Journal of ISSN: 2373-4345JDHODT

Dental Health, Oral Disorders & Therapy
Research Article
Volume 1 Issue 4 - 2014
Three-Dimensional Finite Element Analysis of Lower Molar Tooth Restored with Fully Milled and Layered Zirconia Crowns
Salma M Fathy1*, Mohamed I El-Anwar2, Abeer A El-Fallal1 and Salwa A El-Negoly1
1Department of Dental Biomaterial, Faculty of Dentistry, Mansura University, Egypt
2Department of Mechanical Engineering, National Research Centre, Egypt
Received: August 03, 2014 | Published: August 25, 2014
*Corresponding author: Salma M Fathy, Department of Dental Biomaterial, Faculty of Dentistry, Mansura University, Mansoura, Daqahlia 35516, Egypt, Tel: 00201000153552; Email: @
Citation: Fathy SM, El-Anwar MI, El-Fallal AA, El-Negoly SA (2014) Three-Dimensional Finite Element Analysis of Lower Molar Tooth Restored with Fully Milled and Layered Zirconia Crowns. J Dent Health Oral Disord Ther 1(4): 00022. DOI: 10.15406/jdhodt.2014.01.00022

Abstract

Comparing the principle stresses distributions for both fully milled zirconia (FMZ) crown made of yattria-stabilized zirconia (Y-TZP) and layered crowns made Y-TZP core and feldspathic porcelain veneer using finite element analysis, was shot in this study. A three dimensional finite element model was constructed under ANSYS environment. The natural prepared tooth or titanium (Ti) abutment/implant complex were modeled in 3D on commercial general purpose CAD/CAM software. Crown geometry was acquired by using 3D contact scanner, which goes through successive graphical modification before assembled in a 3D finite element model. Crown made from single material (FMZ) is stiffer than layered one. The crown outer layer (Porcelain) receives more energy and stresses (of order 3.8%) than if it was made from Zirconia. While the crown core (inner part) will receive less stresses (about 38%) and energy if it was coated by Porcelain.
Keywords: Finite element method; Stress distribution; Dental materials; Crown; Dental implant; Fully milled zirconia

Introduction

The introduction of zirconia (ZrO2) in the field of dentistry as restorative material used for crown core substructure or bridge framework manufacture has been widely expanded [1]. Its high flexural strength in comparison to metals [2] and other types of ceramics [3] has made the manufacture of accurate all-ceramic and long-span restorations possible [4]. Over the past two decades improvement in core and veneering ceramic materials together with their manufacture process technique has made these layered restorations successful and reliable [5]. However, clinical studies reported fracture incidences for the core and veneering ceramic in alumina-based restorations and predominantly chipping of the veneering ceramics in zirconia-based systems [6-9].
The problem of chipping arising in ZrO2 based ceramic restoration is due to propagation of crack parallel to the ZrO2/veneer interface [10]. Several studies have been conducted to evaluate the effect of thermally induced failure in such layered restoration [11-13]. However this failure may be also attributed to continue exposure of this layered ceramic restoration to cyclic loading in moist oral environment [14] or even static loading at its maximum values as this study tries to evaluate. The former two cases may contribute to crack propagation at ZrO2 core/veneer interface as well as the case of thermal stresses.
Most ZrO2 based-ceramic restorations do have other problems such opaqueness of the core, which should be masked with a translucent layer of veneer ceramic to achieve the natural appearance [15]. The color of this opaque core significantly influences the color of the ceramic restoration [16]. Low temperature degradation (LTD) is another problem accompanying this type of restorations. Where, progressive spontaneous transformation of the metastable tetragonal phase into the monoclinic phase (t-m transformation) happens in the mouth temperature with its wet environment [17]. That phenomenon was reported to have progressive drawbacks on ZrO2 core properties [18,19]. Zirconia full-coverage restorations without veneering dental porcelain, was recently released. Translucent, FMZ or monolithic zirconia crown has many advantages over the porcelain veneered zirconia copings in that no liability of veneering fracture or chipping as it is already absent. The absence of over layer of porcelain may eliminate the possibility of having internal stresses induced at ZrO2 core/veneer interface [20]. In addition to its high translucency that was still higher than layered ceramic crowns even after exposure to ageing using chewing simulator [21].
Finite element analysis is an accepted and accurate theoretical technique used in solving engineering problems [22]. It has proven to be a reliable method in dentistry, especially in the field of representing the geometry of implant system [23-25]. It will provide a reliable and non-complicated technique evaluating the stresses in a complex geometry formed by two types of crowns and other different substructures used in the present study. The aim of this study was to evaluate and compare the maximum and minimum principle stresses for both FMZ and layered zirconia crowns using finite element stress analysis.

