WO2019098791A1 - Résine de base pour dentiers pour l'impression 3d - Google Patents

Résine de base pour dentiers pour l'impression 3d Download PDF

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WO2019098791A1
WO2019098791A1 PCT/KR2018/014211 KR2018014211W WO2019098791A1 WO 2019098791 A1 WO2019098791 A1 WO 2019098791A1 KR 2018014211 W KR2018014211 W KR 2018014211W WO 2019098791 A1 WO2019098791 A1 WO 2019098791A1
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Prior art keywords
printing
denture base
base resin
resin
udma
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PCT/KR2018/014211
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English (en)
Korean (ko)
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배지명
박다령
신성진
Original Assignee
주식회사 사이버메드
원광대학교산학협력단
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Priority claimed from KR1020170164015A external-priority patent/KR102080721B1/ko
Application filed by 주식회사 사이버메드, 원광대학교산학협력단 filed Critical 주식회사 사이버메드
Priority to US16/764,544 priority Critical patent/US20200383878A1/en
Publication of WO2019098791A1 publication Critical patent/WO2019098791A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/01—Palates or other bases or supports for the artificial teeth; Making same
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K6/00—Preparations for dentistry
    • A61K6/80—Preparations for artificial teeth, for filling teeth or for capping teeth
    • A61K6/884—Preparations for artificial teeth, for filling teeth or for capping teeth comprising natural or synthetic resins
    • A61K6/887—Compounds obtained by reactions only involving carbon-to-carbon unsaturated bonds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K6/00—Preparations for dentistry
    • A61K6/80—Preparations for artificial teeth, for filling teeth or for capping teeth
    • A61K6/884—Preparations for artificial teeth, for filling teeth or for capping teeth comprising natural or synthetic resins
    • A61K6/891—Compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
    • A61K6/893—Polyurethanes

Definitions

  • Disclosure relates generally to denture base resins for 3D printing, and more particularly to denture base resins for 3D printing with improved mechanical properties.
  • PMMA resin is used as a molding material for glass substitution because it permeates about 95% of visible light and thus has excellent transparency as well as excellent surface appearance and relatively high glass transition temperature and thus has excellent mechanical properties.
  • PMMA resin has a disadvantage that it is easily broken by an external force such as drop impact due to its weak impact strength. In addition, due to low surface hardness and abrasion resistance, wear and scratches of the surface tend to occur, and transparency may be lowered.
  • 3D printing is also being introduced into the dental school.
  • 3D printing is introduced into the dental system and is not used for temporary dentures, splints, or surge guides.
  • the saliva is present in the oral cavity, there is a temperature difference depending on the food to be consumed, a constant mechanical pressure is applied, and an abnormal force such as guttate and crenching is applied, , Modulus of elasticity, toughness, fatigue strength, etc.) and should be free of cytotoxicity.
  • the main component of the dental resin substrate is a combination of dimethacrylate, which has been developed in the direction of increasing the degree of polymerization and decreasing the polymerization shrinkage while increasing the mechanical properties.
  • Bis-GMA and UDMA are most commonly used as dental restorative resins. UDMA has fewer polymerization shrinkage and lower viscosity than bis-GMA. Since there is no phenol ring in the monomer of UDMA, the elasticity and toughness are large and the polymerization can be promoted.
  • Bis-GMA is highly viscous and has many functional groups, so TEGDMA is used as a diluent.
  • Methanol Pentamethylene tetryl tetracrylate and di (trimethyl phenol) copolymer are comonomers that perform various functions such as crosslinking agent and diluent, and cause a lot of crosslinking in polymerization.
  • NexDent (Vertex Dental) is the only commercially available denture base resin for 3D printing.
  • Conventional heat-polymerized and self-polymerizing denture resins reproduce blood vessels with nylon fibers, which are very aesthetic.
  • 3D resin is difficult to add fiber, it is impossible to reproduce these blood vessels.
  • the color of the Nexdent resin itself changes, and the color stability of the prosthesis is poor.
