JPH0536056B2 - - Google Patents
Info
- Publication number
- JPH0536056B2 JPH0536056B2 JP1212461A JP21246189A JPH0536056B2 JP H0536056 B2 JPH0536056 B2 JP H0536056B2 JP 1212461 A JP1212461 A JP 1212461A JP 21246189 A JP21246189 A JP 21246189A JP H0536056 B2 JPH0536056 B2 JP H0536056B2
- Authority
- JP
- Japan
- Prior art keywords
- temperature
- sensor
- infrared sensor
- infrared
- measured
- 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.)
- Expired - Fee Related
Links
- 238000005259 measurement Methods 0.000 claims description 8
- 230000036760 body temperature Effects 0.000 description 14
- 238000009529 body temperature measurement Methods 0.000 description 5
- 238000009792 diffusion process Methods 0.000 description 5
- QSHDDOUJBYECFT-UHFFFAOYSA-N mercury Chemical compound [Hg] QSHDDOUJBYECFT-UHFFFAOYSA-N 0.000 description 5
- 229910052753 mercury Inorganic materials 0.000 description 5
- 210000000613 ear canal Anatomy 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 239000000835 fiber Substances 0.000 description 3
- 230000000694 effects Effects 0.000 description 2
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 210000000214 mouth Anatomy 0.000 description 2
- 239000013307 optical fiber Substances 0.000 description 2
- 210000000664 rectum Anatomy 0.000 description 2
- 229910016036 BaF 2 Inorganic materials 0.000 description 1
- 229910004261 CaF 2 Inorganic materials 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 239000002775 capsule Substances 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 239000011521 glass Substances 0.000 description 1
- 229910052751 metal Inorganic materials 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 230000003287 optical effect Effects 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
Landscapes
- Radiation Pyrometers (AREA)
- Measuring And Recording Apparatus For Diagnosis (AREA)
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は、赤外線センサを用いた体温計に関す
るものである。DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a thermometer using an infrared sensor.
従来より体温計は、水銀温度計が広く使用され
ているが、最近では、デジタル電子体温計の普及
が進んで来ている。
Conventionally, mercury thermometers have been widely used as thermometers, but digital electronic thermometers have recently become more popular.
これらデジタル電子体温計は、通常センサにサ
ーミスタを用い、温度算出用の演算回路及びデジ
タル表示器を備えたものが多い。しかしながら、
測温に要する時間は２〜３分で、水銀体温計とほ
ぼ同じである。これに対して、最初の１分程度の
間の温度の上昇経過から最終値を予測する方式の
電子体温計が市販されているが、その予測値は実
際の体温と必ずしも一致しないという問題点があ
る。 These digital electronic thermometers usually use a thermistor as a sensor, and are often equipped with an arithmetic circuit for temperature calculation and a digital display. however,
The time required to measure temperature is 2 to 3 minutes, which is approximately the same as a mercury thermometer. On the other hand, there are electronic thermometers on the market that predict the final value based on the temperature rise over the first minute or so, but the problem is that the predicted value does not necessarily match the actual body temperature. .
測温時間に長時間要する因子としては、センサ
部の熱容量が挙げられる。水銀体温計の場合、ガ
ラス壁を通して水銀溜めを体温で暖め、水銀の膨
張を読み取るという経過をたどるから、加熱対象
の熱容量がかなりおおきく、そのため２〜３分の
測定時間を必要とする。電子体温計も、金属など
で、覆つた検出端を体温で暖め、間接的に熱せら
れたサーミスタの抵抗値を読み取るという経過を
経るため、やはり、測定部の熱容量の大きいこと
が問題となる。 The heat capacity of the sensor section can be cited as a factor that requires a long time for temperature measurement. In the case of a mercury thermometer, the mercury reservoir is warmed with body temperature through a glass wall and the expansion of the mercury is read, so the heat capacity of the heated object is quite large, and therefore a measurement time of 2 to 3 minutes is required. Electronic thermometers also have a problem with the large heat capacity of the measuring part, since the sensing end covered with metal or the like is warmed by body temperature and the resistance value of the heated thermistor is read indirectly.
