USRE34507E - Radiation clinical thermometer - Google Patents

Abstract

A radiation clinical thermometer includes a probe, a detection signal processing section, a body temperature operating section, and a display unit. A filter correction section for setting a correction value based on the transmission wavelength characteristics of a filter is arranged. The body temperature operating section receives infrared data, temperature-sensitive data, and the correction value from the filter correction section so as to calculate body temperature data.

Description

.Iadd.

This is a continuation of application Ser. No. 07/605,589, filed Oct. 29, 1990, now abandoned, which is a reissue of application Ser. No. 07/335,616, filed Jul. 10, 1989, now U.S. Pat. No. 4,932,789. .Iaddend.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to a portable, compact radiation clinical thermometer for measuring a temperature upon insertion in an external ear canal.

2. Description of the Prior Art

Recently, a pen type electronic clinical thermometer has been widely used in place of a glass clinical thermometer.

This electronic clinical thermometer is not fragile, can perform a digital display which is easy to read, and can generate an alarm sound such as a buzzer sound for signaling the end of temperature measurement. However, this clinical thermometer requires about 5 to 10 minutes for temperature measurement, i.e., substantially the same length of time as that required by a glass clinical thermometer. This makes a user feel that body temperature measurement is cumbersome. Such a long measurement time is based on a method of inserting a sensor portion in an armpit or a mouth and bringing it into contact with a portion to be measured. A measurement time is prolonged due to the following two reasons:

(1) A skin temperature at an armpit or a mucous membrane temperature in a mouth is not equal to a body temperature prior to temperature measurement, and gradually reaches the body temperature after the armpit or the mouth is closed.

(2) Since the sensor portion of the clinical thermometer has been cooled down to an ambient temperature, when it is inserted in a portion to be measured, the temperature of the portion is further lowered.

Temperature measurement of a conventional clinical thermometer will be described with refence to FIG. 1.

FIG. 1 shows temperature measurement curves of a contact type electronic clinical temperature. In FIG. 1, temperature measurement time is plotted along the axis of abscissa and measurement temperatures are plotted along the axis of ordinate. A curve H represents a temperature curve of an armpit as a portion to be measured; and a curve M, a measurement temperature curve obtained by the clinical thermometer. Accordingly, the skin temperature of the armpit is 36° C. or less at measurement start time t₁, and the temperature of a clinical thermometer sensor portion is cooled to 30° C. or less. When the sensor portion is inserted in the armpit in this state, and the armpit is closed, the measurement temperature represented by the curve M of the sensor portion is quickly raised. However, the temperature represented by the curve H of the armpit begins to rise gradually toward an actual body temperature T_b after it is cooled by the sensor portion to a temperature at time t₂. The two temperature curves H and M coincidentally rise from time t₃ when the sensor portion is warmed to the skin temperature of the armpit. As described above, however, it takes about 5 to 10 minutes for the curve to reach the actual body temperature. As is known, a method of measuring a body temperature is performed in practice as follows. Measurement is performed from time t₁ at predetermined intervals. The measurement values are compared with each other, and maximum values are sequentially stored. At the same time, a difference between the measurement values is sequentially checked. The instant when the difference becomes smaller than a predetermined value is set at time t₄, and the temperature measurement is stopped. Thus, the greatest value at this time is displayed as a body temperature e.g., Japanese Patent Laid-Open (Kokai) No. 50-31888).

In consideration of the above-described reasons (1) and (2), conditions for performing body temperature measurement within a short period of time are: selection of a portion having a body temperature prior to measurement, and an actual measurement without bringing a cooled sensor portion into contact with the portion to be measured.

A drum membrane is, therefore, selected as a portion having a body temperature prior to measurement, and a radiation clinical thermometer is proposed as a clinical thermometer for measuring the temperature of the portion in a nontact manner (e.g., U.S. Pat. No. 3,282,106).

The principle of a radiation thermometer on which the above radiation clinical thermometer is based will be described below.

A radiation thermometer is based on a law of physics, i.e., "all objects emit infrared radiation from their surfaces, and the infrared radiation amounts and the spectral characteristics of the objects are determined by their absolute temperatures as well as their properties and states of their finished surfaces." This law will be described with reference to the following laws.

The Planck's law states a relationship between the radiant intensity, spectral distribution, and temperature of a blackbody as follows:

W(λ,T)═2πc.sup.2 h/λ.sup.5 (e.sup.hc/k λT -1).sup.-1                                                ( 1)

where

W (λ,T): spectral radiant emittance [W/cm². μm]

T: absolute temperature of blackbody [K]

λ: wavelength of radiation [μm]

c: velocity of light═2.998×10¹⁰ [cm/sec]

h: Planck's constant═6.625×10^-34 [W.sec^2]

k: Boltzmann constant═1.380×10²³ [W.sec/K]

FIG. 3 shows the Planck's law. As is apparent from FIG. 3, as the temperature of the blackbody rises, the radiation energy is increased. In addition, the radiation energy varies depending on wavelengths. The peak value of the radiant emittance distribution shifts to the short wavelength side with an increase in temperature, and the radiation occurs over a wide wavelength band.

Total energy radiated from the blackbody can be obtained by integrating W(λ, T) given by equation (1) with respect to λ from λ═0 to λ═∞. This is the Stefan-Boltzmann law. ##EQU1##

W₁ : total energy radiated from blackbody [W/cm² ]σ: Stefan-Boltzmann constant═5.673×10¹² [W/cm²..deg⁴ ]

As is apparent from equation (2), the total radiation energy W₁ is proportional to a power of four of the absolute temperature of the blackbody light source. Note that equation (2) is obtained by integrating the infrared radiation emitted from the blackbody with respect to all the wavelengths.

All the above-described laws are derived from the blackbody having an emissivity of 1.00. In practice, however, most objects are not ideal radiators, and hence have emissivities smaller than 1.00. For this reason the value obtained by equation (2) must be corrected by multiplying a proper emissivity. Radiation energy of most objects other than the blackbody can be represented by equation (3): ##EQU2##

ε: emissivity of object

Equation (3) represents infrared energy which is radiated from an object and incident on an infrared sensor. However, the infrared sensor itself emits infrared radiation in accordance with the same law described above. Therefore, if the temperature of the infrared sensor itself is T₀, its infrared radiation energy can be given as σT₀⁴, and energy W obtained by subtracting radiation energy from incident energy is given by equation (4):

W═σ(εT.sup.4 +γT.sub.a.sup.4 -T.sub.0.sup.4) (4)

T_a : ambient temperature of object

γ: reflectance of object

Since the transmittance of the object to be measured can be regarded as zero, γ═1-ε can be established.

In equation (4), the infrared sensor is considered to be ideal and hence has an emissivity of 1.00.

In addition, assuming that the infrared sensor is left in an atmosphere of an ambient temperature T_a so that the infrared sensor temperature T₀ is equal to the ambient temperature T_a, equations (4) can be rewritten as equation (5): ##EQU3##

FIG. 2 shows a basic arrangement of a conventional radiation thermometer. The arrangement will be described below with reference to FIG. 2.

A radiation thermometer comprises anoptical system 2, a detectingsection 3, anamplifying section 4, anoperating section 5, and adisplay unit 6.

Theoptical system 2 is constituted by a focusing means 2a for efficiently focusing infrared radiation from an object L to be measured, and afilter 2b having transmission wavelength characteristics. A cylindrical member having an inner surface plated with gold is used as the focusing means 2a. A silicon filter is used as afilter 2b.

The detectingsection 3 is constituted by aninfrared sensor 3a and a temperature-sensitive sensor 3b. Theinfrared sensor 3a converts infrared radiation energy obtained by subtacting its own radiation energy from incident infrared radiation energy focused by theoptical system 2 into an electrical signal, i.e., an infrared voltage v_s. In addition, the temperature-sensitive sensor 3b is arranged near theinfrared sensor 3a to measure the temperature of theinfrared sensor 3a and its ambient temperature T₀, and outputs a temperature-sensitive voltage v_t. A thermopile and a diode are respectively used as theinfrared sensor 3a and the temperature-sensitive sensor 3b.

