JP2000060871A - Dental matrix - Google Patents
Dental matrixInfo
- Publication number
- JP2000060871A JP2000060871A JP10233850A JP23385098A JP2000060871A JP 2000060871 A JP2000060871 A JP 2000060871A JP 10233850 A JP10233850 A JP 10233850A JP 23385098 A JP23385098 A JP 23385098A JP 2000060871 A JP2000060871 A JP 2000060871A
- Authority
- JP
- Japan
- Prior art keywords
- dental
- plastic film
- matrix
- restorative material
- thickness
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C5/00—Filling or capping teeth
- A61C5/80—Dental aids fixed to teeth during treatment, e.g. tooth clamps
- A61C5/85—Filling bands, e.g. matrix bands; Manipulating tools therefor
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、歯科治療におい
て、歯牙に生じたう触や欠損部に窩洞形成を行った後、
歯科用修復材にて修復を行う際に使用する歯科用マトリ
ックスに関するものである。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a dental treatment, in which a cavity is formed in a caries or a defect portion of a tooth,
The present invention relates to a dental matrix used when performing restoration with a dental restorative material.
【０００２】[0002]
【従来の技術】歯牙に生じたう蝕や欠損等の修復は、先
ずう蝕や欠損部に窩洞を成形した後、その窩洞内部に歯
科用コンポジットレジンや歯科用グラスアイオノマーセ
メント等の歯科用修復材を充填して硬化させ、超微粒子
ダイヤモンドポイント等を用いて修復物の形態の修正を
行い、更にシリコーンカップ等を使用して表面を研磨す
ることで行われている。このように成形した窩洞内部に
歯科用修復材を充填して硬化させる際に、比較的粘性の
ある硬化前の歯科用修復材が充填や重合操作時に使用す
る歯科用のインスツルメントや光重合器等に付着するこ
とを防ぎ、歯科用修復材の形態付与作業や重合操作を行
い易くする目的で、歯科用マトリックスと称される主に
長方形で柔軟性のある厚さ10μｍ〜60μｍ程度の薄膜状
物が使用されている。2. Description of the Related Art To repair caries or defects in teeth, first form a cavity in the caries or defects, and then restore the dental composite resin or dental glass ionomer cement to the interior of the cavity. It is performed by filling and hardening the material, correcting the shape of the restoration using ultrafine diamond points, etc., and then polishing the surface using a silicone cup or the like. When filling and curing the dental restorative material inside the cavity thus formed, the relatively viscous dental restorative material before curing is used for dental instruments and photopolymerization used during filling and polymerization operations. A thin film with a thickness of 10 μm to 60 μm, which is mainly rectangular and has a flexibility, which is referred to as a dental matrix, for the purpose of preventing it from adhering to a vessel or the like and facilitating the morphological work or the polymerization operation of the dental restorative material. Are used.
【０００３】窩洞内への充填修復に於ける歯科用マトリ
ックスの使用方法としては、Ｉ級窩洞及びIII級窩洞の
場合には、窩洞内に歯科用修復材を歯科用インスツルメ
ントを使用して気泡が混入しないように注意深く充填し
た後、前記柔軟性を有する薄膜状物である歯科用マトリ
ックスを硬化前の歯科用修復材表面に密着するように押
し当てることにより、歯科用マトリックスを窩洞外面の
型とし、歯科用マトリックスを押し当てたまま窩洞内の
歯科用修復材料を重合する方法が一般に行われている。
また、II級窩洞，IV級窩洞及びＶ級窩洞に使用する場合
のように歯牙の隣接面を含む窩洞の修復の場合には、窩
洞内に歯科用修復材を歯科用インスツルメントを使用し
て気泡が混入しないように注意深く充填した後、前記柔
軟性を有する薄膜状物である歯科用マトリックスを治療
する歯牙に巻き付けるようにしたり、治療を行う歯牙と
その隣接歯との間に挟むことで歯科用マトリックスを窩
洞外面の型とし、歯科用マトリックスを装着したまま窩
洞内の歯科用修復材料を重合する方法が一般に行われて
いる。As a method of using the dental matrix in the restoration of filling into the cavity, in the case of the class I cavity and the class III cavity, a dental restoration material is used in the cavity by using a dental instrument. After carefully filling so that air bubbles do not mix, the dental matrix, which is a thin film having flexibility, is pressed against the surface of the dental restorative material before hardening so as to adhere the dental matrix to the outer surface of the cavity. It is common practice to mold the dental restorative material in the cavity while pressing the dental matrix into the mold.