  • the heat-polymerizable dental restorative resin should have a flexural strength of 65 MPa or more, a flexural modulus of 2 GPa or more, a self-polymerization type of flexural strength of 60 MPa or more, and a flexural modulus of 1.5 GPa or more.
  • a 3D printing denture base resin for 3D printing containing 30% to 43% of urethane dimethacrylate (UDMA) Resin is provided.
  • UDMA urethane dimethacrylate
  • Figure 1 and Figure 2 illustrate components of a denture base resin for 3D printing according to the present disclosure
  • FIG. 3 is a diagram illustrating a method for testing flexural strength and flexural modulus of a denture base resin for 3D printing according to the present disclosure
  • FIG. 4 is a view showing a shape of a specimen and a method of testing a specimen for testing the bonding strength of the denture base resin for 3D printing according to the present disclosure
  • 5 to 6 are views showing the viscosity of the denture base resin for 3D printing according to the present disclosure
  • FIG. 7 to 9 are views showing the bending strength and elastic modulus of the denture base resin for 3D printing according to the present disclosure
  • 10 to 12 are views showing bonding strengths of the denture base resin for 3D printing according to the present disclosure.
  • FIG. 13 is a view showing a fracture mode of a denture base resin for 3D printing according to the present disclosure
  • 14 to 15 are diagrams showing the cytotoxicity of the denture base resin for 3D printing according to the present disclosure.
  • the present disclosure relates to a denture base resin which can be applied to a 3D printer in comparison with a commercially available denture base resin for a 3D printer.
  • the denture base resin exhibits a viscosity, a flexural strength, a flexural modulus, Bond strength and cytotoxicity were evaluated.
  • urethane dimethacrylate (UDMA), bis-phenol A-glycidyl methacrylate (Bis-GMA), triethylene glycol dimethacrylate (TEGDMA) Pentaerythritol tetraacrylate (PETRA), and di (trimethylolpropane) -tetraacrylate Di (TMPTA) tetraacrylate were mixed.
  • Diphenyl (2,4,6-trimethylbenzoyl) phosphine oxide (DTPO) and ethyl 4- (dimethylamino) benzoate (DMAB) were used as photoinitiators and photosensitizers .
  • Erythrosin B Erythrosin B
  • TiO2 titanium oxide
  • UDMA and DTPO were continuously adjusted to find the maximum flexural strength and flexural modulus (wt%).
  • Nextdent Base, Vertex Dental, Netherlands
  • 1 to 3 are views showing components of a denture base resin for 3D printing according to the present disclosure.
  • FIG. 1 shows a material, a component name, an acronym, a manufacturer, and the like constituting the denture base resin for 3D printing.
  • the components of the denture base resin for experimental 3D printing are obtained from the manufacturer shown in Fig. 1, and the control group (T0) is NextDent, which is a commercially available product.
  • the monomer may be selected from the group consisting of urethane dimethacrylate (UDMA), bisphenol A glycidyl methacrylate (hereinafter referred to as Bis-GMA), triethylene glycol dimethacrylate (TEGDMA), pentaerythritol tetraacrylate (Hereinafter referred to as PETRA), and di (trimethylsulfperate) tetracrylate (hereinafter referred to as Di-TMPTA).
  • UDMA urethane dimethacrylate
  • Bis-GMA bisphenol A glycidyl methacrylate
  • TEGDMA triethylene glycol dimethacrylate
  • PETRA pentaerythritol tetraacrylate
  • Di-TMPTA di (trimethylsulfperate) tetracrylate
  • the photoinitiator includes diphenylphosphine oxide (hereinafter referred to as DTPO).
  • the photosensitizer includes ethyl 4- (dimethylaminomino) benzoic acid (hereinafter DMAB).
  • the colorant may include erythrosin B, titanium oxide (hereinafter referred to as TiO 2).
  • FIG. 2 is a graph showing an experimental group and a control group according to the weight ratio of the denture base resin for 3D printing according to the present disclosure.
  • Monomers are formed by mixing UDMA, Bis-GMA, TEGDMA, PETRA and Di-TMPTA.
