KR101682542B1 - Method for manufacturing dental block - Google Patents
Method for manufacturing dental block Download PDFInfo
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- KR101682542B1 KR101682542B1 KR1020150039271A KR20150039271A KR101682542B1 KR 101682542 B1 KR101682542 B1 KR 101682542B1 KR 1020150039271 A KR1020150039271 A KR 1020150039271A KR 20150039271 A KR20150039271 A KR 20150039271A KR 101682542 B1 KR101682542 B1 KR 101682542B1
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Abstract
One embodiment of the present invention provides a method of manufacturing a glass ceramic, comprising: preparing a glass ceramic; Making the glass ceramic porous; Filling the ceramic porous body in a vacuum chamber to remove pores in the porous body in a vacuum state and then impregnating the polymer in a monomer state to realize a biaxial flexural strength of 100 to 150 MPa; .
Description
The present invention relates to a dental block and a method of manufacturing the same, and more particularly, to manufacturing a workpiece for CAD / CAM processing by infiltrating a polymer into a porous glass or a crystallized glass.
With the introduction of CAD / CAM technology in the field of dental prosthesis, there is a need to develop materials that emphasize machinability. In particular, ceramics are used mainly in dental materials as they are capable of sophisticated CAD / CAM processing with aesthetic characteristics similar to natural teeth. However, because of the inherent brittleness of ceramics, chipping occurs during machining, which limits the use of the marginal portion to the processing of prostheses with thin thicknesses.
In addition, the ceramic material has a disadvantage in that dimensional stability is deteriorated due to processing tolerance due to shrinkage due to sintering after processing.
Zirconia, which is most widely used as a dental CAD / CAM material, has excellent mechanical properties with a flexural strength of 1200 MPa. However, it has a low transmittance and poor dimensional stability due to shrinkage during sintering after processing. For machining, it is necessary to have low surface hardness and hardness of the tool resistance. In the case of zirconia, it is processed in the presintering state, and then the high strength is realized through the final sintering process as the sintering process. At this time, dimensional stability is also a problem, but there are various problems such as the inconvenience of re-sintering process and facility investment accordingly.
In terms of machinability, the most easily processed material is a resin block, which is easy to process because of its low modulus of elasticity, and has the advantage of simple process because it does not require a sintering process. However, due to the inherent low chemical durability of the resin, discoloration occurs and the strength is low.
Therefore, in general clinical experiments, it is mainly used as an inlay that is not applied with a high load. However, in-treatment patients are the most popular among in-patient patients, and despite the many disadvantages, they are steadily used in the market. However, resin blocks can not be applied to various crown materials.
The crown material refers to a prosthetic material that restores the dentin and enamel surface of a damaged tooth and is divided into an inlay, an onlay, a veneer, and a crown depending on the application site.
Since the crown material is restored to the outer surface of the teeth, aesthetic characteristics are greatly required, and high strength is required due to abrasion, chipping, and the like due to the abutment.
Ceramic materials used as conventional crown materials are lucite crystallized glass, reinforced porcelain or fluorinated apatite crystallized glass. They have excellent aesthetic characteristics, but they have a low strength of 80 ~ 120 MPa and high fracture possibility. In addition, defects such as cracks, chipping and tearing are frequent due to low toughness during machining. Therefore, ceramic materials having superior machinability are being studied actively with excellent aesthetic properties and physical properties to overcome these disadvantages.
The present invention provides a method of manufacturing a dental block that is easy to process and has excellent strength.
The present invention also provides a method for manufacturing a dental block having excellent aesthetic properties and excellent mechanical properties.
One embodiment of the present invention provides a method of manufacturing a glass ceramic, comprising: preparing a glass ceramic; Making the glass ceramic porous; Filling the ceramic porous body in a vacuum chamber to form a vacuum state to remove pores in the porous body, and then impregnating the polymer in the monomer state to realize a biaxial flexural strength of 100 to 150 MPa. do.
In one embodiment, the glass ceramic comprises 2.0 to 6.0 wt% of N 2 O, 60 to 65 wt% of SiO 2 , 8.0 to 15 wt% of K 2 O, 0.5 to 3.0 wt% of CaO, 0.5 to 2.0 wt% of BaO, 0.2 to 1.0 wt% of CeO 2 , 0.5 wt% or less of TiO 2 , 16.0 to 19.0 wt% of Al 2 O 3 for increasing the glass transition temperature and softening point and improving the chemical durability of the crystallized glass, And 1.0% by weight or less of a toning agent component which exhibits fluorescence.
