JP6916593B2 - Zirconia sintered body and dental products - Google Patents

Description

The present invention relates to a zirconia sintered body. The present invention also relates to a dental product containing a zirconia sintered body.

In recent years, as dental products for dentistry (prostheses such as coated crowns, crowns, crowns, and insert teeth), from the viewpoint of aesthetics and safety, instead of metal, sintered zirconia (zirconia) particles (zirconia) Ceramic materials such as sintered body) are used.

Patent Document 1 discloses a block member for producing a dental prosthesis. The block member described in Patent Document 1 is a ceramic presintered (temporarily baked) at a temperature of 900 ° C. to 1000 ° C. When a prosthesis is produced using the block member described in Patent Document 1, after the molded product is produced from the block member by cutting, the molded product is finish-sintered in order to obtain the required dimensions and final hardness. NS.

JP-A-2007-31453539

The following analysis is given from the point of view of the present invention.

When the prosthesis is made of a sintered body of a ceramic material that can be directly machined, such as a glass-ceramic material, the prosthesis is made after making a block of the sintered body of the glass-ceramic material. It is formed into a predetermined shape by direct machining (for example, cutting). In this case, sintering after molding may not be necessary.

On the other hand, the conventional zirconia sintered body has high strength, and if the zirconia sintered body is directly machined, the cutting tool is immediately damaged and it is not profitable. Therefore, when producing a prosthesis with a conventional zirconia sintered body, first, a block in a state where the zirconia particles are not sintered (temporarily baked body) such as the block member described in Patent Document 1 is produced. Has been done. Next, the prosthesis is formed by machining the block. Then, by firing the molded body of the calcined body thus produced under sintering conditions, a prosthesis as a zirconia sintered body is produced.

However, the method for producing a prosthesis of a zirconia sintered body as described above has the following problems. When treating a patient with a zirconia sintered prosthesis, the dentist first examines the patient to determine the shape of the prosthesis. Next, a dental technician molds the zirconia calcined body into the shape, and then the molded body is fired to prepare a prosthesis of the zirconia sintered body. However, in order to turn the zirconia calcined body into a zirconia sintered body, it is necessary to calm the calcined body at a temperature of, for example, 1400 ° C. or higher. Such high-temperature firing requires time and equipment. Therefore, it is difficult to perform the process from molding to sintering in a dental clinic in several hours. Therefore, it will take several days from the examination to determine the shape of the prosthesis to the examination to treat with the completed prosthesis. That is, with this method, the patient cannot complete the treatment within the day of the visit and must return to the hospital a few days later.

Further, when the zirconia calcined body becomes a zirconia sintered body, the calcined body usually shrinks by about 20%. Although the calcined body is formed assuming this shrinkage, it may not be possible to accurately match the shape of the sintered body to be the prosthesis to the originally planned shape.

Therefore, in order to shorten the production time of the prosthesis and to produce the prosthesis with high accuracy, the zirconia sintered body is directly processed to form the prosthesis instead of processing the zirconia calcined body. It is desired to do. For this purpose, a zirconia sintered body that is easier to machine is required.

According to the first aspect of the present invention, a partially stabilized zirconia sintered body containing 5 mol% to 8 mol% yttria as a stabilizer is provided. The zirconia sintered body has an average crystal grain size of 5 μm or more.
As a modification of the first viewpoint, it is a partially stabilized zirconia sintered body containing 5 mol% to 7.5 mol% yttria as a stabilizer and has an average crystal grain size of 5 μm or more and 10.50 μm or less. , Zirconia sintered body is provided.
As a further modification of the first viewpoint, a partially stabilized zirconia sintered body containing 5 mol% to 7.5 mol% yttria as a stabilizer having an average crystal grain size of 5 μm or more and 10.50 μm or less. has, outside of the translucent [Delta] L of the sintered body is expressed as [Delta] L _1, the inside of the translucent [Delta] L of the sintered body is represented as [Delta] L _2, below the rate of change from [Delta] L ₁ to [Delta] L ₂ Formula:
When expressed in the rate of change of _{ΔL] = (ΔL 2 -ΔL 1} ) / ΔL 1 × 100, the rate of change of [Delta] L is -15% or more, however, the the external, depth from the outer surface during sintering The inside is a part deeper than 4 mm from the outer surface, and the chromaticity (color) in the ^{inner and outer L *} a ^* b ^{* color system (JISZ8781).} for L ^* value of space), using the F11 as the light source, the L ^* values obtained by measuring the background of the sample in the white and the first L ^* value, the same samples were measured first in the L ^* value, when the L ^* value of the background of the sample were measured in the black and the second L ^* value, [Delta] L is a value obtained by deducting the second L ^* value from the first L ^* value, zirconia sintered Bounds are provided.

According to the second aspect of the present invention, there is provided a dental product comprising the zirconia sintered body according to the first aspect.

According to the zirconia sintered body of the present invention, the life of the tool for machining can be extended. As a result, the cost for producing the dental product can be reduced.