The amplifyingsection 4 comprises an infrared amplifier 4a, constituted by an amplifying circuit and an A/D converter for converting an output voltage from the amplifying circuit into digital infrared data V_d, for amplifying the infrared voltage v_s output from the thermopile, and a temperature-sensitive amplifier 4b, constituted by an amplifying circuit and an A/D converter for converting an output voltage from the amplifying circuit into digital temperature-sensitive data, for amplifying the temperature-sensitive voltage v_t as a forward-biased voltage from the temperature-sensitive sensor 3b, i.e., the diode.

Two signals V_d and T₀ from the amplifyingsection 4 are then converted into temperature data T, and are displayed on thedisplay unit 6. Theoperating section 5 comprises an emissivity input means 5a for setting an emissivity ε of the object L, and an operating circuit 5c for performing an operation based on equation (5).

With the above-described arrangement, temperature measurement of the object L can be performed by a noncontact scheme. An operation of this temperature measurement will be described below.

The object L emits infrared radiation, and its wavelength spectrum distribution covers a wide wavelength range, as shown in FIG. 3. The infrared radiation is focused by the focusing means 2a, transmitted through thefilter 2b having the transmission wavelength characteristics, and reaches theinfrared sensor 3a.

Other infrared radiation energies reach theinfrared sensor 3a. One is infrared radiation energy emitted from a certain object near the object L, which is reflected by the object L and is then transmitted through thefilter 2b and reaches the infrared radiation energy. Another is infrared radiation energy emitted from theinfrared sensor 3a or a certain object near thesensor 3a, which is reflected by thefilter 2b and reaches thesensor 3a. Still another is infrared radiation enengy which is emitted from thefilter 2b and reaches thesensor 3a.

The infrared radiation energy from theinfrared sensor 3a can be represented by equation (3). In this case, ε═1.00. That is, to measure the temperature of theinfrared sensor 3a itself is to indirectly measure the infrared radiation energy from theinfrared sensor 3a. For this purpose, the temperature-sensitive sensor 3b is arranged near theinfrared sensor 3a and measures the temperature of theinfrared sensor 3a and the ambient temperature T₀. Theinfrared sensor 3a converts the infrared radiation energy W obtained by subtracting infrared radiation energy emitted therefrom from infrared radiation energy incident thereon into an electrical signal. Since theinfrared sensor 3a employs a thermopile, it outputs the infrared voltage v_s proportional to the infrared radiation energy W.

In this case, the infrared voltage v_s as an output voltage from theinfrared sensor 3a corresponds to a value obtained by multiplying the product of the infrared radiation energy W per unit area and a light-receiving area S of theinfrared sensor 3a by a sensitivity R. The infrared data V_d as an output voltage from the infrared amplifier 4a corresponds to a value obtained by multiplying the infrared voltage v_s from theinfrared sensor 3a by a gain A of the infrared amplifier 4a.

V.sub.s ═R.W.S

V.sub.d ═A.v.sub.s

Since the above equations can be established, equation (5) can be expressed as equation (6) as follows:

V.sub.d ═ε.σSRA(T.sup.4 -T.sub.0.sup.4)  (6)

where

V_d : output voltage from infrared amplifier 4a

S: light-receiving area ofinfrared sensor 3a

R: sensitivity of infrared sensor

A: gain of infrared amplifier 4a

Generally, equation (6) is simplified by setting K₁ ═σSRA, and hence the temperature T of the object L is calculated according to equation (7). ##EQU4##

A thermal infrared sensor used for a conventional radiation thermometer has no wavelength dependency. However, a transmission member such as a silicon or quarts filter is arranged as a window member on the front surface of a can/package in which the infrared sensor is mounted due to the following reason. Since infrared radiation from an object has the wavelength spectrum distribution shown in FIG. 3, such a filter is used to transmit only infrared radiation having a main wavelength band therethrough so as to reduce the influences of external light. Each of the above-described transmission members has unique transmission wavelength characteristics. A proper transmission member is selected on the basis of the temperature of an object to be measured, workability and cost of a transmission member and the like.

FIG. 4 shows the transmittance of a silicon filter as one of the transmission members. The silicon filter shown in FIG. 4 transmits only infrared radiation having a wavelength band from about 1 to 18 [μm] therethrough, and has a transmittance of about 54%.

As described above, an infrared sensor with a filter has wavelength dependency, i.e., transmits infrared radiation having a specific wavelength band because of the filter as a window member although the sensor itself is a temperature sensor and has no wavelength dependency.

Therefore, equation (5) obtained by integrating infrared radiation energy incident on the infrared sensor with a filter with respect to all the wavelengths cannot be applied to the infrared sensor with a filter for transmitting infrared radiation having a specific wavelength band, and an error is included accordingly.

Furthermore, in the conventional arrangement, the sensitivity R of the infrared sensor is used as a constant. In practice, however, the sensitivity R of the infrared sensor varies depending on the infrared sensor temperature T₀. FIG. 5 shows this state. In FIG. 5, the sensitivity R is obtained by actually measuring the output voltage v_s from a thermopile as an infrared sensor by using a blackbody, and the infrared sensor temperature T₀ is changed to plot changes in sensitivity R at the respective temperatures. As a result, it is found that the temperature dependency of the sensitivity R can be approximated to a straight line as represented by equation (8):

R═a {1-β(T.sub.0 -T.sub.m)}                       (8)

where a is the sensitivity R as a reference when T₀ ═T_m,, T_m is a representative infrared sensor temperature, e.g., an infrared sensor temperature measured in a factory, and β represents a coefficient of variation, In this case, a coefficient of variability per 1 [deg] is -0.3 [%/deg]. The variation in sensitivity R described above inevitably becomes an error.

The coefficient of variation β is influenced by the manufacturing conditions of a thermopile, and can be decreased by increasing the purity and process precision of the thermopile. However, thermopiles on the market which are mass-produced have the above value.

A radiation thermometer, however, is normally designed to measure high temperatures, and has a measurement range from about 0° to 300° C. and measurement precision of about ±2° to 3° C. Therefore, errors due to the above-described filter characteristics, variations in sensitivity of an infrared sensor, and the like are neglected, and hence no countermeasure has been taken so far. When measurement conditions as a clinical thermometer are taken into consideration, however, a temperature measurement range may be set to be as small as about 33° C. to 43° C., but ±0.1° C. is required for temperature measurement precision. Therefore, if the above-described radiation thermometer is used as a clincial thermometer, temperature measurement precision must be increased by taking countermeasures against errors due to the filter characteristics and the variations in sensitivity of infrared radiation.

A radiation clinical thermometer disclosed in U.S. Pat. No. 4,602,642 employs the following system as a countermeasure.

This radiation clinical thermometer comprises three units, i.e., a probe unit having an infrared sensor, a chopper unit having a target, and a charging unit. In addition, a heating control means for preheating the infrared sensor and the target to a reference temperature (36.5° C.) of the external ear canal is provided, and is driven by charged energy from the charging unit. When a body temperature is to measured, the probe unit is set in the chopper unit, and the probe unit having the infrared sensor and the target are preheated by the heating control means. In this state, calibration is performed. Thereafter, the probe unit is detached from the chopper unit and is inserted in an external ear canal to detect infrared radiation from a drum membrane. A body temperature measurement is performed by comparing the detected infrared radiation with that from the target.

Temperature measurement precision is increased by the above-described system for the reasons to be described below.

According to this system, various error factors are eliminated by preheating the probe unit having the infrared sensor and the target to a reference temperature (36.5° C.) close to a normal body temperature by using the heating control means. That is, by heating the probe to the reference temperature higher than a room temperature and keeping the infrared sensor at a constant temperature regardless of ambient temperatures, sensitivity variations of the infrared sensor can be eliminated, and hence its error can be neglected. In addition, calibration is performed so as to set the reference temperature of the target to be close to a body temperature to be measured, and a comparative measurement is then performed so that errors and the like due to the filter characteristics are reduced to a negligible level. Furthermore, since the probe is preheated to a temperature close to a body temperature, the problem of the conventional measurement system can be solved, i.e., the problem that when a cool probe is inserted in an external ear canal, the temperatures of the external ear canal and the drum membrane are lowered because of the probe, so that correct body temperature measurement cannot be performed.

The above-described radiation clinical thermometer disclosed in U.S. Pat. No. 4,602,642 is excellent in temperature measurement precision. However, since this therometer requires a heating control unit with high control precision, its structure and circuit arrangement become complicated, thereby increasing the cost. In addition, it requires a long stable period to preheat the probe and the target and control their temperatures to a predetermined temperature. Moreover, since the heating control unit is driven by a relatively large-power energy, a large charging unit having a power source cord is required. Therefore, the above-described system cannot be applied to a portable clinical thermometer using a small battery as an energy source.

