists or dental technicians manually select an appropriate temperature profile, can be avoided.
    [0050] Preferably, the system can have a display unit, and the 3D model of the part of the dental prosthesis to be produced can be graphically presented using a display unit, and certain sections of the 3D model can be graphically displayed. marked by exceeding a certain limit value in relation to the thickness of the lip or occlusal wall.
    [0051] By marking the sections that do not conform to certain geometric parameters, such as the wall thickness, for the first temperature profile, the user can better evaluate the measurements of these sections and the necessary adjustments resulting from the 3D model.
    [0052] Preferably, the system can be equipped with operational means, the user can manually adjust the marked sections using the operational means through virtual tools or the marked sections can be automatically adjusted by the computer so that these sections are below limit value of 6 mm for the thickness of the lip or occlusal wall. In this way, sintering for the part of the dental prosthesis to be produced according to this adjusted 3D model can be performed with the use of the first temperature profile and not with the second temperature profile.
    [0053] Through this adjustment of the 3D model, sintering can be performed using the first temperature profile instead of the second temperature profile, so that the total sintering duration is shortened.
    [0054] Preferably, the system can be equipped with a memory, and the determination of the appropriate temperature profile is carried out by selecting among several temperature profiles that are stored in a database in memory.
    [0055] In a preferential scenario, the determination of the appropriate temperature profile can be performed by computing an individual temperature profile by the computer, and the individual temperature profile is calculated taking into account the geometric parameters and / or the material of the dental prosthesis part to be produced. BRIEF DESCRIPTION OF THE DRAWINGS
    [0056] The invention is explained with reference to the drawings. In the drawings,
    [0057] Figure 1 shows an outline to illustrate the present method,
    [0058] Figure 2 shows a 3D model of the dental prosthesis part with the marked areas,
    [0059] Figure 3 shows several temperature profiles to perform sintering. EXEMPLIFYING MODALITIES
    [0060] Figure 1 shows a sketch illustrating the present method for planning the heat treatment of the dental prosthesis part 1 with the sintering furnace 2. The sintering furnace is provided with insulation elements 3 and heating elements 4 to regulate the temperature inside the combustion chamber 5. The heat treatment of the dental prosthesis part 1, such as sintering, crystallization or vitrification, is carried out starting with a first stage, in which the chamber 5 is heated by the heating elements 4. After a certain temperature load, for example, 300 ° C, is reached, the chamber 5 is opened in a second stage, during which the base 6 is moved to the final position 7. In a third stage, the user, such as a dentist or technician dental, position the dental prosthesis part 1 to be sintered on base 6. In a fourth stage, the chamber closes again, and the base is moved to an upper end position, indicated by arrows 8. In a fifth stage, the chamber 5 is further heated by the heating elements 4 until a heating temperature is reached and this maintenance temperature is maintained for a certain maintenance period. A cooling phase follows a sixth stage. The cooling phase can be started, for example, by turning off the heating elements or additionally by opening the chamber 5 by moving the base to the lowest end position 7.
    [0061] At the same time as the present method is used to plan the thermal treatment, the 3D model 9 of the dental prosthesis part 1 is now available. The project of the dental prosthesis part is already concluded. The 3D model 9 is presented graphically through the display unit 39, as a monitor. The 3D model 9 has certain geometric parameters of the dental prosthesis part 1 such as a side wall thickness 10, an occlusal wall thickness 11, a maximum cross section 12, indicated by a dashed line, as well as a total volume 13. In addition , the material used to create the part of the dental prosthesis to be produced was already determined during the project. The materials used can include, for example, oxide ceramics, such as zirconium dioxide or aluminum oxide, as well as non-precious metal alloys such as a CoCrMo alloy. The maximum cross section 12 of the dental prosthesis part can be determined vertically to the axis of tooth 14, which can correspond to an axis of symmetry of the dental prosthesis part. The thickness of the side wall 10 can, for example, be determined vertically to the axis of the tooth 14 in the labial or buccal area of the dental prosthesis part. The thickness of the occlusal wall 11 can, for example, be determined parallel to the tooth axis 14 on the occlusal surface 15 of the 3D model 9. Using geometric parameters 10, 11, 12, 13, as well as the material parameters, a computer 17 automatically determines a suitable temperature profile 16.
    [0062] Computer 17 can be a microcomputer, a microchip or an ordinary personal computer. The computer 17 can be arranged externally, outside the sintering furnace 2. Alternatively, the computer 17 together with the display unit 39 can be integrated with the sintering furnace 2.
