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The Journal of Advanced Prosthodontics logoLink to The Journal of Advanced Prosthodontics
. 2020 Oct 26;12(5):265–272. doi: 10.4047/jap.2020.12.5.265

An experimental study on hydrothermal degradation of cubic-containing translucent zirconia

Santiphab Kengtanyakich 1, Chaimongkon Peampring 1,✉
PMCID: PMC7604232  PMID: 33149847

Abstract

PURPOSE

The aims of this study were to investigate mechanical properties and hydrothermal degradation behaviour of the cubic-containing translucent yttrium oxide stabilized tetragonal zirconia polycrystal (Y-TZP).

MATERIALS AND METHODS

Four groups of Y-TZP (T, ST, XT, and P), containing different amount of cubic crystal, were examined. Specimens were aged by autoclaving at 122℃ under 2 bar pressure for 8 h. Phase transformation was analyzed using X-ray diffraction (XRD) to measure phase transformation (t→m). Kruskal-Wallis test was used to determine the difference. Surface hardness, biaxial flexural strength, and fracture toughness in values among the experimental groups and verified with Wilcoxon matched pairs test for hardness values and Mann Whitney U for flexural strength and fracture toughness.

RESULTS

XRD analysis showed no monoclinic phase in XT and P after aging. Only Group T showed statistically significant decreases in hardness after aging. Hydrothermal aging showed a significant decrease in flexural strength and fracture toughness in group T and ST, while group XT and P showed no effect of aging on fractural strength and fracture toughness with P<.05.

CONCLUSION

Hydrothermal aging caused reduction in mechanical properties such as surface hardness, biaxial flexural strength, and fracture toughness of Y-TZP zirconia. However, cubic-containing zirconia (more than 30% by volume of cubic crystal) was assumed to have high resistance to hydrothermal degradation. Clinical significance: Cubic-containing zirconia could withstand the intraoral aging condition. It could be suggested to use as a material for fabrication of esthetic dental restoration.

Keywords: Zirconia ceramic, Mechanical properties, Hydrothermal degradation, Cubic phase, Fracture toughness

INTRODUCTION

Yttrium-stabilized tetragonal zirconia polycrystal (Y-TZP) has excellent strength and fracture toughness after machining and sintering, which are higher than those of other dental ceramics.1,2 Tetragonal zirconia structure has been retained at room temperature by application of a stabilizer, yttrium oxide (Y2O3). However, the metastable tetragonal phase can return to a stable monoclinic phase due to the occurrence of local stress and/or humid environments.3 The volume expansion associated with the tetragonal to monoclinic transformation (t→m) results in compressive stress inside the transformed region, and consequently the crack propagation in the ceramic terminates.1

The t→m transformation can spontaneously occur at low temperature especially in the presence of water, known as aging, hydrothermal degradation or low-temperature degradation (LTD).4 Many studies indicated that the adverse effect of the LTD was the deleterious effect on mechanical and physical properties such as flexural strength, surface roughness and hardness.5,6,7,8,9,10 Increasing amount of Y2O3 stabilizer tends to alter the phase structure from tetragonal to cubic phase resulting in increased translucency and improved hydrothermal aging resistance.11,12,13,14 The amount of cubic crystal structures seems to have an effect on the microstructure of zirconia materials,15 particularly mechanical properties.14 Nowadays, the studies have reported that increasing amount of cubic phase in zirconia can improve translucency of cubic-containing zirconia compared to conventional zirconia.12,14,16 However, limited numbers of studies are available regarding the mechanical properties and degradation behavior of cubic zirconia for monolithic restorations.

The aims of this study were to investigate the mechanical properties and hydrothermal degradation behaviour among commercial translucent zirconia products containing different amount of cubic crystal (< 30%, 30 – 50%, and > 50% cubic phase) and compare them with conventional zirconia (0% cubic phase).

