HU200907B - Process for producing dental prothesis - Google Patents

Abstract

A dental prosthesis comprising a base of adurable corrosion-resistant metallic alloy and a harder external decorative layer consisting of at least one compound selected from the nitrides, oxynitrides, carboxynitrides, cyanonitrides, and monoxides of titanium and zirconium, and between the base and the external decorative layer, a protective layer of a metal more electro-negative than the material of the external decorative layer and capable fo being passivated in liquid media of the mouth cavity, the thicknesses of the protective layer, the external decorative layer, and the base being in the ratio of 0.3-1; 1:10-200.

Description

(57) EXTRAS

According to the invention, they are carried out on a purified replacement base

(a) galvanizing to form a protective layer of chromium, cobalt, nickel titanium, zirconium, tantalum or molybdenum on the surface of the replacement base having a thickness of 0,3 to 1: 10 to 200 relative to that of the replacement base; or

(b) applying a plasma technology to a protective layer of chromium, cobalt, nickel, titanium, zirconium, tantalum or molybdenum having a thickness of 0.3 to 1: 1 relative to that of the decorative layer and 0.3 to 1 relative to the thickness of the base. : 10-200, or

c) forming a transition layer of chromium, cobalt, nickel titanium, zirconium, tantalum or molybdenum on the surface of the replacement substrate or of the protective substrate with a protective layer according to a) or b) having a thickness of 0.3-1 to the decorative outer layer; 1 and 0.3 to 1:10 to 200, respectively, relative to the thickness of the replacement base, and then to the pre-treated dental base obtained in a), b) or c) to form a decorative outer layer in a known manner.

CM

Scope of the description: 16 pages, without figure

HU 200907 Β

The present invention relates to a process for the production of a dental prosthesis which comprises a solid, corrosion-resistant metal alloy base and a decorative outer layer, further comprising a protective layer and / or a transition layer.

Prosthetic prostheses of the monolithic type of metal, which are generally made of alloys of precious metals such as gold, platinum, palladium, or various stainless steels or alloys are known.

In the first case, metal dentures are largely inactive, highly decorative and have a cosmetic value. However, these dentures are not durable due to the low wear resistance of the precious metal alloys.

In the second case, precious metals can be saved and the durability of dentures can be guaranteed. However, dental prostheses made of stainless steels and alloys are less than the above in terms of their biologically inert behavior and aesthetic qualities.

Depending on the structural material used, the following non-removable dentures are distinguished:

- dentures made of porcelain and cermet,

- dentures made of precious metal-poor metal alloys,

- dental prostheses with a layered structure, when the precious metal is used only as the outer layer (coating) of the respective denture.

The production of metal ceramic structures is complicated, while porcelain crowns have a very decorative and aesthetic appearance, but they are only used mainly for the reconstruction of anterior teeth. However, due to the brittleness of the porcelain, they are not of sufficient strength.

In precious metal-poor alloys, it is not possible to reduce the precious metal content below 40-60% by weight without adversely affecting the biologically neutral behavior.

Solid dental prostheses with layered structure with favorable medical and biological properties are only worth producing if the use of precious metals is significantly reduced (80-95%) during production.

Currently, these types of dentures are not widely used because of their favorable therapeutic and biological properties and the decorative and aesthetic appearance of dentures only during the first 2-3 months of their use.

No. 1,215,485. A galvanically produced sandwich prosthesis construction is known from British Patent Specification No. 4,194,198. This is done by first making a layer of metal (gold, rhodium or chromium) that can be tolerated by the body's tissues, followed by a second, corrosion-resistant layer of noble wood (nickel), which is somewhat harder than the first layer, and a third a layer is made of metal (gold, rhodium or chromium) that can be tolerated by body tissues.

Further, it is known from U.S. Patent No. 212,442. According to the US patent, a prosthetic construction consists of a solid, corrosion-resistant metal alloy base (an alloy of silver and palladium) and a decorative outer layer. The outer layer is a gold-based alloy that is less solid than the base.

This denture makes it possible to reduce the consumption of precious metals by 90-95% by weight. However, since the precious metal layer in these replacements does not exceed 10-20 micrometers (for larger thicknesses, the layered construction of the prosthesis becomes meaningless due to the increased use of precious metal), the chewing surfaces exposed to intensive wear will rapidly wear out (two to three months). after use) which results in loss of decorative and cosmetic effects. The electrochemical reaction (20-60 mV change in the difference of electric potentials) and the formation of an active micro-galvanic element play an important role in the damage of the decorative outer layer of the denture. The latter may have local and general adverse effects on the human body. As a result, the foundation of the current denture is destroyed by the micro-galvanic element, which also accelerates the damage to the decorative outer layer.

SUMMARY OF THE INVENTION It is an object of the present invention to provide a dental prosthesis which does not contain precious metals, has a longer life than dental precursor monoliths, while preserving its medical, biological, decorative and cosmetic properties throughout its application; besides, it is easy to manufacture and not expensive.

The present invention relates to a method of making a dental filler with a decorative outer layer of chromium-nickel, chromium-cobalt or stainless steel with a solid outer layer formed of a nitride and / or nitride carbide and / or oxide nitride of titanium and / or zirconium. polished, followed by washing with detergent alcohol, optionally in an ultrasonic bath, followed by metal ionization, if desired, and a known plasma technique for applying a single or two layer decorative outer layer, whereby the metal or metals to be deposited are placed on appropriate plasma sources a negative voltage of up to 400 V is applied, the pressure of the gas or gas mixture used is set to 0.1-1 Pa, and a current of 60-120 A is drawn from the plasma source and and maintaining the arc until the thickness of the decorative layer is 1: 1-20 relative to the thickness of the replacement substrate, such that

the. forming chromium, cobalt, nickel, titanium, zirconium, tantalum or molybdenum protective layer by electroplating on the surface of the replacement panel in which the corresponding metal ion aqueous solution applied as an electrode placed in the replacement cover and then the áramsűiűséget between 10 A / cm ² -100 A / cm ² and continue galvanizing until the thickness of the protective layer is 0.3 to 1: 10 to 200 in relation to the thickness of the replacement base, or

b. using a plasma technique, a protective layer of chromium, cobalt, nickel, titanium, zirconium, tantalum or molybdenum is formed on the surface of the replacement substrate, whereby the metal or metals to be deposited are placed in the appropriate plasma sources; the gas or gas mixture used is pressurized to 1.5 x ^{10 4 to} 5, 5 x ^{10 3} , and the arc drawn from the plasma braid is drawn and maintained until the thickness of the protective layer relative to the thickness of the decorative outer layer is 0 To a ratio of 3-1: 1 or 0.3-1: 10-200 relative to the thickness of the replacement base, or

c. using a plasma technique to form a transition layer of chromium, cobalt, nickel, titanium, zirconium, tantalum or molybdenum on the replacement base or

the. or b. According to process the surface of the replacement plate to a protective layer, in which the felvivendő metal or metals are placed in a suitable plasma sources, the maximum coupled 400V negative bias to the target, the gas or the pressure of the gas mixture during the formation of the layer is 1.5x10 ^'4 -5,0x10' ³ Pa continuously from 0.01 to 1 Pa, while pulling a 60-120 A current arc from the plasma source, maintaining the thickness of the protective layer at a ratio of 0.3 to 1: 1 relative to the thickness of the decorative outer layer. , or 0.3-1: 10-200 in relation to the thickness of the replacement base, then a "b. or c. A pre-treated dental prosthesis base obtained by the method of the present invention is provided with a decorative outer layer as described in the subject matter.