According to the zirconia sintered body of the present invention, a dental product can be directly produced from the zirconia sintered body. As a result, the dental product can be produced in a short time after the shape and dimensions of the dental product are determined, as compared with the case where the dental product is produced from the calcined body. Moreover, since it is not necessary to consider shrinkage during sintering, it is possible to manufacture a dental product with high dimensional accuracy.

According to the dental product of the present invention, the patient can complete the treatment on the day of the visit. Patients can also be treated with dental products that are more suited to their oral environment.

Schematic perspective view of the zirconia sintered body. The schematic diagram which shows the measurement method of chromaticity (color space). Schematic perspective view of dental products.

In the following description, the drawing reference reference numerals are added for the purpose of understanding the invention, and are not intended to be limited to the illustrated aspects. Further, the shapes, dimensions, scales, etc. shown in the drawings do not limit the invention to the forms shown in the drawings. In each embodiment, the same elements are designated by the same reference numerals.

Preferred forms of each of the above viewpoints are described below.

According to the preferred form of the first viewpoint, the average crystal grain size is 7 μm or more.

According to the preferred embodiment of the first viewpoint, the average crystal grain size is 8 μm or more.

According to the preferred form of the first viewpoint, the zirconia sintered body contains 6 mol% to 7.5 mol% yttria as a stabilizer.

According to the preferred embodiment of the first viewpoint, the translucency ΔL outside the sintered body _{is expressed as ΔL 1} , the translucency ΔL inside the sintered body is expressed as _{ΔL 2, and ΔL 1} to ΔL ₂ When the rate of change to is expressed by the following equation: [rate of change of ΔL] = (ΔL _{2 -ΔL 1} ) / ΔL ₁ × 100, the rate of change of ΔL is −15% or more. However, the outside is a portion from the outer surface at the time of sintering to a depth of 4 mm. The inside is a portion deeper than 4 mm from the outer surface. For ^{L *} value of the internal and external ^L * ^a * ^{b *} chromaticity in the color system (JISZ8781) (color space), the ^{L *} value of the background of the sample was measured in the white and the first ^{L *} value, For the same sample for which the first L ^* value was measured, when the background of the sample is black and the measured L ^* value is the second L ^* value, ΔL is the second from the ^{first L * value.} It is the value after deducting the L ^{* value.}

According to the preferred form of the first viewpoint, the zirconia sintered body has a cross section of 900 mm ² or less. The shortest transfer length in the cross section is 30 mm or less.

According to the preferred form of the first viewpoint, the zirconia sintered body has a hexahedral or cylindrical shape.

According to the preferred embodiment of the second aspect, the dental product further comprises an attachment for attachment to the processing apparatus. The fixture is joined to the zirconia sintered body.

According to the preferred form of the second viewpoint, the zirconia sintered body has a hexahedral or cylindrical shape.

According to the preferred form of the second viewpoint, the zirconia sintered body has a crown shape.

The zirconia sintered body according to the first embodiment of the present disclosure will be described. The zirconia sintered body of the present disclosure is a sintered body in _{which partially stabilized zirconia crystal particles containing zirconium oxide (ZrO 2} ; zirconia) and a stabilizer thereof are mainly sintered, and the partially stabilized zirconia is used as a matrix phase. Have as. In the zirconia sintered body of the present disclosure, the main crystal phase of zirconia is at least one of a tetragonal system and a cubic system. Zirconia may contain both tetragonal and cubic systems. It is preferable that the zirconia sintered body does not substantially contain a monoclinic crystal system at the stage where the hydrothermal treatment test has not been performed.

The zirconia sintered body of the present disclosure includes not only a sintered body obtained by sintering molded zirconia particles under normal pressure or non-pressurization, but also HIP (Hot Isostatic Pressing) treatment or the like. It also includes sintered bodies that have been densified by high-temperature pressurization.

Examples of the stabilizer in partially stabilized zirconia include calcium oxide (CaO), magnesium oxide (MgO), yttrium oxide (Y ₂ O ₃ ) (hereinafter referred to as “yttria”), cerium oxide (CeO ₂ ) and the like. Oxides include. In order to increase the transparency of the zirconia sintered body, it is more preferable to use yttria. When yttria is used as the stabilizer, the content of yttria is preferably 4 mol% to 8 mol% with respect to partially stabilized zirconia, for example. According to this content, the phase transition to monoclinic crystals can be suppressed and the transparency of the zirconia sintered body can be enhanced. Further, the yttria content is more preferably 5.5 mol% or more with respect to the partially stabilized zirconia in order to increase the transparency. The yttria content is more preferably 7.5 mol% or less with respect to the partially stabilized zirconia in order to maintain the strength. The content of the stabilizer in the zirconia sintered body can be measured by, for example, inductively coupled plasma (ICP) emission spectroscopic analysis, fluorescent X-ray analysis, or the like. Zirconia partially stabilized by adding a stabilizer is called partially stabilized zirconia (PSZ; Partially Stabilized Zirconia).