Materials and Methods

Acrylic tooth representing the lower first molar tooth was ground prepared to receive a full coverage restoration made of either FMZ or layered ZrO2 crown. A shoulder finish line was done using tapered diamond stone with flat end. Axial walls were reduced with a 6o angle of inclination and occlusal surface was reduced by about 1.5 mm. Double layer impressions of the lower and upper acrylic teeth models, representing patient with normal occlusion, were recorded using polysiloxane impression materials (Express, 3M/ESPE, St., Paul, MN, USA). Occlusal bite registration was recorded in centric occlusion between upper and lower models and sent to laboratory to fabricate ceramic crown using CAD/CAM technique according to manufacturer’s instructions on working casts.
Three dimensional finite element model was constructed under ANSYS vr.9.0 (ANSYS Inc., Canonsburg, PA, USA) environment representing both types of crowns as FMZ and layered one. Crown geometry was acquired by using 3D scanner (Roland Modela - model MDX-15 - Roland DG Corporation of Hamamatsu, Japan) and computer graphics program (Roland´s Dr. PICZA 3™ software), utilizing Roland Active Piezoelectric Sensor as presented. Such scanner produced data file containing a cloud of points coordinates, see Figure 1. An intermediate, software was required (Rhino 3.0 - McNeel inc., Seattle, WA, USA) to trim a newly created surface by the acquired points, that was divided into two parts, lower part (not required), and upper part represented the crown surface. Finally, the crown outer surface was closed and filled from its bottom to generate volume representing solid crown. The generated crown contains covering layer of 1mm thickness as a separate part for simulating coating material. Then, the crown geometry was exported to finite element program as SAT file format [26]. Two crown materials, Y-TZP and feldspathic porcelain were investigated in this study. Both crowns were cemented with resin cement (Variolink II, Ivoclar Vivadent, Schaan / Liechtenstein). To be mounted on either dentine abutment/root complex or Ti abutment/implant complex. Simulated resin cement layer was of 50 micrometers in thickness. Both complexes were modeled in 3D as elliptic cross sectional bar (8.7 x 7.0 mm reduced to 6.3 x 7.0 mm linearly along 4.2 mm) on commercial general purpose CAD software “AutoDesk Inventor” version 8.0 (Autodesk Inc., San Rafael, CA, USA). Bone geometry was simplified and simulated as cylinder that consists of two co-axial cylinders. The inner one represents spongy bone (diameter 14 mm & height 22 mm) that filling the internal space of the other cylinder (shell of 1mm thickness) that represents cortical bone (diameter 16 mm & height 24 mm) [27,28]. Weighted average properties for tooth dentine & cementum were used for abutment/root complex. All material properties used in this study were listed in Table 1.

Material

Young’s Modulus [MPa]

Poisson’s Ratio

Cancellous bone

1,370

0.30

Cortical bone

13,700

0.30

Implant complex or natural tooth substructure

  1. Titanium abutment and fixture
  2. Root (weighted average from dentine and cementum)
  3. Dentine abutment

 

110,000

4,450

18,600

 

0.35

0.30

0.31

Resin cement (Variolink II) (50 µm cement layer)

8,300

0.30

Crown materials

  1. Zirconia (core)
  2. Porcelain (coating)
  3. FMZ crown

 

210,000

70,000

210,000

 

0.30

0.19

0.30

Table 1: Material properties.