In order to accomplish this task, the dental prosthesis produced by the process of the present invention is based on a solid stainless steel alloy coated with a decorative outer layer, which is made of a more solid material than the nitrides, hydroxide carbides, metals of the fourth column of the periodic table. nitrides, oxide nitrides and oxides thereof, or mixtures thereof, and wherein the ratio of the thickness of the decorative outer layer to the thickness of the base varies from 1:10 to 1: 200.

One of the basic types of dental prosthesis designed as described above is that there is a protective layer consisting of titanium, tantalum or chromium between the base and the decorative outer layer and the ratio of the protective layer thickness to the decorative outer layer (0.3-1): 1.

Another basic type of dental prosthesis produced by the process according to the invention is characterized in that a suitable intermediate layer consisting of titanium, tantalum or chromium is mixed with the appropriate outer layer between the base and the decorative outer layer, wherein the nitride concentration varies from 0.01 to 9099.9 % by weight and the ratio of the thickness of the transition layer to the thickness of the outer layer of decorative layer (0,03-1): 1.

The tooth replacement according to the present invention is based on a solid, corrosion-resistant material: stainless steel, chromium cobalt or lithium cobalt molybdenum alloys or any other conventional metal alloy. Such a foundation provides the necessary dental strength with varying sign loads when chewing foods. The base of the prosthesis can be made in one piece or made up of individual elements of the structure, whereby these elements are joined together by welding or soldering.

Nitrides, hydroxide nitrides, carbide nitrides, oxide nitrides, and / or oxides of the metals of the fourth column of the fourth column of the periodic table, which form the decorative outer layer of the denture according to the invention, exhibit very high chemical resistance to acidic, alkaline and neutral media. which are found in the oral cavity, are non-toxic and well-tolerated by the body's tissues. Therefore, dentures themselves are resistant to fluids in the oral cavity and are biologically inert.

Nitrides, hydroxide nitrides, carbide nitrides, oxide nitrides and / or oxides of titanium and / or zirconium are preferably used as the material of the decorative outer layer.

Because titanium and / or zirconium nitrides, hydroxynitrides, carbide nitrides, oxide nitrides and / or oxides cover a wide range of shades of gold, gold, gold, red and silver (depending on the type of chemical used and the process parameters) ), applied on a metallic surface, provide the products with the necessary decorative and cosmetic effects. Thus, depending on the nitrogen content, zirconium nitride shades range from silver to dark gold, that is, they are capable of imitating platinum or gold alloys. Titanium nitride, mixtures of titanium nitrides and zirconium nitrides, monooxides and hydroxynitrides of titanium and / or zirconium, can have a variety of shades and ranges of colors ranging from gold to golden yellow, thus expanding the range of shades that can be produced.

The hardness of the materials used to make the decorative outer layer of the tooth replacement according to the invention is 2.2x10 ⁴ -2.9x10 ⁴ MPa, which is much higher than the chimney of known metal alloys currently used in stomatology. As a result, the decorative outer layer of the prosthesis has a very high abrasion resistance (180-220 times greater, namely the abrasion resistance of the galvanic gold layer), which makes this prosthesis effective in resisting abrasion.

The increased brittleness of the decorative outer layer is a limiting condition for the thickness ratio of the base to the outer layer. The thinner the decorative outer layer, the less deformability it will have. However, excessive thinning may shorten the life of the denture due to rapid wear.

It has been experimentally determined that the thickness ratio of the decorative layer to the base of the prosthesis can vary from 1: 10-1: 200. For bridges and removable braces, the thickness of the decorative outer layer shall be calculated according to the thinnest cross-section of the denture structure.

The decorative outer layer of the prosthetic prosthesis can be single, double or multi-layer depending on the application. In the case of a multilayer decorative outer layer, the unitary layers may be of the metallic titanium and zirconium compounds given above. The multilayer structure of the decorative outer layer allows for a comprehensive change of adhesion properties to the base made of different materials, to improve the forming and abrasion resistance of the decorative outer layer and to expand the range of shades.

HU 200907 Β

Dental prostheses according to the invention may include the following products: various die-cast and cast crowns (solid casting crown, equatorial crown, half-crown, three-quarter crown, stud crown), dental bridged dental prostheses, soldered dental prostheses with dentures and self-tapping dental prostheses , and parts and arches of brace prostheses, and bent and molded braces.

Minor damage to the integrity of the decorative outer layer (occurrence of micropores or micro-cracks, local abrasions), which does not impair the decorative and cosmetic properties of the denture, leads to the formation of local micro-galvanic elements as the oral cavity penetrates between the base and decorative outer layer. .

As a consequence of the formation of micro-galvanic elements (in the absence of special measures), one of the metals with a significantly more negative electrical potential, namely the base of the denture, has a corrosion globe. This results in local damage to the foundation, or the weakening of the decorative base layer (without foundation) due to mechanical effects, which eventually diminishes the decorative nature of the denture and loses its cosmetic value.

In order to enhance the corrosion protection of the material on which the dental prosthesis is made according to the invention, a protective layer is formed between the denture base and the decorative outer layer which has a metal material which is electrically more negative than that of the decorative outer layer. passives in its medium.

In the presence of the aforementioned protective layer, the liquid media of the oral cavity, when the integrity of the decorative outer layer is damaged, cannot reach the base of the denture but only the material of the protective layer. A micro-galvanic element is formed between the metals of the protective layer and the decorative outer layer. In this element, the anode plays the role of an electrically negative metal, i.e. the metal of the protective layer. However, the metal of the barrier layer must be selected so that it passes satisfactorily under the conditions of anode polarization. Due to the difference in electrical potential of the metals in contact with each other in the region of damage of the decorative outer layer, the anode polarization always results in passivation of the protective layer (passive thin film). The protective layer, which has a passive thin layer, prevents further deterioration (dissolution) of the metal material of this layer, whereby the corrosion process is terminated. This ensures the corrosion resistance of the denture according to the invention.

Titanium, tantalum and chromium can be used as the protective layer metal. These metals are easily passivated in the oral cavity media, which avoids corrosion of the protective layer or damage to the underlying denture base.

In order to protect the metal alloy on which the denture is based reliably against corrosion, the protective layer must be dense (without pores). As the probability of passing through pores decreases with increasing layer thickness, the protective layer should be made as thick as possible. However, increasing the iron4 membership of the protective layer increases the work required to form it. From the latter point of view, the layer should be as thin as possible. It has been found experimentally that the thickness ratio of the protective layer to the decorative outer layer should preferably be varied between (0.3: 1) and (1: 1). Lower values should be chosen for tantalum and titanium, higher values for chromium.

The physical-mechanical properties (thermal, linear expansion coefficient, ductility, micro-hardness, etc.) of the base and the décorative outer layer and the protective layer and the decorative outer layer are very different (multiple).

In the event of temperature changes or mechanical loads, eg. Concentrated mechanical stresses occur along the boundaries of the abovementioned layers when using dentures. In many cases, this leads to the exterior of the decorative outer layer. In order to avoid the above phenomenon in the case of dental prosthesis produced by the process according to the invention, an intermediate layer consisting of a mixture of titanium, tantalum and chromium and the corresponding nitride is optionally formed between the base layer and the decorative outer layer. The concentration of the above nitrides increases along the thickness of the transition layer towards the decorative outer layer from 0.01% to 90-99.9% by weight, while the ratio of the thickness of the transition layer to the decorative outer layer (0.3: 1). : 1.

Due to the above distribution of metals and nitrides in the transition layer, the physical-mechanical properties in this layer gradually change. The properties of the transition layer vary in thickness from the characteristics of the base to those of the decorative outer layer.

In the practice of dental surgery, bridgehead replacements are used quite often to form a soldered base structure for a dental prosthesis. Elements of such a structure (crowns, bevels, dentures) are produced separately and then formed by welding to form a single structure.