SUMMARY OF THE INVENTION

It is an object of the present invention to provide a portable, compact radition clinical thermometer at low cost while high temperature measurement precision is maintained by solving the above-described problems.

According to an aspect of the present invention, a filter correcting means outputs a correction value based on the transmission wavelength characteristics of a filter so that a body temperature is calculated on the basis of infrared data, temperature-sensitive data, and the filter correction value.

According to another aspect of the present invention, a body temperature is calculated on the basis of infrared data, temperature-sensitive data, a filter correction value, sensitivity data input from a sensitivity data input means.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a graph showing temperature measurement curves of a conventional electronic clinical thermometer;

FIG. 2 is a block diagram showing a circuit arrangement of the conventional electronic thermometer;

FIG. 3 is a graph showing changes in intensity of an infrared wavelength spectrum depending on the temperature of an object;

FIG. 4 is a graph showing the transmission wavelength characteristics of a silicon filter;

FIG. 5 is a graph showing the sensitivity characteristics of an infrared sensor;

FIG. 6 is block diagram showing a circuit arrangement of an electronic clinical thermometer according to an embodiment of the present invention;

FIG. 7 is a graph of temperature characteristics for explaining an approximate expression of temperature measurement by the conventional electronic theremometer;

FIG. 8 is a plan view of an electronic thermometer of the present invention;

FIG 9 is a side view of the electronic thermometer in FIG. 8;

FIG. 10 is a sectional view showing an internal structure of a temperature measuring section of the electronic clinical thermometer in FIG. 8;

FIG. 11 is an enlarged sectional view showing part of the temperature measuring section of the electronic clinical thermometer;

FIG. 12 a side view showing a state wherein the electronic clinical thermometer is stored in a storage case;

FIG. 13 is a view showing a state wherein the temperature measuring section of the electronic clinical thermometer is inserted in an external ear canal;

FIG 14 is a block diagram showing a circuit arrangement of an electronic clinical thermometer according to a second embodiment of the present invention;

FIG. 15 is a flow chart for explaining a body temperature calculating operation in the embodiment shown in FIG. 14;

FIG. 16 is a graph showing a temperature measurement curve of the electronic clinical thermometer of the present invention;

FIG. 17 is a circuit diagram of a peak hold circuit in the embodiment shown in FIG. 14;

FIG. 18 is a sectional view showing an internal structure of a temperature measuring section of an electronic clinical thermometer according to a third embodiment of the present invention;

FIG. 19 is a block diagram showing a circuit arrangement of the electronic clinical thermometer according to the third embodiment of the present invention; and

FIG. 20 is a sectional view showing an internal structure of a modification of the temperature measuring section of the electronic clinical thermometer according to the third embodiment of the present invention shown in FIG. 18.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The present invention will be described below with reference to the accompanying drawings.

FIG. 6 is a block diagram showing a basic circuit arrangement of a radiation clinical thermometer according to a first embodiment of the present invention.

In this embodiment, variations in sensitivity R are reduced to a negligible level by using a thermopile manufactured under good manufacturing conditions so as to correct filter characteristics.

The same reference numerals in FIG. 6 denote the same parts as in FIG. 2, and a description thereof will be omitted.

The radiation clinical thermometer of this embodiment differs from that shown in FIG. 2 in measurement of the temperature of the drum membrane of an ear as an object to be measured and the arrangement of anoperation section 5.

Theoperation section 5 of a radiationclinical thermometer 70 comprises an emissivity input means 5a for setting an emissivity ε of an object L to be measured, a filter correction means 5b for setting transmission wavelength characteristics of afilter 2b, and a body temperature operating circuit 5c.

Theoperating section 5 of this embodiment, therefore, calculates a measurement body temperature T_b on the basis of an emissivity set value from the emissivity input means and a filter correction value from thefilter correcting means 5b.

An equation for temperature calculation with consideration of the wavelength dependency of an infrared sensor with a filter will be described below.

As described above, theinfrared sensor 3a converts the infrared radiation energy W obtained by subtracting radiation energy from incidence energy into the infrared voltage v_s. The energy W can be given by equation (9): ##EQU5## where η(λ) is the transmittance of the filter.

The first term of equation (9) represents infrared radiation energy emitted from the object L having the emissivity ε which is transmitted through thefilter 2b and reaches thesensor 3a. The second term represents infrared radiation energy emitted from emitted from an object located near the object L and having the temperature T₀, which is transmitted through thefilter 2b and reaches thesensor 3a. The third term represents infrared radiation energy emitted from theinfrared sensor 3a having the temperature T₀ or an object located near thesensor 3a, which is reflected by thefilter 2b and reaches thesensor 3a, or infrared radiation energy which is emitted from thefilter 2b having the temperature T₀ and reaches thesensor 3a. In this case, the sum of the transmittance, reflectance, and emissivity of the transmission member is equal to one. The third term is established in consideration of the reflection or radiation by thefilter 2b. Note that the infrared radiation from theinfrared sensor 3a is reflected by thefilter 2b. The fourth term represents infrared radiation energy from theinfrared sensor 3a itself having the temperature T₀, and a sign of this term is negative.

Equation (9) can be rewritten to equation (10) as follows: ##EQU6##

It is found, therefore, that the infrared radiation energy obtained by subtracting radiation energy from incident energy of theinfrared sensor 3a having thefilter 2b does not correspond to "a value proportional to the difference between a power of four of the absolute temperature and that of the temperature of the sensor itself" as represented by equation (5), but must be given by an equation based on the transmission wavelength characteristics of thefilter 2b as represented by equation (10). That is, a new equation must be established in place of the Stefan-Boltzmann law represented by equation (2).

If infrared radiation energy emitted from the blackbody having the absolute temperature T, which is transmitted through a filter having a transmittance η(λ) is set to be F(T),F(T) can be represented by equation (11) as follows: ##EQU7##

In this case, assuming that the absolute temperature T has a temperature range from T_min to T_max, the infrared radiation energy F(T) is calculated with respect arbitrary absolute temperatures T₁, T₂, T₃, . . . , T_n according to equation (11). The calculation results are summarized in Table 1.

              TABLE 1                                                     ______________________________________                                            T   F(T)                                                          ______________________________________                                            T.sub.1                                                                       F(T.sub.1)                                                            T.sub.2                                                                       F(T.sub.2)                                                            T.sub.3                                                                       F(T.sub.3)                                                            .   .                                                                     .   .                                                                     .   .                                                                     T.sub.n                                                                       F(T.sub.n)                                                    ______________________________________

It is, therefore, seen how the relationship between the absolute temperature T and the infrared radiation energy F(T) transmitted through the filter is associated with the Stefan-Boltzmann law. FIG. 7 is a graph for explaining the examination process. The process will be described below with reference to FIG. 7.

In this graph, absolute temperatures [K] are plotted along the axis of abscissa and radiation energies [W/cm² ] are plotted along the axis of ordinate. Referring to FIG. 7, a curve A is a characteristic curve based on equation (2) representing the Stefan-Boltzmann law, and a curve B is a characteristic curve based on the present invention considering the filter characteristics.

The curve B is obtained such that a curve B' is prepared by connecting points respectively representing radiation energies at the absolute temperatures T₁ to T_n shown in Table 1. and the curve A is modified and moved to overlap the curve B'. Types of modification and movement of the curve A' are determined by selecting a coefficient a of a term ofdegree 4 of the curve A, a displacement b in the direction of the abscissa axis, and a displacement c in the direction of the ordinate axis so as to overlap the curve A and the curve B'.

As a result, equation (11) is approximated to equation (12) by using the three types of set values a, b, and c.

F(T)═a.(T-b).sup.4 +c                                  (12)

Subsequently, proper values a, b, and c in equation (12) are obtained from the values shown in Table 1 by a method of least squares or the like. Substitutions of these values into equation (12) yield an approximate equation.

The set values a, b, and c will be described below in comparison with equation (2) representing the Stefan-Boltzmann law.

The set value a is a coefficient of the absolute temperature T ofdegree 4, and corresponds to the Stefan-Boltzmann constant σ of the curve A. The value a takes a unit value of [W/cm² deg⁴ ]. The set value b represents a symmetrical axis temperature. In the curve A, an absolute temperature 0 [K] is set to a symmetrical axis, whereas in the curve B, an absolute temperature b [K] is set to be a symmetrical axis.

