WO2001068013A1 - Wire for use in orthodontics and method for manufacture thereof - Google Patents

Abstract

A wire for use in orthodontics which may be manufactured by a method comprising inserting a continuous fiber bundle into a synthetic resin shell member, injecting a polymerizable component into the synthetic resin shell member, and then forming the synthetic resin shell member into an arc shape approximately fitted to a given dentition while curing by polymerization at least a part of the polymerizable component filled in the synthetic resin shell member. The wire has a shape approximately fitted to a given dentition, has good appearance from the view point of aesthetic sense, is free from the problem of metal allergy and is easy to place.

Description

 Akira Itoda

 FIELD OF THE INVENTION

 The present invention relates to an orthodontic wire (arch wire for orthodontics) having an arcuate shape substantially corresponding to a dentition to be orthodontic, and a method of manufacturing an orthodontic wire having such a form. More specifically, the present invention relates to an orthodontic wire having an arc shape substantially corresponding to a dentition to be orthodontic so as to have an aesthetic property and to facilitate mounting, and to provide such a form and an aesthetic appearance. The present invention relates to a method for manufacturing an orthodontic wire having an elasticity. Background art

 It is desirable to perform orthodontic treatment because malocclusion of human teeth is a psychological disorder, and can also cause masticatory dysfunction, pronunciation problems, caries and periodontal disease.

 Conventionally, in orthodontics, a bracket is attached to the front or back surface of a tooth, a metal wire is attached to the bracket, and the elastic force of the metal wire is used. Because metal wires are easy to handle and have high strength, metal wires are also used in current orthodontics.

By the way, for orthodontics, it is necessary to continuously apply a bending load of about 0.5 to 5 N to a tooth for a long period of time. That is, the teeth to be corrected By continuously applying a constant load to the tooth, the dentition is corrected by continuously applying pressure to the alveolar bone and changing the shape of the alveolar bone using the bone remodeling function. However, there is a periodontal ligament between the tooth and the alveolar bone, and it is necessary to apply a load that does not hinder the blood flow in the periodontal ligament. The capillary pressure in the periodontal ligament is 1.5 to 2 kPa (1 It is about 5 to 20 gf / cm ² ), and the optimal correction force is about 0.5 to 10 N so as not to inhibit blood flow in the capillaries. Especially in the early stages of orthodontics, this orthodontic force must be set at a relatively low value.

 Conventionally, stainless steel, Co-Cr alloy, Co-Cr-Ni alloy, Ni-Ti alloy, and the like have been used as metal wires for orthodontics. In order to achieve the relatively low orthodontic force required in the early stage of orthodontics by using, a method of reducing the cross-sectional diameter of the metal wire has been adopted.

 However, such a metal wire has a very serious drawback that it has a luster peculiar to metal, has a poor appearance, and increases a psychological burden on a patient during treatment. In addition, the onset of allergy due to such metal wires is also a problem. In addition, when performing MRI tomography, metal members (metallic dentures) must be removed to avoid disturbing the image due to metal.

 Under these circumstances, attention has recently been paid to composite wires made of resin impregnated with inorganic fibers such as glass fibers.

Such a composite material wire does not undergo plastic deformation, and is translucent white, so that it is not conspicuous even when attached, and has an aesthetic appearance. In addition, the psychological burden of orthodontic patients is significantly reduced, and there is an advantage that since there is no elution of metal, it does not induce the onset of metal allergy.

 Such a composite material wire is produced, for example, by manufacturing a glass single fiber, performing a coupling treatment on the surface of the single fiber, impregnating the resin, and then drawing the resin together with the resin from a die having a predetermined inner diameter. It is manufactured by this. The composite material wire obtained by such a manufacturing method is linear.

Orthodontic wires wrap the wire over a bracket attached to the surface of the tooth and continue to apply stress to the wire that is radiusing the tooth disturbing the dentition to correct the deflection In this way, using the bone remodeling function, the shape of the alveolar bone is changed to correct the dentition. Thus, it is not necessary to apply flexural stress to teeth that do not require orthodontics. For this reason, when performing orthodontics using a metal wire, before the metal wire is wrapped around the bracket, it is plastically processed into a shape that roughly corresponds to the appropriate dentition, and thus almost corresponds to the dentition. The wire with the above shape was wrapped around the bracket to apply the appropriate flexural stress to the teeth that disturbed the dentition. However, an orthodontic wire composed of a core material such as glass fiber and a resin usually has a linear shape because it is drawn from a die as described above, and has a curved shape. It is virtually impossible to mold. Also, it is very difficult to plastically process the orthodontic wire once formed linearly so as to substantially correspond to the dentition, and this is not the case when using a thermoplastic resin. In addition, an orthodontic wire containing a resin that has lost its plasticity after it has been hardened once, such as a thermosetting resin or a photo-setting resin, is plastically processed so as to approximately correspond to the dentition before being passed over the bracket. It is virtually impossible to do so.

 In the initial stage of orthodontics, it is necessary to apply a small orthodontic force to the dentition, and in order to apply such a small orthodontic force, the orthodontic wire should be formed in a form that substantially corresponds to the dentition. Is preferred.

 From this viewpoint, there are various proposals for orthodontic wires using composite materials that do not use metals. For example, Japanese Patent Publication No. Hei 7-6-1346 discloses that a thermoplastic matrix composition is injection-molded to produce an arcuate wire.

 Also, Japanese Patent Application Laid-Open No. 3-49749 discloses an orthodontic archwire using a heat-resistant plastic optical fiber, and Japanese Patent Application Laid-Open No. 2-109552 discloses a core made of quartz glass or the like. An orthodontic archwire in which the periphery is covered with a resin as a material is disclosed. However, all of these archwires have a predetermined shape by using a thermoplastic resin, and the characteristics thereof are easily changed by heat, and the characteristics are stable. Hateful. Also, if a wire made of a thick glass core such as that used in an optical fiber as described above is used for orthodontics, the wire will be damaged when it is attached to the bracket and bent. There are many.

U.S. Pat. No. 5,869,178 discloses that a photopolymerizable component and a fiber are formed by pultrusion. There is no description about using a sex component to form a predetermined shape. When a straight wire made by this method is applied to orthodontics, the force that attempts to restore it to a straight line may move the teeth at locations that do not require orthodontics. I don't like it.

 Also, Japanese Patent Application Laid-Open No. Hei 1-91851 describes a method of manufacturing an oral cavity or an extraoral prosthetic structure by filling a hose with a fiber and injecting an acrylic plastic into the hose. However, this publication does not describe orthodontic wires.

 In addition, Japanese Patent Application Laid-Open No. 1-135345 discloses an invention of an orthodontic wire made of a reinforced resin using continuous fibers in which a plurality of filaments are directed in one direction as a whole. This publication does not disclose that the orthodontic wire is formed so as to substantially conform to the dentition. Disclosure of the invention

 An object of the present invention is to provide a method for manufacturing an orthodontic wire having a form substantially along a dentition and an orthodontic wire having a form substantially corresponding to a dentition manufactured in this way. I have.

