JP5990083B2 - Manufacturing method of dental medical equipment - Google Patents

Description

The present invention relates to a process for the production of dental equipment.

For intraoral treatment such as caries treatment and inspection, for example, mirror, tweezers, extractor, explorer, cutting turbine, broach, reamer, file, extraction forceps, Hebel, sharp blade, scalpel, dental treatment electric engine, Various dental medical devices such as a dental treatment motor, a handpiece, a dental air scaler, and a dental laser handpiece are used. Since these dental medical devices are used in contact with the skin itself in the mouth, and are usually used repeatedly, cleaning, sterilization and the like are performed thoroughly after each use. As this treatment, for example, boil sterilization, autoclave sterilization, dry heat sterilization, ethylene oxide gas sterilization, ultraviolet sterilization, sterilization with other chemicals, and the like are performed after a cleaning treatment using ultrasonic waves or the like. As described above, the dentistry device is subjected to careful sterilization and the like, but from the viewpoint of improving work efficiency, a dentistry device that can be sterilized simply while maintaining the sterilization performance is required. Yes.

Under such circumstances, dental root canal treatment instruments having a resin handle containing an antibacterial agent such as an oxide photocatalyst have been developed (see Patent Document 1). According to the dental root canal treatment instrument, since the antibacterial agent is contained in the resin handle, the antibacterial properties of the handle can be enhanced. However, this dental root canal treatment instrument contains antibacterial agents only in the handle, improving the bactericidal and antibacterial properties of the parts that are likely to actually work in the mouth and come into contact with the skin I can't let you.

In addition, in order to improve the anti-fogging property of the mirror, a dental mirror in which a surface layer containing photocatalytic titanium oxide particles is formed on the mirror base surface (see Patent Document 2), the friction property is increased, and the gripping performance is improved. In order to improve, a dental instrument (see Patent Document 3) in which ceramics are laminated on the working end surface has been developed. However, none of these improve the bactericidal properties of the intraoral work part (mirror or work end).

JP-A-10-309286 JP-A-9-224960 JP 2001-521579 A

This invention is made | formed based on such a situation, and it aims at providing the manufacturing method of the dental medical device which can simplify the sterilization treatment after use in an intraoral work part.

A dental medical device manufactured by the method for manufacturing a dental medical device according to the present invention that meets the above-described object includes a base and a mouth working part having a bactericidal function layer laminated on the surface of the base,
The sterilizing functional layer is formed by thermal spraying of particles containing a photocatalyst.

According to the dental instrument, because it has a sterilizing function layer formed by thermal spraying of particles in the mouth implement portion including a photocatalyst, or the like is irradiated with light after use, can perform some bactericidal, fungicidal Processing can be simplified. Furthermore, since the sterilization function layer is formed by thermal spraying, it has excellent adhesion to the base material and can improve wear resistance, and since it is formed in a porous shape, the exposed surface area of the photocatalyst is wide and high sterilization. Performance can be demonstrated.

In the dental medical device, the surface of the sterilizing functional layer is preferably polished, and the skewness (Rsk) of the roughness curve on the surface of the sterilizing functional layer is preferably less than zero. Since the surface of the bactericidal functional layer is polished as described above, it is possible to suppress a sense of incongruity when the intraoral work part comes into contact with the skin surface in the mouth, and to prevent the skin from being damaged. In addition, by making Rsk on the surface of the sterilizing functional layer less than 0, it is possible to reduce discomfort and damage to the skin when contacting the skin surface by reducing the crest portion, and by providing a certain amount of trough portion, the surface area And the catalytic function, that is, the sterilizing function can be effectively exhibited.

In the dental medical device, the photocatalyst preferably has visible light responsiveness. By using a photocatalyst having visible light responsiveness in this way, the sterilization treatment can be further simplified and made more efficient, and the adhesion and growth of bacteria during work can be suppressed.

In the dental medical device, the sterilizing functional layer may contain a metal having antibacterial properties. By doing in this way, the microbe removal ability in this sterilization functional layer can further be improved.

In the dental medical device, it is also preferable that the sterilizing functional layer includes a translucent resin filled in a gap between particles containing the photocatalyst while maintaining the exposed state of the photocatalyst. If there are many or large gaps, foreign matter may enter the gap, and the foreign matter may further adhere to the foreign matter that has entered, so that the surface of the sterilization function layer may be covered with foreign matter, resulting in a decrease in sterilization function. . Therefore, as described above, by filling the gap with a translucent resin, it is possible to suppress the intrusion of foreign matter and maintain the long-term maintenance performance of the catalyst function.