このような問題点を解決するため、最近では、
非接触型の体温計が開発されている。この種の温
度計は、赤外線センサを用いたものが多い。しか
し、これまでに開示されている体温計には、以下
のような問題点がある。即ち、特開昭58−88627
号公報、実開昭63−157626号公報、実開昭63−
157627号公報、実開昭63−15728号公報等は赤外
線をセンサに当てるためにレンズ、ミラー等の光
学系の部品を必要とし、構造が複雑となる。ま
た、特開昭61−117422号公報には耳に挿入する方
式のもので、赤外線センサとしてサーモパイルを
用い、センサ部を一定の温度に保つため装置内に
基準温度源をもつているリフアレンス方式で体温
を測定している。これは、技術的には、優れた方
法であるが、センサ部の温度を一定に保つこと
や、基準温度源を持つているため、構造が複雑で
あるとともに製品コストが高くなるといつた問題
点がある。 In order to solve these problems, recently,
A non-contact thermometer has been developed. Many thermometers of this type use infrared sensors. However, the thermometers disclosed so far have the following problems. That is, JP-A-58-88627
Publication No. 157626, Publication No. 157626, Publication No. 157626, Utility Model Application No. 63-
157627, Utility Model Application Publication No. 63-15728, and the like require optical system parts such as lenses and mirrors in order to apply infrared rays to the sensor, resulting in a complicated structure. In addition, Japanese Patent Application Laid-open No. 117422/1983 discloses a device that is inserted into the ear, and uses a thermopile as an infrared sensor, and a reference temperature source within the device to keep the sensor part at a constant temperature. Measuring body temperature. Although this is technically an excellent method, it has problems such as keeping the temperature of the sensor part constant and having a reference temperature source, which makes the structure complicated and increases the product cost. There is.
特開昭61−138130号公報は耳孔内からの赤外線
を光フアイバで焦電センサに導く方式であるが、
体温測定用の赤外線フアイバは開発されていな
い。体温から放射される赤外線の放射エネルギー
の波長帯は８〜13μｍであり、この波長帯の赤外
線を効率よく透過させるフアイバは開発されてお
らず、また、常温付近では、このフアイバ自体か
らの放射が無視できないため、精度的に光フアイ
バを使つた体温計を実現することは困難であり、
実現したとしても非常に高価となる。 Japanese Patent Application Laid-open No. 61-138130 uses an optical fiber to guide infrared rays from inside the ear canal to a pyroelectric sensor.
Infrared fibers for measuring body temperature have not been developed. The wavelength band of infrared energy emitted from body temperature is 8 to 13 μm, and no fiber has been developed that efficiently transmits infrared rays in this wavelength band, and at room temperature, the radiation from the fiber itself is Because this cannot be ignored, it is difficult to realize a thermometer that uses optical fibers with high accuracy.
Even if it were realized, it would be extremely expensive.
また、特開昭56−46440号公報に示されるよう
に、検温時のセンサの温度変化から最終温度を予
測することにより、数十秒で検温を終了させるプ
ログラムを内蔵した体温計が実用化されている。
しかし、温度上昇パターンが人によつて異なるた
め測定精度に問題がある。 Furthermore, as shown in Japanese Patent Application Laid-Open No. 56-46440, a thermometer with a built-in program that can complete temperature measurement in several tens of seconds by predicting the final temperature from the temperature change of the sensor during temperature measurement has been put into practical use. There is.
However, there is a problem with measurement accuracy because the temperature rise pattern differs depending on the person.
本発明は、上記問題点を解決し、構造が簡単で
かつ安価に製造が可能な体温計を提供することを
目的とするものである。
An object of the present invention is to solve the above-mentioned problems and provide a thermometer that has a simple structure and can be manufactured at low cost.
