CN1862241B - 耳式医用温度计 - Google Patents

耳式医用温度计 Download PDF

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CN1862241B
CN1862241B CN2006100678509A CN200610067850A CN1862241B CN 1862241 B CN1862241 B CN 1862241B CN 2006100678509 A CN2006100678509 A CN 2006100678509A CN 200610067850 A CN200610067850 A CN 200610067850A CN 1862241 B CN1862241 B CN 1862241B
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thermistor
thermal insulation
ear
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temperature
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田中秀树
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Bio Echo Net Inc
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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
    • G01K1/16—Special arrangements for conducting heat from the object to the sensitive element
    • G01K1/18—Special arrangements for conducting heat from the object to the sensitive element for reducing thermal inertia
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
    • G01J5/00—Radiation pyrometry, e.g. infrared or optical thermometry
    • G01J5/02—Constructional details
    • G01J5/04—Casings
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
    • G01J5/00—Radiation pyrometry, e.g. infrared or optical thermometry
    • G01J5/02—Constructional details
    • G01J5/04—Casings
    • G01J5/046—Materials; Selection of thermal materials
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
    • G01J5/00—Radiation pyrometry, e.g. infrared or optical thermometry
    • G01J5/02—Constructional details
    • G01J5/04—Casings
    • G01J5/049—Casings for tympanic thermometers
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
    • G01J5/00—Radiation pyrometry, e.g. infrared or optical thermometry
    • G01J5/02—Constructional details
    • G01J5/06—Arrangements for eliminating effects of disturbing radiation; Arrangements for compensating changes in sensitivity
    • 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
    • G01K7/16—Measuring temperature based on the use of electric or magnetic elements directly sensitive to heat ; Power supply therefor, e.g. using thermoelectric elements using resistive elements

Abstract

一种耳式医用温度计20的探测器包括由树脂材料制成的第一热绝缘部件210和通过传统结合机构连接到所述第一热绝缘部件210的远端上由树脂材料制成的第二高热绝缘部件220。该第二高热绝缘部件220向前成锥形并且在远端上提供有凹表面221。保护盖230包围第一热绝缘部件210和第二高热绝缘部件220。热敏电阻细引线240嵌入第一热绝缘部件210和第二高热绝缘部件220内，使得线240的转动端部241桥接在第二高热绝缘部件220的凹表面221上，以在该凹表面221上暴露。超快反应热敏电阻250基本上安装在热敏电阻细引线240的转动端部241的中心上。