It is not necessary to use silver plating metals to weld elements of prosthetic structures made of stainless steel, chromium cobalt and other conventional corrosion resistant metal alloys. The most common silver-cadmium solder metals with a melting point of 620-660 ° C (composition by weight: Ag 45, Cu 25, Cd 15 and Mn 15) and a stag zinc solder with a melting point of 800-850 ° C (composition by weight) in Ag 63, Cu 27, Zn 10, or Ag 37, Cu 38, Zn 15, Cd 0.5, Mn 5.2, Ni 4, Mg 0.3).

At the soldering sites, the decorative outer layer, which is usually formed at 400-500 ° C and above, has low adhesion due to the evaporation of some of the solder metal components. This very often causes the decorative outer layer to peel off and gaps, pores and other defects at the soldering points.

Therefore, it is advisable to apply an additional layer between the decorative outer layer and the replacement base, and optionally the applied intermediate layer and the replacement base, when the base of a stainless steel alloy tooth base consists of soldered elements. The additional layer is preferably cobalt, nickel, chromium, molybdenum or zirconium or chromium or molybdenum nitride.

EN 200907 Β and the additional layer is made of cobalt, nickel, chromium, molybdenum or zirconium. In both cases, the thickness of the additional layer is proportional to (0.5-1) to 1 for the thickness of the decorative layer. If the ratio of the thickness of the auxiliary layer to the thickness of the decorative layer ranges from (0.5: 1) to (1: 1), the auxiliary layer does not contain through pores. The pore-free auxiliary layer provides a reasonably reliable barrier, not only against the liquid of the current solder metal, but also against its vapor-forming components. It is not worth increasing the thickness of the additional layer as it only increases the cost of production.

An additional layer formed in the solder structure of a replacement base allows the integrity of the soldering seam to be maintained, eliminates visible pores at the soldering sites and, consequently, provides high mechanical strength for such prostheses, as well as providing a high quality decorative layer including solder seam range.

In the process of manufacturing such a prosthesis, which aims to use a base formed by a solid, corrosion-resistant metal alloy soldering of the replacement members and an outer decorative layer to be applied by vacuum technology, the solder joining zones of the above structure and the entire outer structure galvanized or vacuum coated with an additional layer of cobalt, nickel, chromium, molybdenum or zirconium or nitrides of chromium or molybdenum, wherein the ratio of the thickness of the above layer to the thickness of the outer decorative layer (0.5-1): 1.

As described above, the auxiliary layer eliminates the possibility of defects in the decorative outer layer of the solder seams and increases the mechanical strength of the solder joints.

The dental prostheses produced by the process of the present invention, in their decorative and cosmetic properties, their chemical-neutral behavior, their chemical resistance and their resistance to corrosion, are not less than the monolithic dental prostheses made of gold-platinum alloys and their superior strength and abrasion resistance. Dentures made by the process of the present invention are 10-15 times cheaper than the types made of gold alloy, cartilage and metal ceramics.

The prosthesis with a decorative outer layer produced by the process of the invention is resistant to common salt and oral cavity secretions, and is neutral in the cultures of blue-pyogenic bacteria, thrips of the human staphylococcus, coli, the fibroblasts of human embryos, digestible types of cells and cells of a human buccal epithelial tissue.

Nor does the decorative outer layer of the dentures produced by the method of the invention cause chromosome aberration.

The process according to the invention is based on the following technologically simple, known technological processes.

In order to carry out the process according to the invention, the dental base is first prepared from solid, corrosion-resistant noble metal alloys (stainless steel, cobalt and chromium, and cobalt, chromium and molybdenum alloys) according to methods commonly used in dentistry (precision casting, punching). . Check the accuracy of placement in the patient's oral cavity. After the test and the fitting, the rag on the surface of the respective mold is removed and the surface polished to a fineness of 0.1-0.4 micrometre R _z . Thereafter, the base of the supplement is washed according to standard technology and degreased in an ultrasound bath.

The protective layer is formed by applying known methods (electroplating, vacuum plasma technology), whereby a layer of titanium, tantalum or chromium is applied to the surface of the denture base before applying further layers, so that the pressure is 1.5x10 It is maintained between ⁴ and 5, with an oxoO ³ Pa value.

In order to reduce the mechanical stress on the interface between the replacement base and the decorative outer layer or the decorative outer layer and the protective layer, a transition layer may also be provided. The transition layer is e.g. known processes in vacuum plasma technology are developed by increasing the nitrogen pressure to 1.5 Pa x ⁴ O 5 to 5 Pa O ² during the construction of this layer.

Then, according to a technique known in the vacuum technology, a decorative outer layer of a specified thickness is applied from a material which provides adherence and abrasion resistance to the coating, as well as the appropriate color tone and tone. As mentioned earlier, the decorative outer layer can be single-, double- or multi-layer. When applying two or more layers, the composition and pressure of the reacting gas, the material to be vaporized, and the technological parameters required to form the layers are varied depending upon the task being solved.

Thereafter, the decorative outer layer of the respective denture is polished as needed and, if necessary, the missing components are formed from plastics for replacement.

For a better understanding of the present invention, the following examples are provided, of which the first eight and the last 24 are provided as comparative examples and illustrate the prior art, while the following examples illustrate possible embodiments of the invention.

Example I

The denture is formed as a monolithic bridge-like structure, with a base of a chromium-cobalt alloy with an outer decorative layer of titanium nitride.

Following the wax model, the desired shape of the replacement base is cast from a chromium-cobalt alloy. The accuracy of this fit is examined in the patient's oral cavity and inserted precisely. The fitted replacement pad is polished with a fine dispersion (0.5-1 micrometer) abrasive. After polishing, the replacement base is thoroughly washed in an ultrasonic bath with 2-3% by weight of hot water (70-80 ° C) containing synthetic detergent. This is followed by washing in running water, petrol baths and degreasing with ethyl alcohol.

HU 200907 Β

The base of the bridge-type prosthesis is then placed in a vacuum chamber with a rotating device, the drum of which is fitted with a replacement base. The chamber is also provided with three sources of titanium plasma, which are directed to the drum of a rotating device. Chemically pure titanium is used as a vaporizer in all three plasma sources.

The vacuum chamber is evacuated to a pressure of 1 x 10 ³ Pa, the rotating device is turned on (9 rpm), a 1.1 kV magnifying voltage is applied to the base and one of the plasma sources is generated, generating an 80 A current. In three minutes, the base is completely cleaned, during which the surface is bombarded with titanium ions.

Then, a negative voltage of 180 V is applied to the base and the second and third plasma sources are switched on. The arc current of each of the three sources is 90 A. Under these conditions, nitrogen is introduced into the chamber while the chamber pressure is adjusted to 6.6 x 10 * Pa. Meanwhile, the decorative outer layer of titanium nitride is formed on the base. When the thickness of this layer reaches 8 micrometers, the plasma sources are switched off, the nitrogen inlet and the rotating device are stopped, the negative voltage is disconnected from the replacement, and after 10 minutes, they are removed from the chamber.

The decorative outer layer has a micro hardness of ^2.5 x ^{10 4} x 2.6 x ^{10 4} MPa and corresponds to a high value gold alloy with good adhesion to the base.

The resulting denture was fixed with Visphat cement in a patient's oral cavity. No negative effects, either local or general, were observed during the four-year follow-up. The replacement was not damaged or discolored.

Example 2

The tooth replacement is made of a monolithic, bridge-like structure, the base material is chrome-cobalt alloy, titanium hydroxide nitride decorative outer layer.

The denture base is prepared as described in Example 1, polished, and washed.

The processing of the replacement base until the nitrogen is introduced into the vacuum chamber is the same as described in Example 1.