The set value c represents a minimum value. In the curve A, 0 [W/cm² ] is set to be an offset, whereas in the curve B, c [W/cm² ] is set to be an offset.

If equation (10) is rewritten by using equation (12), equation (13) is established as follows: ##EQU8##

As is apparent from equation (13), the minimum value c is canceled.

In this case, the infrared data V_d based on infrared radiation emitted from the drum membrane is obtained from the light-receiving area S and the sensitivity R of theinfrared sensor 3a and the gain A of the infrared amplifier 4a by setting K₂ ═aSRA.Equation (13) is then rewritten as equation (14). The body temperature T_b through the drum membrane is calculated by using equation (15) on the basis of equation (14). ##EQU9##

That is, when a filter having transmission wavelength characteristics is used for an optical system member, a temperature calculation is not performed on the basis of the law "infrared radiation energy is proportional to a power of four of the absolute temperature T", but must be based on equation (14) representing the law "Infrared radiation energy is proportional to a power of four of (the absolute temperature T- the symmetrical axis temperature b)."

As a result, thefilter correcting means 5b shown in FIG. 6 outputs the symmetrical axis temperature b, and the operating circuit 5c calculates the body temperature T_b of the object L to be measured, i.e., the drum membrane on the basis of equation (15).

An approximate expression in consideration of a silicon filter used as thefilter 2b in practice will be described below.

FIG. 4 shows the transmission wavelength characteristics of the silicon filter. However, in order to simplify a calculation, the transmission wavelength band of the silicon filter is set to be 1 to 18 [μm], and its transmittance is set to be 54%. ##EQU10##

Equation (1) is substituted into W(λ, T).

Since a measurement environment, i.e., the measurement temperature range of the object to be measured is set between 0 [°C.] and 50 [°C.]. T_min and T_max are respectively

set to be 273 [K] and 323 [K]. Table 2 shows the calculation results of equation (16).

The values a, b, and c when equation (12) is approximated by using the data shown in Table 2 are obtained by a method of least squares:

a═4.101×10^-12 [W/cm².deg⁴ ]

b═45.96[K]

c═-6.144×10⁴ [W/cm² ]

The coefficient a of a term ofdegree 4 and the symmetrical axis b thus obtained represent the transmission wavelength characteristics of the silicon filter. These values a and b are output from thefilter correcting means 5b. Thefilter correcting means 5b is part of an operating program memory of theoperating section 5, in which coefficient a of the term ofdegree 4 and the symmetrical axis temperature b are written.

              TABLE 2                                                     ______________________________________                                    T      f(T) ×    T      f(T) ×                                [K]    10.sup.-3 [W/cm.sup.2 ]                                                                   [K]    10.sup.-3 [W/cm.sup.2 ]                     ______________________________________                                    273    10.290          299    16.208                                      275    10.679          301    16.746                                      277    11.078          303    17.298                                      279    11.487          305    17.862                                      281    11.908          307    18.439                                      283    12.339          309    19.030                                      285    12.782          311    19.634                                      287    13.236          313    20.252                                      289    13.701          315    20.884                                      291    14.178          317    21.530                                      293    14.667          319    22.191                                      295    15.169          321    22.865                                      297    15.682          323    23.555                                      ______________________________________

When a silicon filter is used as a window member for measurement of an infrared sensor, the temperature T of an object to be measured is not calculated by equation (5), but is calculated by equation (14), thereby performing temperature calculations with high precision.

As is apparent from the above description, according to this embodiment, even if a transmission member having transmission wavelength characteristics is used as a window member of an infrared sensor, temperature measurement of an object to be measured can be performed with high precision.

In addition, even if the material of the transmission member as a window member of the infrared sensor is changed, temperature measurement can be performed with high precision by updating the value of thefilter correcting means 5b as part of the program memory.

In the above embodiment, an approximate expression having a term ofdegree 4 as represented by equation (12) is used as a new equation replacing the Stefan-Boltzmann law. However, as shown in FIG. 13, in body temperature measurement, only a portion of the temperature measurement curve is used as a measurement range such as the range from T_min ti T_max . Therefore, an approximate expression having a term ofdegree 4 need not be used. Satisfactory precision of a clinical thermometer can be obtained by using an approximate expression with a proper degree. For example, expression (14) can be employed as an approximate equation having a term of degree 2:

V.sub.d ═εK.sub.2'{(T.sub.b -B').sup.2 -(T.sub.0 -b').sup.2 }(14')

A detailed arraangement of a radiation clinical thermometer which is actually manufctured by using a commercially available thermopile manufactured in consideration of mass production will be described below as a second embodiment of the present invention.

FIGS. 8 and 9 are bottom and side views, respectively, showing a radiation clinical thermometer according to the second embodiment of the present invention.Reference numberal 1 denotes a radiation clinical; thermometer comprising amain body portion 10 and ahead portion 11. Thedisplay unit 6 for displaying a body measurement is arranged on the lower surface of themain body portion 10. Acheck button 12 having a push button structure is formed on the upper surface of theportion 11. Apower switch 13 having a slide structure andmajor buttons 14 and 15 each having a push button structure are respectively formed on the side surfaces of theportion 11.

Thehead portion 11 extend from the end of themain body portion 10 in the form of an L shape. The end of thehead portion 11 constitutes aprobe 16. Theprobe 16 comprises anoptical system 2 and a detectingsection 3 shown in FIG. 6.

The radiationclinical theremometer 1 is operated as follows. A check operation (to be described later) is performed while the power switch is ON. Thereafter, while theprobe 16 is inserted in an external ear canal of a patient to be examined, either or both of themajor switches 14 and 15 is/are depressed, thereby instantaneously completing body temperature measurement. The measurement result is displayed on thedisplay unit 6 as a body temperature.

FIG. 10 is a sectional view of thehead portion 11. Each ofcase members 17 and 18 consists of a resin molded member having a very low thermal conductivity. A portion of thecase 17 covering theprobe 16 constitutes acylindrical member 17a, in which ametal housing 19 consisting of a lightweight metal having a high thermal conductivity such as aluminum is fitted. Themetal housisng 19 .Iadd.is integrally formed and .Iaddend.comprises acylindrical portion 19a and abase portion 19d having ahollow portion 19b communicating with thecylindrical portion 19a and arecess 19c in which a temperature-sensitive element is embedded. In addition, astep portion 19e for attachment of a filter is formed at the distal end of thecylindrical portion 19a. Anoptical guide 20 consisting of a brass (Bu) pipe having an inner surface plated with gold (Au) is fitted in thecylindrical portion 19a. A filter member in the form of a dust-proofhard cap 21 selectively allowing infrared radiation to pass therethrough is fixed to thestep portion 19e. In addition, a thermopile as theinfrared sensor 3a and the temperature-sensitive sensor 3b are respectively embedded in thehollow portion 19b and therecess 19c of thebase portion 19d by sealingresins 22 and 23. Theinfrared sensor 3a and the temperature-sensitive sensor 3b are respectively connected to wiring patterns of acircuit board 26 throughleads 24 and 25, and are led to amplifying circuits to be described later.

According to the above-described arrangement, since theinfrared sensor 3a, theoptical guide 20, and thehard cap 21 are connected to each other through themetal housing 19 having a high thermal conductivity, they can always be kept in a thermal equilibrium state. This uniform-temperature is detected by the temperature-sensitive sensor 3b.Reference numeral 28 denotes a temperature measurement cover which is detachably fitted on theprobe 16 and is constituted by a resin having a low thermal conductivity. Adistal end portion 28a of thecover 28 consists of a material through which infrared radiation can be transmitted.

FIG. 11 is an enlarged sectional view of the distal end portion of theprobe 16. Thedistal end portion 28a of thecover 28 covers the distal end portion of theprobe 16 so as to prevent contact of theprobe 16 with the inner wall of the external ear canal.

