JP5793290B2 - Dental measuring device - Google Patents
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Description
本件はＯＣＴを利用した歯科用計測装置に関する。 This case relates to a dental measuring device using OCT.
近年の歯科診療では予防の観点から、う蝕の進行度のみならず、完全なう蝕になる前の状態である初期う蝕の進行度、つまり歯の脱灰又は再石灰化の程度を診断し、診療方針の決定をすることが必要になってきた。
しかし特に初期う蝕の進行度の診断は、施術者の勘と経験に頼るしかなかった。
そのため、歯に励起光線を照射することにより発生する蛍光光線を検出して歯におけるう蝕、歯石、プラーク又は細菌感染を識別する方法および装置が一部で利用されるようになった。
In recent dental practice, from the viewpoint of prevention, not only the progress of caries, but also the progress of initial caries, which is a state before complete caries, that is, the degree of decalcification or remineralization of teeth. Therefore, it has become necessary to determine the medical treatment policy.
However, diagnosis of the progress of the initial caries had to rely on the practitioner's intuition and experience.
Therefore, some methods and devices have been used to detect caries, calculus, plaque or bacterial infection in teeth by detecting fluorescent light generated by irradiating the teeth with excitation light.
しかし、歯に励起光線を照射することにより発生する蛍光光線を検出する装置では、う蝕、歯石、プラーク又は細菌感染を識別することができるだけで、う蝕や初期う蝕の進行度、つまり歯の脱灰又は再石灰化の程度を診断し、診療方針の決定をすることは困難である。
そこで本発明では、う蝕や初期う蝕の進行度を自動的に判定する歯科用計測装置を提供する。
However, a device that detects fluorescent light generated by irradiating teeth with excitation light can only identify caries, calculus, plaque, or bacterial infection, and the degree of progression of caries and initial caries, i.e., teeth. It is difficult to diagnose the degree of demineralization or remineralization and to determine the treatment policy.
Therefore, the present invention provides a dental measuring device that automatically determines the progress of caries and initial caries.
上記に鑑み本発明者は鋭意実験研究の結果下記の手段によりこの課題を解決した。
（１）歯牙の表面から深さ方向への１次元のＯＣＴ（Ｏｐｔｉｃａｌ Ｃｏｈｅｒｅｎｃｅ Ｔｏｍｏｇｒａｐｈｙ）信号を取得する信号取得手段と、前記ＯＣＴ信号における、前記歯牙の表面に対応する信号強度ピーク位置の検出手段と、前記ＯＣＴ信号の信号強度分布を、う蝕の進行度に応じて分類する手段と、前記う蝕の進行度に応じて分類された分類値を表示する手段から構成されてなり、前記う蝕の進行度に応じて分類する手段が、主成分分析を利用するものであることを特徴とする歯科用計測装置。
In view of the above, the present inventor has solved this problem by the following means as a result of intensive experimental research.
(1) Signal acquisition means for acquiring a one-dimensional OCT (Optical Coherence Tomography) signal from the tooth surface in the depth direction, and signal intensity peak position detection means corresponding to the tooth surface in the OCT signal; the signal intensity distribution of the OCT signal, and means for classifying according to caries progression, Ri Na consists means for displaying the sorted classified values in accordance with the progress of the dental caries, cormorants the It means for classifying according to the progress of the corrosion is, dental measuring apparatus according to claim der Rukoto those utilizing principal component analysis.
（２）前記う蝕の進行度を表示する手段に代わり、前記う蝕の進行度をブザーの音色、音の長さ、メロディー又は音声等により施術者に知らせることを特徴とする前項（１）に記載の歯科用計測装置。
（３）前記信号取得手段が、コリメータレンズと光ファイバー、及びそれらを収納するケースとで構成された計測用のプローブを備えてなることを特徴とする前項（１）又は（２）に記載の歯科用計測装置。
( 2 ) The preceding item (1), wherein the practitioner is informed of the progress of the caries by a buzzer tone, length, melody or voice instead of means for displaying the progress of the caries. dental measuring apparatus according to.
