Method for manufacturing customized denture using self-transforming ni-ti alloy treatment material for 4d printing and denture manufactured thereby

Abstract

The present invention relates to a method for manufacturing a customized denture using a self-transforming Ni-Ti alloy treatment material for 4D printing and a denture manufactured by the method and, more specifically, to a method for manufacturing a customized denture using a self-transforming Ni-Ti alloy treatment material for 4D printing and a denture manufactured by the method, wherein a rough treatment material shape is prepared by a 4D printing process using a human-friendly shape memory alloy (Ni-Ti alloy) powder, and then subjected to shape memory heat treatment (200-300℃) for patient-customized shape memory, followed by external stimulation (pressure, temperature, etc.), thereby manufacturing a precise self-transforming treatment material, that is, a denture, so that the denture is easy for manufacturing and dimension processing and is improved to enable a firm clasp without wobbling during use, ensuring no discomfort during use.

Description

Method for manufacturing customized dentures using self-deforming NI-TI alloy 4D printing therapeutic material and dentures manufactured by the method

[0001] The present invention relates to a method for manufacturing a customized denture using a self-deforming Ni-Ti alloy 4D printing treatment material and a denture manufactured by the method, and more particularly, to a method for manufacturing a customized denture using a self-deforming Ni-Ti alloy 4D printing treatment material, which is improved to be convenient to manufacture, easy to process in dimension, and to hold firmly without shaking during use, by manufacturing a rough shape of a treatment material by a 4D printing process using a human-friendly shape-memory alloy (Ni-Ti alloy) powder, and then performing shape memory heat treatment (200 to 300°C) for patient-tailored shape memory, and then manufacturing a precise self-deforming treatment material, i.e., a denture, by an external stimulus (pressure, temperature, etc.), and to a denture manufactured by the method.

[0002] As life expectancy and the population aged 65 and over accelerate globally, dental care is one of the areas that is gaining the most attention amidst the increasing healthcare spending for the elderly population.

[0003] According to the OECD, among G20 member countries, excluding Argentina and Saudi Arabia, the proportion of the population aged 65 and over is expected to be the highest in Japan in 2030 at 31.8%, followed by Germany at 27.8%, Italy at 27.3%, and Korea at 24.3% (OECD facebook 2009).

[0004] Meanwhile, in countries with large populations such as China and India, along with Korea, the aging of the population is expected to progress rapidly. In 2000, the population aged 65 or older accounted for 7.2%, already entering an aging society. It is expected to reach 14.4% in 2019 and 20% in 2026, becoming a super-aged society (Data: Statistics Korea, 2012, Future Population Projections).

[0005] At this time, the increase in periodontal disease and gingivitis and the increase in the elderly population are expected to increase the demand for complete dentures and partial dentures, and dental diseases have been revealed to be the biggest problem due to aging worldwide.

[0006] In preparation for this aging population, advanced dental medical device manufacturers in Europe, the United States, and Japan are developing various medical devices and commercializing specialized materials to adapt to market changes. When placed in the patient's oral cavity, products that are convenient for chewing and do not shake are required as fixed partial dentures.

[0007] In addition, the basic structure of partial dentures is composed of a metal framework, clasp, and replacement teeth as shown below. The metal frame is mainly made of Co-Cr or Ni-Cr alloy, and is then made by centrifugal casting after making a lead mold.

[0008] [Correction pursuant to Rule 91, October 24, 2023]

[0009] However, this type of cast denture has the inconvenience of a complex manufacturing process and breakage due to repeated attachment and detachment of the clasp portion when placed in the oral cavity.

[0010] In particular, the casting method for Co-Cr alloys requires post-processing (heat treatment, polishing, etc.), which causes many difficulties such as the need for multiple processes and the occurrence of casting defects.

[0011] The present invention is to solve the above-described problems, and the purpose of the present invention is to provide a method for manufacturing a customized denture using a self-deforming Ni-Ti alloy 4D printing treatment material that is convenient to manufacture, easy to process in dimension, and holds firmly without shaking during use by manufacturing a rough shape of a treatment material by a 4D printing process using a human-friendly shape memory alloy (Ni-Ti alloy) powder and then performing shape memory heat treatment (200 to 300°C) for patient-tailored shape memory, and then manufacturing a precise self-deforming treatment material, i.e., a denture, by an external stimulus (pressure, temperature, etc.), and thereby providing an improved method for manufacturing a customized denture using a self-deforming Ni-Ti alloy 4D printing treatment material that is convenient to manufacture, easy to process in dimension, and has no inconvenience in use by not shaking when used.