However, instead of nitrogen, a mixture of nitrogen-oxygen (80% by volume nitrogen, 20% by volume oxygen) is introduced into the vacuum chamber while the pressure in the chamber is adjusted to 6.6 x 10 * Pa. Meanwhile, a layer of titanium hydroxide nitride is formed on the surface of the base (decorative outer layer). When the thickness of this layer reaches 10 micrometers, the plasma source is disconnected from the negative voltage supply to the above gas mixture, and the rotating device is disconnected. After 10 minutes, the replacement can be removed from the chamber.

The decorative outer layer thus formed has a micro hardness of 2.3 x ^{10 4} MPa and corresponds to a good adherence of its high-value gold alloy to the base. The resulting denture is fixed in the patient's oral cavity with Visphat cement. Observations over two years show no local or general negative effects on the body. The replacement has hardly changed.

Example 3

The prosthesis to be produced is a monolithic, bridge-like structure based on a chromium-cobalt alloy with a zirconium nitride decorative outer layer.

The denture base was prepared as described in Example 1, polished and washed, and then placed in a vacuum chamber.

The vacuum chamber is provided with three plasma sources containing zirconium as the material to be evaporated.

Ion purification by zirconium ion bombardment and application of the decorative outer layer was carried out as described in Example 1. The layer to be produced is 20 micrometres thick.

The micro-hardness of the produced layer is 2.5x10 ⁴ MPa, its color shade corresponds to a high-value gold alloy, the adhesion to the base is good.

The resulting denture is fixed in the patient's oral cavity with Visphat cement. During the four-year observations, no local or general negative effects on the human body were observed.

Example 4

The tooth replacement is a monolithic, bridge-like structure based on chromium-cobalt alloy with a decorative outer layer of titanium or zirconium nitrides (70% by weight titanium nitride and 30% by weight zirconium nitride).

The denture base is prepared, polished, washed and placed in a vacuum chamber as described in Example 1.

The vacuum chamber has three plasma sources, one of which is the evaporator zirconium and the other two titanium. Ionic purification is carried out as described in Example 1.

Then, a negative voltage of 200 V is applied to the substrate, and the titanium and zirconium plasma sources are started to operate, where the arc currents of the titanium plasma sources are 90 A, the zirconium plasma source is 80 A. The nitrogen is then introduced into the vacuum chamber. the pressure is adjusted to 6.6 x 10 Pa. The surface of the base forms a decorative outer layer consisting of a mixture of titanium nitride and zirconium nitride (70% by weight titanium nitride and 30% by weight zirconium nitride). When the thickness of the layer reaches 12 micrometers, the plasma sources are switched off, the nitrogen inlet is completed, the turning equipment is stopped, the voltage is removed from the denture, and after 10 minutes the replacement can be removed from the chamber.

The decorative outer layer has a micro hardness of 2.6x1ο ⁴ MPa and a high-quality gold alloy with good adhesion to the base.

The resulting denture is fixed in the patient's oral cavity with Visphat cement. During the four-year observations, no local or general adverse effects on the human body were observed. Zirconium and titanium were not detected in patients' secretions. The replacement color did not change.

Example 5

The prosthesis to be manufactured is a bridge-like, monolithic structure based on a chromium-cobalt alloy with a decorative outer layer consisting of a mixture of titanium and zirconium nitrides (0.1% by weight zirconium nitride and 99.9% by weight titanium nitride).

Preparation, Polishing, Washing, and Vacuuming of Denture Foundation in Example 1

EN 200907 Β. The vacuum chamber has three plasma sources containing an alloy consisting of 99.9% by weight of titanium and 0.1% by weight of zirconium as the substance to be evaporated.

The decorative outer layer is applied as described in Example 1 until a thickness of 15 micrometers is formed. The resulting film has a micro hardness of 2.5 x ^{10 4} MPa, a color equivalent to a high-value gold alloy, and good adhesion to the base.

The manufacturer's denture is anchored in the patient's oral cavity with Visphat cement. Observations over four years did not reveal any local or general negative effects on the human body. The replacement color has not changed.

Example 6

The prosthesis to be manufactured is a monolithic, bridge-like structure based on a chromium-cobalt alloy decorative outer layer consisting of two layers consisting of a mixture of titanium and zirconium carbide nitrides (67% by weight titanium carbide nitride and 33% by weight) zirconium carbide nitride) and the second layer is titanium nitride.

The replacement base is prepared, polished, washed and placed in a vacuum chamber as described in Example 1. The vacuum chamber has three plasma sources, one of which contains zirconium as the material to be evaporated and the other two contains titanium. The base is ionically purified as described in Example 1.

Then, apply a negative voltage of 200 V to the substrate, switch on the titanium and zirconium plasma sources, and set the arc current to 90 A for each of the three sources. Subsequently, a mixture of nitrogen, oxygen and methane (80% by volume nitrogen, 10% by volume oxygen and 10% by volume methane) is introduced into the vacuum chamber and the pressure in the chamber is adjusted to 1.3 x ¹⁰ Pa. Meanwhile, a first layer of decorative outer layer consisting of a mixture of titanium and zirconium carboxide nitrides (67% by weight of titanium carboxide and 33% by weight of zirconium carboxitride) is deposited on the base surface.

When the thickness of this layer reaches 6 micrometers, the source of the zirconium plasma is disconnected, the feed of the above gas mixture is discontinued, and only nitrogen is introduced and the pressure in the chamber is adjusted to ¹⁰⁰ psi. Meanwhile, the second layer of the decorative outer layer consisting of titanium nitride is peeled off.

When the thickness of the titanium nitride layer reaches 3 micrometers, the plasma source is disconnected, nitrogen is discontinued, negative voltage is removed from the denture, and the rotating device is stopped. After 10 minutes, the replacement can be removed from the chamber.

The decorative outer layer produced has a micro hardness of 2.6 x ^{10 4} MPa, a color corresponding to a high value gold alloy, and good adhesion to the base.

The resulting denture is fixed in the patient's oral cavity with Visphat cement. During the two-year follow-up, there were no detectable local, generally negative effects on the patient's body. The replacement color did not change.

Example 7

The prosthesis to be manufactured is a monolithic, bridge-like structure based on a chromium-cobalt alloy with a decorative outer layer consisting of two layers, the material of which bordering the base is titanium carbide nitride and the second layer is titanium oxide nitride.

The replacement pad was prepared as described in Example 1, polished and washed, and then placed in a vacuum chamber.

The replacement base is worked up as described in Example 1 until the nitrogen is introduced into the vacuum chamber.

Instead of nitrogen, a mixture of nitrogen and acetyl is introduced into the vacuum chamber (95% by weight of nitrogen and 5% by weight of acetylene) where the pressure in the chamber is adjusted to Ι, ΟόχΙΟ ¹ Pa. Meanwhile, titanium carbide nitride is formed on the surface of the base. After forming a 5 micrometer layer, the mixture was quenched and the mixture was started to introduce a mixture of nitrogen and oxygen (90% by volume and 10% by volume of oxygen) while adjusting the pressure in the chamber to 8 x 10 ^-1. -nitride layer separates. When the titanium oxide nitride layer reaches a thickness of 5 micrometers, the plasma source is disconnected, the gas mixture is discontinued, the negative voltage from the denture is switched off, and the turning device is stopped. After 10 minutes, the replacement can be removed from the chamber.

The decorative outer layer produced has a micro hardness of 2.4x10 ⁴ MPa and corresponds to a high-grade gold alloy with good adhesion to the base.

The resulting denture is fixed in the patient's oral cavity with Visphat cement. During the two-year follow-up, no local or general adverse effects on the patient's body were detected. The replacement color did not change.

Example 8

The foam to be produced is a monolithic, bridge-like structure based on chromium-cobalt alloy, with a two-layer decorative outer layer, the latter bonded to the base and consisting of titanium monoxide and the material of the second layer being titanium nitride.

