JPH03273121A - Radiation thermometer - Google Patents
Radiation thermometerInfo
- Publication number
- JPH03273121A JPH03273121A JP2072029A JP7202990A JPH03273121A JP H03273121 A JPH03273121 A JP H03273121A JP 2072029 A JP2072029 A JP 2072029A JP 7202990 A JP7202990 A JP 7202990A JP H03273121 A JPH03273121 A JP H03273121A
- Authority
- JP
- Japan
- Prior art keywords
- temperature
- thermopile
- output
- eardrum
- thermistor
- 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
- 230000005855 radiation Effects 0.000 title claims description 7
- 210000003454 tympanic membrane Anatomy 0.000 claims abstract description 23
- 230000036760 body temperature Effects 0.000 claims description 5
- 230000035945 sensitivity Effects 0.000 abstract description 9
- 238000004364 calculation method Methods 0.000 description 9
- 238000005259 measurement Methods 0.000 description 7
- 238000009529 body temperature measurement Methods 0.000 description 4
- 238000010586 diagram Methods 0.000 description 4
- 238000006243 chemical reaction Methods 0.000 description 3
- 238000001514 detection method Methods 0.000 description 3
- 239000000463 material Substances 0.000 description 2
- QSHDDOUJBYECFT-UHFFFAOYSA-N mercury Chemical compound [Hg] QSHDDOUJBYECFT-UHFFFAOYSA-N 0.000 description 2
- 229910052753 mercury Inorganic materials 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 1
- 210000003016 hypothalamus Anatomy 0.000 description 1
- 230000004962 physiological condition Effects 0.000 description 1
- 230000001331 thermoregulatory effect Effects 0.000 description 1
Landscapes
- Photometry And Measurement Of Optical Pulse Characteristics (AREA)
- Radiation Pyrometers (AREA)
- Measuring And Recording Apparatus For Diagnosis (AREA)
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は鼓膜から輻射される赤外線を利用して鼓膜源を
測定する放射体温計に関する。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a radiation thermometer that measures the eardrum source using infrared rays radiated from the eardrum.
体温は生理状態を反映する重要なバロメータであり、水
銀体温計や電子体温計がしばしば使用されている。又近
年ではより医学的に重要な体温計測を行うため、鼓膜源
が体温調節中枢である「視床下部の温度」をよく反映す
る、との医学的定見に基づき、赤外線温度計測技術によ
り鼓膜源を非接触で測定する赤外線体温計が実用化され
ている。Body temperature is an important barometer that reflects physiological conditions, and mercury thermometers and electronic thermometers are often used. In addition, in recent years, in order to measure body temperature, which is more medically important, infrared temperature measurement technology has been used to measure the eardrum source, based on the medical opinion that the tympanic membrane source reflects the temperature of the hypothalamus, which is the thermoregulatory center. An infrared thermometer that measures temperature without contact has been put into practical use.
（たとえばＵＳＰ−４６０２６４２）
〔発明が解決しようとする課題〕
しかしながら水銀体温計や電子体温計では測定に１０分
なし・し２０分もの時間を要し、連続測定も又不可能で
ある。また従来の発明である赤外線体温計（ＵＳＰ−４
６０２６４２）は赤外線温度計測技術を用いているため
郡１定時間は大幅に改善されたものの、赤外線検出素子
（−例としてサーモパイル）の感度や信号処理系の感度
の変動により測定精度が左右されるという欠点を有する
。以下を図を用いてその説明を行う。(For example, USP-4602642) [Problems to be Solved by the Invention] However, mercury thermometers and electronic thermometers require 10 to 20 minutes for measurement, and continuous measurement is also impossible. In addition, a conventional invention, an infrared thermometer (USP-4
602642) uses infrared temperature measurement technology, which greatly improves the time required for group 1, but measurement accuracy is affected by fluctuations in the sensitivity of the infrared detection element (for example, a thermopile) and the sensitivity of the signal processing system. It has the following drawback. The following will be explained using figures.
第２図はＵＳＰ−４６０２６４２に示された赤外線体温
計のブロックダイヤグラムである。第２図に於て２１は
サーモパイルであり、！膜３２からの赤外線の輻射量に
応じた電圧■、を出力する。FIG. 2 is a block diagram of an infrared thermometer shown in USP-4602642. In Figure 2, 21 is a thermopile! A voltage (2) corresponding to the amount of infrared radiation from the film 32 is output.