[0012] The present invention provides a method for manufacturing customized dentures using a self-deforming Ni-Ti alloy 4D printing treatment material, comprising: a data collection step of collecting information on teeth and gums of a patient to whom dentures are to be applied; a scan value processing step of correcting the shape and dimensions of a denture to be applied to the patient based on the tooth and gum information collected in the data collection step; a material preparation step of preparing a denture processing material using shape memory alloy powder; a printing step of printing a denture by processing the shape memory alloy material with a 3D printer according to the denture shape and dimensions corrected in the scan value processing step; and a post-processing step of polishing the denture printed in the printing step, wherein the post-processing step comprises a first step of performing shape memory heat treatment after 3D printing, a second step of removing residual material after the heat treatment, a third step of performing surface treatment after removing the residual material, a fourth step of polishing after the surface treatment, and a fifth step of performing UV curing after the polishing.

[0013] At this time, the shape memory alloy powder formed in the material preparation step is, for 100 parts by weight of Ni-Ti, Ag-Cd: 44-49 parts by weight, Au-Cd: 46.5-50 parts by weight, Cu-Al-Ni: 14-14.5 parts by weight, Cu-Sn: 15-15.5 parts by weight, Cu-Zn: 38.5-41.5 parts by weight, Cu-Zn-X (X=Si,Al,Sn): 5-10 parts by weight, Fe-Pt: 20-25 parts by weight, Mn-Cu: 5-35 parts by weight, Fe-Mn-Si: 2.5-5 parts by weight, Fe-Ni-Co-Al: 2.5-5 parts by weight, Co-Ni-Al: 2.5-5 parts by weight, Co-Ni-Ga: 2.5-5 parts by weight, Ni-Fe-Ga: 2.5-5 parts by weight, Ti-Pd: 2.5-5 parts by weight. It is composed by mixing.

[0014] In addition, the first process is temperature: 250~350℃, heating rate: 5℃ / min, holding time: 20 min, cooling condition: furnace cooling, atmosphere: high vacuum (10 -4 Heat treatment is performed under the condition of 10 torr.

[0015] In addition, the present invention also provides a denture manufactured by a method for manufacturing a customized denture using the self-deforming Ni-Ti alloy 4D printing treatment material described above.

[0016] According to the present invention, a rough shape of a treatment object is manufactured by a 4D printing process using a human-friendly shape memory alloy (Ni-Ti alloy) powder, and a shape memory heat treatment (200-300℃) is performed for patient-tailored shape memory, and then a precise self-deforming treatment object, i.e., a denture, is manufactured by an external stimulus (pressure, temperature, etc.), so that the manufacturing is convenient, the dimensional processing is easy, and it is held firmly without shaking when used, so that an improved effect can be obtained so that there is no inconvenience in use.

[0017] [Revised 24.10.2023 under Rule 91] Figure 1 is a drawing showing the basic structure of a partial denture, Figure 2 is an exemplary flow chart showing a method for manufacturing a customized denture using a self-deforming Ni-Ti alloy 4D printing treatment material according to the present invention, Figure 3 is a drawing showing a first process of performing shape memory heat treatment after 3D printing, and Figure 4 is a drawing showing a second process of removing residual material after heat treatment.

[0018] The present invention can be modified in various ways and has various embodiments, and specific embodiments are illustrated in the drawings and described in detail.

[0019] However, this is not intended to limit the present invention to specific embodiments, but should be understood to include all modifications, equivalents, and alternatives that fall within the spirit and technical scope of the present invention. Similar reference numerals have been used to designate similar components throughout the description of each drawing.

[0020] When a component is referred to as being "connected" or "connected" to another component, it should be understood that it may be directly connected or connected to that other component, but that there may be other components intervening. Conversely, when a component is referred to as being "directly connected" or "connected" to another component, it should be understood that there are no other components intervening.

[0021] The terminology used in this application is only used to describe specific embodiments and is not intended to limit the present invention. The singular expression includes the plural expression unless the context clearly indicates otherwise. In this application, it should be understood that the terms "comprise" or "have" indicate the presence of a feature, number, step, operation, component, part, or combination thereof described in the specification, but do not preclude the possibility of the presence or addition of one or more other features, numbers, steps, operations, components, parts, or combinations thereof.