A method for manufacturing a dental medical device according to the present invention that meets the above-described object has a base material and a bactericidal function layer laminated on the surface of the base material, and makes a tip contact with a tooth to perform examination and removal of dirt. In a manufacturing method of a dental medical device comprising an intraoral work part to be performed and a grip part connected to a rear end surface of the intraoral work part,
A step of roughening the surface of the base material so that the arithmetic average roughness is 0.2 μm or more and 4 μm or less;
In the stirring tank, (1) anatase-type titanium dioxide particles having a primary particle diameter of 10 nm to 50 nm, and (2) iron, copper, chromium, or nickel with respect to 100 parts by mass of the titanium component in the titanium dioxide particles. A water-soluble metal complex or a water-soluble metal salt having a metal component amount of 0.05 to 0.5 parts by mass, (3) a granular antibacterial metal having a diameter of 0.5 to 10 μm, and (4 ) Supplying water and stirring to prepare a slurry in which titanium dioxide particles having a secondary particle diameter of 1 μm to 5 μm and the antibacterial metal are dispersed;
The slurry is placed on the surface of the base material disposed at the spray destination of the thermal spray frame by placing the slurry on the flow of the thermal spray frame having a flame temperature of 750 ° C. to 1500 ° C. and a flame ejection speed of 800 m / second to 2000 m / second. Colliding against and forming a layer on the surface of the substrate ;
Filling the gap between the layers with a translucent resin;
The translucent resin and polished the filled surface of the layer, and a step of obtaining the sterilizing functional layer skewness is less than 0 the roughness curve of the surface.

The manufacturing method of the dental medical device which concerns on this invention can form the bactericidal functional layer by which the surface was grind | polished by having said each process. Therefore, according to this manufacturing method, the dental medical device which can simplify the sterilization process after use in the intraoral work part can be obtained. In addition, according to the manufacturing method, since the surface is polished, the disinfection function layer is formed by thermal spraying, but there is a sense of incongruity or damage to the skin when contacting the skin surface in the mouth. A suppressed dental medical device can be obtained.

According to the dental medical device manufactured by the method according to the present invention, the sterilization treatment after use in the intraoral work part can be simplified. Moreover, according to the manufacturing method of the dental medical device which concerns on this invention, the dental medical device which can simplify the sterilization process after use in an intraoral work part in this way can be obtained.

It is a schematic diagram of the dental medical device which concerns on one embodiment of this invention. It is a typical fragmentary sectional view which shows the intraoral work part of the dental medical device. It is a schematic diagram of the high-speed thermal spraying apparatus used for the manufacturing method of the dental medical device.

Hereinafter, with reference to the drawings as needed, the dental medical device and the manufacturing method thereof according to the embodiment of the present invention will be described in detail.

<Dental medical equipment>
As shown in FIG. 1, a dental medical device 10 according to an embodiment of the present invention is a so-called explorer (probe), which is used for examination of the depth and size of the axilla, the presence or absence of dental pulp, and the removal of dirt. It is what is used. This dental medical device 10 includes an intraoral work part 11 and a grip part 12.

The intraoral work part 11 has a needle shape with a slightly curved tip side. The above-described examination and the like are performed by bringing the tip of the intraoral working portion 11 into contact with the teeth. The intraoral work portion 11 has a rear end side end face connected to the grip portion 12.

The intraoral work part 11 has a base material 13 and a sterilization function layer 14 as a cross-sectional structure as shown in FIG.

The base material 13 has a needle shape with a slightly curved tip side, that is, substantially the same shape as the intraoral work part 11. The material of the substrate 13 is not particularly limited, and examples thereof include resins, ceramics, metals, and the like, but metals are preferable from the viewpoint of durability and heat resistance. Examples of the metal include aluminum, zinc, magnesium, iron, and alloys thereof. Further, these metals may be plated on the surface.

The surface of the substrate 13 is preferably subjected to a roughening treatment. Thus, the roughening process is performed, whereby the adhesion of the sterilization function layer 14 formed by thermal spraying can be enhanced. This roughening treatment can be performed by a known method such as sandblasting. The arithmetic average roughness (Ra) of the surface of the substrate 13 is preferably 0.1 μm or more and 10 μm or less, and more preferably 0.2 μm or more and 4 μm or less. Here, the arithmetic average roughness (Ra) refers to a value measured with a cutoff value of 0.8 mm in accordance with JIS B0601: 2001.

