WO2010098040A1 - Medical thermometer and body temperature measurement system - Google Patents

Medical thermometer and body temperature measurement system Download PDF

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Publication number
WO2010098040A1
WO2010098040A1 PCT/JP2010/000968 JP2010000968W WO2010098040A1 WO 2010098040 A1 WO2010098040 A1 WO 2010098040A1 JP 2010000968 W JP2010000968 W JP 2010000968W WO 2010098040 A1 WO2010098040 A1 WO 2010098040A1
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WO
WIPO (PCT)
Prior art keywords
body temperature
thermometer
unit
data
antenna
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Application number
PCT/JP2010/000968
Other languages
French (fr)
Japanese (ja)
Inventor
小澤仁
栗尾勝
萩野喜晴
Original Assignee
テルモ株式会社
Priority date (The priority date 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 date listed.)
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Publication date
Application filed by テルモ株式会社 filed Critical テルモ株式会社
Priority to CN2010800080947A priority Critical patent/CN102317746A/en
Publication of WO2010098040A1 publication Critical patent/WO2010098040A1/en

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
    • G01K1/00—Details of thermometers not specially adapted for particular types of thermometer
    • G01K1/02—Means for indicating or recording specially adapted for thermometers
    • G01K1/024—Means for indicating or recording specially adapted for thermometers for remote indication
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
    • G01K13/00—Thermometers specially adapted for specific purposes
    • G01K13/20—Clinical contact thermometers for use with humans or animals
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
    • G01K7/00—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements
    • G01K7/01—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements using semiconducting elements having PN junctions

Definitions

  • the present invention relates to a measurement technique for measuring the body temperature of a subject.
  • the present invention relates to a measurement technique with excellent measurement accuracy in a body temperature measurement range of 32 to 42 ° C.
  • thermometer is attached to a measurement site of a subject and kept stationary for a certain period of time until the measurement is completed.
  • the measurer performs an operation of confirming and recording the measurement result.
  • thermometer attached to the measurement site, and accurate temperature measurement is not easy. Further, it is desirable that the work of checking and recording the measurement result is heavy on the measurer and can be recorded without bothering the measurer.
  • thermometer 1 a pasted thermometer including an antenna is proposed.
  • the thermometer since the thermometer is configured to operate by receiving power supply from the RF-ID reader / writer, it is not necessary to mount a power source on the thermometer, and the thermometer can be reduced in size and weight. be able to. As a result, it can be pasted on the measurement site of the subject for a long time.
  • the measurement result can be read simply by bringing the RF-ID reader / writer close to the measurement site to which the thermometer is attached, so that it is possible to greatly reduce the burden of confirmation / recording work of the measurer. .
  • thermometer in the case of the thermometer described in Patent Document 1, a thermistor is used as the temperature sensor.
  • the thermistor is advantageous in that it is small, light, and inexpensive, but has the disadvantage that its temperature characteristics are non-linear, aging is likely to occur, and it is susceptible to noise. For this reason, there is a limit in measurement accuracy, and in order to realize more accurate body temperature measurement (for example, body temperature measurement when accuracy of about ⁇ 0.05 ° C. is required), a temperature sensor having high measurement accuracy It is desirable to apply.
  • the present invention has been made in view of the above problems, and an object of the present invention is to realize highly accurate body temperature measurement in an attached thermometer equipped with an antenna.
  • thermometer has the following configuration. That is, A body temperature tag including an antenna unit and a processing unit; A back film configured to be capable of being attached to the body surface of the subject; and A heat insulating material covering the processing section; A thermometer comprising a surface film sandwiched between the body temperature tag covered with the heat insulating material and the back film,
  • the processor is A power supply circuit connected to the antenna unit and activated in response to generation of an induced electromotive force in the antenna unit; Detection means in which two or more semiconductor temperature sensors for detecting a band gap voltage when two types of semiconductors of P-type and N-type are coupled and current is passed through the coupling portion of the two types of semiconductors are connected in parallel
  • Storage means for storing calibration data for calibrating the band gap voltage detected by the detection means, A band gap voltage detected by the detection means is transmitted through the antenna unit together with the calibration data when the power supply circuit is activated.
  • FIG. 1 is a diagram showing an external configuration of a body temperature measurement system 100 including a thermometer 110 and a data reading device 101 according to the first embodiment of the present invention.
  • FIG. 2 is a diagram illustrating a functional configuration of the body temperature tag 113 including the antenna 114 and the processing unit 115.
  • FIG. 3 is a diagram illustrating a functional configuration of the data reading apparatus 101.
  • FIG. 4 is a diagram illustrating a flow of a body temperature measurement process in the body temperature measurement system 100.
  • FIG. 5 is a diagram illustrating characteristics of the semiconductor temperature sensor.
  • FIG. 1 is a diagram showing an external configuration of a body temperature measurement system 100 including a thermometer 110 and a data reading device 101 according to the first embodiment of the present invention.
  • FIG. 2 is a diagram illustrating a functional configuration of the body temperature tag 113 including the antenna 114 and the processing unit 115.
  • FIG. 3 is a diagram illustrating a functional configuration of the data reading apparatus 101.
  • FIG. 4 is a diagram
  • FIG. 6 is a diagram illustrating a circuit configuration of the sensor unit 211.
  • FIG. 7 is a diagram illustrating a circuit configuration of the circuit unit 212.
  • FIG. 8 is a diagram illustrating a circuit configuration of the excessive rise prevention unit 201.
  • FIG. 9 is a diagram illustrating a manufacturing process of the thermometer 110.
  • FIG. 10 is a diagram for explaining the contents of the body temperature data calculation process in the signal processing unit 304.
  • FIG. 11 is a diagram illustrating an external configuration of a body temperature measurement system 1100 including a thermometer 1110 and a data reading device 1101 according to the second embodiment of the present invention.
  • FIG. 12 is a diagram illustrating a state in which the measurement unit 1140 of the thermometer 1110 is attached to the armpit of the subject 1150.
  • FIG. 13 is a view showing a manufacturing process of the thermometer 1110.
  • thermometer described in each of the following embodiments uses a semiconductor temperature sensor (a sensor that detects a band gap voltage generated in proportion to the temperature at a joint between a P-type semiconductor and an N-type semiconductor) as a temperature sensor.
  • the semiconductor temperature sensor is suitable for high-precision body temperature measurement because it has high linearity in temperature characteristics, is resistant to changes with time, and is hardly affected by noise.
  • FIG. 1 shows a thermometer (an affixed thermometer with an antenna) 110 provided with a wireless tag (RF-ID) including a semiconductor temperature sensor and a portable person by a measurer according to the first embodiment of the present invention. It is a figure which shows the external appearance structure of the body temperature measurement system 100 provided with the data reader (portable apparatus) 101.
  • FIG. 1 shows a thermometer (an affixed thermometer with an antenna) 110 provided with a wireless tag (RF-ID) including a semiconductor temperature sensor and a portable person by a measurer according to the first embodiment of the present invention.
  • RFID wireless tag
  • thermometer 110 is fixed by sandwiching a body temperature tag 113, which is a wireless tag, between a film 111 on the front surface and a film 112 on the back surface (semi-permeable, thickness is about 100 ⁇ m). It becomes the composition.
  • a body temperature tag 113 which is a wireless tag
  • urethane polymers such as polyether urethane and polyester urethane
  • amide polymers such as polyether polyamide block polymer
  • acrylic polymers such as polyacrylate, polyethylene, polypropylene, ethylene / acetic acid It can be obtained from materials such as polyolefin polymers such as vinyl copolymers, and polyester polymers such as polyether polyesters.
  • the film 112 on the back surface is preferably selected from materials having water vapor permeability so as not to cause stuffiness or whitening when applied to the skin surface.
  • materials having water vapor permeability so as not to cause stuffiness or whitening when applied to the skin surface.
  • a urethane or amide film is used. Is preferred.
  • the front film 111 and the back film 112 may be made of any one of the above materials, or may be a laminated film in which a plurality of films made of any material are laminated.
  • the thickness of the film 112 on the back surface should be about 10 to 100 ⁇ m, preferably about 20 to 40 ⁇ m so as not to give a sense of incongruity when applied to the skin surface. Further, in order to improve the skin followability when applied to the skin surface, it is preferable to adjust the tensile strength to 100 to 900 kg / cm 2 and the 100% modulus to about 10 to 100 kg / cm 2 . The use of the back film 112 adjusted to this range is effective when applied to a skin surface with a large movement.
  • the film 112 on the back surface not only a non-porous film but also a porous film that is water vapor permeable and water impermeable is effective from the viewpoint of preventing stuffiness during sticking.
  • the material is not particularly limited, and can be easily obtained by applying a known porous technique.
  • a non-porous film the tendency for water vapor permeability to decrease as the film thickness increases appears significantly, but in the case of a porous film, the decrease in water vapor permeability does not appear in proportion to the thickness, which is useful. It is.
  • the adhesive film is applied to the film 112 on the back surface, and the thermometer 110 can be directly attached to an appropriate measurement site on the body surface of the subject.
  • Any adhesive can be used as long as it is used as a normal medical grade.
  • Solvent-based, water-based, hot-melt-based, and dry blend-based pressure-sensitive adhesives it is desirable to avoid the use of acrylic adhesives and polyurethane adhesives when radiation sterilization, especially intense gamma irradiation sterilization, is required. This is because there is a risk of lowering the adhesive strength due to irradiation.
  • any pressure-sensitive adhesive can be used as long as it is used as a normal medical grade.
  • acrylic pressure-sensitive adhesive, polyurethane-based pressure-sensitive adhesive, natural rubber or synthetic rubber-based pressure-sensitive adhesive, and medical polymer are mainly used.
  • Solvent-based, water-based, hot-melt-based, and dry-blend-based pressure-sensitive adhesives that are used as components are listed.
  • the film 111 on the front surface and the film 112 on the back surface are both flexible, and can be deformed along the shape of the measurement site when the thermometer 110 is attached to the measurement site of the subject. . In this way, the thermometer 110 can accurately detect the body temperature of the subject by fixing the processing unit 115 in close contact with the measurement site.
  • a body temperature tag 113 which is a wireless tag having an RF-ID function and including a semiconductor temperature sensor, includes an antenna coil (hereinafter simply referred to as an antenna) 114 and a processing unit 115 on a base sheet.
  • the body temperature tag 113 receives power supply from the data reading device 101 via the antenna 114 (for example, power supply by generation of induced electromotive force due to electromagnetic waves having a frequency of 13.56 MHz), so that the power supply circuit included in the processing unit 115 By supplying power to (not shown), the entire processing unit 115 is activated, and band gap voltage data (voltage data correlated with the body temperature of the subject) acquired in a temperature sensing unit including a semiconductor temperature sensor described later. ) Are transmitted as data together with various information to the data reading apparatus 101 via the antenna 114.
  • the processing unit 115 is covered with a heat insulating material (for example, an aluminum material having a thickness of about 1 mm) (see the AA cross section). . Thereby, it becomes possible to remove the influence of the outside air temperature.
  • a heat insulating material for example, an aluminum material having a thickness of about 1 mm
  • the data reading device 101 includes an RF-ID reader / writer.
  • the data reader 101 is magnetically coupled to the body temperature tag 113, and is connected to a power supply circuit included in the processing unit 115 of the body temperature tag 113. Power supply and reception of data from the body temperature tag 113.
  • thermometer 110 is an affixed thermometer equipped with an antenna, and is configured to operate by receiving power supply from the RF-ID reader / writer of the data reader. Therefore, there is no need to mount a power source inside, and a reduction in size and weight can be realized. As a result, it can be worn for a long time on the measurement site of the subject.
  • the measurement result is that the data reader 101 having an RF-ID reader / writer that transmits an electromagnetic wave of a predetermined frequency, for example, 13.56 MHz, is brought close to the measurement site to which the thermometer 110 is attached to about 5 to 15 mm. Therefore, it is possible to greatly reduce the burden of confirmation and recording work of measurement results by the measurer.
  • a predetermined frequency for example, 13.56 MHz
  • FIG. 2 is a diagram illustrating a functional configuration of the body temperature tag 113 including the antenna 114 and the processing unit 115.
  • reference numeral 201 denotes an overheating prevention unit, which controls to stop the body temperature measurement process when the body temperature tag 113 enters a state that affects the accuracy of body temperature measurement.
  • the state that affects the accuracy of the body temperature measurement is, for example, that excessive power is supplied from the data reading device 101 via the antenna 114 and the body temperature tag 113 itself generates heat (temperature rise). A state that gives an error to the result. Details of the circuit configuration of the excessive rise prevention unit 201 will be described later.
  • the 202 is a wireless communication unit and includes a rectifier circuit, a booster circuit, and the like.
  • the AC voltage generated in the antenna 114 is converted into a predetermined DC voltage and supplied to the storage unit 203 and the control unit 205.
  • the voltage data acquired by the control unit 205 is transmitted to the data reading apparatus 101 via the antenna 114 as data of a predetermined format together with various information.
  • 203 is a storage unit, which stores calibration data of a temperature sensing unit described later, identification information unique to the body temperature tag 113, and the like.
  • Reference numeral 204 denotes a temperature sensing unit, which includes a sensor unit 211 including a semiconductor temperature sensor and a circuit unit 212 that processes the output of the sensor unit 211. Details of the circuit configurations of the sensor unit 211 and the circuit unit 212 will be described later.
  • the control unit 205 is a control unit that controls the operations of the wireless communication unit 202 and the storage unit 203.
  • the output from the temperature sensing unit 204 is processed and transmitted to the wireless communication unit 202 as voltage data.
  • a sufficient voltage is necessary to achieve highly accurate body temperature measurement, for example, 0.01 ° C to 0.05 ° C measurement accuracy. Therefore, since the voltage (Vcc) higher than the voltage necessary for operating the storage unit 203 and the control unit 205 is required, the control unit 205 is provided with a power supply circuit (boost means) for that purpose. It shall be. This power supply circuit is activated as induction machine power is generated in the antenna 114.
  • FIG. 3 is a diagram illustrating a functional configuration of the data reading apparatus 101.
  • the data reading device 101 includes a power supply unit composed of a battery, a rechargeable battery, etc., a power ON / OFF switch, a selection switch (selection means) for selecting a measurement range, and operation switches including a body temperature data reading start switch. This is omitted here.
  • reference numeral 300 denotes an RF-ID reader / writer, which includes an antenna 301, a wireless communication unit 302, a signal conversion unit 303, and a signal processing unit 304.
  • the antenna 301 generates electromagnetic waves having a predetermined frequency, for example, 13.56 MHz, and magnetically couples with the antenna 114 of the body temperature tag 113 to supply power to the power circuit of the body temperature tag 113, Data is received from the body temperature tag 113.
  • a predetermined frequency for example, 13.56 MHz
  • the wireless communication unit 302 in order to supply power to the body temperature tag 113 via the antenna 301, the voltage applied to the antenna 301 is controlled, and the data received from the body temperature tag 113 via the antenna 301 is converted into the signal conversion unit 303. Or send to.