In addition, in the case of repairing a cavity containing the adjacent surfaces of teeth, such as when used in a class II cavity, a class IV cavity, and a class V cavity, a dental restoration material is used in the cavity and a dental instrument is used. After carefully filling so that air bubbles do not mix, the dental matrix, which is a thin film having flexibility, may be wrapped around the tooth to be treated or sandwiched between the tooth to be treated and its adjacent tooth. A general method is to use a dental matrix as a mold for the outer surface of the cavity and polymerize the dental restorative material in the cavity while the dental matrix is still attached.
【０００４】このように歯科用マトリックスを使用する
と、歯科用修復材を窩洞内へ充填して硬化させる際に硬
化前の歯科用修復材が歯科用のインスツルメントや光重
合器に付着し変形することを防ぎ、各操作を容易に行う
ことができる。更に、硬化前の歯科用修復材が隣接歯へ
接触することを防ぐ効果もある。When the dental matrix is used as described above, when the dental restorative material is filled into the cavity and hardened, the dental restorative material before hardening adheres to the dental instrument or the photopolymerizer and is deformed. It is possible to prevent each operation and easily perform each operation. Further, it also has an effect of preventing the dental restorative material before hardening from contacting adjacent teeth.
【０００５】歯科用マトリックスの材質としては、ステ
ンレスやアルミ等の金属製箔のものと、ポリエステルや
ポリエチレンのフィルムを基材とした有機化合物系のプ
ラスチックフィルムのものとに大別することができる。Materials for the dental matrix can be roughly classified into those made of metal foil such as stainless steel and aluminum, and those made of organic compound type plastic film having a polyester or polyethylene film as a base material.
【０００６】光照射を行う必要がない歯科用セメントや
化学重合型の歯科用コンポジットレジン等を使用する場
合には、ステンレスやアルミ等から成る金属製箔及び前
記した如き有機化合物系のプラスチックフィルム等が使
用目的に合わせて使用されている。また、光重合型の歯
科用コンポジットレジンや歯科用グラスアイオノマーセ
メントのように硬化するために光照射を行うことが必要
である歯科用修復材を用いる場合は、歯科用マトリック
スには光をより多く通す特性が要求されるため、光重合
型の歯科用修復材に光照射される光を通す透明又は半透
明等のプラスチックフィルムを材質とした歯科用マトリ
ックスが使用されている。When a dental cement that does not need to be irradiated with light, a chemically-polymerized dental composite resin, or the like is used, a metal foil made of stainless steel, aluminum, or the like, and an organic compound-based plastic film as described above are used. Is used according to the purpose of use. Also, when using a dental restorative material that needs to be irradiated with light to cure like a photopolymerizable dental composite resin or dental glass ionomer cement, the dental matrix contains more light. Due to the requirement of a transparent property, a dental matrix made of a transparent or semi-transparent plastic film that transmits the light irradiated to the photopolymerizable dental restorative material is used.