[0022] Hereinafter, embodiments of the present invention will be described with reference to the attached drawings. Like reference numerals in each drawing represent like elements. In describing the present invention, detailed descriptions of related, known functions or components are omitted to avoid obscuring the gist of the present invention.

[0023] The present invention relates to the production of medical treatment products capable of self-assembly or self-transformation due to changes in external conditions, and relates to a method for producing a shape-memory medical treatment product (partial dentures, etc.) by applying a 4D metal printing method using a shape-memory Ni-Ti alloy.

[0024] Here, 4D printing refers to the concept of 3D printing + self-deformation, and the feature of the present invention is that when a 4D printed product, i.e. a 4D printed denture, is placed on the gums, the 4D printed denture, which is a shape memory alloy, self-deforms due to the temperature of the gums to stably adhere to the gums.

[0025] In other words, 4D printing is a process of printing thin 2D shapes using smart materials such as shape memory alloys or resins using a 3D printer, and transforming the printed object into a desired shape according to changes in time or the surrounding environment. The conditions under which the shape will change can be programmed and designed in advance. The deformation conditions can be various environments or energy sources such as heat, vibration, gravity, moisture, light, and pH. 4D printing is a field with great industrial applicability expected in terms of shortening manufacturing time, which was a major issue in conventional 3D printing, and is well described in registered patent no. 10-1844892.

[0026] As illustrated in FIG. 1, a method for manufacturing a customized denture using a self-deforming Ni-Ti alloy 4D printing treatment material according to the present invention includes a data collection step of collecting information on teeth and gums of a patient to whom dentures are to be applied; a scan value processing step of correcting the shape and dimensions of a denture to be applied to the patient based on the tooth and gum information collected in the data collection step; a material preparation step of preparing a denture processing material using shape memory alloy powder; a printing step of printing a denture by processing the shape memory alloy material with a 3D printer according to the denture shape and dimensions corrected in the scan value processing step; and a post-processing step of polishing the denture printed in the printing step.

[0027] And, the above post-processing step is composed of a first step of performing shape memory heat treatment after 3D printing, a second step of removing residual material after heat treatment, a third step of performing surface treatment after removing residual material, a fourth step of polishing after surface treatment, and a fifth step of performing UV hardening after polishing.

[0028] Here, the data collection stage is the stage of collecting dental-related data from patients to determine the condition of their teeth and gums when they will be wearing dentures.

[0029] This data collection step involves collecting scanned information about the patient's teeth using computed tomography (CT), magnetic resonance imaging (MRI), X-ray, and ultrasound imaging technologies. This information is then used to determine the shape and dimensions of the patient's teeth, which are then converted into digital data.

[0030] The digital data generated in this data collection stage is converted into digital data that can be linked to a processing program so that dentures can be processed to match the shape of the patient's teeth to be corrected in the scan value processing stage.

[0031] And, the scan value processing step is the step of creating a 3D modeling file using the patient's dental data collected and converted in the data collection step, converting the created 3D modeling file into the STL (Stereolithography) file format, which is data used for 3D printing, so that it is suitable for printing (injection) through a 3D printer, and creating a slice file based on this.

[0032] In addition, the material preparation step is a step of forming a shape memory alloy powder. The shape memory alloy powder is formed as follows. Since these are all alloy powders, the term alloy powder will be omitted and described.

[0033] That is, the shape memory alloy powder composition according to the present invention can be formed by mixing 44-49 parts by weight of Ag-Cd, 46.5-50 parts by weight of Au-Cd, 14-14.5 parts by weight of Cu-Al-Ni, 15-15.5 parts by weight of Cu-Zn, 38.5-41.5 parts by weight of Cu-Zn, 5-10 parts by weight of Cu-Zn-X (X=Si,Al,Sn), 20-25 parts by weight of Fe-Pt, 5-35 parts by weight of Mn-Cu, 2.5-5 parts by weight of Fe-Mn-Si, 2.5-5 parts by weight of Fe-Ni-Co-Al, 2.5-5 parts by weight of Co-Ni-Al, 2.5-5 parts by weight of Co-Ni-Ga, 2.5-5 parts by weight of Ni-Fe-Ga, and 2.5-5 parts by weight of Ti-Pd for 100 parts by weight of Ni-Ti. there is.