    [0063] Temperature profile 16 is represented as a temperature graph 17 as a function of time 18. In a first stage 19, chamber 5 is heated using the first heating rate to reach a pre-drying temperature 20, in a second stage 21, the pre-drying temperature is maintained for a first maintenance time, in a third stage 22, the temperature inside the chamber 5 is heated to reach a charge temperature of, for example, 300 ° Ç. In a fourth stage, the chamber 5 is loaded with a dental prosthesis part 1 to be sintered, so that the temperature is slightly reduced. In a fifth stage 23, the temperature in the chamber 5 rises according to a second heating rate, until a second maintenance temperature 24 is reached. In a sixth stage 25, the heating elements 4 are controlled in such a way that the temperature maintenance 24 is maintained for the duration of a certain maintenance time. In a seventh phase 26, the cooling of the dental prosthesis part 1 follows. In this way, computer 17 determines the appropriate temperature profile 16 depending on the geometric parameters, particularly on the maximum thickness of the side wall 10, the maximum thickness of the occlusal wall 11 and the total volume 13, as well as depending on the parameters of the selected material. In this way, the heating rates for the heating phases 19, 23, the maintenance temperatures 20, 24 and the maintenance times for the phases 21, 25 are set in particular.
    [0064] During a subsequent plausibility check, it is then possible to examine whether the 3D model 9 projected from the dental prosthesis part 1 satisfies certain requirements related to geometric parameters, such as lateral or occlusal wall thickness. Sections that do not fall within the determined limit values, such as sections 27 and 28, which are indicated by a dashed line, can then be marked. For example, sections 27, 28 can be marked because they exceed a limit value of 6 mm in relation to the thickness of the occlusal wall. Subsequently, the marked sections 27 and 28 can be manually changed by the user using a virtual tool 29, such as a cursor or automatically by the computer 17, so that the limit values related to the geometric parameters are met. The control of the virtual tool 29 is carried out through connected input means, such as the use of a keyboard 30 or a mouse 31. When adjusting or forming 3D model 9, an adjusted 3D model 32 is created, which is demonstrated by a line dashed. The adjusted 3D model 32 is then used by a CAM 33 processing machine to create the dental prosthesis part 1 to be sintered from a pellet 34 in a fully automated process. After the dental prosthesis part 1 to be sintered has been produced, sintering in the sintering furnace 2 is carried out as described above.
    [0065] Thus, this method has the advantage that even before producing the dental prosthesis part by a CAM 33 processing machine and before sintering dental prosthesis part 1 in the sintering furnace 2, an adequate temperature profile 16 can be determined and a plausibility check, as well as a possible adjustment of the 3D model 9 can be performed.
    [0066] The temperature profile 16 can, for example, be established by selecting from a series of temperature profiles that are stored in a memory 35. This memory 35 is integrated into the computer 17. As an alternative, the temperature profiles can be stored in a second memory 36, which is integrated with the sintering furnace 2.
    [0067] The appropriate temperature profile can also be established by computing an individual temperature profile, which is calculated by the computer 17.
    [0068] The present method for planning the heat treatment can also be performed for various parts of dental prostheses and various heat treatments before sintering begins. To do this, an overview of orders can be created comprising several orders. An order can thus comprise identification data such as the patient's name, the type of dental prosthesis part, such as a full crown, a partial crown or a bridge, the material for creating the dental prosthesis part, the type of heat treatment, such as sintering, crystallization or vitrification, and the type of suitable temperature profile. Orders with this identification data can, for example, be displayed on a display 37 that is integrated with the sintering furnace 2. As an alternative, orders with the identification data can also be displayed on display unit 39. Before To perform sintering, the user can select the respective order with the designated temperature profile using the control panel 38. After that, the sintering is carried out automatically with a suitable temperature profile.
    [0069] Figure 2 shows the 3D model 9 of the dental prosthesis part 1 of Figure 1, with sections 27 and 28 being marked because they exceed a limit value of, for example, 6 mm in relation to the thickness of the occlusal wall.
    [0070] After adjusting or forming 3D model 9, which is demonstrated with a dashed line, an adjusted 3D model 32 is created. The adjusted 3D model 32 is then used to create the dental prosthesis part 1 using the CAM 33 processing machine of Figure 1.