In one embodiment, the step of forming the glass ceramic into a porous form comprises: milling the glass ceramic and melting at a temperature of 1400 to 1800 ° C; Cooling the melted glass-ceramics, pulverizing the glass-ceramics, mixing the milled glass-ceramics with a binder to prepare granules, molding the glass-ceramics, and calcining at 500 to 700 ° C to remove the binder; And subjecting the glass ceramic on which the calcination process has been performed to a calcination heat treatment at 700 to 840 ° C.
In one embodiment, the step of forming the glass ceramic into a porous form comprises: milling the glass ceramic and melting at a temperature of 1400 to 1800 ° C; Cooling the molten glass-ceramics, pulverizing the glass-ceramics, and performing a crystallization heat treatment at 875 to 970 ° C; Grinding the glass ceramic subjected to the crystallization heat treatment, and performing a porous heat treatment at a temperature of 700 to 840 ° C.
In one embodiment, the porous heat treatment is performed by adding at least one of Ca 3 (PO 4 ) 2 , MgSO 4 , K 2 SO 4 , NaCl, Na 2 SO 4 and K 3 PO 4 to the re- , The glass ceramic may be 70 to 90% by volume, and the salt may be 10 to 30% by volume.
In one embodiment, the porous body formed by the porous heat treatment may have a pore size of 5 μm or less, and the porous body may have a relative density of 60 to 80%.
In one embodiment, the step of infiltrating the polymer comprises: a primary infiltration step of primarily infiltrating the polymer; And a second infiltration step of infiltrating the polymer secondarily before the first infiltrated polymer is fully cured.
Another embodiment of the present invention provides a dental block manufactured by infiltrating a polymer into a porous body formed on a glass ceramic subjected to a porous heat treatment.
The CAD / CAM block permeating the polymer into the ceramic porous body according to the present invention has an elastic modulus higher than that of the conventional polymer block, showing properties similar to those of a natural value and having a high strength due to a ceramic skeleton. Compared with all-ceramic block, it has low elastic modulus and high toughness, so it can be processed to thin part with less bonding of chipping etc. during processing and has high stability of edge.
And excellent processability is effective in terms of production efficiency because it has effects such as tool wear and shortening of working time. It is also important to develop and select the material of the glass or crystallized glass corresponding to the support.
The present invention relates to a method of producing a porous body by using two methods for producing a porous body, that is, a crystallized glass having a small viscosity-viscous flow and increased in strength by surface crystallization, By selecting a chemically stable material for the solution, the production efficiency can be increased as described above.
It should be understood that the effects of the present invention are not limited to the above effects and include all effects that can be deduced from the detailed description of the present invention or the configuration of the invention described in the claims.
FIGS. 1A and 1B are graphs showing the particle size distribution according to an embodiment of the present invention, respectively.
2 is a graph showing the relative density of the glass and the crystallized glass according to the embodiment of the present invention.
FIG. 3 is a diagram showing a crystallization phase and crystallization degree of a glass according to crystallization temperature according to an embodiment.
FIG. 4 is a view showing a crystallization phase and a crystallization degree of a glass according to crystallization time according to an embodiment.
FIG. 5 is a view showing the dissolution rate from the sintered body according to the content of TCP salt according to one embodiment. FIG.
FIG. 6 is a graph showing changes in crystal phase and crystallization phase after elution of TCP salt and crystallized glass after X-ray diffraction analysis according to one embodiment.
7 is a graph showing the biaxial strength of the polymer-infiltrated crystallized glass according to the degree of crosslinking of the polymer according to one embodiment.
FIG. 8 is a graph illustrating a visible light transmission spectrum of a composite according to an embodiment of the present invention. FIG.
FIG. 9 is a graph showing the elastic modulus and hardness of the polymer according to the crosslinking degree according to one embodiment.
10 is a view showing a ceramic porous body, a polymer microstructure, and a polymer infiltration ceramic microstructure using a scanning electron microscope according to an embodiment.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, the present invention will be described with reference to the accompanying drawings. The present invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. In order to clearly illustrate the present invention, parts not related to the description are omitted, and similar parts are denoted by like reference characters throughout the specification.