FIG. 12 is a side view showing a state wherein the radiationclinical thermometer 1 is stored in astorage case 30. Thestorage case 30 comprises a mountingportion 30a for mounting themain body portion 10, and astorage portion 30b for storing theprobe 16. A reflectingplate 31 is fixed to abottom surface 30c of thestorage portion 30b at a position corresponding to the distal end portion of theprobe 16. In addition, a buttondepressing portion 30d is formed on thestorage case 30 at a position corresponding thecheck button 12. Thestorage case 30 is used to perform an operation check of the radiationclinical thermometer 1. When thethermometer 1 is set in thestorage case 30 with thepower switch 13 being turned on as shown in FIG. 12, the distal end portion of theprobe 16 is set on the reflectingplate 31, and at the same time, thecheck buttom 12 is depressed by the buttondepressing portion 30d. This state is a function check state to be described later. In this state, a user can know from a display state of thedisplay unit 6 whether body temperature measurement can be performed.

FIG. 13 is a sectional view of an ear, showing a state wherein a body temperature measurement is performed by the radiationclinical thermometer 1.Reference numeral 40 denotes a canal; 41, external ear canal; and 42, a drum membrane. A large number of downy hairs are grown from the inner wall of theexternal ear canal 41. Earwax is sometimes formed on the inner wall of theexternal ear canal 41. When the distal end portion of theprobe 16 of the radiationclinical thermometer 1 is inserted in theexternal ear canal 41, and themajor buttons 14 and 15 are depressed with the distal end portion directed to thedrum membrane 42 as shown in FIG. 13, a body temperature measurement can be instantaneously performed.

FIG. 14 is a block diagram of the radiationclinical thermometer 1 in FIG. 8. The same reference numerals in FIG. 14 denote the same parts as in FIG. 6, and a description thereof will be omitted.

Portions different from FIG. 6 will be described below.Reference numeral 50 denotes a detection signal porocessing section. FIG. 14 shows a detailed arrangement of thesection 50 corresponding to theamplifying section 4 shown in FIG. 6. More specifically, thesection 50 comprises an infrared amplifying circuit 51 for amplifying an infrared voltage v_s output from theinfrared sensor 3a, a temperature-sensitive amplifying circuit 52 for amplifying a temperatuyre-sensitive voltage v_t output from the temperature-sensitive sensor 3b, apeak hold circuit 53 for holding a peak value of an output voltage V_s from the infrared amplifying circuit 51, a switching circuit 54 for receiving the output voltage V_s from the infrared amplifying circuit 51 and an output voltage V_sp from thepeak hold circuit 53 at input terminals I₁ and I₂, respectively, and selectively outputting them from an output terminal O in accodance with conditions provided from a control terminal C, an A/D converter 55 for converting the infrared voltages V_s or V_sp output from the switching circuit 54 into digital infrared date V_d, and an A/D converter 55 for converting the output voltage V_t from the temperature-sensitive amplifying circuit 52 into digital temperature-sensitive data T₀. With this arrangement, thesection 50 converts the infrared voltage v_s and the temperature-sensitive voltage v_t supplied from the detectingsection 3 into the digital infrared data V_d and temperature-sensitive data T₀, and outputs them.

Anoperating section 60 corresponds to theoperating section 5 shown in FIG. 6, and comprises an emissivity input means 5a, afilter correcting means 5b, a bodytemperature operating circuit 61 corresponding to the operating circuit 5c, adisplay driver 62 for receiving a body temperature data T_b1 calculated by theoperation circuit 61 and displaying it on a bodytemperature display portion 6a of adisplay unit 6, a zerodetector 63 for receiving the infrared data V_d output from the detectionsignal processing section 50 and outputting a detection signal S₀ when the infrared data V_d is detected to be zero so as to illuminate a measurement permission mark 6b of thedisplay unit 6, asensitivity correcting calculator 64 for receiving the temperature-sensitive data T₀ output from thesection 50, calculating a sensitivity R in accordance with equation (8) shown in FIG. 5, and outputting it, and a sensitivity data input means 65 for outputting as sensitivity data D a value which is externally input/set on the basis of the light-receiving area S of theinfrared sensor 3a and the gain A of the infrared amplifying circuit 51 shown in equation (6).

Reference numeral 90 denotes a switch circuit to which a major switch SW_m operated by themajor switches 14 and 15 shown in FIG. 8 and a check switch SW_c operated by thecheck button 12 are connected. When either of themajor buttons 14 and 15 is depressed, the major switch SW_m is turned on, and a major signal S_m is output from a terminal M.

When the radiationclinical thermometer 1 is set in thestorage case 30 as shown in FIG. 12, thecheck button 12 is depressed, and the check switch SW_e is turned on. As a result, a check signal S_c is output from a terminal C.

The major signal S_m output from the terminal M of the switch circuit 90 is supplied to enable terminals E of the body termperature operatingcircuit 61 and thesensitivity correcting calculator 64. As a result, both thecircuit 61 and thecalculator 64 are set in an operative mode, and at the same time, the zerodetector 63 is reset. The check signal S_c output from the terminal C of the switch circuit 90 is supplied to an enable terminal E of the zerodetector 63, the control terminal C of the switching circuit 54, and a reset terminal R of thepeak hold circuit 53.

An operation of the radiationclinical thermometer 1 having the above-described arrangement will be described below.

In an initial state wherein thepower switch 13 of the radiationclinical thermometer 1 shown in FIG. 8 is turned on, since both the check switch SW_c and the major switch SW_m are kept off, the check signal S_c and the major signal S_m are not output from theswitch circuit 70.

Consequently, in theoperation section 60, the bodytemperature operating circuit 61 and thesensitivity correcting calculator 64 are set in a non-calculation mode, and the zerodetector 63 is set in an inoperative mode. In addition, the switching circuit 54 of the detectionsignal processing section 50 selectively outputs the voltage V_sp input to the terminal I₂ to the output terminal O. The reset state of thepeak hold circuit 53 is released and is set in an operative state.

The initial state is established in this manner. A function check mode will be described next.

When thethermometer 1 is set in thestorage case 30 as shown in FIG. 12, thecheck button 12 is urged against the buttondepressing portion 30d of thestorage case 50. As a result, the check switch SW_c shown in FIG. 14 is turned on, and at the same time, the distal end portion of theprobe 16 is set at the position of the reflectingplate 31.

Consequently, the switch circuit 90 outputs the check signal S_c from terminal C when the check switch SW_c is turned on, and supplies it to thepeak hold circuit 53, the switching circuit 54, and the zerodetector 63. Upon reception of the check signal S_c, in the detectionsignal processing section 50, thepeak hold circuit 53 is reset, and at the same time, the switching circuit 54 is switched to a state wherein the voltage V_s supplied to the input terminal I₁ is selectively output to the output terminal O. Subsequently, the A/D converter 55 converts the infrared voltage V_s into a digital value and outputs it as the infrared data V_d. In theoperation section 60, the bodytemperature operating circuit 61 and thesensitivity correcting calculator 64 are set in an inoperative mode, and only the zerodetector 63 is set in an operative state. The state of each portion in the function check mode has been described so far. The radiationclinical thermometer 1 in this function check mode is operated as follows. The infrared data V_d obtained by converting infrared radiation reflected by the reflectingplate 31 into a digital value by using theinfrared sensor 3a, the infrared amplifying circuit 51, the switching circuit 54, and the A/D converter 55 is determined by the zerodetector 63. If this infrared data V_d is zero, the zerodetector 63 outputs the detection signal S₀ from the output terminal O so as to illuminate the measurement permission mark 6b of thedisplay unit 6.

The contents of the function check mode will be described below.

Referring to FIG. 10, as described above, since theinfrared sensor 3a, theoptical guide 20, and thehard cap 21 are connected to each other through themetal housing 19 having a high thermal conductivity, thermal equilibrium of these components can be obtained. The above-described function check mode is a mode for confirming that the thermal equilibrium is satisfactorily obtained. More specifically, infrared radiation energies emitted from theoptical guide 20 and thehard cap 21 each having the temperature T are reflected by the reflectingplate 31, and are incident on theinfrared sensor 3a. In addition infrared radiation energy is emitted from theinfrared sensor 3a having the temperature T₀. The energy W obtained by subtracting the emitted energy from the incident energy is given by equation (5) as described above:

W═εσ(T₄ -T₀⁴)

If T═T₀, the energy W is not present. Hence, all the voltages v_s and V_s, and the infrared data V_d are set to zero, and the detection signal S₀ is output from the zerodetector 63. That is, the measurement ready permission mark 6b is illuminated to confirm that the heat source causing noise is present near theoptical system 2, and hence body temperature measurement can be performed. Note that the zerodetector 63 determines the infrared data V_d as a digital value. A determination value need not be strictly zero. The zerodetector 63 outputs the detection signal S₀ if the infrared date V_d is smaller than a predetermined determination value. In this case, even if the determined value is not zero, it is regraded as negligible. If T≠T₀ according toequation 5, i.e., if there is a temperature difference among theinfrared sensor 3a, theoptical guide 20, and thehard cap 21, the differential energy W is present. Therefore, the infrared data V_d becomes larger than the determination level of the zerodetector 63. As a result, the detection signal S₀ is not output, and the measurement permission mark 6b is not illuminated.

