ライフサイエンスコーパス: porcelain

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 nslucency level comparable to that of dental porcelain.

6 ative to alumina and for alumina relative to 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 to those of the commercial high-translucency porcelains.

12 resin polymerization shrinkage strengthened porcelains.

13 out infiltration and on crowns veneered with porcelains.

14 s veneer layer 1 mm thick (representative of porcelain), adhesively bonded onto a glass-like core sub

15 prepared with a 0.5-mm-thick layer of opaque porcelain and a 1.5-mm-thick layer of body porcelain.

16 Degradation occurs in the porcelain and MGC after approximately 10(4) cycles at lo

17 n four dental ceramics: "aesthetic" ceramics-porcelain and micaceous glass-ceramic (MGC), and "struct

18 re fired to the maturing temperature of body porcelain and then were subjected to three cooling proce

19 er grinding increases the strength of dental porcelain and to determine whether the effectiveness of

20 stereology on 10 specimens each of 6 dental porcelains and Component No.

21 Specimens of six commercial porcelains and the "Component No.

22 The microcrack densities of four of the six porcelains and the Component No.

23 mics, glass-infiltrated alumina, feldspathic porcelain, and transformable zirconiaare presented as ca

24 e much more chip-resistant than conventional porcelains, and at least as chip-resistant as non-infilt

25 For TI, the most common cause was a porcelain aorta (42%); for CLI, it was multiple comorbid

26 rillation, and diabetes but a higher rate of porcelain aorta, lower glomerular filtration rate, and h

27 Reasons for TI included porcelain aorta, previous mediastinal radiation, chest w

28 The leucite particles in dental porcelains are often partially encircled by microcracks

29 nt coronary bypass grafts, and 5 (16%) had a porcelain ascending aorta.

30 Porcelain bars (n = 3) and discs (n = 15) were made with

31 tly small to cause only negligible shifts in porcelain bulk thermal expansion.

32 of cracks induced in the surface of the body porcelain by a microhardness indenter were measured imme

33 measurement of the area fraction of retained porcelain by an x-ray spectrometric technique described

34 the thermal expansion of leucite-reinforced porcelain can be lowered by ion-exchange, which also mod

35 ovides evidence that microcracking in dental porcelain can be minimized by a reduction of the mean le

36 dying rearrangement i, some evidence for the porcelain catalysis was obtained.

37 nd cement moved the fracture origin from the porcelain/cement interface to the cement surface, consis

38 Flat porcelain/metal or porcelain/ceramic structures were cemented to dentin-lik

39 radically in the two bilayer systems: In the porcelain coatings, cone cracks initiate at the coating

40 Metal-porcelain combinations were selected to provide a range

41 We prepared 8 porcelain compositions by mixing increasing amounts of e

42 are observed in the fine glass-ceramics and porcelain; conversely, the most quasi-plastic responses

43 hether multiple firings of commercial dental porcelains could produce changes in microcrack density.

44 We ground 200 porcelain discs to remove imperfections and indented 120

45 Two hundred forty porcelain discs were air-abraded.

46 Dentin porcelain discs were polished with a P4000-grade abrasiv

47 Porcelain disks were made from each composition (n = 10

48 ed the growth of surface cracks in bilayered porcelain disks.

49 orm of leucite in a leucitereinforced dental porcelain, evaluate its effect on the flexural strength,

50 One porcelain exhibited a weak but highly significant positi

51 (r2 = 0.24, p = 0.0003), while the remaining porcelain exhibited a weak but statistically significant

52 neral leucite has been exploited to regulate porcelain expansion.

53 duced, followed by the application of veneer porcelain for a total thickness of 1.5 mm.

54 compressive stresses in the surface of body porcelain for all of the thermal contraction mismatch ca

55 i2O6) is used as a reinforcing agent in some porcelains for all-ceramic restorations; however, it inc

56 s around them, f(mc), was estimated for each porcelain from the microcrack density and the leucite su

57 rosthetic restoration needed: 1) single unit porcelain-fused-to-metal (PFM) crowns (SCs) and 2) 3- to

58 lain thermal expansion during fabrication of porcelain-fused-to-metal crowns and bridges.

59 ich thermal mismatch stresses can develop in porcelain-fused-to-metal restorations, i.e., from room t

60 elains that are designed to be fused to PFM (porcelain-fused-to-metal) alloys are formulated by their

61 the conversion of leucite to sanidine during porcelain heat treatments would produce a detrimental lo

62 r the mean leucite particle size of a dental porcelain influences the degree of microcracking in the

63 ies have shown that, when feldspathic dental porcelain is cooled, leucite undergoes a transformation

64 A serious drawback of veneering porcelains is a pronounced susceptibility to chipping.

65 2O6) or pollucite (CsAlSi2O6) with Optec HSP porcelain (Jeneric/Pentron Inc., Wallingford, CT).