【０００７】このような歯科用マトリックスを使用しな
い場合やプラスチックフィルムから成る歯科用マトリッ
クスを使用する場合において、歯科用修復材として化学
重合型や光重合型の歯科用コンポジットレジンや光重合
型の歯科用グラスアイオノマーセメント等の重合可能な
レジン成分を含む歯科用修復材を使用して歯牙に生じた
う蝕や欠損等の修復を行った場合に、歯科用修復材に充
分な硬化特性が得られない現象が起きることが指摘され
ている。この現象により表面硬度の低下した層は、経時
的に歯科用修復材表面の微少欠損や摩耗を引き起こし、
修復面の面荒れによる審美性の低下等を生じる要因とな
っていた。When such a dental matrix is not used or when a dental matrix made of a plastic film is used, a chemical polymerization type or photopolymerization type dental composite resin or a photopolymerization type dental is used as a dental restorative material. When a dental restoration material containing a polymerizable resin component, such as glass ionomer cement for dental use, is used to repair dental caries, defects, etc. that occur on teeth, sufficient curing characteristics can be obtained for the dental restoration material. It has been pointed out that no phenomenon occurs. Due to this phenomenon, the layer with reduced surface hardness causes minute defects and wear on the surface of the dental restorative material over time,
It was a factor causing deterioration of aesthetics due to the roughened surface of the repaired surface.
【０００８】このように従来のプラスチックフィルムを
材質とした歯科用マトリックスを用いた場合には、表面
硬度の低下した層（以下、低重合層と言う）が硬化表面
で発生していたが、咬合面であるＩ級窩洞又は切削ポイ
ントが比較的届き易い歯牙の頬側面や舌側面では、予め
歯科用修復材を多めに盛り上げるような充填を行うこと
で硬化後の形態修正の際に低重合層を超微粒子ダイヤモ
ンドポイント等で削除することができる。ところが、隣
接面を含む歯牙の修復では予め歯科用修復材を多めに盛
り上げるような充填は臨床的に不可能であるため、低重
合層の発生を生じない歯科用マトリックスが望まれてい
たのである。As described above, when the conventional dental matrix made of a plastic film was used, a layer having a reduced surface hardness (hereinafter referred to as a low polymerization layer) was generated on the hardened surface. On the buccal side and lingual side of the tooth where the class I cavity or the cutting point is relatively easy to reach, by filling the dental restorative material with a large amount in advance, a low polymerization layer at the time of morphological correction after hardening. Can be deleted with ultrafine diamond points or the like. However, since it is not clinically possible to fill up the dental restorative material with a large amount in advance in restoration of teeth including adjacent surfaces, a dental matrix that does not generate a low polymerization layer has been desired. .
【０００９】[0009]
【発明が解決しようとする課題】そこで本発明は、歯科
用修復材表面に低重合層を殆ど発生させることなく歯科
用修復材を硬化させることが可能な歯科用マトリックス
を提供することを課題とする。SUMMARY OF THE INVENTION It is therefore an object of the present invention to provide a dental matrix capable of curing a dental restorative material while hardly generating a low polymerization layer on the surface of the dental restorative material. To do.
【００１０】[0010]
【課題を解決するための手段】本発明者らは前記課題の
解決に鋭意努めた結果、前記低重合層が発生する原因
は、化学重合型や光重合型の歯科用コンポジットレジン
や光重合型の歯科用グラスアイオノマーセメント等の重
合可能なレジン成分を含む歯科用修復材の重合時に大気
に触れている面で大気中の酸素によってレジン成分であ
るモノマー等の重合が阻害され、充分な硬化特性が得ら
れない現象が起きて低重合層が発生すると考えた。As a result of diligent efforts to solve the above problems, the present inventors have found that the cause of the low polymerization layer is a chemical polymerization type or photopolymerization type dental composite resin or photopolymerization type dental composite resin. In the surface of the dental restorative material containing a polymerizable resin component such as dental glass ionomer cement that is exposed to the atmosphere during the polymerization, oxygen in the atmosphere inhibits the polymerization of the monomer that is the resin component, resulting in sufficient curing characteristics. It was considered that a low polymerization layer was generated due to the phenomenon that the above phenomenon was not obtained.
【００１１】そこで、従来のポリエチレンやポリエチレ
ンテレフタレート等のプラスチックフィルムを材質とし
た歯科用マトリックスについて検討した結果、厚さ20μ
mの時の酸素の透過度が約80（ポリエチレンテレフタレ
ート）〜約4000（ポリエチレン）（cc／ｍ2 24hrs at
m）と多く、酸素の遮断が充分ではなかったため、これ
らの歯科用マトリックスをコンポジットレジン等の修復
材表面と密着させて修復材表面を大気から隔離しようと
しても、マトリックスを透過してくる酸素によって歯科
用修復材表面の重合阻害が起きてしまい、低重合層が発
生して硬化後の歯科用修復材表面に悪影響を与えていた
ことを究明したのである。Therefore, as a result of studying a conventional dental matrix made of a plastic film such as polyethylene or polyethylene terephthalate, it was found that the thickness was 20 μm.