 

Nodes

Elements

Cortical

896

2,604

Spongy

1,761

7,697

Abutment (Ti or Dentine)

1,226

5,697

Implant (Ti or Root)

1,758

8,389

Cement layer

496

1,393

Crown (core)

1,257

5,169

Crown (coating)

1,346

4,732

Table 2: Number of nodes and elements.
Figure 1: Pictures of (a) scanned crown, (b) 3D Scanner, and (c) resulted cloud of points.
The two crowns were subjected to oblique load of 300 N with 45°, and vertical compressive loading of 655 N, at two points, which were selected near the cusp tips of mesiobuccal (MB) cusp (29) and distobuccal (DB) cusp inclines on the occlusal table (equally distributed on four close points), which is too close to implant-abutment complex axis. The base of the finite element models set to be fixed which defined the boundary condition [28].
The bonding simulates perfect osseointegration in which the implant and the surrounding compact bone are fully integrated that neither sliding nor separation in the implant-bone interface is possible, similarly as cement layer bond with either crown and tooth (abutment). Analyzing force transfer at bone-implant interface is an essential step in the overall analysis of loading case, which determines the success or failure of an implant. It has long been recognized that both implant and bone should be stressed within a certain range for physiologic homeostasis. Overload can lead to bone resorption or fatigue failure of the implant, whereas under loading of the bone may cause disuse atrophy and subsequent bone loss.
However, the validity of a linear static analysis is questionable for more realistic situations such as sudden loading. But in such studies the endurance limit (fatigue failure limit), governs most cases of dental analysis. In case of having static stresses lower than endurance limit under worst case of external loads it will be safe from fatigue failure.