  • the mixture was mainly added with DTPO (1.2 wt.% And 2.6 wt.%) And Erythrosin (0.0015 wt.% And 0.0012 wt.%), Photoinitiators and colorants based on 30.6 wt.% And 41.9 wt.% Of the UDMA TiO2 (325 mesh; 0.15wt% and 0.12wt%) was added for the opacity of the resin.
  • the experimental group was divided into two types, T1 and T3, and T2 and T4 groups, respectively (Fig. 3). All percentages are expressed by weight ratios.
  • the T1 study group contained 14.7% of Bis-GMA, 30.6% of UDMA, 24.5% of TEGDMA, 12.2% of PETRA, 14.7% of Di-TMPTA, 1.2% of DTPO and 2% of DMAB in weight ratio.
  • the T3 group contained 12.0% of Bis-GMA, 41.9% of UDMA, 20.0% of TEGDMA, 10.0% of PETRA, 12.0% of Di-TMPTA, 2.6% of DTPO and 1.6% of DMAB.
  • the T2 and T4 groups were supplemented with coloring agents Erythrosin and TiO2 to match the silver color of the T1 and T3 groups.
  • the viscosities ( ⁇ , Pa s) of all test groups were measured at 25 using a viscometer (DV2TRVTJ0, No. 8692529, Brookfield Ametek, USA). A # 21 spindle was used and the viscosity measured at a torque of 60 to 90% torque was measured.
  • FIG. 3 is a diagram showing a method for testing the flexural strength and flexural modulus of a denture base resin for 3D printing according to the present disclosure.
  • Fig. 3 (a) is a schematic view showing a bending strength and a bending coefficient test
  • Fig. 3 (b) is a bending strength and bending coefficient test photograph.
  • the flexural strength of the specimen was measured at a crosshead speed of 5 mm / min using a universal tester (Z020, Zwick, Germany) until fracture of the specimen according to ISO 20795-1 [17].
  • the elastic modulus (E, GPa) was calculated from the data obtained from the initial linear part of the load-displacement curve.
  • ⁇ and E were calculated respectively according to the equation (Eq. (1) (2)).
  • FIG. 4 is a view showing a specimen and a method for testing the bonding strength of the denture base resin for 3D printing according to the present disclosure.
  • Fig. 4 (a) is a photograph of a bonding strength specimen
  • Fig. 4 (b) is a photograph of a specimen mounted on a bonding strength jig manufactured according to ISO22112: 2005.
  • Bond strength specimens were produced in accordance with ISO 22112: 2005.
  • the prosthetic dentures were used in the experimental group (T1, T2, T3, T4) as the control (T0), as in the flexural strength test, and the prostheses were used in the maxillary right and left central incisors, lateral incisors and canines (Biotone, Dentsply, USA) ) And total of 300 specimens were prepared.
  • the bond strength specimen the area of the ridge lap of the artificial tooth was scanned, and the denture resin was 3D printed. The size of the resin was 20 mm x 6.2 mm wide x 6.2 mm wide.
  • the 3D-printed denture resin was abraded with Al 2 O 3 (Aluminum oxide, Danville, Germany) with 50um particle size for 30 seconds at 2 bar air pressure and the area where the artificial teeth came into contact with the artificial teeth. Respectively. All samples were ultrasonically cleaned in distilled water at a frequency of 40 kHz for 20 minutes to remove residual particles. The sample was dried at room temperature. The artificial teeth and 3D printed denture resin patterns were bonded using self-adhesive resin cement (Rely XTM U200, 3M ESPE, Germany). All dentures were photopolymerized for 40 seconds using an LED light curing machine (VALO, Ultradent, USA) with a denture resin pressed against a prosthesis bonded with a static load.
  • VALO LED light curing machine
  • the sizes of the specimens in each group were 10 mm long x 10 mm wide x 3.3 mm thick.
  • the specimens were placed in a 24-well plate according to the International Standard ISO 10993-5 (Tests for in vitro cytotoxicity) and extracted in a 37 oven oven for 24 hours using RPMI medium .
  • the extraction ratio was such that the ratio of the surface area of the specimen to the extract was 3 cm 2 / mL as specified in ISO 10993-12 (Biological evaluation of medical devices-Part 12).
