KR102582076B1 - Dental bulk block for cad/cam machining process and manufacturing method of the same - Google Patents

Abstract

The present invention is a glass ceramic block containing a crystalline phase within an amorphous glass matrix, wherein the main crystalline phase is lithium disilicate, and the additional crystalline phase is at least one selected from cristobalite and tridymite, and quartz. Disclosing a dental bulk block for cutting, which is a slope functional material made of (quartz) and lithium phosphate, has a slope of the main crystal phase size with respect to depth, and does not have an interface at the point of change in the slope value of the main crystal phase size. This is useful for manufacturing artificial tooth prosthesis similar to natural teeth. This not only shortens the time and process for manufacturing artificial tooth prosthesis, but also increases structural stability in terms of force dispersion through gradient functionalization of mechanical properties. It can bring about the same effect.

Description

Dental bulk block for cutting processing and manufacturing method thereof {DENTAL BULK BLOCK FOR CAD/CAM MACHINING PROCESS AND MANUFACTURING METHOD OF THE SAME}

The present invention relates to a dental bulk block for cutting processing, which is useful for manufacturing artificial teeth similar to the structural characteristics of natural teeth, and a method for manufacturing the same.

Crown material refers to a prosthetic material that restores the dentin and enamel of damaged teeth, and can be classified into inlays, onlays, veneers, crowns, etc. depending on the application area. Because the location where the crown material is restored is the outer surface of the tooth, great aesthetic properties are required, and high strength is required due to wear of the opposing tooth or fracture such as chipping. Materials currently used as crown materials include leucite glass-ceramics, reinforced porcelain, and fluorapatite (Ca ₅ (PO ₄ ) ₃ F) crystallized glass, which have excellent aesthetic properties but low strength. The disadvantage is that it is low at 80-120 MPa, so the possibility of fracture is high. Accordingly, research is currently underway to develop high-strength crown materials made of various materials.

Lithium silicate crystallized glass was discovered in 1973 by Marcus P. Borom and Anna M. Turkalo (The Pacific Coast Regional Meeting, The American Ceramic Society, San Francisco, CA, October 31, 1973 (Glass division, No.3-G-73P)). It was introduced by .

The crystal phase and strength of Li ₂ O-Al ₂ O ₃ -SiO ₂ -Li ₂ OK ₂ OB ₂ O ₃ -P ₂ O ₅ glass were studied under various crystal nucleus formation and growth heat treatment conditions. When forming a high-temperature lithium disilicate crystalline phase from a low-temperature lithium metasilicate, a strength of 30 to 35 KPS was shown, which is the residual stress due to the difference in thermal expansion coefficients of the matrix glass, moyuri, Li ₂ SiO ₅ , and Li ₂ SiO ₃ phases. It was because.

Materials and methods for manufacturing artificial teeth (monolithic dental crowns) using glass containing lithium disilicate crystals are already known in several patents. However, known technologies have a large crystalline size, making it difficult to machine them directly. For processing, a lithium metasilicate crystalline phase (machinable crystalline) is first formed and processed, and then a second heat treatment is performed to form a high-strength lithium disilicate crystalline phase. It goes through a forming method, and in this case, the accuracy of the dimensions decreases due to shrinkage due to the post-heat treatment process, and there is the inconvenience of having to add a heat treatment process. In general, prosthesis processing using CAD/CAM requires the hospital to directly process the bulk material to produce the prosthesis and try it on the patient as quickly as possible (one-day appointment), so the time delay due to the heat treatment process is not economical for the patient and user. adds to the difficulty.

In addition, the existing lithium disilicate crystallized glass material has limitations in realizing high light transmittance or opalescence similar to natural teeth due to its coarse crystal phase.

In particular, the existing lithium disilicate crystallized glass material is first made into lithium metasilicate crystallized glass with good processability for processing, and after processing, lithium disilicate is formed through secondary crystallization heat treatment to improve strength. At this time, the size of the crystal phase was about 3 ㎛ or more, and in this state, processability was significantly reduced and only the strength part could be realized.

In order to solve this problem, the present applicant proposed a method for manufacturing crystallized glass containing a lithium disilicate crystal phase and a silicate crystal phase with excellent processability by controlling the crystal size by changing the primary heat treatment temperature, and has already received a patent (Domestic Patent Registration 10- 1975548). Specifically, here, 60-83% by weight of SiO ₂ , 10-15% by weight of Li ₂ O, 2-6% by weight of P ₂ O ₅ that acts as a nucleation agent, increases the glass transition temperature and softening point, and increases the chemical durability of glass. 1 to 5% by weight of Al ₂ O ₃ to increase the softening point of the glass, 0.1 to 3% by weight of SrO, 0.1 to 2% by weight of ZnO, 1 to 5% by weight of colorant, and increase the coefficient of thermal expansion of the glass. Performing primary heat treatment at 400°C to 850°C on a glass composition containing 2.5 to 6% by weight of Na ₂ O+K ₂ O, which is an alkali metal oxide; A step of performing a secondary heat treatment at 780°C to 880°C after the first heat treatment, wherein a nano-sized lithium disilicate crystal phase and a silica crystal phase of 5 nm to 2000 nm are generated by the first heat treatment, and the secondary heat treatment A method for manufacturing crystallized glass for teeth containing a silica crystal phase is disclosed, wherein light transmission is controlled by heat treatment temperature.

Meanwhile, as human living standards improve, the demand for aesthetics is increasing in the field of dentistry. As patients' aesthetic needs are increasing, much research is being conducted on aesthetic prosthetic restorations using various materials.