In the zirconia sintered body, it is preferable that the stabilizer is uniformly distributed. That is, in the zirconia sintered body, it is preferable that the content of the stabilizer is constant. For example, in the zirconia sintered body, it is preferable not to change the content of the stabilizer stepwise or partially. This is because if the content of the stabilizer is partially different, the shrinkage rate at the time of sintering will be different, and defects will occur in the zirconia sintered body. The variation of the stabilizer is preferably 1 mol% or less, and more preferably 0.5 mol% or less.

The zirconia sintered body preferably contains components other than the colorant and the fluorescent agent to the extent that the transparency described later is not impaired. For example, the content of components other than the colorant and the fluorescent agent is preferably less than 1 part by mass and less than 0.5 part by mass with respect to 100 parts by mass of the total mass of zirconia and the stabilizer. More preferably, it is more preferably less than 0.1 parts by mass, and further preferably not substantially contained. For example, the zirconia sintered body may be _{substantially free of aluminum oxide (Al 2} O ₃ ; alumina) (for example, 0 parts by mass).

In the zirconia sintered body, the crystal grain size of zirconia is preferably 1.5 μm or more, preferably 3 μm or more, more preferably 5 μm or more, more preferably 7 μm or more, and more preferably 8 μm or more. More preferably, it is more preferably 9 μm or more. The crystal grain size of zirconia is preferably 40 μm or less, more preferably 30 μm or less, and even more preferably 20 μm or less. By setting the crystal grain size in the above range, it is considered that the cutting process for the zirconia sintered body can be facilitated and the transparency and strength described later can be maintained.

The crystal particle size of zirconia can be calculated, for example, as the average particle size obtained by observing the cross section of the zirconia sintered body with a scanning electron microscope (SEM). For example, on the SEM cross-sectional image, all the zirconia particles in which all the contours appear (the contours are not interrupted) are picked up. Next, the cross-sectional area on the SEM photograph is calculated for each of the picked up particles. Then, the particle size (diameter) when the zirconia particles are assumed to be circular on the SEM cross-sectional image is calculated based on the cross-sectional area of each particle. The average crystal grain size can be calculated based on the calculated grain size. The above-mentioned preferable particle size is a numerical value in a state where the hydrothermal treatment test has not been performed.

The processability of the zirconia sintered body is preferably 5 times or more higher, more preferably 8 times or more higher, and more preferably 9 times or more higher than that of the zirconia sintered body produced from the zirconia powder ZpexSmile manufactured by Tosoh Corporation. It is preferable that it is 12 times or more higher, more preferably 16 times or more, and even more preferably 16 times or more. The workability can be measured, for example, by a single processing amount in which the zirconia sintered body can be processed with a processing tool (bar) (used at the same time) using a processing apparatus. By increasing the workability, the processing cost of the dental product can be suppressed and the processing time can be shortened.

The workability of the zirconia sintered body is determined by using two cutting tools, SEREC step bar 12S (for MCXL) and SEREC cylinder pointed bar 12S (for MCXL), which are used at the same time using SEREC MC XL manufactured by Sirona. preferably the cuttable volume is 2 mm ³ or more, more preferably 4 mm ³ or more, more preferably 5 mm ³ or more and further preferably 8 mm ³ or more.

The zirconia sintered body ^{preferably has a cross section of 28 mm 2} or more, more preferably has a cross section of 50 mm ² or more, and further preferably has a cross section of ^{78 mm 2 or more.} The shortest transfer length in the cross section is preferably 6 mm or more, more preferably 8 mm or more, and further preferably 10 mm or more. When a columnar sintered body having a cross section with a diameter of 6 mm or more is manufactured by a conventional manufacturing method (for example, a manufacturing method including a firing step at a temperature rising rate of 10 ° C./min or more), the internal translucency is improved. This is because the translucency of the surface is lower than that of the surface, but according to the manufacturing method of the present disclosure, it is possible to suppress a decrease in the translucency of the inside.

The zirconia sintered body preferably has a cross section of ^{900 mm 2} or less, more preferably has a cross section of ^{625 mm 2} or less, and further preferably has a cross section of ^{400 mm 2 or less.} The shortest transfer length in the cross section is preferably 30 mm or less, more preferably 25 mm or less, and even more preferably 20 mm or less. This is because in a sintered body having a square cross section (cross-sectional area 900 mm ² ) having a side of 30 mm or more, a phenomenon occurs in which the translucency of the inside becomes lower than the translucency of the surface.

The zirconia sintered body of the present invention can have a shape such as a cylinder, a polygonal prism, or a hexahedron. The cylindrical body includes not only a cylinder having a circular bottom surface but also an elliptical shape, and a cylinder having a circular shape and an elliptical shape. FIG. 1 shows a schematic perspective view of a zirconia sintered body having a rectangular parallelepiped shape. When the shape of the zirconia sintered body 1 is a rectangular parallelepiped, the dimensions, for example, the length _d 1 13Mm～17mm, width _(depth) d 2 _15mm~19mm, height _(thickness) and d 3 18mm~32mm be able to.