  • the signal conversion unit 303 converts the data transmitted from the wireless communication unit 302 into digital data and transmits it to the signal processing unit 304.
  • the signal processing unit 304 processes the digital data received from the signal conversion unit 303 and calculates the body temperature. Specifically, body temperature data is calculated based on voltage data and calibration data included in the received digital data. The calculated body temperature data is transmitted to the control unit 311 together with the identification information included in the received digital data.
  • the control unit 311 controls operations of the wireless communication unit 302, the signal conversion unit 303, and the signal processing unit 304.
  • the body temperature data transmitted from the signal processing unit 304 is stored in the storage unit 312 together with the identification information, or displayed on the display unit 313. Furthermore, body temperature data stored in the storage unit 312 is transmitted to the other information processing apparatus (another information processing apparatus connected by wire via the wired communication unit 314) via the wired communication unit 314 together with the identification information.
  • the other information processing apparatus another information processing apparatus connected by wire via the wired communication unit 314
  • FIG. 4 is a diagram illustrating a flow of a body temperature measurement process in the body temperature measurement system 100.
  • the data reading device 101 is placed under the armpit where the measurer (not shown) is one of the appropriate locations for the body temperature measurement of the subject (not shown).
  • the measurer is one of the appropriate locations for the body temperature measurement of the subject (not shown).
  • a body temperature data reading start switch for example, an electromagnetic wave of a predetermined frequency, for example, 13.56 MHz is generated, and the magnetic coupling between the antenna 301 and the antenna 114 Power is supplied from the data reader 101 to the thermometer 110 (401).
  • the processing unit 115 In the thermometer 110 to which power is supplied, the processing unit 115 is activated, and it is determined whether or not the body temperature tag 113 is in a state that affects the accuracy of body temperature measurement. When it is determined that the processing unit 115 is in a state that affects the accuracy of body temperature measurement, the processing unit 115 does not perform subsequent processing. In this case, the data reading apparatus 101 determines that no data is transmitted from the thermometer 110 within a predetermined time after power is supplied, and displays an error on the display unit 313 as a display process (421).
  • the processing unit 115 starts processing.
  • a current is passed through the semiconductor temperature sensor in the sensor unit 211 to detect a band gap voltage (413).
  • circuit unit 212 processes the detected band gap voltage (414), and the control unit 205 acquires voltage data (415).
  • the acquired voltage data is transmitted to the data reading device 101 together with the calibration data and identification information stored in the storage unit 203 (402, 416).
  • the data reader 101 calculates body temperature data based on voltage data and calibration data transmitted from the thermometer 110 as display processing. Further, the calculated body temperature data is stored in the storage unit 312 in association with the identification information and displayed on the display unit 313 (421).
  • FIG. 5 is a diagram illustrating characteristics of the semiconductor temperature sensor.
  • the semiconductor temperature sensor applied to the sensor unit 211 is configured by combining a P-type semiconductor and an N-type semiconductor, and when a direct current is passed, the semiconductor temperature sensor correlates with the temperature and is connected to the coupling unit (junction).
  • the generated voltage (band gap voltage Vb) is detected (5a in FIG. 5).
  • the band gap voltage Vb and the temperature have a linearity in a wide range of about ⁇ 40 ° C. to + 150 ° C. as shown in 5b of FIG.
  • the semiconductor temperature sensor has an advantage that it is more resistant to changes with time and less susceptible to noise than the thermistor.
  • FIG. 6 is a diagram illustrating a circuit configuration of the sensor unit 211 configured using the semiconductor temperature sensor illustrated in 5a of FIG.
  • reference numeral 601 denotes a constant current circuit, which adjusts the current flowing through each semiconductor temperature sensor to be uniform based on the power supply Vcc supplied from the control unit 205.
  • the 602 is a semiconductor temperature sensor, and is connected in series to the constant current circuit 601 on the downstream side of the constant current circuit 601.
  • a plurality of semiconductor temperature sensors 602 are connected to the constant current circuit 601, preferably 6 to 10, particularly preferably 8, and the semiconductor temperature sensors are connected in parallel to each other. The greater the number of semiconductor temperature sensors connected in parallel, the better the temperature resolution, but the higher the manufacturing cost, while the smaller the temperature resolution, the lower the temperature resolution.
  • the reason why the plurality of semiconductor temperature sensors are connected in parallel is to eliminate the influence of individual differences of the semiconductor temperature sensors. In order to realize more accurate body temperature measurement, the influence of individual differences of semiconductor temperature sensors cannot be ignored.
  • a plurality of semiconductor temperature sensors particularly preferably 8 to 10 semiconductor temperature sensors, are arranged in parallel. By connecting and taking an average value, the influence of individual differences is eliminated, a temperature resolution of 0.01 ° C. is obtained, and a measurement accuracy within 0.05 ° C. is obtained.
  • the sensor unit 211 outputs an average value Vb_avg of the voltages Vb1, Vb2,... Vbn output from each semiconductor temperature sensor.
  • each semiconductor temperature sensor is not limited to once, and may be configured to flow multiple times.
  • the voltage Vb_avg is output from the sensor unit 211 a plurality of times.
  • FIG. 7 is a diagram illustrating a circuit configuration of the circuit unit 212.
  • the circuit unit 212 includes a system connected to the A / D converter 701 via the comparison / amplifier 711 and the analog switch 712, and an A / D via the comparison / amplifier 721 and the analog switch 722. It is composed of two systems connected to the D converter 701.
  • the former system inputs the voltage Vb_avg output from the sensor unit 211 to the A / D converter 701 in the measurement range of ⁇ 40 ° C. to + 150 ° C.
  • the latter system outputs the voltage Vb_avg output from the sensor unit 211 to the A / D converter 701 in a measurement range of 20 ° C. to 50 ° C.
  • Whether to output using the first system or the second system is determined by selecting the measurement range with the selection switch (not shown) of the data reader 101. It is controlled by switching the analog switches 712 and 722 based on a signal from the control circuit 702.
  • the second system is selected.
  • the voltage Vb_avg input to the A / D converter 701 is A / D converted by the A / D converter 701 and input to the control circuit 702 as digital data.
  • Digital data input to the control circuit 702 is transmitted to the wireless communication unit 202.
  • each digital data is temporarily stored in the memory 703, and all the digital data stored in the memory 703 is stored in the control circuit 702. After calculating the average value, it may be transmitted to the wireless communication unit 202.
  • FIG. 8 is a diagram illustrating a circuit configuration of the excessive rise prevention unit 201.
  • reference numerals 801 and 802 denote switches.
  • the temperature upper limit signal is output when the digital data value calculated by the control unit 205 is less than or equal to a predetermined value, determining that the temperature measurement accuracy has been affected. .
  • a predetermined value determining that the temperature measurement accuracy has been affected.
  • the processing unit 115 stops the processing when it enters a state that affects the accuracy of body temperature measurement. As a result, it is possible to avoid displaying an erroneous measurement result in the data reading apparatus 101.
  • FIG. 9 is a diagram illustrating a manufacturing process of the thermometer 110.
  • thermometer 110 can be roughly divided into a body temperature tag manufacturing process, a calibration process, and a post-processing process.
  • a band-shaped base sheet 901 in which a plurality of antennas 114 are arranged is sequentially conveyed to the semiconductor temperature sensor mounting device 911, and the processing unit 115 is electrically connected to each antenna 114. Thereby, the body temperature tag 113 will be produced
  • the constant temperature bath 912 is a bath managed at a preset temperature, for example, 37 ° C.
  • An RF-ID reader / writer 913 is disposed inside the thermostat 912, and each body temperature tag 113 is transmitted by an electromagnetic wave having a predetermined frequency, for example, 13.56 MHz when passing over the RF-ID reader / writer 913. Communicate with each body temperature tag 113.
  • the band gap voltage data in each body temperature tag 113 is received, and the received band gap voltage data is written into the storage unit 203 of each body temperature tag 113 as calibration data together with the temperature of the thermostat 912.
  • the base sheet 901 is conveyed at a sufficiently low speed, the temperature in the thermostat 912 is transmitted to the body temperature tag 113, and the temperature reaches an equilibrium state, and then the RF-ID reader / writer 913 is It is designed to pass through.
  • thermostat 912 only one thermostat 912 is disposed, but the number of thermostats is not limited to one.
  • a plurality of thermostats set at different temperatures for example, 32 ° C. and 42 ° C., or 32 ° C., 36 ° C. and 42 ° C. are prepared, and calibration data at each temperature is written to each temperature tag 113. Also good.
  • one of the thermostats may be used for testing the body temperature tag 113.
  • the body temperature tag 113 in which the calibration data is written is transported to a thermostat (temperature test chamber) controlled at a preset temperature, and band gap voltage data and calibration data are received from the body temperature tag 113. To do. Then, the temperature calculated based on the voltage data and the calibration data is compared with the temperature of the thermostatic chamber, and it is determined whether or not it is within a predetermined error range.
  • the base sheet 901 in which a plurality of body temperature tags 113 in which calibration data is written is arranged is sequentially conveyed to the film superposing device 914.
  • the processing unit 115 of each body temperature tag 113 is covered with a heat insulating material (for example, aluminum material having a thickness of about 1 mm, foaming polyurethane, or the like), and the films 111 and 112 are formed on the front and back surfaces of the base sheet 901. (Semi-permeable, thickness is about 100 ⁇ m) is bonded with an adhesive.
  • the adhesive mentioned above is applied to the film 112 on the back surface.
  • the base sheet 901 on which the film is bonded in the film superimposing device 914 is conveyed to the punching device 915 and cut for each body temperature tag 113, so that the thermometer 110 is generated.
  • FIG. 10 is a diagram for explaining the content of processing for calculating body temperature data in the signal processing unit 304.
  • the signal processing unit 304 corrects the graph (function) indicating the correspondence between the band gap voltage data and the body temperature data in the reference semiconductor temperature sensor based on the calibration data, and then substitutes the received band gap voltage data. By doing so, body temperature data is derived.
  • 10a in FIG. 10 is a diagram showing a correction process when one type of calibration data corresponding to one type of temperature is received.
  • the offset value of the correspondence relationship between the band gap voltage data and the body temperature data in the semiconductor temperature sensor serving as a reference is received.
  • the graph 1001 is translated in the direction of the arrow as a whole, and a graph 1002 is obtained.
  • the signal processing unit 304 derives body temperature data by substituting the voltage data received from the thermometer 110 into the graph 1002 after the parallel movement.
  • 10b in FIG. 10 is a diagram showing a correction process when two types of calibration data corresponding to two types of temperatures are received. As shown in 10b of FIG. 10, when two types of calibration data corresponding to two types of temperatures are received, a straight line 1011 passing through the two points is calculated, and this is calculated as band gap voltage data in the semiconductor temperature sensor. It is a graph showing the correspondence with body temperature data.
  • the signal processing unit 304 derives body temperature data by substituting the band gap voltage data received from the thermometer 110 into the calculated straight line.
  • 10c of FIG. 10 is a diagram showing a correction process when three or more types of calibration data corresponding to three or more types of temperatures are received. As shown in 10c of FIG. 10, when three or more kinds of calibration data corresponding to three or more kinds of temperatures are received, a regression line 1021 is calculated by the least square method based on the three or more points. This is a graph showing the correspondence between the band gap voltage data and the body temperature data in the semiconductor temperature sensor.
  • the signal processing unit 304 calculates the body temperature data by substituting the band gap voltage data received from the thermometer 110 into the calculated regression line 1021.
  • thermometer in the present embodiment is configured to apply a semiconductor temperature sensor as an affixed thermometer equipped with an antenna.
  • the treatment part is covered with a heat insulating material.
  • a plurality of semiconductor temperature sensors are connected in parallel in the sensor unit.
  • a current was passed through the sensor section a plurality of times and an average value was output during one body temperature measurement.
  • calibration data is stored for each body temperature tag in the storage section of the body temperature tag, and when the voltage data is transmitted by the data reader, the calibration data is also transmitted. It was set as the structure to do.
  • the overheating prevention unit stops the body temperature measurement and the erroneous measurement result is not displayed on the data reader.
  • the processing unit is arranged in the antenna.
  • the present invention is not limited to this, and the processing unit is connected to the antenna via a conductor extending from the antenna. May be.
  • the body temperature measurement system in the present embodiment will be described. For the sake of simplification, the description will mainly be made on differences from the first embodiment.
  • FIG. 11 shows a thermometer (attached thermometer equipped with an antenna) 1110 provided with a wireless tag (RF-ID) including a semiconductor temperature sensor according to the second embodiment of the present invention, and portable by a measurer. It is a figure which shows the external appearance structure of the body temperature measurement system 1100 provided with the data reader (portable apparatus) 1101.
  • RF-ID wireless tag
  • thermometer 1110 can be functionally divided into three parts.
  • the first part is an antenna part 1120 including an antenna 1114
  • the second part is an extension part 1130 provided with a conducting wire 1115 that electrically connects the antenna 1114 and the processing part 1116, and a third part.
  • the antenna 1114 has the same configuration and function as the antenna 114 described in the first embodiment.
  • the processing unit 1116 has the same configuration and function as the processing unit 115 in the first embodiment.
  • the body temperature measurement unit 1140 has the same configuration and function as the processing unit 115 in the first embodiment.
  • the data reading device (portable device) 1101 also has the same configuration and function as the data reading device 101 described in the first embodiment.
  • the antenna 1114 constituting the antenna portion 1120, the conducting wire 1115 constituting the extending portion 1130, and the processing portion 1116 constituting the body temperature measuring portion 1140 are integrally formed on the base sheet as a body temperature tag, Between the film 1111 and the back film 1112 (semi-permeable, thickness is about 100 ⁇ m).
  • the antenna 1114, the conductive wire 1115, and the processing unit 1116 that are integrally formed on the base sheet are collectively referred to as a body temperature tag 1113.
  • the film 1112b constituting the antenna portion 1120 and the extending portion 1130 is a urethane polymer such as polyether urethane or polyester urethane, an amide polymer such as polyether polyamide block polymer, poly It can be obtained from materials such as acrylic polymers such as acrylate, polyolefin polymers such as polyethylene, polypropylene, and ethylene / vinyl acetate copolymers, and polyester polymers such as polyether polyester.
  • the film 1112a constituting the body temperature measuring unit 1140 can be selected from materials having water vapor permeability so as not to cause stuffiness or whitening when being applied to the skin surface.
  • a urethane film or an amide film is used.
  • the front film 1111 and the back film 1112b may be made of any one of the above materials, or may be a laminated film in which a plurality of films made of any material are laminated.
  • the thickness of the film 1112a on the back surface should be about 10 to 100 ⁇ m, preferably about 20 to 40 ⁇ m, so as not to give a sense of incongruity when it is applied to the skin surface. Further, in order to improve the skin followability when applied to the skin surface, it is preferable to adjust the tensile strength to 100 to 900 kg / cm 2 and the 100% modulus to about 10 to 100 kg / cm 2 . Use of the back film 1112a adjusted to this range is effective when affixed to a skin surface with large movement.