本発明は、容器の先端部に設置した赤外線透過
窓と、前記赤外線透過窓の後方に設置した赤外線
センサと、前記赤外線センサと隣接して設置して
ある温度センサとからなる体温計であつて、前記
温度センサの測定温度に前記赤外線センサの測定
値を加算して前記温度センサと測定対象物の間に
温度差があるために生ずる前記温度センサの表示
温度の時間的遅れを補正する演算部と、前記演算
部からの出力を表示する表示部とからなることを
特徴とする赤外線センサを用いた体温計であり、
容器の先端部に設置した赤外線透過窓と、前記
赤外線透過窓の後方に設置した赤外線センサから
なる体温計であつて、測定時の前記赤外線センサ
のインピーダンスから求める測定温度に前記赤外
線センサの起電力から求める前記赤外線センサと
測定対象物の温度差を加算して、前記赤外線セン
サ本体と測定対象物の間に温度差があるために生
ずる前記インピーダンスから求める測定温度の時
間的遅れを前記赤外線センサの起電力から求める
温度を加算して補正する演算部と、前記インピー
ダンスを求めるための電流印加回路と電圧読取回
路および前記起電力と前記インピーダンスを求め
るための電流印加回路と電圧読取回路および前記
起電力と前記インピーダンスを交互に読み取るた
めの切り換え機構と、前記演算部からの出力を表
示する表示部からなることを特徴とする赤外線セ
ンサを用いた体温計である。
The present invention is a thermometer comprising an infrared transmitting window installed at the tip of a container, an infrared sensor installed behind the infrared transmitting window, and a temperature sensor installed adjacent to the infrared sensor, an arithmetic unit that adds the measured value of the infrared sensor to the measured temperature of the temperature sensor to correct a time delay in the displayed temperature of the temperature sensor that occurs due to a temperature difference between the temperature sensor and the object to be measured; , a display section that displays the output from the arithmetic section, and an infrared transmitting window installed at the tip of the container; and an infrared transmitting window installed at the rear of the infrared transmitting window. The thermometer includes an infrared sensor, and the temperature difference between the infrared sensor and the object to be measured, which is determined from the electromotive force of the infrared sensor, is added to the measured temperature determined from the impedance of the infrared sensor at the time of measurement, and the temperature difference between the infrared sensor body and the object to be measured is determined. a calculation unit that corrects a time delay in the measured temperature determined from the impedance caused by a temperature difference between the objects to be measured by adding the temperature determined from the electromotive force of the infrared sensor; and a current for determining the impedance. an application circuit, a voltage reading circuit, a current application circuit and a voltage reading circuit for determining the electromotive force and the impedance, a switching mechanism for alternately reading the electromotive force and the impedance, and displaying the output from the calculation section. This thermometer uses an infrared sensor and is characterized by comprising a display section.
また、赤外線センサとしてサーモパイルを用い
ることを特徴とし、温度センサが直接温度を測定
するサーミスタ、ダイオード、トランジスタであ
ることを特徴とする。 It is also characterized in that a thermopile is used as the infrared sensor, and the temperature sensor is a thermistor, diode, or transistor that directly measures temperature.
本発明は、通常のサーミスタ等を利用した体温
を直接測定している電子体温計の応答性の遅さを
応答性の速い赤外線センサの出力で補正すること
により、短時間に体温が測定できるようにしたも
のである。
The present invention makes it possible to measure body temperature in a short time by correcting the slow response of electronic thermometers that directly measure body temperature using ordinary thermistors, etc., with the output of a fast-responsive infrared sensor. This is what I did.
以下、図面を用いて本発明を詳細に説明する。
第１図は、本発明の実施態様の一例を示したもの
で、１は赤外線センサ（サーモパイル）である。
サーモパイル１には温度センサ２が付設されてい
る。３は赤外線を透過する赤外線透過窓、４は体
温計を耳孔又は口腔や直腸に挿入するための容器
であり外側が濡れても測定に支障がないように密
閉してある。５，６は赤外線センサ及び温度セン
サからの出力を取り出すためのリード線で外側は
絶縁してあり、７は信号処理部、８は表示部であ
る。 Hereinafter, the present invention will be explained in detail using the drawings.
FIG. 1 shows an example of an embodiment of the present invention, where 1 is an infrared sensor (thermopile).
A temperature sensor 2 is attached to the thermopile 1. 3 is an infrared transmitting window that transmits infrared rays; 4 is a container for inserting the thermometer into the ear canal, oral cavity, or rectum; the container is sealed so that measurement will not be affected even if the outside gets wet. 5 and 6 are lead wires for taking out the output from the infrared sensor and the temperature sensor, and are insulated on the outside, 7 is a signal processing section, and 8 is a display section.