In the zirconia sintered body of the present invention, it is preferable that the difference between the internal translucency and the external translucency is small. In the present specification, the outside of the zirconia sintered body means a portion within 4 mm in depth from the unprocessed outer surface (as-sintered surface) after sintering. The inside of the zirconia sintered body means a portion deeper than 4 mm from the unprocessed outer surface after sintering. The outer surface is preferably a surface that intersects the cross section described above.

The translucency inside and outside the zirconia sintered body can be expressed by ΔL described below. A large ΔL indicates that the zirconia sintered body has high transparency, and a small ΔL indicates that the zirconia sintered body has low transparency.

The above-mentioned ΔL will be described. Translucent zirconia sintered body (transparency) ^can be expressed using the ^{L *} values of chromaticity (color space) in the L ^* a * ^{b *} color system (JISZ8781). FIG. 2 shows a schematic diagram for explaining a method of measuring chromaticity. Samples (e.g. zirconia sintered body) the background (underlay) 22 of 20 in the white (by the measuring device 21 opposite to the white to the sample 20) measured ^L * ^a * ^{b *} color system ^{L *} Let the value be the first L ^* value. For the same sample 20 for which the first L ^* value was measured, the background (underlay) 22 of the sample 20 was made black (the side opposite to the measuring device 21 was made black with respect to the sample 20), and the measured L ^* a ^*. b ^* Let the L ^* value of the ^{color system be the second L *} value. In the present disclosure, the difference between ^{the first L *} value and the second L ^{* value (the value obtained by subtracting the second L *} value from the first L ^* value) is expressed as ΔL. For the black and white used as the background (underlay) 22 in the chromaticity measurement, the hiding ratio measuring paper used for the measurement related to the paint can be used.

The rate of change from ΔL outside the zirconia sintered body ( _{denoted as “ΔL 1} ”) to ΔL inside the zirconia sintered body ( _{denoted as “ΔL 2} ”) can be expressed by the following equation.
[Rate of change of ΔL (%)] = (ΔL _{2 -ΔL 1} ) / ΔL ₁ × 100

In the zirconia sintered body, when F11 is used as a light source and a masking mask having a hole diameter of 8 mm is used, the rate of change of ΔL is preferably -15% or more, more preferably -14% or more. -13% or more is more preferable, -10% or more is more preferable, -5% or more is more preferable, -3% or more is more preferable, and -1% or more is further preferable. By reducing the difference in translucency between the inside and the outside, a prosthesis with high translucency can be cut out from the inside of the sintered body. According to the test in the present invention, the fact that the internal translucency of the zirconia sintered body is higher than the external translucency (that is, the rate of change is a positive value) is not a measurement error. , It is thought that it is unlikely to occur. Further, ΔL ₁ and ΔL ₂ are values when the zirconia sintered body does not contain a colorant, a fluorescent agent and an opaque agent.

In the zirconia sintered body, the density measured according to JIS R1634 can be, for example, 5.8 g / cm ³ or more. Further, the density can be, for example, 6.1 g / cm ³ or less.

The bending strength of the zirconia sintered body of the present invention measured in accordance with JIS R1601 is preferably 200 MPa or more, more preferably 300 MPa or more, and even more preferably 400 MPa or more. The bending strength is preferably 1200 MPa or less, more preferably 1000 MPa or less, and even more preferably 800 MPa or less. By setting the bending strength within the above range, it is possible to facilitate the cutting process on the zirconia sintered body and maintain the strength as a dental prosthesis. The above-mentioned preferable bending strength is a numerical value in a state where the hydrothermal treatment test has not been performed.

The zirconia sintered body can contain at least one of a colorant (pigment) and a fluorescent agent. Examples of the colorant include a group of P, Ti, V, Cr, Mn, Fe, Co, Ni, Zn, Y, Zr, Sn, Sb, Bi, Ce, Pr, Sm, Eu, Gd, Tb and Er. The oxide of at least one element selected from the above can be mentioned. Examples of the fluorescent agent include Y ₂ SiO ₅ : Ce, Y ₂ SiO ₅ : Tb, (Y, Gd, Eu) BO ₃ , Y ₂ O ₃ : Eu, YAG: Ce, ZnGa ₂ O ₄ : Zn, BaMgAl. ₁₀ O ₁₇ : Eu and the like can be mentioned.

When it is insufficient or difficult to specify the zirconia sintered body due to the composition or characteristics of the crystal particle size, composition, etc., the zirconia sintered body can be specified in addition to the composition or characteristics or by the production method described later alone. It is useful for identifying the zirconia sintered body of the present invention. For example, the zirconia sintered body of the present invention includes a zirconia sintered body produced by firing at a firing rate of 1000 ° C. or higher and a heating rate of 5 ° C./min or lower, a zirconia sintered body fired at 1550 ° C. or higher, and the highest. It can be specified as a zirconia sintered body or the like that has been fired at a temperature for 1 hour or more.

