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1 cluding other surfaces (glass, aluminum, and porcelain).
2 mount of strengthening of feldspathic dental porcelain.
3 r of crack deflections in leucite-reinforced porcelain.
4 Y-TZP system cores were veneered with 1.5 mm porcelain.
5 ative to alumina and for alumina relative to porcelain.
6 nslucency level comparable to that of dental porcelain.
7 nfluences the degree of microcracking in the porcelain.
8 nts within the normal firing range of dental porcelain.
9 nd flexural strength of a leucite-reinforced porcelain.
10 e porcelain and a 1.5-mm-thick layer of body porcelain.
11 out infiltration and on crowns veneered with porcelains.
12 to those of the commercial high-translucency porcelains.
13  resin polymerization shrinkage strengthened porcelains.
14 eanwhile, the least reported was "modify the porcelain" 41.8%.
15 s veneer layer 1 mm thick (representative of porcelain), adhesively bonded onto a glass-like core sub
16 prepared with a 0.5-mm-thick layer of opaque porcelain and a 1.5-mm-thick layer of body porcelain.
17                    Degradation occurs in the porcelain and MGC after approximately 10(4) cycles at lo
18 n four dental ceramics: "aesthetic" ceramics-porcelain and micaceous glass-ceramic (MGC), and "struct
19 nce, we know that cups are typically made of porcelain and shatter when we accidentally drop them.
20 re fired to the maturing temperature of body porcelain and then were subjected to three cooling proce
21 er grinding increases the strength of dental porcelain and to determine whether the effectiveness of
22  stereology on 10 specimens each of 6 dental porcelains and Component No.
23                  Specimens of six commercial porcelains and the "Component No.
24  The microcrack densities of four of the six porcelains and the Component No.
25 mics, glass-infiltrated alumina, feldspathic porcelain, and transformable zirconiaare presented as ca
26 e much more chip-resistant than conventional porcelains, and at least as chip-resistant as non-infilt
27          For TI, the most common cause was a porcelain aorta (42%); for CLI, it was multiple comorbid
28 rillation, and diabetes but a higher rate of porcelain aorta, lower glomerular filtration rate, and h
29                      Reasons for TI included porcelain aorta, previous mediastinal radiation, chest w
30              The leucite particles in dental porcelains are often partially encircled by microcracks
31 nt coronary bypass grafts, and 5 (16%) had a porcelain ascending aorta.
32                                              Porcelain bars (n = 3) and discs (n = 15) were made with
33 tly small to cause only negligible shifts in porcelain bulk thermal expansion.
34 of cracks induced in the surface of the body porcelain by a microhardness indenter were measured imme
35 measurement of the area fraction of retained porcelain by an x-ray spectrometric technique described
36  the thermal expansion of leucite-reinforced porcelain can be lowered by ion-exchange, which also mod
37 ovides evidence that microcracking in dental porcelain can be minimized by a reduction of the mean le
38 dying rearrangement i, some evidence for the porcelain catalysis was obtained.
39 nd cement moved the fracture origin from the porcelain/cement interface to the cement surface, consis
40                      Flat porcelain/metal or porcelain/ceramic structures were cemented to dentin-lik
41 radically in the two bilayer systems: In the porcelain coatings, cone cracks initiate at the coating
42                                        Metal-porcelain combinations were selected to provide a range
43                                We prepared 8 porcelain compositions by mixing increasing amounts of e
44  are observed in the fine glass-ceramics and porcelain; conversely, the most quasi-plastic responses
45 hether multiple firings of commercial dental porcelains could produce changes in microcrack density.
46                                We ground 200 porcelain discs to remove imperfections and indented 120
47                            Two hundred forty porcelain discs were air-abraded.
48                                       Dentin porcelain discs were polished with a P4000-grade abrasiv
49                                              Porcelain disks were made from each composition (n = 10
50 ed the growth of surface cracks in bilayered porcelain disks.
51 orm of leucite in a leucitereinforced dental porcelain, evaluate its effect on the flexural strength,
52                                          One porcelain exhibited a weak but highly significant positi
53 (r2 = 0.24, p = 0.0003), while the remaining porcelain exhibited a weak but statistically significant
54 neral leucite has been exploited to regulate porcelain expansion.
55 duced, followed by the application of veneer porcelain for a total thickness of 1.5 mm.
56  compressive stresses in the surface of body porcelain for all of the thermal contraction mismatch ca
57 i2O6) is used as a reinforcing agent in some porcelains for all-ceramic restorations; however, it inc
58 s around them, f(mc), was estimated for each porcelain from the microcrack density and the leucite su
59 rosthetic restoration needed: 1) single unit porcelain-fused-to-metal (PFM) crowns (SCs) and 2) 3- to
60 lain thermal expansion during fabrication of porcelain-fused-to-metal crowns and bridges.
