KR101439512B1 - manufacturing method of antibacterial alloy for dental prosthesis - Google Patents

Abstract

The present invention relates to a manufacturing method of alloy materials for dental prosthesis having antibacterial activity and, more specifically, to a manufacturing method of alloy materials for dental prosthesis having excellent abrasion resistance and corrosion resistance and having ability of preventing oral cavity from various diseases due to excellent antibacterial activity and biocompatibility as silver or magnesium is mixed in titanium or zirconium. A manufacturing method of alloy materials for dental prosthesis of the present invention comprises a first arc dissolving step for manufacturing a metal briquette in which a first metal and a second metal are combined while creating arc and dissolving the arc after putting the first metal of one selected among titanium (Ti) and zirconium (Zr) and the second metal having antibacterial activity into a vacuum melting furnace; an electrode manufacturing step for manufacturing a bar-shaped consumable electrode having a size of 20 mm in diameter, 700 to 800 mm in length after preparing several metal briquettes and butt-welding; and a second arc dissolving step for manufacturing alloy materials by creating arc after installing the consumable electrode in the vacuum melting furnace and dissolving the consumable electrode.

Description

BACKGROUND OF THE INVENTION 1. Field of the Invention [0001] The present invention relates to a method for manufacturing an antibacterial alloy for dental prosthesis,

More particularly, the present invention relates to a method for producing an alloy material for dental prosthesis having an antibacterial activity, and more particularly, to a method for manufacturing an alloy material for dental prosthesis having antimicrobial activity, wherein titanium or zirconium is mixed with silver or magnesium to have excellent antimicrobial activity, To a method of manufacturing an alloy material for dental prosthesis excellent in corrosion resistance.

In general, a normal person has 16 teeth in the maxilla (maxilla) and 16 teeth in the mandible (total 16 teeth). In total, 32 teeth are generated in the infants. .

As described above, one or more teeth may be damaged due to various oral diseases (tooth decay or periodontal disease, etc.) after the formation of the device, and in this case, it is impossible to smoothly perform pronunciation or food crushing, Which often hinders normal social life.

As a method for restoring or treating the damaged tooth as described above, denture through a dental prosthesis is applied to restore masticatory function, aesthetic restoration, and normal pronunciation.

As described above, the types of prostheses through dentures include general prosthetic teeth that cover teeth weakened by excessive tooth decay or neurological treatment or restoration of areas where teeth have been lost, and tooth decay, shape abnormality, A tooth is placed on the damaged part of the tooth so as to avoid the inconvenience caused by the removal of the healthy teeth on both sides or the use of the denture for restoration of the tooth on the lost part, Implant prosthesis.

Titanium having the appropriate mechanical strength, biocompatibility, excellent corrosion resistance and excellent osseointegration ability as the prosthetic material is most widely used as a dental implant. Alumina, hydroxyapatite (HA) and zirconia ceramics have been studied as substitutes for titanium.

Among these materials, zirconia is a generic term for zirconium oxide (ZrO ₂ ), which shows chemical stability and volume stability. It has a polymorphic structure that inhibits the progress of cracks due to volume expansion due to the transformation mechanism during phase transition, It has strength and fracture toughness, does not cause toxic reaction when inserted into human body, and has excellent resistance to corrosion and abrasion.

There have been various attempts to impart antimicrobial properties to the above-mentioned materials for prosthesis. One known technique is coating a metal such as silver, which has been proved to have antibacterial activity, on a prosthetic material.

Korean Patent Publication No. 2004-0035636 discloses a dental antimicrobial prosthesis. The above-described conventional technique is to coat an outer surface of a dental prosthesis with nano-sliver or fluorine to form an antibacterial layer on the outer surface of the dental prosthesis so as to suppress or kill the activity of harmful microorganisms in the oral cavity The present invention relates to a dental antimicrobial prosthesis.

However, the conventional art has a problem that when the prosthesis is mechanically abraded in the oral cavity, the coating layer of nanosilver is easily broken when the nano silver is simply coated on the outer surface of the prosthesis.

A dry thin film coating process such as a PVD (Physical Vapor Deposition) process is a promising method for solving the problem of the wet plating process. The dry thin film coating process can be largely divided into PVD method and CVD method. The CVD method has a problem that the process temperature is higher than 1200 ° C., the process control is difficult, and the precursor production is difficult. On the other hand, the PVD process is an eco-friendly process with no emission of pollutants and has excellent adhesion and abrasion resistance.

In order to coat the metal on the surface of the prosthesis using the PVD method, a cathode, that is, a target, which is a supply source of a metal substance, is required.

The present invention has been made to overcome the above problems, and it is an object of the present invention to provide a dental prosthesis such as a dental prosthesis such as an implant or a denture orthodontic appliance, which is used as a target for coating by PVD method so as to form a coating film excellent in antibacterial activity and durability The present invention has been made in view of the above problems.