( 3 ) The dental apparatus according to (1) or (2) , wherein the signal acquisition means includes a measurement probe including a collimator lens, an optical fiber, and a case for housing them. Measuring device.
（４）前記ＯＣＴ信号の信号強度分布をう蝕の進行度に応じて分類する手段が、初期う蝕を脱灰又は再石灰化の程度に応じてさらに複数の段階に分類するものであることを特徴とする前項（１）〜（３）のいずれか１項記載の歯科用計測装置。 ( 4 ) The means for classifying the signal intensity distribution of the OCT signal according to the progress of caries classifies the initial caries into a plurality of stages according to the degree of decalcification or remineralization. The dental measurement device according to any one of the preceding items (1) to ( 3 ), characterized in that:
１．本発明の請求項１の発明によれば、
歯牙の表面から深さ方向への１次元のＯＣＴ信号取得手段と、前記ＯＣＴ信号における前記歯牙の表面に対応する信号強度ピークの検出手段と、
前記ＯＣＴ信号の信号強度分布を、う蝕の進行度に応じて分類する手段と、前記う蝕の進行度に応じて分類された分類値を表示する手段から構成されてなり、前記う蝕の進行度に応じて分類する手段が、主成分分析を利用するものであるため、う蝕の進行度を自動的に判定することができる。
またＯＣＴの信号強度分布は、組織内の屈折率の変化、つまり組織内の微細な構造をそのままあらわしており、歯の脱灰又は再石灰化の進行状況に敏感に反応して変化するので、蛍光等の化学的性質を利用する他の方法より的確な診断ができる。
1. According to the invention of claim 1 of the present invention,
One-dimensional OCT signal acquisition means in the depth direction from the tooth surface; and signal intensity peak detection means corresponding to the tooth surface in the OCT signal;
The signal intensity distribution of the OCT signal, and means for classifying according to caries progression, Ri Na consists means for displaying the sorted classified values in accordance with the progress of the caries, the carious It means for classifying according to the degree of progress, because der those utilizing principal component analysis, the progress of dental caries can be determined automatically.
In addition, the signal intensity distribution of OCT represents a change in refractive index in the tissue, that is, a fine structure in the tissue as it is, and changes in response to the progress of tooth demineralization or remineralization. More accurate diagnosis can be made than other methods using chemical properties such as fluorescence.
また、信号強度分布をう蝕の進行度に応じて分類する手段が、主成分分析を利用するものであるため、
信号強度分布を既に確立された統計的手法により短時間で正確に分類し、う蝕の進行度を判定することができる。
Furthermore, since means for classified according to signal intensity distribution caries progression is to utilize the main component analysis,
The signal intensity distribution can be accurately classified in a short time by an already established statistical method, and the progress of caries can be determined.
２．本発明の請求項２の発明によれば
う蝕の進行度を表示する手段に代わり、前記う蝕の進行度をブザーの音色、音の長さ、メロディー又は音声等により施術者に知らせるため、施術者は患者から目を離して表示部を見ることなく、う蝕の進行度を把握することができ効率的な診療が可能である。
2 . According to the invention of claim 2 of the present invention, instead of means for displaying the progress of caries, in order to inform the practitioner by the tone of the buzzer, the length of the sound, the melody or the voice, etc. The practitioner can grasp the progress of the caries without looking away from the patient and looking at the display unit, and can perform efficient medical care.
３．本発明の請求項３の発明によれば
前記ＯＣＴ信号取得手段が、コリメータレンズと光ファイバー、及びそれらを収納するケースとで構成された計測用のプローブを備えてなり、
光走査機構やその他のレンズ等がなく、歯科診療で特に重要な計測用のプローブの低コスト化と軽量化を同時に実現できる。また構造が簡単であるため、患者に接触する部分を容易に取り外して滅菌したり、使い捨てにしたりできるので衛生的である。
3 . According to the invention of claim 3 of the present invention, the OCT signal acquisition means comprises a probe for measurement composed of a collimator lens, an optical fiber, and a case for storing them,
Since there is no optical scanning mechanism or other lenses, the cost and weight of a measurement probe that is particularly important in dental practice can be realized at the same time. In addition, since the structure is simple, the portion that comes into contact with the patient can be easily removed and sterilized, or can be disposable.