  • the material is not particularly limited, and can be easily obtained by applying a known porous technique.
  • a non-porous film the tendency for water vapor permeability to decrease as the film thickness increases appears significantly, but in the case of a porous film, the decrease in water vapor permeability does not appear in proportion to the thickness, which is useful. It is.
  • the adhesive film is applied to the film 1112a on the back surface, and the thermometer 1110 can be directly attached to an appropriate measurement site on the body surface of the subject.
  • Any adhesive can be used as long as it is used as a normal medical grade.
  • Solvent-based, water-based, hot-melt-based, and dry blend-based pressure-sensitive adhesives it is desirable to avoid the use of acrylic adhesives and polyurethane adhesives when radiation sterilization, especially intense gamma irradiation sterilization, is required. This is because there is a risk of lowering the adhesive strength due to irradiation.
  • the film 1111 on the front surface and the film 1112a on the back surface are both flexible, and can be deformed along the shape of the measurement site when the thermometer 1110 is attached to the measurement site of the subject. . In this way, the thermometer 1110 can accurately detect the body temperature of the subject by fixing the processing unit 1116 in close contact with the measurement site.
  • the processing unit 1116 is covered with a heat insulating material (for example, an aluminum material having a thickness of about 1 mm). Thereby, the influence of outside temperature (environment temperature) can be removed.
  • a heat insulating material for example, an aluminum material having a thickness of about 1 mm.
  • the data reading device 1101 includes an RF-ID reader / writer.
  • a predetermined frequency for example, 13.2.
  • a 56 MHz electromagnetic wave is generated and magnetically coupled with the body temperature tag 1113, and power is supplied to the power supply circuit included in the processing unit 115 of the body temperature tag 1113 and data is received from the body temperature tag 1113.
  • FIG. 12 shows a state in which the body temperature measurement unit 1140 of the thermometer 1110 is attached to the armpit, which is one of the appropriate positions of the body temperature measurement site of the subject 1150.
  • the body temperature measuring unit 1140 and the antenna unit 1120 are connected via the extending portion 1130, so that the body temperature measuring unit 1140 is attached to the armpit of the subject 1150. Even in this state, the antenna unit 1120 can be disposed at a position away from the armpit of the subject 1150.
  • the measurer 1160 brings the data reading device 1101 close, for example, by pressing a body temperature data reading start switch (not shown), an electromagnetic wave having a predetermined frequency, for example, 13.56 MHz is generated, and the body temperature tag 1113 Can be magnetically coupled easily and reliably. That is, it is possible to prevent the problem of reading error that may occur in the case of a pasted thermometer equipped with an antenna.
  • FIG. 13 is a diagram showing a manufacturing process of the thermometer 1110.
  • the manufacturing process of the thermometer 1110 is the same as that shown in FIG. 9 except that the shape of the body temperature tag 1113 is different, and thus the description thereof is omitted here.
  • the measurement accuracy is 0 by obtaining a temperature resolution of 0.01 ° C. in 32 to 42 ° C., which is a general measurement range of human body temperature. It became possible to achieve highly accurate body temperature measurement within 0.05 ° C, and to reliably read data from an attached thermometer equipped with an antenna.
  • the antenna unit 1120, the extending unit 1130, and the body temperature measuring unit 1140 are arranged on the same plane.
  • the present invention is not limited to this. It is good also as a shape which distributes the installation part 1130 perpendicularly
  • the antenna part 1120 and The extending portion 1130 may have a shape that is asymmetrically arranged with respect to the body temperature measuring portion 1140.
  • the body temperature measurement unit 1140 has a shape and size suitable for the measurement site of the subject to be pasted. Further, the extension unit is arranged so that the antenna unit 1120 can be securely magnetically coupled to the data reader 1101 in a state where the body temperature measurement unit 1140 is attached to the measurement site of the subject. It is desirable that the shapes and sizes of the 1130 and the antenna unit 1120 be determined.
  • the processing unit 115 determines that the measurement accuracy is affected and forcibly turns off the switch. You may comprise as follows.
  • the number of semiconductor temperature sensors connected in parallel in the sensor unit 211 is not specifically mentioned. For example, it is desirable to connect approximately eight semiconductor temperature sensors in parallel. This is because if the number of semiconductor temperature sensors connected in parallel is small, the influence of individual differences increases and the measurement accuracy decreases, while if the number of semiconductor temperature sensors is too large, the influence of errors due to heat generation increases.
  • thermometer 110 transmits voltage data, calibration data, and identification information to the data reading device 101.
  • the present invention is not limited to this.
  • information regarding the measurement range after switching may be transmitted.
  • the data reading apparatus 101 calculates the body temperature data in consideration of the received information regarding the measurement range.
  • the measurement range may be switched based on an instruction from the data reading device 101.
  • the data reading apparatus 101 calculates body temperature data in consideration of the instructed measurement range.

Abstract

High accuracy body temperature measurement is achieved in an adhesive thermometer. The disclosed medical thermometer is equipped with a body temperature tag (113), a back film (112) that is constituted to be adhesive, a heat insulating material that covers a processor (115), and a surface film (111) that is sandwiched between the processor (115) and the back film (112). The thermometer is characterized in that the processor (115) is equipped with a power circuit that is connected to an antenna (114) and that is activated accompanying the generation of induced electromotive force in the antenna (114), a detection means to which two types of semiconductors—a P-type and an N-type—are coupled and wherein two or more semiconductor temperature sensors which detect band-gap voltage are connected in parallel, and a storage means which stores calibration data to calibrate the band-gap voltage detected by the aforementioned detection means. With the activation of the aforementioned power circuit, the band-gap voltage detected by the aforementioned detection means is transmitted via the antenna (114) together with the aforementioned calibration data.

Description

体温計及び体温測定システムThermometer and body temperature measurement system
　本発明は、被検者の体温を測定する測定技術に関するものである。特に、体温の測定レンジである３２～４２℃での測定精度に優れた測定技術に関するものである。 The present invention relates to a measurement technique for measuring the body temperature of a subject. In particular, the present invention relates to a measurement technique with excellent measurement accuracy in a body temperature measurement range of 32 to 42 ° C.
　従来より、病院等では、定期的に患者の体温を測定し、測定結果の管理を行っている。一般に、体温の測定に際しては、体温計を被検者の測定部位に装着し、測定が完了するまでの一定時間、静止した状態を維持させる。また、測定が完了すると、測定者が測定結果を確認し記録するといった作業を行う。 Conventionally, hospitals and the like regularly measure patient temperature and manage measurement results. In general, when measuring body temperature, a thermometer is attached to a measurement site of a subject and kept stationary for a certain period of time until the measurement is completed. When the measurement is completed, the measurer performs an operation of confirming and recording the measurement result.
　しかしながら、被検者が幼児や重病の患者の場合、体温計を測定部位に装着させつづけることは困難であり、正確な体温測定を行うことは容易ではない。また、測定結果を確認し記録する作業は、測定者にとって負荷が高く、測定者の手を煩わせることなく記録できることが望ましい。 However, when the subject is an infant or a seriously ill patient, it is difficult to keep the thermometer attached to the measurement site, and accurate temperature measurement is not easy. Further, it is desirable that the work of checking and recording the measurement result is heavy on the measurer and can be recorded without bothering the measurer.
　これに対して、例えば、下記特許文献１では、アンテナを備える貼り付け型の体温計が提案されている。当該特許文献１によれば、体温計がＲＦ－ＩＤリーダ／ライタより電力供給を受けて作動する構成となっているため、体温計に電源を搭載させる必要がなく、体温計の小型・軽量化を実現することができる。この結果、被検者の測定部位に長時間貼り付けておくことが可能となっている。 On the other hand, for example, in Patent Document 1 below, a pasted thermometer including an antenna is proposed. According to Patent Document 1, since the thermometer is configured to operate by receiving power supply from the RF-ID reader / writer, it is not necessary to mount a power source on the thermometer, and the thermometer can be reduced in size and weight. be able to. As a result, it can be pasted on the measurement site of the subject for a long time.
　また、測定結果は、体温計が貼り付けられた測定部位にＲＦ－ＩＤリーダ／ライタを近づけるだけで読み取ることができるため、測定者の確認・記録作業の負荷を大幅に軽減させることが可能である。 In addition, the measurement result can be read simply by bringing the RF-ID reader / writer close to the measurement site to which the thermometer is attached, so that it is possible to greatly reduce the burden of confirmation / recording work of the measurer. .
特開２００３－２７００５１号公報JP 2003-270051 A
　しかしながら、上記特許文献１に記載の体温計の場合、温度センサとして、サーミスタが用いられる構成となっている。一般に、サーミスタは小型・軽量かつ安価であるといった利点がある反面、温度特性が非線形であり、経年変化が生じやすく、かつ、ノイズの影響を受けやすいといった欠点がある。このため、測定精度には限界があり、より高精度な体温測定（例えば、±０．０５℃程度の精度が求められる場合の体温測定）を実現するためには、高い測定精度を有する温度センサを適用することが望ましい。 However, in the case of the thermometer described in Patent Document 1, a thermistor is used as the temperature sensor. In general, the thermistor is advantageous in that it is small, light, and inexpensive, but has the disadvantage that its temperature characteristics are non-linear, aging is likely to occur, and it is susceptible to noise. For this reason, there is a limit in measurement accuracy, and in order to realize more accurate body temperature measurement (for example, body temperature measurement when accuracy of about ± 0.05 ° C. is required), a temperature sensor having high measurement accuracy It is desirable to apply.
　本発明は上記課題に鑑みてなされたものであり、アンテナを備える貼り付け型の体温計において、高精度な体温測定を実現することを目的とする。 The present invention has been made in view of the above problems, and an object of the present invention is to realize highly accurate body temperature measurement in an attached thermometer equipped with an antenna.
　上記の目的を達成するために、本発明に係る体温計は以下のような構成を備える。即ち、
　アンテナ部と処理部とを備える体温タグと、
　被検者の体表面に貼り付け可能に構成される裏面フィルムと、
　前記処理部を覆う保温材と、
　前記保温材で覆われた前記体温タグを、前記裏面フィルムとの間で挟む表面フィルムと、を備える体温計であって、
　前記処理部は、
　　前記アンテナ部に接続され、該アンテナ部における誘導起電力の発生に伴って起動される電源回路と、
　　Ｐ型とＮ型の２種類の半導体が結合され、該２種類の半導体の結合部に電流を流した場合のバンドギャップ電圧を検出する半導体温度センサが、２個以上並列に接続された検出手段と、
　　前記検出手段により検出されるバンドギャップ電圧を校正するための校正データを記憶する記憶手段と、を備え、
　　前記電源回路の起動に伴って、前記検出手段により検出されたバンドギャップ電圧を、前記校正データとともに、前記アンテナ部を介して送信することを特徴とする。 In order to achieve the above object, the thermometer according to the present invention has the following configuration. That is,
A body temperature tag including an antenna unit and a processing unit;
A back film configured to be capable of being attached to the body surface of the subject; and
A heat insulating material covering the processing section;
A thermometer comprising a surface film sandwiched between the body temperature tag covered with the heat insulating material and the back film,
The processor is
A power supply circuit connected to the antenna unit and activated in response to generation of an induced electromotive force in the antenna unit;
Detection means in which two or more semiconductor temperature sensors for detecting a band gap voltage when two types of semiconductors of P-type and N-type are coupled and current is passed through the coupling portion of the two types of semiconductors are connected in parallel When,
Storage means for storing calibration data for calibrating the band gap voltage detected by the detection means,
A band gap voltage detected by the detection means is transmitted through the antenna unit together with the calibration data when the power supply circuit is activated.
　本発明によれば、アンテナを備える貼り付け型の体温計において、特に、０．０１℃の温度分解能による体温測定を実現することが可能となる。 According to the present invention, it is possible to realize body temperature measurement with a temperature resolution of 0.01 ° C., in particular, in an attached thermometer equipped with an antenna.
　本発明のその他の特徴及び利点は、添付図面を参照とした以下の説明により明らかになるであろう。なお、添付図面においては、同じ若しくは同様の構成には、同じ参照番号を付す。 Other features and advantages of the present invention will become apparent from the following description with reference to the accompanying drawings. In the accompanying drawings, the same or similar components are denoted by the same reference numerals.
　添付図面は明細書に含まれ、その一部を構成し、本発明の実施の形態を示し、その記述と共に本発明の原理を説明するために用いられる。
図１は、本発明の第１の実施形態における体温計１１０とデータ読み取り装置１０１とを備える体温測定システム１００の外観構成を示す図である。 図２は、アンテナ１１４と処理部１１５とを備える体温タグ１１３の機能構成を示す図である。 図３は、データ読み取り装置１０１の機能構成を示す図である。 図４は、体温測定システム１００における体温測定処理の流れを示す図である。 図５は、半導体温度センサの特性を示す図である。 図６は、センサ部２１１の回路構成を示す図である。 図７は、回路部２１２の回路構成を示す図である。 図８は、過昇防止部２０１の回路構成を示す図である。 図９は、体温計１１０の製造工程を示した図である。 図１０は、信号処理部３０４における体温データ算出処理の内容を説明するための図である。 図１１は、本発明の第２の実施形態における体温計１１１０とデータ読み取り装置１１０１とを備える体温測定システム１１００の外観構成を示す図である。 図１２は、体温計１１１０の測定部１１４０を被検者１１５０の腋下に装着した様子を示す図である。 図１３は、体温計１１１０の製造工程を示した図である。 The accompanying drawings are included in the specification, constitute a part thereof, show an embodiment of the present invention, and are used to explain the principle of the present invention together with the description.
FIG. 1 is a diagram showing an external configuration of a body temperature measurement system 100 including a thermometer 110 and a data reading device 101 according to the first embodiment of the present invention. FIG. 2 is a diagram illustrating a functional configuration of the body temperature tag 113 including the antenna 114 and the processing unit 115. FIG. 3 is a diagram illustrating a functional configuration of the data reading apparatus 101. FIG. 4 is a diagram illustrating a flow of a body temperature measurement process in the body temperature measurement system 100. FIG. 5 is a diagram illustrating characteristics of the semiconductor temperature sensor. FIG. 6 is a diagram illustrating a circuit configuration of the sensor unit 211. FIG. 7 is a diagram illustrating a circuit configuration of the circuit unit 212. FIG. 8 is a diagram illustrating a circuit configuration of the excessive rise prevention unit 201. FIG. 9 is a diagram illustrating a manufacturing process of the thermometer 110. FIG. 10 is a diagram for explaining the contents of the body temperature data calculation process in the signal processing unit 304. FIG. 11 is a diagram illustrating an external configuration of a body temperature measurement system 1100 including a thermometer 1110 and a data reading device 1101 according to the second embodiment of the present invention. FIG. 12 is a diagram illustrating a state in which the measurement unit 1140 of the thermometer 1110 is attached to the armpit of the subject 1150. FIG. 13 is a view showing a manufacturing process of the thermometer 1110.