Results

This study includes four combinations of material cases, two types of crowns (monolithic ZrO2, and ZrO2 core layered with porcelain veneer), two types of abutments (dentine and Ti) and two types of roots dental root (weighted average of dentine and cementum), or Ti implant. Each of these cases was subjected to two types of loading (655 N vertical and 300 N oblique) to obtain eight model runs. Each run can produce thousands of graphical results pictures showing all possible types of deformations, strains, and stresses on each part of the studied model. Principal and Von Mises stresses distributions, and deformations in the global Cartesian coordinates, in addition to the equivalent deformation distributions were obtained as pictures for each component of the studied model. Most important deformations/stresses components were presented and discussed here within this research. The FMZ crown showed maximum Von Mises stress values of 86.05 MPa directly under vertical loading and 27.4 MPa under oblique loading at the areas of load application on the slope of MB cusp toward central groove as presented in Figure 3. However the layer of porcelain veneer received higher Von Mises stress by about 3.7% than FMZ and it reduced its value transferred to ZrO2 core by about 33.9% (to be 59.06 MPa). Figure 4 illustrate deformation and stress distribution on the porcelain layer. The ZrO2 core received lower value of maximum principal shear stress than porcelain veneer by about 35.6%. That stress was concentrated on occlusal surface of the core on veneer/core interface. These results were obtained under vertical load application and were comparable to oblique load results with both dentine and Ti abutments underneath. Generally, Figure 3 & 4 show maximum stresses at applied load locations, on crown (layered ZrO2 and FMZ). The maximum Von Mises stress values are within the safe levels that ensure lifetime functioning of both types of crowns.
Figure 2: Complete model and Sectional view in the meshed model showing cement layer around implant-abutment complex.
Figure 3: Crown (a) vertical deformation and (b) Von Mises Stress distributions in case of FMZ Crown, and natural tooth substructure under oblique load.
Figure 4: Porcelain layer (a) total deformation and (b) Von Mises stress distributions in case of Ti substructure under oblique load.
Figure 5: Cement layer (a) total deformation and (b) Von Mises Stress distributions in case of FMZ crown, and Ti abutment/ implant complex under vertical load.
Figure 6: Abutment (a) deformation in X direction and (b) maximum compressive stress in case of layered ceramic crown and natural root under vertical load.
Figure 7: Ti implant (a) deformation in Z direction and (b) Von Mises stress in case of layered ZrO2 crown under oblique load.
Figure 8: Cortical bone (a) maximum compressive stress and (b) Von Mises distributions in case of dental root and FMZ crown under Vertical Load.
Figure 9: Spongy bone (a) deformation in Z direction and (b) Von Mises stress distribution in case of FMZ crown and natural root under oblique load.
Figure 10: Bones and crown Von Mises stress comparison of different model combinations (cases) under vertical load.
Maximum values of Von Mises stress on cement layer showed no significant difference under both crowns and they were concentrated on the occlusal part of the cement from the buccal side as well as the maximum total deformations as presented in Figure 5. Although the maximum values can be considered as critical values (maximum Von Mises stress of 60.67 MPa under vertical loading on layered crown) but it can be accepted for two reasons; (1) value of applied load is rarely occurred and, (2) sharp edge of cement layer will produce stress concentration that suddenly increases the stress value.
Dentine abutment showed maximum Von Mises stress lower values than those of Ti abutment by about 29.5 % under both vertical and oblique loads. On the other hand it showed higher total deformation than Ti abutment by 54.5 % and 33.3 % under vertical and oblique load, respectively, as presented in Figure 6. Ti implant showed worse performance than natural root. It transferred higher stress to underlying spongy bone denoting lower susceptibility of osseointegration around Ti implant. Samples of Ti implant results under layered ZrO2 crown that subjected to oblique load are presented in Figure 7.
Cortical and spongy bones behavior was illustrated in Figure 8 and 9 as distributions of deformation and different stress types. Spongy bone showed higher value of maximum Von Mises stress in case of Ti implant than dental root in case of FMZ and under both vertical and oblique loads.
The two substructure results both crown types (FMZ, and layered ZrO2 crown) had negligible effect on either Ti implant or dentine root or on two types of bone as presented in Figure 10. Which contain a graphical comparison of maximum Von Mises stress, on bones and crown under vertical load.