２２は増幅器であり微弱なサーモパイル２１の出力電圧
■、を所定の大きさに増幅する。２５はサーミスタであ
りヒータ２４、サーモパイル２１とともに熱伝導性の良
い材質で作られたブロック２６の中に収納される。２６
は抵抗−電圧変換回路でありサーミスタ２５の抵抗を電
圧に変換する。Reference numeral 22 denotes an amplifier which amplifies the weak output voltage (2) of the thermopile 21 to a predetermined magnitude. A thermistor 25 is housed together with the heater 24 and the thermopile 21 in a block 26 made of a material with good thermal conductivity. 26
is a resistance-voltage conversion circuit that converts the resistance of the thermistor 25 into voltage.
２９＆工温度演算回路Ａであり、サーミスタ２５の抵抗
を温度に換算する。即ちサー□スタ２５のＢ定数をＢ。29 & temperature calculation circuit A, which converts the resistance of the thermistor 25 into temperature. That is, the B constant of the sensor 25 is B.
、温度Ｔｎの時の抵抗値をＲｎとすれば、サーミスタの
温度がＴｏの時の抵抗値Ｒｔは（１）式の如くなる。, the resistance value Rt when the temperature of the thermistor is To is expressed by equation (1).
１
Ｒｔ ＝Ｒｎ ｅｘｐ ［Ｂｏ （）コ −・−・
−・−＋１３ｏ Ｔｎ
（１）式より
Ｂｏ 、 Ｂ ｎ、 Ｔ ｎはサーミスタ２５の特性
値としてあらかじめ与えられているのでＲｔを知ること
によってＴｏが算出される。このためには例えばＵＳＰ
−４４６４０６７等の方法を使うことが出来る。この様
にして得られたサーミスタ２５の温度（即ちサーモパイ
ルの温度）Ｔｏは後述する温度演算回路Ｂ６０に入力さ
れる。1 Rt = Rn exp [Bo () ko -・-・
-.-+13o Tn From equation (1), since Bo, Bn, and Tn are given in advance as characteristic values of the thermistor 25, To is calculated by knowing Rt. For this, for example, USP
-4464067 and other methods can be used. The temperature of the thermistor 25 (that is, the temperature of the thermopile) To obtained in this manner is input to a temperature calculation circuit B60, which will be described later.
２７は差動電力増幅器であり抵抗−電圧変換回路２３の
出力と基準電圧発生回路２８の出力の差に応じた電圧を
出力し、ヒータ２４を加熱する。A differential power amplifier 27 outputs a voltage corresponding to the difference between the output of the resistance-voltage conversion circuit 23 and the output of the reference voltage generation circuit 28 to heat the heater 24.
即ち、ヒータ２４、サーミスタ２５、差動電力増幅器２
７によってフィードバック制御ル−プが構成され、ブロ
ック２６の温度、すなわちブーモノζイル２１の温度は
Ｔ。の一定値に維持される。That is, the heater 24, thermistor 25, differential power amplifier 2
7 constitutes a feedback control loop, and the temperature of the block 26, that is, the temperature of the boolean ζ coil 21 is T. is maintained at a constant value.
６０は温度演算回路Ｂであり増幅器２２により増幅され
たサーモパイル２１の出力Ｇ ａ Ｖ ｐと、前述の如
く一定値Ｔ。に維持されているブーモノ〈イル２１の温
度Ｔ０から鼓膜源Ｔ’を算出し、表示手段６１にて表示
する。60 is a temperature calculation circuit B which outputs the output G a V p of the thermopile 21 amplified by the amplifier 22 and the constant value T as described above. The tympanic membrane source T' is calculated from the temperature T0 of the boolean 21 maintained at , and is displayed on the display means 61.
以上を式を用いて詳述すると、
サーモパイルの出力■ｐは、
Ｖｐ＝σ・Ｋ・（Ｔ’−１４） ・・・・・・・
・・（３）の如くステファン−ボルツマンの法則によっ
て導き出される。To explain the above in detail using a formula, the output ■p of the thermopile is Vp=σ・K・(T'-14) ・・・・・・・・・
...is derived from the Stefan-Boltzmann law as shown in (3).