The replacement base is prepared, polished, washed and placed in a vacuum chamber as described in Example 1.

The processing of the replacement base until the nitrogen is introduced into the vacuum chamber is the same as described in Example 1.

Instead of nitrogen, oxygen is introduced into the vacuum chamber while the pressure is adjusted to ⁶ psi. Meanwhile, a layer of titanium monoxide is deposited on the base surface. When the thickness of this layer reaches 5 micrometers, the oxygen supply is completed and the nitrogen supply is begun while the pressure in the chamber is adjusted to ¹⁰ x ¹⁰ Pa and the titanium nitride layer is peeled off. When the titanium nitride layer reaches a thickness of 5 micrometers, the plasma sources are switched off, the nitrogen inlet is stopped, the negative voltage is disconnected from the replacement, and the rotating device is stopped. After 10 minutes, the replacement can be removed from the chamber.

The decorative outer layer produced has a micro hardness of 2.5 x ^{10 4} MPa and a color equivalent to a high value 7

EN 200907 Β Adhesion of gold alloy with replacement base good ·

The resulting denture is anchored in the patient's oral cavity with Visphat cement. During the two-year follow-up, no local or general negative effects on the patient's body could be detected.

Example 9

The prosthesis to be produced is a monolithic, bridge-like structure based on a decorative outer layer consisting of a mixture of chromium-cobalt alloy and titanium zirconium nitride (33% by weight zirconium nitride and 67% by weight titanium nitride) and a titanium protective layer.

The replacement base is prepared, polished, washed and placed in a vacuum chamber as described in Example 1. The ionic purification of the prosthesis base is carried out by titanium ion bombardment as described in Example 1.

Subsequently, a negative voltage of 200 V is applied to the replacement base, the second titanium plasma source is turned on, having an arc current of 80 A, and a 3 micrometer titanium protective layer is formed. The third zirconium plasma source is then switched on while adjusting the arc current of each of the three plasma sources to 90 A and introducing nitrogen into the chamber while adjusting its pressure to 6.6 x 10 Pa. The decorative outer layer is formed by separating a mixture of titanium and zirconium nitride. When the thickness of this layer reaches 10 micrometers, the plasma sources are switched off, the gas supply is stopped, the negative voltage is disconnected from the replacement, and the rotator is stopped.

The technical and medical characteristics of the denture are the same as those of Example 4.

Example 10

The prosthesis to be made is a separate crown of stainless steel with a titanium nitride decorative outer layer and a tantalum protective layer.

A cylindrical hollow body of stainless steel is heated to a temperature of 800-900 ° C and the shape of the crown is used to form the body to be molded. The molded body is then annealed at high temperature, followed by a check of the latter's fitting accuracy on the respective tooth, followed by positioning according to the position of the teeth at the bite on the opposite tooth. The crown is then removed by immersion in a solution (g / l) of sulfuric acid 100, nitric acid 150, folic acid 30. The mold is kept in this solution until complete removal of the crust (20-60 s). The crown is then washed with running water, dried and polished with a fine dispersion (0.5-1 micrometer) abrasive. The replacement base was washed in an ultrasonic bath with hot water (70-80 ° C) containing 3% by weight of synthetic detergent followed by petrol and ethyl alcohol. The replacement base is then fixed. It is fixed in the vacuum apparatus chamber, on the rotating apparatus drum. The vacuum chamber has three plasma sources, one of which contains tantalum as the substance to be evaporated and the other two contains titanium.

The vacuum chamber is vented to 1.3 x 10 < ³ &^gt;

A negative voltage of V is applied, the tantalum plasma source is actuated while the arc current is set to 200 A.

Ion purification is accomplished by tantalum bombardment of the replacement base for two minutes. Thereafter, 50

Apply a negative voltage of V to the replacement base and create a tantalum protective layer. When the thickness of the protective layer reaches 3 micrometers, turn on the and titanium plasma source while adjusting the arc current to 90 A each, turn off the tantalum plasma source and apply a negative voltage of 180 V to the replacement base, and pressurize nitrogen into the chamber It is adjusted to 6.6 x 10 'Pa, whereby the decorative outer layer of titanium nitride is peeled off. When the thickness of this layer reaches 9 micrometers, the plasma sources are turned off and the rotating device is stopped. After 10 minutes, the replacement can be removed from the chamber.

The manufactured denture has a micro hardness of 2.5x10 ⁴ MPa, a color corresponding to a large gold alloy, and a very good abrasion resistance (190 times the gold alloy).

The resulting denture is fixed in the patient's oral cavity with Visphat cement. During the four-year follow-up, there were no local or general adverse effects on the patient's body. The replacement color did not change.

Example 11

The dental prosthesis to be manufactured is a soldered bridge-type structure based on stainless-chromium-nickel steel with silver-cadmium solder, a chromium barrier and a mixture of titanium and zirconium nitride (0.5 wt% zirconium nitride and 99.5 wt% titanium). nitride) with a decorative outer layer.

The crown shape of the bridge-like replacement is prepared as described in Example 10. Subsequently, the middle part of the prosthesis (the bevel and the dentures) is cast on the basis of a wax model and silver-cadmium soldered soldering is used to create a uniform basic structure of the bridge type replacement. The grater is then removed and then polished and washed as described in Example 10.

Subsequently, the foundation is immersed in a galvanic bath to apply the chromium barrier.

The aqueous electrolyte used is a g / l chromium bath of chromic anhydride 250 and sulfuric acid 2.5. The galvanic layer is deposited at an electrolyte temperature of 60 ° C and a current density of 50 A / dm ² . Under the above conditions, a chromium barrier layer of 8 micrometer thickness is deposited.

Subsequently, the protective coating base is polished with a fine dispersion diamond paste, washed in an ultrasonic bath, with hot water, 3% w / w synthetic water, gasoline and ethyl alcohol.

In the next step, the replacement base is placed in a vacuum chamber on the drum of the rotating device. The vacuum chamber has three plasma sources containing a mixture of titanium and zirconium (0.5 wt% zirconium and 99.5 wt% titanium) as the material to be evaporated. Cleaning the replacement base is titanium and

EN 200907 Β zirconium ion bombardment, and the application of an 8 micrometer thick decorative coating from a mixture of titanium and zirconium nitride was performed as described in Example 1.

The denture produced has the same technical and medical characteristics as the type described in Example 5.

Example 12

The prosthesis to be produced is a monolithic, bridge-like structure based on a chromium-cobalt alloy with a titanium oxide nitride decorative outer layer and a transition layer consisting of a mixture of titanium and titanium nitride. The replacement base is prepared, polished, washed and placed in a vacuum chamber as described in Example 1. The vacuum chamber has three plasma sources containing titanium as the substance to be evaporated.

Ion purification of the replacement base is performed as described in Example 1.

Subsequently, 200 V negative voltage is placed on the replacement page, then switch on the two additional plasma source having íváramerősségét individually adjusted to 80 erőségűre, nitrogen is fed into the chamber while keeping the pressure gradually, l, 3xl0 ^"3 braised-l, 3xl0 ² Pa increasing over a time period of 6 micrometers of transition layer total separation. The titanium nitride content in the transition layer increases from 0.1% to 90% by weight.

When the transition layer has a thickness of 6 micrometers, the nitrogen inlet is stopped and a mixture of nitrogen and oxygen (85% by volume and 15% by volume of oxygen) is introduced while the pressure is adjusted to 6.6 x 10 "Pa. A decorative outer layer of 25 microns is then formed. The technical and medical characteristics of the dental prosthesis thus produced are as given in Example 2.

Example 13

The prosthesis to be produced is a monolithic, bridge-like structure based on a chromium-cobalt alloy and a decorative outer layer made of a mixture of titanium and zirconium nitride (50% by weight titanium nitride and 50% by weight zirconium nitride), a transition layer made of a mixture of tantalum nitride.