　はじめに、本発明の各実施形態の概要について説明する。以下の各実施形態において説明する体温計は、温度センサとして、半導体温度センサ（Ｐ型半導体とＮ型半導体との結合部において、温度に比例して生じるバンドギャップ電圧を検出するセンサ）を用いることを特徴とする。 First, an overview of each embodiment of the present invention will be described. The thermometer described in each of the following embodiments uses a semiconductor temperature sensor (a sensor that detects a band gap voltage generated in proportion to the temperature at a joint between a P-type semiconductor and an N-type semiconductor) as a temperature sensor. Features.
　当該半導体温度センサは、温度特性における線形性が高いうえ、経時変化に強く、かつノイズの影響を受けにくいといった特性があり、高精度な体温測定に適している。 The semiconductor temperature sensor is suitable for high-precision body temperature measurement because it has high linearity in temperature characteristics, is resistant to changes with time, and is hardly affected by noise.
　しかしながら、上記特許文献１において適用されたサーミスタを、単純に半導体温度センサに置き換えただけで、０．０１℃という高精度な温度分解能の体温測定を実現することはできず、適用に際しては体温測定の精度に影響を及ぼす各種要因を排除することが重要となってくる。 However, by simply replacing the thermistor applied in Patent Document 1 with a semiconductor temperature sensor, it is not possible to realize body temperature measurement with a high accuracy temperature resolution of 0.01 ° C. It is important to eliminate various factors that affect the accuracy of the system.
　そこで、以下に説明する各実施形態では、アンテナを備える貼り付け型の体温計において当該半導体温度センサを含む無線タグ（ＲＦ－ＩＤ機能を備えるタグ）を適用するにあたり、体温測定の精度に影響を及ぼす各種要因を排除することで、所望の精度を実現することとした。以下、本発明の各実施形態の詳細について図面を参照しながら説明する。なお、本発明は以下の各実施形態に限定されるものではなく、種々の変形例が採用されうるものとする。 Therefore, in each of the embodiments described below, in applying a wireless tag (a tag having an RF-ID function) including the semiconductor temperature sensor to an affixed thermometer including an antenna, the accuracy of body temperature measurement is affected. By eliminating various factors, the desired accuracy was achieved. Hereinafter, details of each embodiment of the present invention will be described with reference to the drawings. The present invention is not limited to the following embodiments, and various modifications can be adopted.
　［第１の実施形態］
　＜１．体温測定システムの外観構成＞
　図１は、本発明の第１の実施形態における、半導体温度センサを含む無線タグ（ＲＦ－ＩＤ）が配された体温計（アンテナを備える貼り付け型の体温計）１１０と、測定者によって携帯可能なデータ読み取り装置（携帯装置）１０１とを備える体温測定システム１００の外観構成を示す図である。 [First Embodiment]
<1. External configuration of body temperature measurement system>
FIG. 1 shows a thermometer (an affixed thermometer with an antenna) 110 provided with a wireless tag (RF-ID) including a semiconductor temperature sensor and a portable person by a measurer according to the first embodiment of the present invention. It is a figure which shows the external appearance structure of the body temperature measurement system 100 provided with the data reader (portable apparatus) 101. FIG.
　図１に示すように、体温計１１０は、表面のフィルム１１１と裏面のフィルム１１２（半透過性で、厚さは１００μｍ程度）との間に、無線タグである体温タグ１１３が挟まれて固定された構成となっている。 As shown in FIG. 1, the thermometer 110 is fixed by sandwiching a body temperature tag 113, which is a wireless tag, between a film 111 on the front surface and a film 112 on the back surface (semi-permeable, thickness is about 100 μm). It becomes the composition.
　表面のフィルム１１１及び裏面のフィルム１１２としては、ポリエーテルウレタンやポリエステルウレタンなどのウレタン系ポリマー、ポリエーテルポリアミドブロックポリマーなどのアミド系ポリマー、ポリアクリレートなどのアクリル系ポリマー、ポリエチレンやポリプロピレン、エチレン／酢酸ビニル共重合体などのポリオレフィン系ポリマー、ポリエーテルポリエステルなどのポリエステル系ポリマーなどの材料から得ることができる。 As the front film 111 and the back film 112, urethane polymers such as polyether urethane and polyester urethane, amide polymers such as polyether polyamide block polymer, acrylic polymers such as polyacrylate, polyethylene, polypropylene, ethylene / acetic acid It can be obtained from materials such as polyolefin polymers such as vinyl copolymers, and polyester polymers such as polyether polyesters.
　また、裏面のフィルム１１２は皮膚面への貼り付け時にムレや白化などを生じないようにするために、水蒸気透過性を有する材質から選択することが好ましく、例えばウレタン系やアミド系のフィルムを用いることが好適である。なお、表面のフィルム１１１、裏面のフィルム１１２は上記材料のうちの何れか一種からなるものであってもよいし、任意の材料からなるフィルムを複数枚積層した積層フィルムであってもよい。 The film 112 on the back surface is preferably selected from materials having water vapor permeability so as not to cause stuffiness or whitening when applied to the skin surface. For example, a urethane or amide film is used. Is preferred. The front film 111 and the back film 112 may be made of any one of the above materials, or may be a laminated film in which a plurality of films made of any material are laminated.
　裏面のフィルム１１２は皮膚面に貼付した際に、違和感を生じないようにするために、その厚みを１０～１００μｍ、好ましくは２０～４０μｍ程度にすることがよい。また、皮膚面に貼り付けした際の皮膚追従性を良好にするためには、引張強度を１００～９００ｋｇ／ｃｍ２、１００％モジュラスを１０～１００ｋｇ／ｃｍ２程度に調整することが好ましい。この範囲に調整した裏面のフィルム１１２を用いると、動きの大きい皮膚面に貼付した際に効果的である。 The thickness of the film 112 on the back surface should be about 10 to 100 μm, preferably about 20 to 40 μm so as not to give a sense of incongruity when applied to the skin surface. Further, in order to improve the skin followability when applied to the skin surface, it is preferable to adjust the tensile strength to 100 to 900 kg / cm 2 and the 100% modulus to about 10 to 100 kg / cm 2 . The use of the back film 112 adjusted to this range is effective when applied to a skin surface with a large movement.
　また、上記裏面のフィルム１１２として、無孔フィルムだけでなく、水蒸気透過性であって非透水性である多孔性フィルムを用いることも、貼付中のムレの防止の点から効果的である。このようなフィルムの場合には、材質には特に制限はされず、公知の多孔化技術を施すことによって簡単に得ることができる。無孔性フィルムの場合にはフィルム厚が大きくなるほど水蒸気透過性は低下する傾向が顕著に現れるが、多孔性フィルムの場合には厚みに比例して水蒸気透過性の低下が顕著に現れないので有用である。 Also, as the film 112 on the back surface, not only a non-porous film but also a porous film that is water vapor permeable and water impermeable is effective from the viewpoint of preventing stuffiness during sticking. In the case of such a film, the material is not particularly limited, and can be easily obtained by applying a known porous technique. In the case of a non-porous film, the tendency for water vapor permeability to decrease as the film thickness increases appears significantly, but in the case of a porous film, the decrease in water vapor permeability does not appear in proportion to the thickness, which is useful. It is.
　裏面のフィルム１１２には、粘着剤が塗布されており、体温計１１０を、被検者の体表面の適所の測定部位に直接、貼り付けることができるように構成されている。粘着剤は、通常の医療用グレードとして用いられるものであればいずれを用いてもよく、例えばアクリル系粘着剤、ポリウレタン系粘着剤、天然ゴム又は合成ゴム系粘着剤、医用高分子を主成分とする溶剤系、水系、ホットメルト系、ドライブレンド系の粘着剤があげられる。ただし放射線滅菌特に強度のガンマー線照射滅菌が必要な場合にはアクリル系粘着剤やポリウレタン系粘着剤の使用は避けた方が望ましい。これらは放射線照射による粘着力の低下を招くおそれがあるからである。 The adhesive film is applied to the film 112 on the back surface, and the thermometer 110 can be directly attached to an appropriate measurement site on the body surface of the subject. Any adhesive can be used as long as it is used as a normal medical grade. For example, an acrylic adhesive, a polyurethane adhesive, a natural rubber or a synthetic rubber adhesive, and a medical polymer as a main component. Solvent-based, water-based, hot-melt-based, and dry blend-based pressure-sensitive adhesives. However, it is desirable to avoid the use of acrylic adhesives and polyurethane adhesives when radiation sterilization, especially intense gamma irradiation sterilization, is required. This is because there is a risk of lowering the adhesive strength due to irradiation.
　また、裏面のフィルム１１２よりも表面のフィルム１１１の面積が大きい場合には、被検者の測定部位に貼り付けられるように貼り付け領域が残されていて、その領域には粘着剤が設けられ、この粘着剤は、通常の医療用グレードとして用いられるものであればいずれを用いてもよく、例えばアクリル系粘着剤、ポリウレタン系粘着剤、天然ゴム又は合成ゴム系粘着剤、医用高分子を主成分とする溶剤系、水系、ホットメルト系、ドライブレンド系の粘着剤があげられる。ただし放射線滅菌特に強度のガンマー線照射滅菌が必要な場合にはアクリル系粘着剤やポリウレタン系粘着剤の使用は避けた方が望ましい。これらは放射線照射による粘着力の低下を招くおそれがあるからである。 In addition, when the area of the film 111 on the front surface is larger than that of the film 112 on the back surface, a pasting area is left to be pasted on the measurement site of the subject, and an adhesive is provided in that area. Any pressure-sensitive adhesive can be used as long as it is used as a normal medical grade. For example, acrylic pressure-sensitive adhesive, polyurethane-based pressure-sensitive adhesive, natural rubber or synthetic rubber-based pressure-sensitive adhesive, and medical polymer are mainly used. Solvent-based, water-based, hot-melt-based, and dry-blend-based pressure-sensitive adhesives that are used as components are listed. However, it is desirable to avoid the use of acrylic adhesives and polyurethane adhesives when radiation sterilization, especially intense gamma irradiation sterilization, is required. This is because there is a risk of lowering the adhesive strength due to irradiation.
　また、表面のフィルム１１１と裏面のフィルム１１２は、いずれも柔軟性があり、体温計１１０を被検者の測定部位に貼り付けた際に、測定部位の形状に沿って変形できるようになっている。このように、処理部１１５が測定部位に密着して固定されることにより、体温計１１０は、被検者の体温を正確に検出することができる。 Moreover, the film 111 on the front surface and the film 112 on the back surface are both flexible, and can be deformed along the shape of the measurement site when the thermometer 110 is attached to the measurement site of the subject. . In this way, the thermometer 110 can accurately detect the body temperature of the subject by fixing the processing unit 115 in close contact with the measurement site.
　ＲＦ－ＩＤ機能を有し半導体温度センサを含む無線タグである体温タグ１１３は、ベースシート上にアンテナコイル（以下、単にアンテナと称す）１１４と処理部１１５とを備える。体温タグ１１３は、データ読み取り装置１０１から、アンテナ１１４を介して電力供給（例えば１３．５６ＭＨｚの周波数の電磁波による誘導起電力の発生による電力供給）を受けることで、処理部１１５に含まれる電源回路（不図示）に電源が供給されることで、処理部１１５全体が起動し、後述する半導体温度センサを含む感温部において取得されたバンドギャップ電圧データ（被検者の体温と相関する電圧データ）を、各種情報とともにデータとしてアンテナ１１４を介してデータ読み取り装置１０１に送信する。 A body temperature tag 113, which is a wireless tag having an RF-ID function and including a semiconductor temperature sensor, includes an antenna coil (hereinafter simply referred to as an antenna) 114 and a processing unit 115 on a base sheet. The body temperature tag 113 receives power supply from the data reading device 101 via the antenna 114 (for example, power supply by generation of induced electromotive force due to electromagnetic waves having a frequency of 13.56 MHz), so that the power supply circuit included in the processing unit 115 By supplying power to (not shown), the entire processing unit 115 is activated, and band gap voltage data (voltage data correlated with the body temperature of the subject) acquired in a temperature sensing unit including a semiconductor temperature sensor described later. ) Are transmitted as data together with various information to the data reading apparatus 101 via the antenna 114.
　なお、体温タグ１１３を構成するアンテナ１１４と処理部１１５のうち、処理部１１５は、保温材（例えば、厚さ１ｍｍ程度のアルミ材）により覆われているものとする（Ａ－Ａ断面参照）。これにより、外気温度の影響を除去することが可能となる。 Of the antenna 114 and the processing unit 115 constituting the body temperature tag 113, the processing unit 115 is covered with a heat insulating material (for example, an aluminum material having a thickness of about 1 mm) (see the AA cross section). . Thereby, it becomes possible to remove the influence of the outside air temperature.
　データ読み取り装置１０１は、ＲＦ－ＩＤリーダ／ライタを備えており、体温タグ１１３に近づけた際に、体温タグ１１３との間で磁気結合し、体温タグ１１３の処理部１１５に含まれる電源回路への電力供給と、体温タグ１１３からのデータの受信とを行う。 The data reading device 101 includes an RF-ID reader / writer. When the data reading device 101 is close to the body temperature tag 113, the data reader 101 is magnetically coupled to the body temperature tag 113, and is connected to a power supply circuit included in the processing unit 115 of the body temperature tag 113. Power supply and reception of data from the body temperature tag 113.
　このように、体温測定システム１００では、体温計１１０が、アンテナを備える貼り付け型の体温計となっており、データ読み取り装置が有するＲＦ－ＩＤリーダ／ライタより電力供給を受けて作動する構成となっているため、内部に電源を搭載しておく必要がなく、小型・軽量化を実現することができる。この結果、被検者の測定部位に長時間装着しておくことが可能となる。 Thus, in the thermometer measurement system 100, the thermometer 110 is an affixed thermometer equipped with an antenna, and is configured to operate by receiving power supply from the RF-ID reader / writer of the data reader. Therefore, there is no need to mount a power source inside, and a reduction in size and weight can be realized. As a result, it can be worn for a long time on the measurement site of the subject.
　また、測定結果は、所定の周波数、例えば１３．５６ＭＨｚの電磁波を送信するＲＦ－ＩＤリーダ／ライタを備えるデータ読み取り装置１０１を、体温計１１０が貼り付けられた測定部位に５～１５ｍｍ程度に近づけるだけで読み取ることができるため、測定者による測定結果の確認・記録作業の負荷を大幅に軽減させることができる。 In addition, the measurement result is that the data reader 101 having an RF-ID reader / writer that transmits an electromagnetic wave of a predetermined frequency, for example, 13.56 MHz, is brought close to the measurement site to which the thermometer 110 is attached to about 5 to 15 mm. Therefore, it is possible to greatly reduce the burden of confirmation and recording work of measurement results by the measurer.
