CN1051297A - 无创测量血糖浓度的方法和装置 - Google Patents
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Abstract
无创测量血糖浓度的方法和装置。本发明使来
自半导体二极管激光器的滤长为1.3-1.9微米的电
磁辐射线,通过皮肤传到血管。在那里光与血液中的
不均匀成分相互作用,然后由血液漫反射。被反射的
光将为血液主要成分的分子的特性振动所调制。该
反射光被检测并以数字信号提供给单片微计算机。
该单片微计算机根据该数字信号并参照储存在其存
储器中的一条标定曲线算出血糖浓度。然后将该浓
度值显示在数字显示器上。
Description
本发明涉及测量血糖浓度的方法和装置,具体涉及使用近红外辐射漫反射激光光谱测定法来测量血糖浓度的无创技术。
一般地说,糖尿病患者每天要使用便携式测量装置测量血糖浓度2至8次,该装置包括一个注射器(取血样)和试纸(测试血内葡萄糖量)。这就是众所周知的“酶”测法。
血糖浓度的酶测法因需抽血和费用高而不受欢迎。虽然现已引用基于试纸的、花费较少的方法,但是它们的精度较差并且仍然需要抽血。因此,业已进行研究以致力于解决这些问题。
人们希望提供一种准确而不需抽血的、测量血糖浓度的方法。
为此,本发明的一个目的是提供一种无创测量血糖浓度的技术,亦即为进行这项测量而无需抽血。
本发明的另一目的是提供一种方便而价廉、便携和容易使用的测量血糖浓度的装置。
本发明基于近红外照射漫反射激光光谱学,借助用无害电磁射线辐照血管来测量血糖浓度。本发明利用具有能穿过皮肤到达测量部位(例如血管)的波长的电磁波的辐照。由于皮肤主要是由水组成的,水几乎在整个红外光谱范围内吸收红外射线,因此在称为“水传输窗口”的红外光谱范围中只有某一窄小部分的射线能穿透皮肤。
直到最近,水传输窗口被认为只包含3-5μm之间的波长。然而,根据本发明人的调查研究,能够通过水传输窗口到达血管的波长包括1.3-1.9微米之间的波长。
据此,本发明使用了来自一个半导体二极管激光器的1.3-1.9微米波长射线的电磁波进行照射。当这些波长的电磁波照射皮肤时,光穿过皮肤到达血管,在那里光与血液的不均匀成分(heterogeneons componmt)相互作用。到达血液的光经由血液漫反射。被反射的光将为血液主要组分的分子的特性振动所调制。
在本发明中,上述被漫反射的光由一个汇集球(integrating sphere)来汇集。如上所述被汇集的光子(hν)由一个检测器转换为电测值并将该值提供给一个处理装置(例如一个单片微计算机)。该单片微计算机利用精确的标定方法来计算血糖浓度。在本发明中近红外线辐照规定如下(根据国际理论与应用化学联合会(IUPAC)的规定)频率约为1013-3.75×1014赫兹,能量约为0.951-35.8(千卡/克分子),0.0412-1.55电子伏特;波长约为0.8-30微米。本发明基于有关描述用近红外辐射漫反射激光光谱测定法测量血糖分子振动运动的物理和化学原理。这种振动运动既包括转动运动也包括平移运动,还包括谐波振动和组合振动。在这些振动之中,谐波振动是主要的。
在本发明中包含的分析方法包括一个数学模型,该模型基于本发明人为了确定血糖浓度而改善的多线性回归分析和多变量分析。
本发明提供用以测量血糖浓度的一种方法和装置,它具有患者容易使用和化费最低的优点。本发明没有耗能部件并且是便携式的,能方便地在户外进行测试。本发明要比先有技术方便得多。此外,本发明不存在由长期使用注射器可能造成对身体的伤害等弊病。
本发明的测量装置可在短时间内不被人注意地测量血糖浓度。因而将使先有技术因其不便和昂贵终被废弃。
本发明的上述目的和其它目的通过采用无创技术测量血糖浓度而得以实现。该技术在于:
一个能源,例如电池,它通过电源开关给单片微计算机、数字显示器、激光二极管电源、检测器(如果需要的话),以及光学单元(如果需要的话)供电。该单片微计算机控制所述激光二极管电源,以使它以稳定的电压和温度逐步地给激光二极管供以电流。该激光二极管通过起动/复位开关发出所需波长的辐射。该单片微计算机操作时使由其控制的并驱动所述激光二极管电源的数/模(D/A)转换器将数字控制信号转换为模拟控制信号。