４．本発明の請求項４の発明によれば
ＯＣＴ信号の信号強度分布をう蝕の進行度に応じて分類する手段が、初期う蝕を脱灰又は再石灰化の程度に応じて、さらに複数の段階に分類するものであるため、初期う蝕の進行度を自動的に判定し診療方針の決定に役立てることができる。
またＯＣＴの信号強度分布は、組織内の屈折率の変化、つまり組織内の微細な構造をそのままあらわしており、歯の脱灰又は再石灰化の進行状況に敏感に反応して変化するので、蛍光等の化学的性質を利用する他の方法より的確な診断ができる。
4). According to the invention of claim 4 of the present invention, the means for classifying the signal intensity distribution of the OCT signal according to the progress of the caries further includes a plurality of initial caries according to the degree of decalcification or remineralization. Since it is classified into stages, it is possible to automatically determine the progress of the initial caries and to help determine the treatment policy.
In addition, the signal intensity distribution of OCT represents a change in refractive index in the tissue, that is, a fine structure in the tissue as it is, and changes in response to the progress of tooth demineralization or remineralization. More accurate diagnosis can be made than other methods using chemical properties such as fluorescence.
発明を実施するための最良の形態を以下に説明する。 The best mode for carrying out the invention will be described below.
図１は、本発明の歯科用計測装置の外観斜視図である。
図において、１は歯科用計測装置、２はプローブ、３は本体、３ａは表示部、３ｂはメインスイッチを示す。
図２は、本発明の歯科用計測装置のプローブの縦断面図である。
図において、２ａはコリメータレンズ、２ｂは光ファイバー、２ｃはケースを示す。
光ファイバー２ｂを接続したコリメータレンズ２ａが、先端を細くしたケース２ｃ内の先端近くに取り付けられる。
施術者は、プローブ２を手に持ち先端を計測部位に接触又は近接させて計測を行う。
光走査機構やその他のレンズ等がないため、軽量かつ低コストである。
FIG. 1 is an external perspective view of a dental measuring apparatus according to the present invention.
In the figure, 1 is a dental measuring device, 2 is a probe, 3 is a main body, 3a is a display unit, and 3b is a main switch.
FIG. 2 is a longitudinal sectional view of the probe of the dental measuring apparatus of the present invention.
In the figure, 2a is a collimator lens, 2b is an optical fiber, and 2c is a case.
A collimator lens 2a to which an optical fiber 2b is connected is attached near the tip in a case 2c having a thin tip.
The practitioner performs measurement by holding the probe 2 in his hand and bringing the tip into contact with or close to the measurement site.
Since there is no optical scanning mechanism or other lens, it is lightweight and low cost.
図３は、前歯縦断面を表す模式図である。
図において、１１は前歯、１１ａはエナメル質、１１ｂは象牙質、１１ｃは歯髄、１１ｄは歯肉、１１ｅは歯槽骨を示す。
進行したう蝕はもちろん、初期う蝕でもその有無は施術者が目視により判断できるので、う蝕の進行度の判定を目的として、施術者は例えば前歯１１の表面のう蝕又は初期う蝕のある位置にプローブ２を接触又は近接させて計測を行う。
この場合は、前記表面はエナメル質１１ａであるが、エナメル質１１ａが失われている場合や、歯肉１１ｄが退縮している場合等は、エナメル質１１ａ以外の組織にプローブ２を接触又は近接させて計測を行うこともあり得る（図示せず）。
また実際の臨床では、前記前歯１１以外のすべての歯牙が対象となり得ることは言うまでも無い。
本発明者は、ＯＣＴ信号の信号強度分布をう蝕の進行度に応じて分類するための基準となるデータベースを作成しており、そのために臨床及び実験室で多数のデータを採取した。
それらのデータの一例として、ヒト抜去歯（犬歯）を実験室において酸を使用して人工的に脱灰させ、時間経過とともに脱灰が進む状態を作って計測した結果を図４〜７に示す。 そして、ＯＣＴ信号の信号強度分布が脱灰の程度に応じて変化することを以下に説明する。
FIG. 3 is a schematic diagram showing a front tooth longitudinal section.