    [0071] Figure 3 shows several temperature profiles to perform sintering, with temperature 17 in ° C being demonstrated as a function of time 18 in minutes. A first temperature profile 40 has a heating rate 41 of 100 ° C / min, a maintenance temperature 42 of 1580 ° C and a maintenance time 43 of 6 minutes. A second temperature profile 44 has a heating rate 45 of 100 ° C / min, a maintenance temperature 46 of 1510 ° C and a maintenance time 47 of 30 minutes. A third temperature profile 48, indicated by a dashed and dotted line, has a heating rate 49 of 25 ° C / min, a maintenance temperature 50 of 1510 ° C and a maintenance time 51 of 120 minutes. A fourth temperature profile 52, indicated by a dashed line, has a pre-drying phase 53, the temperature being raised to reach the pre-drying temperature 54 and is maintained for 20 minutes. Thereafter, the heating phase continues with a heating rate 55 of 100 ° C / minute to a maintenance temperature 56 of 1510 ° C. This maintenance temperature 56 is then maintained for a maintenance time 57 of 30 minutes, followed by a cooling phase. A fifth temperature profile 58 has a heating rate 59 of 300 ° C / min, a maintenance temperature 60 of 1580 ° C and a maintenance time of 6 minutes.
    [0072] The first temperature profile 40 is particularly suitable for small parts of dental prosthesis with a small wall thickness of, for example, less than 6 mm, and a small total volume, so that the high heating rate 41 and the short maintenance time 43 of 6 minutes allows short-term sintering. The second temperature profile 44 is suitable for medium to large dental prosthesis parts with a maximum wall thickness of more than 6 mm and consisting of no more than six individual teeth. The third temperature profile 48 is suitable for large dental prosthetic parts with bridges consisting of more than six individual teeth. The fourth temperature profile 52 is suitable for materials that require pre-drying before sintering.
    [0073] The 3D model 9 of Figure 1 and Figure 2 can, therefore, be formed by the user or automatically, provided that the requirements or limit values for a given temperature profile are satisfied. Figure 2 shows that the 3D model 9 has been adjusted in such a way that the thickness of the occlusal wall 11 does not exceed a limit value of 6 mm. In this way, sintering for the dental prosthesis part 1 to be produced according to this adjusted 3D model 32 can be performed using the first temperature profile 40 instead of the second temperature profile 44. The advantage of this adjustment is in the fact that that the duration of sintering is reduced. List of reference numbers 1 Dental prosthesis part 2 Sintering oven 3 Insulation element 4 Heating element 5 Combustion chamber 6 Base 7 Final position 8 Arrow 9 3D model 10 Sidewall thickness 11 Occlusal wall thickness 12 Cross section 13 Total volume 14 Tooth axis 15 Occlusion surface 16 Temperature profile 17 Computer 18 Time 19 First stage 20 Pre-drying temperature 21 Second stage 22 Third stage 23 Fifth stage 24 Maintenance temperature 25 Sixth stage 26 Seventh stage 27 Section 28 Section 29 Virtual tool 30 Keyboard 31 Mouse 32 Adjusted 3D model 33 CAM processing machine 34 Pellet 35 Memory 36 Second memory 37 Display 38 Control panel 39 Display unit 40 First temperature profile 41 Heating rate 42 Maintenance temperature 43 Maintenance temperature 44 Second temperature profile 45 Heating rate 46 Maintenance temperature 47 Maintenance temperature 48 Third temperature profile temperature 49 Heating rate 50 Maintenance temperature 51 Maintenance temperature 52 Fourth temperature profile 53 Pre-drying phase 54 Pre-drying temperature 55 Heating rate 56 Maintenance temperature 57 Maintenance temperature 58 Fifth temperature profile 59 heating 60 Maintenance temperature
    权利要求:
    Claims (19)
    [0001]
    1. Method for planning a heat treatment of a dental prosthesis part (1), and a 3D model (9) of the dental prosthesis part (1) to be produced already exists, characterized by the fact that, depending on certain parameters geometries (10, 11, 12, 13) of the dental prosthesis part to be produced (1) and of certain material parameters of the dental prosthesis part to be produced (1), a temperature profile (16) for the heat treatment of the dental prosthesis part (1) is automatically determined by means of a computer (17), and the material parameters of a material selected to produce the dental prosthesis part (1) are heat conductivity, shock resistance electrical, a maximum heating rate and / or a temperature limit value for a phase transformation of the material.