Throughout the specification, when a part is referred to as being "connected" to another part, it includes not only "directly connected" but also "indirectly connected" . Also, when an element is referred to as "comprising ", it means that it can include other elements, not excluding other elements unless specifically stated otherwise.
Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.
A method of manufacturing a dental block according to an embodiment is a method in which a polymeric polymer is impregnated into a porous ceramic support with a penetrant to increase machinability and physical properties.
The ceramic porous body itself uses a ceramic glass having excellent aesthetics or crystallized glass crystallized therefrom, and a polymer material excellent in biocompatibility is used as the impregnating body.
The ceramic-polymer composites thus produced can be applied to dental restorations by machining to 1: 1 dimensions through CAD / CAM machining. In order to increase the mechanical properties, aesthetics and machinability, it is important to select the material of the porous body, the structure of the pores, and the polymer penetration technique for the dense structure.
In one embodiment, in using glass ceramics as a porous body, a method of infiltrating a polymer into a ceramic porous body having an open pore structure so that the permeation of the polymer is easy and the mechanical properties are excellent.
In order to realize open pores, there are optimal porosity heat treatment conditions and pore generation methods by dissolution. In order to minimize the closed pores generated by the contraction of the penetrating polymer, a double penetration method is proposed.
The composition of the porous ceramics-based glass ceramic was 2.0 to 6.0 wt% of N 2 O, 60.0 to 65.0 wt% of SiO 2 , 8.0 to 15.0 wt% of K 2 O, 0.5 to 3.0 wt% of CaO, 0.5 to 2.0 wt% of BaO, 2 0.2 to 1.0
The starting materials mentioned above may be weighed and mixed and Na 2 CO 3 may be added instead of Na 2 O. Carbon dioxide which is the carbon (C) component of Na 2 CO 3 is discharged into the form of gas in the melting process of glass do. K 2 CO 3 and CaCO 3 may be added instead of K 2 O and CaO in the alkali oxide, Carbon dioxide (CO 2 ), a carbon component of K 2 CO 3 and CaCO 3 , is released to the outside as a gas in the melting process of glass.
Mixing is performed using a dry mixing process, and a ball milling process can be used as a dry mixing process. Specifically, the starting material is charged into a ball miller, the ball mill is rotated at a constant speed, the starting material is mechanically pulverized and uniformly mixed. The ball used in the ball miller may be a ball made of ceramics such as zirconia or alumina, and the balls may have the same size or at least two or more sizes. The ball miller adjusts the size of the ball, the milling time, the rotation speed per minute of the ball miller, etc., considering the size of the target particle. For example, it is preferable to carry out the treatment for 1 to 48 hours in consideration of the particle size and the like. By the ball milling process, the starting material is pulverized into fine sized particles, having a uniform particle size and being uniformly mixed at the same time.
The mixed starting material is placed in a melting crucible and the starting material is melted by heating the melting crucible containing the starting material. Here, melting means that the starting material is changed into a liquid state viscous material state instead of a solid state.
The molten crucible is preferably made of a material having a low contact angle in order to suppress the phenomenon that the molten material has a high melting point while having a high melting point, and for this purpose, platinum (Pt), diamond-like-carbon (DLC), chamotte Or a melting crucible having a surface coated with a material such as platinum or DLC.
The melting is preferably carried out at 1400 to 1800 ° C at normal pressure for 1 to 12 hours. When the melting temperature is less than 1400 ° C, the starting material may not be melted. If the melting temperature exceeds 1800 ° C, excessive energy consumption may be caused. This is not economically feasible, . If the melting time is too short, the starting material may not be sufficiently melted, and if the melting time is too long, excessive energy consumption is required, which is not preferable from the economical point of view.
If the temperature of the melting furnace is excessively low, productivity is deteriorated due to a long melting time. If the temperature of the melting furnace is too high, the temperature of the melting furnace is increased The volatilization amount of the raw material becomes large and the physical properties of the glass ceramic may be poor. Therefore, it is preferable to raise the temperature of the melting furnace at the temperature raising rate within the above-mentioned range. The melting is preferably carried out in an oxidizing atmosphere such as oxygen (O 2 ) and air.
The molten glass from which the starting material is melted is poured out from the crucible and is crushed against the cooled glass lumps and the like. At this time, glass particles having an average particle size of 3 to 30 μm are prepared by pulverizing the coarse powder and the fine powder. 1A and 1B show the particle size distribution according to each crushing time. Particularly, FIG. 1A shows the particle size distribution of the glass lumps broken down for 0.5 hour, and FIG. 1B shows the particle size distribution of the glass lumps broken down for 3.5 hours .