According to the first embodiment, even if the prosthesis is produced by directly cutting the zirconia sintered body, it is possible to produce a prosthesis having the same translucency as the outside of the block of the zirconia sintered body. can. For example, according to the first embodiment, a highly translucent prosthesis can be produced by direct processing of the zirconia sintered body.

By allowing direct processing of the zirconia sintered body, for example, a prosthesis can be produced in the dental clinic where the patient visited. This allows the patient to complete treatment for a short period of time, eg, within the day of the visit.

Further, by enabling the direct processing of the zirconia sintered body, the shape and dimensions of the prosthesis can be determined without considering the sintering shrinkage. This makes it possible to prepare a prosthesis that is more suitable for the oral environment of the patient.

Next, the dental product according to the second embodiment of the present disclosure will be described. FIG. 3 shows a schematic perspective view of the dental product of the present disclosure. The dental product 10 is for producing a dental prosthesis or the like by setting it in a processing device (not shown), for example. The dental product 10 includes a zirconia sintered body 1 and an attachment 11 attached to the zirconia sintered body 1. The zirconia sintered body 1 can be the zirconia sintered body according to the first embodiment of the present disclosure. The fixture 11 is a component for setting the zirconia sintered body 1 in the processing apparatus. The fixture 11 conforms to the specifications of the processing apparatus. As the joining form of the zirconia sintered body 1 and the attachment 11, any form can be adopted as long as the production of the prosthesis is not hindered. For example, the zirconia sintered body 1 and the attachment 11 can be joined with an adhesive.

According to the second embodiment, a prosthesis using the zirconia sintered body according to the first embodiment can be easily produced.

Next, the dental product according to the third embodiment of the present disclosure will be described. The dental product according to the third embodiment can be made from the zirconia sintered body according to the first embodiment or the dental product according to the second embodiment. Dental products include, for example, prostheses such as ceramic frames, full cantor crowns and the like. The zirconia sintered body can have a crown shape. Dental products can further include porcelain (eg, glass material) (not shown) laminated on the zirconia sintered body. Further, the dental product can be, for example, an orthodontic product (for example, an orthodontic bracket) or a dental implant product (for example, a dental implant abutment).

According to the third embodiment, the zirconia sintered body has high transparency and can be more adapted to the oral environment of the patient.

Next, the composition for producing the zirconia sintered body of the present disclosure and the calcined body will be described. The composition and the calcined product are precursors (intermediate products) of the above-mentioned zirconia sintered body of the present invention. The calcined body is obtained by calcining (that is, calcining) the composition at a temperature that does not lead to sintering. In addition, the calcined body includes a molded body. For example, a dental product (for example, a crown-shaped prosthesis) obtained by processing a calcined zirconia disc by a CAD / CAM (Computer-Aided Design / Computer-Aided Manufacturing) system is also included in the calcined body.

The compositions of the present disclosure also include powder, a fluid in which the powder is added to a solvent, and a molded product obtained by molding the powder into a predetermined shape. That is, the composition may be in powder form, in paste form or in wet composition (ie, in solvent or may contain solvent). Further, the composition may contain additives such as binders and pigments. In calculating the content, the mass of additives such as solvents and binders is not taken into consideration. When the composition of the present disclosure is a molded product, it may be molded by any molding method, and may be molded by, for example, press molding, injection molding, or stereolithography, and is multi-step. It may be molded. For example, the composition of the present invention may be press-molded and then further subjected to CIP (Cold Isostatic Pressing) treatment.

The molded product can be molded so as to have a shape and dimensions suitable for the sintered body to be manufactured, in consideration of shrinkage during sintering.

The compositions and calcined bodies of the present disclosure contain partially stabilized zirconia. The type and content of the stabilizer in the composition and the calcined product can be the same as described above. It is preferable that the variation in the content of the stabilizer (for example, Itria) is small in the composition and the calcined product. For example, the variation in the content of the stabilizer is preferably 1 mol% or less, more preferably 0.5 mol%, and more preferably no significant difference can be detected.

The molded composition (molding composition) and calcined product of the present disclosure have the same constitution as the zirconia sintered body to be produced.

The composition of the present disclosure is a calcined product of the present disclosure by firing the composition of the present invention under normal pressure at, for example, 800 ° C. to 1200 ° C.

The composition and calcined product of the present disclosure become the zirconia sintered body of the present disclosure by firing at, for example, 1400 ° C. to 1700 ° C. under normal pressure.

According to the composition and calcined product of the present disclosure, the zirconia sintered body of the present disclosure can be produced.

Next, a method for producing a zirconia sintered body, a zirconia calcined body, and a zirconia composition, and a method for producing a dental product will be described.