　＜２．体温タグ１１３の機能構成＞
　次に、体温タグ１１３の機能構成について説明する。図２は、アンテナ１１４と処理部１１５とを備える体温タグ１１３の機能構成を示す図である。 <2. Functional configuration of body temperature tag 113>
Next, the functional configuration of the body temperature tag 113 will be described. FIG. 2 is a diagram illustrating a functional configuration of the body temperature tag 113 including the antenna 114 and the processing unit 115.
　図２において、２０１は過昇防止部であり、体温タグ１１３が体温測定の精度に影響を与える状態となった場合に、体温測定処理を中止するように制御する。ここで体温測定の精度に影響を与える状態とは、例えば、アンテナ１１４を介してデータ読み取り装置１０１より過剰な電源が供給され、体温タグ１１３自体が発熱（温度上昇）することで、体温測定の結果に誤差を与えるような状態をいう。なお、過昇防止部２０１の回路構成の詳細は、後述する。 In FIG. 2, reference numeral 201 denotes an overheating prevention unit, which controls to stop the body temperature measurement process when the body temperature tag 113 enters a state that affects the accuracy of body temperature measurement. Here, the state that affects the accuracy of the body temperature measurement is, for example, that excessive power is supplied from the data reading device 101 via the antenna 114 and the body temperature tag 113 itself generates heat (temperature rise). A state that gives an error to the result. Details of the circuit configuration of the excessive rise prevention unit 201 will be described later.
　２０２は無線通信部であり、整流回路や昇圧回路等を備える。無線通信部２０２では、アンテナ１１４において生じた交流電圧を、所定の直流電圧に変換し、記憶部２０３及びコントロール部２０５に供給する。また、コントロール部２０５において取得された電圧データを各種情報とともに、所定形式のデータとして、アンテナ１１４を介してデータ読み取り装置１０１に送信する。 202 is a wireless communication unit and includes a rectifier circuit, a booster circuit, and the like. In the wireless communication unit 202, the AC voltage generated in the antenna 114 is converted into a predetermined DC voltage and supplied to the storage unit 203 and the control unit 205. In addition, the voltage data acquired by the control unit 205 is transmitted to the data reading apparatus 101 via the antenna 114 as data of a predetermined format together with various information.
　２０３は記憶部であり、後述する感温部の校正データや、体温タグ１１３固有の識別情報等を記憶する。 203 is a storage unit, which stores calibration data of a temperature sensing unit described later, identification information unique to the body temperature tag 113, and the like.
　２０４は感温部であり、半導体温度センサを備えるセンサ部２１１と、センサ部２１１の出力を処理する回路部２１２とを備える。なお、センサ部２１１及び回路部２１２の回路構成の詳細は、後述する。 Reference numeral 204 denotes a temperature sensing unit, which includes a sensor unit 211 including a semiconductor temperature sensor and a circuit unit 212 that processes the output of the sensor unit 211. Details of the circuit configurations of the sensor unit 211 and the circuit unit 212 will be described later.
　２０５はコントロール部であり、無線通信部２０２及び記憶部２０３の動作を制御する。また、感温部２０４からの出力を処理し、電圧データとして無線通信部２０２に送信する。なお、感温部２０４のセンサ部２１１に適用される半導体温度センサにおいて、精度の高い体温測定、例えば０．０１℃～０．０５℃の測定精度を実現するためには、充分な電圧が必要となるため（記憶部２０３やコントロール部２０５を作動させるのに必要な電圧よりも高い電圧（Ｖｃｃ）が必要となるため）、コントロール部２０５には、そのための電源回路（昇圧手段）が備えられているものとする。この電源回路は、アンテナ１１４における誘導機電力の発生に伴って起動される。 205 is a control unit that controls the operations of the wireless communication unit 202 and the storage unit 203. In addition, the output from the temperature sensing unit 204 is processed and transmitted to the wireless communication unit 202 as voltage data. In addition, in the semiconductor temperature sensor applied to the sensor unit 211 of the temperature sensing unit 204, a sufficient voltage is necessary to achieve highly accurate body temperature measurement, for example, 0.01 ° C to 0.05 ° C measurement accuracy. Therefore, since the voltage (Vcc) higher than the voltage necessary for operating the storage unit 203 and the control unit 205 is required, the control unit 205 is provided with a power supply circuit (boost means) for that purpose. It shall be. This power supply circuit is activated as induction machine power is generated in the antenna 114.
　＜３．データ読み取り装置の機能構成＞
　次に、データ読み取り装置１０１の機能構成について説明する。図３は、データ読み取り装置１０１の機能構成を示す図である。データ読み取り装置１０１は、電池、充電池等で構成される電源部、電源ＯＮ／ＯＦＦスイッチ、測定レンジを選択する選択スイッチ（選択手段）、体温データ読み取り開始スイッチを含む操作スイッチを備えているが、ここでは省略している。 <3. Functional configuration of data reader>
Next, the functional configuration of the data reading apparatus 101 will be described. FIG. 3 is a diagram illustrating a functional configuration of the data reading apparatus 101. The data reading device 101 includes a power supply unit composed of a battery, a rechargeable battery, etc., a power ON / OFF switch, a selection switch (selection means) for selecting a measurement range, and operation switches including a body temperature data reading start switch. This is omitted here.
　図３において、３００はＲＦ－ＩＤリーダ／ライタであり、アンテナ３０１、無線通信部３０２、信号変換部３０３、信号処理部３０４とを備える。 3, reference numeral 300 denotes an RF-ID reader / writer, which includes an antenna 301, a wireless communication unit 302, a signal conversion unit 303, and a signal processing unit 304.
　アンテナ３０１は、所定の周波数、例えば１３．５６ＭＨｚの周波数の電磁波を発生させて、体温タグ１１３のアンテナ１１４との間で磁気結合することで、体温タグ１１３の電源回路に電源を供給したり、体温タグ１１３よりデータを受信したりする。 The antenna 301 generates electromagnetic waves having a predetermined frequency, for example, 13.56 MHz, and magnetically couples with the antenna 114 of the body temperature tag 113 to supply power to the power circuit of the body temperature tag 113, Data is received from the body temperature tag 113.
　無線通信部３０２では、アンテナ３０１を介して体温タグ１１３に電源を供給するために、アンテナ３０１に印加する電圧を制御したり、アンテナ３０１を介して体温タグ１１３より受信したデータを信号変換部３０３に送信したりする。 In the wireless communication unit 302, in order to supply power to the body temperature tag 113 via the antenna 301, the voltage applied to the antenna 301 is controlled, and the data received from the body temperature tag 113 via the antenna 301 is converted into the signal conversion unit 303. Or send to.
　信号変換部３０３では、無線通信部３０２より送信されたデータをデジタルデータに変換し、信号処理部３０４に送信する。 The signal conversion unit 303 converts the data transmitted from the wireless communication unit 302 into digital data and transmits it to the signal processing unit 304.
　信号処理部３０４では、信号変換部３０３より受信したデジタルデータを処理し、体温を算出する。具体的には、受信したデジタルデータに含まれる、電圧データと校正データとに基づいて体温データを算出する。また、算出した体温データを、受信したデジタルデータに含まれる識別情報とともにコントロール部３１１に送信する。 The signal processing unit 304 processes the digital data received from the signal conversion unit 303 and calculates the body temperature. Specifically, body temperature data is calculated based on voltage data and calibration data included in the received digital data. The calculated body temperature data is transmitted to the control unit 311 together with the identification information included in the received digital data.
　コントロール部３１１では、無線通信部３０２、信号変換部３０３、信号処理部３０４の動作を制御する。また、信号処理部３０４から送信された体温データを、識別情報とともに記憶部３１２に格納したり、表示部３１３に表示したりする。更に、記憶部３１２に格納された体温データを、識別情報とともに有線通信部３１４を介して、他の情報処理装置（有線通信部３１４を介して有線接続された他の情報処理装置）に送信したりする。 The control unit 311 controls operations of the wireless communication unit 302, the signal conversion unit 303, and the signal processing unit 304. The body temperature data transmitted from the signal processing unit 304 is stored in the storage unit 312 together with the identification information, or displayed on the display unit 313. Furthermore, body temperature data stored in the storage unit 312 is transmitted to the other information processing apparatus (another information processing apparatus connected by wire via the wired communication unit 314) via the wired communication unit 314 together with the identification information. Or
　＜４．体温測定処理の流れ＞
　次に、体温測定システム１００における体温測定処理の流れについて説明する。図４は、体温測定システム１００における体温測定処理の流れを示す図である。 <4. Flow of temperature measurement process>
Next, the flow of the body temperature measurement process in the body temperature measurement system 100 will be described. FIG. 4 is a diagram illustrating a flow of a body temperature measurement process in the body temperature measurement system 100.
　図４に示すように、データ読み取り装置１０１が起動した後に、データ読み取り装置１０１を、測定者（不図示）が被検者（不図示）の体温測定部位の適所の１つである腋下に装着された体温計１１０の近傍に近づけ、例えば体温データ読み取り開始スイッチ（不図示）を押すことで、所定の周波数、例えば１３．５６ＭＨｚの電磁波が発生し、アンテナ３０１とアンテナ１１４との磁気結合により、データ読み取り装置１０１から体温計１１０に対して電源が供給される（４０１）。 As shown in FIG. 4, after the data reading device 101 is activated, the data reading device 101 is placed under the armpit where the measurer (not shown) is one of the appropriate locations for the body temperature measurement of the subject (not shown). By approaching the vicinity of the mounted thermometer 110 and pressing a body temperature data reading start switch (not shown), for example, an electromagnetic wave of a predetermined frequency, for example, 13.56 MHz is generated, and the magnetic coupling between the antenna 301 and the antenna 114 Power is supplied from the data reader 101 to the thermometer 110 (401).
　電源が供給された体温計１１０では、処理部１１５が起動し、体温タグ１１３が体温測定の精度に影響を与える状態になっているか否かを判定する。処理部１１５が体温測定の精度に影響を与える状態になっていると判定された場合には、処理部１１５では、以降の処理は行わない。この場合、データ読み取り装置１０１では、電源供給を行ってから一定時間内に体温計１１０よりデータの送信がないと判断し、表示処理として表示部３１３にエラー表示を行う（４２１）。 In the thermometer 110 to which power is supplied, the processing unit 115 is activated, and it is determined whether or not the body temperature tag 113 is in a state that affects the accuracy of body temperature measurement. When it is determined that the processing unit 115 is in a state that affects the accuracy of body temperature measurement, the processing unit 115 does not perform subsequent processing. In this case, the data reading apparatus 101 determines that no data is transmitted from the thermometer 110 within a predetermined time after power is supplied, and displays an error on the display unit 313 as a display process (421).
　一方、体温タグ１１３が体温測定の精度に影響を与える状態になっていないと判定された場合には、処理部１１５では処理を開始する。 On the other hand, when it is determined that the body temperature tag 113 is not in a state of affecting the accuracy of body temperature measurement, the processing unit 115 starts processing.
　具体的には、予め設定された測定レンジ（詳細は後述）に切り替えた後（４１２）、センサ部２１１内の半導体温度センサに電流を流し、バンドギャップ電圧を検出する（４１３）。 Specifically, after switching to a preset measurement range (details will be described later) (412), a current is passed through the semiconductor temperature sensor in the sensor unit 211 to detect a band gap voltage (413).
　更に、回路部２１２が当該検出されたバンドギャップ電圧を処理し（４１４）、コントロール部２０５では、電圧データを取得する（４１５）。 Further, the circuit unit 212 processes the detected band gap voltage (414), and the control unit 205 acquires voltage data (415).
　取得された電圧データは、記憶部２０３に記憶された校正データ及び識別情報とともに、データ読み取り装置１０１に送信される（４０２、４１６）。 The acquired voltage data is transmitted to the data reading device 101 together with the calibration data and identification information stored in the storage unit 203 (402, 416).
　データ読み取り装置１０１では、表示処理として体温計１１０より送信された電圧データ及び校正データに基づいて体温データを算出する。更に、算出された体温データを、識別情報と対応付けて記憶部３１２に記憶するとともに表示部３１３に表示する（４２１）。 The data reader 101 calculates body temperature data based on voltage data and calibration data transmitted from the thermometer 110 as display processing. Further, the calculated body temperature data is stored in the storage unit 312 in association with the identification information and displayed on the display unit 313 (421).
　＜５．半導体温度センサの説明＞
　次に、センサ部２１１に適用される一般的な半導体温度センサについて説明する。図５は、半導体温度センサの特性を示す図である。本実施形態において、センサ部２１１に適用される半導体温度センサは、Ｐ型半導体とＮ型半導体とが結合して構成され、直流電流を流した場合に温度に相関して結合部（ジャンクション）に生じる電圧（バンドギャップ電圧Ｖｂ）を検出するものである（図５の５ａ）。 <5. Description of semiconductor temperature sensor>
Next, a general semiconductor temperature sensor applied to the sensor unit 211 will be described. FIG. 5 is a diagram illustrating characteristics of the semiconductor temperature sensor. In this embodiment, the semiconductor temperature sensor applied to the sensor unit 211 is configured by combining a P-type semiconductor and an N-type semiconductor, and when a direct current is passed, the semiconductor temperature sensor correlates with the temperature and is connected to the coupling unit (junction). The generated voltage (band gap voltage Vb) is detected (5a in FIG. 5).
　なお、半導体温度センサの場合、図５の５ｂに示すように、バンドギャップ電圧Ｖｂと温度とは、概ね－４０℃から＋１５０℃の広範囲において線形性を有している。また、半導体温度センサは、サーミスタと比較して、経時変化に強く、かつノイズの影響を受けにくいといった利点も有している。 In the case of the semiconductor temperature sensor, the band gap voltage Vb and the temperature have a linearity in a wide range of about −40 ° C. to + 150 ° C. as shown in 5b of FIG. In addition, the semiconductor temperature sensor has an advantage that it is more resistant to changes with time and less susceptible to noise than the thermistor.
　＜６．センサ部２１１の回路構成＞
　次に、センサ部２１１の回路構成について説明する。図６は、図５の５ａに示す半導体温度センサを用いて構成されたセンサ部２１１の回路構成を示す図である。 <6. Circuit Configuration of Sensor Unit 211>
Next, the circuit configuration of the sensor unit 211 will be described. FIG. 6 is a diagram illustrating a circuit configuration of the sensor unit 211 configured using the semiconductor temperature sensor illustrated in 5a of FIG.
　図６において、６０１は定電流回路であり、コントロール部２０５より供給される電源Ｖｃｃに基づいて、各半導体温度センサに流す電流が均一になるように調整する。 In FIG. 6, reference numeral 601 denotes a constant current circuit, which adjusts the current flowing through each semiconductor temperature sensor to be uniform based on the power supply Vcc supplied from the control unit 205.