Discussion

All parts of the model are safe under such loading conditions. Vertical loading is more critical from mechanical point of view specially that its value is about double the oblique one. Zirconia has showed higher stability and durability in comparison to other ceramic materials used as frameworks. While the major problem accompanied with ZrO2 framework is the chipping of porcelain veneer [31]. That may be precipitated due to difference in CTE between core and veneer material, surface finish of core material causing flaws and defects which, yield residual stresses at the interface or due to wettability of the veneer material and its volumetric shrinkage properties [32]. Not much research were done on FEA of monolithic ZrO2 till now but by analyzing the results of this study it was found that maximum Von Mises stress resulted in FMZ crown are within the safe levels (86.05 MPa) that far away below the fatigue limit of colored Y-TZP type (600 MPa) used in this study [33]. In contrast with the results of a previous study, [34] where the difference in young’s modulus between ZrO2 and Porcelain affected Von Mises stress resulted within cement layer, the present study showed no significant difference in maximum Von Mises stress values within the cement layer under both types of crowns. That may be attributed to the fact that cement had the lowest elastic modulus value that in turn had led to higher energy absorbance by this weak layer by almost the same amount. On the other hand porcelain veneer had significantly reduced the principal stresses by about 30 % than it was in case of FMZ. This finding support the theory that porcelain veneer has protected the core by reducing the stresses or energy transferred to it (31). Although stresses are safe for both FM and core ZrO2 but the fact that the flexural strength of core ZrO2 is higher than that of FMZ material [35] puts the material with lower flexural strength under higher Von Mises stress and vice versa. That point concerned with material durability needs more research. In agreement with a previous study [31] the lower elastic modulus value for porcelain veneer resulted in lower energy transferred to the ZrO2 core in which the maximum Von Mises stress and principal shear stress were concentrated on the occlusal surface below the applied force in the interface region. Although, the maximum Von Mises stress may exceed the values of ceramic veneers chipping shear stress (31 – 38 MPa) [36], it is not dangerous for the bond between core and veneer materials under applied compressive loads. That, the coating layer stress state, is dominated by compressive stress, while shear stress did not exceed 30 MPa. Monolithic ZrO2 crown has the advantage of absence of this veneer coating thus eliminating that risk of chipping failure. In general layered crown may absorb more energy than FMZ crown, therefore it may be recommended over the FMZ one for two reasons first porcelain veneer may protect the underplaying core and second it is supposed to transfer lower energy to the underlying cement phase.
Titanium implant has more rigid properties than bone material resulting in unresolved compatibility between the two structures and the modified active coating is easily lost during implant process [37]. In agreement with previous study, material (dental root) with lower elastic modulus resulted in lower energy or stresses transferred to surrounding spongy bone by 29.5 % than material with higher elastic modulus (Ti implant) [38,39]. This may be attributed to higher stiffness of Ti implant that resulted in higher stress transfer to surrounding bone and thus impaired durability of the implant material resulted from higher possibility of future bone resorption under applied vertical or oblique loads. The high Ti implant elasticity may produce significantly higher spongy bone deformation under vertical load by 75 % higher than the case with dental root. Von Mises stress values on both types of bones are accepted and ensured safe lifetime functioning. Both cases showed safe and acceptable values and no worry from fatigue failure on these parts.
Oblique loading in this study generates stresses of order 30% of the vertical load cases at the top (outer) layer of the crown. The inner part (core) of the crown showed the same trend and order of magnitude for different types of stresses and deformations. These results were easily expected from the load value and oblique angle under linear analysis.

Conclusion

Spongy bone suffers from higher stresses under implant (Titanium root) by about 8.8%, that Titanium is stiffer (or more rigid) than dentine root. That is why it may transfer more energy to the spongy bone than the dental root. While spongy bone showed higher deformation of about 1.0 to 1.5 microns under dental root than it did under the Ti implant.
Cortical bone is safe in all cases included in this study. About only 0.65% maximum difference between stresses generated on cortical bone under both types of crowns and both types of infra-structure complexes was detected.
Dentine Root (natural root) receive less stresses than titanium implant by about 36% that it matches bone(s) properties. Lower deformation in Ti implant, in comparison to natural root helps in fast osseointegration.
Cement of 50 µm layer thickness is safe in all cases included in this study. Dentine root is better than implant (Titanium root) that reduces generated stresses, but deformations showed the opposite trend. Both types of crowns showed insignificant difference on stresses generated on the cement layer and root.
Crown made from single material (Zirconia) is stiffer than ZrO2 core with porcelain veneer. Therefore the crown outer layer receives more energy and stresses (of order 3.8%) if it was manufactured from less rigid material than Zirconia like Porcelain. That the crown core (inner part) will receive less stresses (about 38%) and energy if it was coated by Porcelain (softer than Zirconia).
Coating Material (Porcelain) deforms about 1 micron more than the same layer if it was made from Zirconia (as the crown core material). This deformation is indicative for more energy absorption. This as a general rule using softer crown coating material is preferred to reduce energy and stresses transfer to the underneath parts.
Generally, Porcelain veneer had higher deformation than FMZ surface and transferred lower energy to core substructure. Thus, layered crown may have higher probability to veneer chipping, hence, a probability to failure under maximum occlusal loading which is rarely occurred.