Description

耳式医用温度计
背景技术
本发明总体上涉及以非接触方式测量要被测量对象的温度的温度计，并且尤其涉及通过将探测器的端部插入耳中测量耳鼓温度的医用温度计。 
为了解释方便，下面将参照图8和9描述典型的传统耳式医用温度计。图8是传统耳式医用温度计的示意框图，说明了操作原理。图9是在典型的传统耳式医用温度计中探测器的端部的纵向截面图。如图8和9所示，典型的传统耳式医用温度计的探测器10使用温差电堆11。一般，温差电堆通过在温差电堆上的冷结点和热结点之间的温度差值产生电位差值(塞贝克效应)。为了使用温差电堆作为用于测量温度的探测器，有必要使得室温(环境温度)的补偿有效，与热电偶的情况一样。从而，传统耳式医用温度计已经使用热敏电阻12。 
当被测量物体的温度等于在温差电堆11上的冷结点中的温度时，来自探测器10的输出为零(零点)。另一方面，当被测量物体的温度高于在温差电堆11上的冷结点中的温度时，来自探测器10的输出变得很非线性。 
在探测器10测量身体温度的情况下，来自探测器10的输出是很微弱的水平。因此，有必要信号放大器13将来自探测器10的输出放大到信号处理能够应用的水平。而且，线性化电路14a有必要线性化非线性输出。另一方面，由于来自热敏电阻12的输出是非线性的，线性化电路14b必须线性化来自热敏电阻12的输出。 
在环境温度的稳定条件下，在热敏电阻12中的温度等于在温差电堆11上的冷结点中的温度。来自探测器10的输出的线性化信号指示在热敏电阻12中的温度和在被测量物体之间的差值。因此，在通过发射率修正装置15修正将探测器10的输出线性化的信号，并且通过加 算装置16使得室温的补偿或被修正信号和来自热敏电阻12的线性化信号的冷结点温度的补偿生效之后，通过温度转换装置17来修正环境温度，能够获得被测量物体的温度。这将在显示器18上显示。 
由于温差电堆具有个体差异的不稳定敏感性，即使存在某种温度差值，输出电压也是不稳定的。从而，有必要使用温差电堆单独使得探测器的敏感性调节(修正操作)生效。尽管用于温差电堆的红外吸收膜(在图9中与红外吸收膜和热结点整体形成的部分116)通过吸收红外线而增加温度，温差电堆的封装也辐射红外线到红外吸收膜上。在公共使用的方法中，认为该封装与温差电堆中的热沉(热吸收段)的温度相同。然而，当该封装由于外部因素经受温度的突然变化时，将会引起在封装的头部和温差电堆的热沉之间的温度差并且探测器将瞬变地输出不稳定的电压。 
因此，为了将均匀和平缓变化的温度施加到探测器10上，如图9所示，温差电堆110放置在由具有良好导热性(例如铝)的金属制成的支架111中，并且该支架111由盖114覆盖，以便由用作绝热材料的空气层112和树脂113封闭温差电堆110。在温差电堆110的前侧上提供有金属管115以便减小来自被测量物体(人体)的热辐射的影响。该金属管115镀有金以尽可能减少发射率并用作导波器。尽管半导体、热敏电阻等等通常用作补偿冷结点温度的传感器，但是考虑到低成本生产和高精度，已经通常使用热敏电阻。 
在温差电堆上的冷结点和热敏电阻之间的热耦合较弱的情况下，引起温度差值并且不能够进行精确的测量。热敏电阻(未示出)与温差电堆一起安装在封装中，以增强在电堆冷结点的热沉和热敏电阻之间的热耦合。即使任意热敏电阻均具有相同标准，B常数(阻抗温度特征，也即，用于指示从任意两点处的温度获得的阻抗值的变化的常数)也是不稳定的，因此难于在宽范围的环境温度内维持精度。例如，在34到42℃的范围内电子医用温度计中的热敏电阻测量体温的情况下，热敏电阻的精度会保持在8℃的范围内。然而，在温差电堆中的环境温度范围设定到处于5到40℃的范围内时，热敏电阻的精度必须 维持在35℃(40-5＝35)的范围内。 
在环境温度增加的过程中，在图9中示出的探测器10的结构引起在温差电堆110和探测器10的远端之间的温度差。由于在探测器10远端的温度高于温差电堆110的温度，该探测器10将产生正误差。在环境温度降低的过程中，探测器10引起在温差电堆110和探测器10的远端之间的温度差。由于在探测器10远端的温度低于温差电堆110的温度，该探测器10将产生负误差。为了减少这种误差，盖114封闭温差电堆110以降低温度变化的影响。然而，考虑到被测量物体，金属支架111的外尺寸受到限制。通过计算每个与温差电堆封装中的热敏电阻相关的时间内的变化率，抵抗由环境温度变化引起的误差的相反措施进行对探测器的输出的修正，由此减少误差。 
本发明的第一方面在于提供一种耳式医用温度计，其能够在短时间段内消除由环境温度变化引起的影响并且不产生由于环境温度变化引起的误差。 