　６０２は半導体温度センサであり、定電流回路６０１の下流側において、定電流回路６０１に対して直列に接続されている。なお、半導体温度センサ６０２は定電流回路６０１に対して複数個、好ましくは６～１０個、特に好ましくは８個接続されており、それぞれの半導体温度センサは、互いに並列接続される。並列接続される半導体温度センサの個数は、多いほど温度分解能に優れるが、製造コストが高くなり、一方、少ないと温度分解能が低下する。 602 is a semiconductor temperature sensor, and is connected in series to the constant current circuit 601 on the downstream side of the constant current circuit 601. A plurality of semiconductor temperature sensors 602 are connected to the constant current circuit 601, preferably 6 to 10, particularly preferably 8, and the semiconductor temperature sensors are connected in parallel to each other. The greater the number of semiconductor temperature sensors connected in parallel, the better the temperature resolution, but the higher the manufacturing cost, while the smaller the temperature resolution, the lower the temperature resolution.
　このように、複数の半導体温度センサを並列接続したのは、半導体温度センサの個体差の影響を排除するためである。より高精度な体温測定を実現するためには、半導体温度センサの個体差の影響も無視することはできず、センサ部２１１では、複数、特に好ましくは８～１０個の半導体温度センサを並列に接続し平均値をとることで、個体差の影響を排除し、０．０１℃の温度分解能を得て、０．０５℃以内の測定精度を得るようにしている。 The reason why the plurality of semiconductor temperature sensors are connected in parallel is to eliminate the influence of individual differences of the semiconductor temperature sensors. In order to realize more accurate body temperature measurement, the influence of individual differences of semiconductor temperature sensors cannot be ignored. In the sensor unit 211, a plurality of semiconductor temperature sensors, particularly preferably 8 to 10 semiconductor temperature sensors, are arranged in parallel. By connecting and taking an average value, the influence of individual differences is eliminated, a temperature resolution of 0.01 ° C. is obtained, and a measurement accuracy within 0.05 ° C. is obtained.
　このため、センサ部２１１からは、各半導体温度センサより出力された電圧Ｖｂ１、Ｖｂ２、・・・Ｖｂｎの平均値Ｖｂ_ａｖｇが出力される。 Therefore, the sensor unit 211 outputs an average value Vb_avg of the voltages Vb1, Vb2,... Vbn output from each semiconductor temperature sensor.
　なお、各半導体温度センサに電流を流すのは１回に限られず、複数回流すように構成してもよい。その場合、センサ部２１１からは、電圧Ｖｂ_ａｖｇが複数回出力されることとなる。 It should be noted that the current flowing through each semiconductor temperature sensor is not limited to once, and may be configured to flow multiple times. In that case, the voltage Vb_avg is output from the sensor unit 211 a plurality of times.
　＜７．回路部２１２の回路構成＞
　次に、回路部２１２の回路構成について説明する。図７は、回路部２１２の回路構成を示す図である。 <7. Circuit Configuration of Circuit Unit 212>
Next, the circuit configuration of the circuit unit 212 will be described. FIG. 7 is a diagram illustrating a circuit configuration of the circuit unit 212.
　図７に示すように、回路部２１２は、比較・増幅器７１１とアナログスイッチ７１２とを介してＡ／Ｄコンバータ７０１に接続される系と、比較・増幅器７２１とアナログスイッチ７２２とを介してＡ／Ｄコンバータ７０１に接続される系の２系統から構成されている。 As shown in FIG. 7, the circuit unit 212 includes a system connected to the A / D converter 701 via the comparison / amplifier 711 and the analog switch 712, and an A / D via the comparison / amplifier 721 and the analog switch 722. It is composed of two systems connected to the D converter 701.
　前者の系（第１の系）は、センサ部２１１より出力された電圧Ｖｂ_ａｖｇを、－４０℃～＋１５０℃の測定レンジでＡ／Ｄコンバータ７０１に入力する。一方、後者の系（第２の系）は、センサ部２１１より出力された電圧Ｖｂ_ａｖｇを、２０℃～５０℃の測定レンジでＡ／Ｄコンバータ７０１に出力する。 The former system (first system) inputs the voltage Vb_avg output from the sensor unit 211 to the A / D converter 701 in the measurement range of −40 ° C. to + 150 ° C. On the other hand, the latter system (second system) outputs the voltage Vb_avg output from the sensor unit 211 to the A / D converter 701 in a measurement range of 20 ° C. to 50 ° C.
　第１の系を用いて出力するか、第２の系を用いて出力するかは（つまり、測定レンジは）、データ読み取り装置１０１の選択スイッチ（不図示）で、測定レンジを選択することで指示され、制御回路７０２からの信号に基づいてアナログスイッチ７１２、７２２を切り替えることにより制御される。より高精度、即ち０．０１℃の温度分解能で、０．０５℃以内の測定精度の体温測定を行う場合には、第２の系が選択されることとなる。 Whether to output using the first system or the second system (that is, the measurement range) is determined by selecting the measurement range with the selection switch (not shown) of the data reader 101. It is controlled by switching the analog switches 712 and 722 based on a signal from the control circuit 702. When performing body temperature measurement with higher accuracy, that is, with a temperature resolution of 0.01 ° C. and measurement accuracy within 0.05 ° C., the second system is selected.
　Ａ／Ｄコンバータ７０１に入力された電圧Ｖｂ_ａｖｇは、Ａ／Ｄコンバータ７０１においてＡ／Ｄ変換され、デジタルデータとして制御回路７０２に入力される。 The voltage Vb_avg input to the A / D converter 701 is A / D converted by the A / D converter 701 and input to the control circuit 702 as digital data.
　制御回路７０２に入力されたデジタルデータは、無線通信部２０２に送信される。 Digital data input to the control circuit 702 is transmitted to the wireless communication unit 202.
　なお、センサ部２１１より電圧Ｖｂ_ａｖｇが複数回出力される場合にあっては、それぞれのデジタルデータをメモリ７０３に一時的に格納し、制御回路７０２において、メモリ７０３に格納された全てのデジタルデータの平均値を算出した後に、無線通信部２０２に送信するようにしてもよい。 When the voltage Vb_avg is output from the sensor unit 211 a plurality of times, each digital data is temporarily stored in the memory 703, and all the digital data stored in the memory 703 is stored in the control circuit 702. After calculating the average value, it may be transmitted to the wireless communication unit 202.
　＜８．過昇防止部の回路構成＞
　次に、過昇防止部２０１の回路構成について説明する。図８は、過昇防止部２０１の回路構成を示す図である。 <8. Circuit configuration of excessive rise prevention unit>
Next, the circuit configuration of the excessive rise prevention unit 201 will be described. FIG. 8 is a diagram illustrating a circuit configuration of the excessive rise prevention unit 201.
　図８において、８０１及び８０２はスイッチであり、コントロール部２０５より温度上限信号が入力された場合に、処理部１１５内への電源の供給を停止するとともに、データ読み取り装置１０１へのデータの送信を停止する。 In FIG. 8, reference numerals 801 and 802 denote switches. When a temperature upper limit signal is input from the control unit 205, supply of power to the processing unit 115 is stopped and transmission of data to the data reading apparatus 101 is performed. Stop.
　なお、温度上限信号はコントロール部２０５において算出されたデジタルデータの値が、所定の値以下であった場合に、体温測定の精度に影響を与える状態になったと判断し、出力されるものとする。上述したように、ＲＦ－ＩＤリーダ／ライタより過剰な電源が供給された場合、体温タグ１１３全体が発熱し、高精度な体温測定を行うことができなくなるからである。 The temperature upper limit signal is output when the digital data value calculated by the control unit 205 is less than or equal to a predetermined value, determining that the temperature measurement accuracy has been affected. . As described above, when excessive power is supplied from the RF-ID reader / writer, the whole body temperature tag 113 generates heat, and it becomes impossible to perform highly accurate body temperature measurement.
　このように、処理部１１５では、体温測定の精度に影響を与える状態となった場合に、処理を停止する。これにより、データ読み取り装置１０１において、誤った測定結果が表示されることを回避することが可能となる。 In this way, the processing unit 115 stops the processing when it enters a state that affects the accuracy of body temperature measurement. As a result, it is possible to avoid displaying an erroneous measurement result in the data reading apparatus 101.
　＜９．体温計１１０の製造工程＞
　次に体温計１１０の製造工程について説明する。図９は、体温計１１０の製造工程を示した図である。 <9. Manufacturing process of thermometer 110>
Next, the manufacturing process of the thermometer 110 will be described. FIG. 9 is a diagram illustrating a manufacturing process of the thermometer 110.
　図９に示すように、体温計１１０は、体温タグ製造工程と、校正工程と、後処理工程とに大別することができる。 As shown in FIG. 9, the thermometer 110 can be roughly divided into a body temperature tag manufacturing process, a calibration process, and a post-processing process.
　体温タグ製造工程では、アンテナ１１４が複数配列された帯状のベースシート９０１が、順次、半導体温度センサ実装装置９１１に搬送され、それぞれのアンテナ１１４に処理部１１５が電気的に接続される。これにより、体温タグ１１３が生成されることとなる。 In the body temperature tag manufacturing process, a band-shaped base sheet 901 in which a plurality of antennas 114 are arranged is sequentially conveyed to the semiconductor temperature sensor mounting device 911, and the processing unit 115 is electrically connected to each antenna 114. Thereby, the body temperature tag 113 will be produced | generated.
　校正工程では、体温タグ１１３が複数配列されたベースシート９０１が、順次、恒温槽９１２に搬送される。恒温槽９１２は、予め設定された温度、例えば３７℃に管理された槽である。 In the calibration process, the base sheets 901 on which a plurality of body temperature tags 113 are arranged are sequentially conveyed to the thermostat 912. The constant temperature bath 912 is a bath managed at a preset temperature, for example, 37 ° C.
　恒温槽９１２の内部には、ＲＦ－ＩＤリーダ／ライタ９１３が配置されており、各体温タグ１１３がＲＦ－ＩＤリーダ／ライタ９１３上を通過する際に所定の周波数、たとえば１３．５６ＭＨｚの電磁波により、各体温タグ１１３と通信を行う。 An RF-ID reader / writer 913 is disposed inside the thermostat 912, and each body temperature tag 113 is transmitted by an electromagnetic wave having a predetermined frequency, for example, 13.56 MHz when passing over the RF-ID reader / writer 913. Communicate with each body temperature tag 113.
　具体的には、各体温タグ１１３におけるバンドギャップ電圧データを受信し、該受信したバンドギャップ電圧データを恒温槽９１２の温度とともに、校正データとして各体温タグ１１３の記憶部２０３に書き込む。なお、恒温槽９１２において、ベースシート９０１は充分に低速で搬送され、恒温槽９１２内の温度が体温タグ１１３に伝達され、温度が平衡状態になったうえで、ＲＦ－ＩＤリーダ／ライタ９１３上を通過するように設計されているものとする。 Specifically, the band gap voltage data in each body temperature tag 113 is received, and the received band gap voltage data is written into the storage unit 203 of each body temperature tag 113 as calibration data together with the temperature of the thermostat 912. In the thermostat 912, the base sheet 901 is conveyed at a sufficiently low speed, the temperature in the thermostat 912 is transmitted to the body temperature tag 113, and the temperature reaches an equilibrium state, and then the RF-ID reader / writer 913 is It is designed to pass through.
　なお、図９の例では、恒温槽９１２は１つのみ配置されているが、恒温槽の数は１つに限られない。異なる温度、例えば３２℃と４２℃、もしくは３２℃、３６℃及び４２℃に設定された複数の恒温槽を用意し、それぞれの温度における校正データを、各体温タグ１１３に書き込むように構成してもよい。 In addition, in the example of FIG. 9, only one thermostat 912 is disposed, but the number of thermostats is not limited to one. A plurality of thermostats set at different temperatures, for example, 32 ° C. and 42 ° C., or 32 ° C., 36 ° C. and 42 ° C. are prepared, and calibration data at each temperature is written to each temperature tag 113. Also good.
　さらに、複数の恒温槽を用意した場合にあっては、そのうちの１つの恒温槽を体温タグ１１３の検定用として用いるようにしてもよい。具体的には、校正データが書き込まれた体温タグ１１３を予め設定された温度に管理された恒温槽（検定用の恒温槽）に搬送し、体温タグ１１３よりバンドギャップ電圧データ及び校正データを受信する。そして、該電圧データ及び校正データに基づいて算出された温度と恒温槽の温度とを対比し、予め定められた誤差範囲にあるか否かを判定する。 Furthermore, when a plurality of thermostats are prepared, one of the thermostats may be used for testing the body temperature tag 113. Specifically, the body temperature tag 113 in which the calibration data is written is transported to a thermostat (temperature test chamber) controlled at a preset temperature, and band gap voltage data and calibration data are received from the body temperature tag 113. To do. Then, the temperature calculated based on the voltage data and the calibration data is compared with the temperature of the thermostatic chamber, and it is determined whether or not it is within a predetermined error range.
　後処理工程では、校正データが書き込まれた体温タグ１１３が複数配列されたベースシート９０１が、順次、フィルム重ね合わせ装置９１４に搬送される。フィルム重ね合わせ装置９１４では、それぞれの体温タグ１１３の処理部１１５を保温材（例えば、厚さ１ｍｍ程度のアルミ材や発泡性ポリウレタン等）により覆うとともに、ベースシート９０１の表裏面にフィルム１１１、１１２（半透過性で、厚さは１００μｍ程度）を接着剤で貼り合わせる。また、裏面のフィルム１１２には、上述した粘着剤が塗布される。 In the post-processing step, the base sheet 901 in which a plurality of body temperature tags 113 in which calibration data is written is arranged is sequentially conveyed to the film superposing device 914. In the film superposing device 914, the processing unit 115 of each body temperature tag 113 is covered with a heat insulating material (for example, aluminum material having a thickness of about 1 mm, foaming polyurethane, or the like), and the films 111 and 112 are formed on the front and back surfaces of the base sheet 901. (Semi-permeable, thickness is about 100 μm) is bonded with an adhesive. Moreover, the adhesive mentioned above is applied to the film 112 on the back surface.
　フィルム重ね合わせ装置９１４においてフィルムが貼り合わされたベースシート９０１は、打ち抜き装置９１５に搬送され、体温タグ１１３ごとに切断されることで、体温計１１０が生成される。 The base sheet 901 on which the film is bonded in the film superimposing device 914 is conveyed to the punching device 915 and cut for each body temperature tag 113, so that the thermometer 110 is generated.
　＜１０．データ読み取り装置における体温データ算出処理＞
　次に、データ読み取り装置１０１の信号処理部３０４において体温データを算出するための処理について説明する。図１０は、信号処理部３０４において体温データを算出するための処理の内容を説明するための図である。 <10. Body temperature data calculation process in data reader>
Next, processing for calculating body temperature data in the signal processing unit 304 of the data reading apparatus 101 will be described. FIG. 10 is a diagram for explaining the content of processing for calculating body temperature data in the signal processing unit 304.