Oxygen permeability at m is about 80 (polyethylene terephthalate) to about 4000 (polyethylene) (cc / m 2 24hrs at
m) and the oxygen was not sufficiently blocked, so even if these dental matrices were made to adhere to the surface of the restorative material such as composite resin to isolate the restorative material surface from the atmosphere, the oxygen permeating through the matrix It was determined that polymerization inhibition on the surface of the dental restorative material occurred, and a low polymerization layer was generated, which had a bad influence on the surface of the dental restorative material after curing.
【００１２】この究明に基づいて、本発明者らは前記課
題を解決するには、歯科用マトリックスの材質をその厚
さが20μmの時の酸素透過度（Ｏ2ＧＴＲ）が５０（cc／
ｍ224hrs atm）以下であるプラスチックフィルムとする
ことにより、従来の歯科用マトリックスとしての機能を
損なうことなく、歯科用修復材表面に酸素の重合阻害に
よって生じる低重合層の発生が非常に少ない歯科用マト
リックスとすることができることを究明して本発明を完
成したのである。Based on this investigation, the inventors of the present invention can solve the above problems by using a material for the dental matrix having an oxygen permeability (O 2 GTR) of 50 (cc / cc / cc) when the thickness is 20 μm.
By using a plastic film of m 2 24hrs atm) or less, a dental polymer with a very low generation of a low-polymerization layer caused by the inhibition of oxygen polymerization on the surface of the dental restorative material without impairing its function as a conventional dental matrix. The present invention has been completed by researching that it can be used as a matrix for use.
【００１３】[0013]
【発明の実施の形態】本発明に係る歯科用マトリックス
は、その厚さが20μmの時の酸素透過度（Ｏ2ＧＴＲ）が
５０（cc／ｍ2 24hrs atm）以下であるプラスチックフ
ィルムから成ることを特徴とする歯科用マトリックスで
ある。BEST MODE FOR CARRYING OUT THE INVENTION The dental matrix according to the present invention comprises a plastic film having an oxygen permeability (O 2 GTR) of 50 (cc / m 2 24 hrs atm) or less when its thickness is 20 μm. Is a dental matrix characterized by:
【００１４】歯科用マトリックスに於いて、その厚さが
20μmの時の酸素透過度が５０（cc／ｍ2 24hrs atm）以
下であると、歯科用マトリックスとして使用される厚さ
10μｍ〜60μｍの時の酸素遮断効果を得ることができ、
硬化後の歯科用修復材表面に発生する低重合層を非常に
少なくすることができるのである。特に、その厚さが20
μmの時の酸素透過度が２０（cc／ｍ2 24hrs atm）以下
であると、厚さ10μｍ〜60μｍの時の酸素遮断効果が充
分となって低重合層が発生しないためより好ましい。そ
して、そのプラスチックフィルムは、光重合型の歯科用
修復材に光照射される光を通す透明又は半透明等のプラ
スチックフィルムであることが好ましい。In the dental matrix, its thickness is
When the oxygen permeability at 20 μm is 50 (cc / m 2 24hrs atm) or less, the thickness used as a dental matrix
Oxygen blocking effect can be obtained at 10 μm to 60 μm,
The low polymerization layer generated on the surface of the dental restorative material after curing can be extremely reduced. Especially, its thickness is 20
When the oxygen permeability is 20 (cc / m 2 24 hrs atm) or less when the thickness is μm, the oxygen blocking effect is sufficient when the thickness is 10 μm to 60 μm, and the low polymerization layer is not generated, which is more preferable. The plastic film is preferably a transparent or semi-transparent plastic film that allows the light irradiated to the photopolymerizable dental restorative material to pass therethrough.