但し σ：鼓膜の放射率
に：サーモパイルの感度
Ｔ：鼓膜の温度
Ｔｏ：サーモパイルの温度
増幅器２２の利得をＧａとすると温度演算回路Ｂ３０の
入力には
ａＶｐ
なる電圧が入力される。温度演算回路Ｂ３０は次の（４
）式に基づいて鼓膜源Ｔを算出する。However, σ: Emissivity of the eardrum: Sensitivity of the thermopile T: Temperature of the eardrum To: Temperature of the thermopile When the gain of the amplifier 22 is Ga, a voltage aVp is input to the input of the temperature calculation circuit B30. The temperature calculation circuit B30 performs the following (4
) The tympanic membrane source T is calculated based on the formula.
前述した様に、ＵＳ Ｐ−４６０２６４２に於てはサー
モパイルの温度Ｔ０をヒータ２４とサーミスタ２５を用
いて一定の温度に保つ工夫がなされてはいるものの増幅
器２２の利得Ｇ ａ 、サーモパイル２１の感度にの変
動に対しては考慮されておらず、これらの変動が直ちに
測定精度の低下につながる。また（４）式は４乗根を解
くアルゴリズムを必要としシステムの複雑さを招来する
。As mentioned above, in US Pat. No. 4,602,642, the temperature T0 of the thermopile is kept constant using the heater 24 and thermistor 25, but the gain G a of the amplifier 22 and the sensitivity of the thermopile 21 These fluctuations immediately lead to a decrease in measurement accuracy. Furthermore, equation (4) requires an algorithm to solve the fourth root, which increases the complexity of the system.
本発明の目的はかかる欠点を克服し、赤外線温度測定技
術の優れた応答速度を活かしつつ、かつ赤外検出素子（
サーモパイル）の感度変動や電気回路の緒特性等の影響
を受けない高精度の鼓膜源測定装置（放射体温計）を提
供するものである。The purpose of the present invention is to overcome such drawbacks, take advantage of the excellent response speed of infrared temperature measurement technology, and use an infrared detection element (
The present invention provides a highly accurate tympanic membrane source measurement device (radiation thermometer) that is not affected by sensitivity fluctuations of thermopiles or electrical circuit characteristics.
前記問題点を解決するため本発明は次の様な構成として
いる。即ち、耳道内に挿入したサーモパイルによって鼓
膜から輻射される赤外線を計測し体温を算出する体温測
定手段に於て、サーモパイルの出力に応じてサーモパイ
ルの温度を制御する温度調節手段を設けたことを特徴と
する。In order to solve the above problems, the present invention has the following configuration. That is, the body temperature measurement means for calculating body temperature by measuring infrared rays radiated from the eardrum by a thermopile inserted into the auditory canal is characterized by being provided with a temperature adjustment means for controlling the temperature of the thermopile according to the output of the thermopile. shall be.
〔作用〕
本発明によれば本構成による鼓膜源の測定は以下の様に
して可能である。即ち（４）式に於て、サーモパイルの
温度Ｔ。はサーモパイルの出力電圧ｖｐによって制御さ
れる。−例としてサーモパイルの出力を増幅器に入力し
、その出力でサーモパイルに近接したヒータを加熱する
温度調節制御を行うと、サーモパイルの出力ＶｐがＯに
なる様にフィードバック制御が行われるので前記の（４
）式は次の（５）式の如くになる。[Function] According to the present invention, the measurement of the tympanic membrane source with this configuration is possible in the following manner. That is, in equation (4), the temperature T of the thermopile. is controlled by the thermopile output voltage vp. - For example, if the output of the thermopile is input to an amplifier and the output is used to control the temperature to heat a heater close to the thermopile, feedback control is performed so that the output Vp of the thermopile becomes O.
) is as shown in the following equation (5).