熱電型の赤外線センサはサーモパイル、焦電素
子、ボロメータ等があるが、サーモパイルが使用
簡便性、コンパクト性等から望ましい。また温度
センサ２としては、サーモパイル等のように冷接
点と温接点の温度差によつて生じる起電力から被
測定物の温度を間接的にもとめるセンサではな
く、通常の電子体温計のように直接温度を求める
センサ即ちサーミスタ、ダイオード、トランジス
タ等のセンサを用いる。ポジスタやダイオード等
は温度が上昇すると抵抗値や拡散電位が直線的に
変化する事は公知である。その一例としてダイオ
ードの拡散電位の温度特性を第３図に示す。縦軸
に拡散電位、横軸に温度をとつたもので、温度の
上昇と共に拡散電位が下降する事が明らかであ
る。温度センサ２によつて体温を測定する際に
は、人体から温度センサ２に熱が伝わり温度セン
サ２の温度が体温に一致する必要がある。通常
は、温度センサ２と被測定物である人体の間に温
度差があるために、数分以上の時間遅れが発生す
る。一方、赤外線センサ１は、センサと被測定物
の温度差しか測れないが、非常に応答性が速いと
いう特徴を持つている。 Thermoelectric infrared sensors include thermopiles, pyroelectric elements, bolometers, etc., but thermopiles are preferred because of their ease of use and compactness. In addition, the temperature sensor 2 is not a sensor that indirectly determines the temperature of the object to be measured from the electromotive force generated by the temperature difference between cold and hot junctions, such as a thermopile, but a sensor that directly measures the temperature of the object, such as an ordinary electronic thermometer. A sensor such as a thermistor, diode, or transistor is used to determine the It is well known that the resistance value and diffusion potential of POSISTORs, diodes, etc. change linearly as the temperature rises. As an example, the temperature characteristics of the diffusion potential of a diode are shown in FIG. The vertical axis represents the diffusion potential and the horizontal axis represents the temperature, and it is clear that the diffusion potential decreases as the temperature rises. When measuring body temperature with the temperature sensor 2, heat must be transferred from the human body to the temperature sensor 2, and the temperature of the temperature sensor 2 must match the body temperature. Usually, a time delay of several minutes or more occurs because there is a temperature difference between the temperature sensor 2 and the human body as the object to be measured. On the other hand, the infrared sensor 1 can only measure the difference in temperature between the sensor and the object to be measured, but it has a feature of very quick response.
本発明では、この温度センサ２と人体の間に温
度差があるために生ずる温度センサ２の応答の時
間遅れを応答速度の速い赤外線センサ１の出力で
補正をおこなう。 In the present invention, the time delay in the response of the temperature sensor 2, which occurs due to the temperature difference between the temperature sensor 2 and the human body, is corrected by the output of the infrared sensor 1, which has a fast response speed.
補正の方法としては、赤外線センサ１が検出す
る温度センサ２と被測定物の間の温度差を温度セ
ンサ２が示す温度値に加える事により、被測定物
の温度が迅速に計測できる。第１図の信号処理部
７では、温度センサ２と赤外線センサ１の出力を
増幅した後、それぞれ温度センサ２の温度と温度
センサ２・被測定物間の温度差に変換して加え合
わせて被測定物の温度を求める。温度センサ２と
赤外線センサ１の感度は個々のセンサによつて異
なるので、予め例えば、第３図や第５図のような
データを用いて校正しておく。 As a correction method, the temperature of the object to be measured can be quickly measured by adding the temperature difference between the temperature sensor 2 detected by the infrared sensor 1 and the object to be measured to the temperature value indicated by the temperature sensor 2. In the signal processing unit 7 in FIG. 1, the outputs of the temperature sensor 2 and the infrared sensor 1 are amplified, and then converted into the temperature of the temperature sensor 2 and the temperature difference between the temperature sensor 2 and the object to be measured, and added. Find the temperature of the object to be measured. Since the sensitivities of the temperature sensor 2 and the infrared sensor 1 differ depending on the individual sensors, they are calibrated in advance using data such as those shown in FIGS. 3 and 5, for example.