  • An aluminum oxide ceramic rod was used as a negative control and 1% phenol was used as a positive control.
  • L929 cells (NCTC clone 929, CCL 1, ARCC) were used.
  • RPMI medium (AB10131148, Hyclone, USA) containing 10% fetal bovine serum (FBS, Gibco) was cultured in a 37, 5% CO2 incubator.
  • FBS fetal bovine serum
  • 0.1 ml of each well was added to a 96-well plate at a concentration of 1 ⁇ 10 4 cells / well and cultured for 24 hours.
  • the culture medium was removed and 100 ⁇ l of each resin group extract and RPMI medium were added for 37 to 24 hours.
  • 5 to 6 are views showing the viscosities of the denture base resin for 3D printing according to the present disclosure.
  • the mean and standard deviation of the viscosity measurements are shown in FIG. All differences between groups were statistically significant (p ⁇ 0.05).
  • the control group (T0) was twice as high as the other experimental groups and showed the highest average value.
  • the viscosity of the group based on UDMA increased steadily with increasing UDMA concentration.
  • the T2 and T4 groups showed higher viscosity than the T1 and T3 groups due to the addition of colorants and TiO2.
  • the viscosity of the control group (T0; Nextdent) was the highest and the viscosity of the T1 group was significantly lower than that of the control group (p ⁇ 0.05).
  • the T2 and T4 experimental groups with colorants and TiO2 added showed higher viscosity values than the higher T1 and T3 experimental groups. It was found that the viscosity changes depending on the presence or absence of the colorant, and the viscosity increases as the UDMA increases.
  • the viscosity of the resin for 3D printing has a great influence on the printing result.
  • the viscosity of the control group (T0; 877.7 ⁇ 1.5) shows about 3 times higher viscosity than the T1 to T4 experimental group, which is the 3D printing denture base resin. Therefore, the T1 and T3 test groups showed less smooth slurries than the T2 and T4 test groups of the 3D printing denture resin prepared for the better flow than the control (TO) samples, This is better.
  • FIG. 7 to 9 are views showing the bending strength and elastic modulus of the denture base resin for 3D printing according to the present disclosure.
  • the bending strength showed a result opposite to the viscosity (Fig. 8).
  • the highest flexural strength of the T3 test group (41.9% UDMA) was 138.23 MPa (p ⁇ 0.05), and the T1 test group (30.6% UDMA) had the next highest flexural strength of 121.71 MPa (p ⁇ 0.05).
  • UDMA mixed with resin showed higher flexural strength.
  • the T2 and T4 test groups with colorants and TiO2 showed a significant decrease in flexural strength at 107.62 MPa and 100.65 MPa, respectively, but there was no significant difference between the two groups (p> 0.05).
  • the flexural strength of the group having a high flexural strength value was also high. (P ⁇ 0.05). However, the difference between the two groups was not statistically significant (p> 0.05). The elastic modulus was decreased in the T2 and T4 experimental groups added with the coloring agent and TiO2 (p ⁇ 0.05), but the difference between the two groups was not significant (p> 0.05). In addition, the flexion modulus of the control group (T0) was the lowest among all groups (p ⁇ 0.05).
  • the flexural strength and flexural modulus of the T2 and T4 test groups with colorants and TiO2 were lower than those of the T1 and T3 test groups. This is because the color of the resin becomes darker and the transparency decreases because of the colorant and TiO2 particles when mixing the resin, so that the flexural strength and the flexural modulus of the DLP type 3D printer are decreased.
  • the bending strength standard value of denture thermally polymerized resin is 65 MPa or more
  • the bending strength standard value of autopolymerizing resin is 60 MPa or more
  • Is 2 GPa or more the reference value of self-polymerization resin is 1.5 GPa or more.
  • the T1 to T4 test groups showed results exceeding the flexural strength of the thermally polymerized resin of the international standard and the modulus of elasticity of the thermally polymerized resin.
  • the flexural strength of T3 group (41.29 ⁇ 10.12 MPa) containing 41.19% UDMA was the highest (p ⁇ 0.05).