 Further, the present invention provides a method for producing an orthodontic wire having excellent esthetics, good orthodontic power, and having a form substantially corresponding to a dentition to be corrected, and having the above-described characteristics and forms. The purpose is to provide orthodontic tires.

Further, another object of the present invention is to provide a member for manufacturing an orthodontic wire for manufacturing the above-described orthodontic wire. In one embodiment of the present invention, after inserting a continuous glass fiber bundle into a synthetic resin sheath member, a polymerizable component is injected into the synthetic resin sheath member, and then the synthetic resin sheath member is formed into a dentition. A method for producing an orthodontic wire having a form substantially corresponding to a dentition by polymerizing and curing at least a part of a polymerizable component filled in the synthetic resin sheath member while keeping the shape substantially in an arc shape. It is in.

 Another embodiment of the present invention is a method of inserting a continuous glass fiber bundle into a mold in which a concave portion having an arcuate shape substantially corresponding to a tooth row is formed, injecting a polymerizable component into the mold, A method for producing an orthodontic wire having a form substantially corresponding to the dentition by polymerizing and curing at least a part of the polymerizable component filled in the dentition.

 Further, an orthodontic wire according to the present invention comprises a continuous glass fiber bundle and a cured product of a polymerizable component impregnated in the continuous glass fiber bundle, and cures the continuous glass fiber bundle and the polymerizable component. It is characterized in that the orthodontic wire composed of the body is given a form corresponding to the approximate dentition.

 The orthodontic wire of the present invention comprises a continuous glass fiber bundle and a cured product of a polymerizable component impregnated in the continuous glass fiber bundle, and forms an arc in a form corresponding to a substantially dentition. ing. The cured product of the polymerizable component constituting the orthodontic wire of the present invention is preferably a cured product of a photopolymerizable component and Z or a thermopolymerizable component.

In the orthodontic wire having such a configuration, after a continuous glass fiber bundle is inserted into a synthetic resin sheath member, a polymerizable component (uncured material) is injected into the sheath member, and the polymerizable component is injected. Sheath member corresponds to approximately dentition The polymer can be manufactured by molding into a form and then curing the polymerizable component.

 The orthodontic wire formed in this way is composed of continuous glass fiber and a cured polymerizable component, and substantially no metal is exposed on the wire surface, and the overall shape is substantially tooth-shaped. Since it corresponds to a row, it has good aesthetics and does not cause metal allergy. Further, since the orthodontic wire of the present invention has a form substantially corresponding to the dentition to be orthodontic, it is easy to mount it on the bracket. In addition, the orthodontic wire of the present invention preferably inserts glass fiber into a sheath member, fills the polymerizable component, and then cures the polymerizable component into a predetermined shape. Are not protruding from the wire surface, and the wire surface is very smooth.

 Furthermore, when a photopolymerizable component is used, the polymerizable component can be cured in the patient's mouth to produce an orthodontic wire suitable for the patient. BRIEF DESCRIPTION OF THE FIGURES

 FIG. 1 is a perspective view showing an example of the orthodontic wire of the present invention. FIG. 2 is an enlarged cross-sectional view showing an X-X cross section in FIG. 1 of the present invention in an enlarged manner.

 FIG. 3 is a diagram schematically showing a production example of the orthodontic wire of the present invention.

FIG. 4 is a view schematically showing a production example of the orthodontic wire according to the present invention. is there. BEST MODE FOR CARRYING OUT THE INVENTION Next, an orthodontic wire of the present invention will be described along a manufacturing method.

 FIG. 1 is a perspective view showing an example of the orthodontic wire of the present invention, and FIG. 2 is an enlarged cross-sectional view showing an X-X cross section of the orthodontic wire. FIG. 3 and FIG. 4 are views showing an example of a method for producing an orthodontic wire of the present invention.

 As shown in FIG. 1, the orthodontic wire 10 of the present invention has a form substantially corresponding to the dentition, and usually has an arc portion 11 formed in a substantially semicircular shape and the arc It has linear portions 12a and 12b extending almost linearly from both ends 11a and lib of the portion 11.

As shown in FIG. 2, the cross section of the orthodontic wire 10 is composed of glass fibers and a cured polymerizable component. In the orthodontic wire of the present invention, by changing the ratio between the glass fiber and the cured product of the polymerizable component, the lmm deflection load of this orthodontic wire is usually 0.1 to 0.1 mm. It can be arbitrarily adjusted within the range of 1 ON, preferably in the range of 0.3 to 4N. In other words, a metal orthodontic wire that has been used conventionally can exhibit good orthodontic power in a region where the orthodontic power is relatively high, but a material that exhibits a relatively low orthodontic power is extremely difficult. It is limited to. In the orthodontic wire of the present invention, by adjusting the volume content of the glass fiber and the cured polymerizable component, this lmm is reduced. The deflection load can be set to any value within the above range. The bending load of the orthodontic wire can also be adjusted by adjusting the number of crossings per unit length of continuous glass fibers or glass fiber bundles. For example, by forming two or more glass fibers into a twisted yarn, or by knitting a fiber bundle made of a plurality of glass fibers into a braid, the same resin and fiber content are obtained. The deflection load can be adjusted.

 For example, as shown in FIGS. 3 and 4, the orthodontic wire according to the present invention is obtained by inserting a glass fiber 31 into a synthetic resin sheath member 33 and further filling a polymerizable component. It can be manufactured by forming the sheath member 33 into a predetermined shape and curing the polymerizable component.

 In order to inject the polymerizable component 34 into the sheath member 33, the polymerizable component is injected under pressure from one end of the sheath member 33 with a syringe 41 and from the other end. By depressurizing and sucking the polymerizable component, the polymerizable component 34 can be relatively easily injected into the sheath member 33. In addition, the polymerizable component 34 has a force for impregnating the glass fiber 31 before being inserted into the sheath member 33, and a pre-prepared state in which a part of the polymerized component impregnated is hardened. It is preferable to use a material which has been subjected to the method described above, since air entrapment can be further reduced. The polymerizable component used for impregnation may be different from the polymerizable component 34 injected later, or may be the same component.

The synthetic resin sheath member 33 used in the present invention is a hollow tube made of a synthetic resin. The sheath 3 3 made of synthetic resin is formed. Various synthetic resins can be selected depending on the method of curing the polymerizable component injected into the sheath member 33. For example, when the polymerizable component is a photopolymerizable component, it is preferable to use a light-transmitting resin, and when the polymerizable component is a thermopolymerizable component, a heat-resistant resin is used. Is preferred. Further, since the sheath member 33 is removed after the polymerizable component 34 is cured to form the polymerizable component cured body 35, the sheath member 33 does not strongly adhere to the polymerizable component cured body 35. It is preferably formed from a resin. Examples of the resin forming the sheath member 33 include polyolefin such as polyethylene, fluorine resin, silicone resin, and polyvinyl chloride. Among such resins, it is preferable to use a fluororesin or polyethylene. This sheath member may be heat-shrinkable.