    [0002]
    2. Method, according to claim 1, characterized by the fact that the geometric parameters (10, 11, 12, 13) of the dental prosthesis part (1) are a maximum thickness of the side wall (10), a maximum thickness of the occlusal wall (11), a ratio of the maximum thickness of the occlusal wall (11) to the maximum thickness of the lateral wall (10), a maximum cross section (12) of the dental prosthesis part (1), a total volume ( 13) of the dental prosthesis part (1), a maximum total length of the dental prosthesis part (1) and / or a maximum change in the cross section of the dental prosthesis part (1).
    [0003]
    3. Method according to claim 2, characterized by the fact that the temperature profile (16) is determined so that, with the increase in the maximum thickness of the side wall (10), with the increase in the maximum thickness of the wall occlusal (11), with the increase in the maximum cross section of the component and / or with the increase in the total volume (13) of the dental prosthesis part (1), a heating rate (41, 45, 49, 55, 59) of the temperature profile (16) decreases, a maintenance time (43, 47, 51, 57) of the temperature profile (16) increases and / or a maintenance temperature (42, 46, 50, 56, 60) of the profile temperature (16) decreases.
    [0004]
    4. Method according to claim 1, characterized by the fact that the temperature profile (16) is determined so that, when there is an increase in heat conductivity and / or an increase in resistance to thermal shock, a rate heating (41, 45, 49, 55, 59) of the temperature profile (16) increases.
    [0005]
    Method according to any one of claims 1 to 4, characterized in that the heat treatment is a sintering, a crystallization, a combination of a sintering and a vitrification or a combination of a crystallization and a vitrification.
    [0006]
    6. Method, according to any one of claims 1 to 5, characterized by the fact that the material selected for the production of the dental prosthesis part (1) is zirconium dioxide (ZrO2), with the dental prosthesis a to be produced (1) is an individual tooth, a complete crown, at least a partial crown or at least one inlay (inlay), the total volume (13) of the dental prosthesis part (1) at most corresponding to the volume of one molar, with the maximum thickness of the lateral wall (10) and / or the maximum thickness of the occlusal wall (11) being below a limit value of 6 mm, with a first temperature profile (40) being established to sinter at a heating rate (41) between 100 ° C / minute and 400 ° C / minute, with a maintenance temperature (42) between 1500 ° C and 1600 ° C and a maintenance time (43) between 5 minutes and 10 minutes.
    [0007]
    7. Method according to any one of claims 1 to 5, characterized by the fact that the selected material is zirconium dioxide (ZrO2), the part of the dental prosthesis to be produced being a bridge with a maximum of 6 connected teeth or at most 6 individual teeth or partial crowns, with a second temperature profile (44) being established for sintering with a heating rate (45) between 70 ° C / minute and 200 ° C / minute, with a temperature of maintenance (46) between 1450 ° C and 1550 ° C and a maintenance time (47) between 20 minutes and 40 minutes.
    [0008]
    8. Method according to any one of claims 1 to 5, characterized by the fact that the selected material is zirconium dioxide (ZrO2), with the part of the dental prosthesis to be produced comprising more than 6 individual teeth, being that a third temperature profile (48) is established for sintering with a heating rate (49) between 10 ° C / minute and 70 ° C / minute, with a maintenance temperature (50) between 1500 ° C and 1600 ° C and a maintenance time (51) between 100 minutes and 140 minutes.
    [0009]
    9. Method according to any one of claims 1 to 5, characterized by the fact that the selected material is aluminum oxide (Al2O3), with a fourth temperature profile (52) being determined for sintering with a rate of heating (55) between 10 ° C / minute and 70 ° C / minute, with a maintenance temperature (56) between 1500 ° C and 1600 ° C and a maintenance time (57) between 100 minutes and 140 minutes.
    [0010]
    10. Method according to any one of claims 1 to 9, characterized by the fact that the 3D model (9) of the part of the dental prosthesis to be produced (1) can be graphically represented by means of a display unit (39 ), and certain sections (27, 28) of the 3D model (9) can be graphically marked, which exceed a certain limit value in relation to the thickness of the labial wall or the thickness of the occlusal wall (11).
    [0011]
    11. Method, according to claim 10, characterized by the fact that the user adjusts the marked sections (27, 28) manually using virtual tools (29) or the marked sections (27, 28) are automatically adjusted by means of the computer (17) in such a way that the limit value for the thickness of the lip wall (10, 11) or the thickness of the occlusal wall (11) are below, so that for the part of the dental prosthesis to be produced (1) adjusted accordingly, sintering can be carried out with the first temperature profile (40) instead of the second temperature profile (44).
    [0012]
    12. Method according to any one of claims 1 to 11, characterized in that the determination of the appropriate temperature profile (16) occurs through a choice of a plurality of temperature profiles (40, 48, 52, 58 ) that are stored in a database.