66 to both occlusal surface contact damage and porcelain lower surface radial fracture, while porcelain

67 d these leucite particles when cooled during porcelain manufacture are a potential source of change i

68 The microstructure of the two exchanged porcelain materials was dense, with well-dispersed small

69 .947) between the area fractions of retained porcelain measured in the present study and the oxide ad

70 elling support for the oxide layer theory of porcelain-metal bonding in dental alloy systems.

71 indered the elucidation of the mechanism for porcelain-metal bonding in dental systems, because a tes

72 test capable of detecting differences among porcelain-metal bonds of various qualities is required b

73 ce for the presence of an oxide layer at the porcelain-metal interface, provides compelling support f

74 onversion on porcelain thermal expansion and porcelain-metal thermal compatibility have been uncertai

75 Flat porcelain/metal or porcelain/ceramic structures were cem

76 Hereditary leukonychia (porcelain nails or white nails) is a rare nail disorder

77 cimens, were prepared from experimental body porcelain (No. 36, J.F. Jelenko & Co., Armonk, NY).

78 rcelain lower surface radial fracture, while porcelain on a higher-hardness palladium-silver alloy fr

79 Findings indicated that porcelain on a low-hardness gold-infiltrated alloy was v

80 posite extremes of elastic/plastic mismatch: porcelain on glass-infiltrated alumina ("soft/hard"); an

81 in the veneer layer, similar to that in the porcelain/palladium-silver system.

82 A dental porcelain powder was mixed with rubidium or cesium nitra

83 Controls were made of untreated Optec HSP porcelain powder, formed into bars and disks, and baked

84 Dental porcelains rely on the high-thermal-expansion mineral le

85 The functional surfaces of porcelain restorations are often ground to adjust occlus

86 flexural failure resistance of metal opaque-porcelain strips.

87 Existing dentures without porcelain teeth were modified for use as a surgical guid

88 Dental porcelains that are designed to be fused to PFM (porcela

89 results of this study indicate that even for porcelains that exhibit a measurable change in microcrac

90 The effects of this conversion on porcelain thermal expansion and porcelain-metal thermal

91 ure are a potential source of change in bulk porcelain thermal expansion during fabrication of porcel

92 would produce a detrimental lowering of the porcelain thermal expansion.

93 systems included chipping or fracture of the porcelain veneer initiating at the indentation site.

94 be predominantly chips and fractures in the porcelain veneer, from occlusally induced sliding contac

95 Porcelain-veneered alumina crown restorations often fail

96 ch, clinical long-term studies indicate that porcelain-veneered alumina or zirconia full-coverage cro

97 Porcelain-veneered crowns are widely used in modern dent

98 ed as a die for fabrication of zirconia core porcelain-veneered crowns.

99 ave a significant effect on the longevity of porcelain-veneered crowns.

100 Porcelain-veneered restorations often chip and fracture

101 nia is more than 4 times higher than that of porcelain-veneered zirconia and is at least as high as t

102 Plates of porcelain-veneered zirconia and monolithic zirconia serv

103 ng and fracture are common failure modes for porcelain-veneered zirconia dental restorations.

104 To test this hypothesis, we cemented flat porcelain-veneered zirconia plates onto dental composite

105 to veneer chipping and fracture relative to porcelain-veneered zirconia, while providing necessary e

106 were orders of magnitude longer than that of porcelain-veneered zirconia.

107 ations, whether monolithic (single layer) or porcelain-veneered, often chip and fracture from repeate

108 ure from chipping and/or delamination of the porcelain veneers.

109 fracture is the predominant fracture mode of porcelain veneers.

110 The porcelains were partitioned according to whether their m

111 ring (T) by blasting the surface of the body porcelain with compressed air.

112 the current study indicate that re-firing of porcelain with large surface flaws does not significantl

113 ciated with combinations containing the body porcelain with the smaller contraction coefficient.

114 ction of cracked particles compared with the porcelains with mean leucite particle diameters above Dc

115 The porcelains with mean leucite particle diameters below Dc

116 Fracture in the porcelain/zirconia system was limited to surface damage

117 e trilayer, post mortem damage evaluation of porcelain/zirconia/composite trilayers by a sectioning t