于是,激光二极管电源使激光二极管发出适合于测量所需波长的光。来自激光二极管的光要经平行校准,或受光学上的控制、分开或组合。利用受光学控制的光照射邻近血管处的皮肤,穿过皮肤由血液吸收,分散和漫反射返回的光由一个汇集球进行汇集。由该汇集球收集的光子由检测器转换为模拟电信号。该模拟电信号被传送到一个前置放大器,在那里它被放大。将这个放大了的模拟电信号送到模/数(A/D)转换器将其转换为相应的数字信号,并将这个数字信号输出给单片微计算机。该单片微计算机根据该数字信号参照储存在该单片微计算机的存储器内的标定曲线来推算和计算血糖浓度,并将其显示在一个数字显示器上。
本发明采用无创技术测量血糖浓度的装置包括:单片微计算机,用以控制激光二极管电源,以便逐步地以稳定电压和温度给激光二极管供以电流。单片微计算机通过将一被检测值与储存在该微计算机的存储器内一标定曲线相比较来推算和计算血糖浓度;一个数/模转换器,将来自所述单片微计算机输出的数字控制信号转换为模拟控制信号,以控制给激光二极管供电的激光二极管电源,该激光二极管是进行血糖浓度测量的光源,它可包括多个激光二极管,用以根据激光二极管电源提供的电流发射不同波长的光,或相同波长的光;一个温度控制器,用以控制激光二极管的温度,它连接在激光二极管电源和激光二极管之间;一个光学单元,它平行校正激光二极管发出的光,或从光学上控制、分开或组合激光二极管的光;一个汇集球,用以在光学单元来的光穿过皮肤照射血液时对由血液分散和漫反射的光进行汇集;一个检测器,用以将汇集球收集的光子转换为一个电的模拟值,然后该值在前置放大器内被放大;一个模/数转换器,将电的模拟测量值转换为数字值;一个数字显示器,用以显示单片微计算机算出的血糖浓度。
本发明的这些目的和特点以及其它的目的和特点将通过阅读下面参照附图的实施例就会明了附图中;
图1 示出本发明的血糖浓度测量装置的方框图;
图2 是图1所示装置的详细电路图。
下面,参照附图来描述本发明测量装置的最佳实施例。
参照图1,当电源开关1被接通时,电池(通常是4.5-9伏,尤其适合为6伏充电电池)给单片微计算机2供电,同时,该电源向数字显示器3、激光二极管电源4,以及光学单元6(需要时)供电。
当起动/复位开关8接通时,激光二极管电源4根据单片微计算机2提供的控制信号向激光二极管5供电,其结果是,当电流超过阈值电流时(约20毫安),激光二极管电流逐步增加。于是,激光二极管5就开始发射光线。
激光二极管5发出血糖浓度测量所需波长的光(例如:具有1.3-1.9微米波长的光,尤其是具有1.4-1.8微米波长的光或其它)。这个波长的取得是通过逐步增加这样的电流来实现的,该电流是根据激光二极管的特性以稳定的电压和温度在约为20-200毫安范围内提供的。在本发明中,激光二极管5包含1-30个二极管,每个二极管都能发射不同波长的光或相同波长的光。
来自激光二极管5中收集二极管(collective diodes)发射的光可由这些二极管同时发射,或各二极管依次顺序发射。在同时工作的情况下,长度就要被选定,例如用傅里叶变换来选取。
从激光二极管5的收集二极管输出的光施加到光学单元6并且被校正,或者使该光受光学控制、分开或组合。然后让该光经过一个汇集球9,再在一个或多个方向上分光。
经过汇集球9的光连续地照射对象的皮肤,或者连续照射到在这种情况下事先准备好的一个参考部件上,在这里,该参考部件并不是必不可少的。
由血液吸收、分散或漫反射的光在由汇集球9汇集之后由检测器7进行检测。该汇集球呈球状或类似形状。在这里,汇集球9长、宽、高的尺寸小于2.56厘米,合适的大小是小于1.28厘米,特别是小于0.64厘米。该汇集球汇集由血液分散和反射的光。
如上所述检测的电模拟测量值由连接到该检测器7上的一个前置放大器进行放大。然后这个电模拟测量值由模/数转换器11转换为数字测量值。
接着,单片微计算机2通过将这个由模/数转换器11转换为数字测量值的信号与储存在该单片微计算机2的存储器内的一个标定曲线相比较,来计算该被测值。将该计算得出的数值显示在数字显示器3上。
上述测量装置的尺寸可以是:宽×长×高小于170毫米×80毫米×25毫米,合适的是小于150毫米×75毫米×22毫米,特别是小于130毫米×70毫米×20毫米。