First, zirconia and a stabilizer are wet-mixed in water to form a slurry. Next, the slurry is dried and granulated. Next, the granulated product is calcined to prepare a primary powder. Next, the primary powder is pulverized and mixed in water until the desired particle size is obtained to form a zirconia slurry. Next, the slurry is dried and granulated to prepare a secondary powder as a composition.

Next, the secondary powder is press-molded to prepare a molded product as a composition having a predetermined shape. The molded product may be further subjected to CIP treatment.

When producing a calcined body, the calcined product can be produced by firing the molded product at, for example, 800 ° C. to 1000 ° C. The molding may be carried out by cutting or the like at the stage of the calcined body. Molding can be performed in a CAD / CAM system.

Next, the zirconia powder can be sintered by firing the molded product or calcined product at, for example, 1400 ° C. to 1650 ° C., preferably 1450 ° C. to 1600 ° C. to produce the zirconia sintered body of the present invention. can. When firing a molded product or calcined body for producing a sintered body, the temperature rise rate from the temperature at which the calcined body is formed, for example, 1000 ° C., to the sintering temperature (for example, the maximum firing temperature) is 5. The temperature is preferably ° C./min or lower, more preferably 3 ° C./min or lower, more preferably 2 ° C./min or lower, and even more preferably 1 ° C./min or lower. By producing the sintered body at such a temperature rising rate, it is possible to produce a sintered body having enhanced translucency to the inside of the sintered body. The maximum temperature is preferably 1500 ° C. or higher, more preferably 1550 ° C. or higher, and even more preferably 1600 ° C. or higher. It is considered that the crystal grain size can be grown by increasing the maximum temperature. The holding time at the maximum temperature is preferably 1 hour or more, and more preferably 2 hours or more. It is considered that the crystal grain size can be grown by lengthening the holding time to some extent. Then, by growing the crystal grain size, the translucency and processability of the sintered body can be improved.

Firing for sintering can also be performed in an atmospheric (air) atmosphere. Further, the firing for sintering can also be performed in an atmosphere having an oxygen concentration higher than that of air, for example, in an oxygen gas aeration. The flow rate of oxygen gas can be set as appropriate. Sintering can be promoted by aerating oxygen gas.

Dental products can be produced by joining a fixture to the produced zirconia sintered body. The fixture can be bonded to the zirconia sintered body using, for example, an adhesive.

It is also possible to set a dental product having an attachment in a processing device, for example, a CAD / CAM system, and use the processing device to form a zirconia sintered body into a predetermined shape, for example, the shape of a prosthesis. After molding the zirconia sintered body, the fixture can be removed.

[Examples 1 to 10 and Comparative Examples 1 to 5]
A zirconia sintered body was prepared, and the density, crystal grain size and machinability of the zirconia sintered body were measured. In addition, the translucency inside and outside the sintered body was compared. In Examples 9 to 10, sintered bodies having a size different from that of Examples 1 to 8 were produced. Further, as a comparative example, the same measurement was performed on a zirconia sintered body having a smaller crystal grain size.

A partially stabilized zirconia powder containing yttria at the content shown in Table 1 was prepared as a stabilizer. The raw materials of Examples 1 to 10 and Comparative Examples 1 and 2 are zirconia powder manufactured by Kuraray Noritake Dental Co., Ltd. The raw material of Comparative Example 3 is zirconia powder ZpexSmile manufactured by Tosoh Corporation. The raw material of Comparative Example 4 is zirconia powder TZ-6YS manufactured by Tosoh Corporation. The raw material of Comparative Example 5 is zirconia powder TZ-8YS manufactured by Tosoh Corporation. Table 1 shows the average particle size of the raw material powder. Next, the zirconia powder was formed into a rectangular parallelepiped shape and fired under the firing conditions shown in Table 1 under air and normal pressure to prepare a zirconia sintered body having a rectangular parallelepiped shape having the dimensions shown in Table 2. The rate of temperature rise shown in Table 1 is the rate of temperature rise from 1000 ° C. to the maximum temperature.

For each zirconia sintered body, the particle size of the crystals in the image was measured based on the SEM image of the cross section of the sintered body taken with a scanning electron microscope, and the average value was calculated. As the electron microscope, a field emission scanning electron microscope (FE-SEM) (S-4700) manufactured by Hitachi High-Tech Fielding Co., Ltd. was used. The measurement results are shown in Table 2.

The density of each zirconia sintered body was measured according to JIS R1634. The measurement results are shown in Table 2.

For each zirconia sintered body, the volume that can be cut with two cutting tools, SEREC step bar 12S (for MCXL) and SEREC cylinder pointed bar 12S (for MCXL), which are used at the same time using SEREC MC XL manufactured by Sirona. Was measured. The machinable volume is the amount of machining that has been cut from the start of machining to the time when the machining device automatically stops due to inability to machine. The measurement results are shown in Table 2.