[0034] The reason for formulating shape memory alloy powder in this way is that shape memory alloys have the property of immediately recovering their original shape even when deformed at a temperature above their transformation point, and this property is called superelasticity. If the transformation point of an alloy is below room temperature, it is called a superelastic alloy. The present invention is a powder combination for making an alloy with a transformation point below room temperature, which corresponds to such a superelastic alloy.

[0035] At this time, Ni-Ti alloy powder is the most basic base alloy powder of shape memory alloy.

[0036] Additionally, Ag-Cd alloy powder is added to increase corrosion resistance and durability.

[0037] Additionally, Au-Cd alloy powder is added to make the structure dense and prevent breakage of the molded product.

[0038] In addition, Cu-Al-Ni alloy powder is added to increase impact resistance and compression resistance through partial reinforcement by alumina and to realize high thermal stability.

[0039] In addition, Cu-Sn alloy powder is added to suppress the spreading phenomenon of microbumps and induce homogenization of the molded product.

[0040] Furthermore, Cu-Zn alloy powder is added to induce mechanical changes during heat treatment, thereby contributing to improved strength and durability.

[0041] And, Cu-Zn-X (X=Si,Al,Sn) alloy powder is added to induce thermodynamic equilibrium.

[0042] Additionally, Fe-Pt alloy powder is added to stabilize the thermal transition metal and to contribute to achieving structural stabilization of the molded product.

[0043] In addition, Mn-Cu alloy powder is added to provide ductility to improve formability and processability, as well as to enhance corrosion resistance.

[0044] In addition, Fe-Mn-Si alloy powder is added to secure the tensile strength and elongation of the molded product and to increase elasticity.

[0045] Furthermore, Fe-Ni-Co-Al alloy powder is added to smoothly induce deformation of thermoelastic martensite and increase shape memory.

[0046] Additionally, Co-Ni-Al alloy powder is added to increase magnetic controllability.

[0047] In addition, Co-Ni-Ga alloy powder is added because it has the property of enhancing high-temperature shape memory with high Curie and martensite characteristics.

[0048] In addition, Ni-Fe-Ga alloy powder is added to induce single crystal high-elastic behavior of the shape memory alloy.

[0049] In addition, Ti-Pd alloy powder is added to induce changes in the surface microstructure of the molded product to enhance mechanical properties and corrosion resistance.

[0050] Here, the shape memory effect means that when a sample in the mother phase (austenite phase) is cooled, the crystal structure changes shear-wise and transforms into a martensite phase, and at this time, the shape change as a whole is offset to create a number of different martensite crystals (variants), and when stress is applied in the martensite phase, the variant in the direction that is most stable with respect to the stress grows (rearrangement of variants).

[0051] The apparent plastic deformation occurs due to the rearrangement of these variants, and the rearrangement progresses until a single variant is formed, and since the lattice correspondence between the martensite phase and the parent phase is maintained, when a reverse transformation occurs due to heating, the shape is completely restored by returning to the original crystal lattice. This phenomenon is called the shape memory effect.

[0052] In this case, when stress is applied in the mother state (loaded in a temperature environment higher than the reverse transformation termination temperature), martensite transformation occurs due to stress induction, and at this time, martensite variants in the direction of stress relief are preferentially created and grow, so the shape changes with little increase in stress.

[0053] In this state, if the load is removed, reverse deformation occurs just by removing it, and the shape is restored. However, if the temperature environment that loads stress is too high, slip takes precedence over martensite transformation due to stress induction, so if a stress exceeding the elastic limit is loaded, plastic deformation due to slip occurs, and superelasticity does not appear.

[0054] Therefore, shape memory alloys exhibit elasticity and the property of returning to their original shape when a certain temperature is applied to a bending (distortion) of less than 10% of the metal crystal structure. However, when a high temperature is applied that changes the metal crystal structure, this elasticity is damaged and the shape at that time is remembered through plasticity.

[0055] Meanwhile, the printing step is a step in which the 3D printer prints the three-dimensional shape of the denture using the shape memory alloy powder prepared according to the corrected denture information received from the PC.

[0056] At this point, the most crucial steps before starting 3D printing are part orientation and data fixing. Appropriate positioning is essential, taking into account the part's geometric characteristics, surface roughness, and heat dissipation capabilities. Furthermore, various variables must be considered when manufacturing.

[0057] And, data fixing checks for defects (holes, flipped faces, breaks, etc.) in the 3D modeling data, takes appropriate measures, completes the slice data and equipment settings, and then performs 3D printing.