光敏二极管适合作为检测器7,并且可以是锗检测器,更具体地说,可以是与一个前置放大器相连接的锗检测器。另外,光学单元6包括形成光的元件,它的尺寸小于0.5-5毫米(尤其小于2毫米),以便平行地聚光和漫射光。
再者,本发明并非局限于具有球状或类似形状的汇集球9,而它还可以是椭圆形或半椭圆形或其它的形状。
在本发明中,该部件可与上述的测量装置分开。在这种情况下,激光二极管5发射的光可通过光纤传送给该部件,该部件与所述测量装置之间的距离是100-1000毫米,其中,包括合适的是500毫米,更具体地说,可以是300毫米。当然,该部件不能与所述测量装置分开。
本发明不限于单片微计算机2与数/模转换器10和模/数转换器11分离,它也可以是包含在数/模转换器10和模/数转换器11之内的一个单片微计算机2。
此外,在本发明中,它可与辅助电路12一起使用,该辅助电路包括随机存储器RAM121和可擦可编程序只读存储器122,用以辅助单片微计算机2的一个操作。
本发明并不局限于血糖浓度的测量,例如,还可以用于胆甾醇浓度或酒精浓度的测量。
如上所述,根据本发明,提供了一种经济的无创方式测量血糖浓度的方法和装置,只要将该装置的端口放在人体的看得见血管的某一部位上便可容易地测出血糖浓度,而无需用诸如常规的注射器那样的器械。
Claims (8)
1、一种测量血糖浓度的方法,包括以下步骤:
通过电源开关让电池给处理装置、数字显示器、激光二极管电源、检测器以及光学单元供电;
控制所述处理装置以使所述激光二极管电源通过起动1复位开关以稳定的电压和温度逐渐地给所述激光二极管提供电流;
控制所述处理装置以使连接在所述处理装置与所述激光二极管电源之间的一个数/模转换器将数字控制信号转换为电控制信号;
借助于所述激光二极管电源,在所述激光二极管内发射有足以满足测量要求的波长的光;
校正由激光二极管发射的光,使之平行于相应的目标,或者光学控制、分开或组合所述激光二极管发出的光;
通过一个汇集球使所述光学控制的光照射到一条血管上,以测量血糖浓度;
在光穿过皮肤到达血液之后,借助于上述泄集球对由该血液吸收、散射和漫反射的光进行汇集;
在将上述汇集球汇集的并由所述检测器检测的光子转换为电的模拟测量值以后,将连接在所述检测器的一个前置放大器所放大的信号传送给一个模/数转换器;
在由所述模/数转换器将所述电模拟测量值转换为数字测量值以后,将该信号传送到所述处理装置;
通过将储存在所述处理装置的存储区内的一条标定曲线与由所述模/数转换器转换的数字测量值相比较,推测和计算血糖浓度;
在所述数字显示器上显示计算出的血糖浓度。
2、根据权利要求1所述的测量血糖浓度的方法,其中所述测量方法是基于利用谐波振动和其它类型振动的组合以及由于振动、旋转和平移运动而引起在近红外辐射漫反射激光光谱学中血糖分子振动运动的物理原理和化学原理。
3、根据权利要求1所述的测量血糖浓度的方法,其中,通过将储存在所述处理装置的存储器内一标定曲线与由所述模/数转换器转换的数字测量值相比较来推测和计算血糖浓度的步骤是使用了诸如多线性回归分析和多变量分析的数学方法。
4、一种测量血糖浓度的装置,它包括:
处理装置,用以控制激光二极管电源提供给激光二极管的电流的流动以使电流以稳定的电压和温度等级逐步地施加,所述处理装置通过将检测器检测和转换一个电的模拟测量值与储存在所述处理装置的存储器内的标定曲线相比较而推算和计算血糖浓度;
一个数/模转换器,通过将一个数字控制信号转换为模拟控制信号来控制激光二极管电源,其中所述激光二极管电源作为血糖浓度测量的一个光源作为血糖浓度测量的一个光源对所述激光二极管供以电源,所述激光二极管包括多个二极管,它们根据所述激光二极管电源提供的电流发出不同波长的发射光或者相同波长的发射光;
一个温度控制器,用以控制所述激光二极管的温度,所述温度控制器连接在所述激光二极管电源与所述激光二极管之间;
一个光学单元,用以校正所述激光二极管所发射的光使之平行于相应的目标,并且光学地控制、分开或组合所述激光二极管所发射的光;
一个汇集球,通过将由所述光学单元控制的光照射到一位糖尿病患者的作为测量部位的皮肤上,该汇集球则汇集由血液散射和漫反射的光;