In order to accomplish the above object, the present invention provides a method for manufacturing a dental prosthetic alloy material having antimicrobial activity, comprising the steps of: forming a first metal selected from titanium (Ti) and zirconium (Zr) A first arc melting step of charging a vacuum melting furnace and generating and dissolving an arc to produce a metal single beam mixed with the first and second metals; Preparing a plurality of the metal single beams and then welding them together to produce a rod-shaped consumable electrode having a diameter of 20 mm and a length of 700 to 800 mm; And a second arc dissolving step of disposing the consumable electrode in a vacuum melting furnace and generating an arc to dissolve the consumable electrode to produce an alloy material.

And the second metal is one selected from the group consisting of silver (Ag) and magnesium (Mg).

Wherein the alloy material is composed of 88 to 95% by weight of the first metal and 5 to 12% by weight of the second metal.

As described above, the present invention can provide an alloy material in which silver or magnesium having antibacterial activity is mixed with titanium or zirconium. By using this alloy material as a target and forming a coating film on the surface of dental prosthesis such as implants or orthodontic appliance by PVD method, it is possible to precisely control the content of silver or magnesium contained in the coating film .

In addition, since alloy materials are based on high-strength titanium or zirconium, coating films formed from these alloy materials have excellent durability and wear resistance.

1 is a photograph showing the result of an antibacterial experiment,
Fig. 2 is a photograph showing a measurement site when calculating the size of the clear zone.

Hereinafter, a method for producing a dental prosthetic alloy material having antibacterial activity according to a preferred embodiment of the present invention will be described in detail.

The present invention provides alloy materials based on titanium or zirconium. The alloy material produced by the present invention provides an alloy material in which two kinds of metals are mixed. That is, the alloy material is a mixture of the first metal and the second metal.

The first metal is any one selected from titanium (Ti) and zirconium (Zr). And the second metal is one selected from silver (Ag) and magnesium (Mg). The second metal imparts an antimicrobial activity to the alloy material.

The alloy material in which the first metal and the second metal are mixed is Ti-Ag or Ti-Mg alloy based on titanium, or Zr-Ag or Zr-Mg alloy based on zirconium. These alloy materials are based on titanium or zirconium, so they have excellent hardness and strength.

The alloy material produced by the present invention is composed of 88 to 95% by weight of the first metal and 5 to 12% by weight of the second metal. If the content of the second metal is more than 12% by weight, it may cause toxicity in vivo. If the content of the second metal is less than 5% by weight, the antibacterial effect is insignificant.

The metal composition of the coating film formed on the surface of the prosthesis is determined by the composition ratio of each metal of the alloy material.

In the present invention, the production of the alloy material is made by vacuum melting the first metal and the second metal. The vacuum arc melting method can be applied as a vacuum melting method. In the vacuum arc melting method, a metal to be melted is charged into a vacuum melting furnace and an arc is generated in a vacuum or inert gas atmosphere to melt the metal in the vacuum melting furnace.

The vacuum arc melting method is divided into a consumable electrode method in which the electrode itself of the metal material installed in the vacuum melting furnace is melted and a non-consumable electrode method in which a separate metal material is melted in the vacuum melting furnace.

The present invention applies a first arc dissolution step using a non-consumable electrode method and a second arc dissolution step using a second consumable electrode method for the production of an alloy material.

A method of manufacturing an alloy material for dental prosthesis according to an embodiment of the present invention includes charging a first metal and a second metal into a vacuum melting furnace and generating an arc to dissolve the metal to dissolve the first and second metals, An electrode manufacturing step of preparing a rod-shaped consumable electrode having a diameter of 20 mm and a length of 700 to 800 mm by preparing a plurality of metal single rays and then welding them together; And a second arc melting step of generating an arc to dissolve the consumable electrode to produce an alloy material. The present invention will be described in detail in each step.

1. First arc melting step

First, in the first arc melting step, the first metal and the second metal are dissolved to produce a metal single beam mixed with two kinds of metals.

A first metal selected from titanium and zirconium and a second metal selected from silver or magnesium are charged into a vacuum melting furnace equipped with a non-consumable electrode, and an arc is generated.

The vacuum arc melting apparatus for performing the first arc melting step may be a conventional one. For example, a mold having a hemispherical groove is provided in a vacuum melting furnace, and a rod-shaped non-consumable electrode (tungsten material) is disposed on the upper side of the mold. An arc is generated by the electrode, and the metal material located in the mold is melted by the generated arc.

The metal charged in the vacuum melting furnace is the first and second metals. The first and second metals are charged into a vacuum furnace in the form of a briquette having a purity of at least 99.9%. The content ratio of the first and second metals charged in the vacuum melting furnace is adjusted to 0.88 to 0.95: 0.05 to 0.12. An arc is generated and the melted first and second metals flow into the center of the mold and are mixed.

When the melted metal is cooled, a metal single crystal mixed with the first metal: the second metal at a weight ratio of 0.88-0.95: 0.05-0.12 is produced. The size of the single-metal light is approximately 20 mm in diameter and 200 mm in length.

2. Electrode Fabrication Step

Next, a consumable electrode to be used in the second arc melting step is produced. For this purpose, a plurality of rod-shaped metal single beams are prepared and then welded to each other to produce a long stick-shaped consumable electrode. The consumable electrode has a diameter of 20 mm and a length of 700 to 800 mm.