References

  1. Aboushelib MN, Kleverlaan CJ, Feilzer AJ (2008) Effect of zirconia type on its bond strength with different veneer ceramics. J Prosthodont 17(5): 401-408.
  2. Piconi C, Maccauro G (1999) Zirconia as a ceramic biomaterial. Biomaterials 20(1): 1-25.
  3. White SN, Miklus VG, McLaren EA, Lang LA, Caputo AA (2005) Flexural strength of a layered zirconia and porcelain dental all-ceramic system. J Prosthet Dent 94(2): 125-131.
  4. Gravei RC, Hannink RH, Pascoe RT (1975) Ceramic steel? Nature 258(5537): 703-704.
  5. Rekow D, Zhang Y, Thompson V (2007) Can material properties predict survival of all-ceramic posterior crowns? Compend Contin Educ Dent 28(7): 362-368.
  6. Heintze SD, Rousson V (2010) Survival of zirconia- and metal-supported fixed dental prostheses: a systematic review. Int J Prosthondont 23(6): 493-502.
  7. Schley JS, Heussen N, Reich S, Fischer J, Haselhuhn K, et al. (2010) Survival probability of zirconia-based fixed dental prostheses up to 5 yr: a systematic review of the literature. Eur J Oral Sci 118(5): 443-450.
  8. Pjetursson BE, Sailer I, Zwahlen M, Hammerle CH (2007) A systematic review of the survival and complication rates of all-ceramic and metal-ceramic reconstructions after an observation period of at least 3 years. Part I: Single crowns. Clin Oral Implants Res 18(Suppl 3): 73-85.
  9. Odman P, Andersson B (2001) Procera AllCeram crowns followed for 5–10.5 years: a prospective clinical study. Int J Prosthodont 14(6): 504-509.
  10. Sailer I, Feher A, Filser F, Gauckler LJ, Luthy H, et al. (2007) Five-year clinical results of zirconia frameworks for posterior fixed partial dentures. Int J Prosthodont 20(4): 383-388.
  11. Coelho PG, Silva NR, Bonfante EA, Guess PC, Rekow ED, et al. (2009) Fatigue testing of two porcelain-zirconia all-ceramic crown systems. Dent Mater 25(9): 1122-1127.
  12. DeHoff PH, Anusavice KJ, Gotzen N (2006) Viscoelastic finite element analysis of an all-ceramic fixed partial denture. J Biomech 39(1): 40-48.
  13. Isgro G, Wang H, Kleverlaan CJ, Feilzer AJ (2005) The effects of thermal mismatch and fabrication procedures on the deflection of layered all-ceramic discs. Dent Mater 21(7): 649-655.
  14. DeHoff PH, Anusavice KJ (2009) Viscoelastic finite element stress analysis of the thermal compatibility of dental bilayer ceramic systems. Int J Prosthodont 22(1): 56-61.
  15. Lim HN, Yu B, Lee YK (2010) Spectroradiometeric and spectrophotometric translucency of ceramic materials. J Prothetic Dent 104(4): 239-246.
  16. Li Q, Yu H, Wang YN (2009) Spectrophotometric evaluation of the optical influence of core build-up composites on all-ceramic materials. Dent Mater 25(2): 158-165.
  17. Lawson S (1995) Environmental degradation of zirconia ceramics. J Eur Ceram Society 15(6): 485-502.
  18. Basu B, Vleugels J, Biest O (2004) Microstructure-toughness-wear relationship of tetragonal zirconia ceramics. J Eur Ceram Soc 24(7): 2031-2040.
  19. Basu B, Vitchev RG, Vleugels J, Celis JP, Van Der Biest O (2000) Influence of humidity on the fretting wear of self-mated tetragonal zirconia ceramics. Acta Materialia 48(10): 2461-2471.
  20. Yu-Soek J, Jae-Whang L, Yeon-Jo C, Jim-Soo A, Sang-Wan S, et al. (2010) A study on the in vitro wear of the natural tooth structure by opposing zirconia or dental porcelain. J Adv Prothodont 2(3): 111-115.
  21. Beuer F, Stimmelmayr M, Gueth JF, Edelhoff D, Naumann M (2012) In vitro performance of full-contour zirconia single crowns. Dent Mater 28(4): 449-456.