次に、赤外線センサのインピーダンスを測定し
て体温を求める場合について説明する。第２図に
その実施態様の例を示す。１０はサーモパイル、
３は赤外線透過窓、４は体温計を耳孔または口腔
や直腸に挿入するための容器で密閉してある。５
はサーモパイルの出力を取り出すためのリード線
で外側は絶縁してあり、１７は信号処理部、８は
表示部である。 Next, a case will be described in which body temperature is determined by measuring the impedance of an infrared sensor. FIG. 2 shows an example of its implementation. 10 is a thermopile,
3 is an infrared transmitting window, and 4 is a sealed container for inserting the thermometer into the ear canal, oral cavity, or rectum. 5
1 is a lead wire for taking out the output of the thermopile and is insulated on the outside, 17 is a signal processing section, and 8 is a display section.
被測定物の温度は第４図に示した関係から赤外
線センサ１のインピーダンスの変化により測定す
る。この場合、被測定物と赤外線センサ１の温度
差によりインピーダンスの変化に応答遅れのある
ことは温度センサ２を用いた場合と同様である。
温度センサ２を用いた場合と異なる点として、第
２図では、赤外線センサのインピーダンスを測定
するために赤外線センサに電流を印加する機構が
必要となる。この電流印加機構は特殊な回路は必
要とせず、ごく普通の定電流回路で良い。またサ
ーモパイルのインピーダンスの測定と、赤外線が
照射されたことによるサーモパイル自身の赤外線
センサとしての起電力を交互に測定する必要があ
る。この機構は切り換え機構付き定電流回路９に
より達成される。このようにして得られたサーモ
パイルのインピーダンスと起電力は信号処理部１
７によつて、補正加算され、温度表示部８で表示
される。 The temperature of the object to be measured is measured by changing the impedance of the infrared sensor 1 based on the relationship shown in FIG. In this case, as in the case where the temperature sensor 2 is used, there is a response delay in impedance change due to the temperature difference between the object to be measured and the infrared sensor 1.
2 requires a mechanism for applying current to the infrared sensor in order to measure the impedance of the infrared sensor. This current applying mechanism does not require any special circuit, and may be a very ordinary constant current circuit. It is also necessary to alternately measure the impedance of the thermopile and the electromotive force of the thermopile itself as an infrared sensor due to irradiation with infrared rays. This mechanism is achieved by a constant current circuit 9 with a switching mechanism. The impedance and electromotive force of the thermopile obtained in this way are determined by the signal processing unit 1.
7, the temperature is corrected and added and displayed on the temperature display section 8.
補正の方法としては、赤外線センサ１のインピ
ーダンスから得られる赤外線センサ１自身の温度
に赤外線センサ１の起電力として表れる赤外線セ
ンサ１と被測定物の間の温度差を加える事により
被測定物の温度が迅速に計測できる。第２図の信
号処理部１７では、先ず定電流を印加した時の赤
外線センサ１の出力と定電流を印加しない時の赤
外線センサ１の出力の差から赤外線センサ１のイ
ンピーダンスを求めて赤外線センサ１の温度をも
とめる。本方法によつてもとめた赤外線センサ１
の温度は、サーモパイルの温接点と冷接点の中間
の温度であるが、体温測定の場合温接点と冷接点
の温度差は0.01℃以下であるから大きな誤差は生
じない。赤外線センサ１のインピーダンス変化は
個々のセンサによつて異なるので、予め例えば第
４図のようなデータを用いて校正しておく。この
インピーダンスの個々のセンサによる差は素線の
材質・太さ等によるもので、同じ材質でも線の幅
が太く、厚みが厚くなれば、インピーダンスは小
さくなる。赤外線センサ１の起電力から求められ
る赤外線センサ１・被測定物間の温度差を赤外線
センサ１の温度に加えて被測定物の温度を求め
る。 The correction method is to calculate the temperature of the object to be measured by adding the temperature difference between the infrared sensor 1 and the object to be measured, which appears as the electromotive force of the infrared sensor 1, to the temperature of the infrared sensor 1 itself obtained from the impedance of the infrared sensor 1. can be measured quickly. The signal processing unit 17 in FIG. 2 first calculates the impedance of the infrared sensor 1 from the difference between the output of the infrared sensor 1 when a constant current is applied and the output of the infrared sensor 1 when no constant current is applied. Find the temperature of Infrared sensor 1 obtained by this method
The temperature is between the hot and cold junctions of the thermopile, but when measuring body temperature, the temperature difference between the hot and cold junctions is less than 0.01°C, so there is no large error. Since the impedance change of the infrared sensor 1 differs depending on the individual sensor, it is calibrated in advance using data as shown in FIG. 4, for example. This difference in impedance between individual sensors is due to the material and thickness of the wire, and even if the wire is made of the same material, the wider and thicker the wire, the smaller the impedance. The temperature difference between the infrared sensor 1 and the object to be measured, which is determined from the electromotive force of the infrared sensor 1, is added to the temperature of the infrared sensor 1 to obtain the temperature of the object to be measured.