[0058] Then, the next post-processing step is as described above, which consists of the first step of shape memory heat treatment after 3D printing, the second step of removing residual material after heat treatment, the third step of surface treatment after removing residual material, the fourth step of polishing after surface treatment, and the fifth step of UV hardening after polishing, which performs a type of self-deformation to complete the 4D printing concept.

[0059] Here, the first process is a heat treatment process to obtain a shape memory effect at room temperature, temperature: 250 to 350°C, heating rate: 5°C / min, holding time: 20 min, cooling conditions: furnace cooling, atmosphere: high vacuum (10 -4 It is made under the condition of torr).

[0060] [Correction under Rule 91 24.10.2023] As shown in Figure 3,

[0061] [Correction pursuant to Rule 91, October 24, 2023]

[0062] The purpose is to make it so that even if the shape is deformed at low temperature because the crystal structure is significantly different between the high-temperature parent phase and the low-temperature martensite phase, it returns to its original shape (parent phase) when heated above a certain temperature (reverse transformation temperature).

[0063] That is, when the alloy is cooled below the martensite initiation temperature (Ms) in the parent state to completely martensite and then bent at a temperature below the martensite finish temperature (Mf), the shape does not return to its original state even if the deformation force is removed at a temperature below the finish temperature (Mf), but when the temperature is raised above the martensite reverse transformation initiation temperature (As), the shape begins to return to its original state due to reverse transformation, and when it is raised above the martensite reverse transformation finish temperature (Af), it is completely restored to its original state. Therefore, the purpose is to form a new phase in the single-crystal shape memory alloy by a process in which plastic deformation is applied in the martensite transformation temperature range (Ms-Mf) and maintained for a certain period of time at a temperature exceeding the martensite reverse transformation finish temperature (Af).

[0064] This treatment achieves a shape memory alloy effect at room temperature, so when the dentures are heat-treated, they tighten tightly at the user's body temperature after wearing them, and when the dentures are removed, if kept at room temperature, the dentures spread apart and can be easily removed, so they do not fall off easily when worn, significantly improving convenience of use.

[0065] [Correction under Rule 91 24.10.2023] And, the second process is as shown in Figure 4,

[0066] [Correction pursuant to Rule 91, October 24, 2023]

[0067] This is a process of electrical discharge machining using wire discharge machining equipment (EDM), removing primary foreign substances and residual powder, and finally removing foreign substances and powder using light vibration and an air gun, and then removing the supporter.

[0068] In addition, the third process is a process of treating the surface using a hand grinder and a sander, and is comprised of a first step of initially smoothing the rough surface, and a second step of evaluating whether the surface roughness has reached the set value by polishing the surface using a blasting bead after the first step.

[0069] And, the fourth process is a polishing process, which is a process of polishing the surface by spraying polishing liquid using a spindle to make it uniform.

[0070] At this time, a corrosion-preventing layer is formed on the sus pin performing the polishing work to prevent corrosion of the metal surface. The corrosion-preventing layer is formed by applying a coating solution composed of 100 parts by weight of bisphenol A type epoxy resin, 15 parts by weight of butyl carbitol, 10 parts by weight of isopropylamine, 15 parts by weight of hafnium oxide, 10 parts by weight of sodium sesquicarbonate, 10 parts by weight of organic acid magnesium, 9 parts by weight of titanium oxide (TiO2), and 10 parts by weight of aluminum oxide (Al2O3) to a thickness of 10 μm.

[0071] Here, bisphenol A type epoxy resin is the base resin, boasting excellent thermal properties, chemical resistance, and excellent curing and water resistance. Butyl carbitol provides flame retardancy, antistatic properties, and corrosion inhibition. Isopropylamine, a substance with CAS No: 75-31-0, also provides corrosion and discoloration prevention.

[0072] In addition, Hafnium Oxide, a substance corresponding to CAS No: 12055-23-1, is added to ensure corrosion resistance and waterproofing. In addition, Sodium Sesquicarbonate is added to enhance antifouling properties, which are characteristics that prevent the adhesion of contaminants. In addition, organic magnesium acid plays a role in providing alkali resistance and wettability to the surface of the coating film, and titanium oxide and aluminum oxide are added for the purpose of fire resistance and chemical stability.

[0073] Lastly, the fifth process is a process of finishing by irradiating the surface-treated and polished surface with ultraviolet rays to harden the surface, and then washing it using ultrapure water using a vacuum ultrasonic method.