即ちサーモパイルの温度Ｔ。が直ちに鼓膜温ＴＴ−ゾ□
二Ｔ。 ・・・・・・・・・（５）を与える
。温度Ｔ。はサーモパイルに近接したサーミスタ等の温
度検出素子によって算出することが出来るので鼓膜基の
測定が可能とｔｌる。That is, the temperature T of the thermopile. Immediately the eardrum temperature TT-zo□ 2T.・・・・・・・・・(5) is given. Temperature T. Since it can be calculated using a temperature detection element such as a thermistor close to the thermopile, it is possible to measure the base of the tympanic membrane.
以下本発明の一実施例を図面に基づいて詳述する。 An embodiment of the present invention will be described below in detail with reference to the drawings.
第１図は本発明による放射体温計のブロックダイヤグラ
ムである。第１図に於て１１はサーモパイルであり鼓膜
２０からの赤外線の輻射量に応じた電圧Ｖｐを出力する
。１２は増幅器であり微弱にサーモパイル１１の出力電
圧ｖｐを所定の大きさに増幅する。１６は差動電力増幅
器で、増幅器１２の出力Ｖａと基準電圧Ｖｂ（本実施例
ではＶｂ＝Ｏと設定されている。）の差に比例した出力
ｖ０はヒータ１４に加えられる。１５はサーミスタであ
りヒータ１４、サーモパイル１１とともに熱伝導性の良
い材質で作られたブロック１６の中に収納される。１７
は温度演算回路でありサーミスタの抵抗Ｒｔからブロッ
ク１６の温度、即ちサーモパイル１１の温度Ｔ。を算出
し表示手段１８によって表示する。FIG. 1 is a block diagram of a radiation thermometer according to the present invention. In FIG. 1, a thermopile 11 outputs a voltage Vp corresponding to the amount of infrared radiation from the eardrum 20. An amplifier 12 slightly amplifies the output voltage vp of the thermopile 11 to a predetermined magnitude. 16 is a differential power amplifier, and an output v0 proportional to the difference between the output Va of the amplifier 12 and the reference voltage Vb (in this embodiment, Vb=O is set) is applied to the heater 14. A thermistor 15 is housed together with the heater 14 and the thermopile 11 in a block 16 made of a material with good thermal conductivity. 17
is a temperature calculation circuit which calculates the temperature of the block 16, that is, the temperature T of the thermopile 11 from the resistance Rt of the thermistor. is calculated and displayed by the display means 18.
次に動作の詳細を式を用いて詳述する。サーモパイル１
１の出力電圧■、は（３）式の如く表せる。Next, details of the operation will be explained using equations. thermopile 1
The output voltage (■) of 1 can be expressed as in equation (3).
ｖｐ＝σ・Ｋ （Ｔ’ Ｔｏ’ ） −−−
（３１一方サーモパイル１１の温度Ｔ。は、ヒータ１４
に印加される電力をＰ１周囲温度をＴａとすれば
Ｔｏ ＝ Ｔ ａ ＋ Ｐ・α ・・・・
・・・・・（６）α：比例定数
と表わすことが出来る。ヒータ１４に印加される電力Ｐ
は、差動電力増幅器１３の出力電圧Ｖ。の二乗に比例す
るので増幅器１２の利得をＧａ、差動電力増幅器１６の
利得をＧｂとすればＰ＝β・ｖｏ２
・・・・・・・・・（７）β：比例定数
＝β・ｃ、ｂ （Ｖａ Ｖｂ ）２
ここで Ｖｂ ＝ Ｏと設定されているので、Ｐ：β、
Ｇ乙Ｇハ４ ・・・・・・・・・（８）と
ｋる。（６）〜（８）式、及び（３）式よりと表せる。vp=σ・K (T'To' ) ---
(Temperature T of thermopile 11 is 31. Temperature T of thermopile 11 is
If the power applied to P1 is the ambient temperature Ta, then To = Ta + P・α...
...(6) α: Can be expressed as a constant of proportionality. Electric power P applied to heater 14
is the output voltage V of the differential power amplifier 13. Therefore, if the gain of the amplifier 12 is Ga and the gain of the differential power amplifier 16 is Gb, then P=β・vo2
・・・・・・・・・(7) β: Constant of proportionality = β・c, b (Va Vb)2 Here, since Vb = O, P: β,
G O G H 4 ・・・・・・・・・(8) and k. It can be expressed from equations (6) to (8) and equation (3).