As an aesthetic restorative material that is currently mainly used, factors that affect the aesthetics of ceramic restorations include the appearance of the tooth, surface condition, transparency, and color tone. Among these, transparency can be said to be an important factor for successful restoration production. Although there has been much research and development on the mechanical and physical properties of ceramic materials for aesthetic prosthetics, there are still many problems with color harmony, and from a clinical and technical perspective, the color selection of restorations, especially transparency, is difficult. There are many difficulties.

In aesthetic prosthodontics, factors that affect aesthetics during tooth restoration include color, shape and size of teeth, arrangement and proportions of teeth, light, transparency, design of restorations, etc., and are actually sensitive to our eyes. What appears can be said to be color and form.

Natural teeth have no part of the same color from the neck to the cutting edge.

Reflecting this point, a method of manufacturing artificial teeth that can imitate the deep color of natural teeth using the so-called build-up method has also been known.

The build-up method is a method of forming colored artificial teeth by layering powders such as porcelain or zirconia and then heat-treating them to achieve a color similar to natural teeth layer by layer. Although it is quite similar to the color of natural teeth, Although it can be imitated, the aesthetics of the artificial tooth are determined entirely by the technician's skill, which results in low reproducibility, is not advantageous to the patient as it cannot be manufactured in an immediate manner, and requires cutting processing such as CAD/CAM. There are problems with this method that make it difficult to implement.

On the other hand, when artificial teeth are manufactured using existing bulk blocks using cutting processing methods such as CAD/CAM, the bulk blocks themselves are made of materials with uniform physical properties, so the resulting artificial teeth, unlike natural teeth, are single. It had no choice but to be obtained in a tinted form. In particular, in the case of artificial teeth using this method, when applied to front teeth, etc., there is bound to be a problem in that they give an aesthetically heterogeneous feeling and are less natural.

Although transparency and processability can be adjusted through the secondary heat treatment process through the crystallized glass manufacturing method described in the above-mentioned domestic patent registration No. 10-1975548 by the present applicant, the obtained crystallized glass also has the same physical properties as one block itself. In order to use this to realize deep colors like natural teeth, it is necessary to apply a method of combining multiple results. In other words, it was not easy to immediately create natural-colored teeth by directly applying cutting processing such as CAD/CAM using the bulk block itself.

By improving these points, the present applicant is useful in manufacturing artificial tooth prosthesis similar to natural teeth. Through this, not only can the time and process for manufacturing artificial tooth prosthesis be shortened, but also in terms of force dispersion through gradient functionalization of mechanical properties. An application has been filed and registered for a bulk block that can provide increased structural stability (Korean Patent Registration No. 10-2246195).

The present invention was conceived to provide a gradient bulk block with improved aesthetic properties such as permeability and shade, more similar to natural teeth in physical properties, and improved machinability.

The present invention is a cutting process that can be used to manufacture artificial tooth restorative materials that exhibit multi-gradation permeability or physical properties similar to natural teeth with repeatability without the addition of other processes through cutting processing such as CAD/CAM. We would like to provide dental bulk blocks for processing.

The present invention can also shorten the time and process for manufacturing artificial tooth prosthesis, and can also bring about increased structural stability in terms of force dispersion through gradient functionalization of mechanical properties, which can be used in dentistry for cutting processing. We would like to provide bulk blocks for use.

The present invention also aims to provide a method for simply manufacturing dental bulk blocks for cutting that can be used in the manufacture of artificial tooth restorative materials that exhibit multi-gradation permeability and physical properties similar to natural teeth. do.

The present invention also seeks to provide a method of easily manufacturing dental bulk blocks into dental restorations using a processing machine.

One embodiment of the present invention is a glass ceramic block including a crystalline phase in an amorphous glass matrix, wherein the main crystalline phase is lithium disilicate and the additional crystalline phase is at least one selected from cristobalite and tridymite. is a dental material for cutting processing that is made of quartz and lithium phosphate, has a slope of the main crystal phase size with respect to depth, and is a slope functional material with no interface at the point of change in the slope value of the main crystal phase size. Bulk blocks are provided.

In a preferred embodiment of the present invention, the inclination of the size of the main crystal phase may be such that its average particle diameter is within the range of 0.05㎛ to 1.5㎛.

The dental bulk block according to one embodiment of the present invention may also have a gradient of light transmittance with respect to depth.

In a preferred embodiment, the slope of light transmittance may be in the range of 28 to 37% based on a wavelength of 550 nm.

In a preferred embodiment, the slope of light transmittance may change within a range of 0.5 mm or less with respect to depth.

In a preferred embodiment, the slope of light transmittance may change within a range of 0.31 mm with respect to depth.

The dental bulk block according to one embodiment of the present invention also has slopes of L ^* , a ^* and b ^* values according to color difference analysis with respect to depth, and the color deviation (ΔE) value changes even within the range of 0.31 mm with respect to depth. It may be.

The dental bulk block according to a preferred embodiment may have a crystallinity of 35 to 70%.

The dental bulk block according to one embodiment of the present invention may also have a biaxial bending strength gradient with respect to depth.

In a preferred embodiment, the slope of the biaxial bending strength may be in the range of 280 MPa to 450 MPa.

The dental bulk block according to one embodiment of the present invention may be made of a continuous glass matrix.

In a preferred embodiment, the glass matrix contains 69.0-75.0% by weight of SiO _{2 ,} 12.0-14.0% by weight of Li ₂ O , 2.5-5.5% by weight of Al ₂ O ₃ , 0.23-0.6% by weight of ZnO, and 2.8-3.5% by weight of K ₂ O Weight%, Na ₂ O 0.3 to 1.0 weight% and P ₂ O ₅ 2.0 to 6.0 weight%, and the Al ₂ O ₃ /(K ₂ O+ZnO) molar ratio may satisfy 1.0 to 1.6.

