WO2021035956A1 - 一种可控阵列反射式光电传感器模组 - Google Patents

一种可控阵列反射式光电传感器模组 Download PDF

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WO2021035956A1
WO2021035956A1 PCT/CN2019/116012 CN2019116012W WO2021035956A1 WO 2021035956 A1 WO2021035956 A1 WO 2021035956A1 CN 2019116012 W CN2019116012 W CN 2019116012W WO 2021035956 A1 WO2021035956 A1 WO 2021035956A1
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light
sensor module
array
photoelectric sensor
tube
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PCT/CN2019/116012
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French (fr)
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周聪聪
胡钧
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杭州兆观传感科技有限公司
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure

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  • the application discloses a controllable array reflective photoelectric sensor module, which relates to the field of photoelectric physiological signal acquisition, and can be applied to various places such as blood oxygen saturation, heart rate, blood pressure, and sleep monitoring.
  • the human pulse wave contains rich health information, and stable and reliable pulse wave signal monitoring can provide a basis for continuous monitoring of the health of the body. From the pulse wave, the human body's blood oxygen saturation, pulse rate, heart rate variability, and peripheral vascular resistance can be analyzed, reflecting the health of the human respiratory system and cardiovascular system.
  • photoelectric sensors are commonly used to monitor human pulse wave signals.
  • the previous solutions for fixing the LED-PD distance have defects and cannot be adapted to a wider group of people;
  • different parts such as fingers, wrists, chest, forehead and other tissues have different optical parameters.
  • different parts needed different sensors, which was less applicable.
  • controllable array reflective photoelectric sensor module which can adapt to the optical parameters of the tissue to be measured, and provide a signal acquisition method with the best signal-to-noise ratio. It is very necessary to be able to obtain physiological signals stably.
  • the sensor module includes a light-emitting tube array, a photoelectric receiving tube, a light-emitting tube array, and a photoelectric sensor module.
  • the luminous tube array is used to emit light. The light is focused by the lens and transmitted into the human tissue. After diffuse reflection and refraction, it is received by the receiving tube and converted into electrical signals.
  • the luminous tube array includes a plurality of luminous units.
  • the luminous tube array designed in this application is symmetrical about the center of the photoreceiving tube in physical space, and in terms of control logic, the working light-emitting unit can be freely controlled.
  • the sensor module can adapt to the tissue optical parameters of the part to be measured, and provide the best signal-to-noise ratio signal acquisition method.
  • the module can be used for long-term continuous pulse wave oxygen saturation, heart rate, and blood pressure monitoring, The application prospect is broad.
  • Fig. 1 is a schematic diagram of a photoplethysmographic waveform according to an embodiment of the present application.
  • FIG. 2 is a schematic diagram of pulse wave waveforms collected by different light-emitting units of the array sensor module according to an embodiment of the present application.
  • Fig. 3 is a schematic diagram of the radial and axial distribution of diffuse reflection of photons according to an embodiment of the present application.
  • FIG. 4 is a top view of a controllable array reflective photoelectric dual optical path sensor module according to an embodiment of the present application.
  • Figure 5(a) is a front view of a controllable array reflective photoelectric dual optical path sensor module according to an embodiment of the present application.
  • Fig. 5(b) is a front view of a controllable array reflective photoelectric dual optical path sensor module according to another embodiment of the present application.
  • Fig. 6 is a top view of a controllable array reflective photoelectric dual optical path sensor module according to another embodiment of the present application.
  • PPG Photoplethysmography
  • the Lambert-Beer law is summarized as follows:-A beam of monochromatic light irradiates the surface of a certain absorption medium. After passing through a certain thickness of the medium, because part of the light energy is absorbed by the medium, the intensity of the transmitted light will be correspondingly weakened. The greater the concentration of the absorbing medium and the greater the thickness of the medium, the more significant the weakening of the light intensity.
  • the mathematical expression is shown in formula (1-1):
  • A is the absorbance
  • I 0 is the intensity of the incident light
  • I t is the intensity of the transmitted light
  • T is the transmittance or transmittance
  • K is the absorption coefficient or molar absorption coefficient
  • L is the thickness of the absorbing medium
  • c is the thickness of the light-absorbing material. concentration.
  • the volume of blood changes, resulting in changes in the amount of light absorbed by blood, and changes in the amount of light absorbed by arterial blood.
  • This component is called the pulsation component or the amount of communication (AC); it is generally considered that certain tissues of the human body Such as skin, venous blood, muscle, bone, etc., the amount of light absorption is constant, and this component is called direct current (DC).
  • Photoplethysmography obtains the pulse wave signal by extracting the amount of communication.
  • a complete photoplethysmography pulse wave is shown in Figure 1.
  • OA is the ascending branch, which represents the rapid ejection process of the heart contraction
  • AE is the descending branch, which reflects the process of diastolic blood flow reduction.
  • the end point E also represents The beginning of the next cardiac cycle.
  • Point A is the peak point of the main wave, that is, the point where the pressure is highest during the systole.
  • B represents the tidal wave point.
  • the tidal wave is also called the dicrotic pre-wave, which is formed by the impact of the left ventricular ejection from the aortic artery.