増幅器１２と差動電力増幅器１６の利得Ｇａ、Ｇｂを十
分大きくすることによって
とすることが出来るので（９）式は（５）式の如くｋる
。This can be achieved by sufficiently increasing the gains Ga and Gb of the amplifier 12 and the differential power amplifier 16, so equation (9) becomes k as shown in equation (5).
’ｒ ＝ Ｔ、 ・・・・・
・・・・（５）Ｔｏはサーミスタ１５により検出可能で
ある。'r = T, ...
(5) To can be detected by the thermistor 15.
即ち、サーミスタ１５０Ｂ定数をＢ。、温度Ｔｎの時の
抵抗値をＲｎとすれば、サーミスタの温度がＴ。の時の
抵抗値Ｒｔは（１０１式の如くなる。That is, the thermistor 150B constant is B. , the resistance value at temperature Tn is Rn, then the temperature of the thermistor is T. The resistance value Rt at the time is as shown in equation 101.
１１ ・・・・・・・・・α０Ｒｔ＝Ｒｎｅｘ
ｐ［Ｂｏ（、； Ｔ、）］（ｔ１式より
とたりＢ。、Ｒｎ、Ｔｎを知ることによってＴ。11 ・・・・・・α0Rt=Rnex
p[Bo(,;T,)](T from the t1 formula, and by knowing B., Rn, and Tn.
が算出される。この具体的方法は例えばＵＳＰ−４４６
４０６７に記述されている。is calculated. This specific method is, for example, USP-446
4067.
以上の如くして鼓膜基Ｔが測定される。The tympanic membrane base T is measured as described above.
以上の説明で明らか々よ５に本発明によれば、鼓膜基Ｔ
はサーモパイルの感度にや増幅器の利得Ｇａ、Ｇｂ等の
変動の影響を受げｋい高精度の測定が可能となる。即ち
（９）式に於て、利得Ｇ ａ 、 Ｇ ｂ、感度Ｋ及び
他の比例定数α、β、室温Ｔａ等は全て２つの増幅器の
利得Ｇａ、Ｇｂを十分大きくすることによって無視出来
る程度に減少する。また、かくして鼓膜基はサーミスタ
の温度Ｔ。と同一となり、Ｔｏはサーミスタの抵抗−温
度換算によって知ることが可能であり、サーミスタの確
立された品質水準と相まって信頼性が高（、実現のため
のコストも安い。From the above explanation, it is clear that according to the present invention, the tympanic membrane base T
This enables highly accurate measurement, which is not affected by the sensitivity of the thermopile or variations in the gains Ga, Gb of the amplifier, etc. That is, in equation (9), the gains Ga, Gb, sensitivity K, other proportionality constants α, β, room temperature Ta, etc. can all be made negligible by making the gains Ga and Gb of the two amplifiers sufficiently large. Decrease. Also, the base of the tympanic membrane is at the temperature T of the thermistor. is the same, and To can be determined by converting the resistance of the thermistor to temperature, and coupled with the established quality standards of thermistors, the reliability is high (and the cost of implementation is low).
第１図は本発明のブロックダイヤグラムであり、第２図
は従来例のブロックダイヤグラムである。
１１・・・・・・サーモパイル、１２・・・・・・増幅
器、１６・・・・・・差動電力増幅器、１４・・・・・
・ヒータ、１５・・・・・・サーミスタ、１６・・・・
・・ブロック、１７・・・・・・温度演算回路、１８・
・・・・・表示手段、２０・・・・・・鼓Ｍ、２１・・
・・・・サーモパイル、２２・・・・・・増幅器、２６
・・・・・・抵抗−電圧変換回路、２４・・・・・・ヒ
ータ、２５・・・・・・サーミスタ、２６・・・・・・
ブロック、２７・・・・・・差動電力増幅器、２８・・
・・・・基準電圧発生回路、２９・・・・・・温度演算
回路Ａ、６０・・・・・・温度演算回路Ｂ、６１・・・
・・・表示手段、３２・・・・・・鼓膜。FIG. 1 is a block diagram of the present invention, and FIG. 2 is a block diagram of a conventional example. 11...Thermopile, 12...Amplifier, 16...Differential power amplifier, 14...