 The shape of the hollow portion or the cross-sectional shape of the mold formed in the sheath member 33 can be appropriately selected according to the cross-sectional shape of the orthodontic wire to be obtained. For example, the cross-sectional shape of the hollow portion can be circular, elliptical, semi-circular, square, or polygonal. Such a maximum cross length of the cross section of the sheath member 33 can be set in consideration of the bending load of the orthodontic wire 10 to be obtained. For example, when an lmm deflection load of 0.1 to 5 N is to be obtained, the inner diameter of the sheath member 33 having a circular cross-sectional shape is usually 0.1 to 2 mm, preferably 0.2 to 1 mm. It is.

After such a sheath member 33 is filled with a guide liquid 32 made of a polymerizable component as necessary, a continuous glass fiber bundle 31 is placed in the sheath member 33. Insert Is a continuous glass fiber bundle 3 1 used in here, other conventional glass fibers, in particular bioglass _{(SiO 2 -Na 2 O-CaO} -P 2 0 5 system), Se Love evening Ichiru (SiO My power _{system; 2 -CaO-Na 2 OP 2} 0 5 -K 2 O-MgO -based) and CPSA glass _{(CaO-P 2 0 5 -SiO} 2 -Al 2 O 3 system) in vivo activity bioglass such as crystallized glass _{(Si0 2 -B 2 0 3 -Al} 2 0 3 -MgO-K 2 0-F based), A- W crystallization glass _{(SiO 2 -CaO-MgO-P} 2 0 5 system) and 3 - C a (PO ₄₎ 2 based crystallized glass (CaO-P ₂ 0 ₅ system) bioactivation crystallized glass such as; Hyde Rokishiapatai Bok _{(Ca 10 (PO 4) 6} (OH) 2) in vivo, such as calcium activity-phosphate; Application Benefits calcium Umuhosu phosphate (TCP: (Ca ₃ (P_rei_4) 2), Te preparative La calcium phosphate off E one preparative _{(4 CP: (Ca 4 0} (P0 4) 2) and Biodegradable calcium phosphate such as low crystalline hydroxyapatite; and soluble calcium alcohol It can be mentioned fibers formed from Natick preparative (CaO-Al ₂ O ₃ system) bioerodible calcium aluminate Arumine bets like.

Vivo activity bioglass fibers Among these fibers rather preferable, and et al in _{CaO-P 2 0 5 -Si0 2} -Al 2 0 3 based biomaterials glass fibers (CPSA glass fibers), compared biological This is a particularly preferred fiber in the present invention. In this CPSA glass fiber, the molar ratio of calcium Z-line in the fiber is usually in the range of 0.5 to 3.0, and the sum of the calcium oxide component and the diphosphorus pentoxide component in the fiber is usually It is in the range of 20 to 60% by weight, and the sum of the silicon dioxide component and the aluminum oxide component is usually in the range of 35 to 80% by weight. The details of such _{CaO-P 2 0 5 -Si0 2} -Al 2 0 3 based biomaterials for glass fibers (CPSA glass fiber), Kokoku 6 2 - 1 2 3 2 2 Patent Publication, Japanese Patent Publication No. 1,092,727 and Japanese Patent Publication No. 2-10,244, U.S. Pat.No. 4,613,577, and U.S. Pat. It is described in the specification of No. 3.

 The average thickness of such glass fibers (one) is usually in the range from 1.0 to 50 am, preferably in the range from 5 to 30 im.

 In the present invention, two or more continuous glass fibers as described above are inserted into the sheath member 33. These continuous glass fiber bundles 31 can cross each other. That is, the glass fiber can be formed into a twisted yarn, and the fiber or the fiber bundle can be formed into a braid. By intersecting glass fibers or glass fiber bundles in this way, the bending strength of the obtained orthodontic wire can be adjusted.

Fibers such as those described above include, for example, α-methacryloxypropyltrimethoxysilane, α-methacryloxypropyltriethoxysilane, R-methacryloxypropyltrimethoxysilane, α-methacryloxypropyltrimethoxysilane, and α-methacryloxypropyltrimethoxysilane. It is preferably used after pre-treatment with a coupling agent such as methacryloxypropyltriethoxyaminosilane or the like, particularly a silane coupling agent. The pretreatment using such a coupling agent usually involves dissolving the coupling agent in an organic solvent, immersing the above continuous glass fiber in the solvent, and then pulling up from the solution and drying. Is adopted. Further, it is preferable that the continuous glass fiber is baked at a temperature of, for example, about 100 to 200 X: after being immersed in the coupling agent and pulled up. Furthermore, the continuous glass fiber thus obtained forms a wire. The surface can be coated with a resin to be formed or a resin having an affinity for this resin.

 By coating the surface of continuous glass fiber with resin in this way, the affinity between the fiber and resin is improved, the porosity in the wire is reduced, and a highly uniform orthodontic wire is manufactured. It's easy to do. Further, the continuous glass fiber may be impregnated with the polymerizable component or may be inserted into the sheath member or the mold in a pre-prepared state in which a part thereof is polymerized. By using a resin-coated fiber or a fiber in a pre-prepared state in this manner, it becomes easy to effectively control the bending behavior in a low region. In the present invention, the above continuous glass fibers are used alone, but other fibers can be used in combination with such glass fibers. Here, examples of fibers that can be used in combination with glass fibers include organic fibers, inorganic fibers (excluding glass fibers), and metal fibers.

Examples of organic fibers that can be used here are acryl fiber, acetate fiber, cuprammonium fiber, polyamide fiber, aramide fiber, polyamide fiber, polyimide fiber, and bismuth. Coarse Rayon fiber, polyvinylidene fiber, vinylon fiber, fluororesin fiber, polyacetone fiber, polyurethane fiber, polyolefin fiber, ultra-high molecular weight polyolefin fiber and polyvinyl chloride fiber Further it is, in an example of the inorganic fibers, silica mosquito (SIOS), alumina (A1 ₂ 0 _3), di Rukonia (Zr0 _2), calcium aluminate Natick preparative (CaO -Al ₂ 0 ₃ system) and § Rumi Nojiri cable Bok _{(Na 2 O -Al 2 0 3} -Si0 2 system) in vivo inert oxides such as; Power one carbon (virtous, pyrolytic, grap hite) , it is the this include vivo inert non-oxide such as silicon nitride (Si ₃ N ₄₎ and carbonization silicon (S i C). In addition to using glass fiber, a thin wire (thickness of about 1.0 to 50 mm) made of metal (eg, stainless steel, titanium alloy, etc.) that has been used as an orthodontic wire has been used. A high strength orthodontic wire can be obtained.

 Usually, the continuous glass fiber bundle 31 as described above is inserted so that the volume occupying the sheath member 33 is 5 to 90%, preferably 10 to 70%.