  • the elastic modulus was also highest in T1 (3.12 ⁇ 0.1GPa) and T3 (3.19 ⁇ 0.11 GPa) denture resins for 3D printing (p ⁇ 0.05). Therefore, the higher the content of UDMA, the higher the flexural strength and elastic modulus, and the lower the flexural strength and elastic modulus when the colorant is added.
  • the flexural strengths of the T1 and T3 experimental groups were significantly higher than the flexural strength of the control group (T0), and the flexural modulus of all experimental groups was higher than that of the control group (T0). All experimental groups showed results exceeding the flexural strength standard of 65 MPa or more and the flexural modulus of 2 GPa or more according to the international standard (ISO).
  • 10 to 12 are views showing bonding strengths of the denture base resin for 3D printing according to the present disclosure.
  • Bond strength was higher in the T1 and T3 groups than in the other groups (P ⁇ 0.05). It is believed that the colorant and TiO2 also affect the strength itself, but also affect the bonding with cement and decrease the bond strength. According to the artificial teeth (depending on which of the six teeth were teeth), there was a significant difference (p ⁇ 0.05). According to the artificial teeth, 23 teeth (303.31 ⁇ 89.38 N) showed the highest bond strength. It seems that the size of the teeth affects the bonding strength. When the artificial teeth and the resin made by 3D printing were bonded with cement, the bonding strength of the teeth with larger surface area tended to be higher.
  • FIG. 13 is a view showing the fracture mode of the denture base resin for 3D printing according to the present disclosure.
  • Cohesive failure and mixed failure were observed in all experimental groups. Cohesive fractures were divided into fractures in artificial teeth and fractures in denture base resin. According to International Standard No. 22112 (ISO22112: 2009), fracture patterns should show cohesive or mixed fractures in artificial or denture resisting resins. Mixed fracture refers to the case where the residue of an artificial tooth remains adhered to the resin or, conversely, the residue of the resin remains adhered to the artificial tooth. Therefore, according to the standard of ISO 22112, specimens with only 100% adhesive failure were rejected, but no corresponding specimens were found. Fracture patterns are important because dentures and denture base resins for 3D printing are cemented together. In the case of high adhesiveness, fracture occurs in the cohesive fracture or two mixed state in tooth or denture resin, and when the adhesiveness is low, adhesive fracture occurs at the interface between the tooth and dental restorative resin.
  • the T1 to T4 test groups showed cohesive fracture and mixed fracture patterns, which were found to conform to the ISO standard.
  • 14 to 15 are diagrams showing the cytotoxicity of the denture base resin for 3D printing according to the present disclosure.
  • the measured activity of the prepared resin after elution for 24 hours is shown in Fig. In all experimental groups, cell activity was higher than negative control (p ⁇ 0.05).
  • the MTT test in ISO 10993-5: 2009 (E) states that if the cell activity is above 70%, the material is not toxic. Not only did all of the test groups used in this experiment show cell activity above 70% And thus it is not only toxic but also biocompatible.
  • This disclosure attempts to evaluate the mechanical and biological properties of denture base resins for 3D printing applications that can be applied to 3D printers.
  • the mechanical properties and biological properties of the denture base resin for 3D printing for 3D printing showed the results which are in conformity with the ISO standard.
  • the T3 test group showed superior flexural strength, elastic modulus, bond strength and MTT test than the control (T0), a denture base resin for 3D printing for 3D printing sold in the market.
  • a denture base resin for 3D printing applicable to 3D printers is manufactured, and mechanical properties and biological properties are evaluated, and the following results are obtained.
  • the flexural strength and modulus of elasticity of the denture base resin for 3D printing were significantly higher than those of T3 (p ⁇ 0.05).
  • the denture base resin T3 for 3D printing was found to have better mechanical properties and better biological properties than the denture base resin for 3D printing sold in the market.
  • the T1 and T3 experimental groups showed low flexural strength and elastic modulus with low viscosity.