In another embodiment of the present invention, SiO ₂ 69.0-75.0% by weight, Li ₂ O 12.0-14.0% by weight, Al ₂ O ₃ 2.5-5.5% by weight, ZnO 0.23-0.6% by weight, K ₂ O 2.8-3.5% by weight %, 0.3 to 1.0% by weight of Na ₂ O and 2.0 to 6.0% by weight of P ₂ O ₅ , and melting a glass composition satisfying the Al ₂ O ₃ /(K ₂ O+ZnO) molar ratio of 1.0 to 1.6, Manufacturing a block of a predetermined shape including forming and cooling in a mold and annealing from 480° C. to 280° C. at a set rate for 20 minutes to 2 hours; and

A method of manufacturing a dental bulk block for cutting processing is provided, which includes the step of heat treating the block at a temperature range of 760 to 880° C. and applying a temperature gradient in the depth direction of the block.

In the method of manufacturing a dental bulk block according to a preferred embodiment, the heat treatment step is performed so that the upper layer of the block is applied at a temperature range of 840 to 880 ° C. and the lower layer of the block is applied at a temperature range of 760 to 800 ° C. You can.

In a preferred embodiment, the heat treatment step may be performed in a gradient heat treatment furnace at an operating temperature of 900 to 1,100° C. for 1 to 40 minutes.

One embodiment of the present invention also includes the steps of manufacturing a predetermined dental restoration by processing the dental bulk blocks for cutting of the above embodiments using a processing machine; and polishing or glazing.

In the method of manufacturing a dental restoration according to a preferred embodiment, glazing may be performed at 730 to 820° C. for 30 seconds to 10 minutes.

Glazing within the above range may correspond to conventional glazing in a range that does not impair the inherent light transparency of the dental restoration obtained from the previous step.

As another example, glazing may be performed as a step of adjusting the light transmittance of the dental restoration obtained from the previous step to a certain extent according to the user's needs. In this respect, glazing is performed through heat treatment at at least 825°C to improve the processed dental restoration. It can be used to control light transmittance. At this time, preferably, glazing may be performed at a temperature of at least 825°C for 1 to 20 minutes. In particular, the light transmittance decreases after a temperature of 840°C, so if you want to further lower the light transmittance, you can further increase the glazing temperature to allow additional crystallization to a certain extent.

The bulk block of the present invention can be easily applied to the manufacture of artificial tooth restorative materials with multi-gradation light transmittance or physical properties similar to natural teeth, and can be used to create teeth whose light transmittance is adjusted through a simple heat treatment method on the user's side. There is an advantage in that restorations can be obtained, contributing to the simplification of logistics management.

The dental bulk block according to the present invention is used for the manufacture of artificial tooth restorative materials with multi-gradation light transmission and physical properties similar to natural teeth with repeatable reproducibility without adding other processes through cutting processing such as CAD/CAM, etc. It can be easily used, and not only can it shorten the time and process for manufacturing artificial tooth prosthesis, but it can also have the effect of increasing structural stability in terms of force dispersion through gradient functionalization of mechanical properties, and this dental bulk The block has the advantage of being manufactured through a simple method of gradient heat treatment using a single glass composition having a specific composition.

1 is a graph showing the results of X-ray diffraction analysis of the bulk block of the present invention.
Figure 2 is a scanning electron microscope (SEM) photograph showing the microstructure and crystal phase size at each depth of the bulk block of the present invention.
Figure 3 is a visible light transmittance measurement graph for 0.31 mm thick slice specimens of the bulk block of the present invention.
Figure 4 is a comparative graph of cutting resistance for the bulk block of the present invention.
Figure 5 is a schematic diagram showing a method of manufacturing a dental bulk block of the present invention as an example.
Figure 6 is a graph showing the particle size of the main crystal phase according to the depth of the bulk block obtained according to one embodiment of the present invention.
Figure 7 is a graph showing the change in biaxial bending strength by depth of the bulk block obtained according to one embodiment of the present invention.

The foregoing and additional aspects of the present invention will become more apparent through preferred embodiments described with reference to the accompanying drawings. Hereinafter, these embodiments of the present invention will be described in detail so that those skilled in the art can easily understand and reproduce them.

The dental bulk block for cutting of the present invention is a glass ceramic block containing a crystalline phase within an amorphous glass matrix. The main crystalline phase is lithium disilicate, and the additional crystalline phase is selected from cristobalite and tridymite. At least one type, quartz and lithium phosphate, is a gradient functional material that has a gradient of the main crystal phase size with respect to depth and has no interface at the point of change in the gradient value of the main crystal phase size.

In the description above and below, the term main crystal phase is defined as a crystal phase that accounts for at least 80% by weight of the total crystal phase, and the term additional crystal phase may be defined as the remaining crystal phase other than the main crystal phase among the total crystal phases.

The content of the crystal phase can be calculated through X-ray diffraction analysis. For example, in a specimen consisting of two polymorphs a and b, the ratio F _a of the crystal phase a is quantitatively expressed by the following equation 1.

This value can be obtained by measuring the intensity ratio of the two crystal phases and obtaining the constant K. K is the absolute intensity ratio of the two pure polymorphs, I _oa /I _ob , and is obtained by measuring a standard material.

In the description above and below, the term main crystal phase may be defined as being set based on the content calculated according to this method.

In addition, 'having a gradient of the size of the main crystal phase with respect to depth' means that when graphing the size of the main crystal phase according to the depth of the bulk block, there is a gradient of change in the size of the main crystal phase. That is, this means that the size of the main crystal phase is expressed in a gradation with respect to the depth of the bulk block.