The difference in translucency between the outside and the inside of each zirconia sintered body was measured. As the outside of the zirconia sintered body, a sample of 10 mm × 10 mm × 1.2 mm was cut out so that the outer surface at the time of sintering was a large surface. Similarly, a 10 mm × 10 mm × 1.2 mm sample was cut out as the inside of the zirconia sintered body so as to include the center of the height (longer direction). Then, mirror surface processing was performed on both sides (large surfaces) of the sample. Next, the chromaticity was measured for both the external and internal samples. ^{For the chromaticity, the above-mentioned first L * value and second L *} value were measured using a chromaticity measuring machine (SPECTROPHOTOMETER CM-3610A manufactured by KONIKA MINOLTA) and analysis software (Spectra Magic NX), and the first L * value and the second L * value were measured. was calculated 1 ^{L *} value and a [Delta] L ₁ and [Delta] L ₂ is the difference of the second ^{L *} value. F11 was used as the light source, and a masking mask having a hole diameter of 8 mm was used. For the black and white background (underlay), the concealment rate measurement paper used for the measurement of paint was used. Based on the above formula, the rate of change of ΔL was calculated from ΔL ₁ and ΔL _2. The results are shown in Table 3.

In Examples 1 to 10, a zirconia sintered body having higher machinability than Comparative Examples 1 to 5 could be obtained. For example, in Examples 1 to 10, 2.5 mm ³ or more could be cut, whereas in Comparative Examples 1 to 5, the cutting amount was less than ^{2 mm 3.} Compared with the sintered body of Comparative Example 3, the workability of Example 8 was 5 times and that of Example 4 was 16 times or more.

Looking at Table 2, it can be seen that increasing the crystal grain size of the sintered body tends to improve workability. It is considered that the crystal grain size is influenced by the zirconia raw material, the yttria content, the rate of temperature rise and the maximum temperature. That is, according to Tables 1 and 2, the yttria content is increased (for example, 6 mol% or more) and the temperature rising rate at 1000 ° C. or higher is lowered (for example, 5 ° C./min) by using the zirconia raw material manufactured by Clarenoritake Dental Co., Ltd. Below), it is considered that the crystal grain size can be increased by raising the maximum firing temperature (1550 ° C. or higher).

In Examples 8 and 9 and Comparative Examples 1 and 2 in which the heating rate was 10 ° C./min, the rate of change in translucency was −15% or less. On the other hand, in Examples 1 to 7 and 10 and Comparative Examples 3 to 5 in which the rate of temperature rise is 1 ° C./min, 3 ° C./min and 5 ° C./min, the rate of change in translucency is -15. Could be higher than%. In particular, when the rate of temperature rise was 1 ° C./min, there was a tendency that the rate of change in translucency could be increased. In Examples 2 to 4 and 7, and Comparative Examples 4 and 5, the rate of change in translucency can be −5% or more, and in Examples 3 and 4, the rate of change in translucency can be −5% or more. It could be 1% or more. From this, in the firing for sintering, the heating rate in the region of 1000 ° C. or higher is set to less than 10 ° C./min, preferably 5 ° C./min or less, 3 ° C./min or less, or 1 ° C./min or less. , It was found that the inside of the sintered body and the translucency can be improved.

In Example 9 in which the size of the sample was 10 mm × 10 mm × 10 mm (cross-sectional area 100 mm ² , shortest delivery length 10 mm), a decrease in internal translucency occurred. On the other hand, in Examples 1 to 8, even if the sample is 11 mm × 14 mm × 18 mm (cross-sectional area 154 mm ² , shortest delivery length 11 mm) larger than the sample of Example 9, the decrease in internal translucency is suppressed. We were able to. Further, in Example 10, even a sample having a size of 30 mm × 30 mm × 30 mm (cross-sectional area 900 mm ² , shortest delivery length 30 mm) could suppress a decrease in internal translucency.

Comparing the external translucency ΔL ₁ , in Examples 1 to 6 and 10, ΔL ₁ was 19 or more, and the translucency could be improved as compared with other Examples and Comparative Examples. It is considered that this is influenced by the Itria content, the rate of temperature rise, and the maximum temperature. According to Examples 1-6 and 10, a highly translucent dental prosthesis can be more easily produced from the block of the zirconia sintered body.

Each disclosure of the above patent documents shall be incorporated herein by reference. The zirconia sintered body of the present invention and a method for producing the same, and a dental product and the method for producing the same are described based on the above-described embodiment, but the present invention is not limited to the above-described embodiment. Various for various disclosure elements (including each element of each claim, each element of each embodiment or embodiment, each element of each drawing, etc.) within the framework and based on the basic technical idea of the present invention. Needless to say, it can include modifications, changes and improvements of. Further, within the framework of all disclosure of the present invention, various combinations / substitutions or substitutions of various disclosure elements (including each element of each claim, each element of each embodiment or embodiment, each element of each drawing, etc.) or You can choose.