　信号処理部３０４では、基準となる半導体温度センサにおける、バンドギャップ電圧データと体温データとの対応関係を示すグラフ（関数）を、校正データに基づいて補正した後に、受信したバンドギャップ電圧データを代入することにより、体温データを導出する。 The signal processing unit 304 corrects the graph (function) indicating the correspondence between the band gap voltage data and the body temperature data in the reference semiconductor temperature sensor based on the calibration data, and then substitutes the received band gap voltage data. By doing so, body temperature data is derived.
　図１０の１０ａは、１種類の温度に対応する１種類の校正データを受信した場合における補正処理を示す図である。図１０の１０ａに示すように、１種類の温度に対応する１種類の校正データを受信した場合には、基準となる半導体温度センサにおける、バンドギャップ電圧データと体温データとの対応関係のオフセット値を調整する。具体的には、グラフ１００１を全体として矢印方向に平行移動させ、グラフ１００２を得る。 10a in FIG. 10 is a diagram showing a correction process when one type of calibration data corresponding to one type of temperature is received. As shown at 10a in FIG. 10, when one type of calibration data corresponding to one type of temperature is received, the offset value of the correspondence relationship between the band gap voltage data and the body temperature data in the semiconductor temperature sensor serving as a reference. Adjust. Specifically, the graph 1001 is translated in the direction of the arrow as a whole, and a graph 1002 is obtained.
　信号処理部３０４では、体温計１１０より受信した電圧データを、当該平行移動後のグラフ１００２に代入することで、体温データを導出する。 The signal processing unit 304 derives body temperature data by substituting the voltage data received from the thermometer 110 into the graph 1002 after the parallel movement.
　図１０の１０ｂは、２種類の温度に対応する２種類の校正データを受信した場合における補正処理を示す図である。図１０の１０ｂに示すように、２種類の温度に対応する２種類の校正データを受信した場合には、当該２点を通る直線１０１１を算出し、これを半導体温度センサにおけるバンドギャップ電圧データと体温データとの対応関係を示すグラフとする。 10b in FIG. 10 is a diagram showing a correction process when two types of calibration data corresponding to two types of temperatures are received. As shown in 10b of FIG. 10, when two types of calibration data corresponding to two types of temperatures are received, a straight line 1011 passing through the two points is calculated, and this is calculated as band gap voltage data in the semiconductor temperature sensor. It is a graph showing the correspondence with body temperature data.
　信号処理部３０４では、体温計１１０より受信したバンドギャップ電圧データを、当該算出された直線に代入することで、体温データを導出する。 The signal processing unit 304 derives body temperature data by substituting the band gap voltage data received from the thermometer 110 into the calculated straight line.
　図１０の１０ｃは、３種類以上の温度に対応する３種類以上の校正データを受信した場合における補正処理を示す図である。図１０の１０ｃに示すように、３種類以上の温度に対応する３種類以上の校正データを受信した場合には、当該３点以上の点に基づいて、最小２乗法により回帰直線１０２１を算出し、これを半導体温度センサにおけるバンドギャップ電圧データと体温データとの対応関係を示すグラフとする。 10c of FIG. 10 is a diagram showing a correction process when three or more types of calibration data corresponding to three or more types of temperatures are received. As shown in 10c of FIG. 10, when three or more kinds of calibration data corresponding to three or more kinds of temperatures are received, a regression line 1021 is calculated by the least square method based on the three or more points. This is a graph showing the correspondence between the band gap voltage data and the body temperature data in the semiconductor temperature sensor.
　信号処理部３０４では、体温計１１０より受信したバンドギャップ電圧データを、当該算出された回帰直線１０２１に代入することで、体温データを算出する。 The signal processing unit 304 calculates the body temperature data by substituting the band gap voltage data received from the thermometer 110 into the calculated regression line 1021.
　以上の説明から明らかなように、本実施形態における体温計では、アンテナを備える貼り付け型の体温計として、半導体温度センサを適用する構成とした。 As is clear from the above description, the thermometer in the present embodiment is configured to apply a semiconductor temperature sensor as an affixed thermometer equipped with an antenna.
　また、半導体温度センサの適用にあたり、
・外気温度の影響を除去するために、処理部を保温材で覆う構成とした。
・半導体温度センサの個体差の影響を排除するため、センサ部において、複数の半導体温度センサを並列に接続する構成とした。
・測定誤差を排除するため、１回の体温測定に際して、センサ部に対して複数回電流を流し、その平均値を出力する構成とした。
・体温タグの個体差の影響を排除するため、体温タグ内の記憶部に体温タグごとに校正データを記憶しておき、データ読み取り装置により電圧データを送信する際に、合わせて校正データを送信する構成とした。
・体温タグの発熱により測定に誤差が生じる恐れがある場合には、過昇防止部が体温測定を中止し、誤った測定結果がデータ読み取り装置に表示されることがないように構成した。 In application of semiconductor temperature sensor,
-In order to remove the influence of the outside air temperature, the treatment part is covered with a heat insulating material.
In order to eliminate the influence of individual differences of the semiconductor temperature sensors, a plurality of semiconductor temperature sensors are connected in parallel in the sensor unit.
-In order to eliminate measurement errors, a current was passed through the sensor section a plurality of times and an average value was output during one body temperature measurement.
・ In order to eliminate the influence of individual differences in body temperature tags, calibration data is stored for each body temperature tag in the storage section of the body temperature tag, and when the voltage data is transmitted by the data reader, the calibration data is also transmitted. It was set as the structure to do.
・ If there is a risk of measurement errors due to the heat generated by the body temperature tag, the overheating prevention unit stops the body temperature measurement and the erroneous measurement result is not displayed on the data reader.
　この結果、特に、人体の体温測定の一般的な測定レンジである３２～４２℃において０．０１℃の温度分解能を得ることで、測定精度が０．０５℃以内の高精度な体温測定を実現することが可能となった。 As a result, a high-accuracy body temperature measurement with a measurement accuracy of 0.05 ° C or less is achieved by obtaining a temperature resolution of 0.01 ° C in 32 to 42 ° C, which is the general measurement range of human body temperature. It became possible to do.
　［第２の実施形態］
　上記第１の実施形態では、アンテナ内に処理部を配する構成としたが、本発明はこれに限られず、アンテナから延設された導線を介して、アンテナに処理部を接続するように構成してもよい。以下、本実施形態における体温測定システムについて説明する。なお、簡略化のため、説明は、主に上記第１の実施形態との相違点について行うものとする。 [Second Embodiment]
In the first embodiment, the processing unit is arranged in the antenna. However, the present invention is not limited to this, and the processing unit is connected to the antenna via a conductor extending from the antenna. May be. Hereinafter, the body temperature measurement system in the present embodiment will be described. For the sake of simplification, the description will mainly be made on differences from the first embodiment.
　＜１．体温測定システムの外観構成＞
　図１１は、本発明の第２の実施形態における、半導体温度センサを含む無線タグ（ＲＦ－ＩＤ）が配された体温計（アンテナを備える貼り付け型の体温計）１１１０と、測定者によって携帯可能なデータ読み取り装置（携帯装置）１１０１とを備える体温測定システム１１００の外観構成を示す図である。 <1. External configuration of body temperature measurement system>
FIG. 11 shows a thermometer (attached thermometer equipped with an antenna) 1110 provided with a wireless tag (RF-ID) including a semiconductor temperature sensor according to the second embodiment of the present invention, and portable by a measurer. It is a figure which shows the external appearance structure of the body temperature measurement system 1100 provided with the data reader (portable apparatus) 1101.
　図１１に示すように、体温計１１１０は、機能的に３つの部位に区分することができる。第１の部位はアンテナ１１１４を備えるアンテナ部１１２０であり、第２の部位はアンテナ１１１４と処理部１１１６とを電気的に接続する導線１１１５が配された延設部１１３０であり、第３の部位は、処理部１１１６を備える体温測定部１１４０である。 As shown in FIG. 11, the thermometer 1110 can be functionally divided into three parts. The first part is an antenna part 1120 including an antenna 1114, and the second part is an extension part 1130 provided with a conducting wire 1115 that electrically connects the antenna 1114 and the processing part 1116, and a third part. Is a body temperature measurement unit 1140 including a processing unit 1116.
　アンテナ１１１４は、上記第１の実施形態において説明したアンテナ１１４と同一の構成、機能を有している。処理部１１１６は、第１の実施形態における処理部１１５と同一の構成、機能を有している。体温測定部１１４０は、第１の実施形態における処理部１１５と同一の構成、機能を有している。データ読み取り装置（携帯装置）１１０１もまた、第１の実施形態において説明したデータ読み取り装置１０１と同一の構成、機能を有している。 The antenna 1114 has the same configuration and function as the antenna 114 described in the first embodiment. The processing unit 1116 has the same configuration and function as the processing unit 115 in the first embodiment. The body temperature measurement unit 1140 has the same configuration and function as the processing unit 115 in the first embodiment. The data reading device (portable device) 1101 also has the same configuration and function as the data reading device 101 described in the first embodiment.
　アンテナ部１１２０を構成するアンテナ１１１４と、延設部１１３０を構成する導線１１１５と、体温測定部１１４０を構成する処理部１１１６とは、体温タグとしてベースシート上に一体的に構成されており、表面のフィルム１１１１と裏面のフィルム１１１２（半透過性で、厚さは１００μｍ程度）との間に、固定されている。なお、以下では、ベースシート上に一体的に構成されたアンテナ１１１４と導線１１１５と処理部１１１６とを総称して体温タグ１１１３と称することとする。 The antenna 1114 constituting the antenna portion 1120, the conducting wire 1115 constituting the extending portion 1130, and the processing portion 1116 constituting the body temperature measuring portion 1140 are integrally formed on the base sheet as a body temperature tag, Between the film 1111 and the back film 1112 (semi-permeable, thickness is about 100 μm). Hereinafter, the antenna 1114, the conductive wire 1115, and the processing unit 1116 that are integrally formed on the base sheet are collectively referred to as a body temperature tag 1113.
　表面のフィルム１１１１及び裏面のフィルム１１１２のうちアンテナ部１１２０と延設部１１３０を構成するフィルム１１１２ｂは、ポリエーテルウレタンやポリエステルウレタンなどのウレタン系ポリマー、ポリエーテルポリアミドブロックポリマーなどのアミド系ポリマー、ポリアクリレートなどのアクリル系ポリマー、ポリエチレンやポリプロピレン、エチレン／酢酸ビニル共重合体などのポリオレフィン系ポリマー、ポリエーテルポリエステルなどのポリエステル系ポリマーなどの材料から得ることができる。 Of the film 1111 on the front surface and the film 1112 on the back surface, the film 1112b constituting the antenna portion 1120 and the extending portion 1130 is a urethane polymer such as polyether urethane or polyester urethane, an amide polymer such as polyether polyamide block polymer, poly It can be obtained from materials such as acrylic polymers such as acrylate, polyolefin polymers such as polyethylene, polypropylene, and ethylene / vinyl acetate copolymers, and polyester polymers such as polyether polyester.
　また、裏面のフィルム１１１２のうち、体温測定部１１４０を構成するフィルム１１１２ａは皮膚面への貼り付け時にムレや白化などを生じないようにするために、水蒸気透過性を有する材質から選択することが好ましく、例えばウレタン系やアミド系のフィルムを用いることが好適である。なお、表面のフィルム１１１１、裏面のフィルム１１１２ｂは上記材料のうちの何れか一種からなるものであってもよいし、任意の材料からなるフィルムを複数枚積層した積層フィルムであってもよい。 In addition, among the films 1112 on the back surface, the film 1112a constituting the body temperature measuring unit 1140 can be selected from materials having water vapor permeability so as not to cause stuffiness or whitening when being applied to the skin surface. Preferably, for example, a urethane film or an amide film is used. The front film 1111 and the back film 1112b may be made of any one of the above materials, or may be a laminated film in which a plurality of films made of any material are laminated.
　裏面のフィルム１１１２ａは皮膚面に貼付した際に、違和感を生じないようにするために、その厚みを１０～１００μｍ、好ましくは２０～４０μｍ程度にすることがよい。また、皮膚面に貼り付けした際の皮膚追従性を良好にするためには、引張強度を１００～９００ｋｇ／ｃｍ２、１００％モジュラスを１０～１００ｋｇ／ｃｍ２程度に調整することが好ましい。この範囲に調整した裏面のフィルム１１１２ａを用いると、動きの大きい皮膚面に貼付した際に効果的である。また、上記裏面のフィルム１１１２ａとして、無孔フィルムだけでなく、水蒸気透過性であって非透水性である多孔性フィルムを用いることも、貼付中のムレの防止の点から効果的である。このようなフィルムの場合には、材質には特に制限はされず、公知の多孔化技術を施すことによって簡単に得ることができる。無孔性フィルムの場合にはフィルム厚が大きくなるほど水蒸気透過性は低下する傾向が顕著に現れるが、多孔性フィルムの場合には厚みに比例して水蒸気透過性の低下が顕著に現れないので有用である。 The thickness of the film 1112a on the back surface should be about 10 to 100 μm, preferably about 20 to 40 μm, so as not to give a sense of incongruity when it is applied to the skin surface. Further, in order to improve the skin followability when applied to the skin surface, it is preferable to adjust the tensile strength to 100 to 900 kg / cm 2 and the 100% modulus to about 10 to 100 kg / cm 2 . Use of the back film 1112a adjusted to this range is effective when affixed to a skin surface with large movement. Moreover, it is effective from the point of prevention of the stuffiness during sticking to use not only a non-porous film but the water-permeable porous film which is water-impermeable as the film 1112a of the said back surface. In the case of such a film, the material is not particularly limited, and can be easily obtained by applying a known porous technique. In the case of a non-porous film, the tendency for water vapor permeability to decrease as the film thickness increases appears significantly, but in the case of a porous film, the decrease in water vapor permeability does not appear in proportion to the thickness, which is useful. It is.
　裏面のフィルム１１１２ａには、粘着剤が塗布されており、体温計１１１０を、被検者の体表面の適所の測定部位に直接、貼り付けることができるように構成されている。粘着剤は、通常の医療用グレードとして用いられるものであればいずれを用いてもよく、例えばアクリル系粘着剤、ポリウレタン系粘着剤、天然ゴム又は合成ゴム系粘着剤、医用高分子を主成分とする溶剤系、水系、ホットメルト系、ドライブレンド系の粘着剤があげられる。ただし放射線滅菌特に強度のガンマー線照射滅菌が必要な場合にはアクリル系粘着剤やポリウレタン系粘着剤の使用は避けた方が望ましい。これらは放射線照射による粘着力の低下を招くおそれがあるからである。 The adhesive film is applied to the film 1112a on the back surface, and the thermometer 1110 can be directly attached to an appropriate measurement site on the body surface of the subject. Any adhesive can be used as long as it is used as a normal medical grade. For example, an acrylic adhesive, a polyurethane adhesive, a natural rubber or a synthetic rubber adhesive, and a medical polymer as a main component. Solvent-based, water-based, hot-melt-based, and dry blend-based pressure-sensitive adhesives. However, it is desirable to avoid the use of acrylic adhesives and polyurethane adhesives when radiation sterilization, especially intense gamma irradiation sterilization, is required. This is because there is a risk of lowering the adhesive strength due to irradiation.