  • Viscosity increased continuously according to UDMA concentration and there was a significant difference according to the presence or absence of coloring agent (p ⁇ 0.05). Flexural strength, modulus of elasticity and adhesive strength were high (p ⁇ 0.05) and not cytotoxic (p> 0.05) before coloring. After adding the colorant, there was a significant difference between the flexural strength and the elastic modulus (p ⁇ 0.05).
  • DTPO is the most widely used photoinitiator for 3D printers and was used as a photoinitiator with the nearest optical waveguide to the used 3D printer.
  • a denture base resin for 3D printing bisphenol A-glycidyl methacrylate (Bis-GMA), urethane dimethacrylate (UDMA), triethylene glycol dimethacrylate (TEGDMA), pentaerythritol tetraacrylate (PETRA), and di (trimethylolpropane) -tetraacrylate (Di-TMPTA) Denture resin for printing.
  • Bis-GMA bisphenol A-glycidyl methacrylate
  • UDMA urethane dimethacrylate
  • TEGDMA triethylene glycol dimethacrylate
  • PETRA pentaerythritol tetraacrylate
  • DI-TMPTA di (trimethylolpropane) -tetraacrylate
  • composition comprising 12 to 15% of bisphenol A glycidyl methacrylate, 0 to 31% of urethane dimethacrylate, 20 to 25% of triethylene glycol dimethacrylate, A denture base resin for 3D printing comprising 10 to 13% by weight of dicarboxylic acid and 12 to 15% by weight of di (trimethylsulfurate) tetracrylate.
  • Denture base resin for 3D printing is DTPO.
  • a denture base resin for 3D printing comprising 0 to 1.2% of DTPO by weight.
  • a denture base resin for 3D printing comprising 1.2 to 3% by weight of DTPO.
  • a denture base resin for 3D printing including a co-initiator.
  • the damping resin for 3D printing is DMAB.
  • a denture base resin for 3D printing comprising 0 to 1.6% of DMAB by weight.
  • a denture base resin for 3D printing comprising 1.6 to 2% of DMAB in a weight ratio.
  • a denture base resin for 3D printing comprising a pigment.
  • a denture base resin for 3D printing comprising 0 to 0.0012% of erythrosin and 0.12 to 0.2% of TiO2 in a weight ratio.
  • a denture base resin for 3D printing comprising 0 to 0.0012% of erythrosin and 0 to 0.12% of TiO2 in a weight ratio.
  • a denture base resin for 3D printing comprising 30% to 43% of urethane dimethacrylate (UDMA) in a denture base resin for 3D printing.
  • UDMA urethane dimethacrylate
  • the strength is low when UDMA contains less than 30%, and it is not preferable that the strength decreases when it is more than 43%. It is best to show the highest strength between UDMA and 41.3% ⁇ 43%.
  • the denture base resin for 3D printing is composed of 30.2 ⁇ 30.9% UDMA and 0.5 ⁇ 2.6% DTPO by weight ratio.
  • the denture base resin for 3D printing is less than 30.2% for UDMA and 30.9% for UDMA.
  • the UDMA is between 30.2% and 30.9%, the shape becomes smooth during printing due to the proper viscosity and exhibits high strength.
  • the DTPO content is 0.2% or less, the polymerization is not performed well. If the DTPO content is 2.6% or more, the polymerization degree is too high. When DTPO is between 0.2% and 2.6%, the most suitable degree of polymerization is shown.
  • a denture base resin for 3D printing comprising 30.2 to 30.9% of UDMA, 0.5 to 2.6% of DTPO, 0.0012 to 0.006% of erythrosin and 0.12 to 0.15% of TiO2 in weight ratio for 3D printing.
  • the denture base resin for 3D printing is less than 30.2% for UDMA and 30.9% for UDMA.
  • the UDMA is between 30.2% and 30.9%, the shape becomes smooth during printing due to a suitable viscosity and high strength can be obtained.
  • DTPO When DTPO is contained in an amount of 0.2% or less, the polymerization does not proceed well, and when the amount of DTPO is 2.6% or more, the degree of polymerization is too high. When DTPO is between 0.2% and 2.6%, the most suitable degree of polymerization is shown.