In actual use of the radiationclinical thermometer 1, the state of T≠T₀ occurs as follows.

When the environmental temperature in use of the radiationclinical thermometer 1 is abruptly changed, the above state occurs. In this case, T≠T₀ occurs due to differences in heat capacity and response characteristics of the respective elements. Since a measurement error corresponding to the value of the infrared data V_d based on the differential energy W occurs, thethermometer 1 is set in a measurement disable state. In this state, if thethermometer 1 is left in a constant environmental temperature for a while, the respective elements are stabilized in a thermal equilibrium state upon thermal conduction through themetal housing 19, and thethermometer 1 is set in a measurement permission state. However, it may takes several tens of minutes to established such a stable state.

The function check mode has been described so far. A body temperature measurement mode will be described next.

The radiationclinical thermometer 1 is detached from thestorage case 30 after illumination of the measurement permission mark 6b is confirmed in the above-described function check mode. When thethermometer 1 is detached from the case, depression of thecheck button 12 is released, so that the check switch SW_c is turned off, and output of the check signal S_c from the terminal C of the switch circuit 90 is stopped. As a result, the reset state of thepeak hold circuit 53 is released. At the same time, the switching circuit 54 is returned to the selection state for the input terminal I₂, and the zerodetector 63 is returned to the inoperative state.

Consequently, in the detectionsignal processing circuit 50, the peak voltage V_sp of the infrared voltage V_s output from the infrared amplifying section 51, which is held by thepeak hold circuit 53, is supplied to the A/D converter 55 through the switching circuit 54, thereby outputting the digital infrared data V_d converted from the peak voltage V_sp.

Although the zerodetector 63 of theoperating section 60 is returned to the inoperative state, the measurement permission mark 6b of thedisplay unit 6 is kept illuminated because the detection signal S₀ is held by a storage circuit arranged in the zerodetector 63. Since the major signal S_m is supplied to the reset terminal R, the detection signal S₀ if the zerodetector 63 is maintained until the storage circuit is reset.

In this manner, the apparatus is prepared for measurement. When themajor buttons 14 and 15 are depressed after the radiationclinical thermometer 1 is inserted in theexternal ear canal 41 in this state as shown in FIG. 13, a body temperature measurement is performed. More specifically, when themajor buttons 14 and 15 are depressed, the major switch SW_m shown in FIG. 14 is turned on, and the major signal S_m is output from the terminal M of the switch circuit 90. As a result, in theoperation section 60, the bodytemperature operating circuit 61 and thesensitivity correcting calculator 64 are set in an operative mode, and at the same time, the zerodetector 63 is reset to turn off the measurement permission mark 66 of thedisplay unit 6. Infrared radiation energy which is emitted from thedrum membrane 42 and is incident on the the probe 16 (theoptical system 2 and thedetection section 3 in FIG. 14) inserted in theexternal ear canal 41 is converted into the infrared voltage v_s by theinfrared sensor 3a, and is amplified to the voltage V_s by the infrared amplifying circuit 51. Thereafter, the peak voltage V_sp is held by thepeak hold circuit 53. The peak voltage V_sp is converted into the infrared data V_d by the A/D converter 55, and is supplied to theoperating section 60. In addition, the temperature-sensitive sensor 36 embedded in themetal housing 19 detects the temperature of theinfrared sensor 3a and converts it into the temperature-sensitive voltage v_t. The voltage is converted into the temperature-sensitive data T₀ by the A/D converter 56, and is then supplied to theoperation section 60.

When the infrared data V_d and the temperature-sensitive data T₀ are supplied to theoperation section 60, thesensitivity correcting calculator 64 calculates the sensitivity R by using the data T₀ on the basis of equation (8). Note that the coefficient of variation β is set to be -0.03. The bodytemperature operating circuit 61 then receives the sensitivity R calculated by thecalculator 64, the sensitivity data D from the sensitivity data input means, and the coefficient a of a term ofdegree 4 from thefilter correcting means 5b, and calculates a sensitivity coefficient K₃ of this system as K₃ ═aRD.

Upon reception of the calculated sensitivity coefficient K₃, the emissivity ε from the emissivity input means 5a, and the symmetrical axis temperature b from thefilter correcting means 5b, the bodytemperature operating circuit 61 performs a calculation based on equation (17):

V.sub.d ═εK.sub.3 {(T.sub.b1 -b).sup.4 -(T.sub.0-b).sup.4 }(17)

Equation (17) is further rewritten to equation (18) so as to calculate the body temperature data T_b1. Since the external ear canal has a uniform temperature, and the canal is regarded as a blackbody, the emissivity ε is set set as ε═1. ##EQU11## for b═45.95[K±]. Thus, the body temperature data T_b1 is displayed on adigit display portion 6a of thedisplay unit 6 through thedisplay driver 62.

One body temperature measurement is performed in this manner. A procedure of this operation will be described with reference to the flow chart of FIG. 15.

When theprobe 16 is inserted in the external ear canal 41 (step 1), infrared radiation energy from thedrum membrane 42 is converted into the infrared voltage V_s, and its peak voltage V_sp is held by the peak hold circuit 53 (step 2). The presence/absence of the major signal S_m is then determined (step 3). If themajor buttons 14 and 15 are not depressed, NO is obtained in this step, and only the peak value holding operation instep 2 is performed.

If themajor buttons 14 and 15 are depressed, YES is obtaianed instep 3. As a result, the zerodetector 63 is reset by the major signal S_m (step 4). At the same time thesensitivity correcting calculator 64 reads the temperature-sensitive data T₀ (step 5) and calculates the sensitivity R (step 6).

The bodytemperature operating circuit 61 reads the emissivity ε, the coefficient a, the sensitivity R, and the sensitivity data D (step 7), and calculates the sensitivity coefficient K₃ by using the values a, R, and D (step 8). In addition, the operatingcircuit 61 reads the symmetrical axis temperature b and at the peak-held infrared data V_d (step 9) and calculates the body temperature data step T_b1 (step ○ 10 ). Thedisplay driver 62 receives the body temperature data T_b1 and displays the body temperature on the display unit 6 (step ○ 11 ), thereby completing the body temperature measurement.

The function of thepeak hold circuit 53 shown in FIG. 14 will be described below with reference to FIG. 16.

FIG. 16 shows a temperature measurement curve of the radiationclinical thermometer 1 of the present invention, which corresponds to the temperature measurement curve of the conventional electronic clinical thermometer shown in FIG. 1.

Temperature measurement time is plotted along the abscissa axis, and measurement temperatures are plotted along the ordinate axis. Theexternal ear canal 41 is a portion to be measured. A temperature curve H_s of theexternal ear canal 41 coincides with a measurement temperature curve M_s of the radiationclinical thermometer 1. As describe above, thedowny hairs 43 and theearwax 44 are present in theexternal ear canal 41, as shown in FIG. 13. Similar to thedrum membrane 42, thedowny hairs 43 and theearwax 44 are warmed to a temperature very close to a body temperature prior to the start of temperature measurement. This state is indicated at time T₁ in FIG. 16. More specifically, time t₁ is the instant when theprobe 16 is inserted in theexternal ear canal 41. Since the temperature in theexternal ear canal 41 at this instant is substantially equal to the body temperature T_b1, infrared radiation energy having a body temperature level is incident on theinfrared sensor 3a, and is stored in thepeak hold circuit 53 as the peak voltage V_sp. However, the temperature in theexternal ear canal 41 is cooled by theprobe 16 and quickly drops immediately after theprobe 16 is inserted, as indicated by the temperature curve H_s. With this temperature drop, the infrared voltage V_s detected by theinfrared sensor 3a drops to the level of the temperature measurement curve M_s, and hence cannot exceed the peak voltage V_sp. For this reason, the peak voltage V_sp at time t₁ is stored in thepeak hold circuit 53. It takes about 10 minutes for the lowered temperature represented by the curve H_s to return to the origianl body temperature T_b1. The reason will be described below with reference to FIG. 13.