　また、表面のフィルム１１１１と裏面のフィルム１１１２ａは、いずれも柔軟性があり、体温計１１１０を被検者の測定部位に貼り付けた際に、測定部位の形状に沿って変形できるようになっている。このように、処理部１１１６が測定部位に密着して固定されることにより、体温計１１１０は、被検者の体温を正確に検出することができる。 Moreover, the film 1111 on the front surface and the film 1112a on the back surface are both flexible, and can be deformed along the shape of the measurement site when the thermometer 1110 is attached to the measurement site of the subject. . In this way, the thermometer 1110 can accurately detect the body temperature of the subject by fixing the processing unit 1116 in close contact with the measurement site.
　なお、体温タグ１１１３を構成するアンテナ１１１４と導線１１１５と処理部１１１６のうち、処理部１１１６は、保温材（例えば、厚さ１ｍｍ程度のアルミ材）により覆われているものとする。これにより、外気温度（環境温）の影響を除去することができる。 Of the antenna 1114, the conductive wire 1115, and the processing unit 1116 constituting the body temperature tag 1113, the processing unit 1116 is covered with a heat insulating material (for example, an aluminum material having a thickness of about 1 mm). Thereby, the influence of outside temperature (environment temperature) can be removed.
　一方、データ読み取り装置１１０１は、ＲＦ－ＩＤリーダ／ライタを備えており、体温タグ１１３に近づけた際に、例えば体温データ読み取り開始スイッチ（不図示）を押すことで、所定の周波数、例えば１３．５６ＭＨｚの電磁波が発生し、体温タグ１１１３との間で磁気結合し、体温タグ１１１３の処理部１１５に含まれる電源回路への電力供給と、体温タグ１１１３からのデータの受信とを行う。 On the other hand, the data reading device 1101 includes an RF-ID reader / writer. When the data reading device 1101 approaches the body temperature tag 113, for example, by pressing a body temperature data reading start switch (not shown), a predetermined frequency, for example, 13.2. A 56 MHz electromagnetic wave is generated and magnetically coupled with the body temperature tag 1113, and power is supplied to the power supply circuit included in the processing unit 115 of the body temperature tag 1113 and data is received from the body temperature tag 1113.
　＜２．体温測定システムにおける体温測定方法＞
　次に、体温測定システム１１００における体温測定方法について説明する。図１２は、体温計１１１０の体温測定部１１４０を被検者１１５０の体温測定部位の適所の１つである腋下に装着した様子を示している。本実施形態における体温計１１１０では、体温測定部１１４０とアンテナ部１１２０とが、延設部１１３０を介して接続された構成となっているため、体温測定部１１４０が被検者１１５０の腋下に装着された状態においても、アンテナ部１１２０を、被検者１１５０の腋下から離れた位置に配置させることができる。 <2. Body temperature measurement method in body temperature measurement system>
Next, a body temperature measurement method in the body temperature measurement system 1100 will be described. FIG. 12 shows a state in which the body temperature measurement unit 1140 of the thermometer 1110 is attached to the armpit, which is one of the appropriate positions of the body temperature measurement site of the subject 1150. In the thermometer 1110 according to the present embodiment, the body temperature measuring unit 1140 and the antenna unit 1120 are connected via the extending portion 1130, so that the body temperature measuring unit 1140 is attached to the armpit of the subject 1150. Even in this state, the antenna unit 1120 can be disposed at a position away from the armpit of the subject 1150.
　このため、測定者１１６０がデータ読み取り装置１１０１を近づけた際に、例えば体温データ読取り開始スイッチ（不図示）を押すことで、所定の周波数、例えば１３．５６ＭＨｚの電磁波が発生させて体温タグ１１１３との間で簡単かつ確実に磁気結合させることができる。つまり、アンテナを備える貼り付け型の体温計の場合に生じうる読み取りエラーの問題を未然に防ぐことが可能となる。 For this reason, when the measurer 1160 brings the data reading device 1101 close, for example, by pressing a body temperature data reading start switch (not shown), an electromagnetic wave having a predetermined frequency, for example, 13.56 MHz is generated, and the body temperature tag 1113 Can be magnetically coupled easily and reliably. That is, it is possible to prevent the problem of reading error that may occur in the case of a pasted thermometer equipped with an antenna.
　＜３．体温計１１１０の製造工程＞
　次に体温計１１１０の製造工程について説明する。図１３は、体温計１１１０の製造工程を示した図である。なお、体温計１１１０の製造工程は、体温タグ１１１３の形状が異なること以外は、図９と同じであるため、ここでは説明を省略する。 <3. Manufacturing process of thermometer 1110>
Next, the manufacturing process of the thermometer 1110 will be described. FIG. 13 is a diagram showing a manufacturing process of the thermometer 1110. The manufacturing process of the thermometer 1110 is the same as that shown in FIG. 9 except that the shape of the body temperature tag 1113 is different, and thus the description thereof is omitted here.
　以上の説明から明らかなように、本実施形態によれば、特に人体の体温測定の一般的な測定レンジである３２～４２℃において０．０１℃の温度分解能を得ることで、測定精度が０．０５℃以内の高精度な体温測定を実現することが可能となるとともに、アンテナを備える貼り付け型の体温計から、確実にデータを読み取ることが可能となった。 As is apparent from the above description, according to the present embodiment, the measurement accuracy is 0 by obtaining a temperature resolution of 0.01 ° C. in 32 to 42 ° C., which is a general measurement range of human body temperature. It became possible to achieve highly accurate body temperature measurement within 0.05 ° C, and to reliably read data from an attached thermometer equipped with an antenna.
　［第３の実施形態］
　上記第２の実施形態では、アンテナ部１１２０と延設部１１３０と体温測定部１１４０とを同一平面上に配する形状としたが、本発明はこれに限定されず、例えば、アンテナ部１１２０と延設部１１３０とを、体温測定部１１４０に対して垂直に配する形状としてもよい。 [Third Embodiment]
In the second embodiment, the antenna unit 1120, the extending unit 1130, and the body temperature measuring unit 1140 are arranged on the same plane. However, the present invention is not limited to this. It is good also as a shape which distributes the installation part 1130 perpendicularly | vertically with respect to the body temperature measurement part 1140.
　また、上記第１の実施形態では、アンテナ部１１２０と延設部１１３０と体温測定部１１４０とを左右対称に配置する形状としたが、本発明はこれに限定されず、例えば、アンテナ部１１２０と延設部１１３０とを、体温測定部１１４０に対して非対称に配置する形状としてもよい。 Moreover, in the said 1st Embodiment, although it was set as the shape which arrange | positions the antenna part 1120, the extension part 1130, and the body temperature measurement part 1140 symmetrically, this invention is not limited to this, For example, the antenna part 1120 and The extending portion 1130 may have a shape that is asymmetrically arranged with respect to the body temperature measuring portion 1140.
　また、いずれの場合も、体温測定部１１４０は、貼り付けられる被検者の測定部位に適した形状・大きさであることが望ましい。更に、体温測定部１１４０が被検者の測定部位に貼り付けられた状態で、アンテナ部１１２０が、データ読み取り装置１１０１との間で確実に磁気結合できる位置に配置されるように、延設部１１３０及びアンテナ部１１２０の形状・大きさが決定されることが望ましい。 In any case, it is desirable that the body temperature measurement unit 1140 has a shape and size suitable for the measurement site of the subject to be pasted. Further, the extension unit is arranged so that the antenna unit 1120 can be securely magnetically coupled to the data reader 1101 in a state where the body temperature measurement unit 1140 is attached to the measurement site of the subject. It is desirable that the shapes and sizes of the 1130 and the antenna unit 1120 be determined.
　［第４の実施形態］
　上記第１の実施形態では、コントロール部２０５において算出されたデジタルデータの値が所定の値以下であった場合に、体温測定の精度に影響を与える状態になったと判断し、過昇防止部２０１のスイッチをＯＦＦすることで、処理部１１５による処理を停止する構成としたが、本発明はこれに限定されない。 [Fourth Embodiment]
In the first embodiment, when the value of the digital data calculated by the control unit 205 is less than or equal to a predetermined value, it is determined that the temperature measurement accuracy has been affected, and the overheating prevention unit 201 is determined. Although the processing by the processing unit 115 is stopped by turning off the switch, the present invention is not limited to this.
　例えば、アンテナ１１４を介して供給された電源電圧が所定の電圧値以上になった場合には、処理部１１５が、測定精度に影響を与える状態になったと判断し、強制的にスイッチをＯＦＦするように構成してもよい。 For example, when the power supply voltage supplied via the antenna 114 exceeds a predetermined voltage value, the processing unit 115 determines that the measurement accuracy is affected and forcibly turns off the switch. You may comprise as follows.
　また、上記第１の実施形態では、センサ部２１１において並列接続した半導体温度センサの数について具体的に言及しなかったが、例えば、８個程度の半導体温度センサを並列接続することが望ましい。並列接続する半導体温度センサの数が少ないと、個体差の影響が大きくなり測定精度が低下する一方で、半導体温度センサの数が多すぎると、発熱による誤差の影響が大きくなるからである。 In the first embodiment, the number of semiconductor temperature sensors connected in parallel in the sensor unit 211 is not specifically mentioned. For example, it is desirable to connect approximately eight semiconductor temperature sensors in parallel. This is because if the number of semiconductor temperature sensors connected in parallel is small, the influence of individual differences increases and the measurement accuracy decreases, while if the number of semiconductor temperature sensors is too large, the influence of errors due to heat generation increases.
　また、上記第１の実施形態では、体温計１１０からデータ読み取り装置１０１に対して、電圧データと校正データと識別情報とを送信する構成としたが、本発明はこれに限定されない。例えば、測定レンジを切り替えた場合には、切り替えた後の測定レンジに関する情報を送信するように構成してもよい。この場合、データ読み取り装置１０１では、受信した測定レンジに関する情報も考慮して、体温データを算出することとなる。 In the first embodiment, the thermometer 110 transmits voltage data, calibration data, and identification information to the data reading device 101. However, the present invention is not limited to this. For example, when the measurement range is switched, information regarding the measurement range after switching may be transmitted. In this case, the data reading apparatus 101 calculates the body temperature data in consideration of the received information regarding the measurement range.
　また、測定レンジの切り替えを、データ読み取り装置１０１からの指示に基づいて行うように構成してもよい。この場合、データ読み取り装置１０１では、指示した測定レンジを考慮して、体温データを算出することとなる。 Further, the measurement range may be switched based on an instruction from the data reading device 101. In this case, the data reading apparatus 101 calculates body temperature data in consideration of the instructed measurement range.
　本発明は上記実施の形態に制限されるものではなく、本発明の精神及び範囲から離脱することなく、様々な変更及び変形が可能である。従って、本発明の範囲を公にするために、以下の請求項を添付する。 The present invention is not limited to the above embodiment, and various changes and modifications can be made without departing from the spirit and scope of the present invention. Therefore, in order to make the scope of the present invention public, the following claims are attached.
　本願は、２００９年２月２５日提出の日本国特許出願特願２００９－０４３０７１を基礎として優先権を主張するものであり、その記載内容の全てを、ここに援用する。 This application claims priority on the basis of Japanese Patent Application No. 2009-043071 filed on Feb. 25, 2009, the entire contents of which are incorporated herein by reference.

Claims (3)

  1. 　アンテナ部と処理部とを備える体温タグと、
    　被検者の体表面に貼り付け可能に構成される裏面フィルムと、
    　前記処理部を覆う保温材と、
    　前記保温材で覆われた前記体温タグを、前記裏面フィルムとの間で挟む表面フィルムと、を備える体温計であって、
    　前記処理部は、
    　　前記アンテナ部に接続され、該アンテナ部における誘導起電力の発生に伴って起動される電源回路と、
    　　Ｐ型とＮ型の２種類の半導体が結合され、該２種類の半導体の結合部に電流を流した場合のバンドギャップ電圧を検出する半導体温度センサが、２個以上並列に接続された検出手段と、
    　　前記検出手段により検出されるバンドギャップ電圧を校正するための校正データを記憶する記憶手段と、を備え、
    　　前記電源回路の起動に伴って、前記検出手段により検出されたバンドギャップ電圧を、前記校正データとともに、前記アンテナ部を介して送信することを特徴とする体温計。     A body temperature tag including an antenna unit and a processing unit;
    A back film configured to be capable of being attached to the body surface of the subject; and
    A heat insulating material covering the processing section;
    A thermometer comprising a surface film sandwiched between the body temperature tag covered with the heat insulating material and the back film,
    The processor is
    A power supply circuit connected to the antenna unit and activated in response to generation of an induced electromotive force in the antenna unit;
    Detection means in which two or more semiconductor temperature sensors for detecting a band gap voltage when two types of semiconductors of P-type and N-type are coupled and current is passed through the coupling portion of the two types of semiconductors are connected in parallel When,
    Storage means for storing calibration data for calibrating the band gap voltage detected by the detection means,
    A thermometer that transmits the band gap voltage detected by the detection means together with the calibration data via the antenna unit when the power supply circuit is activated.
  2. 　前記処理部は、前記アンテナ部から延設された導線を介して、該アンテナ部に接続されていることを特徴とする請求項１に記載の体温計。 The thermometer according to claim 1, wherein the processing unit is connected to the antenna unit via a conductive wire extending from the antenna unit.
  3. 　請求項１または２のいずれかに記載の体温計と、該体温計と磁気結合する携帯装置とを備える体温測定システムであって、
    　前記携帯装置は、
    　前記アンテナ部を介して送信された校正データに基づいて、バンドギャップ電圧と温度との対応関係を示す関数を算出する算出手段と、
    　前記算出手段により算出された関数に、前記アンテナ部を介して送信されたバンドギャップ電圧を代入することにより、前記被検者の体温データを導出する導出手段と
    　前記導出された体温データを格納する格納手段と、
    　を備えることを特徴とする体温測定システム。     A body temperature measurement system comprising the thermometer according to claim 1 and a portable device magnetically coupled to the thermometer,
    The portable device is:
    Based on calibration data transmitted through the antenna unit, a calculation unit that calculates a function indicating a correspondence relationship between the band gap voltage and the temperature;
    By substituting the band gap voltage transmitted via the antenna unit into the function calculated by the calculating means, the derivation means for deriving the body temperature data of the subject and the derived body temperature data are stored. Storage means;
    A body temperature measurement system comprising:
PCT/JP2010/000968 2009-02-25 2010-02-17 Medical thermometer and body temperature measurement system WO2010098040A1 (en)

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CN105046314A (en) * 2015-07-22 2015-11-11 杭州浙港智能科技有限公司 NFC (near field communication) radio-frequency protocol based body temperature detection tag applied to human body surface and temperature measurement method for body temperature detection tag

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