MATERIALS AND METHODS

Four different commercially available zirconia materials were tested in this study (Table 1). A water-cooled precision saw (Buehler, ISOMET 4000, Buehler Ltd., Lake Bluff, IL, USA) was used to section cylindrical zirconia blocks into disk-shaped (n = 22/ each group) and rectangular-shaped specimens (n = 10/ each group). All zirconia specimens were fully crystallized using high temperature furnace (VITA Zyrcomat® 6000 MS, Vita Zahnfabrik H. Rauter GmbH & Co. KG, Bad Säckingen, Germany) according to respective manufacturer's recommendations (Table 2). The final dimensions for each test specimen were confirmed with a digital caliper (Mitutoyo, Mitutoyo Manufacturing Company Ltd., Kawasaki, Japan); 15 mm diameter, 1 mm thickness for disk-shaped specimens, and 24 × 6 × 3 mm3 for rectangular-shaped specimens. Afterwards, all specimens were ultrasonicated (Model: 460/M, Elma Schmidbauer GmbH, Singen, Germany) in distilled water for 10 min before testing.

Table 1. Study materials.

Material Type Code Components (wt%) Amount of cubic structure (%) Lot number Manufacturer
Vita YZ T 3Y-TZP T ZrO2 (90–95), Y2O3 (4–6), HfO2 (1–3), Al2O3 (0–1), Pigments(0–1) 0 73830 VITA Zahnfabrik, Bad Säckingen, Germany
Vita YZ ST 4Y-TZP ST ZrO2 (88–93), Y2O3 (6–8), HfO2 (1–3), Al2O3 (0–1), Pigments (0–1) < 30 65890 VITA Zahnfabrik, Bad Säckingen, Germany
Vita YZ XT 5Y-TZP XT ZrO2 (86–91), Y2O3 (8–10), HfO2 (1–3), Al2O3 (0–1), Pigments (0–) 30 – 50 61960 VITA Zahnfabrik, Bad Säckingen, Germany
Prettau Anterior 6Y-TZP P ZrO2 (Main component), Y2O3 (< 12), Al2O3 (< 1), SiO2 (< 0.02), Fe2O3 (< 0.02) > 50 ZB6124B Zirkonzahn GmbH, Bruneck, Italy
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Table 2. Sintering protocol of each group.

Group Heating rate (°C/min) Final temperature (°C) Holding time (min) Cooling protocol
T 17 1530 120 Cooling off at 100% to 200°C
ST 8 1530 120 Cooling off at 100% to 200°C
XT 4 1450 120 Cooling off at 100% to 200°C
P 8 1500 120 Cooling rate 8°C/min to 50°C
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Scanning electron microscopy (SEM, FEI Quanta 400) was used to characterize the microstructure of four as sintered groups. The result of grain size in each group was reported in average grain size (µm). Hydrothermal aging simulation were set up using an autoclave (TOMY ES 215/ES-315, Tomy Kogyo Co., Ltd., Nerima, Japan) at 122℃ under 2 bar pressure over a period of 8 h. Crystal structure identification of experimented zirconia was done by X-ray diffraction analysis (XRD, Philips X'Pert MPD, Philips, Eindhoven, Netherlands) using Cu-Kα radiation from 5 – 90° (2θ). To measure phase structure before and after aging, specimens were subject to XRD to determine the peak position and composition. Peaks from the XRD output were compared to XRD library data to identify the occurrence phase structure. As a result, the tetragonal to monoclinic phase transformation was detected at the surface of the specimens. The volume fractions of transformed monoclinic zirconia (Vm) were calculated from the integral intensities of the monoclinic and tetragonal peaks (Xm). This characterization was based on the following equations proposed by Garvie and Nicholson17 and Toraya et al.18

Xm = [Im(111) + Im(111−)] / [Im(111) + Im(111−) + It(101)]
Vm = 1.311Xm / [1 + 0.311Xm]

where Im(111) and Im(111−) represent the intensity of monoclinic phase peaks (2θ = 28° and 2θ = 31.2°, respectively) and It(101) represent the intensity of tetragonal phase peak (2θ = 30°). All data of control groups (no aging) and aging groups were compared.