【００１５】その厚さが20μmの時の酸素透過度（Ｏ2Ｇ
ＴＲ）が５０（cc／ｍ2 24hrs atm）以下であるプラス
チックフィルムとしては、ポリアミド（厚さが20μmの
時の酸素透過度：３５cc／ｍ2 24hrs atm），ポリ塩化
ビニリデン（厚さが20μmの時の酸素透過度：３０cc／
ｍ2 24hrs atm），塩化ビニリデンコートポリプロピレ
ン（厚さが20μmの時の酸素透過度：１２cc／ｍ2 24hrs
atm），ポリアクリロニトリル（厚さが20μmの時の酸
素透過度：１１cc／ｍ2 24hrs atm），酸化ケイ素コー
トポリエチレン（厚さが20μmの時の酸素透過度：７cc
／ｍ2 24hrs atm），酸化アルミニウムコートポリエチ
レン（厚さが20μmの時の酸素透過度：２cc／ｍ2 24hrs
atm），ポリテトラフロロエチレン（厚さが20μmの時
の酸素透過度：１.５cc／ｍ2 24hrs atm），ポリエチレ
ンビニルアルコール（厚さが20μmの時の酸素透過度：
０.２cc／ｍ2 24hrs atm）等を例示することができる。Oxygen permeability (O 2 G when the thickness is 20 μm)
As a plastic film having a TR of 50 (cc / m 2 24hrs atm) or less, polyamide (oxygen permeability at a thickness of 20 μm: 35 cc / m 2 24hrs atm), polyvinylidene chloride (thickness of 20 μm) Oxygen transmission rate: 30cc /
m 2 24hrs atm), vinylidene chloride coated polypropylene (oxygen permeability when the thickness is 20 μm: 12 cc / m 2 24hrs
atm), polyacrylonitrile (oxygen permeability when the thickness is 20 μm: 11 cc / m 2 24 hrs atm), silicon oxide coated polyethylene (oxygen permeability when the thickness is 20 μm: 7 cc
/ M 2 24hrs atm), aluminum oxide coated polyethylene (oxygen permeability when the thickness is 20μm: 2cc / m 2 24hrs
atm), polytetrafluoroethylene (oxygen permeability when the thickness is 20 μm: 1.5 cc / m 2 24 hrs atm), polyethylene vinyl alcohol (oxygen permeability when the thickness is 20 μm:
0.2 cc / m 2 24 hrs atm) and the like can be exemplified.
【００１６】本発明に係る歯科用マトリックスの形状
は、従来の歯科用マトリックスと同様であり、厚さ10μ
ｍ〜60μｍ、外形は幅５mm〜１５mm程度，長さが２０〜
１８０mm程度の長方形、又は術者によって希望の長さに
切って使用される厚さ10μｍ〜60μｍ、幅５mm〜１５mm
程度のテープ状のものが好ましく使用できる。The shape of the dental matrix according to the present invention is the same as that of the conventional dental matrix, and the thickness is 10 μm.
m ~ 60μm, outer shape is about 5mm ~ 15mm, length is 20 ~
A rectangle of about 180 mm or a thickness of 10 μm to 60 μm and a width of 5 mm to 15 mm used by the operator to cut it to a desired length
A tape-shaped tape is preferably used.
【００１７】[0017]
【実施例】以下、実施例を挙げて本発明に係る歯科用マ
トリックスを具体的に説明するが本発明はこれらに限定
されるものではない。なお、各測定は以下のように行っ
た。EXAMPLES Hereinafter, the dental matrix according to the present invention will be specifically described with reference to examples, but the present invention is not limited thereto. In addition, each measurement was performed as follows.
【００１８】＜酸素透過度の測定＞歯科用マトリックス
として使用される各プラスチックフィルムについて、JI
SK 7126により測定した酸素透過度の値を表１に纏めて
表記する。<Measurement of Oxygen Permeability> For each plastic film used as a dental matrix, JI
The values of oxygen permeability measured by SK 7126 are collectively shown in Table 1.