・Heater, 15... Thermistor, 16...
...Block, 17...Temperature calculation circuit, 18.
... Display means, 20 ... Drum M, 21 ...
...Thermopile, 22 ...Amplifier, 26
...Resistance-voltage conversion circuit, 24 ... Heater, 25 ... Thermistor, 26 ...
Block, 27...Differential power amplifier, 28...
... Reference voltage generation circuit, 29 ... Temperature calculation circuit A, 60 ... Temperature calculation circuit B, 61 ...
...display means, 32... eardrum.
Claims (1)
れる赤外線を計測し体温を算出する体温測定手段に於て
、サーモパイルの出力に応じてサーモパイルの温度を制
御する温度調節手段を設けたことを特徴とする放射体温
計。A body temperature measuring means for calculating body temperature by measuring infrared rays radiated from the eardrum by a thermopile inserted into the auditory canal, characterized by being provided with a temperature adjustment means for controlling the temperature of the thermopile according to the output of the thermopile. Radiation thermometer.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2072029A JPH03273121A (en) | 1990-03-23 | 1990-03-23 | Radiation thermometer |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2072029A JPH03273121A (en) | 1990-03-23 | 1990-03-23 | Radiation thermometer |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH03273121A true JPH03273121A (en) | 1991-12-04 |
Family
ID=13477579
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2072029A Pending JPH03273121A (en) | 1990-03-23 | 1990-03-23 | Radiation thermometer |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH03273121A (en) |
Cited By (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO1999058940A1 (en) * | 1998-05-08 | 1999-11-18 | Kazuhito Sakano | Radiation thermometer |
| WO2000004353A1 (en) * | 1998-07-14 | 2000-01-27 | Kazuhito Sakano | Radiation thermometer |
| WO2000035339A1 (en) * | 1998-12-15 | 2000-06-22 | Citizen Watch Co., Ltd. | Radiation clinical thermometer |
| JP2002214045A (en) * | 2001-01-12 | 2002-07-31 | Bio Ekoonetto:Kk | Infrared ray clinical thermometer |
| US6626835B1 (en) | 1999-09-03 | 2003-09-30 | Braun Gmbh | Infrared sensor stabilizable in temperature, and infrared thermometer with a sensor of this type |
| US6886978B2 (en) * | 2001-06-18 | 2005-05-03 | Omron Corporation | Electronic clinical thermometer |
| US7014358B2 (en) * | 2001-02-19 | 2006-03-21 | Braun Gmbh | Radiation thermometer comprising a heated measuring tip |
| JP2007505300A (en) * | 2003-09-09 | 2007-03-08 | ブラウン ゲーエムベーハー | Heatable infrared sensor and infrared thermometer with infrared sensor |
-
1990
- 1990-03-23 JP JP2072029A patent/JPH03273121A/en active Pending
Cited By (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO1999058940A1 (en) * | 1998-05-08 | 1999-11-18 | Kazuhito Sakano | Radiation thermometer |
| WO2000004353A1 (en) * | 1998-07-14 | 2000-01-27 | Kazuhito Sakano | Radiation thermometer |
| WO2000035339A1 (en) * | 1998-12-15 | 2000-06-22 | Citizen Watch Co., Ltd. | Radiation clinical thermometer |
| US6626835B1 (en) | 1999-09-03 | 2003-09-30 | Braun Gmbh | Infrared sensor stabilizable in temperature, and infrared thermometer with a sensor of this type |
| JP2002214045A (en) * | 2001-01-12 | 2002-07-31 | Bio Ekoonetto:Kk | Infrared ray clinical thermometer |
| JP4621363B2 (en) * | 2001-01-12 | 2011-01-26 | 株式会社バイオエコーネット | Infrared thermometer |
| US7014358B2 (en) * | 2001-02-19 | 2006-03-21 | Braun Gmbh | Radiation thermometer comprising a heated measuring tip |
| US6886978B2 (en) * | 2001-06-18 | 2005-05-03 | Omron Corporation | Electronic clinical thermometer |
| JP2007505300A (en) * | 2003-09-09 | 2007-03-08 | ブラウン ゲーエムベーハー | Heatable infrared sensor and infrared thermometer with infrared sensor |
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