In the figure, 11 is an anterior tooth, 11a is enamel, 11b is dentin, 11c is pulp, 11d is gum, 11e is alveolar bone.
Since the practitioner can visually determine the presence or absence of the advanced caries as well as the initial caries, for the purpose of determining the progress of the caries, the practitioner may, for example, evaluate the caries on the front teeth 11 or the initial caries. Measurement is performed by bringing the probe 2 into or close to a certain position.
In this case, the surface is the enamel 11a, but when the enamel 11a is lost or the gingiva 11d is retracted, the probe 2 is brought into contact with or close to the tissue other than the enamel 11a. May be measured (not shown).
In actual clinical practice, it goes without saying that all teeth other than the front teeth 11 can be targeted.
The present inventor has created a database serving as a reference for classifying the signal intensity distribution of the OCT signal according to the degree of progression of caries. For this purpose, a large number of data were collected in clinical and laboratory laboratories.
As an example of such data, human extracted teeth (canine teeth) are artificially decalcified using acid in the laboratory, and the measurement results are shown in FIGS. . And it demonstrates below that the signal intensity distribution of an OCT signal changes according to the degree of demineralization.
図４は、う蝕の無いヒト抜去歯（犬歯）のエナメル質表面から計測したときの計測結果である。
これは人工的な脱灰を開始する前の状態である。
図において、２１は信号強度分布、２１ａはエナメル質表面のピークを示す。
信号強度分布２１のグラフは、横軸は深さ（μｍ）、縦軸は信号強度（ｄＢ）である。
横軸の０の位置が計測開始点で、ここでは歯牙表面から離れた空間のある一点である。
グラフ中の深さは計測開始点からの光学距離を表しており、後述する信号強度分布２２〜２４においても同様である。
エナメル質表面のピーク２１ａにおける横軸の数値は、エナメル質表面の位置（計測開始点からの光学距離）を表している。
ただし、光学距離は、該当する組織の屈折率に実際の距離を掛けたものである。
FIG. 4 shows the measurement results when measured from the enamel surface of a human extracted tooth (canine) without caries.
This is the state before the start of artificial demineralization.
In the figure, 21 indicates the signal intensity distribution, and 21a indicates the peak of the enamel surface.
In the graph of the signal intensity distribution 21, the horizontal axis represents depth (μm) and the vertical axis represents signal intensity (dB).
The position of 0 on the horizontal axis is the measurement start point, and here is one point with a space away from the tooth surface.
The depth in the graph represents the optical distance from the measurement start point, and the same applies to signal intensity distributions 22 to 24 described later.
The numerical value on the horizontal axis at the peak 21a on the enamel surface represents the position of the enamel surface (optical distance from the measurement start point).
However, the optical distance is obtained by multiplying the refractive index of the corresponding tissue by the actual distance.
図５は、前記抜去歯の人工的な脱灰開始１０分後の計測結果である。
その他の計測条件は図４とまったく同じである。
図において、２２は信号強度分布、２２ａはエナメル質表面のピークである。人工的な脱灰を行っているので経過時間とともに脱灰は進む。
したがって図５は図４よりやや脱灰が進んだ状態であり、エナメル質表面のピーク２２ａの幅が、エナメル質表面のピーク２１ａの幅より広くなっていることが分かる。
FIG. 5 is a measurement result 10 minutes after the start of artificial demineralization of the extracted tooth.
Other measurement conditions are exactly the same as in FIG.