  22. Holmes DC, Loftus JT (1997) Influence of bone quality on stress distribution for endosseous implants. J Oral Implantol 23(3): 104-111.
  23. Akca K, Iplikcioglu H (2001) Finite element stress analysis of the influence of staggered versus straight placement of dental implants. Int J Oral Maxillofac Implants 16(5): 722-730.
  24. Chun HJ, Cheong SY, Han JH, Heo SJ, Chung JP, et al. (2002) Evaluation of design parameters of osseointegrated dental implants using finite element analysis. J Oral Rehabil 29(6): 565-574.
  25. Holmgren EP, Seckinger RJ, Kilgren LM, Mante F (1998) Evaluating parameters of osseointegrated dental implants using finite element analysis—a two-dimensional comparative study examining the effects of implant diameter, implant shape, and load direction. J Oral Implantol 24(2): 80-88.
  26. El-Anwar MI (2009) Simple technique to build complex 3D solid models, 19th International Conference on Computer Theory and Applications, Alexandria, Egypt.
  27. El-Anwar MI, El-Zawahry MM, El-Mofty M (2012) Load transfer on dental implants and surrounding bones. Australian Journal of Basic and Applied Sciences 6(3): 551-560.
  28. El-Anwar MI, El-Zawahry MM (2011) A three dimensional finite element study on dental implant design. Journal of Genetic Engineering and Biotechnology 9(1): 77-82.
  29. Brian TR, Malvin NJ, Ricardo AZ, Nelson RFAS, Danne ER, et al. (2010) Clinically-releavant design features of three-dimensional correct molar crown and related maximum principal stress. A finite element model study. Dent Mater 26(2): 156.
  30. Kohnke P (1994) ANSYS Theory Reference Manual. ANSYS Inc., Canonsburg, PA, USA.
  31. Rocha EP, Anchieta RB, Freitas AC Jr, de Almeida EO, Cattaneo PM, et al. (2011) Mechanical behavior of ceramic veneer in zirconia-based restorations: a 3-dimensional finite element analysis using microcomputed tomography data. J Prothet Dent 105(1): 14-20.
  32. Isgro G, Pallav P, van der Zel JM, Feilzer AJ (2003) The influence of the veneering porcelain and different surface treatments on the biaxial flexural strength of a heat-pressed ceramic. J Prosthet Dent 90(5): 465-473.
  33. Scherrer SS, Cattani-Lorente M, Vittecoq E, de Mestral F, Griggs JA, et al. (2011) Fatigue behavior in water of Y-TZP zirconia ceramics after abrasion with 30 μm silica-coated alumina particles. Dent Mater 27(2): e28-e42.
  34. Dejak B, Mlotkowski A, Langot C (2012) Three-dimensional finite element analysis of molars with thin-walled prosthetic crowns made of various materials. Dent Mater 28(4): 433-441.
  35. http://www.zirkonzahn.com/en/prettau-zirconia/prettau zirconia/characteristics
  36. Taskonak B, Yan J, Mecholsky JJ Jr, Sertqoz A, Kocak A (2008) Fractographic analyses of zirconia-based fixed partial dentures. Dent Mater 24(8): 1077-1082.
  37. Chen LJ, He H, Li YM, Li T, Guo XP, et al. (2011) Finite element analysis of stress at implant–bone interface of dental implants with different structures. Trans Nonferrous Met Soc 21(7): 1602-1610.
  38. Kayabas O, Yuzbasiog Lu E, Erzincanli F (2006) Static, dynamic and fatigue behaviors of dental implant using finite element method. Advances in Engineering Software 37(10): 649-658.
  39. Meijer GJ, Cune MS, Vandooren M, De Putter C, Van Blitterswijk CA (1997) A comparative study of flexible (Polyactive®) versus rigid hydroxyapatite) permucosal dental implants. I. clinical aspects. J Oral Rehabil 24(2): 85-92.
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