61 lgam with dental composite and all-metal and porcelain-fused-to-metal indirect restorations with rein
62 ich thermal mismatch stresses can develop in porcelain-fused-to-metal restorations, i.e., from room t
63 elains that are designed to be fused to PFM (porcelain-fused-to-metal) alloys are formulated by their
64 the conversion of leucite to sanidine during porcelain heat treatments would produce a detrimental lo
65 r the mean leucite particle size of a dental porcelain influences the degree of microcracking in the
66 ies have shown that, when feldspathic dental porcelain is cooled, leucite undergoes a transformation
67              A serious drawback of veneering porcelains is a pronounced susceptibility to chipping.
68 2O6) or pollucite (CsAlSi2O6) with Optec HSP porcelain (Jeneric/Pentron Inc., Wallingford, CT).
69  to both occlusal surface contact damage and porcelain lower surface radial fracture, while porcelain
70 d these leucite particles when cooled during porcelain manufacture are a potential source of change i
71      The microstructure of the two exchanged porcelain materials was dense, with well-dispersed small
72 .947) between the area fractions of retained porcelain measured in the present study and the oxide ad
73 elling support for the oxide layer theory of porcelain-metal bonding in dental alloy systems.
74 indered the elucidation of the mechanism for porcelain-metal bonding in dental systems, because a tes
75  test capable of detecting differences among porcelain-metal bonds of various qualities is required b
76 ce for the presence of an oxide layer at the porcelain-metal interface, provides compelling support f
77 onversion on porcelain thermal expansion and porcelain-metal thermal compatibility have been uncertai
78                                         Flat porcelain/metal or porcelain/ceramic structures were cem
79                      Hereditary leukonychia (porcelain nails or white nails) is a rare nail disorder
80 cimens, were prepared from experimental body porcelain (No. 36, J.F. Jelenko & Co., Armonk, NY).
81 rcelain lower surface radial fracture, while porcelain on a higher-hardness palladium-silver alloy fr
82                      Findings indicated that porcelain on a low-hardness gold-infiltrated alloy was v
83 posite extremes of elastic/plastic mismatch: porcelain on glass-infiltrated alumina ("soft/hard"); an
84 ry resulting in an unusual purple iridescent porcelain overglaze, called Bottger luster, at the Meiss
85  in the veneer layer, similar to that in the porcelain/palladium-silver system.
86                           We inserted glass, porcelain, plastic, wood, pencil tip, chicken bone, iron
87                                     A dental porcelain powder was mixed with rubidium or cesium nitra
88    Controls were made of untreated Optec HSP porcelain powder, formed into bars and disks, and baked
89 es with a range of glass, hydroxyapatite and porcelain reinforcements within a methacrylate-based pho
90                                       Dental porcelains rely on the high-thermal-expansion mineral le
91                   The functional surfaces of porcelain restorations are often ground to adjust occlus
92  flexural failure resistance of metal opaque-porcelain strips.
93                    Existing dentures without porcelain teeth were modified for use as a surgical guid
94                                       Dental porcelains that are designed to be fused to PFM (porcela
95 results of this study indicate that even for porcelains that exhibit a measurable change in microcrac
96            The effects of this conversion on porcelain thermal expansion and porcelain-metal thermal
97 ure are a potential source of change in bulk porcelain thermal expansion during fabrication of porcel
98  would produce a detrimental lowering of the porcelain thermal expansion.
99 systems included chipping or fracture of the porcelain veneer initiating at the indentation site.
100  be predominantly chips and fractures in the porcelain veneer, from occlusally induced sliding contac
101                                              Porcelain-veneered alumina crown restorations often fail
102 ch, clinical long-term studies indicate that porcelain-veneered alumina or zirconia full-coverage cro
103                                              Porcelain-veneered crowns are widely used in modern dent
104 ed as a die for fabrication of zirconia core porcelain-veneered crowns.
105 ave a significant effect on the longevity of porcelain-veneered crowns.
106                                              Porcelain-veneered restorations often chip and fracture
107 nia is more than 4 times higher than that of porcelain-veneered zirconia and is at least as high as t
108                                    Plates of porcelain-veneered zirconia and monolithic zirconia serv
109 ng and fracture are common failure modes for porcelain-veneered zirconia dental restorations.
110    To test this hypothesis, we cemented flat porcelain-veneered zirconia plates onto dental composite
111  to veneer chipping and fracture relative to porcelain-veneered zirconia, while providing necessary e
112 were orders of magnitude longer than that of porcelain-veneered zirconia.
113 ations, whether monolithic (single layer) or porcelain-veneered, often chip and fracture from repeate
114 ure from chipping and/or delamination of the porcelain veneers.
115 fracture is the predominant fracture mode of porcelain veneers.
116                                          The porcelains were partitioned according to whether their m
117 vessel vasculopathy that appear as atrophic, porcelain-white papules with red, telangiectatic borders
118 ring (T) by blasting the surface of the body porcelain with compressed air.
119 the current study indicate that re-firing of porcelain with large surface flaws does not significantl
120 ciated with combinations containing the body porcelain with the smaller contraction coefficient.
121 ction of cracked particles compared with the porcelains with mean leucite particle diameters above Dc
122                                          The porcelains with mean leucite particle diameters below Dc
123                              Fracture in the porcelain/zirconia system was limited to surface damage
124 e trilayer, post mortem damage evaluation of porcelain/zirconia/composite trilayers by a sectioning t

 
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