The surface hardness was measured on disk-shaped specimens (n = 5) by the indentation method using Vickers microhardness test (Mitutoyo, Model: HM-211, Mitutoyo Corporation, Kawasaki, Japan) with load 1 kg for 10 s. Five indents were placed in each specimen, and the Vickers hardness was calculated using the following equation:19

Hv = (1.8544P)d2

where Hv is the Vickers hardness, P is the applied load (kg), and d is the mean indentation diagonal length (mm).

Afterwards, the same specimen was hydrothermal aged and microhardness test was repeatedly evaluated to compare with results of the specimen before aging.

The biaxial flexural strength testing was performed according to ISO standard number 6872.20 Disk-shaped specimens (n = 5) were positioned with the hydrothermally-aged surface facing down on three support balls (Ø = 2.5 mm), which were placed 10 mm apart from each other in a triangular position. A flat circular tungsten piston (Ø = 1.6 mm) was used to apply an increasing load (0.5 mm/min) until catastrophic failure occurs using a universal testing machine (Lloyd instruments, Model LRX-Plus, AMETEK Lloyd Instrument Ltd., Hamphshire, UK). Biaxial flexural strength was calculated according to this following equation:

σ = [−0.2387P(X − Y)] / b2

where σ is the maximum tensile stress (MPa), P is the total load to fracture (N), b is the thickness at fracture origin (mm), and X and Y are calculated according to:

X = (1 + ν) ln(r2/r3)2 + [(1 - ν)/2)](r2/r3)2
Y = (1 + ν)[1 + ln(r1/r3)2] + (1 − ν)(r1/r3)2

where ν is Poisson's ratio (ν = 0.30),21 r1 is the radius of the support circle (6.05 mm), r2 is the radius of the loaded area (0.8 mm), and r3 is the radius of the specimen.

The biaxial flexural strength testing was performed on both specimens with and without hydrothermal aging and compared statistically.

The fracture toughness evaluation was performed on both specimens with and without hydrothermal aging. The test was set by using the single-edged-notched-beam (SENB) method. Rectangular-shaped specimens (n = 10) were prepared according to the previous study.22 For the SENB test set-up (Fig. 1), a notch was created on a specimen using a 0.12-mm-thick diamond disk equipped on a vertical milling machine (Mini vertical milling machine, Model CH-10M, Chung Hsiwh Industrial Co., Ltd., Ningbo, China). The specimens were cleaned ultrasonically in distilled water for 10 min and air dry for 20 s before testing.

Fig. 1. Geometry of single-edged-notched-beam (SENB) test specimen.

Fig. 1

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All test specimens were subjected to a three-point bending fixture equipped in a universal testing machine and loaded until fracture with a crosshead speed of 0.5 mm/min. Two halves of the broken specimens were evaluated to measure the notch depth under a stereoscopic microscope (Nikon, smz1500, Nikon Instech Co., Ltd., Tokyo, Japan) . The depth, a, was the average of six values at three locations of the notch, middle point, and two sides of each section. The fracture toughness value (KIC) was calculated according to the following equations:22

KIC = [FcL((a/d))] / bd3/2
(a/d) = 2.9(a/d)1/2 − 4.6(a/d)3/2 + 21.8(a/d)5/2 − 37.6(a/d)7/2 + 38.7(a/d)9/2

where Fc is the critical load or the maximum load (MN), d is the specimen thickness (m), b is the specimen width (m), L is the span length between supports (0.016 m), a is the notch depth (m) and (a/d) is the stress intensity shape factor. The actual values of a and d of each specimen were used.