[0074] By doing so, a rough shape of a treatment object is manufactured using a 4D printing process using a human-friendly shape memory alloy (Ni-Ti alloy) powder, and a shape memory heat treatment (200-300℃) is performed for patient-tailored shape memory, and then a precise self-deforming treatment object, i.e., a denture, is manufactured by an external stimulus (pressure, temperature, etc.), thereby making it convenient to manufacture, easy to process dimensions, and holding it firmly without shaking when used, so that there is no inconvenience in use. A method for manufacturing a customized denture using an improved self-deforming Ni-Ti alloy 4D printing treatment object and a denture manufactured by the method can be provided.

[0075] In addition, in the present invention, 10 parts by weight of HAP (Hydroxyapatite), 5 parts by weight of CNC (Cellulose Nanocrystal), and 5 parts by weight of ethylene bis stearamide may be further added to 100 parts by weight of the shape memory alloy powder composition described above.

[0076] At this time, HAP (Hydroxyapatite) is a bioceramic that has properties similar to actual human bones, especially teeth, making it a human-friendly material with almost no side effects for manufacturing dentures.

[0077] Additionally, cellulose nanocrystals, or CNCs, are added to induce linear changes in stiffness and ductility that cannot be achieved with bioceramics, and to compensate for the disadvantage of being brittle and easily broken when using only bioceramics, which appear nonlinearly.

[0078] In addition, ethylene bis stearamide is added to suppress yellowing, increase surface smoothness, improve gloss, and thereby suppress whitening.

[0079] As described above, the present invention has been disclosed in its optimal embodiments in the drawings and specifications. While specific terminology has been used herein, it is solely for the purpose of describing the present invention and is not intended to limit the scope of the invention as defined in the claims. Therefore, those skilled in the art will understand that various modifications and equivalent embodiments are possible. Therefore, the true technical protection scope of the present invention should be defined by the technical spirit of the appended claims.

Claims

1. A data collection step for collecting information on teeth and gums of a patient to whom dentures are to be applied; a scan value processing step for correcting the shape and dimensions of a denture to be applied to a patient based on the tooth and gum information collected in the data collection step; a material preparation step for preparing a denture processing material using shape memory alloy powder; a printing step for printing a denture by processing the shape memory alloy material with a 3D printer according to the denture shape and dimensions corrected in the scan value processing step; and a post-processing step for polishing the denture printed in the printing step. The above post-processing step is, A method for manufacturing a customized denture using a self-deforming Ni-Ti alloy 4D printing treatment material, characterized by comprising a first step of performing shape memory heat treatment after 3D printing, a second step of removing residual material after heat treatment, a third step of performing surface treatment after removing residual material, a fourth step of polishing after surface treatment, and a fifth step of performing UV hardening after polishing.

2. In paragraph 1, The shape memory alloy powder formed in the above material preparation step is Self-deforming Ni-Ti alloy 4D characterized by being composed by mixing 44-49 parts by weight of Ag-Cd, 46.5-50 parts by weight of Au-Cd, 14-14.5 parts by weight of Cu-Al-Ni, 15-15.5 parts by weight of Cu-Zn, 38.5-41.5 parts by weight of Cu-Zn, 5-10 parts by weight of Cu-Zn-X (X=Si,Al,Sn), 20-25 parts by weight of Fe-Pt, 5-35 parts by weight of Mn-Cu, 2.5-5 parts by weight of Fe-Mn-Si, 2.5-5 parts by weight of Fe-Ni-Co-Al, 2.5-5 parts by weight of Co-Ni-Al, 2.5-5 parts by weight of Co-Ni-Ga, 2.5-5 parts by weight of Ni-Fe-Ga, and 2.5-5 parts by weight of Ti-Pd for 100 parts by weight of Ni-Ti. Method for manufacturing customized dentures using a printing material.

3. In paragraph 1, The above first process is temperature: 250~350℃, heating rate: 5℃ / min, holding time: 20min, cooling condition: furnace cooling, atmosphere: high vacuum (10 -4 A method for manufacturing customized dentures using a self-deforming Ni-Ti alloy 4D printing treatment material characterized by heat treatment under conditions of 10 torr.

4. A denture manufactured by a method for manufacturing a customized denture using a self-deforming Ni-Ti alloy 4D printing treatment material described in Article 1.

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