耳孔等に挿入される容器は円筒形のものがもち
いられるが、必ずしも円筒形である必要はなく、
四角形、多角形、カプセルタイプ等どのような形
でもよい。また、赤外線透過窓には、Si、BaF2、
CaF2、KrF等が用いられる。また窓そのものを
省略できる場合は省略してもよい。 A cylindrical container is used for the container inserted into the ear canal, but it does not necessarily have to be cylindrical.
It may be of any shape such as rectangle, polygon, capsule type, etc. In addition, the infrared transmitting window contains Si, BaF 2 ,
CaF 2 , KrF, etc. are used. Furthermore, if the window itself can be omitted, it may be omitted.
以下、実施例により具体的に説明する。 Hereinafter, this will be explained in detail using examples.
第６図、第１図の体温計で舌下の温度を測定し
た際に得られるデータである。ａは温度センサ２
の出力であり、測定開始より２分過ぎても指示値
は上昇し続ける。一方、ｂのサーモパイルの温度
差出力は、測定開始後すぐに応答し、温度センサ
２の温度が上昇するにつれてサーモパイルの温度
も上昇するためサーモパイルの起電力は小さくな
る。そこで、ａの温度指示値にｂの温度差出力を
加えると体温ｃが迅速に得られる。
FIG. 6 is data obtained when sublingual temperature is measured with the thermometer shown in FIG. a is temperature sensor 2
The indicated value continues to rise even after 2 minutes have passed since the start of measurement. On the other hand, the temperature difference output of the thermopile b responds immediately after the start of measurement, and as the temperature of the temperature sensor 2 rises, the temperature of the thermopile also rises, so the electromotive force of the thermopile becomes smaller. Therefore, by adding the temperature difference output b to the temperature instruction value a, the body temperature c can be quickly obtained.
第７図は第１図の体温計で耳腔内の温度を測定
した例である。容器４と耳腔との接触は舌下の場
合ほど密ではないので、温度センサ２ａの出力は
第６図よりさらに応答が遅い。しかし、サーモパ
イルの温度差出力ｂがその分を補うため、最終的
な体温の測定ｃは第６図同様瞬時に行える。 FIG. 7 is an example of measuring the temperature inside the ear cavity using the thermometer shown in FIG. Since the contact between the container 4 and the ear cavity is not as close as under the tongue, the response of the output of the temperature sensor 2a is even slower than in FIG. However, since the temperature difference output b of the thermopile compensates for this difference, the final body temperature measurement c can be performed instantaneously as in FIG.
第８図は、第２図の体温計で舌下の温度を測定
した際に得られたデータである。サーモパイルの
インピーダンス変化でサーモパイルの温度を測定
している点と室温が高い点が第６図・第７図と異
なるが、最終的な体温の測定結果ｃは、第６図・
第７図と同等である。 FIG. 8 shows data obtained when sublingual temperature was measured with the thermometer shown in FIG. 2. The difference from Figures 6 and 7 is that the temperature of the thermopile is measured by changes in the impedance of the thermopile and that the room temperature is higher, but the final body temperature measurement result c is as shown in Figures 6 and 7.
It is equivalent to Fig. 7.
本発明は、通常の電子体温計に対し、サーミス
タ、ダイオード、トランジスタ等直接温度を測定
する温度センサの昇温の時間遅れを、赤外線セン
サの出力で補正する機能を付加したことにより、
迅速かつ正確に体温の測定が可能になり、その実
用価値をさらに高めることができる。
The present invention adds a function to a normal electronic thermometer that uses the output of an infrared sensor to correct the time delay in temperature rise of temperature sensors such as thermistors, diodes, and transistors that directly measure temperature.