After inserting the continuous glass fiber bundle 31 into the sheath member 33 in this way, the polymerizable component 34 is injected into the sheath member 33. The polymerizable component 34 joins the sheath 41 to one end of the sheath member 33 via a first joint 42 and the second joint 43 to the other end. Through a suction device (not shown). A continuous glass fiber 31 is inserted into the sheath member 3 3 together with a guide liquid 32 made of a polymerizable component, and is joined to the sheath member 33 via the first joint 42. The polymerizable component 34 is filled in the syringe 41. The polymer 41 is pressed into the sheath 33 by pressing the piston of the syringe 41, and the suction device joined via the second joint 43 is operated. The guide liquid 32 made of a polymerizable component filled in the sheath member 3 3 is sucked. In this way, the guide liquid agent 32 composed of the polymerizable component filled in the sheath member 33 is pulled by the suction device while being pushed by the polymerizable component 34, and air bubbles are formed in the sheath member 33. Etc. should not be left Further, the polymerizable component 34 can be filled in the sheath member 33. The polymerizable component thus pressed into the sheath member 33 is a liquid that is a mixture of a monomer and / or a lower-order polymer and a polymerization initiator that can form a cured product in the following step. Examples of such monomers and / or lower polymers are (meth) acrylic acid, 4- (meth) acryloxyshethyl pyromellic acid, 1,4- Di (meta) acryloxyshethyl pyromellitic acid, 6- (meth) acryloxyshethylnaphthalene-1,2,6-tricarboxylic acid, N- (meth) acrylic acid P -Aminobenzoic acid, N- (meth) acryloyl -0-Aminobenzoic acid, N- (meta) acryloyl -m- Aminobenzoic acid, N- (meta) Acryloyl-5-aminosalicylic acid, N- (meth) acryloylile-4-aminosalicylic acid, 4- (meth) acryloxyshethyl trimellitic acid and its anhydride 4- (meth) acryloxybutyl trimellitic acid and its anhydride, 4- (meth) acryloxyhexyl trimellitic acid and its anhydride, 4- (meta) Acrylo Sidedecyl trimellitic acid and its anhydride, 2- (meth) acryloyloxybenzoic acid, 3- (meth) acryloyloxybenzoic acid, 4- (meth) acryloyloxybenzoic acid,) 3-(meta) Acryloyloxyle high dross sine sine, 3-(meta) acryloyloxydyl dolene male, 3-(meta) acryloyloxy A monomer containing a carboxylic acid group such as tilneudrogen phosphate, 11- (meta) acryloyloxy-1,1-didecanedicarboxylic acid, p-vinylbenzoic acid, or an anhydride thereof;

(2- (meth) acryloxyshethyl) phosphoric acid, (2- (meta) P-styrenesulfonic acid, 2-acrylamide, etc. Monomers having a phosphoric acid group such as acryloxyshethylphenyl) phosphoric acid and 10- (meth) acryloxydecylphosphoric acid; A monomer having a sulfonic acid group, such as -2-methylpropanesulfonic acid;

 Methyl acrylate, ethyl (meth) acrylate, butyl (methyl) acrylate, hexyl (meth) acrylate, 2-ethyl hexyl (meth) acrylate , Dodecyl (meth) acrylate, lauryl (meth) acrylate, cyclohexyl (meth) acrylate, benzyl (meth) acrylate, isobornyl (meta) ) Alkyl esters of (meth) acrylic acid such as acrylates and adamantyl (meth) acrylates;

 2-hydroxyhexyl (meth) acrylate, 2- or 3-hydroxypropyl (meth) acrylate, 4-hydroxybutyl (meth) acrylate, 5-hydroxy Roxypentyl (meth) acrylate, 6-hydroxyhexyl (meth) acrylate, 1,2- or 1,3-dihydroxypropyl mono (meth) acrylate and Hydroxyalkyl esters of (meth) acrylic acid, such as erythritol mono (meth) acrylate;

Diethylene glycol mono (meth) acrylate, triethylene glycol mono (meth) acrylate, polyethylene glycol mono (meth) acrylate, and polypropylene glycol mono (meth) yl ) Polyethylene glycol mono (meta) acrylates such as acrylicates; Fluoroalkyl esters of (meth) acrylic acid, such as perfluorooctyl (meth) acrylate and hexafluorobutyl (meth) acrylate;

 Silanes having a (meth) acryloxyalkyl group such as r- (meth) acryloxypropyltrimethoxysilane and a- (meth) acryloxypropyltri (trimethylsiloxy) silane Compounds; polyfunctional acrylates having a bisphenol skeleton or a disocyanurate ring;

 (Meth) acrylates having a cyclic structure such as styrene, α-methylstyrene, ρ-methylstyrene, and tetrafuryl (meth) acrylate;

 Epoxy resin precursor, phenol resin precursor, alkyd resin precursor, carbon resin precursor, formaldehyde resin precursor, melamine-formaldehyde resin precursor, unsaturated polyester resin precursor, unsaturated poly Ester resin precursor, polyamide-imide resin precursor, polybenzothiazole resin precursor, polyimide precursor, novolak resin precursor, resole resin precursor, urea resin precursor, melamine Resin precursor, unsaturated polyester resin precursor, alkyd resin precursor, polyaryl phthalate precursor, urethane resin precursor, diethylene glycol bisaryl carbonate copolymer precursor, bismalei Mid polyadduct precursor, epoxy (meth) acrylate, urethane (meth) acrylate, vinyl Monomer or a cage Goma;

Ethylene glycol (meth) acrylate, propylene glycol (Meth) acrylate, butylene glycol (meta) acrylate, neopentyl alcohol glycol (meta) acrylate, hexylene glycol (meta) acrylate, trimethylol Poly (meta) acrylates of alkanol polyols such as propane (meta) acrylates and pen erythritol tetra (meth) acrylates;

 Diethylene glycol (meth) acrylate, triethylene glycol (meta) acrylate, polyethylene glycol (meth) acrylate, dipropylene glycol (meta) acrylate Poly (meth) acrylates of polyoxyalkanolpolyols, such as poly (propylene glycol) (meth) acrylate and diphenyl erythrhexa (meth) acrylate;

 2,2-bis {4- (meth) acryloxyphenyl} propane, 2,2-bis {4- (meth) acryloxyethoxycarbonyl} propane, 2,2-bis {4- ( (Meth) acryloxydiethoxyphenyl} pronon, 2,2-bis {4- (meth) acryloxytriethoxyphenyl} propane, 2,2-bis {4- (meta) co Aromatic di (meta) such as propoxy and 2,2-bis {4- [3- (meth) acryloxy] -2-hydroxypropoxyphenyl} propane A di (meth) acrylate having an aliphatic group or a di (meth) acrylate having an aromatic group;

Aliphatic epoxy di (meth) acrylate or aromatic epoxy di (meth) acrylate; Polyfunctional (meth) acrylates having a urethane bond in the molecule, such as urethane acrylate and urethane acrylate, can be mentioned.

 In the present invention, the following isocyanurate can be used as an example of the multi-sensitive monomer to be filled in the sheath member.

0

N N c C

(I)

 However, in the above formula (I), R is a group represented by the following formula (II).

CH, OOC (X) C = CH.

-(CH ₂ ) _n -NHCOO- CH

CH OOC (X ¹ ) C = CH-

(II)

 In the present invention, when a polyfunctional monomer as described above is used, in the above formula, n is 3 to 10, preferably 4 to 8, and particularly preferably n.

Compounds that are 6 are preferred. In the above formula, X 1 and X ² Is usually an alkyl group, preferably a methyl group.

 These monomers / oligomers may be used alone or as a mixture of two or more components.

 The polymerizable component used in the present invention may contain at least one kind of filler selected from an organic filler, an inorganic filler and an organic composite filler. Blending characteristics and torsion characteristics can be improved by adding a filler.