热敏电阻用于补偿在红外医用温度计中使用的温差电堆上的冷结点的温度。尽管在有限范围的温度内易于调节热敏电阻的特征，正像在电子医用温度计中使用的热敏电阻的情况一样，但将会难于在热敏电阻用在医用温度计中的情况下在宽范围的温度内调节这些特征。因此，本发明的第二目的在于提供能够确保在宽范围的环境温度中的精度的耳式医用温度计。 
由于温差电堆具有很大的个体差别，温差电堆需要修正操作以保持精度。温差电堆的修正操作将在生产中带来高成本。因此，本发明的第三目的在于提供一种耳式医用温度计，与温差电堆系统相比，其能够不需要修正操作或者获得极大简化的修正。 
当传统耳式医用温度计在较低温度环境中测量体温时，温度计的探测器将冷却外耳道。尽管在第一次测量的精度将会相当好，但是在不花费太多时间的第二次或更多次之后的测量显示很可能降低。因此，考虑到环境温度的影响，在传统耳式医用温度计中的测量值将会不稳定。因此本发明的第四目的在于提供能够消除由环境温度的影响引起 的不稳定指示的耳式医用温度计。 
发明内容
根据本发明包含探测器的耳式医用温度计，该探测器包括：由树脂材料制成的第一热绝缘部件；连接到第一热绝缘部件的远端上由树脂材料制成的第二高热绝缘部件；包围第一热绝缘部件和第二高热绝缘部件的保护盖；嵌入第一热绝缘部件和第二高热绝缘部件内的热敏电阻细引线；以及基本安装在热敏电阻细引线的转动端部的中心上的超快反应热敏电阻。第二高热绝缘部件用作在测量体温的过程中探测器不吸收外耳道中的热量。 
优选地，第二高热绝缘部件向前成锥形并且在远端上提供有凹表面。热敏电阻细引线的转动端部桥接在第二高热绝缘部件的凹表面上以在该凹表面上暴露。第二高热绝缘部件的凹表面优选以镜面抛光方式加工。该凹表面具有反射红外线到热敏电阻上的作用。 
超快反应热敏电阻的热量时间常数优选是1秒或更低，以便缩短测量时间段。 
优选在温度测量线路中的电源线路的输出侧处提供具有多个终端的模拟开关，以便修正在温度测量线路中的误差。 
根据本发明，热敏电阻能够保持精度的温度范围仅仅是要被测量的体温范围并且不必在要被测量的环境温度的整个范围内维持热敏电阻的精度，这与使用温差电堆的传统耳式医用温度计的情况一样。因此，本发明的探测器不受环境温度变化(在短时间段内温度的变化)的影响，也即不存在所谓的探测器“烘烤”现象。在本发明的耳式医用温度计中的温度测量线路能够比使用温差电堆的传统温度测量线路进一步简化。在大量生产的基础上能够方便本发明耳式医用温度计的装配工作，并且由于探测器很小尺寸，因此不限制医用温度计主体的外部构造。 
附图说明
相信具有新颖性的本发明的特征和本发明的元件特征特别是在附加的权利要求中进行阐述。附图仅仅出于说明的目的并且未成比例绘 制。然而本发明自身在结构和操作方法两方面都可以参照后面与附图相结合的详细描述进行最佳地理解，附图为： 
图1是根据本发明的耳式医用温度计中的探测器的端部的纵向截面视图； 
图2是沿图1中线II-II截取的探测器端部的前正视图； 
图3是类似于图1的截面图，示出图1所示的探测器端部的替换例； 
图4是示意性说明图，其中根据本发明的耳式医用温度计的探测器端部插入耳中； 
图5是示出热敏电阻的热量时间常数的图表； 
图6是示出由根据本发明的耳式医用温度计所测量的身体温度结果的图表； 
图7是在根据本发明的耳式医用温度计中温度测量线路的框图； 
图8是传统耳式医用温度计的示意性框图，示出温度计的操作原理；以及 
图9是在传统耳式医用温度计中探测器的端部的纵向截面视图。 
具体实施方式
在描述本发明的优选实施例中，这里将对附图中的图1到7进行参照，其中相同的数字指示本发明的相同的特征。本发明的特征在附图中不必成比例示出。 
现在参照图1到7，下面将要解释根据本发明的耳式医用温度计的实施例。图1和2示出在根据本发明的耳式医用温度计的探测器20的结构。在探测器20中，由树脂材料制成的第二高热绝缘部件220通过传统的结合机构(例如焊接、胶粘、按压配合、螺丝结合等等)连接到第一热绝缘部件210上。第二高热绝缘部件220从结合到第一热绝缘部件210上的部分起向端表面221向前成锥形。保护盖230覆盖第一热绝缘部件210和第二高热绝缘部件220。热敏电阻细引线240嵌入第一热绝缘部件210和第二高热绝缘部件220，使得线240的转动端部241桥接在第二高热绝缘部件220的表面221上，该第二高热 绝缘部件220暴露在表面221以上。超快反应热敏电阻250基本上安装在热敏电阻细引线240的转动端部241的中心。尽管在传统耳式医用温度计中使用的热敏电阻12(参见图8)具有1mm的直径和2到3mm的长度，但是在本发明耳式医用温度计中使用的热敏电阻250例如是具有0.3mm侧部的立方体。 
优选的，如图3所示，第二高热绝缘部件220的表面221形成为凹形构造，以便增强到热敏电阻250上的红外线的反射效果。通过以镜面抛光方式加工凹形表面221，能够进一步增强反射效率。 