The replacement base is prepared, polished, washed and placed in a vacuum chamber as described in Example 1.

The vacuum chamber has three plasma sources, of which tantalum, titanium and zirconium are the vaporizable material. Ionic purification is performed as described in Example 10.

Subsequently, a negative voltage of 100 V is applied to the replacement base and nitrogen is introduced into the chamber while gradually increasing its pressure from 1.3 x 10 ³ Pa to 1.0 x 10 10 Pa over the course of the 4 micrometer thick transition layer. The tantalum nitride content of the transition layer increases from 0.01% to 90% by weight of the total layer thickness. When the transition layer reaches a thickness of 4 micrometers, the titanium and zirconium plasma sources are switched on, while the arc currents are 90

Set to, stop the tantalum plasma source, and apply a negative voltage of 250 V to the replacement base. Nitrogen is then introduced into the chamber while the pressure is adjusted to 5.3 x 10 Pa and the decorative outer layer consisting of a mixture of titanium and zirconium nitride is deposited. When the thickness of this layer reaches 9 micrometers, the plasma sources are switched off, the nitrogen inlet is stopped, the negative voltage from the denture is turned off, and the rotating device is stopped. After 10 minutes, the replacement can be removed from the chamber.

The dental prosthesis thus produced has the technical and medical characteristics of the type described in Example 6.

Example 14

The prosthesis to be manufactured is a soldered bridge-type structure based on stainless steel and silver-zinc solder with a decorative outer layer of titanium nitride and a transition layer of a mixture of chromium and chromium nitride.

The replacement base is prepared and molten as described in Example 11. The replacement base is then placed in a vacuum chamber on the drum of the rotating device. The vacuum chamber has three plasma sources, one of which contains chromium as the substance to be evaporated and titanium as the other two.

The vacuum chamber is evacuated to a pressure of 1.3 x ^{10 3} Pa, the rotary device is turned on, a negative voltage of 700 V is applied to the replacement base and the ion purification is performed for 4 minutes.

A negative voltage of 30 V is then applied to the replacement base, 90 A arc current set by plasma spinning, and nitrogen is introduced into the chamber. Nitrogen pressure is gradually increased from 1.3 x ^{10 3} Pa to 3.9 x 10 ² Pa over the entire deposition time of the 4 micrometer thick transition layer. The concentration of chromium nitride in the thickness of the transition layer increases from 0.01% to 90% by weight. This layer increases to 2,6x10 ⁴ MPa micro hardness 4x1ο ⁴ MPa. When the thickness of the transition layer reaches 4 micrometers, the two titanium plasma braids are turned on, each with an arc current of 90 A, a negative voltage of 180 V applied to the replacement bases, and the chromium plasma source disconnected. Nitrogen was then introduced into the chamber at a pressure of 6 x 10 10 Pa and a 10 micrometer decorative outer layer of titanium nitride was deposited. When this layer reaches a thickness of 10 micrometers, the plasma sources are switched off, the nitrogen supply is stopped, the voltage is disconnected from the replacement, and the rotation device is stopped.

The technical and medical characteristics of the denture thus obtained correspond to those of the type shown in Example 1.

Example 15

The dental prosthesis to be produced is a bridged, bridge-like structure based on stainless-chrome-nickel steel and silver-zinc, with a decorative outer layer of zirconium nitride, a transition layer of a mixture of chromium and chromium nitride and a protective layer of chromium.

The preparation of the replacement base was carried out as described in Example 11, as was the washing.

The replacement base is then placed in a vacuum chamber on the drum of the rotating device. The vacuum9

EN 200907 Β has three plasma sources, one containing chromium as a vaporizer and the other two containing zirconium. Ion purification of the replacement base is performed as described in Example 14.

Subsequently, a negative voltage of 30 V is applied to the substrate, an arc current of 90 A is applied to the plasma source, and the 4 micrometer thick chromium protective layer is peeled off. After reaching the required thickness for the protective layer, the transition layer is peeled off as described in Example 14. The decorative outer layer is deposited as described in Example 14, except that the only material to be evaporated is zirconium.

The decorative outer layer produced has a micro hardness of 2.5 x ^{10 4} MPa and corresponds to a high-value gold alloy where the individual layers are bonded to each other and to the base with favorable adhesive properties.

The prepared replacement is fixed in the patient's oral cavity with Visphat cement. During the four-year follow-up, no local or general negative effects on the patient's body could be detected.

Example 16

The prosthesis to be produced is a monolithic, bridge-like structure based on a chromium-cobalt alloy with a decorative outer layer consisting of a layer of titanium carbide nitride and a titanium oxynitride, with a transition layer of a mixture of titanium and titanium nitride and a protective layer of titanium.

The replacement base is prepared, polished and placed in a vacuum chamber as described in Example 1. The vacuum chamber has three plasma sources containing titanium as the substance to be evaporated. Ion purification of the replacement base is performed as described in Example 1. Subsequently, a negative voltage of 180 A is applied to the replacement base, the other two plasma sources are switched on, each set at 80 A, and the protective layer of 6 micrometer thickness is removed. Subsequently, a transition layer consisting of a mixture of titanium and titanium nitride was separated, as seen in Example 12, except that the pressure of nitrogen was increased to 9.3 x 10 ² Pa. This increases the titanium nitride content to 99% by weight on the surface adjacent to the decorative outer layer. When the transition layer reaches 6 micrometers, stop the introduction of nitrogen, adjust the plasma source arc current to 90 A, and add a mixture of nitrogen, methane, and oxygen (85% nitrogen, 10% oxygen and 5% methane) to the chamber. ), the pressure in the chamber is adjusted to 2.6 x 1ο · ¹ Pa, and the first layer of the decorative outer layer is separated from the titanium carbide nitride. When the thickness of this layer reaches 3 micrometers, stopping the mixture gas introduction, and start a gas mixture consisting of nitrogen and oxygen (90 vol% nitrogen + 10% oxygen) introduction, while the pressure of this mixture was adjusted 6,6x1ο ¹ Pa, and is separated a second layer of the decorative outer layer consisting of titanium hydroxide nitride. When the thickness of this layer reaches 3 micrometers, the plasma sources are switched off, the gas mixture introduction is stopped, the negative voltage from the denture is switched off and the rotation stop is stopped. After 10 minutes, the replacement is removed from the chamber.

The manufactured denture has a micro hardness of 2.5x1ο ⁴ MPa, good adhesion between the individual layers and the base, and the color corresponds to a high-value gold alloy.

The resulting denture is fixed in the patient's oral cavity with Visphat cement. Observations over two years did not reveal any local or general adverse effects on the patient's body. The replacement color did not change.

Example 17

The prosthesis to be manufactured is a soldered, bridge-like construction with a base made of stainless chromium-nickel steel with silver-cadmium solder, consisting of a mixture of titanium and zirconium nitride (67% by weight titanium nitride and 33% by weight zirconium nitride) contains a protective layer of cobalt.

Making and washing the replacement base all. example. Subsequently, the replacement base is immersed in a galvanic bath to apply a protective cobalt layer. To apply the layer from an aqueous solution, the following composition (g / l) is used: cobalt sulfate 500, sodium chloride 17 and boric acid 45. The cobalt layer is deposited at a current density of 3 A / cm ² , an electrolyte temperature of 45 ° C and a pH of 4. . The protective cobalt layer is peeled off at a thickness of 8 micrometers. Subsequently, the base with a protective cobalt layer is polished with fine dispersion pastes. The replacement pad is then washed and placed in a vacuum chamber as described in Example 1.

The decorative protective layer is then peeled off as described in Example 9 until it is 25 microns thick. When the thickness of the decorative outer layer reaches 25 micrometers, the peeling process is completed as described in Example 9.