The crushed glass lumps are mixed with the mixed solution to prepare a slurry, followed by spray drying to obtain a granular phase, which is then molded in a mold. The compacted body is subjected to a calcining process at 500 to 700 ° C, thereby removing the polymer binder and the like incorporated into the ceramic powder.
The calcined body is subjected to calcination heat treatment at 700 to 840 ° C to produce a porous body. FIG. 2 shows relative densities of glass and crystallized glass according to an embodiment of the present invention.
A method of producing a crystallized glass from glass to produce a porous body is characterized in that the pulverized glass powder is subjected to crystallization heat treatment for 30 minutes to 5 hours at 875 to 970 ° C. FIG. 3 shows crystallization phases and crystallization degrees of crystallization temperatures of glass according to an embodiment of the present invention. At this time, the crystal phase is tetragonal lucite crystal, showing 18% crystallinity at 875 ° C and 30% crystallinity at 950 ° C. And above 950 ℃, the crystal melted again in the glass, and the crystallinity decreased to 25% at 970 ℃. Therefore, the optimum temperature range that the lucite crystal phase can form is 875 to 950 占 폚, as can be seen from Fig.
Crystallization of the glass is generated after 30 minutes, and crystals are excessively precipitated for 5 hours or more, and light transmittance is deteriorated, so that it is preferable to have a limited heat treatment temperature and a holding time.
FIG. 4 shows crystallization phases and crystallization degrees of crystallization time of glass according to an embodiment of the present invention. After the crystallization heat treatment is finished, the powder is re-pulverized to prepare a powder having a particle size of 3 to 30 mu m. After molding, the porous powder is subjected to a heat treatment for 30 minutes to 5 hours at 700 to 840 DEG C as shown in Fig. Below 700 캜, large pores are formed, and the strength of the skeleton is low, which is not suitable as the heat treatment temperature of the porous body. When the temperature is higher than 840 DEG C, the formed body becomes dense, which is a temperature that can not be used for producing a porous body.
A method of preparing a porous body by eluting a salt is a method of preparing a porous body by mixing at least one of a crushed glass or a crystallized glass with a salt (TCP (Ca 3 (PO 4 ) 2 ), MgSO 4 , NaCl, Na 2 SO 4 , K 3 PO 4 These salts are limited to components that do not react with the glass or the crystallized glass during the heat treatment but are selectively eluted by the eluting solution. The addition amount of the glass or the crystallized glass is 70 to 90% by volume A sufficient amount of salt is important because 10% by volume or less of the salt is difficult to form pores of the connected structure, and more than 30% by volume of the salt may collapse after elution.
The solution for eluting these salts uses acidic solution or distilled water. As the amount of salt-in-TCP added to glass or crystallized glass is increased, the removal rate of TCP is increased and the porosity is increased. Shows the dissolution rate (removal ratio) from the sintered body according to the content of TCP salt according to an embodiment of the present invention.
6 shows that TCP can be removed by reacting with the eluting solution without reacting with the crystallized glass after the pore-forming heat treatment. FIG. 6 shows the crystal phase after the synthesis of the TCP salt and the crystallized glass through the X-ray diffraction analysis according to an embodiment of the present invention and the crystal phase change after the elution.
In order to permeate the polymer into the thus-prepared porous ceramic body, the porous body is first charged into a vacuum chamber to form a vacuum state (100 to 400 Pa) to permeate the polymer into the porous body. The impregnation of the polymer at this time implies that the polymer is ultimately penetrated by being impregnated with a monomer (Bis-GMA, Bis-EMA, UDMA, TEGDMA, Urethane modified Bis-GMA or MMA) and cured to become a polymer. In order to increase the permeability, pressurization (0.1 to 300 MPa) may be applied depending on the pore size and porosity of the porous body. The polymer hardening is carried out at a temperature of 30 to 100 ° C., and a temperature increase rate of 0.1 to 20 K / min.