 As the organic filler, the polymer Z or a monomer Z containing a filler or a cross-linking agent of a powdered polymer obtained by pulverization or dispersion polymerization is polymerized and then pulverized. Can be listed. There is no particular limitation on the monomer / oligomer used as a raw material for the filler that can be used here, and the monomer Z oligomer described above can be mentioned as a preferable example. For example, poly (methyl methacrylate) (PMMA), poly (methyl acrylate), poly (methyl acrylate) pill, poly (butyl methacrylate) (PBMA), polyvinyl acetate (PVAc), polyethylene Examples include glycol (PEG), polypropylene glycol (PPG), and polyvinyl alcohol (PVA).

Examples of the inorganic filler include silica, silica alumina, alumina, alumina quartz, glass (including barium glass), titania, zirconia, calcium carbonate, kaolin, clay, mica, aluminum sulfate, and sulfuric acid. Examples include barium, calcium sulfate, titanium oxide, and phosphoric acid. Examples of the organic composite filler include a filler obtained by polymerizing and coating the surface of the inorganic filler described above with a polymerizable monomer and then pulverizing the polymer. Specifically, fine powder silica or zirconium oxide of the inorganic filler is a polymerizable monomer mainly composed of trimethylolpropane tri (meth) acrylate (TMPT). A filler (TMPT · f) obtained by polymerizing and coating the obtained polymer can be mentioned. The content of the filler is usually 30 to 900 parts by weight, preferably 100 to 900 parts by weight, per 100 parts by weight of the monomer.

0 parts by weight

 Further, a coloring agent such as a pigment or a dye for coloring the cured product may be added to enhance the aesthetics.

 These monomers and Z or a lower polymer are polymerized in the next step to obtain a cured product. In the present invention, light and Z or heat can be used for this polymerization curing. Particularly, in the present invention, it is preferable to use a polyfunctional (meth) acrylate as a main component as a polymerizable component, and these polyfunctional (meth) acrylates are preferably used. Among the rates, it is particularly preferable to use urea (meth) acrylate as a main component (usually at least 50% by weight). By using such polyfunctional (meth) acrylate in an amount of usually at least 50% by weight, preferably at least 90% by weight, the cured product will not have thermoplasticity.

When polymerizing and curing the monomer oligomer component as described above, a polymerization initiator is blended into a polymerizable component.These polymerization initiators include a heat polymerization type, a room temperature chemical polymerization type, and a photopolymerization type. Type, and, These combined dual types are examples.

 Examples of peroxides used in heat polymerization and room temperature chemical polymerization types include, for example, diacetylperoxide, dipropylperoxide, dibutylperoxide, dicaprylperoxide, dilaurylperoxide, dilaurylperoxide, and peroxide. Benzoyl oxide (BP〇), p, p'-Dichlorobenzylyl reoxide, p, p'-Dimethoxybenzoylperoxide, P, p'-Dimethylbenzoylperoxide, P, p '-Organic peroxides such as dinitrodibenzoylperoxide and ammonium persulfate, potassium persulfate, potassium chlorate, lithium bromate and potassium peroxide And other inorganic peroxides. These peroxides are usually used in an amount in the range from 0.01 to 5% by weight, based on the polymerizable component.

 As the boron-containing polymerization initiator among the polymerization initiators, an organic boron compound or a composition containing the same can be generally mentioned.

 Organic boron compounds include, for example, triethyl boron, tripropyl boron, triisopropyl boron, tributyl boron, tri-sec-butyl boron, triisobutyl boron, tripentyl boron, tripentyl boron, Trialkyl borons such as trihexyl boron, trioctyl boron, tridecyl boron, tridodecyl boron, tricyclopentyl boron, tricyclohexyl boron;

Alkoxyalkylborons such as butoxydibutylboron; butyldicyclohexylborane, diisoamylporane, 9-borabi Dialkylboranes such as cyclo [3.3.1] nonane; and

 Examples thereof include compounds in which a part of the above compounds is partially oxidized.

 Furthermore, these compounds can be used in combination. Of these, tributylboron or partially oxidized tripleboron is preferably used.

 As an example of the partially oxidized tributylboron, one obtained by adding 0.3 to 0.9 mol of oxygen to 1 mol of tributylboron is preferably used. These organoboron compounds are usually used in an amount in the range of 0.1% to 50% by weight based on the polymerizable component.

 The polymerization initiator used in the photopolymerization type is a polymerization initiator that can be photopolymerized by irradiation with ultraviolet light or visible light. There is no particular restriction on the polymerization initiator that can be used in the photopolymerization. Ultraviolet or visible light sensitizers such as non, 9,10-anthraquinone, diacetyl, d, l-camphorquinone (CQ), and trimethylbenzoyl diphenyl phosphoxide. These polymerization initiators that can be photopolymerized by irradiating ultraviolet light or visible light generally have a content of 0.01 to 5% by weight based on the polymerizable component. Used in quantity.

When polymerizing and curing by room temperature chemical polymerization or photopolymerization type, a reducing compound can be used in combination. Here, organic reduction Compounds include, for example, N, N-dimethylaniline, 1 ^, 1 ^ -dimethyl-toluidine (DMPT), N, N-Jetyl toluidine, N, N-Jetanol-P-toluene Gin (DEPT), N, N-dimethyl-P-tert-butylaniline, N, N-dimethylanisidine, N, N-dimethyl-P-chloroaniline, N, N-dimethylaminoethyl (meth) Acrylate, N, N-methylaminoethyl (meth) acrylate, N, N-dimethylaminobenzoic acid and its alkyl ester, N, N-ethylaminobenzoic acid (DEABA) and its alkyl ester Aromatic amines such as N, N, N-dimethylaminobenzaldehyde (DMABA d); N-phenylglycine (NPG), N-triglycine (NTG), N, (3-methacrylic acid) Royloxy-2-hydroxypropyl) phenylglycyi (NPG - GMA) can and this in combination, and the like.

 These amine compounds can be used alone or in combination of two or more.

 Examples of the reducing compound include, for example, benzenesulfonic acid, 0-toluenesulfonic acid, P-toluenesulfonic acid, ethyl benzenesulfonic acid, decylbenzenesulfonic acid, and dodecylbenzene. Aromatic sulfinic acids such as benzenesulfuric acid, chlorobenzenesulfuric acid, and naphthorinsulfuric acid or salts thereof can be used in combination.

As the inorganic reducing compound, a sulfur-containing reducing inorganic compound can be preferably used. As such a compound, a reducing inorganic compound used as a redox polymerization initiator is preferable. Examples include acids, bisulfite, metasulfite, metabisulfite, pyrosulfite, thiosulfate, dithionite, 1,2 thionate, hyposulfite, hydrosulfite, and salts thereof. Of these, sulfites are preferably used, and sodium sulfite, potassium sulfite, sodium hydrogen sulfite, and calcium hydrogen sulfite are particularly preferable. These reducing inorganic compounds can be used alone or in combination of two or more. These reducing inorganic compounds are usually used in an amount in the range of 0.01 to 5% by weight based on the polymerizable component.