The technical and medical characteristics of the denture produced are the same as those of Example 4.

Example 18

The prosthesis to be manufactured is a soldered, bridge-like structure based on a stainless chromium-nickel steel silver-cadmium solder with a decorative outer layer of titanium oxide nitride and a protective molybdenum layer.

Making and washing the replacement base all. example. The base is then placed in a vacuum chamber on a drum of a rotating apparatus. The vacuum chamber has three plasma braids, of which one is molybdenum and one is titanium as the substance to be evaporated. The vacuum chamber is vented to a pressure of 2.6 x 10 ³ Pa, the rotator is turned on, a negative voltage of 600 V is applied to the base, the molybdenum plasma source is turned on, the arc current is adjusted to 130 A and ionic purification of the replacement base is performed.

Subsequently, a negative voltage of 25 V is applied to the substrate and the protective molybdenum layer is separated.

Then turn on the titanium plasma sources, which are set to an arc current of 90 A, turn off the molybdenum plasma source, and then apply a negative voltage of 200 V to the base with the protective molybdenum layer.

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HU 200907 Β

Consisting of nitrogen and oxygen in the chamber gas mixture (80 vol% nitrogen and 20 térfoogat% oxygen) is introduced, where the pressure was set 6,6xl0 ^_1 Pa értéékre, and the formation of 15 micrometers in thickness, of titanium oxynitride decorative outer layer. The technical and medical characteristics of the denture are the same as those of Example 2.

Example 19

The dental prosthesis to be manufactured is a soldered, bridge-like structure based on stainless chromium-nickel steel and silver-cadmium solder, consisting of a mixture of titanium and zirconium nitride (30% by weight titanium nitride + 70% by weight zirconium nitride) a protective layer of zirconium is present.

Removing, polishing and washing the replacement pad a

Example 11. The base is then placed in a vacuum chamber on a drum of a rotating apparatus. The vacuum chamber has three plasma sources, one of which is titanium, the other two zirconium is the substance to be evaporated. The vacuum chamber is vented to a pressure of 1.3x10 ³ Pa, the rotating device is switched on, a negative voltage of 900 V is applied, the base is switched on, and the zirconium plasma source is turned on, and the arc current is set to 80 A. Ion purification of the replacement base by zirconium ion bombardment for 3 minutes.

Subsequently, a negative voltage of 50 V is applied to the substrate, the second zirconium plasma source is switched on while its amperage is set to 80 A, and the protective zirconium layer is deposited at a thickness of 3 micrometers. Subsequently, the decorative outer layer consisting of a mixture of titanium and zirconium nitride is peeled off.

The technical and medical characteristics of the denture follow those of Example 6.

Example 20

The prosthesis to be produced is a soldered, bridge-like structure based on stainless chromium-nickel steel and silver-cadmium solder on which a decorative zirconium nitride outer layer and a molybdenum nitride intermediate layer are placed.

The replacement base is prepared, polished and washed as described in Example 11. The base is then placed in a vacuum chamber on a drum of a turning apparatus. The vacuum chamber has 3 plasma sources, one of which contains molybdenum, the other two contains zirconium as the substance to be evaporated. Subsequently, the vacuum chamber is vented to a pressure of 1 x ³ x ¹⁰ Pa, the rotary device is turned on, a negative voltage of 600 V is applied to the base, and the molybdenum plasma source is turned on and the arc current is set to 130 A. The ionic cleaning of the base takes 3 minutes with molybdenum bombardment.

Subsequently, a negative voltage of 25 V is applied to the substrate, nitrogen is introduced into the chamber, the pressure is adjusted to 1.06 x 10 " Pa, and the transition molybdenum nitride layer is deposited at a thickness of 5 micrometers. When the thickness of the transition layer reaches 5 micrometers, the zirconium plasma sources are turned on, the arc current is set to 90 A each, the molybdenum plasma source is turned off, a negative voltage of 200 V is applied to the base, and nitrogen is introduced into the chamber. Set to 3x10 '' Pa. Meanwhile, a 15 micrometer thick zirconium nitride decorative layer is deposited.

The decorative outer layer produced has a micro hardness of 2.5x1ο ⁴ MPa, a color corresponding to a high-value gold alloy, and good adhesion.

The resulting denture is fixed in a patient's oral cavity with Visphat cement. The three-year follow-up showed no local and general negative effects on the patient's body, and the color of the replacement did not change. During the period mentioned above, no soldering or black discoloration was observed at the soldering points.

Example 21

The prosthesis to be repaired is a soldered bridge-type structure with a base made of stainless chromium-nickel steel with silver-zirconium solder having a decorative outer layer of titanium nitride, a transition layer of a mixture of chromium and chromium nitride, and a protective layer of nickel.

The replacement base is prepared, polished and washed as described in Example 11. Subsequently, the substitution base is immersed in a galvanic plaster to apply the additional nickel layer. The composition of the aqueous solution (g / l) for the application of the layer is as follows: Nickel Sulfate 300, Magnesium Sulfate 50, Sodium Chloride 10 and Boric Acid 30. The application is 40 ° C electrolyte temperature, 3 A / dm ² current density and pH 4 , At 0. After applying the protective layer at 4 micrometer thickness, the denture is washed with running water and polished. The replacement base is then placed in a vacuum chamber on a rotating drum. The vacuum chamber has three plasma sources, one of which contains chromium and the other two contains titanium as a vaporizer. Subsequently, a transition layer consisting of a mixture of chromium and chromium nitride having a thickness of 5 micrometers was deposited as described in Example 14. This is followed by peeling off the decorative outer layer of titanium nitride, 8 microns thick. Finish the unmounting

This is done as described in Example 1. After 10 minutes, the replacement can be removed from the chamber.

The technical and medical characteristics of the denture produced are the same as those described in Example 1.

Example 22

The dental prosthesis to be manufactured is a soldered, bridge-like structure based on a stainless chromium-nickel steel silver-cadmium phosphor with a two-layer decorative outer layer, the base of which is based on a mixture of titanium and zirconium carbide nitride (% by weight) and 33% by weight zirconium nitride), while the second layer is a mixture of titanium and zirconium nitrides (67% by weight titanium nitride and 33% by weight zirconium nitride), and the substitution has a protective chromium layer and a Ti + TiN transition layer.

The replacement base is prepared and washed as described in Example 11. Subsequently, the fund shall be subject to Article 5

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EN 200907 Β micrometer thickness protective chromium all. Immersed in a galvanic bath as described in Example 1b. The replacement pad with the protective layer is polished, washed and placed in a vacuum chamber as described in Example 11. The vacuum chamber has three plasma sources, one of which contains zirconium and two further titanium as vaporizers. The ionic cleaning of the base on the chromium-plated surface is carried out by zirconium ion bombardment as described in Example 6.

Subsequently, a transition layer consisting of a mixture of titanium and titanium nitride is separated as described in Example 12. Then, apply a 220V negative voltage to the base, turn on the plasma sources, and adjust the 90A arc current in each of the three plasma sources. A gas mixture of nitrogen and acetylene (90% by volume nitrogen and 10% by volume 5 acetylene) was introduced into the vacuum chamber, and a first 9 micrometer layer of the decorative outer layer was deposited. After reaching the required thickness, the gas mixture is stopped, the nitrogen is introduced into the chamber, pressurized to 6.6 x 10 Pa, and the second layer of the decorative outer layer, consisting of a mixture of titanium and zirconium nitride, having a thickness of 4 micrometers.

The technical and medical characteristics of the dental prosthesis produced are the same as those described in Example 7.