In addition, 'the point of change in the slope value of the main crystal phase size' refers to the point where the slope value of the change in the size of the main crystal phase substantially changes when graphing the size of the main crystal phase according to the depth of the bulk block. Here, the meaning of 'substantial change' may mean change as a single number, but of course it can also include substantial change in light of the distribution of the value.

In addition, 'no interface exists at the point where the slope value of the main crystal phase size changes' means that there is no significant boundary surface indicating interlayer separation at the depth of the bulk block that indicates the change in the slope value of the main crystal phase size. It can be interpreted as In other words, this means that the bulk block has a gradient of the size of the main crystal phase in a continuous form without an interface depending on the depth.

Meanwhile, 'Functionally Gradient Material (FGM)' refers to a material in which the properties of the constituent material continuously change from one side to the other. In the present invention, there is substantially no interface, but the constituent material The expression ‘inclined functional material’ is adopted from the aspect that the properties of the material continuously change.

In the description above and below, the bulk block is not limited in its shape, and can be used in various shapes such as block shape, disk shape, ingot shape, cylinder shape, etc. Of course, it can be included.

The bulk block according to the present invention has a main crystal phase of lithium disilicate and an additional crystal phase of at least one selected from cristobalite and tridymite, quartz, and lithium phosphate. It does not include other crystal phases other than the crystal phases described above.

The graph of the XRD analysis results for the bulk block according to a preferred embodiment may be as shown in FIG. 1.

In Figure 1, the main crystal phase of the dental bulk block according to an embodiment of the present invention is lithium disilicate. In addition, the main peak appears at 2θ = 21.7 (degree) as an additional crystal phase, which is a homogeneous ideal of SiO ₂ called cristobalite (JCPDS #39-1425, 2θ = 21.83 (degree) main peak) or tridymite. , JCPDS #01-0378, 2θ=21.76(degree)). As another additional crystal phase, the main peak appears at 2θ = 20.8, 26.3 (degree), which is low-temperature quartz (α-quartz, JCPDS #83-0539, 2θ = 20.8, 26.6 (degree), which is an isomorph of SiO ₂ can be interpreted as a major peak). As another additional crystal phase, the main peak appears at 2θ = 22.18, 22.9 (degree), which can be defined as lithium phosphate (JCPDS #15-0760, main peak at 2θ = 22.3, 23.1).

In the above and below descriptions, XRD analysis was performed using an ), Rigaku, Japan).

This crystalline phase can be formed into microcrystals and has the properties of various sizes and size distributions depending on temperature, and the ability to implement various mechanical properties and light transmittance.

In addition, by having a gradient of the size of the main crystal phase with respect to depth, the bulk block can implement gradient light transmission and mechanical properties with respect to depth. Moreover, since there is no interface at the point of change in the inclination value of the main crystal phase size, processing through interlayer bonding is not necessary and the problem of layer separation during cutting processing can be resolved. In addition, this tilt functionalization can provide an artificial tooth prosthesis with increased structural stability in terms of force distribution.

In the bulk block of the present invention, the gradient of the main crystal phase size can be realized within the average particle diameter range of 0.05㎛ to 1.5㎛.

As an example, Figure 2 shows a scanning electron microscope (SEM) photograph of the dental bulk block of the present invention. Figure 2a shows the low temperature part (block bottom) of the block subjected to gradient heat treatment, Figure 2b shows the medium temperature part, and Figure 2c shows the high temperature part (bottom of the block). block upper layer). Specifically, Figure 2a shows an SEM picture of the lower part of the block (depth 20 mm), Figure 2b shows an SEM picture of the middle part (depth 10 mm), and Figure 2c shows an SEM picture of the upper part of the block (depth 0.5 mm).

Through the SEM photo obtained in this way, the average size of crystalline particles can be derived. Specifically, by drawing a diagonal or random straight line on the SEM photo, dividing the number of crystal phases through which the straight line passes by the length of the straight line, and taking the magnification into consideration, the linear intercept It can be obtained according to the method.

In the description above and below, it will be understood that the size of the crystal phase was calculated according to this method.

The bulk block of the present invention is an inclined functional material, and as such inclined functional material is applied to cutting processing, for example, CAD/CAM processing, etc. under the same processing conditions, machinability is taken into consideration, and the permeability that can be used clinically, such as artificial tooth restorative material, is achieved. In terms of expression, it may be desirable for the gradient of the main crystal phase size to have an average particle diameter within the range of 0.05㎛ to 1.5㎛.

The dental bulk block of the present invention has a gradient of light transmittance with respect to depth according to the gradient of the main crystal phase size as described above.

In particular, considering the range of average particle diameter in terms of the slope of the crystalline size described above, the slope of light transmittance may be in the range of 28 to 37% based on a wavelength of 550 nm.

In the description above and below, light transmittance was measured using a UV-visible spectrometer (UV-2401PC, Shimadzu, Japan).

As described above, the dental bulk block of the present invention does not have an interface at the point of change in the inclination value of the main crystal phase size. In this respect, the inclination of light transmittance changes within a range of 0.5 mm or less with respect to depth, and substantially changes in depth. It can be confirmed that it changes even within the range of 0.31mm.

To measure the light transmittance at each gradient position for the dental bulk block according to the present invention, cut about 0.31 mm in the depth direction where transparency decreases, clean the specimen surface using ethanol, and use a UV-visible spectrometer (UV-2401PC, Shimadzu). , Japan) was used. At this time, the measurement wavelength range was 300-800 nm, and the slit width was 2.0 nm. It can be seen from the results in Figure 3 that there is a difference in transmittance between slice specimens with a thickness of 0.31 mm.