 In the present invention, the polymerizable component 34 mixed with the polymerization initiator as described above is pressed into the sheath member 33 to thereby guide the polymerizable component filled in the sheath member 33 in advance. Most of the solution 32 is replaced with the polymerizable component 34. However, even if a part of the guide liquid 32 composed of the polymerizable component remains in the sheath member 33, the reactive liquid reacts with the polymerizable component in a later step to form a cured product. I do.

 The polymerizable component containing a polymerization initiator as described above has photopolymerizability or thermopolymerizability, and is cured by irradiation with light or heating. In the present invention, when these polymerizable components are cured, the sheath member 33 is formed, for example, by forming a mold frame 45 or a substantially toothed surface having a molding groove 46 corresponding to a substantially tooth row as shown in FIG. It is fixed to an arc-shaped jig (not shown) corresponding to the row to cure at least a part, preferably most of the polymerizable component.

When curing the polymerizable component by photopolymerization, ultraviolet curing or visible light curing is appropriately selected and used. Polymerization as described above Depending on the type of initiator or sensitizer, the polymer is usually polymerized by irradiating UV light of 200 to 350 nm from a lamp 47 for 0.1 to 30 minutes. About 40% by weight or more of the components polymerize. In the orthodontic wire formed by irradiating ultraviolet rays as described above, the shape substantially corresponding to the dentition is maintained even if it contains an unpolymerized material, but the remaining unreacted material remains unmodified. In order to further react the polymer, heat treatment is preferably performed. In this heat treatment, the orthodontic wire 10 formed by polymerizing at least a part of the polymerizable component is combined with the sheath member 33 at 40 to 300 ° (: preferably 50 to 300 °). Heat for 1 to 60 minutes, preferably for 5 to 30 minutes, at a temperature of 250. Through the heating step, the polymerizable component is further polymerized, and The shape of the orthodontic wire substantially corresponding to the dentition according to the present invention is stabilized, and even when the orthodontic wire is attached, there is almost no possibility that the uncured material or the like is eluted. In addition, when the orthodontic wire of the present invention is manufactured by heat curing, the orthodontic wire can be used more safely and in a predetermined shape together with the sheath member 33 as described above. After molding, it is usually at a temperature of 40 to 150 ^, preferably at a temperature of 50 to 100 ° C; Heat for 60 minutes In this case, the heat curing may be performed in one step or in multiple steps.

 After curing the polymerizable component in this manner, the sheath member and the manufactured orthodontic wire are usually separated.

The orthodontic wire thus formed has an arc portion 11 formed in a semicircular shape, an elliptical shape, a parabolic shape, a suspended curve shape, or the like, and the circular portion 11. It has linear portions 12a and 12b extending almost linearly from both ends lla and lib of the arc portion 11. The size of the orthodontic wire of the present invention only needs to roughly correspond to the dentition of the person who is going to correct the dentition, and the length of the portion indicated by A in FIG. The length indicated by 10 cm and B is 4 to 8 cm. Further, usually, linear portions 12a and 12b are linearly formed from both end portions 11a and lib of the arc portion 11 and are straightened when the orthodontic wire is mounted on a bracket. A part that is cut according to the dentition, and the length of which can be adjusted as appropriate. Force Considering the handling of this orthodontic wire, it is usually 3 to 8 cm, preferably It is desirable to be about 4-5 cm.

 The orthodontic wire according to the present invention thus obtained has a form substantially corresponding to the dentition, and its cross section is such that a continuous glass fiber bundle is impregnated with a polymerizable component. To a hardened state.

Such an orthodontic wire according to the present invention has a deflection load of 1 mm, which is usually in the range of 0.3 to 5 N, preferably 0.3 to 4 N. The load is the number of crossings of the continuous glass fiber bundle, the average diameter of the continuous glass fiber, the number of continuous glass fiber bundles, and the volume content of the cured resin in the wire (volume ratio between the cured resin and the continuous glass fiber bundle). Alternatively, it can be adjusted by changing the diameter of the wire. In other words, this 1 mm deflection load can be adjusted by changing the state of the continuous glass fiber bundle even if the orthodontic wire has the same volume ratio of the hardened body and the continuous glass fiber bundle. Can be. For example, even if continuous glass fiber bundles of the same volume content were used, The use of glass fiber in a wire, such as when it is used as a fiber without being formed, when a continuous glass fiber bundle is used as a twisted yarn, or when a continuous glass fiber bundle is used as a braid The 1 mm deflection load of the orthodontic wire obtained by the difference in the form also differs.

 In general, when designing an orthodontic wire that exhibits a specified orthodontic force (1 mm bending load), the volume content of glass fiber in the wire and the wire diameter can be set arbitrarily, It is calculated by the following equation by multiplying by a coefficient (described later).

P '= [(4 8/ 6 4 - 7r - h - E) / L 3] · D 4 · i

 In the above equation, “E” is the modulus of elasticity (GPa) and is a measured value. “L” is the span for measuring the deflection load and is set to 14 mm in orthodontics. “D” is the diameter (mm) of the wire and is set to any value. “H” is the amount of deflection, and is “1.0 mm” when designing orthodontic wires. “I” is an in vitro coefficient, which is the load retention of 1 mm of deflection when a given orthodontic wire is immersed in artificial saliva. 0.9 ”.

Thus, from the above equation, the lmm deflection load of an orthodontic wire having a certain diameter can be controlled by changing the modulus of this wire. In the orthodontic wire according to the present invention, the elastic modulus is determined by the number of crossings of the continuous glass fiber bundle, the average diameter of the continuous glass fiber, the number of the continuous glass fiber bundle, and the volume content of the cured resin in the wire. Rate (volume ratio of cured resin and continuous glass fiber bundle) And the diameter of the wire can be changed. In the orthodontic wire of the present invention, by changing these, the elastic modulus is usually in the range of 3 to 200 GPa, It can be adjusted preferably in the range of 10 to 80 GPa. As can be seen from the above equation, the 1 mm bending load of the orthodontic wire having the above elastic modulus is 0 ::! It can be controlled to any value within the range of ~ 10N.

 The orthodontic wire of the present invention having such a deflection load is suitable as a wire used in the initial stage of orthodontics in which it is necessary to stably apply a relatively low deflection load.

 In addition, the orthodontic wire of the present invention having such a configuration does not exhibit specific absorption for visible light having a wavelength of 400 nm or more, and emits light in the visible light having a wavelength of 400 nm or more. The transmittance is usually 80% or more. Therefore, the orthodontic wire of the present invention has a white translucent appearance. Even if such an orthodontic wire is wrapped around a plastic or ceramic bracket (almost white) adhered to the tooth surface, the bracket and the orthodontic wire are hardly used in the distance. It is inconspicuous, does not give the feeling of using a metal bracket and a metal wire, and reduces the psychological burden of orthodontic patients.

 In addition, since the orthodontic wire contains substantially no metal, it does not cause metal allergy due to metal elution.

 Furthermore, it does not interfere with tomography (CT, MRI) like metal.

Further, the orthodontic wire according to the present invention has a form substantially corresponding to the dentition. Because of this, the stress applied to the normal dentition can be made uniform in all regions of the wire.

