Abstract: A palladium-dominated dental alloy, in particular a ceramic-bonding dental alloy for the manufacture of dental prostheses such as crowns, bridges, inlays, or onlays, containing at least gold, palladium, and silver, as well as a grain-growth inhibitor in the form of ruthenium. In order to achieve a fine-grained separation without the formation of agglomerates to obtain a dental alloy with high mechanical stability and excellent polishing characteristics, it is proposed that the dental alloy contain—in addition to ruthenium as grain-growth inhibitor—at least one element of the group tantalum, niobium, yttrium, zirconium, chromium, and molybdenum as grain-refinement control element.

Abstract: A dental alloy with a high gold content that is devoid of palladium and copper. To achieve high mechanical stability, the dental alloy contains between 75 and 95 wt. % Au, between 5 and 20 wt. % Pt, between 0.5 and 3.5 wt. % Zn and/or Sn and/or In, between 0.1 and 0.8 wt. % of an element of a group I, in addition to a single particle refiner of a group II. The weight fraction of the element of group I is between 2 and 6 times that of the single particle refiner of group II, and one element of group I is represented by Nb or Ta or Ti or V and the particle refiner of group II is represented by Ir or Rh.

Abstract: A palladium-dominated dental alloy, in particular a ceramic-bonding dental alloy for the manufacture of dental prostheses such as crowns, bridges, inlays, or onlays, containing at least gold, palladium, and silver, as well as a grain-growth inhibitor in the form of ruthenium. In order to achieve a fine-grained separation without the formation of agglomerates to obtain a dental alloy with high mechanical stability and excellent polishing characteristics, it is proposed that the dental alloy contain—in addition to ruthenium as grain-growth inhibitor—at least one element of the group tantalum, niobium, yttrium, zirconium, chromium, and molybdenum as grain-refinement control element.

Abstract: The invention relates to the use of a cobalt-chromium alloy in the manufacture of a dental prosthesis. The alloy contains: 43-68% by weight cobalt, 12-30% by weight chromium, 8-25% by weight tungsten, 0-13% by weight iron, 0-30% by weight manganese, 0-10% by weight molybdenum, 0-5% by weight of at least one of the elements aluminum, tantalum, rhenium, titanium and less than 0.1% by weight carbon. A dental prosthesis with favorable workability and a low corrosion rate is obtained by manufacturing the dental prosthesis by means of a laser melting and/or sintering process.

Abstract: A dental alloy with a high gold content that is devoid of palladium and copper. To achieve high mechanical stability, the dental alloy contains between 75 and 95 wt. % Au, between 5 and 20 wt. % Pt, between 0.5 and 3.5 wt. % Zn and/or Sn and/or In, between 0.1 and 0.8 wt. % of an element of a group I, in addition to a single particle refiner of a group II. The weight fraction of the element of group I is between 2 and 6 times that of the single particle refiner of group II, and one element of group I is represented by Nb or Ta or Ti or V and the particle refiner of group II is represented by Ir or Rh.

Abstract: A method of producing a sintered, very high density dental prosthesis from a suspension containing noble-metal powder mixtures with bi or multimodal particle-size distribution and a mixing liquid. The suspension is molded to the desired shape and then the dental prosthesis is dried. The molded dental prosthesis is then heat-treated 5 to 45 minutes between 100.degree. and 400.degree. C., then heated with an average temperature elevation of 50 to 300 K/min. to 800.degree. C. and then brought to the sintering temperature T at 20 to 200 K/min. The sintering temperature T is between T.sub.solidus - 200) and T.sub.solidus - 70), whereby T.sub.solidus is the solidus temperature of the sintered alloy. The cooling-down of the dental prosthesis takes place under a vacuum or a protective gas.

Abstract: A denture with a metallic microstructure and with low shrinkage and porosity is produced by metallurgical sintering by providing a multimodal size distribution of coarse and fine fractions of metal powder, optionally also with glass or ceramic powder, converting this powder mixture with water into a slip, modelling the denture with this, and sintering the slip at a temperature which exceeds the solidus temperature of at least one component of the powder mixture.

Abstract: Low gold dental alloys, especially for firing on dental porcelains, should be easily worked, result in no discolorations and bubble formation in the firing, and have a physiologically replaceable hardness and a low melting interval. These properties are shown by alloys having 20 to 35 wt. % gold and 45 to 65 wt. % palladium if they also contain(a) 6 to 15 wt. % copper and 0 to 10 wt. % nickel,(b) 0 to 12 wt. % indium, 0 to 12 wt. % tin, and 0 to 4 wt. % gallium, with the proviso that the sum of the content of indium and tin added to two and one-half times the gallium content must give a value between 5 and 15 wt. %,(c) 0.1 to 1 wt. % iridium and/or rhenium and/or ruthenium, and(d) optionally 0 to 1 wt. % aluminum, 0 to 1 wt. % tantalum, 0 to 1 wt. % titanium and/or 0 to 5 wt. % silver.