In the figure, 22 is the signal intensity distribution, and 22a is the peak of the enamel surface. Since artificial demineralization is performed, demineralization progresses with time.
Therefore, FIG. 5 shows a state in which deashing has advanced a little more than FIG. 4, and it can be seen that the width of the peak 22a on the enamel surface is wider than the width of the peak 21a on the enamel surface.
図６は、前記抜去歯の人工的な脱灰開始３０分後の計測結果である。
その他の計測条件は図４とまったく同じである。
図において、２３は信号強度分布、２３ａはエナメル質表面のピークである。図５より脱灰が進んだ状態である。
FIG. 6 is a measurement result 30 minutes after the start of artificial demineralization of the extracted tooth.
Other measurement conditions are exactly the same as in FIG.
In the figure, 23 is the signal intensity distribution, and 23a is the peak of the enamel surface. FIG. 5 shows a state where decalcification has advanced.
図７は、前記抜去歯の人工的な脱灰開始６０分後の計測結果である。
その他の計測条件は図４とまったく同じである。
図において、２４は信号強度分布、２４ａはエナメル質表面のピークである。図６より脱灰が進んだ状態である。
FIG. 7 is a measurement result 60 minutes after the start of artificial demineralization of the extracted tooth.
Other measurement conditions are exactly the same as in FIG.
In the figure, 24 is the signal intensity distribution, and 24a is the peak of the enamel surface. FIG. 6 shows a state where decalcification has advanced.
以上の様に脱灰の程度によって信号強度分布が目に見えて変化する。
臨床におけるう蝕又は初期う蝕においても同様で、信号強度分布を見れば進行度に応じて分類することができ、コンピュータを利用して統計的手法で演算させれば短時間で正確に分類し、う蝕又は初期う蝕の進行度を判定することができる。
As described above, the signal intensity distribution changes visibly depending on the degree of decalcification.
The same applies to clinical caries or initial caries, and it can be classified according to the degree of progression by looking at the signal intensity distribution, and it can be accurately classified in a short time by using a statistical method using a computer. The progress of caries or initial caries can be determined.
臨床において本発明の歯科用計測装置を使用する際、本体３に内蔵するコンピュータで行われる演算について説明する。
ここでは一例として、歯牙表面のエナメル質のう蝕又は初期う蝕のある位置において深さ方向へ１次元のＯＣＴ信号を取得し、
前記ＯＣＴ信号におけるエナメル質表面の信号強度ピーク位置を検出し、
前記ＯＣＴ信号の信号強度分布からう蝕又は初期う蝕の進行度を自動的に判定し表示する方法について以下に説明する。以下の説明では便宜上図６を利用する。
Calculations performed by a computer built in the main body 3 when using the dental measurement apparatus of the present invention in clinical practice will be described.
Here, as an example, a one-dimensional OCT signal is acquired in the depth direction at a position where there is enamel caries or initial caries on the tooth surface,
Detecting the signal intensity peak position of the enamel surface in the OCT signal;
A method of automatically determining and displaying the progress of caries or initial caries from the signal intensity distribution of the OCT signal will be described below. In the following description, FIG. 6 is used for convenience.
１．臨床にて施術者が本発明の歯科用計測装置を用いて、図６のように歯牙のエナメル質表面から深さ方向への１次元のＯＣＴ信号を取得する。
２．前記１次元のＯＣＴ信号において、必要に応じて高速フーリエ変換によるフィルタ処理を行い、前記ＯＣＴ信号からノイズとなる高周波成分を取り除く。この処理を行えば、以下の処理がより簡単になる。
またこれらの処理が、以下の処理も含め本発明の歯科用計測装置に内蔵されるコンピュータにより自動的に行われるものである。
３．必要に応じて高周波成分を取り除かれた前記ＯＣＴ信号の傾きの変化から、エナメル質表面に対応するピーク位置を検出する。つまりエナメル質表面のピーク２２ａにおける深さを求めるということであり、エナメル質表面のピーク２２ａでは２３００μｍとなる。
４．前記ピーク位置から後方の歯牙に対応している部分の前記ＯＣＴ信号の信号強度分布は、う蝕又は初期う蝕の進行度に応じて後述する分類方法により自動的に分類される。
５．分類の結果は、例えば英数字、記号、バーグラフ等を用いて表示される。
1. In practice, the practitioner uses the dental measurement apparatus of the present invention to obtain a one-dimensional OCT signal in the depth direction from the tooth enamel surface as shown in FIG.