It becomes possible to measure body temperature quickly and accurately, further increasing its practical value.
第１図は本発明の実施態様の１例を示したもの
で、第２図は実施態様の別の例を示したもので、
第３図はダイオード温度センサの拡散電位と温度
の関係を示す一例であり、第４図は、サーモパイ
ルのインピーダンスと温度の関係を示す一例であ
り、第５図は人体・サーモパイル間の温度差とサ
ーモパイルの起電力の関係を示すデータ例、第６
図は、第１図の体温計で舌下温を測定したデータ
例、第７図は第１図の体温計で耳腔内温を測定し
たデータ例、第８図は第２図の体温計で舌下温を
測定したデータ例である。
１……赤外線センサ、２……温度センサ、３…
…赤外線透過窓、４……容器、５，６……リード
線、７，１７……信号処理部、８……表示部、１
０……サーモパイル。
FIG. 1 shows one example of the embodiment of the present invention, and FIG. 2 shows another example of the embodiment,
Figure 3 is an example of the relationship between the diffusion potential of a diode temperature sensor and temperature, Figure 4 is an example of the relationship between thermopile impedance and temperature, and Figure 5 is an example of the relationship between the temperature difference between the human body and the thermopile. Example of data showing the relationship between electromotive force of thermopile, No. 6
The figure shows an example of data obtained by measuring sublingual temperature with the thermometer shown in Fig. 1, Fig. 7 shows an example of data measuring temperature inside the ear cavity with the thermometer shown in Fig. 1, and Fig. 8 shows an example of data obtained by measuring sublingual temperature with the thermometer shown in Fig. 2. This is an example of data obtained by measuring temperature. 1...Infrared sensor, 2...Temperature sensor, 3...
...Infrared transmission window, 4... Container, 5, 6... Lead wire, 7, 17... Signal processing section, 8... Display section, 1
0...Thermopile.
Claims (1)
記赤外線透過窓の後方に設置した赤外線センサ
と、前記赤外線センサと隣接して設置してある温
度センサとからなる体温計であつて、 前記温度センサの測定温度に前記赤外線センサ
の測定値を加算して前記温度センサと測定対象物
の間に温度差があるために生ずる前記温度センサ
の表示温度の時間的遅れを補正する演算部と、 前記演算部からの出力を表示する表示部とから
なることを特徴とする赤外線センサを用いた体温
計。 ２ 容器の先端部に設置した赤外線透過窓と、前
記赤外線透過窓の後方に設置した赤外線センサか
らなる体温計であつて、 測定時の前記赤外線センサのインピーダンスか
ら求める測定温度に、前記赤外線センサの起電力
から求める前記赤外線センサと測定対象物の温度
差を加算して前記赤外線センサ本体の温度と測定
対象物の間に温度差があるために生ずる前記イン
ピーダンスから求めた測定温度の時間的遅れを補
正する演算部と、 前記インピーダンスを交互に読み取るための切
り換え機構と、 前記演算部からの出力を表示する表示部からな
ることを特徴とする赤外線センサを用いた体温
計。 ３ 赤外線センサとしてサーモパイルを用いるこ
とを特徴とする請求項１又は２記載の体温計。 ４ 温度センサが直接温度を測定するサーミス
タ、ダイオード、トランジスタであることを特徴
とする請求項１記載の体温計。[Scope of Claims] 1. A thermometer comprising an infrared transmitting window installed at the tip of a container, an infrared sensor installed behind the infrared transmitting window, and a temperature sensor installed adjacent to the infrared sensor. The temperature measured by the infrared sensor is added to the temperature measured by the temperature sensor to correct a time delay in the temperature displayed by the temperature sensor that occurs due to a temperature difference between the temperature sensor and the object to be measured. A thermometer using an infrared sensor, comprising: a calculation section; and a display section that displays an output from the calculation section. 2. A thermometer consisting of an infrared transmitting window installed at the tip of a container and an infrared sensor installed behind the infrared transmitting window, wherein the measurement temperature determined from the impedance of the infrared sensor at the time of measurement is Adding the temperature difference between the infrared sensor and the object to be measured obtained from the electric power to correct a time delay in the measured temperature obtained from the impedance that occurs due to a temperature difference between the temperature of the infrared sensor body and the object to be measured. A thermometer using an infrared sensor, comprising: a calculation section for reading the impedance alternately, a switching mechanism for alternately reading the impedance, and a display section for displaying the output from the calculation section. 3. The thermometer according to claim 1 or 2, characterized in that a thermopile is used as the infrared sensor. 4. The thermometer according to claim 1, wherein the temperature sensor is a thermistor, diode, or transistor that directly measures temperature.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1212461A JPH0375531A (en) | 1989-08-18 | 1989-08-18 | Clinical thermometer using infared-ray sensor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1212461A JPH0375531A (en) | 1989-08-18 | 1989-08-18 | Clinical thermometer using infared-ray sensor |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH0375531A JPH0375531A (en) | 1991-03-29 |