The sterilizing function layer 14 is laminated on the surface of the base material 13. The sterilization function layer 14 is formed by thermal spraying of particles containing a photocatalyst, as will be described in detail later. Since the dental medical device 10 has the bactericidal function layer 14 formed by spraying particles containing a photocatalyst on the surface of the mouth working portion 11 as described above, it can be sterilized to some extent by irradiating light after use. And sterilization can be simplified. Furthermore, since the sterilization function layer 14 is formed by thermal spraying, it has excellent adhesion to the base material 13 and can improve wear resistance, and since it is formed in a porous shape, the exposed surface area of the photocatalyst is wide. High sterilization performance can be exhibited.

The sterilization function layer 14 covers substantially the entire surface of the base material 13, but the sterilization function layer 14 is not laminated and the base material 13 is exposed, for example, at the forefront of the intraoral work portion 11. You may do it.

As the particles containing a photocatalyst, (1) particles composed of only a photocatalyst (hereinafter also referred to as “photocatalyst particles”), (2) a photocatalyst particle carrying a sensitizer, etc. (3) particles composed of mixed particles of photocatalyst particles and other particles not containing photocatalyst, (4) particles composed of photocatalyst and other compounds, and other particles not containing photocatalyst Any of those composed of mixed particles may be used.

The photocatalyst is not particularly limited as long as it is a compound having a photocatalytic function, and a known one can be used. Here, the photocatalytic function is a photo-semiconductor material, and when irradiated with light having energy larger than the band gap energy between the valence band and the conduction band, the electrons in the valence band are excited and conducted. It means a function of inducing a redox reaction by transitioning to a band to become excited electrons, generating electron-hole pairs between holes formed in the valence band and excited electrons. Examples of such a compound include titanium dioxide, tungsten oxide, tin oxide and the like, and titanium dioxide is preferable. Examples of titanium dioxide include those having a rutile crystal structure and those having an anatase crystal structure.

The photocatalyst is preferably a photocatalyst having visible light responsiveness. By using a photocatalyst having visible light responsiveness in this way, the sterilization treatment can be further simplified and made more efficient, and the adhesion and growth of bacteria during work can be suppressed.

The photocatalyst having visible light responsiveness refers to a photocatalyst that exhibits catalytic activity by irradiation with visible light (360 nm to 830 nm). Examples of such a visible light responsive photocatalyst include (1) a titanium dioxide crystal lattice doped with one or more of nitrogen, carbon, and sulfur atoms, and (2) a photocatalyst carrying a sensitizer. Can be mentioned.

The visible light responsive photocatalyst (1) can be obtained by a known production method. For example, titanium oxide can be obtained in a sulfur dope by a sol-gel method using a titanium alkoxide mixed with a sulfur source such as thiourea as a raw material.

The sensitizer carried by the visible light responsive photocatalyst (2) means a sensitizer that generates excited electrons by visible light and supplies the excited electrons to a photocatalyst such as titanium dioxide. Examples of the sensitizer include metal hydroxides such as iron, copper, chromium, and nickel, oxyhydroxides, and oxides. Specifically, for example, CuO, Cu (OH) ₂ , FeO (OH), Fe (OH) ₃ , Ni (OH) ₂ , NiO (OH), Cr (OH) ₃ , Cr ₂ O (OH) ₄ , Cr ₂ O _{3 and the} like can be mentioned.

The sterilizing function layer 14 preferably contains a translucent resin filled in the gaps between the particles containing the photocatalyst while maintaining the exposed state of the photocatalyst. The gap between the particles includes a gap between melt-solidified products derived from the particles formed by melt-solidification during spraying. If there are many or large gaps, foreign matter enters the gap, and the foreign matter adheres to the entered foreign matter, so that the surface of the sterilization function layer 14 is covered with the foreign matter. As a result, the photocatalytic function (sterilization function) May decrease. Therefore, as described above, maintaining the long-term maintenance performance of the catalyst function by filling the gap between the particles while maintaining the exposed state of the particles containing the photocatalyst, etc. it can.

The translucent resin is not particularly limited as long as it does not substantially absorb visible light, but a water-soluble acrylic resin and a water-soluble urethane resin are preferable. These resins can exhibit the maintenance performance more effectively and can be easily filled in the gaps, and are excellent in productivity and the like.