Descriptive statistics were conducted for phase characterization. Mean and standard deviations of all data for each experiment were calculated. Assessment of normality distribution and homogeneity of variance were carried out using the Shapiro-Wilk test and Levene's test, respectively. Because the data was not normally distributed and homogeneity of variance was not equal in each group, so the parametric test cannot be used in this study. The Kruskal-Wallis test was used to determine the significant difference in hardness, flexural strength, and fracture toughness values between various types of zirconia in relation to aging condition. When a significant difference was detected, it was then verified with Wilcoxon matched pairs test for hardness values and Mann Whitney U test for flexural strength and fracture toughness values. The statistical analysis was done using SPSS software, version 24.0 (IBM Corporation, Armonk, NY, USA) to detect statistically significant differences (α = .05).

RESULTS

SEM images of the as-sintered specimens were shown in Fig. 2. The average grain size for group T, ST, and XT were 1.42, 1.35, and 1.57 µm, respectively. Group P had the largest average grain sizes of 2.28 µm.

Fig. 2. Scanning electron microscope images of four groups after sintering. (A) Group T, (B) Group ST, (C) Group XT, (D) Group P (magnification × 20000).

Fig. 2

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No monoclinic phase was detected in all material groups before aging. The amount of tetragonal to monoclinic phase transformation increased after aging in T and ST groups, up to 16.45% and 5.06% respectively, as opposed to undetectable amount of monoclinic phase after aging in XT and P groups (Fig. 3, Fig. 4). The hardness value for the each group at before and after aging was showed in Table 3. Before aging, the mean hardness values showed no significant differences among the material groups. Group T showed statistically significant decrease in hardness after aging (P < .05) The mean flexural strengths in group T and ST were significantly higher than those in group XT and P in specimens without aging. Groups T and ST were significant lower in flexural strength in hydrothermally-aged specimens compared to specimens without aging. However, group XT and P showed no significant difference in flexural strength between with and without aging (Table 4). Fracture toughness values showed statistical differences amongst the material groups and aging conditions (P < .05). Mann Whitney U test analysis showed fracture toughness in no aging specimens in group in the following order: T > ST > XT, P. With aging, the fracture toughness of the group XT and P were statistically the same, whereas the fracture toughness showed statistically significant decreases for group T and ST (P < .05) (Table 5).

Fig. 3. X-ray diffraction analysis of group T (A) before and (B) after hydrothermal aging.

Fig. 3

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Fig. 4. X-ray diffraction analysis of group P (A) before and (B) after hydrothermal aging.

Fig. 4

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Table 3. Mean ± SD and medians of hardness (GPa).

Group Before aging After aging
Mean (SD) Median Mean (SD) Median
T 13.65 ± 0.21Aa 13.65 12.58 ± 0.15Bb 12.61
ST 13.96 ± 0.22Aa 13.94 13.60 ± 0.22Aa 13.66
XT 13.62 ± 0.22Aa 13.70 13.62 ± 0.27Aa 13.70
P 13.72 ± 0.18Aa 13.74 13.57 ± 0.16Aa 13.64
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* A, BDifferent letters present significant differences between materials (P < .05).

a, bDifferent letters present significant differences between aging conditions (P < .05).

Table 4. Mean ± SD and medians of flexural strength (MPa).

Group Without aging With aging
Mean (SD) Median Mean (SD) Median
T 872.73 ± 124.16Aa 821.82 705.75 ± 55.54Ab 728.20
ST 779.92 ± 32.77Aa 780.91 641.19 ± 64.60Ab 674.67
XT 463.37 ± 39.10Ba 477.48 473.67 ± 74.89Ba 467.55
P 450.60 ± 77.34Ba 494.20 483.23 ± 33.64Ba 485.14
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* A, BDifferent letters present significant differences between materials (P < .05).

a, bDifferent letters present significant differences between aging conditions (P < .05).

Table 5. Mean ± SD and medians of fracture toughness (MPa m1/2).