In Figure 3, each specimen corresponds to a specimen by depth in Table 1 below.

Psalm No. depth(mm) One 0.31 2 0.62 3 0.93 4 1.24 5 1.55

This result can be seen as meaning that the light transmittance value changes with respect to depth even within the range of 0.31 mm, that is, gradient transmittance appears even at this thickness. This can be said to be a result that clearly shows that the dental bulk block of the present invention is an inclined functional material.

In addition, it can be seen from the results of these permeability that it is possible to provide artificial teeth with excellent aesthetics and appropriate hiding properties.

In another aspect, the dental bulk block of the present invention has a gradient in shade, specifically, a gradient of L ^* , a ^* and b ^* values according to color difference analysis with respect to depth. As described above, the dental bulk block of the present invention does not have an interface at the point of change in the inclination value of the main crystal phase size. In this respect, it can be confirmed that the color deviation (ΔE) value changes with respect to depth even within the range of 0.31 mm. there is.

Color standardization became necessary for accurate measurement, transmission, and reproduction of colors, and thus a color system was devised. Many color systems have been proposed, and the most widely used to date is the CIE L* a* b* color space (CIELAB color space) established by the Commission International de l'Eclairage (CIE) in 1976. Here, L* represents lightness, and a* and b* represent chromaticity coordinates. In coordinates, L ^* indicates brighter colors as the value increases, and darker colors as it decreases, +a* means red, -a* means green, +b* means yellow, and -b* means blue.

In order to measure the color of the dental bulk block according to the present invention at each gradient position, it was cut by about 0.31 mm in the depth direction where transparency decreases, the surface of the specimen was wiped clean using ethanol, and the surface of the specimen was cleaned using a UV-visible spectrometer (UV-2401PC, Shimadzu, Japan) was used for analysis. At this time, the measurement wavelength range was 380-780 nm, and the slit width was 2.0 nm. After setting the baseline using the reference sample, the reflectance of the specimen was measured to obtain the L ^* a ^* b ^* colorimetric system. The measured L ^* a ^* b ^* value was repeated three times and the average value was used to reduce errors. Using these three values, ΔE, which represents the difference in color, was calculated. If the ΔE value of the two specimens is 0, it means that there is no difference in color, and a value between 0 and 2 means that there is a very slight color difference. A value of 2 to 4 means that the color difference is noticeable (noticeable), and a value of 4 to 6 means that the color difference is easily (appreciable) distinguished. A value of 6 to 12 means that the color difference remains much, and over 12 means that the color difference remains very much.

A glass ceramic block containing a crystalline phase in an amorphous glass matrix as shown in Figures 1 and 2, wherein the main crystalline phase is lithium disilicate and the additional crystalline phase is at least one selected from cristobalite and tridymite, and quartz. (quartz) and lithium phosphate, has a slope of the main crystal phase size with respect to depth, and has no interface at the point of change in the slope of the main crystal phase size. For the dental bulk block, a 0.31 mm thick block is a slope functional material. It can be confirmed from the results in Table 2 below that the color deviation (ΔE) with respect to depth for the slice specimens was 0.9 to 4.8. This result can be seen as meaning that the color deviation (ΔE) value changes with respect to depth even within the range of 0.31 mm, that is, a gradient shade with a different color appears even at this thickness. In another aspect, this can be said to be a result that clearly shows that the dental bulk block of the present invention is an inclined functional material.

Psalm No. depth(mm) L ^* a ^* b ^* ΔE One 0.31 68.82 -1.65 9.42 2 0.62 70.80 -1.71 11.50 4.7791 3 0.93 71.20 -2.00 11.80 0.9949 4 1.24 72.10 -2.40 12.00 1.2247 5 1.55 74.40 -3.00 11.20 1.9235

Additionally, the dental bulk block of the present invention has a biaxial bending strength gradient depending on the depth. In particular, considering the range of average particle size in the above-described crystalline size gradient, the biaxial bending strength gradient may be within the range of 280 MPa to 450 MPa.

Meanwhile, the dental bulk block of the present invention may preferably have a crystallinity of 35 to 70% in consideration of processability and the aspect of being able to realize the functional gradient of various physical properties as described above.

In the description above and below, 'crystallinity' can be defined as the ratio of the crystalline phase to the amorphous glass matrix, which can be obtained through various methods. In one embodiment of the present invention, through an X-ray diffraction analyzer. This is an automatically calculated value.

The dental bulk block of the present invention is a glass ceramic in which a crystalline phase is precipitated within a continuous amorphous glass matrix. The main crystalline phase is lithium disilicate and the additional crystalline phase is at least one selected from cristobalite and tridymite, and quartz ( It is possible to obtain a gradient functional material that includes a crystal phase composed of quartz and lithium phosphate crystal phases, has a gradient of the size of the main crystal phase with respect to depth, and has no interface at the point of change in the gradient value of the size of the main crystal phase.

In the description above and below, the term “continuous glass matrix” may be defined as one in which no interlayer interface exists within the glass matrix and the composition constituting the glass matrix is the same within the entire block.

The preferred glass matrix specifically contains 69.0-75.0% by weight of SiO ₂ , 12.0-14.0% by weight of Li ₂ O , 2.5-5.5% by weight of Al ₂ O ₃ , 0.23-0.6% by weight of ZnO, 2.8-3.5% by weight of K ₂ O, and Na. It may contain 0.3 to 1.0% by weight of ₂ O and 2.0 to 6.0% by weight of P ₂ O ₅ , and the Al ₂ O ₃ /(K ₂ O+ZnO) molar ratio may satisfy 1.0 to 1.6.