3. Second arc melting step

Next, a second arc melting step is performed in which a consumable electrode is installed in a vacuum melting furnace, and an arc is generated to dissolve the consumable electrode to produce an alloy material.

The second arc melting step is a consumable electrode type vacuum arc melting process. The vacuum arc melting apparatus for performing the second arc melting step may be a conventional one. For example, the vacuum melting furnace has a mold formed with hemispherical grooves in the inside thereof, and a consumable electrode is provided on the upper side of the mold. When an arc is generated, the consumable electrode is melted, and the molten molten metal is moved to a mold to produce an ingot-shaped alloy material.

As described above, the alloy material manufactured according to one embodiment of the present invention is used as a target material for forming a coating film on the surface of a dental prosthesis by the PVD method.

In addition, the alloy material produced according to the present invention can be used as a material for dental prosthesis manufacturing. That is, the dental prosthesis itself can be manufactured using the alloy material produced according to the present invention. In this case, since prosthesis itself contains silver or magnesium, it is not necessary to form a separate coating film on the surface of the prosthesis.

<Antibacterial activity test>

In order to evaluate the antibacterial activity of the Ti-Ag alloy material prepared according to one embodiment of the present invention, the following experiment was conducted.

1. Preparation of specimens

The test specimens were classified into a control group using titanium metal of 99.9% purity and a test group using titanium and silver mixed alloy. In the test group, five kinds were prepared by varying the mixing ratio of silver to 3 wt%, 5 wt%, 7 wt%, 10 wt% and 12 wt%.

A total of six specimens were processed into disks of 15 mm in diameter and 3 mm in height. All specimens were ultrasonically cleaned in ethanol for 20 minutes and sterilized by autoclave (121 ° C / 20min).

The types of the specimens are shown in Table 1 below.

division Components of the specimen Control group Ti (99.9%)

Test group

Ti-3Ag Ti (97%) - Ag (3%) Ti-5Ag Ti (95%) - Ag (5%) Ti-7Ag Ti (93%) - Ag (7%) Ti-10Ag Ti (90%) - Ag (10%) Ti-12Ag Ti (88%) - Ag (12%)

2. Experimental Method

Streptococcus mutans, which induces cavities in the oral cavity as a published strain, mutans ) KCTC3065. The deep freezers were kept frozen and used for the experiment.

Brain Heart Infusion (BHI, Difco, CA) containing 10% (v / v) horse blood serum (Oxide, Italy) supplemented with Streptococcus Mutans were diluted to 0.5 McFarland turbidity (1.6x10 ⁸ cells / ml), 100 ㎕ inoculated and spread. Then, the prepared specimen was placed on BHI medium and anaerobically cultured in a 37 ° C incubator for 18 hours.

3. Experimental Results

The size of the clear zone formed around the specimen after incubation for 18 hours is shown in Fig. Table 2 shows the size of the clear zone. The size of the clear zone was calculated by averaging the four values shown in FIG.

Clear Zone Control group
(Reference) Ti-3Ag Ti-5Ag Ti-7Ag Ti-10Ag Ti-12Ag ① - - 1.8 2.8 1.2 2.9 ② - - - 2.5 3.0 2.8 ③ - - 1.0 3.0 3.0 3.0 ④ - - 2.5 2.8 1.5 3.0 Average - - 1.325 2.775 2.175 2.925

Referring to Table 2 and FIG. 1, no clear zone was formed in Ti-3Ag among the control and experimental groups, but clear zones were formed in Ti-5Ag to Ti-12Ag. It is expected that the alloy material having the silver content of 5 ~ 12 wt% will have excellent antimicrobial activity.

While the present invention has been particularly shown and described with reference to exemplary embodiments thereof, it is to be clearly understood that the same is by way of illustration and example only and is not to be taken by way of limitation. Accordingly, the true scope of protection of the present invention should be determined only by the appended claims.

The present invention can be utilized as an alloy material for dental prosthesis having an excellent antibacterial activity.

By using this alloy material as a target, it is possible to form a coating film having excellent durability and wear resistance on the surface of a dental prosthesis such as an implant or a orthodontic appliance by the PVD method.

In addition, the dental prosthesis itself can be manufactured from the alloy material produced according to the present invention.

Claims (3)

delete A first metal selected from titanium (Ti) and zirconium (Zr) and a second metal having antibacterial activity are charged into a vacuum melting furnace equipped with a non-consumable electrode made of tungsten, and arc is generated and dissolved, And a second arc melting step of producing a rod-shaped metal single beam mixed with the second metal;
Preparing a plurality of the metal single beams and then welding them together to produce a rod-shaped consumable electrode having a diameter of 20 mm and a length of 700 to 800 mm;
And a second arc dissolving step of disposing the consumable electrode in a vacuum melting furnace and generating an arc to dissolve the consumable electrode to produce a target alloy material,
Wherein the second metal is one selected from silver (Ag) and magnesium (Mg). 3. The method according to claim 2, wherein the alloy material comprises 88 to 95% by weight of the first metal and 5 to 12% by weight of the second metal.

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