图4示出当探测器20插入外耳道时本发明的耳式医用温度计中的探测器20的测量位置。探测器20的端部优选形成为如下构造：其中探测器20的中间位置紧密接触外耳道1的进口并且在探测器20的远端和耳鼓2之间的空间变得尽可能小。 
确定热敏电阻250的温度的因素包括：由红外线的直接辐射引起的在热敏电阻细引线240和热敏电阻250中的温度增加，在外耳道中的空气的直接热传导，以及由插入外耳道内的探测器20引起的直接热传导。有必要当探测器20插入外耳道1内时探测器20的远端不影响在外耳道1中的温度。从而，第二高热绝缘部件220和保护盖230用于减小这种影响。 
图5是限定热量时间常数的说明图。热量时间常数意味着如下的一段时间：当保持在任意温度T1的热敏电阻250突然插入处于周围温度T2的环境时，热敏电阻250从温度T1变化到目标温度T2。一般，热量时间常数是到达在温度T1和T2之间的温度差ΔT(ΔT＝T2-T1)的63.2％的时间段X。本发明中使用的热敏电阻250是在空气中具有1秒或更低(优选0.1秒或更低)的热量时间常数的超快反应热敏电阻。 
图6是说明当图1或2所示的探测器20测量身体温度时热敏电阻中温度变化的图表。在图6中，纵轴指示温度(℃)而横轴指示过去的时间(秒)。同时，安装在探测器20上的热敏电阻的热量时间常数是1(一)秒和用于测量温度的一段时间是在10(十)秒以内。为了在短时间段内测量温度，优选在空气中热敏电阻250的热量时间常数 是大约0.1秒。从而，这能够缩短测量时间1到2秒。 
由于已经一般使用在传统电子医用温度计中的V-F转换系统尽管具有高精确度但花费大量时间用于测量，因此不可能通过使用V-F转换系统来利用探测器20的高反应速度。因此，本发明的耳式医用温度计采用温度测量线路系统，例如图7所示的系统。该温度测量线路系统使用包含AD转换器31和控制信号处理器32的微控制器单元(MCU)30。包含AD转换器的MCU已经变得广泛可见，并且特别是包含在十位以内的AD转换器的MCU易于得到和低价格。“Vref”指示用于AD转换器31的参考电源电压和AD转换数值的全标度数值。在MCU中获得的AD转换器的情况下，Vref通常设定为等于MCU的电源电压。在电源线路40中的参考电源电压Vref的并联电压V1、V2和V3由下面的等式(1)、(2)和(3)表示。R1、R2、R3、R4、Rref和Rth分别指示在电源线路40中的电阻。P1、P2和P3指示在模拟开关50中的相应终端。 
P1：V1＝R2/(R1+R2)×Vref        (1) 
P2：V2＝R3/(R3+R4)×Vref        (2) 
P3：V3＝Rth/(Rth+Rref)×Vref    (3) 
这里，V2＞V3＞V1。 
误差因素包括在操作放大器(OP)60中的偏置误差和在操作放大器60中的增益误差(GE)。包含在MCU中的十位AD转换器使用连续的比较系统并且显著遭受诸如AD偏置误差之类的误差。当切换在模拟开关50中相应的终端P1、P2和P3时，AD转换数值分别由A1、A2和A3指示。当N指示在操作放大器60中的放大程度时，V1、V2 和V3的相应AD转换数值由下面的等式(4)、(5)、(6)和(7)表达。 
A1＝V1+N×GE×OP偏置误差+AD偏置误差(4) 
A2＝(OP偏置误差+V2-V1)×N×GE+AD偏置误差(5) 
A3＝(OP偏置误差+V3-V1)×N×GE+AD偏置误差(6) 
A2-A1＝(V2-V1)×N×GE                   (7) 
由于V1、V2和N已知，GE能够通过下面的等式(8)获得。 
GE＝(A2-A1)/N(V2-V1)(8) 
如果读取在模拟开关50中的相应终端P1和P2的AD转换数值的操作由线路修正循环指定，该循环将会是A3-A1＝(V3-V1)×N×GE。由于GE由线路修正循环获得，能够消除操作放大器(OP)60的增益误差(GE)。在测量温度时，MCU30能够使得终端P1和P2的修正循环有效，然后测量终端P3，消除来自测量数值的误差因素，并且从储存在MCU中的表格获得热敏电阻温度。这将作为身体温度显示在显示器70上。 
本发明的耳式医用温度计能够应用于动物以及人。 
在2005年3月14日申请的日本专利申请No.2005-071350的包括说明书、权利要求、附图和摘要在内的全部公开内容全部在此进行结合作为参考。 
虽然已经结合具体的优选实施例特别描述了本发明，但是显然在前面的描述的启示下，许多替换例、修改例和变体将会对本领域熟练技术人员来说变得明显。因此预期附加的权利要求将包括落入本发明实质范围和精神内的任何这种替换例、修改例和变体。 