The glass composition precipitates a crystalline phase in an amorphous glass matrix through crystal nucleation and crystal growth heat treatment to generate crystallization. The temperature of the above-described glass matrix at which crystal growth occurs is 760°C to 880°C. That is, crystal nuclei begin to form at a minimum of 490°C and crystal growth occurs as the temperature rises, and this crystal growth shows the lowest light transmittance for use as artificial teeth at a maximum of 880°C. In other words, the light transmittance gradually decreases from the temperature at which crystals are grown up to 880°C. Considering this crystal growth, if this is implemented in one bulk block, it can imitate the multi gradation of natural teeth. do.

In natural teeth, not only one tooth itself but all teeth have various light transmittances, and if these changes in light transmittance according to heat treatment temperature can be embodied in one bulk block, multi-gradation of natural teeth can be sufficiently realized.

From this point of view, the present invention is SiO ₂ 69.0-75.0% by weight, Li ₂ O 12.0-14.0% by weight, Al ₂ O ₃ 2.5-5.5% by weight, ZnO 0.23-0.6% by weight, K ₂ O 2.8-3.5% by weight, Na Melting a glass composition containing 0.3 to 1.0% by weight of 2 O and 2.0 to 6.0% by weight of P ₂ O ₅ and satisfying the Al ₂ O ₃ /(K ₂ O+ZnO ₎ molar ratio of 1.0 to 1.6, and forming it in a mold. and cooling and annealing from 480°C to 280°C at a set rate for 20 minutes to 2 hours to produce a block of a predetermined shape; and

A method of manufacturing a dental bulk block for cutting processing is provided, which includes the step of heat treating the block at a temperature range of 760 to 880° C. and applying a temperature gradient in the depth direction of the block.

As mentioned above, the glass composition can exhibit characteristics in which the light transmittance of the material varies depending on the heat treatment temperature range. When heat treatment is applied uniformly to the entire block, it exhibits constant light transmittance, but the heat treatment creates a temperature gradient to the block. When applied, multiple gradations of physical properties or light transmission can be expressed in one block.

In the case of bulk blocks, they are used as workpieces for machining such as CAD/CAM processing. The manufacturing method of the present invention improves light transmittance and strength by applying heat by applying a temperature gradient in the depth direction when heat treating the block. It can be manufactured as a multi-graded bulk block.

Conventional crystallized glasses generally have a coarse crystal size, making it difficult to control light transmission, and their strength is also strong, making processing difficult. However, in the case of the glass composition adopted in the present invention, it is possible to form microcrystals, which have various sizes and size distributions depending on temperature. Each of the physical properties and light transmittance can appear in various ways, reflecting this advantage by manufacturing a block from a single glass composition and then heat-treating it with a temperature gradient to improve the mechanical properties and light transmittance of one bulk block. It has become possible to embody multi-gradation.

At this time, the meaning of 'the step of heat treatment by providing a temperature gradient in the depth direction of the block' is that not only can a sequentially increased temperature gradient be provided in the depth direction of the block from the bottom to the top, but also a partial temperature difference can be achieved. Temperature gradients can also be tolerated. Of course, the selection of this temperature gradient method may vary depending on the characteristics of the natural teeth of a patient requiring an artificial tooth prosthesis or may vary depending on the unique characteristics of the part of the tooth requiring the prosthesis.

However, considering normal natural values, it may be desirable to provide a heat treatment temperature gradient in such a way that the temperature gradually increases from the bottom to the top with respect to the depth of the block.

In a preferred example, the heat treatment step is performed so that the upper part of the block is applied to a temperature range of 840 to 880 ℃, and the lower part of the block is applied to a temperature range of 760 to 800 ℃. The actual heat treatment step for this temperature gradient is gradient heat treatment. It may be preferable to carry out the operation in a furnace at an operating temperature of 900 to 1,100° C. for 1 to 40 minutes.

When using the above-described heat treatment method of the present invention using the above-described glass composition, it is possible to imitate the characteristic of a natural tooth structure in which light transmittance is low toward the cervical side and light transmittance increases toward the incisal side. This can be very economically advantageous because there is no need to separately characterize the prosthesis as in the existing method.

In addition, the physical properties of natural teeth are that the enamel, which is the surface layer, has high bending strength, and the inner dentin has low strength, so it plays a role in absorbing and dispersing external forces. In the present invention, the mechanical properties, In particular, since it is possible to use an inclined functional material with a biaxial bending strength gradient, it is characterized by being able to reproduce the physical properties of natural teeth very similarly.

Manufacturing a dental restoration using the dental bulk block obtained according to the present invention can be expected to significantly improve processability. As a specific example, in one embodiment of the present invention, the dental bulk block described above is manufactured using a processing machine. Processing to produce a desired dental restoration; and polishing or glazing.

In the description above and below, it goes without saying that dental restorations include crowns, inlays, onlays, veneers, abutments, etc.

Here, glazing may be performed at 730 to 820°C for 30 seconds to 10 minutes, and in this case, it may be a typical finishing heat treatment step with little change in light transmittance due to heat treatment. Glazing is usually performed within the range that does not change the inherent light transmittance of the bulk block, and during glazing heat treatment, the strength can be increased by more than 50% while microcracks on the surface are alleviated (surface healing).

However, in a specific embodiment, in the method of manufacturing a dental restoration using a bulk block according to the present invention, glazing can be used to adjust the light transparency of the processed dental restoration through heat treatment at at least 825°C. . In other words, after processing the bulk block and manufacturing it into a dental restoration, glazing can be used to control brightness by reducing light transmission in the final finishing stage.