  • the amount of erythrosin is less than 0.0012%, the color is not aesthetically favorable. If it is 0.006% or more, it is too red. When the colorant is increased, the degree of polymerization is decreased and the strength is also decreased. Erythrosin is best reproduced in natural color between 0.0012% and 0.006%.
  • the denture base resin for 3D printing is a denture base resin for 3D printing containing UDMA in a ratio of 41.3 to 43% by weight and DTPO in an amount of 0.4 to 4%.
  • the denture base resin for 3D printing has a UDMA content of not more than 41.3%, or a strength of less than 43%, which is not good. Between 41.3% and 43% of UDMA, it is good to be able to show high accuracy in printing due to proper viscosity and fluidity.
  • the degree of polymerization is low. If the amount of DTPO is 4% or more, the degree of polymerization is too high, which may cause polymerization problems before printing. It is preferable that the degree of polymerization is sufficient when DTPO is between 0.4% and 4%.
  • the denture base resin for 3D printing is a 3D denture resin containing UDMA in a ratio of 41.3 to 43%, DTPO in an amount of 0.4 to 4%, Erythrosin in an amount of 0.0012 to 0.006%, and TiO2 in an amount of 0.12 to 0.15%.
  • the UDMA for 3D printing denture resin is not good because it is less than 41.3% or more than 43%. Between 41.3% and 43% of UDMA, it is good to be able to show high accuracy in printing due to proper viscosity and fluidity.
  • DTPO When DTPO is contained in an amount of 0.4% or less, the degree of polymerization is low. If the amount of DTPO is 4% or more, the degree of polymerization is too high, which may cause polymerization problems before printing. It is preferable that the degree of polymerization is sufficient when DTPO is between 0.4% and 4%. In addition, if the amount of erythrosin is less than 0.0012%, it is not preferable that the color is not aesthetic. If the amount is more than 0.006%, it is too red, and the intensity is decreased by the amount of the particles. Erythrosin is best reproduced in natural color between 0.0012% and 0.006%.
  • TiO 2 is contained in an amount of 0.12% or less, the resin becomes transparent and has low transparency. If the content of TiO 2 is 0.15% or more, the amount of the particles increases and the strength of the TiO 2 is also influenced. If the opacity is too high, It is not good because it affects.
  • a denture base resin for 3D printing comprising 1.6 to 2.1% DMAB.
  • the resin In the denture base resin for 3D printing, when the DMAB is contained at 1.6% or less, the resin does not act as a photosensitizer and the polymerization degree is low. When the resin is 2.1% or more, it is not preferable that the photopolymerization occurs due to too much light absorption. Between 1.6% and 2.1%, it is preferable to have a proper degree of polymerization with the photoinitiator.
  • 3D printing denture base resin is TEGDMA comprises less than 19.2%, not good point flowable the resin components are not mixed well less, not less than 25% Because of the high amount of diluent good point is the resin has been diluted is the strength decrease Between 19.2% and 25%, it is good that all materials are well mixed and have sufficient fluidity.
  • the denture base resin for 3D printing has lower strength when it contains less than 19.2% of Bis-GMA. If it is more than 15%, the viscosity is too high and there are many problems in resin printing. It exhibits viscosity and high strength.
  • the PENTRA For denture base resins for 3D printing, if the PENTRA contains less than 10%, it is not preferable that the strength decreases. If the PENTRA resin is more than 14.5%, the viscosity increases and it affects the printing. In the case of 10% ⁇ 14.5% It is good that it can exhibit proper strength and appropriate viscosity.
  • Di-TMPTA contains less than 11.5%, and it is not good that the strength decreases. If it exceeds 15%, viscosity increases and it affects the printing. It is good to be able to show proper strength and appropriate viscosity when printing.
  • One denture base for 3D printing according to the present disclosure can be used in 3D printers.
  • Another denture base for 3D printing according to the present disclosure meets the requirements of ISO standard 20795-1 and is not toxic.
  • Another denture base resin for 3D printing according to the present invention has excellent bending strength, elastic modulus, bonding strength and MTT, and is excellent in all parts.
  • Another denture base for 3D printing according to the present disclosure has a lower viscosity than conventional materials, leaving a small amount of slurry and forming a smooth surface.