 Although the orthodontic wire of the present invention has been described along with its manufacturing method, it goes without saying that the orthodontic wire of the present invention is not limited by this manufacturing method.

 Further, the orthodontic wire according to the present invention has a form almost corresponding to the dentition to be constituted, and this form is further described in detail. The shape of the straight portion can be a shape specifically exemplified in (a) to (h) of FIG. Industrial applicability

 According to the present invention, a novel orthodontic wire having a form substantially corresponding to a dentition is provided.

 The orthodontic wire according to the present invention is composed of a continuous glass fiber bundle and a cured resin and contains substantially no metal, so that it has excellent esthetics and does not cause metal allergy. .

 Further, since the orthodontic wire of the present invention has an arc-shaped structure substantially corresponding to the dentition to be orthodontic, it is easy to attach to the bracket and does not require orthodontics. The stress applied to the teeth is extremely small, and the teeth to be corrected can be stably applied with the corrective force.

Furthermore, since the orthodontic wire of the present invention can arbitrarily change the deflection load, the use of the orthodontic wire of the present invention is advantageous. Optimal orthodontic power can be applied to the teeth to be corrected.

 In addition, orthodontic wires such as those described above can be formed on the fly to match the dentition of the patient whose orthodontics is to be corrected. Example

 Next, the orthodontic wire of the present invention will be described in more detail by way of examples. The present invention is not limited to these examples.

 Test method

 1. Bending test

 3-point bending test, distance between gauges: 14 mm,

 Crosshead speed: 1 mm

 2. Evening Ibo Dont Method

 The orthodontic wire of the present invention was attached to the orthodontic articulator, and the presence or absence of the orthodontic force was confirmed. Orthodontic appliance immersion temperature 60 ° C

[Example 1]

 Production of C P S A glass fiber

2 4.6 3% by weight,? ₂ 〇 _5; 1 7.4 8 _{wt%, S i O 2; 3} 3.3 9 wt%, A 1 ₂ 0 a; 2 4.2 The raw oxide placed in a platinum crucible in earthenware pots by of 8 wt%, 1 5 The raw material oxide was melted by heating for 3 hours in an electric furnace adjusted to 00 ° C. The raw material glass (CPSA glass) thus melted was taken out of the crucible, cooled, and ground. Separately from the platinum crucible, the crushed material was placed in a platinum crucible having a single hole with an inner diameter of 2.5 mm at the bottom, and heated again in the electric furnace to melt the crushed material.

 At a temperature of 144 ° C, the melt was discharged from a single hole provided at the bottom of the platinum crucible, and the glass yarn was continuously spun at a speed of 450 m / min by a winder. CPSA glass fibers with a diameter of 20 m were produced. The diameter of this CPS A glass fiber was 20 ± 2.0 m.

 The CPSA glass fiber obtained in this manner was immersed in an α-methacryloxypropyltrimethoxysilane solution (cutting agent) for 5 minutes, taken out, dried for 24 hours and dried. They were baked in a high-temperature dryer at 5 ° C for 5 minutes.

Preparation of orthodontic wire by thermal polymerization method

 CPSA glass fiber (diameter: 20 / xm ± 2.0 IB, 32 cm in length, 0.07 g) was dispensed as described above and treated with a hot-shrinkable fiber. When inserting this glass fiber into the tube, one end of the tube was connected to a vacuum device and the inside of the tube was evacuated to a reduced pressure. The CPSA glass fiber bundle was sucked from the other end of the tube and the CPSA glass fiber bundle was inserted into the tube.

Then, while connecting one end of the tube into which the glass fiber was inserted to the vacuum device, suction was further performed, and from the other end of the tube, 30 parts by weight of methyl methacrylate was added to methyl methacrylate. A solution dissolved in 70 parts by weight of a relay (this solution further contains a polymerization initiator and It contains organic peroxides and amines used as such, and is further sucked and defoamed. ) Was suction-filled.

 After filling the polymerizable component in this way, the tube was drawn so that the glass fiber volume content (Vf) force S50% in the obtained orthodontic wire was obtained.

 Next, the tube was fixed with a jig to give an arched shape, and the tube was held together with the jig in a 60 ° C incubator for 60 minutes, and then the temperature was raised to 130 ° C. And then left standing for 60 minutes to carry out heat polymerization.After the above time has elapsed and heat polymerization is completed, remove the orthodontic wire with tube from the jig and attach it to the tube in the length direction. A cut was made at one time and an orthodontic wire corresponding to the dentition was taken out of the tube, and the characteristics of the orthodontic wire were measured.

 Table 1 shows the results.

 The orthodontic wire obtained in this way was translucent white, the surface of the wire was very smooth, and there was no loss due to glass fiber.

 [Example 2]

In Example 1, as a method of inserting the CSPA glass fiber into the tube, instead of using a vacuum device, a thread was previously passed through the tube, and one end of this thread was used to cut the end of the above amount of glass fiber. Bundled, pulled the other end of this thread, and manufactured an orthodontic wire in the same manner except that a method of filling the tube with CSPA glass fiber was used.The strength of the obtained orthodontic wire was measured. As a result, the It was equivalent to a given orthodontic wire.

 [Embodiment 3]

Preparation of orthodontic wire by photopolymerization method (1)

 In Example 1, the amount of glass fiber used was set to 0.5 llg, a fluororesin tube having an inner diameter of 0.56 mm was used as a fluororesin tube, and a diluent was used as a filling liquid. Methacryloxyshethyl) Trimethylhexamethylene diurethane (UDA: manufactured by Shin-Nakamura Chemical Co., Ltd.): 90% by weight, triethylene glycol dimethyl acrylate (TEGDMA, Shin-Nakamura Chemical) A photopolymerizable mixture obtained by adding 0.3% by weight of camphorquinone as a photosensitizer to a mixture of 10% by weight was used. Using the above glass fiber, fluororesin tube, and photopolymerizable mixture, a glass fiber bundle was inserted into the fluororesin tube in the same manner as in Example 1, and the photopolymerizable mixture was further inserted into the tube. The mixture was charged.

 In this way, the tube filled with the photopolymerizable mixture and the glass fiber is fixed in an arched mold, and light is radiated from one end of the tube sequentially with a visible light irradiator to remove the photopolymerizable mixture in the tube. Polymerized. The moving speed of the device for irradiating visible light was about 5 minutes per 20 cm of wire.

 After photopolymerization was performed as described above, a cut was made in the lengthwise direction of the tube at intervals, and the manufactured orthodontic wire was extracted.

The orthodontic wire thus obtained was further heated in a thermostat at 110 ° C. for about 10 minutes to complete the polymerization reaction. The surface of the orthodontic wire obtained in this way was very smooth, and no scorching caused by glass fibers was observed. Table 1 shows the properties of the obtained wire.

 [Example 4]

Preparation of orthodontic wire by photopolymerization method (2)

 Urethane acrylate U6H: Shin-Nakamura Chemical Co., Ltd.): 75% by weight as the polymerizable component to be filled, and triglyceride glycolate (TEGDMA, Shin-Nakamura) Chemical Co., Ltd.): A photopolymerizable mixture obtained by adding 0.3% by weight of camphorquinone and 1.4% by weight of N-phenylidlysine as a photosensitizer to a 25% by weight mixture. The procedure was performed in the same manner as in Example 3 except for the above.