When manufacturing dental restorations by machining by the processor or user using a bulk block, there may be cases where the light transmittance is unintentionally changed to a high level. In this case, a typical lithium disilicate-based bulk block is used as the processed bulk block. The block must be discarded, undergo a predetermined heat treatment from the bulk block, reprocess the bulk block that satisfies the desired light transmittance, and then process it again into a dental restoration. However, in the case of the bulk block according to the present invention, it is a specific bulk block with a fine crystalline phase and can exhibit the characteristic of adjusting light transmittance depending on the heat treatment temperature, so reprocessing is not necessary and the workpiece processed into a dental restoration is finalized. Light transmittance can be easily adjusted again by going through a glazing process under predetermined conditions in the process. As a result, colored teeth generated during processing of dental restorations can be shielded in a simple way through glazing.

Glazing for this purpose is preferably carried out at a temperature of at least 825° C. for 1 to 20 minutes.

Characteristically, in the case of the dental bulk block obtained according to the present invention, when processing using a processing machine, the resistance generated in the tool during processing can be significantly reduced. As a specific example, an amorphous block as shown in Figures 1 and 2 A glass ceramic block comprising a crystalline phase within a glass matrix, wherein the main crystalline phase is lithium disilicate and the additional crystalline phase is at least one selected from cristobalite and tridymite, quartz, and lithium phosphate. Regarding the dental bulk block (this invention), which is a slope functional material that has a slope of the size of the main crystal phase with respect to depth and does not have an interface at the point of change in the slope value of the size of the main crystal phase, the size is 12 × 14 × 18 mm. The cutting time was measured by rotating at 250 RPM using a low-speed saw (IOMET low speed saw, Buehler, Germany) and a diamond electroplated wheel (2514485H17, Norton, USA). And in the same way, the most common lithium disilicate block (Rosetta SM, manufactured by HASS Corp), zirconia reinforced lithium disilicate bulk block (Celtra Duo, manufactured by DentsplySiron) and lithium Cutting time was measured for alumino silicate reinforced lithium disilicate bulk block (LAS reinforced lithium disilicate) (Nice, Straumann company).

Cutting resistance (%) was calculated from each cutting time value obtained in this way. Specifically, the cutting time obtained for a general lithium disilicate block was set as 100%, and the cutting time was converted to a relative percentage. This was calculated as each cutting resistance value.

The results are shown in Figure 4.

From the results in FIG. 4, the general lithium disilicate block had the highest cutting resistance, followed by LAS (lithium alumino silicate) crystallized glass and zirconia reinforced crystallized glass, and the block according to the present invention had the lowest cutting resistance. showed cutting resistance. From these results, it can be confirmed that the glass ceramic block of the present invention is the most machinable.

A specific embodiment of the present invention is first, SiO ₂ 69.0-75.0% by weight, Li ₂ O 12.0-14.0% by weight, Al ₂ O ₃ 2.5-5.5% by weight, ZnO 0.23-0.6% by weight, K ₂ O 2.8-3.5% by weight Weighing a glass composition containing 0.3-1.0% by weight of Na ₂ O and 2.0-6.0% by weight of P ₂ O ₅ , and having an Al ₂ O ₃ /(K ₂ O+ZnO) molar ratio of 1.0-1.6. Mix.

When Al ₂ O ₃ is added to silicate glass, it enters the tetrahedral site and acts as a glass former, increasing viscosity and reducing the mobility of ions. On the other hand, K ₂ O and ZnO lower the viscosity and increase the mobility of ions. It can be predicted that as the mobility of ions increases, the formation of cristobalite or tridymite grows in a preferential orientation. In addition, an increase in modifiers such as ZnO increases the mobility of ions, and when excessive amounts of SiO ₂ are included, minor crystal phases such as cristobalite, tridymite, and quartz are within the glass matrix along with lithium disilicate, which is the main crystal phase. It precipitates. In this respect, an Al ₂ O ₃ /(K ₂ O+ZnO) molar ratio of 1.0 to 1.6 is preferred for providing the bulk block of the present invention containing cristobalite, tridymite, or quartz as an additional crystal phase. You can.

Li ₂ CO ₃ may be added to the glass composition instead of Li ₂ O, and carbon dioxide (CO ₂ ), which is the carbon (C) component of Li ₂ CO ₃ , is discharged as a gas during the glass melting process. Additionally, in the alkaline oxide, K ₂ CO ₃ and Na 2 CO ₃ may be added instead of K ₂ O and Na ₂ O, respectively, and carbon dioxide (CO ₂ ), which is the carbon (C) component of K ₂ CO ₃ and _{Na 2 CO 3} ) is discharged as gas and escapes during the glass melting process.

Mixing uses a dry mixing process, and a ball milling process, etc. can be used as the dry mixing process. Looking at the ball milling process in detail, the starting raw materials are charged into a ball milling machine, and the ball milling machine is rotated at a constant speed to mechanically crush and mix the starting raw materials uniformly. The balls used in the ball mill can be made of ceramic materials such as zirconia or alumina, and the balls can all be the same size or have at least two different sizes. Considering the target particle size, adjust the ball size, milling time, and rotation speed per minute of the ball mill. For example, considering the size of the particles, the size of the ball can be set in the range of about 1 mm to 30 mm, and the rotation speed of the ball mill can be set in the range of about 50 to 500 rpm. Ball milling is preferably performed for 1 to 48 hours, considering the target particle size, etc. By ball milling, the starting materials are pulverized into fine-sized particles, have uniform particle sizes, and are uniformly mixed at the same time.