【００１９】＜ヌープ硬さ率の測定＞歯科用修復材とし
て、歯科用光重合型コンポジットレジン（商品名：エス
ティオＬＣ，ジーシー社製）を用い、この歯科用コンポ
ジットレジンを製品シリンジから押し出して、内径１１
mm，深さ４mmの金型内に充填した。そしてこの金型内に
充填した歯科用修復材を歯科用マトリックスの材質であ
るプラスチックフィルムを介してガラス板で圧接し、硬
化面にそのプラスチックフィルムを密着させ平面化した
後、ガラス板を外しプラスチックフィルム上面方向から
可視光線照射器（商品名：ラボライトＬＶ-II，ジーシ
ー社製）にて５分間光照射を行って歯科用修復材を硬化
させた。しかる後、プラスチックフィルムを取り除き、
金型内から取り出した硬化した歯科用修復材をそのプラ
スチックフィルムで被覆されていた上面側から底面側に
かけて中央部をダイヤモンドカッター（商品名：ISOMET
2000，BUEHLER社製）で切断し、切断面のプラスチック
フィルムで被覆されていた側から０.１mm，０.６mm，
１.１mmの深さのヌープ硬度を測定した。切断面の各試
料で被覆されていた側の硬化表面から１.１mmの深さの
ヌープ硬度を基準として、硬化表面から０.１mm，０.６
mmの各測定深さのヌープ硬度をヌープ硬さ率（％）で評
価した。<Measurement of Knoop hardness ratio> As a dental restorative material, a dental photopolymerizable composite resin (trade name: Estio LC, manufactured by GC Corporation) was used, and this dental composite resin was extruded from a product syringe, Inner diameter 11
It was filled in a mold with a depth of 4 mm and a depth of 4 mm. Then, the dental restorative material filled in the mold is pressure-contacted with a glass plate through a plastic film which is a material of the dental matrix, and the plastic film is brought into close contact with the cured surface to make it flat, and then the glass plate is removed to remove the plastic. The dental restorative material was cured by irradiating light for 5 minutes from the direction of the upper surface of the film with a visible light irradiator (trade name: Labolite LV-II, manufactured by GC Corporation). After that, remove the plastic film,
The hardened dental restoration material taken out from the mold was covered with the plastic film. From the top side to the bottom side, the central part was diamond cutter (Product name: ISOMET
2000, manufactured by BUEHLER) and cut from the side covered with the plastic film of the cut surface to 0.1 mm, 0.6 mm,
The Knoop hardness at a depth of 1.1 mm was measured. Based on the Knoop hardness at a depth of 1.1 mm from the hardened surface of the cut surface, which was covered with each sample, 0.1 mm from the hardened surface, 0.6
The Knoop hardness at each measurement depth of mm was evaluated by the Knoop hardness ratio (%).
【００２０】＜歯ブラシ磨耗率の測定＞歯科用修復材と
して、歯科用光重合型コンポジットレジン（商品名：ク
リアフィルＡＰＸ，クラレ社製）を用い、この歯科用コ
ンポジットレジンを製品シリンジから押し出して、内径
１１mm，深さ４mmの金型内に充填した。そしてこの金型
内に充填した歯科用修復材を歯科用マトリックスの材質
であるプラスチックフィルムを介してガラス板で圧接
し、硬化面にそのプラスチックフィルムを密着させ平面
化した後、片側上方より可視光線照射器（商品名：Opti
lux 400，クラレ社製）にて全体に光が当たるように５
分間光照射を行って歯科用修復材を硬化させた。しかる
後、プラスチックフィルムを取り除き、金型内から取り
出した硬化した歯科用修復材をそのプラスチックフィル
ムで被覆されていた試験片の上面側を歯ブラシ摩耗器
（東京技研社製）に固定し、飽和炭酸カルシウム懸濁液
中で歯ブラシ（商品名：プロスペック，ジーシー社製）
を滑走距離５０mm、荷重５００gfで10000回往復運動さ
せて磨耗量を重量で測定し、測定前の重量に対する歯ブ
ラシ摩耗率（％）として評価した。<Measurement of Toothbrush Abrasion Rate> As a dental restorative material, a dental photopolymerizable composite resin (trade name: Clearfil APX, manufactured by Kuraray Co., Ltd.) was used, and this dental composite resin was extruded from a product syringe. It was filled in a mold having an inner diameter of 11 mm and a depth of 4 mm. Then, the dental restoration material filled in this mold is pressure-contacted with the glass plate through the plastic film which is the material of the dental matrix, and the plastic film is brought into close contact with the cured surface to make it flat, and then visible light is applied from above one side. Irradiator (Product name: Opti
lux 400, made by Kuraray Co., Ltd.)