When theprobe 16 is inserted in theexternal ear canal 41, all the temperatures of thedrum membrane 42, eachdowny hair 43, and theearwax 44 are decreased. Of these portions the temperature of thedrum membrane 42 can return to the level of the body temperature T_b1 relatively quickly because of the themal conduction from the body. However, since the thermal conduction from the body to eachdowny hair 43 and theearwax 44 having low degree of adhesion to the body is less, about 10 minutes are required for their temperatures to return to the level of the body temperature T_b1. Therefore, the temperature in theexternal ear canal 41 is set at the level of the body temperature T_b1 only at time T₁, i.e., the instant when theprobe 16 is inserted. Since the series of operation processing of the radiationclinical thermometer 1 cannot be performed by using the infrared radiation energy in such a short period of time, the peak voltage V_sp appearing at the instant is stored in thepeak hold circuit 53 as analog data, as indicated by a dotted line in FIG. 16. The A/D conversion and the series of operating processing are performed by using this stored peak voltage V_sp, thereby performing the body temperature measurement.

Thus, in a radiation clinical thermometer without a preheating unit as in the present invention, thepeak hold circuit 53 is indispensable. By using thepeak hold circuit 53, the body temperature T_b1 at time T₁ can be measured within a very short period of time.

FIG. 17 a detailed arrangement of thepeak hold circuit 53. Thepeak hold circuit 53 comprises aninput buffer 80, anoutput buffer 81, adiode 82 for preventing a reverse current flow, asignal charging capacitor 83, and a switchingtransistor 84 for casuing thecapacitor 83 to discharge a charged voltage. Thepeak hold circuit 53 receives the infrared voltage V_s and outputs its peak value as the peak voltage V_sp. In addition, when the switchingtransistor 84 is turned on by the check signal S_c supplied to the reset terminal R, thecircuit 53 causes thecapacitor 83 to discharge a charged voltage.

FIG. 18 is a sectional view of ahead portion 110 according to a third embodiment of the present invention. The same reference numerals in FIG. 18 denote the same parts as in FIG. 10, and a description thereof will be omitted.

The head portion in FIG. 18 differs from that in FIG. 10 in that a throughhole 19f is formed in acylindrical portion 19a of ametal housing 19 so as to expose anoptical guide 20, and a temperature-sensitive sensor 3c is fixed to the exposed portion of theoptical guide 20. This temperature-sensitive sensor 3c is identical to the temperature-sensitive sensor 3b, and is also fixed by a molding resin.

The third embodiment differs from the second embodiment in a system for correcting thermal equilibrium in aprobe 16. The second embodiment employs the system of permitting measurement upon confirmation of thermal equilbrium by the function check mode. In this system, measurement is inhibited while thermal equilibrium is not established. In contrast to this, the third embodiment comprises the two temperature-sensitive sensors 3b and 3c to detect a temperture difference between aninfrared sensor 3a and theoptical guide 20. In this system, if this temperature difference is excessively large, measurement is inhibited. If it is smaller than a predetermined value, body temperature measurement is permitted even though thermal equilibrium is not established. In this case, body temperature data is calculated by adding a correction value based on the temperature difference to the measurement value, thus widening the range of measurement conditions of the radiation clinical thermometer.

The circuit arrangement and operation of the radiation clinical thermometer of the third embodiment will be described below with reference to FIG. 19. The same reference numerals in FIG. 19 denote the same parts as in FIG. 14, and a description thereof will be omitted.

As shown in FIG. 18, a detectingsection 3 comprises a temperature-sensitive sensor 3c for measuring a temperature T_p of theoptical guide 20. In the detectionsignal processing section 50, the switching circuit 54 is omitted, and an output voltage V_sp from apeak hold circuit 53 is directly supplied to an A/C converter 55. A temperature-sensitive amplifying circuit 57 and an A/D converter 58 are additionally arranged in thesection 50 so as to output the temperature sensitive data T_p.

In anoperating section 60, an emissivity ε_p of theoptical guide 20 is set in an emissivity input means 5a, and atemperature difference detector 67 is arranged in place of the zerodetector 67 shown in FIG. 1. Thetemperature difference detector 67 receives temperature data T₀ of theinfrared sensor 3a detected by the two temperature-sensitive sensors 3b and 3c and the temperature data T_p of theoptical guide 20, and performs temperature difference determination with respect to a predetermined measurement limit temperature difference T_d. If |T₀ -T_p |<T_d, i.e., the temperature difference is smaller than the limit temperature difference, thedetector 67 outputs a detection signal S₀ so as to illuminate a measurement permission mark 6b of adisplay unit 6. This temperature difference determination is continued while thepower switch 13 shown in FIG. 9 is turned on. Therefore, the operation of thecheck button 12 as in the second embodiment is not required.

When the measurement permission mark 66 is illuminated, a body temperature measurement mode is set in the same manner as in the second embodiment. However, the difference is that the temperature-sensitive data T_p of theoptical guide 20 is supplied to a bodytemperature operating circuit 61 in addition to the respective data described with reference to FIG. 14. In this embodiment, thecircuit 61 calculates body temperature data T_b2 in accordance with the following equation (19): ##EQU12## where b═45.95[K] and ε_p ═0.05. This body temperature data T_b2 is obtained by correcting the temperature difference by the arithmetic operations described above, and is displayed on a bodytemperature display portion 6a of thedisplay unit 6. Furthermore, in this embodiment, a check signal S_c output from a switch circuit 90 resets only thepeak hold circuit 53. Therefore, when re-measurement of a body temperature is to be performed, thepeak hold circuit 53 must be reset first by operating the check button after illumination of the measurement permission mark 6b is confirmed.

As described above, according to this embodiment, since body temperature measurement can be performed without waiting for perfect thermal equilibrium of the respective elements of theprobe 16, intervals of repetitive measurements can be reduced. In addition, since the function check using infrared radiation is not required, a switching circuit and a storage case are not required so that the arrangement can be simplified.

In this embodiment, as an optimal embodiment, the arrangement wherein the second temperature-sensitive sensor 3c is attached to theoptical guide 20 is shown. However, the present invention is not limited to this. More specifically, the second temperature-sensitive sensor 3c is designed to detect the surface temperature of theoptical guide 20 which responds to an ambient temperature more sensitively than the portion in which the temperature-sensitive sensor 3b is embedded. In consideration of the fact that the surface temperature of theoptical guide 20 is substantially equal to the ambient temperature, the temperature-sensitive sensor 3c may be mounted on a circuit board on which a measurement IC chip is mounted as shown in FIG. 20 so as to measure an ambient temperature, so that the measured ambient temperature is used as the surface temperature of theoptical guide 20. This arrangement can also be satisfactorily used in practice.

As has been described above, according to the present invention, a filter correction value and a sensitivity correction value are supplied to a body temperature operating circuit to calculate body temperature data, so that high measurement precision can be realized without using a heating unit as in the conventional thermometer, thus realizing a compact, low-cost radiation clinical thermometer which can be driven by a small battery and which can shorten a measurement time.

In addition, by employing a peak hold circuit for analog data in the radiation clinical thermometer, instantaneous measurement can be performed, thus preventing a measurement disable state due to a temperature drop of a portion to be measured upon insertion of a probe.

Moreover, by employing a temperature difference correcting system using two temperature-sensitive sensors, re-measurement intervals can be shortened, and the problem of thermal equilibrium of a probe, which narrows the range of measurement conditions of the radiation clinical thermometer, can be solved. Therefore, the present invention is very effective to widely use a radiation clinical thermometer as a home thermometer, which has been used exclusively for a medical instrument.

Claims (23)

What is claimed is:

1. A radiation clinical thermometer comprising:

a probe including an optical system constituted by focusing means for focusing infrared radiation from an object to be measured and a filter having transmission wavelength characteristics, an infrared sensor for converting infrared radiation energy into an electrical signal, and a temperature-sensitive sensor for measuring a temperature of said infrared sensor and an ambient temperature thereof;

detection signal processing means for receiving electrical signals from said infrared sensor and said temperature-sensitive sensor and outputting the electrical signals as digital infrared data and temperature-sensitive data, respectively;

body temperature operating means for calculating body temperature data; and

a display unit for displaying a body temperature in accordance with the body temperature data, including filter correcting means for setting a correction value based on the transmission wavelength characteristics of said filter, wherein said body temperature operating means receives the infrared data, the temperature-sensitive data, and the correction value from said filter correcting means so as to calculate body temperature data.