| JPH0536056B2 true JPH0536056B2 (en) | 1993-05-28 |
Family
ID=16623020
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1212461A Granted JPH0375531A (en) | 1989-08-18 | 1989-08-18 | Clinical thermometer using infared-ray sensor |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0375531A (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110022793A (en) * | 2016-12-05 | 2019-07-16 | 夏普株式会社 | Thermointegrator tool |
| CN116723798A (en) * | 2021-01-18 | 2023-09-08 | 索尼集团公司 | Biological information processing device, biological information processing system, and biological information processing method |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5310467A (en) * | 1976-07-16 | 1978-01-30 | Citizen Watch Co Ltd | Electronic timepiece with multiple alarms |
| JPS6017711U (en) * | 1975-03-15 | 1985-02-06 | ハインツ・マック | Dental articulator resin model mounting plate |
| US4784149A (en) * | 1986-01-13 | 1988-11-15 | Optical Sensors, Inc. | Infrared thermometer with automatic calibration |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS63157628U (en) * | 1987-04-03 | 1988-10-17 |
-
1989
- 1989-08-18 JP JP1212461A patent/JPH0375531A/en active Granted
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS6017711U (en) * | 1975-03-15 | 1985-02-06 | ハインツ・マック | Dental articulator resin model mounting plate |
| JPS5310467A (en) * | 1976-07-16 | 1978-01-30 | Citizen Watch Co Ltd | Electronic timepiece with multiple alarms |
| US4784149A (en) * | 1986-01-13 | 1988-11-15 | Optical Sensors, Inc. | Infrared thermometer with automatic calibration |
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0375531A (en) | 1991-03-29 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| JP2826337B2 (en) | Radiation thermometer | |
| RU2118116C1 (en) | Thermometer for measuring the temperature of body and method of measuring the patient's body temperature (variants) | |
| JP4214124B2 (en) | Ear thermometer | |
| USRE34507E (en) | Radiation clinical thermometer | |
| US7036978B2 (en) | Pyrometer | |
| US5232284A (en) | Radiation clinical thermometer | |
| JPH0741026B2 (en) | Thermometer | |
| JP2603004B2 (en) | Temperature measuring device and method for providing temperature signal | |
| JP2828258B2 (en) | Radiation thermometer | |
| JPH0666639A (en) | Infrared thermometer | |
| JPH0536056B2 (en) | ||
| JPH04299225A (en) | Clinical thermometer | |
| JPH03273121A (en) | Radiation thermometer | |
| JP2813331B2 (en) | Radiation thermometer | |
| KR100458154B1 (en) | forehead fitted type infrared thermometer and control method thereof | |
| JPH0271124A (en) | Optical thermometer | |
| JP3733846B2 (en) | Correction system control method, thermometer and correction device | |
| JPH08278203A (en) | Infrared ray radiation thermometer | |
| JP3338456B2 (en) | Radiation thermometer and method of measuring temperature of radiation thermometer | |
| JP3175775B2 (en) | Temperature measurement method of radiation thermometer and radiation thermometer | |
| JPH08254466A (en) | Radiation thermometer | |
| JPH10290790A (en) | Radiation thermometer | |
| JPH03249527A (en) | Bodily temperature measuring instrument | |
| JPH0375530A (en) | Radiation thermometer | |
| JP2005334254A (en) | Eardrum thermometer |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20080528 Year of fee payment: 15 |
|
| FPAY | Renewal fee payment (event date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20090528 Year of fee payment: 16 |
|
| LAPS | Cancellation because of no payment of annual fees |