Further issues, objectives and developments of the present invention will also be apparent from all disclosures of the present invention, including the scope of the claims.

Regarding the numerical range described in this document, it should be interpreted that any numerical value (including after the decimal point) or small range included in the range is specifically described even if there is no other description. be.

A part or all of the above-described embodiment may be described as in the following appendix, but is not limited to the following description.
[Appendix 1]
Including a sintering step of calcining a zirconia composition containing 5 mol% to 8 mol% yttria as a stabilizer into a sintered body.
A method for producing a zirconia sintered body, wherein the heating rate from 1000 ° C. to the maximum temperature is 5 ° C./min or less in the sintering step.
[Appendix 2]
The method for producing a zirconia sintered body according to the appendix, wherein the heating rate is 3 ° C./min or less.
[Appendix 3]
The method for producing a zirconia sintered body according to the appendix, wherein the maximum temperature is 1550 ° C. or higher.
[Appendix 4]
The method for producing a zirconia sintered body according to the appendix, further comprising a molding step of molding the composition into a hexahedral or cylindrical shape.
[Appendix 5]
The composition further includes a calcining step of calcining the composition at a temperature that does not lead to sintering to prepare a calcined body.
The method for producing a zirconia sintered body according to the appendix, wherein the calcined body is fired in the sintering step.
[Appendix 6]
The method for producing a zirconia sintered body according to the appendix, wherein in the sintering step, firing is performed in an atmosphere having an oxygen concentration higher than that of air.
[Appendix 7]
A method for producing a dental product, which comprises a processing step of molding the zirconia sintered body produced by the method for producing a zirconia sintered body described in the appendix.
[Appendix 8]
The zirconia sintered body further includes a step of joining a fitting for attaching to the processing apparatus.
The method for manufacturing a dental product according to the appendix, wherein in the processing step, the zirconia sintered body is molded by the processing apparatus.
[Appendix 9]
The method for manufacturing a dental product according to the appendix, wherein the zirconia sintered body is molded into a crown shape in the processing step.

The zirconia sintered body of the present invention includes dental materials such as prostheses, connecting parts for optical fibers such as ferrules and sleeves, various tools (for example, crushing balls and grinding tools), and various parts (for example, screws, bolts and nuts). ), Various sensors, electronic parts, decorations (for example, watch bands) and the like. When zirconia sintered bodies are used in dental materials, for example, coping, frameworks, crowns, crown bridges, abutments, implants, implant screws, implant fixtures, implant bridges, implant bars, brackets, prostheses, inlays, It can be used for onlays, onlays, straightening wires, laminated veneers, etc.

1 Zirconia sintered body 10 Dental product 11 Fixture 20 Sample 21 Measuring device 22 Underlay

Claims (10)

A partially stabilized zirconia sintered body containing 5 mol% to 7.5 mol% yttria as a stabilizer.
5μm or more and have a an average grain size less 10.50Myuemu,
The translucency ΔL outside the sintered body is expressed as _{ΔL 1.}
The translucency ΔL inside the sintered body is expressed as _{ΔL 2.}
The _{rate of change from ΔL 1} to ΔL ₂ is calculated by the following equation:
[Rate of change _{ΔL] = (ΔL 2 -ΔL 1} ) / ΔL 1 × 100
When represented by
The rate of change of ΔL is -15% or more.
However, the outside is a portion from the outer surface at the time of sintering to a depth of 4 mm.
The inside is a portion deeper than 4 mm from the outer surface.
For the ^{L *} value of chromaticity (color space) in the internal and the external ^L * ^a * ^{b *} color system (JISZ8781), using the F11 as a light source, ^{L *} value measured background samples in the white Is the first L ^* value,
The same samples were measured first in the L ^* value, when the L ^* value of the background of the sample were measured in the black and the second L ^* value,
ΔL is a ^{value obtained by subtracting the second L *} value from the first L ^* value, which is a zirconia sintered body. The zirconia sintered body according to claim 1, wherein the average crystal grain size is 7 μm or more. The zirconia sintered body according to claim 1, wherein the average crystal grain size is 8 μm or more. The zirconia sintered body according to any one of claims 1 to 3, which contains 6 mol% to 7.5 mol% yttria as the stabilizer. It has a cross-sectional area of 900 mm ² or less and has a cross-sectional area of 900 mm 2.
The zirconia sintered body according to any one of claims 1 to 4 , wherein the shortest delivery length in the cross section is 30 mm or less. The zirconia sintered body according to any one of claims 1 to 5 , which has a hexahedral or cylindrical shape. A dental product comprising the zirconia sintered body according to any one of claims 1 to 5. Further equipped with attachments for attaching to processing equipment,
The dental product according to claim 7 , wherein the fitting is joined to the zirconia sintered body. The dental product according to claim 7 or 8 , wherein the zirconia sintered body has a hexahedral or cylindrical shape. The dental product according to claim 7 or 8 , wherein the zirconia sintered body has a crown shape.

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