2. A thermometer according to claim 1, further comprising sensitivity correction calculating means for receiving the temperature-sensitive data and calculating sensitivity data of said infrared sensor, and wherein said body temperature operating means calculates the body temperature data by receiving the infrared data, the temperature-sensitive data, the correction value from said filter correcting means, and the sensitivity data from said sensitivity correction calculating means.

3. A thermometer according to claim 2, wherein said sensitivity correction calculating means calculates sensitivity data R according to the following equation:

R═a{1+β (T.sub.0 -T.sub.m)}

where T₀ is sensitivity data of said temperature-sensitive sensor, T_m is a temperature at the time of sensitivity adjustment, α is a sensitivity at the temperature T_m, and β is a coefficient of variation of sensitivity.

4. A thermometer according to claim 1, wherein said filter correcting means outputs a symmetrical axis, temperature correction value which is used to change a symmetrical axis temperature of a temperature-radiation energy characteristic curve represented by a temperature equation of a higher degree approximated to a temperature-radiation eneregy characteristic curve based on a Stefan-Boltzmann law.

5. A thermometer according to claim 1, wherein said probe comprises an optical guide for focusing infrared radiation energy, a filter member arranged at one end of said optical guide, .[.an.]. infrared sensor arranged at the other end of said optical guide, and .[.a.]. .Iadd.said .Iaddend.temperature-sensitive sensor arranged near said infrared sensor, said optical guide, said filter member, said infrared sensor, and said temperature-sensitive sensor being coupled to each other by a metal housing having a high thermal conductivity.

6. A thermometer according to claim 5, wherein said metal housing is an integrally formed housing comprising a cylindrical portion in which said optical guide is inserted and a base portion formed at one end of said cylindrical portion and having a storage recess for housing said infrared sensor and said temperature-sensitive sensor, said optical guide being inserted and fixed in said cylindricl portion, said infrared sensor and said temperature-sensitive sensor being embedded in said storage recess of said base portion with a .[.molding.]. .Iadd.sealing .Iaddend.resin.

7. A thermometer according to claim 5, further comprising a second temperature-sensitive sensor for detecting a surface temperature of said optical guide.

8. A thermometer according to claim 7, further comprising said second temperature-sensitive sensor arranged on a surface of said optical guide in tight contact therewith.

9. A thermometer according to claim 7, wherein said detection signal processing section comprises an A/D converter for converting an electrical signal from said second temperature-sensitive sensor into second digital temperature-sensitive data, and said body temperature operating means calculates the body temperature data by using the second temperature-sensitive data as one of input signals.

10. A thermometer according to claim 9, further comprising a temperature difference detector for receiving the temperature-sensitive data from said temperature-sensitive sensor arranged at said base protion of said probe and the second temperature-sensitive data from said second temperature-sensitive sensor, and wherein said temperature difference detector outputs a detection signal when a temperature difference is determined to be smaller than a predetermined measurement limit temperature difference.

11. A thermometer according to claim 10, wherein said display unit comprises a measurement permission mark adapted to be illuminated by the detection signal output from said temperature difference detector.

12. A radiation clinical thermometer comprising:

a probe including an optical means for focusing infrared radiation from an object to be measured, an infrared sensor for converting infrared radiation energy into an electrical signal, and a temperature-sensitive sensor for measuring a temperature of said infrared sensor and an ambient temperature thereof;

detection signal processing means for receiving electrical signals from said infrared sensor and said temperature-sensitive sensor and outputting the electrical signals as digital infrared data and temperature-sensitive data, respectively;

body temperature operating means for calculating body temperature data, and

a display unit for displaying a body temperature in accordance with the body temperature data, characterized by

a zero detector for receiving the infrared data output from said detection signal processing means and determining presence/absence of the infrared data, wherein said zero detector outputs a detection signal when the infrared data is determined to be zero or a small value.

13. A thermometer according to claim 12, further comprising a storage case for storing said radiation clinical thermometer and a reflecting plate arranged in said storage case at a position corresponding to a probe end of said radiation clinical thermometer stored in said storage case.

14. A thermometer according to claim 13, wherein said display unit comprises a measurement permission mark adapted to be illuminated by the detection signal output from said zero detector.

15. A radiation clinical theremometer comprising:

a probe including an optical means for focusing infrared radiation from an object to be measured, an infrared sensor for converting infrared radiation energy into an electrical signal, and a temperature-sensitive sensor for measuring a temperature of said infrared sensor and an ambient temperature thereof;

detection signal processing means for receiving electrical signals from said infrared sensor and said temperature-sensitive sensor and outputting the electrical signals as digital infrared data and temperature-sensitive data, respectively;

body temperature operating means for calculating body temperature data; and

a display unit for displaying a body temperature in accordance with the body temperature data, wherein said detection signal processing means includes a peak holding circuit for holding a peak value of the electrical signal from said infrared sensor as analog data and an A/D converter for converting a peak value voltage held in said peak holding circuit into digital infrared data, and said body temperature operating means calculates the body temperature data by using the infrared data converted from the peak value voltage; and

wherein said probe l .[.including.]. .Iadd.includes .Iaddend.a filter having transmission wavelength characteristics and wherein said display unit includes filter correcting means for setting a correction value based on the transmission wavelength characteristics of said filter, wherein said body temperature operating means receives the infrared data, the temperature-sensitive data, and the correction value from said filter correcting means so as to calculate body temperature data.

16. A thermometer according to claim 15 wherein said filter correcting means outputs a symmetrical axis temperature correction value which is used to change a symmetrical access temperature of a temperature-radiation energy characteristic curve represented by a temperature equation of a higher degree approximated to a temperature-radiation energy characteristic curve based on Stefan-Boltzmann law.

17. A thermometer according to claim 15 wherein said probe includes a filter having transmission wavelength characteristics and wherein said display unit includes filter correcting means for setting a correction value based on the transmission wavelength characteristics of said filter and further comprising sensitivity correction calculating means for receiving the temperature-sensitive data and calculating sensitive data of said infra-red sensor and wherein said body temperature operating means calculates the body temperature data by receiving the infra-red data, the temperature-sensitive data, the correction value from said filter correcting means, and the sensitivity data from said sensitivity correction calculating means.

18. A thermometer according to claim 17, wherein said sensitivity correction calculating means calculates sensitivity data R according to the following equation:

R═a{1+β (T.sub.0 -T.sub.m)}

where T₀ is sensitivity data of said temperature-sensitive sensor, T_m is the temperature at the time of sensitivity adjustment, α is a sensitivity at the temperature T_m, and β is a coefficient of variation of sensitivity.

19. A thermometer according to claim 15, wherein said optical means comprises an optical guide, a filter member arranged at one end of said optical guide, said infrared sensor arranged at the other end of said optical guide, .[.and.]. .Iadd.said .Iaddend.a temperature-sensitive sensor arranged near said infrared sensor, said optical guide, said filter member, said infrared sensor, and said temperature-sensitive sensor being coupled to each other by a metal housing having a high thermal conductivity.

20. A thermometer according to claim 19, wherein said metal housing is an integrally formed housing comprising a cylindrical portion in which said optical guide is inserted and a base portion formed at one end of said cylindrical portion and having a storage recess for housing said infrared sensor and said temperature-sensitive sensor, said optical guide being inserted and fixed in said cylindrical portion, said infrared sensor and said temperature-sensitive sensor being embedded in said storage recess of said base portion with a .[.molding.]. .Iadd.sealing .Iaddend.resin.

21. A thermometer according to claim 15, wherein said display unit includes a zero detector for receiving the infrared data output from said detection signal processing means and determining presence/absence of the infrared data, wherein said zero detector outputs a detection signal when the infrared data is determined to a zero of a small value.

22. A thermometer according to claim 15, further comprising a storage case for storing said radiation clinical thermometer and a reflecting plate arranged in said storage case at a position corresponding to a probe end of said radiation clinical thermometer stored in said storage case.

23. A thermometer according to claim 22, wherein said display unit comprises a zero detector and a measurement permission mark adapted to be illuminated by detection signal output from said zero detector.

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