Claims (6)

1.一种包含探测器的耳式医用温度计，该探测器包括：由树脂材料制成的第一热绝缘部件；连接到所述第一热绝缘部件的远端上由树脂材料制成的第二高热绝缘部件；包围所述第一热绝缘部件和第二高热绝缘部件的保护盖；嵌入所述第一热绝缘部件和第二高热绝缘部件内的热敏电阻细引线；以及安装在所述热敏电阻细引线的转动端部的中心上的超快反应热敏电阻。
2.如权利要求1所述的耳式医用温度计，其中所述第二高热绝缘部件向前成锥形并且在远端上提供有凹表面，并且其中所述热敏电阻细引线的转动端部桥接在所述第二高热绝缘部件的所述凹表面上，以在所述凹表面上暴露。
3.如权利要求2所述的耳式医用温度计，其中所述第二高热绝缘部件的所述凹表面以镜面抛光方式加工。
4.如权利要求1所述的耳式医用温度计，其中所述超快反应热敏电阻的热量时间常数是1秒或更低。
5.如权利要求1所述的耳式医用温度计，其中所述超快反应热敏电阻的热量时间常数是0.1秒或更低。
6.如权利要求1所述的耳式医用温度计，其中在温度测量线路中的电源线路的输出侧处提供具有多个终端的模拟开关。
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EP1703267A1 (en) 2006-09-20
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US20060239329A1 (en) 2006-10-26
CN1862241A (zh) 2006-11-15

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