The dental restorative material was cured by light irradiation for minutes. Then, the plastic film was removed, and the hardened dental restorative material taken out from the mold was fixed to the toothbrush wearer (manufactured by Tokyo Giken Co., Ltd.) with the upper surface side of the test piece covered with the plastic film, and saturated carbonic acid. Toothbrush in calcium suspension (trade name: Prospec, manufactured by GC)
Was reciprocated 10,000 times with a sliding distance of 50 mm and a load of 500 gf, and the amount of wear was measured by weight. The toothbrush wear rate (%) was evaluated with respect to the weight before measurement.
【００２１】[0021]
【表１】 [Table 1]
【００２２】[0022]
【発明の効果】表１から明らかな如く、本発明に係る歯
科用マトリックスはその厚さが20μｍの時の酸素透過度
（Ｏ2ＧＴＲ）が５０（cc／ｍ2 24hrs atm）以下である
プラスチックフィルムとすることにより、歯科用マトリ
ックスとしての機能を損なうことがないばかりか、歯科
用修復材表面に低重合層を殆ど生ぜず、歯科用修復材表
面の硬度低下を起こさない歯科用マトリックスであるこ
とが確認できた。このことは特に隣接面を含む窩洞の修
復等の歯科用修復材表面の低重合層が削除できない場合
において問題とされていた経時的な歯科用修復材表面の
微少欠損，摩耗，歯科用修復材表面の面荒れによる歯科
用修復材料の審美性低下等を防ぐことが可能であること
を意味している。そして、特にその厚さが20μｍの時の
酸素透過度（Ｏ2ＧＴＲ）が２０（cc／ｍ2 24hrs atm）
以下であるプラスチックフィルムの場合には、歯科用修
復材表面の低重合層が生じる程度が非常に低く、しかも
歯科用修復材表面の硬度低下の割合も非常に低い歯科用
マトリックスであることが確認できたのであり、またプ
ラスチックフィルムが光重合型の歯科用修復材に光照射
される光を通す透明又は半透明等のプラスチックフィル
ムであることが化学重合型と光重合型の歯科用修復材の
何れにも使用可能であるので好ましいのである。かかる
効果を奏する本発明に係る歯科用マトリックスの歯科分
野に貢献する価値の非常に大きなものである。As is apparent from Table 1, the dental matrix according to the present invention is a plastic having an oxygen permeability (O 2 GTR) of 50 (cc / m 2 24 hrs atm) or less when its thickness is 20 μm. By forming a film, the function of the dental matrix is not impaired, and a low polymerization layer is hardly formed on the surface of the dental restorative material, and the hardness of the surface of the dental restorative material is not lowered. I was able to confirm that. This has been a problem especially when the low-polymerization layer on the surface of the dental restorative material cannot be removed, such as when repairing the cavity including the adjacent surface. This means that it is possible to prevent deterioration of aesthetics of the dental restorative material due to surface roughness. And, especially when the thickness is 20 μm, the oxygen permeability (O 2 GTR) is 20 (cc / m 2 24hrs atm)
In the case of the following plastic films, it was confirmed that the degree of formation of a low polymerization layer on the surface of the dental restorative material is extremely low, and the rate of hardness decrease on the surface of the dental restorative material is also very low. Moreover, the fact that the plastic film is a transparent or semi-transparent plastic film through which light is irradiated to the photopolymerization type dental restorative material It is preferable because it can be used for both. The dental matrix according to the present invention having such an effect is of great value in contributing to the dental field.