  • Another denture base for 3D printing according to the present disclosure exhibits cytotoxicity of less than 70% of cytotoxicity.
  • the bonding strengths were significantly different in the T1 to T4 test groups except the T2 and T4 test groups, and according to the artificial teeth, the teeth 12 and 21 were compared (P ⁇ 0.05). There was no significant difference between the two groups. Especially, 23 teeth of T3 group (303.31 ⁇ 89.38 N) showed the best bond strength (p ⁇ 0.05). The appearance of tackiness and mixing was observed in T1 ⁇ T4 experimental group when the fracture pattern was observed.
  • the T1 and T3 test groups have superior flexural strength and flexural modulus, lower viscosity and bonding strength to artificial teeth than denture resins for commercial 3D printing Do.
  • Biological features also conform to ISO standards.

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  • Health & Medical Sciences (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Epidemiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Plastic & Reconstructive Surgery (AREA)
  • Dentistry (AREA)
  • Dental Preparations (AREA)
  • Dental Prosthetics (AREA)

Abstract

La présente invention concerne une résine de base pour dentiers pour l'impression 3D comprenant une résine de base pour dentiers pour l'impression 3D comprenant entre 30-43 % de diméthacrylate d'uréthane (UDMA).
PCT/KR2018/014211 2017-11-17 2018-11-19 Résine de base pour dentiers pour l'impression 3d WO2019098791A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US16/764,544 US20200383878A1 (en) 2017-11-17 2018-11-19 Denture base resin for 3d printing

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
KR10-2017-0154268 2017-11-17
KR20170154268 2017-11-17
KR1020170164015A KR102080721B1 (ko) 2017-11-17 2017-12-01 3d 프린팅용 의치상 레진
KR10-2017-0164015 2017-12-01

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Cited By (1)

* Cited by examiner, † Cited by third party
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CN112043608A (zh) * 2020-09-11 2020-12-08 无锡市腰果新材料有限公司 一种可用于临床牙科的dlp型3d打印光固化材料

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Publication number Priority date Publication date Assignee Title
US20090148813A1 (en) * 2007-08-31 2009-06-11 Sun Benjamin J Three-dimensional printing methods and materials for making dental products
KR20160055727A (ko) * 2013-04-18 2016-05-18 덴카, 인크. 광경화성 수지 조성물 및 인공 치아 및 의치상 제조를 위한 3차원 인쇄에 이를 이용하는 방법
KR101658079B1 (ko) * 2014-12-11 2016-09-20 충북보건과학대학교 산학협력단 3d프린터를 이용한 치과 치료용 도재수복물 제조방법
CN105943406A (zh) * 2016-05-19 2016-09-21 深圳长朗三维科技有限公司 口腔修复用3d打印复合材料及其制备和使用方法
WO2016182444A1 (fr) * 2015-05-12 2016-11-17 Rijksuniversiteit Groningen Résines composites antimicrobiennes pouvant être imprimées en 3d et procédés de fabrication associés

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090148813A1 (en) * 2007-08-31 2009-06-11 Sun Benjamin J Three-dimensional printing methods and materials for making dental products
KR20160055727A (ko) * 2013-04-18 2016-05-18 덴카, 인크. 광경화성 수지 조성물 및 인공 치아 및 의치상 제조를 위한 3차원 인쇄에 이를 이용하는 방법
KR101658079B1 (ko) * 2014-12-11 2016-09-20 충북보건과학대학교 산학협력단 3d프린터를 이용한 치과 치료용 도재수복물 제조방법
WO2016182444A1 (fr) * 2015-05-12 2016-11-17 Rijksuniversiteit Groningen Résines composites antimicrobiennes pouvant être imprimées en 3d et procédés de fabrication associés
CN105943406A (zh) * 2016-05-19 2016-09-21 深圳长朗三维科技有限公司 口腔修复用3d打印复合材料及其制备和使用方法

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN112043608A (zh) * 2020-09-11 2020-12-08 无锡市腰果新材料有限公司 一种可用于临床牙科的dlp型3d打印光固化材料

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