Group Without aging With aging
Mean (SD) Median Mean (SD) Median
T 15.49 ± 1.08Aa 15.91 11.56 ± 0.45Ab 11.60
ST 10.01 ± 0.58Ba 9.88 7.45 ± 1.16Bb 6.99
XT 3.30 ± 0.40Ca 3.16 3.19 ± 0.22Ca 3.22
P 3.48 ± 0.36Ca 3.41 3.46 ± 0.36Ca 3.38
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* A, B, CDifferent letters present significant differences between materials (P < .05)

a, bDifferent letters present significant differences between aging conditions (P < .05)

DISCUSSION

The increased demands of patients for esthetic restorations have been driving the development of dental restorative materials from conventional zirconia to highly translucent monolithic zirconia ceramic materials. Fabrication of translucent zirconia can be performed in many ways: changing the composition and grain size, and altering the sintering conditions and material thickness.23,24,25,26,27 Recently, many companies have been improving zirconia translucency by trying to retain more cubic structure at room temperature. This recent study used various commercial products, which could be classified based upon the amount of cubic structure as low (< 30%), moderate (30 – 50%), and high cubic-containing zirconia (> 50%).

This study investigated the mechanical properties and accelerated aging characteristics of 3 categories of commercial translucent zirconia as mentioned previously (< 30%, 30 – 50%, and > 50% cubic-containing) under extreme in vitro conditions. From the result of this study, the null hypothesis that the mechanical properties of the cubic zirconia material would not be influenced by hydrothermal aging was rejected. The strategy of increasing the amount of cubic crystals to improve translucency of monolithic zirconia resulted in reduction of mechanical properties such as flexural strength and fracture toughness.28 Fracture toughness is a mechanical property that describes the resistance of brittle materials to catastrophic propagation of flaws under applied stress.21 This in vitro study evaluated the fracture toughness by using SENB method because it is considered to be a reliable method.22 Also, specimen preparation, especially notch creation, was not technique sensitive.

The transformation toughening is a process in which the stresses induce transformation of tetragonal crystal to monoclinic crystal in stabilized zirconia. This process is associated with a large volume expansion (3 – 5%) resulting in occurrence of compressive stresses opposing crack opening and acts to increase resistance to crack propagation.29 Zirconia containing cubic crystal more than 30% by volume (group XT and P) showed significant decrease in flexural strength and fracture toughness. It is because the cubic zirconia structure is more stable phase and it reduces its potential for stress-induced transformation toughening.30 The average flexural strength and fracture toughness in cubic-containing group (cubic > 30%) were lower than 500 MPa and 3.5 MPa m1/2 respectively. Therefore it is recommended to used monolithic restoration for a three-unit fixed prosthesis not involving molar restoration, clinically. However, group ST containing cubic crystal less than 30% by volume presented higher amount of tetragonal structure for transformation toughening phenomenon. As a result, flexural strength for group ST was still greater than 500 MPa but not exceeding 800 MPa. Therefore, it can be recommended to fabricate prosthesis involving molar restoration with the span not more than four units. On the other hand, conventional zirconia in this present study exhibited the highest strength. Therefore, it is recommended for the fabrication of prostheses involving partially or fully covered substructure for four or more units.20