    [0013]
    13. Method according to any one of claims 1 to 11, characterized by the fact that the determination of the appropriate temperature profile (16) occurs by computing an individual temperature profile that is calculated taking into account the geometric parameters and / or the material parameters of the part of the dental prosthesis to be produced (1).
    [0014]
    14. System for carrying out a method for planning a heat treatment of a part of dental prosthesis (1) by means of a sintering furnace (2) comprising a computer (17), with a 3D model (9) of the prosthesis part to be produced (1) already exists, characterized by the fact that, depending on certain geometric parameters (10, 11, 12, 13) of the part of the dental prosthesis to be produced (1) and of certain material parameters of the part of dental prosthesis to be produced (1), a temperature profile (16) for sintering the dental prosthesis part (1) can be automatically determined by means of the computer (17), and the material parameters of a material selected for producing the dental prosthesis part (1) are a heat conductivity, a thermal shock resistance, a maximum heating rate and / or a temperature limit value for a phase transformation of the material.
    [0015]
    15. System according to claim 14, characterized by the fact that the geometric parameters (10, 11, 12, 13) of the dental prosthesis part (1) are a maximum thickness of the side wall (10), a maximum thickness of the occlusal wall (11), a ratio of the maximum thickness of the occlusal wall (11) to the maximum thickness of the lateral wall (10), a maximum cross section (12) of the dental prosthesis part, a total volume (13) of the dental prosthesis part (1), a maximum total length of the dental prosthesis part (1) and / or a maximum change in the cross section of the dental prosthesis part.
    [0016]
    16. System, according to claim 14 or 15, characterized by the fact that the system has a display unit (39), and the 3D model (9) of the part of the dental prosthesis to be produced (1) can be graphically represented by the display unit (39), and certain sections (27, 28) of the 3D model (9) can be graphically marked, which exceed a certain limit value in relation to the thickness of the lip wall or in relation to the thickness of the occlusal wall.
    [0017]
    17. System, according to claim 16, characterized by the fact that the system has operational means (30, 31), the user being able to adjust the marked sections (27, 28) manually using the operating elements (30, 31) by means of virtual tools (29) or marked sections (27, 28) are automatically adjusted by means of the computer (17) in such a way that the limit value for the thickness of the lip wall or the thickness of the occlusal wall (11 ) are below, so that for the part of dental prosthesis to be produced according to this, sintering can be performed with the first temperature profile (16) instead of the second temperature profile (16).
    [0018]
    18. The system according to any one of claims 14 to 17, characterized by the fact that the system has a memory (35), the determination of the appropriate temperature profile (16) taking place by choosing from a plurality of temperature profiles (16, 40, 48, 52, 58) that are stored in a database in memory (35).
    [0019]
    19. Method according to any one of claims 14 to 17, characterized by the fact that the determination of the appropriate temperature profile (16) occurs by computing an individual temperature profile (16) by means of the computer (17 ), and the individual temperature profile (16) is calculated individually taking into account the geometric parameters (10, 11, 12, 13) and / or the material parameters of the dental prosthesis part (1) to be produced .
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    同族专利:
    公开号 | 公开日
    EP3082643A1|2016-10-26|
    DE102013226497A1|2015-06-18|
    JP6846198B2|2021-03-24|
    CN105813593A|2016-07-27|
    DK3082643T3|2019-08-12|
    US20160317257A1|2016-11-03|
    CN105813593B|2019-09-10|
    AU2014368622A1|2016-06-16|
    AU2014368622B2|2019-01-31|
    KR102027418B1|2019-11-04|
    CA2934416A1|2015-06-25|
    JP2016540562A|2016-12-28|
    EP3082643B1|2019-05-22|
    US10939980B2|2021-03-09|
    WO2015091744A1|2015-06-25|
    KR20160099543A|2016-08-22|
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    法律状态:
    2020-04-28| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2021-02-09| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2021-04-27| B16A| Patent or certificate of addition of invention granted|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 18/12/2014, OBSERVADAS AS CONDICOES LEGAIS. |
    优先权:
    申请号 | 申请日 | 专利标题
    DE102013226497.6|2013-12-18|
    DE102013226497.6A|DE102013226497A1|2013-12-18|2013-12-18|Method for planning a sintering of a tooth replacement part|
    PCT/EP2014/078387|WO2015091744A1|2013-12-18|2014-12-18|Method for planning a sintering of a dental prosthesis part|
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