The sterilizing function layer 14 can contain a metal having antibacterial properties (hereinafter also referred to as an antibacterial metal). Examples of the antibacterial metal include silver, copper, zinc, aluminum, nickel, cobalt, and chromium. The antibacterial metal may be a single metal or a salt, complex, oxide, hydroxide, oxyhydroxide or the like of these metals. The antibacterial metal may be sprayed together with the photocatalyst particles to be sprayed as particles or the like, or may be contained in a translucent resin. By including such an antibacterial metal in the bactericidal function layer 14, the bacteria removing ability in the bactericidal function layer 14 can be further enhanced.

Moreover, when spraying an antibacterial metal as a particle with a photocatalyst particle, this antibacterial metal can also function as a binder. In this case, the thermal spraying temperature is preferably not less than the melting point of the antibacterial metal and not more than the melting point of the photocatalyst. By forming the bactericidal functional layer by spraying at such a spraying temperature, it is possible to effectively function the antibacterial metal as a binder while suppressing reduction of the surface area of the photocatalyst, deterioration of the photocatalytic function, and the like.

The surface of the sterilizing function layer 14 is preferably polished. Since the surface of the bactericidal function layer 14 is polished in this way, it is possible to suppress a sense of incongruity when the intraoral work part 11 comes into contact with the skin surface in the mouth, and it is also possible to suppress damage to the skin. Also, by polishing the surface, the surface of the photocatalyst particles deteriorated by the heat during thermal spraying is scraped, and when an antibacterial metal is used as a binder, the photocatalyst particles are laminated on the surface of the layer. Therefore, the photocatalyst having a sufficient catalytic function can be exposed on the surface and the sterilizing function of the sterilizing function layer 14 can be enhanced.

The skewness (Rsk) of the roughness curve on the surface of the sterilizing function layer 14 is preferably less than 0. This Rsk is one of the indices of the surface roughness, and indicates which of the crest portion (projection portion) and the trough (hole portion) is larger than the average value. That is, by making Rsk on the surface of the bactericidal functional layer 14 less than 0 in this way, it is possible to reduce discomfort and skin damage when touching the skin surface, and there is a certain valley portion. By expanding the surface area, the catalytic function, that is, the sterilizing function can be effectively exhibited. In addition, although it does not restrict | limit especially as a minimum of Rsk of this bactericidal function layer 14, It can be set to -5, for example. Here, the skewness (Rsk) of the roughness curve refers to a value measured with a cutoff value of 0.8 mm in accordance with JIS B0601: 2001.

The arithmetic average roughness (Ra) on the surface of the bactericidal function layer 14 is preferably 0.05 μm or more and 5 μm or less, and more preferably 0.2 μm or more and 2 μm or less. By controlling the arithmetic average roughness (Ra) of the surface of the bactericidal function layer 14 within the above range, it is possible to further reduce the uncomfortable feeling when contacting the skin in the mouth while exhibiting a sufficient catalytic function. When the arithmetic average roughness is less than 0.05 μm, the surface area is too small and the catalytic function, that is, the sterilizing function may not be effectively expressed. On the other hand, when the arithmetic average roughness exceeds 5 μm, when it comes into contact with the skin in the mouth, it becomes easy to cause a sense of incongruity. Here, the arithmetic average roughness (Ra) refers to a value measured with a cutoff value of 0.8 mm in accordance with JIS B0601: 2001.

Although it does not specifically limit as average thickness of the bactericidal function layer 14, For example, 1 micrometer or more and 100 micrometers or less are preferable. If this average thickness is less than 1 μm, a sufficient sterilizing function may not be expressed partially. On the other hand, when the average thickness exceeds 100 μm, it is uneconomical, for example, the amount of photocatalyst used is increased.

The grip portion 12 is a portion that is actually gripped by a dentist or the like during treatment or the like. The grip portion 12 has a substantially cylindrical shape. One end side end face of the gripping part 12 is connected to the rear end side end face of the intraoral work part 11 having substantially the same central axis.

The grip portion 12 has a base material and a sterilization function layer laminated on the surface of the base material, like the intraoral work portion 11. The material and the like of the base material and the sterilization function layer of the grip portion 12 are not particularly limited, but are integrally formed from the same material as the base material 13 and the sterilization function layer 14 of the intraoral work part 11 from the viewpoint of productivity. It is preferable.