2. In the one-dimensional OCT signal, filter processing by fast Fourier transform is performed as necessary to remove a high-frequency component that becomes noise from the OCT signal. If this processing is performed, the following processing becomes easier.
Further, these processes are automatically performed by a computer built in the dental measurement apparatus of the present invention including the following processes.
3. A peak position corresponding to the enamel surface is detected from a change in the slope of the OCT signal from which high frequency components have been removed as necessary. In other words, the depth at the peak 22a on the enamel surface is obtained, and at the peak 22a on the enamel surface, the depth is 2300 μm.
4). The signal intensity distribution of the OCT signal in the portion corresponding to the tooth behind the peak position is automatically classified by a classification method to be described later according to the progress of caries or initial caries.
5. The classification result is displayed using, for example, alphanumeric characters, symbols, bar graphs, and the like.
以下に、一例として主成分分析による前記分類方法について説明する。そのために、まず分類のために必要な固有ベクトルの求め方について説明する。
（１）う蝕又は初期う蝕の進行度が異なるサンプルを多数準備し、前記サンプル表面から深さ方向へ１次元のＯＣＴ信号のデータを十分に多く取る。
ここでデータ数はｍ個とする。
（２）必要に応じて高速フーリエ変換によるフィルタ処理を行い、各データからノイズとなる高周波成分を取り除く。
（３）各データの波形全体から歯牙表面に対応するピーク位置付近から後方の歯牙に対応している部分のデータを取り出す。
取り出したデータの範囲（長さ）はサンプル毎に等しくなるようにしておく。
（４）前記範囲における計測ポイント数をn個とし、取り出された各データをn次のベクトルと考える。データ数はｍ個であり、前記ベクトルをｍ×ｎ行列に置き換える。
Below, the said classification method by principal component analysis is demonstrated as an example. For this purpose, a method for obtaining eigenvectors necessary for classification will be described first.
(1) A large number of samples having different degrees of progression of caries or initial caries are prepared, and a sufficient amount of one-dimensional OCT signal data is taken from the sample surface in the depth direction.
Here, the number of data is m.
(2) If necessary, filter processing by fast Fourier transform is performed to remove high-frequency components that become noise from each data.
(3) From the entire waveform of each data, the data of the portion corresponding to the rear tooth is extracted from the vicinity of the peak position corresponding to the tooth surface.
The range (length) of the extracted data is set to be equal for each sample.
(4) Assume that the number of measurement points in the range is n, and that each piece of extracted data is an n-order vector. The number of data is m, and the vector is replaced with an m × n matrix.
（５）各行列の固有ベクトルを求める。固有ベクトルは第一、第二・・・の順に予め決めたところまで求めるが、最後の確認の段階で十分な分類精度が得られない場合は（５）からやり直し、より下位のものまで求める。
（６）多数準備した前記サンプルや、他のサンプルにて、再度、表面から深さ方向へ１次元のＯＣＴ信号を取得する。
（７）必要に応じて高速フーリエ変換によるフィルタ処理を行い、データからノイズとなる高周波成分を取り除く。
（８）データの取り出す範囲は（３）と同じにする。
（９）各データをn次のベクトルと考え、前記各行列の固有ベクトルとの内積を求める。
（１０）内積は各データと前記各行列の固有ベクトルとの距離を現しているので、これが最も小さいものが、各データの属するう蝕又は初期う蝕の進行度のグループとなる。
ここで、分類の精度が高ければ各固有ベクトルが確定するが、分類の精度が不十分な場合は、（３）や（５）に戻ってやり直す。
ここで、（１）から（１０）までの作業は本発明者により行われるものであり、前記各固有ベクトルは予め本発明の歯科用計測装置に入力しておくものである。
(5) The eigenvector of each matrix is obtained. The eigenvectors are obtained up to predetermined points in the order of first, second,..., But if sufficient classification accuracy cannot be obtained at the final confirmation stage, the procedure is repeated from (5) and the lower ones are obtained.