This study investigated in vitro accelerated hydrothermal aging characteristics of material using autoclave condition at 122℃ under 2 bar pressure over a period of 8 h. It is possible to assume that 1 h of autoclave aging in this condition has the same effect as 1 year in clinical services.31 X-ray diffraction analysis showed that there was no monoclinic phase presented after hydrothermal aging in group XT and P. The results indicated that high amount of cubic crystal caused a more stable condition of zirconia; therefore, t→m transformation did not occur. The present results correspond with a previous study evaluating the aging stability of 5Y-0.05Al after accelerated hydrothermal aging in steam at 134℃ and 2 MPa in water vapour. The authors reported that cubic zirconia did not show any transformation after 300 h of accelerated hydrothermal treatment.11 It can be assumed that a zirconia containing cubic crystal more than 30% by volume had a pronounced effect on retarding the hydrothermal degradation. On the contrary, zirconia containing less than 30% by volume of cubic crystal exhibited the presence of monoclinic phase, which approximately 5.06% after hydrothermal aging for 8 h. The negligible amount of monoclinic phase presented after aging in zirconia containing less than 30% of cubic crystal was accepted in the engineering guidelines for use of zirconia-based materials.4 For conventional zirconia, the presence of monoclinic phase after autoclave aging was agreed in part with the finding of Kim et al.,3 who evaluated the amount of monoclinic phase on IPS e.max ZirCAD (conventional zirconia) by XRD after 8 h of aging. Flinn et al. assessed the effect of aging on mechanical properties of zirconia. Based on their results, hydrothermal aging of conventional Y-TZP materials can cause a significant t→m phase transformation, which resulted in a statistically significant decrease in the mechanical properties of zirconia.8,9,10 Results of the above study corresponded to our present study, which reported that flexural strength and fracture toughness were reduced significantly after hydrothermal aging, especially in conventional group. On the other hand, some previous studies reported that dental zirconia had no significant difference in bulk properties such as flexural strength after aging.7 The present results showed that amount of cubic crystal more than 30% by volume could increase the hydrothermal aging resistance, even though the mechanical properties were significantly altered. More stable zirconia crystal results in decreased potential for t→m phase transformation after hydrothermal aging.11

Ramesh et al.13 stated that a small grain size is beneficial in suppressing hydrothermal aging induced t→m phase transformation of Y-TZP. It was found that if grain sizes were below 0.5 µm, the t→m phase transformation was suppressed. The result of this study was not coinciding with result of previously mentioned study. It could be explained that the average grain size for group P was 2.28 µm and the t→m transformation did not occur after aging. However, the various processing condition to prepare the zirconia materials and the amount of yttria stabilizer added during powder preparation may affect the optimum grain size.13

Zirconia with no cubic content or high amount of tetragonal phase increases hydrothermal degradation and phase transformation, which could correspond to several mechanisms.32 Hydrothermal degradation is a process in which the transformation of tetragonal to monoclinic phase occurs because of humidity. Formation of the hydroxyl ions (OH-) in water molecules can diffuse into the zirconia lattice then water reacts with ZrO2 or Y2O3 bonds at crack tips. As a consequence, Zr-OH or Y-OH bonds are formed. The Zr-OH or Y-OH bond brings about the lattice strain on the surface. Strain accumulation creates nucleation sites for phase transformation on the surface; consequently, the metastable tetragonal transformation to stable monoclinic phase can occur.33,34,35 Therefore, when the amount of monoclinic was increased and continued from the external surface to the internal of material, the volume expansion by phase transformation and the degradation of the mechanical properties occurred. For this reason, the strengths of group T and ST were decreased. Further studies are required to investigate the other properties of the cubic-containing commercial translucent zirconia such as optical properties. Furthermore, researches are necessary to assess the long-term cyclic fatigue resistance of this type of zirconia. Lastly, the in vivo studies and wear characteristic of the cubic-containing commercial translucent zirconia should be evaluated.

CONCLUSION

Based on the limitations of this in vitro study, the mechanical properties evaluation showed that cubic-containing zirconia materials (group ST, XT, and P) exhibited lower flexural strength and fracture toughness than non-cubic 3Y-TZP zirconia (group T). However, hydrothermal aging in autoclave for 8 h caused a statistically significant decrease in the mechanical properties of non-cubic 3Y-TZP zirconia (group T) and cubic-containing zirconia with the amount of cubic content less than 30 % by volume (group ST), owing to the spontaneous t→m transformation. In addition, zirconia containing more than 30% by volume of cubic crystal (group XT and P) were assumed to have high resistance to low temperature degradation.

ACKNOWLEDGMENTS

The authors gratefully thank Mrs. Chanya Chuena-rrom, Faculty of Dentistry, Prince of Songkla University for supporting in this work and we would like to thank all companies for access to the zirconia materials.

Footnotes

The study was provided by the Technologies and Materials in Digital Dentistry Research Unit, Faculty of Dentistry, Prince of Songkla University, Songkhla Province, Thailand.

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