The surface of the grip portion 12 may or may not be polished. Conversely, a surface roughening process may be performed on the region 12 a that is touched by the finger when gripped by the grip portion 12. When at least a part of the surface of the gripping portion 12 is not polished or roughened, the gripability of the gripping portion 12 can be improved.

According to the dentistry device 10, since the intraoral work part 11 has the sterilization function layer 14 formed by thermal spraying of particles containing a photocatalyst, sterilization to a certain degree is performed by irradiating light after use. And sterilization can be simplified.

The light to be irradiated for sterilization may be appropriately selected according to the photocatalyst to be used, such as visible light or ultraviolet light. When using a visible light responsive photocatalyst, visible light may be irradiated. Since sterilization becomes possible by irradiation with visible light, sterilization treatment becomes easier. A light source used for irradiation is not particularly limited, such as a fluorescent lamp, an incandescent lamp, a halogen lamp, an LED, and natural light. The sterilization treatment of the dental medical device 10 includes sterilization by light irradiation and other sterilization means such as cleaning, boiling sterilization, autoclave sterilization, dry heat sterilization, ethylene oxide gas sterilization, ultraviolet sterilization, and other chemical sterilization. It can also be done in combination.

<Method of manufacturing dental equipment>
Although the manufacturing method of the dental medical device 10 is not particularly limited,
A step of spraying particles containing a photocatalyst on the surface of the substrate 13 (spraying step), and a step of polishing the surface of the layer formed by the spraying (polishing step)
It can manufacture suitably by the manufacturing method containing. In addition, it is preferable to have the process (slurry preparation process) of preparing the slurry used for a thermal spraying before the said thermal spraying process. Hereinafter, it explains in full detail for every process.

1. Slurry preparation process In this process, particles containing a photocatalyst and a dispersion medium are supplied to a container (for example, a stirring tank) to prepare a slurry.

As described above, the particles containing a photocatalyst may include particles (photocatalyst particles) usually made of a photocatalyst and may contain other particles (antibacterial metal particles and the like).

The content of photocatalyst particles (titanium dioxide particles and the like) in the slurry is usually 1% by mass to 30% by mass, preferably 3% by mass to 15% by mass, and more preferably 5% by mass to 10% by mass. . When the content of the photocatalyst particles is less than 1% by mass, the thickness of the layer obtained by thermal spraying becomes too small, and there is a possibility that a sufficient sterilizing function cannot be expressed. On the other hand, when the content exceeds 30% by mass, stress is generated inside the layer obtained by thermal spraying due to the difference in thermal expansion coefficient between the layer obtained by thermal spraying and the base material 13, and cracks are generated. It tends to occur.

The diameter (secondary particle diameter) of the photocatalyst particles is, for example, from 0.5 μm to 10 μm, and more preferably from 1 μm to 5 μm. When the diameter of the photocatalyst particles is less than 0.5 μm, the kinetic energy of the particles is lowered, and the film forming property may be lowered. On the contrary, when the diameter exceeds 10 μm, the dispersibility may be lowered. The primary particle diameter of the photocatalyst particles is preferably, for example, 10 nm or more and 50 nm or less. By using photocatalyst particles having a primary particle diameter in such a range, it is possible to increase the supportability of other metal particles and the like while suppressing the manufacturing cost. In addition, the diameter of the particle | grains in this specification says the value measured by a dynamic light scattering method.

When visible light responsiveness is developed by supporting a sensitizer on the photocatalyst, a water-soluble metal complex such as iron, copper, chromium, or nickel or a water-soluble metal salt may be contained in the slurry. These water-soluble metal complexes and water-soluble metal salts react with water when sprayed to become the above-mentioned hydroxide, oxyoxide or oxide, and are supported on the photocatalyst particles as a sensitizer.

Specific examples of water-soluble metal complexes include [Cu (NH ₃ ) ₄ ] ²⁺ , [Fe (CN) ₆ ] ⁴⁻ , [Fe (CN) ₆ ] ³⁻ , C ₁₀ H ₁₂ FeN ₂ O _{8, and the} like. Specific examples of the water-soluble metal salt include FeCl ₃ , Fe ₂ (SO ₄ ) ₃ , Fe (NO ₃ ) ₃ , CuSO ₄ , Cu (NO ₃ ) ₂ , CuCl ₂ , Ni (NO ₃ ) ₂ , NiCl ₂ , NiSO ₄ , Cr (NO ₃ ) _{3 and the} like can be mentioned.