(6) A one-dimensional OCT signal is acquired again from the surface in the depth direction using the prepared samples and other samples.
(7) If necessary, filter processing by fast Fourier transform is performed to remove high-frequency components that become noise from the data.
(8) The data extraction range is the same as (3).
(9) Consider each data as an nth-order vector, and calculate an inner product with the eigenvector of each matrix.
(10) Since the inner product represents the distance between each data and the eigenvector of each matrix, the smallest one is a group of the degree of progression of caries or initial caries to which each data belongs.
Here, if the classification accuracy is high, each eigenvector is determined, but if the classification accuracy is insufficient, return to (3) and (5) and start again.
Here, the operations from (1) to (10) are performed by the present inventor, and each of the eigenvectors is input in advance to the dental measurement apparatus of the present invention.
前項４．における分類方法について以下に説明する。これは確定した前記各固有ベクトルを使い主成分分析を利用した方法である。
ａ．前記ＯＣＴ信号の信号強度分布の波形全体から歯牙表面に対応するピーク２２ａの付近から後方の歯牙に対応している部分のデータを取り出す。データの取り出す範囲は（３）と同じである。
ｂ．前記データをｎ次のベクトルと考え、前記各固有ベクトルとの内積を求める。
ｃ．内積は前記データと前記各固有ベクトルとの距離を現しているので、これが最も小さいものが、各データの属するう蝕又は初期う蝕の進行度のグループとなり、分類が完了する。
Previous item 4. The classification method will be described below. This is a method using principal component analysis using the determined eigenvectors.
a. Data of the portion corresponding to the rear tooth is extracted from the vicinity of the peak 22a corresponding to the tooth surface from the entire waveform of the signal intensity distribution of the OCT signal. The data extraction range is the same as (3).
b. The data is considered as an n-th vector and an inner product with each eigenvector is obtained.
c. Since the inner product represents the distance between the data and the eigenvectors, the smallest one becomes a group of the caries to which each data belongs or the progress of the initial caries, and the classification is completed.
本発明の歯科用計測装置を歯牙切削のためのエアタービンハンドピース、マイクロモータハンドピース、又は歯科用レーザー装置のプローブ等に装備し、計測しながら歯牙を切削することにより、う蝕又は初期う蝕の切削が完了した時点で自動的に前記エアタービンハンドピース、マイクロモータハンドピース、又は歯科用レーザー装置を停止させるようにし、健常組織の切削を最小限に留めることもできる。
本実施例では、1次元のＯＣＴ信号を取得するとしているが、２次元又は３次元のＯＣＴ信号を取得し、そこから必要な箇所の１次元のＯＣＴ信号を取り出しても良い。また、計測対象を歯牙とし、う蝕又は初期う蝕の分類を行うとしているが、歯科の他の症例や、皮膚科、眼科等の医療分野、工業分野、あるいは化粧品分野等においても、組成、構成、構造、密度、温度、圧力等により変化するＯＣＴ信号を利用すれば計測対象を必要に応じた方法で分類することができるので、あらゆる分野において応用できることは言うまでもない。
The dental measurement device according to the present invention is mounted on an air turbine handpiece, a micromotor handpiece, or a probe of a dental laser device for tooth cutting, and caries or initial caries are obtained by cutting teeth while measuring. When the cutting of erosion is completed, the air turbine handpiece, the micromotor handpiece, or the dental laser device may be automatically stopped to cut healthy tissue to a minimum.