Example 23

The prosthesis to be manufactured is a soldered, bridge-like structure based on a stainless-chromium-nickel steel silver-cadmium solder with a two-layer decorative outer layer consisting of a mixture of titanium and zirconium monoxides (33% by weight cationium oxide and 67% by weight titanium oxide). oxide), and the second layer is a mixture of titanium and zirconium monoxide nitrides (33% by weight titanium monoxide nitride and 67% by weight zirconium monoxide nitride), with a replacement layer of chromium nitride.

Making and washing the replacement base all. example. The base is then placed in a vacuum chamber on a drum of a turning apparatus. The vacuum chamber has four plasma sources, the first containing chromium, the second titanium, and the third and larger zirconium as vaporizers. The vacuum chamber is vented to a pressure of 2.6 x ^{10 3} , the rotary device is turned on, a negative voltage of 700 V is applied to the base, and the chromium plasma source is turned on and the arc current is set to 80 A. Ion purification is carried out by chromium ion bombardment for 4 minutes.

Subsequently, a negative voltage of 30 V is applied to the base, nitrogen is introduced into the chamber while the pressure is adjusted to ⁶ x 10 ² Pa and the final chromium nitride layer is separated at a thickness of 4 micrometers. When the thickness of the transition layer reaches the specified value, the two zirconium plasma sources are turned on, while their arc current is set to 90 A, the chromium plasma source is turned off and a 200 V negative voltage is applied to the base with the transition chromium nitride layer. The introduction of nitrogen into the chamber is then completed and the oxy12 gene is introduced at a pressure of 3.9 x 10 ² , and the first layer of the decorative outer layer consisting of a mixture of titanium and zirconium oxide (33% by weight titanium and 67% by weight zirconium monoxide) is removed. 4 micrometers thick. Subsequently, the oxygen supply is stopped and a nitrogen / oxygen gas mixture (82% by volume nitrogen and 18% by volume oxygen) is drawn in while the pressure in the chamber is adjusted to 6,6 x 10 Pa and the decorative outer layer is removed by titanium zirconium monoxide. a second layer of a mixture of its nitrides with a thickness of 6 micrometers.

The decorative outer layer produced has a micro hardness of 2.2 x ^{10 4} MPa, good adhesion to the transition layer and a color corresponding to a high-value gold alloy.

The resulting denture is fixed in the patient's oral cavity with Visphat cement. Observations over two years have not shown any local or general negative effect on the patient's body.

The integrity of the replacement is not impaired, color is not variable.

Example 24

The prosthesis to be produced is a monolithic, bridge-like structure based on chromium-cobalt alloy with a three-layer decorative outer layer, of which the base material is titanium carbide nitride, the second is titanium oxynitride and the third is titanium nitride.

The replacement base is prepared, polished, washed and placed in a vacuum chamber as described in Example 1. The vacuum chamber has three plasma sources made of titanium to be evaporated. The base is ionically purified by titanium ion bombardment as described in Example 1.

Subsequently, a 220 V negative voltage is applied to the base, the plasma sources are turned on and the power is set to 90 A. Subsequently, a mixture of nitrogen and acetylene (90% by volume nitrogen and 10% by volume acetylene) was introduced into the chamber and the pressure was adjusted to 6.6 x 10 ² Pa and the first outer layer of the decorative outer layer, titanium carbide nitride, was deposited at a thickness of 4 micrometers. Subsequently, the supply of gas mixture is completed and the mixture of nitrogen and oxygen (82% by volume nitrogen and 18% by volume oxygen) is introduced into the chamber while the chamber pressure is adjusted to 1.3 x 10 < Pa > a second layer of hydroxynitride in a thickness of 4 micrometers.

Subsequently, the introduction of the above gas mixture is completed and the introduction of the mitrogen at 6.6 x 10 Pa and the third layer of titanium nitride on the outer layer of the decorative layer is separated by a thickness of 5 micrometers.

The decorative outer layer produced has a micro hardness of 2.5x1ο ⁴ MPa, very good adhesion to the base and a color corresponding to a high-value gold alloy.

The resulting denture is fixed in the oral cavity of the patient. Observations over two years have not shown any local or general negative impact on the patient's body. The replacement color did not change. No damage to the integrity of the layer could be detected.

Most of the structural variations of the dentures of the present invention are of sufficient degree and depth

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EN 200907 Β biomedical studies that went beyond clinical trials.

The investigations were basically conducted in the following main directions:

1. Hygiene-chemical studies on particle migration of dental prosthesis metals in model fluids.

2. Studies on the effect of the materials of each layer and their particular composition on the micro-organisms and microflora of the oral cavity and on the development of living tissue culture.

3. Histological and histochemical examinations of body tissue reactions in the vicinity of the coated implant to be examined.

4. Examination of the animal's body after implantation: - state of general reactivity,

- body mass dynamics,

- the amount of histamine in the blood,

- the vitamin C content of the blood,

- resistance to functional loads,

- central nervous system status,

- liver and kidney function.

5. Histological and histochemical examination of internal organs (liver, kidney, spleen, heart, adrenal glands).

6. Clinical examination of denture replacement constructs according to the invention.

In most structural versions of the dentures of the present invention, the research program carried out has been completely closed with positive results. For other structural types, the program is in the finalization stage with favorable prospects.

Patent Claim Point

Claims (1)

CLAIMS 1. A method of making a dental prosthesis with a solid outer layer of chromium-nickel, chromium-cobalt or stainless steel, with a decorative outer layer of a titanium and / or zirconium nitride and / or nitride carbide and / or oxide nitride. polished, then washed with detergent alcohol, optionally in an ultrasonic bath, and optionally metal ionization, and using a known plasma technology to apply one or two layers of decorative outer layer, by placing the metal or metals to be deposited in the appropriate plasma sources. a negative voltage of 400 V maximum is applied to the target, the pressure of the gas or gas mixture used is set at 0.1 to 1 Pa, and a current of 60-120 A is drawn from the plasma source and the arc is held for above, while the thickness of the decorative layer reaches a ratio of 1: 1-20 relative to the thickness of the replacement base, characterized in that the. By galvanizing, a protective layer of chromium, cobalt, nickel, titanium, zirconium, tantalum, or molybdenum is formed on the surface of the replacement base by applying the replacement base as an electrode to an aqueous solution of the corresponding metal ion and a current density of 10A / cm ² to 100A / cm ² . and continue galvanizing until the thickness of the barrier layer is 0.3-1: 10-200 in relation to the thickness of the pore base, or b. using a plasma technique, a protective layer of chromium, cobalt, nickel, titanium, zirconium, tantalum or molybdenum is formed on the surface of the replacement base by placing the metal or metals to be deposited in the appropriate plasma sources, applying a negative voltage of 400 V or 1.5 x ^{10 4 to} -5.0 x ^{10 3} Pa, an arc current of 60-120 A is drawn from the plasma source and the arc is maintained until the protective layer thickness is 0.3-1: 1 relative to the thickness of the decorative outer layer. or 0.3 to 1:10 to 200-200 of the thickness of the replacement base, or c. using a plasma technique to form a transition layer of chromium, cobalt, nickel, titanium, zirconium, tantalum or molybdenum on the replacement base or the. or b. According to process the surface of the replacement plate to a protective layer, in which the felvivendő metal or metals are placed in a suitable plasma sources, the maximum coupled 400V negative bias on the target pressure of the form set out in the gas or gas mixture during formation of the layer L between 5xl0 ^"4 5,0xl0 ^'3 Pa continuously changing from 0.01 to 1 Pa while pulling the plasma current source from 60 to 120 A and maintaining the barrier thickness at a ratio of 0.3 to 1: 1 relative to the thickness of the decorative outer layer, or 0.3-1: 10-200 in relation to the thickness of the replacement base, then a., b. or c. Pretreated dental prosthesis obtained by the method of the present invention is decortative in the manner described herein