Claims (3)
際に使用する歯科用マトリックスであって、その厚さが
20μmの時の酸素透過度（Ｏ2ＧＴＲ）が５０（cc／ｍ2
24hrs atm）以下であるプラスチックフィルムから成る
ことを特徴とする歯科用マトリックス。1. A dental matrix used when a tooth is restored using a dental restorative material, the thickness of which is a matrix.
Oxygen permeability (O 2 GTR) at 20 μm is 50 (cc / m 2
A dental matrix comprising a plastic film having a thickness of 24 hrs atm) or less.
ＧＴＲ）が２０（cc／ｍ2 24hrs atm）以下である請求
項１に記載の歯科用マトリックス。2. The oxygen permeability (O 2 when its thickness is 20 μm).
The dental matrix according to claim 1, which has a GTR of 20 (cc / m 2 24 hrs atm) or less.
用修復材に光照射される光を通す透明又は半透明等のプ
ラスチックフィルムである請求項１又は２に記載の歯科
用マトリックス。3. The dental matrix according to claim 1 or 2, wherein the plastic film is a transparent or semitransparent plastic film that allows light to be irradiated onto the photopolymerizable dental restorative material.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP10233850A JP2000060871A (en) | 1998-08-20 | 1998-08-20 | Dental matrix |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP10233850A JP2000060871A (en) | 1998-08-20 | 1998-08-20 | Dental matrix |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JP2000060871A true JP2000060871A (en) | 2000-02-29 |
Family
ID=16961560
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP10233850A Pending JP2000060871A (en) | 1998-08-20 | 1998-08-20 | Dental matrix |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JP2000060871A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2015096243A (en) * | 2015-01-29 | 2015-05-21 | 直樹 丸矢 | Swinging tooth fixing structure |
| US9192452B2 (en) | 2011-08-25 | 2015-11-24 | King Saud University | Plastic clear band for dental restorations |
| CN113639696A (en) * | 2021-08-11 | 2021-11-12 | 牡丹江医学院 | Tooth exploration device |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH07261400A (en) * | 1994-03-22 | 1995-10-13 | Konica Corp | Image forming material |
| JPH0839718A (en) * | 1994-07-27 | 1996-02-13 | Kureha Chem Ind Co Ltd | Vacuum-deposited composite film and its production |
| JPH0841044A (en) * | 1994-07-22 | 1996-02-13 | Bayer Ag | Di(meth)acrylate with cyclic carbonate group |
| JPH09290210A (en) * | 1996-02-28 | 1997-11-11 | Nippon Shokubai Co Ltd | Continuous production of coating film |
| JPH09309173A (en) * | 1996-03-21 | 1997-12-02 | Showa Denko Kk | Ion conductive laminated matter, its manufacture, and use thereof |
-
1998
- 1998-08-20 JP JP10233850A patent/JP2000060871A/en active Pending
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH07261400A (en) * | 1994-03-22 | 1995-10-13 | Konica Corp | Image forming material |
| JPH0841044A (en) * | 1994-07-22 | 1996-02-13 | Bayer Ag | Di(meth)acrylate with cyclic carbonate group |
| JPH0839718A (en) * | 1994-07-27 | 1996-02-13 | Kureha Chem Ind Co Ltd | Vacuum-deposited composite film and its production |
| JPH09290210A (en) * | 1996-02-28 | 1997-11-11 | Nippon Shokubai Co Ltd | Continuous production of coating film |
| JPH09309173A (en) * | 1996-03-21 | 1997-12-02 | Showa Denko Kk | Ion conductive laminated matter, its manufacture, and use thereof |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US9192452B2 (en) | 2011-08-25 | 2015-11-24 | King Saud University | Plastic clear band for dental restorations |
| JP2015096243A (en) * | 2015-01-29 | 2015-05-21 | 直樹 丸矢 | Swinging tooth fixing structure |
| CN113639696A (en) * | 2021-08-11 | 2021-11-12 | 牡丹江医学院 | Tooth exploration device |
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