In the present embodiment, a one-dimensional OCT signal is acquired. However, a two-dimensional or three-dimensional OCT signal may be acquired, and a one-dimensional OCT signal at a necessary location may be extracted therefrom. In addition, it is said that the measurement object is a tooth, and caries or initial caries are classified, but in other cases of dentistry, medical fields such as dermatology and ophthalmology, industrial fields, cosmetics fields, etc., Needless to say, the measurement object can be classified by a method according to necessity by using an OCT signal that varies depending on the configuration, structure, density, temperature, pressure, and the like, and can be applied in various fields.
１：歯科用計測装置
２：プローブ
２ａ：コリメータレンズ
２ｂ：光ファイバー
２ｃ：ケース
３：本体
３ａ：表示部
３ｂ：メインスイッチ
１１：前歯
１１ａ：エナメル質
１１ｂ：象牙質
１１ｃ：歯髄
１１ｄ：歯肉
１１ｅ：歯槽骨
２１：信号強度分布
２１ａ：エナメル質表面のピーク
２２：信号強度分布
２２ａ：エナメル質表面のピーク
２３：信号強度分布
２３ａ：エナメル質表面のピーク
２４：信号強度分布
２４ａ：エナメル質表面のピーク
1: Dental measuring device 2: Probe 2a: Collimator lens 2b: Optical fiber 2c: Case 3: Body 3a: Display unit 3b: Main switch 11: Anterior tooth 11a: Enamel 11b: Dentin 11c: Pulp 11d: Gingiva 11e: Alveolar Bone 21: Signal intensity distribution 21a: Enamel surface peak 22: Signal intensity distribution 22a: Enamel surface peak 23: Signal intensity distribution 23a: Enamel surface peak 24: Signal intensity distribution 24a: Enamel surface peak
Claims (4)
前記ＯＣＴ信号における、前記歯牙の表面に対応する信号強度ピーク位置の検出手段と、
前記ＯＣＴ信号の信号強度分布を、う蝕の進行度に応じて分類する手段と、
前記う蝕の進行度に応じて分類された分類値を表示する手段から構成されてなり、
前記う蝕の進行度に応じて分類する手段が、主成分分析を利用するものであることを特徴とする歯科用計測装置。 A signal acquisition means for acquiring a one-dimensional OCT (Optical Coherence Tomography) signal from the tooth surface in the depth direction;
A means for detecting a signal intensity peak position corresponding to the surface of the tooth in the OCT signal;
Means for classifying the signal intensity distribution of the OCT signal according to the progress of caries;
Ri Na consists means for displaying the sorted classified values in accordance with the progress of the dental caries,
It means for classifying according to the progress degree of the caries, dental measuring apparatus according to claim der Rukoto those utilizing principal component analysis.
前記う蝕の進行度をブザーの音色、音の長さ、メロディー又は音声等により施術者に知らせることを特徴とする請求項１に記載の歯科用計測装置。 Instead of means for displaying the progress of the caries,
The dental measurement apparatus according to claim 1, wherein the progress of the caries is notified to a practitioner by a tone color of a buzzer, a length of a sound, a melody or a voice.
初期う蝕を脱灰又は再石灰化の程度に応じて、さらに複数の段階に分類するものであることを特徴とする請求項１〜３のいずれか１項に記載の歯科用計測装置。 Means for classifying the signal intensity distribution of the OCT signal according to the progress of caries,
The dental measurement apparatus according to any one of claims 1 to 3 , wherein the initial dental caries is further classified into a plurality of stages according to the degree of decalcification or remineralization.
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| WO2018193936A1 (en) * | 2017-04-21 | 2018-10-25 | 株式会社モリタ製作所 | Medical examination device |
| JP7188826B1 (en) | 2022-01-28 | 2022-12-13 | 株式会社吉田製作所 | AI diagnostic imaging system and dental OCT diagnostic imaging system |
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| JP4338142B2 (en) * | 2006-08-31 | 2009-10-07 | 国立長寿医療センター総長 | Dental optical tomographic image display system |
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