The biaxial flexural strength was measured at 100 to 150 MPa in accordance with the degree of crosslinking of the polymer when the polymer was permeated into the thus prepared porous article. Figure 7 shows the biaxial flexural strength of the polymer-infiltrated crystallized glass according to the degree of crosslinking of the polymer according to one embodiment of the present invention. As the degree of crosslinking is increased, the polycondensation reaction is promoted, and the shrinkage ratio is increased, thereby lowering the strength at a high degree of crosslinking. Pores are generated by the shrinkage generated during the curing process of such a polymer, which is a main cause of the strength drop. In order to solve this problem, a process of filling the internal pores by introducing a new polymer into the pressure chamber secondarily before the first penetrated polymer is completely cured is proposed. Since the polymer has a low viscosity that allows penetration, it is noted that the polymer can penetrate deeply by the capillary force. As a result of the visible light transmittance of these specimens, the visible light transmittance is higher than that of the first penetrated specimen in the second penetrated specimen as shown in FIG. This is because the pores generated in the shrinkage after the first infiltration have a large difference in the incident light and the refractive index, and the transmission becomes less due to scattering of light. It can be seen that the scattering of light by air is reduced as the pores remaining through the secondary infiltration are filled with the new polymer. The elastic modulus and surface hardness affecting machining were measured for these specimens.
9 shows elastic modulus and hardness of the polymer according to the crosslinking degree according to an embodiment of the present invention. The elastic modulus of dentin of natural teeth is about 20 ~ 30 GPa and similar elastic modulus (26 ~ 33 GPa) is expected. In addition, if chipping or the like has been a problem during the course of all the ceramic materials showing 60 to 80 GPa, the ceramic-polymer composite of the present invention is excellent in processability and edge stability due to its elastic modulus close to its natural value.
The physical properties and machinability of the polymer - impregnated ceramic composites are closely related to the pore structure of the ceramic porous body and the penetration technique of the polymer. The average pore size of the porous article obtained in the present invention is a channel structure connected to each other within 5 mu m. 10 shows a ceramic porous body, a polymer microstructure, and a polymer infiltration ceramic microstructure using a scanning electron microscope according to an embodiment of the present invention. In the polymer-impregnated composite specimen, the connected channel structure can be confirmed in the network of the polymer dissolved in only the ceramics. Polymer penetration ceramics can achieve maximum physical properties and machinability by densely penetrating the polymer into the pores of this network structure.
If the pore size is large, the specific gravity of the polymer is increased, and the mechanical properties and the elastic modulus will decrease. In order to obtain a ceramic-polymer composite exhibiting physical properties closest to a natural value, the material and particle size of the pore structure, the heat treatment and elution conditions thereof and the like must be optimized. The present invention proposes such a process as described above have.
It will be understood by those skilled in the art that the foregoing description of the present invention is for illustrative purposes only and that those of ordinary skill in the art can readily understand that various changes and modifications may be made without departing from the spirit or essential characteristics of the present invention. will be. It is therefore to be understood that the above-described embodiments are illustrative in all aspects and not restrictive. For example, each component described as a single entity may be distributed and implemented, and components described as being distributed may also be implemented in a combined form.
The scope of the present invention is defined by the appended claims, and all changes or modifications derived from the meaning and scope of the claims and their equivalents should be construed as being included within the scope of the present invention.
Claims (8)
Forming a ceramic porous body by forming the glass ceramic into a porous body;
A primary infiltration step of charging the ceramic porous body into a vacuum chamber to primarily infiltrate the polymer into the ceramic porous body in a vacuum state; And
And a second infiltration step of infiltrating the polymer into the ceramic porous body secondarily before the first infiltrated polymer is completely cured,
Wherein a biaxial flexural strength of 100 to 150 MPa is realized.