The content of the water-soluble metal complex and the water-soluble metal salt in the slurry is 0.05 parts by mass or more and 0.5 parts by mass as the metal component amount with respect to 100 parts by mass of the metal component amount (for example, titanium component amount) in the photocatalyst particles. It can be as follows.

The slurry may contain an antibacterial metal as other particles. The content of the antibacterial metal in the slurry is preferably 1% by mass to 30% by mass, more preferably 3% by mass to 15% by mass, and still more preferably 5% by mass to 10% by mass. When the content of the antibacterial metal is less than 1% by mass, a sufficient antibacterial function may not be exhibited. On the other hand, when the content of the antibacterial metal exceeds 30% by mass, the dispersibility in the slurry may be lowered due to precipitation, segregation, or the like.

When the antibacterial metal is granular, the diameter is preferably 0.5 μm or more and 10 μm or less, for example. When the diameter of the antibacterial metal is less than 0.5 μm, secondary aggregation tends to occur, and when it exceeds 10 μm, precipitation or the like easily occurs.

As the dispersion medium used in the slurry, water is usually used, but other organic solvents such as alcohols and mixtures of water and organic solvents can also be used.

The slurry can further contain a surfactant in order to enhance dispersibility. Examples of the surfactant include anionic surfactants such as polycarboxylic acid-based polymer surfactants and nonionic surfactants. As content of surfactant, 0.5 mass part or more and 3 mass parts or less are preferable with respect to 100 mass parts of particle | grains containing a photocatalyst.

The slurry can be prepared by supplying particles containing a photocatalyst and a dispersion medium to a container and stirring them. In addition, you may perform ultrasonic irradiation with stirring instead of stirring.

2. Thermal spraying process In this process, the slurry containing particles containing the photocatalyst prepared in the slurry adjustment process is sprayed onto the surface of the base material 13. Although this thermal spraying can be performed by a known method, it is preferable to perform high-speed thermal spraying at a low temperature using a high-speed thermal spraying apparatus. By performing such thermal spraying, for example, when anatase-type titanium dioxide particles are used as photocatalyst particles, transformation to the rutile type during thermal spraying is suppressed, and a bactericidal functional layer having high catalytic activity can be obtained. Hereinafter, an example of the high-speed spraying apparatus will be described with reference to FIG.

The high-speed spraying device 20 shown in FIG. 3 mainly includes a spray gun 21 and a slurry mixing unit 22 attached to the tip of the spray gun 21. The slurry mixing unit 22 includes a cylindrical frame guide portion 23 through which a spray frame ejected from the tip of the spray gun 21 passes, and the slurry (particles including a photocatalyst, etc.) in the spray frame passing through the frame guide portion 23. And a nozzle 24 for mixing the slurry in the thermal spray frame.

The slurry stored in the slurry tank 26 is supplied to the slurry mixing unit 22 by the pump 25 while ejecting the spray frame from the spray gun 21 using the high-speed spray device 20. In addition, the base material 13 is arrange | positioned in the spray destination of a spraying flame | frame. By doing in this way, slurry (particles containing a photocatalyst, etc.) can collide with the base material 13 at high speed on the flow of the thermal spray frame ejected from the tip of the frame guide portion 23, and the surface of the base material 13 A layer that becomes the sterilization function layer 14 can be formed.

As the thermal spraying conditions, the flame temperature is preferably 700 ° C. or higher and 2000 ° C. or lower, and more preferably 750 ° C. or higher and 1500 ° C. or lower. Further, the frame ejection speed is preferably 800 m / sec or more and 2000 m / sec or less. When the temperature of the thermal spray flame is less than 700 ° C., the flame temperature becomes too low, and it becomes difficult to stably form a layer on the substrate surface. On the other hand, when the temperature of the thermal spray flame exceeds 2000 ° C., the flame temperature becomes too high. For example, when anatase type titanium dioxide is used, the amount of titanium dioxide transformed from the anatase type to the rutile type increases, and titanium dioxide. May not be able to exhibit a sufficient photocatalytic function. The flame temperature is a temperature measured at a position 200 mm from the tip of the thermal spray gun 21 on the thermal spray frame center line. The temperature was measured using a thermocouple (eg, alumel / chromel up to 1000 ° C., tungsten / tungsten rhenium above 1000 ° C.), and the tip of the thermocouple inserted into the thermal spray frame. To do.