一个检测器,在将上述汇集球汇集的光子转换为电模拟测量值以后,借助于与其连接的前置放大器放大一个信号;
一个模/数转换器,用以将所述电的模拟测量值转换为数字测量值;以及
一个数字显示器,用以显示所述推算和计算的血糖浓度。
5、根据权利要求4所述的测量血糖浓度的装置,其中由所述激光二极管发射的电磁辐射的波长是在近红外线区域内,尤其是1.3至1.9微米,更具体地说是1.4至1.8微米;以及
由所述激光二极管发射的光同时通过皮肤照射血液,或者顺序地通过皮肤照射血液。
6、根据权利要求4所述的测量血糖浓度的装置,其中所述的汇集球呈球状、椭圆形或半椭圆形或其它形状;以及
所述测量装置的宽×长×高小于130毫米×70毫米×20毫米,尤其适合于小于150毫米×75毫米×22毫米,更具体地说,适合于小于130毫米×70毫米×20毫米。
7、根据权利要求4所述的测量血糖浓度的装置,其中所述端口可借助于光纤与该测量装置分开,而且端口与测量装置之间的距离是100-1000毫米,尤其适合于500毫米,具体地说,适合于300毫米。
8、根据权利要求4所述的测量血糖浓度的装置,其中使用一个光敏二极管作为所述检测器用以检测由所述汇集球汇集的光子,并且使用一个锗检测器,更具体地说,使用一个连接到一前置放大器的锗检测器;
所述数/模转换器和模/数转换器是与所述处理装置分离的,或者包括在所述处理装置之内;以及
用作为电源的所述电池是4.5至9伏的,尤其适合于6V的充电电池。
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KR15584/89 | 1989-10-28 | ||
KR1019890015584A KR930011586B1 (ko) | 1989-10-28 | 1989-10-28 | 난-인베이시브 혈당농도 측정방법 및 그 장치 |
KR11241/90 | 1990-07-24 | ||
KR1019900011241A KR920002091A (ko) | 1990-07-24 | 1990-07-24 | 난-인베이시브 혈당농도 측정방법 및 그 장치 |
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CN107505268A (zh) * | 2017-08-04 | 2017-12-22 | 中国科学院半导体研究所 | 血糖检测方法及系统 |
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Also Published As
Publication number | Publication date |
---|---|
CA2028261C (en) | 1995-01-17 |
DE69033104T2 (de) | 1999-10-28 |
HUT58145A (en) | 1992-01-28 |
CA2028261A1 (en) | 1991-04-29 |
RU2122208C1 (ru) | 1998-11-20 |
US5267152A (en) | 1993-11-30 |
DE69033104D1 (de) | 1999-06-17 |
CN1025410C (zh) | 1994-07-13 |
EP0426358B1 (en) | 1999-05-12 |
ATE179874T1 (de) | 1999-05-15 |
JP2588468Y2 (ja) | 1999-01-13 |
HU906914D0 (en) | 1991-05-28 |
JPH0581253B2 (zh) | 1993-11-12 |
JPH10181U (ja) | 1998-08-25 |
JPH03146032A (ja) | 1991-06-21 |
HU213438B (en) | 1997-06-30 |
EP0426358A1 (en) | 1991-05-08 |
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