The glass ceramic is N 2 O 2.0 ~ 6.0 wt%, SiO 2 60 ~ 65 wt%, K 2 O 8.0 ~ 15 wt%, CaO 0.5 ~ 3.0% by weight, BaO 0.5 ~ 2.0% by weight, CeO 2 0.2 ~ 1.0 wt. % Of TiO 2 , not more than 0.5% by weight of TiO 2 , 16.0 to 19.0% by weight of Al 2 O 3 for increasing the glass transition temperature and softening point and improving the chemical durability of the crystallized glass and not more than 1.0% by weight of color- ≪ / RTI >
The step of forming the ceramic porous body into a ceramic porous body includes:
Milling the glass ceramic and melting at a temperature of 1400 to 1800 ° C;
Cooling the melted glass-ceramics, pulverizing the glass-ceramics, mixing the milled glass-ceramics with a binder to prepare granules, molding the glass-ceramics, and calcining at 500 to 700 ° C to remove the binder;
Performing a calcination heat treatment at 700 to 840 캜 for the glass ceramic on which the calcination process has been performed;
≪ / RTI >
The step of forming the ceramic porous body into a ceramic porous body includes:
Milling the glass ceramic and melting at a temperature of 1400 to 1800 ° C;
Cooling the molten glass-ceramics, pulverizing the glass-ceramics, and performing a crystallization heat treatment at 875 to 970 ° C;
Pulverizing the glass-ceramics subjected to the crystallization heat treatment, and performing a porous heat treatment at a temperature of 700 to 840 ° C;
≪ / RTI >
Forming a ceramic porous body by forming the glass ceramic into a porous body; And
Charging the ceramic porous body into a vacuum chamber to permeate the polymer into the ceramic porous body in a vacuum state to realize biaxial flexural strength of 100 to 150 MPa,
The step of forming the ceramic porous body may include:
Milling the glass ceramic and melting at a temperature of 1400 to 1800 ° C;
Cooling the molten glass-ceramics, pulverizing the glass-ceramics, and performing a crystallization heat treatment at 875 to 970 ° C; And
Grinding the glass-ceramics subjected to the crystallization heat treatment, and performing a porous heat treatment at a temperature of 700 to 840 ° C,
In the porous heat treatment,
The glass ceramic is mixed with a salt of at least one of Ca 3 (PO 4 ) 2 , MgSO 4 , K 2 SO 4 , NaCl, Na 2 SO 4 and K 3 PO 4 , And the salt is 10 to 30% by volume.
Forming a ceramic porous body by forming the glass ceramic into a porous body; And
Charging the ceramic porous body into a vacuum chamber to permeate the polymer into the ceramic porous body in a vacuum state to realize biaxial flexural strength of 100 to 150 MPa,
The step of forming the ceramic porous body may include:
Milling the glass ceramic and melting at a temperature of 1400 to 1800 ° C;
Cooling the molten glass-ceramics, pulverizing the glass-ceramics, and performing a crystallization heat treatment at 875 to 970 ° C; And
Grinding the glass-ceramics subjected to the crystallization heat treatment, and performing a porous heat treatment at a temperature of 700 to 840 ° C,
Wherein the porous body formed by the porous heat treatment has a pore size of 5 占 퐉 or less and a porous body has a relative density of 60 to 80%.
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| WO2022270973A1 (en) | 2021-06-25 | 2022-12-29 | 주식회사 하스 | Bulk block for manufacturing dental prosthesis |
| KR20230151120A (en) | 2022-04-22 | 2023-11-01 | 주식회사 하스 | Dental blank for dental prosthesis |
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| KR101141750B1 (en) | 2009-11-30 | 2012-05-09 | 한국세라믹기술원 | Manufacturing method of dental implant |
| JP5276175B2 (en) | 2008-09-12 | 2013-08-28 | ミッシェル サドゥン | Composite ceramic block |
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| KR101026853B1 (en) | 2008-02-27 | 2011-04-06 | 전북대학교산학협력단 | Borosilicate glass composition, and artificial tooth using the same and method for fabricating artificial tooth |
| US8696954B2 (en) | 2010-06-09 | 2014-04-15 | Tanaka Dental Products | Method, system, and composition for coloring ceramics |
| KR101961684B1 (en) | 2011-06-22 | 2019-03-26 | 비타 찬파브릭 하. 라우터 게엠베하 & 코.카게 | Dental restoration, method for its production and ingot |
| KR101609291B1 (en) * | 2014-06-30 | 2016-04-06 | 주식회사 하스 | Polymer infiltrated glass or glass-ceramic composites for dental blanks and preparation method thereof |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| JP5276175B2 (en) | 2008-09-12 | 2013-08-28 | ミッシェル サドゥン | Composite ceramic block |
| KR101141750B1 (en) | 2009-11-30 | 2012-05-09 | 한국세라믹기술원 | Manufacturing method of dental implant |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2022270973A1 (en) | 2021-06-25 | 2022-12-29 | 주식회사 하스 | Bulk block for manufacturing dental prosthesis |
| KR20230151120A (en) | 2022-04-22 | 2023-11-01 | 주식회사 하스 | Dental blank for dental prosthesis |
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