The mixed starting materials are placed in a melting furnace, and the melting furnace containing the starting materials is heated to melt the starting materials. Here, melting means that the starting material is changed from a solid state to a material state having the viscosity of a liquid state. It is desirable that the melting furnace be made of a material that has a high melting point, great strength, and a low contact angle to prevent the melt from sticking. To this end, platinum (Pt), diamond-like-carbon (DLC), chamotte, and It is preferable that the melting furnace is made of the same material or has a surface coated with a material such as platinum (Pt) or diamond-like-carbon (DLC).

Melting is preferably performed at 1,400 to 2,000°C and normal pressure for 1 to 12 hours. If the melting temperature is less than 1,400℃, the starting material may not be melted, and if the melting temperature exceeds 2,000℃, excessive energy consumption is required and it is not economical, so it is preferable to melt at a temperature within the above-mentioned range. do. Additionally, 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 economical. It is desirable that the temperature increase rate of the melting furnace is around 5 to 50℃/min. However, if the temperature increase rate of the melting furnace is too slow, it takes a long time and productivity decreases, and if the temperature increase rate of the melting furnace is too fast, the temperature rises rapidly, resulting in loss of starting raw materials. Since the amount of volatilization may increase and the physical properties of the crystallized glass may not be good, it is desirable to increase the temperature of the melting furnace at a temperature increase rate in the above-mentioned range. Melting is preferably performed in an oxidizing atmosphere such as oxygen (O ₂ ) or air.

The melt is poured into a designated mold to obtain dental crystallized glass of the desired shape and size. The forming mold is preferably made of a material that has a high melting point, high strength, and a low contact angle to suppress the sticking phenomenon of glass melt. To this end, it is made of a material such as graphite or carbon and is resistant to thermal shock. To prevent this, it is advisable to preheat to 200-300℃ and pour the melt into the mold.

As the melt contained in the mold is molded and cooled, it may be desirable to go through a step of annealing from 480°C to 280°C at a set rate for 20 minutes to 2 hours after the cooling process. This slow cooling step reduces the stress deviation within the molded product, preferably preventing stress from existing, which can have a desirable effect on controlling the size of the crystal phase and improving the homogeneity of crystal distribution in the subsequent crystallization step. , Thus, ultimately, the desired inclined functional material can be obtained.

The speed set here is preferably 1.6°C/min to 10°C/min.

The molded product that has undergone this slow cooling process is transferred to a crystallization heat treatment furnace to form nuclei and grow crystals to produce the desired crystallized glass.

Figure 5 schematically shows a method of performing crystallization heat treatment by providing a temperature gradient according to the present invention. In crystallization heat treatment of a block-type or ingot-type bulk block, the top is heat treated at high temperature according to the depth direction. temperature) and the bottom is heat treated by providing a temperature gradient to perform low temperature heat treatment.

In the above and below descriptions, the step of heat treatment by applying a temperature gradient is not limited to a specific device or method, but may be performed in a gradient heat treatment furnace, for example, and when considering the heat treatment temperature, the operating temperature is 900 to 900 degrees Celsius. It may be desirable to carry out at 1,100°C.

Through heat treatment with such a temperature gradient, the light transmittance has a gradient of high transmittance from the high temperature portion to the low temperature portion, and the biaxial flexural strength has a gradient of low flexural strength. This is because the crystal size within the crystallized glass can be adjusted depending on temperature. The crystalline phase generated after heat treatment with a temperature gradient includes lithium disilicate, at least one additional crystalline phase selected from cristobalite and tridymite, quartz, and lithium phosphate crystalline phases, and a temperature gradient of 760 to 880°C. It can be produced to have a size gradient of the main crystal phase with an average particle diameter of 0.05㎛ to 1.5㎛.

Meanwhile, the crystalline particle size of the bulk block obtained according to the present invention was analyzed with respect to depth, and this is shown in Figure 6.

In addition, the change in biaxial bending strength with respect to depth was measured for the bulk block obtained according to the present invention, and this is shown in Figure 7.

The present invention has been described with reference to an embodiment shown in the drawings, but this is merely illustrative, and those skilled in the art will understand that various modifications and other equivalent embodiments are possible therefrom. .

Claims (19)

delete delete delete delete delete delete delete delete delete delete delete delete SiO ₂ 69.0-75.0% by weight, Li ₂ O 12.0-14.0% by weight, Al ₂ O ₃ 2.5-5.5% by weight, ZnO 0.23-0.6% by weight, K ₂ O 2.8-3.5% by weight, Na ₂ O 0.3-1.0% by weight % and P ₂ O ₅ 2.0 to 6.0% by weight, and the Al ₂ O ₃ /(K ₂ O+ZnO) molar ratio satisfies 1.0 to 1.6. A glass composition is melted, formed and cooled in a mold, and heated to 480°C. Manufacturing a block of a predetermined shape, including annealing at a set rate from 280° C. to 280° C. for 20 minutes to 2 hours; and
Heat-treating the block at a temperature range of 760 to 880°C, comprising heat-treating the block by applying a temperature gradient in the depth direction of the block.
Method for manufacturing dental bulk blocks for cutting processing.
The method of claim 13, wherein the heat treatment step is performed so that the upper layer of the block is applied at a temperature range of 840 to 880 ° C. and the lower layer of the block is applied at a temperature range of 760 to 800 ° C.
Method for manufacturing dental bulk blocks for cutting processing.
The method of claim 13 or 14, wherein the heat treatment step is performed in a gradient heat treatment furnace at an operating temperature of 900 to 1,100° C. for 1 to 40 minutes.
Method for manufacturing dental bulk blocks for cutting processing.
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