3. Polishing process In this process, the surface of the layer formed by thermal spraying is polished to obtain the sterilization function layer 14. A specific method of the polishing treatment is not particularly limited, and buff polishing, brush polishing, sand blasting, liquid honing, and the like can be used.

In addition, after forming the layer used as a disinfection function layer by thermal spraying, it can be filled with translucent resin in gaps, such as between the particles of this layer (translucent resin filling process). This filling can be performed, for example, by applying an aqueous solution of a water-soluble acrylic resin or a water-soluble urethane resin to the surface of the layer. Further, the aqueous solution may contain an antibacterial metal. By containing the antibacterial metal in the aqueous solution, the antibacterial metal can be present in the filled translucent resin, and the antibacterial performance of the antibacterial metal can be exhibited.

The translucent resin filling step is preferably performed before the polishing treatment step. Thus, after filling a translucent resin by application | coating etc., the exposed state of the photocatalyst in the bactericidal function layer surface can be made favorable by grind | polishing the layer surface.

The production method of dental equipment according to the present invention is not limited to the embodiments described above. The dental medical device is not limited to an explorer, but other mirrors, tweezers, extractors, cutting turbines, broaches, reamers, files, tooth extraction forceps, hebels, sharps, scalpels, dental treatment electric engines, dentistry Medical devices used for oral treatment in general and medical devices used for oral examination, such as therapeutic motors, handpieces, dental air scalers, and dental laser handpieces. As the dental medical devices, other instruments used in the caries treatment and periodontal disease therapy, implant treatment, orthodontic treatment, aesthetic dentistry also includes instruments used in the prevention dentistry.

Further, the dental appliance has a mouth working portion and the gripping portion may be formed from another material may, even if it is not formed integrally. For example, the gripping part can be made of resin, or only the base material is integrally formed in the mouth working part and the gripping part, and the gripping part has a structure in which the resin is laminated on the surface of the base material. Also good. Furthermore, a structure in which the intraoral work portion and the grip portion cannot be clearly distinguished may be employed. Even in such a dental medical device, at least the intraoral work part has a sterilization function layer, and if the sterilization function layer is formed by thermal spraying of particles containing a photocatalyst, the effect of the present invention can be enjoyed. it can.

The dental medical device manufactured by the method according to the present invention can be suitably used for various dental treatments including caries treatment and periodontal treatment.

10: Dental medical equipment, 11: Work part in mouth, 12: Holding part, 12a: Area, 13: Base material, 14: Sterilization functional layer, 20: High-speed spraying device, 21: Thermal spray gun, 22: Slurry mixing part, 23 : Frame guide part, 24: Nozzle, 25: Pump, 26: Slurry tank

Claims (1)

It has a base material and a bactericidal function layer laminated on the surface of the base material, and is connected to the mouth working portion for performing examination and removing dirt by bringing the tip into contact with the teeth, and the rear end face of the mouth working portion. In a manufacturing method of a dental medical device provided with a gripping part,
A step of roughening the surface of the base material so that the arithmetic average roughness is 0.2 μm or more and 4 μm or less;
In the stirring tank, (1) anatase-type titanium dioxide particles having a primary particle diameter of 10 nm to 50 nm, and (2) iron, copper, chromium, or nickel with respect to 100 parts by mass of the titanium component in the titanium dioxide particles. A water-soluble metal complex or a water-soluble metal salt having a metal component amount of 0.05 to 0.5 parts by mass, (3) a granular antibacterial metal having a diameter of 0.5 to 10 μm, and (4 ) Supplying water and stirring to prepare a slurry in which titanium dioxide particles having a secondary particle diameter of 1 μm to 5 μm and the antibacterial metal are dispersed;
The slurry is placed on the surface of the base material disposed at the spray destination of the thermal spray frame by placing the slurry on the flow of the thermal spray frame having a flame temperature of 750 ° C. to 1500 ° C. and a flame ejection speed of 800 m / second to 2000 m / second. Colliding against and forming a layer on the surface of the substrate ;
Filling the gap between the layers with a translucent resin;
Said translucent polishing treatment of the surface of said layer filled with a resin, the dental device, characterized in that it comprises a step of obtaining the sterilizing functional layer skewness is less than 0 the roughness curve in the surface Production method.

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