[Examples 5 and 6]

 An orthodontic wire was manufactured in the same manner as in Example 4, except that the volume content (Vf) of the glass fiber was changed to 20% (Example 5) and 60% (Example 6). .

 The surface of the orthodontic wire obtained in this way was very smooth, and no depletion due to glass fibers was observed.

 The characteristics of the obtained orthodontic wire were measured in the same manner. This property is also described in Table 1.

 [Example 6]

In order to evaluate the orthodontic power of the orthodontic wire according to the present invention, the movement of the teeth was observed by the typodont method. As a result, the orthodontic wires used in Examples 1 to 5 had sufficient orthodontic power. 【table 1 】

Diameter Vf Flexural modulus Bending strength fes 1 mm isj Maximum deflection (mm) (%) (Gpa) (MPa) (N) (mm) Example 1 0.50 50 4 0 1 1 5 0 2.8 1 .9 Example 5 0.50 20 2 2 5 0 0 1 .8 2 2 Example 3 0.50 50 4 2 1 2 0 0 2 .8 1 .9 Example 4 4 0.45 30 2 3 7 0 0 0 .8 0 3 .7 Example 6 0.50 60 5 0 1 4 0 0 3 .0 1.8

Claims

Claim scope

1. After the continuous glass fiber bundle is inserted into the synthetic resin sheath member, a polymerizable component is injected into the synthetic resin sheath member, and then the synthetic resin sheath member is formed into an arc shape substantially corresponding to the dentition. A method for producing an orthodontic wire having a form substantially corresponding to a dentition by polymerizing and curing at least a part of the polymerizable component filled in the synthetic resin sheath member.

 2. After inserting the continuous glass fiber bundle into a mold having a concave portion having an arc shape substantially corresponding to the tooth row, inject the polymerizable component into the mold, and then polymerize the mold. A method for producing an orthodontic wire having a form substantially corresponding to the dentition by polymerizing and curing at least a part of the sexual component.

 3. Before inserting the continuous glass fiber bundle into a synthetic resin sheath member or into a mold having a concave portion having an arc shape substantially corresponding to a tooth row, the glass fiber bundle is impregnated with a polymerizable component in advance, A polymerizable component impregnated in the glass fiber bundle or at least a part of the polymerizable component is polymerized and hardened to produce a continuous glass fiber bundle, and the continuous glass fiber bundle containing the polymerizable component is converted into a sheath member. Alternatively, a method for producing an orthodontic wire, wherein the polymerizable component is further hardened after being inserted into a mold.

4. The method for producing an orthodontic wire according to any one of claims 1 to 3, wherein the polymerizable component is a photopolymerizable resin-forming component.

5. The method for producing an orthodontic wire according to any one of claims 1 to 3, wherein the polymerizable component is a thermopolymerizable resin-forming component.

 6. Before inserting the above continuous glass fiber bundle into a synthetic resin sheath member or into a mold having a concave part having an arc-like shape corresponding to a tooth row, impregnate the glass fiber bundle with a polymerizable component in advance. The polymerizable component or at least a part of the polymerizable component impregnated in the glass fiber bundle is polymerized and cured to produce a continuous glass fiber bundle, and the continuous glass fiber containing the polymerizable component is sheathed or The method for producing an orthodontic wire according to any one of claims 1 to 5, wherein a polymerizable component is further injected after being inserted into the mold.

 7. The polymerizable component is a light and heat polymerizable resin forming component, and the polymerizable resin forming component is irradiated with light to polymerize and cure at least a part of the polymerizable resin forming component. 4. The method for producing an orthodontic wire according to claim 3, wherein a polymerizable component remaining in the synthetic resin sheath member is polymerized and cured by heat treatment.

 8. The method for producing an orthodontic wire according to claim 1, wherein after the polymerizable component is polymerized and cured, the synthetic resin sheath member and the wire are separated.

 9. The method for producing an orthodontic wire according to claim 1, wherein the continuous glass fiber bundle is a glass fiber bundle composed of at least two continuous glass fibers.

10. The inner diameter of the hollow portion of the synthetic resin sheath member is 0. The method for producing an orthodontic wire according to claim 1, wherein the distance is in a range of 1 to 2.0 mm.

 11. The orthodontic wire according to claim 1 or 2, wherein the synthetic resin sheath member or mold is formed of a light-transmitting synthetic resin or a transparent mold. Manufacturing method.

 12. When manufacturing the orthodontic wire, the orthodontic wire manufacturing member is formed into an arcuate shape along the dentition, and then the polymerizable component is cured inside or outside the oral cavity. And a method for manufacturing an orthodontic wire.

 13. An orthodontic wire comprising a continuous glass fiber bundle and a cured polymerizable component impregnated in the continuous glass fiber bundle, and an orthodontic wire comprising the continuous glass fiber bundle and a cured product of the polymerizable component. An orthodontic wire, characterized in that a shape corresponding to a substantially dentition is added to the orthodontic wire.

 14. The orthodontic wire has a semicircular arc portion and a linear portion extending substantially linearly from both ends of the arc portion. 13. The orthodontic wire according to item 3.

 15. The continuous glass fiber bundle is formed from a plurality of continuous glass fibers or a glass fiber bundle composed of at least two continuous glass fibers, and the continuous glass fiber or the glass fiber bundle is 14. The orthodontic tire according to claim 13, wherein the orthodontic teeth cross each other.

16. The glass fiber according to claim 13 or 15, wherein the average diameter of one glass fiber is in the range of 1.0 to 100 Lm. An orthodontic wire as described.

 17. The orthodontic wire according to claim 13 or 15, wherein the volume content of the glass fiber in the orthodontic wire is in a range of 5 to 90%. one.

 1 8. The 1mm deflection load of the above orthodontic wire is 0.1 ~

The method according to any one of claims 13, 15, 16, or 17, wherein the value can be adjusted to any value within the range of 10 N. Orthodontic wire.

1 9. The glass fiber _{strength, CaO-P 2 0 5 -Si0} 2 -Al 2 03 system first claim 1, characterized in that it is a glass fiber biomaterials section 3 or the teeth of the first 5 Claims Straightening wire.

 20. The orthodontic wire according to claim 13, wherein a cross-sectional shape of the orthodontic wire is circular, oval, semi-circular, square or polygonal.

 2 1. The maximum cross length of the cross section of the orthodontic wire is

The orthodontic wire according to claim 13, wherein the orthodontic wire is within a range of 0.1 to 2 mm.

 22. The orthodontic wire according to claim 13, wherein an elastic modulus of the orthodontic wire is in a range of 3 to 200 GPa.

23. The orthodontic wire according to claim 13, wherein the filler is contained in an amount of 30 to 95 parts by weight based on 100 parts by weight of the polymerizable monomer in the polymerizable component.

24. An orthodontic wire-manufacturing member characterized in that a continuous glass fiber bundle is inserted into a synthetic resin sheath member and a photopolymerizable component is injected.