  • the lowest point C of the end-systole is the descending isthmus, after which the blood vessels relax. After descending the isthmus, a short upward wave CD appears, called the dicrotic wave, which is formed due to the closure of the aortic valve and the temporary backflow of arterial blood.
  • the shape detection of pulse wave plays an important role in the design of the health parameter algorithm. Finding the best morphological detection method in the part to be tested can effectively improve the signal-to-noise ratio and ensure the stability of signal monitoring.
  • Fig. 2 shows a schematic diagram of pulse wave waveforms collected by different light-emitting units of an array sensor module according to an embodiment of the present application.
  • there are four different light-emitting unit combinations namely light-emitting combinations 1 to 4, namely: only light-emitting combination 1 of the light-emitting unit where the number 1 in the figure is located, and only light the number in the figure
  • the light-emitting units of the controllable array reflective photoelectric sensor module choose different combinations, different photoelectric pulse waves can be obtained.
  • the pulse wave images obtained by the four combinations are shown in the lower part of FIG. The waveform is shown.
  • the pulse wave amplitude obtained is small and easily affected.
  • the pulse wave amplitude obtained by the receiving tube monitoring is larger and the shape is more stable. , Can better deal with individual differences, differences in detection parts and other issues. Therefore, lighting up light-emitting units with different distances from the receiving tube, or lighting up light-emitting units with different positions or numbers, etc., will obtain different monitoring signals.
  • a controllable array reflective photoelectric sensor module designed in this application is used to detect human physiological signals such as pulse waves, temperature, etc. based on photoplethysmography.
  • the module includes a light emitting tube array, a photoelectric receiving tube, and a light emitting tube.
  • the light barrier between the tube and the receiving tube and the lens located on the luminous tube the light is emitted from the luminous tube array, is focused by the lens, and is transmitted into the human body tissue.
  • the photons are collected by the receiving tube after diffuse reflection and refraction. Converted into electrical signals.
  • the controllable array reflective photoelectric dual optical path sensor module may adopt the following technical solutions: the module may include light-emitting tube arrays 2-1, 2-2, and photoelectric receiving tubes 1.
  • the light-emitting tube array includes n 2 light-emitting units.
  • the light sources 2-1-1, 2-1-2, and 2-1-3 of the luminous tube array 2-1 are symmetrical about the center of the photoreceiving tube 1 in physical space, and it can be seen that there are on the luminous tube array 2-2
  • the light source corresponding to the wavelength.
  • the working light-emitting unit can be freely controlled.
  • the typical working state is that the light-emitting unit and the light sources 2-1-1, 2-1-2, and 2-1-3 are also symmetrical about the center of the photoelectric receiving tube 1.
  • the number of luminous tube arrays and receiving tubes is not limited, and can be expanded according to the described implementation mode.
  • the controllable array reflective photoelectric sensor module can detect human physiological signals, such as pulse wave, temperature, etc., based on photoplethysmography.
  • Figures 5(a) and 5(b) show the front view of a controllable array reflective photoelectric dual optical sensor module according to some embodiments of the present application, wherein Figure 5(a) is a schematic diagram of a planar structure, and Figure 5 (b) is a schematic diagram of the arc structure.
  • the light barriers 3-1, 3-2 surround the photoelectric receiver 1, and there are openings at the top of the light barriers 3-1, 3-2.
  • the light emitted from the light source in the luminous tube arrays 2-1, 2-2 cannot directly enter the photoreceiver ⁇ 1. This design can effectively avoid the interference caused by the light leakage problem.
  • the light barrier 3-1, 3-2 makes the light emitted by the light source in the luminous tube array 2-1, 2-2 focus on the lens 5-1, 5-2 and enter the skin It can reach the photoreceiving tube 1 after diffuse reflection or enter the photoreceiving tube 1 after passing through the lens 5-3.
  • the lenses 5-1, 5-2, and 5-3 can be coated with a wavelength selective film for selection Different wavelengths make the characteristics of the light source better.
  • the lens material can be cured glue or glass with good biocompatibility.
  • Fig. 6 shows an embodiment of a controllable array reflective photoelectric dual optical path sensor module with multiple photoreceiving tubes.
  • the module can include a light emitting tube array 2-1, photoelectric receiving tubes 1-1, 1-2, 1-3, 1-4 located between the light emitting tube and the light barrier 3 between the receiving tube, light Emitted from the luminous tube array 2-1, focused by the lens, and transmitted into the human body tissues. After diffuse reflection and refraction, the photons are collected and converted by the receiving tubes 1-1, 1-2, 1-3, 1-4. For electrical signals.
  • 2-1-1, 2-1-2, 2-1-3 are respectively It represents three typical light sources with different wavelengths in the three light-emitting units.
  • the photo-receiving tubes 1-1, 1-2, 1-3, 1-4 are symmetrical with respect to the light-emitting tube array 2-1.
  • the number of luminous tube arrays and receiving tubes is not limited, and can be expanded according to the described implementation.
  • the form of the receiving tube may be a curved structure located in the luminous tube array.
  • the light source emits light after diffuse reflection from the tissue. At the strongest ring.
  • the distance between the luminous tube arrays 2-1, 2-2, and the photoelectric receiving tube 1 can be calculated by simulation.
  • a static state when light propagates through human tissue, it is absorbed, reflected and scattered by the tissue layer. Since the propagation speed of light in vacuum is 3 ⁇ 10 8 m/s, and the thickness of the tissue layer is mm level, the photon emission time is ps level. This process can be approximated as a transient process.
  • LiHong Wang and Gardner et al. performed Monte Carlo (MC) simulations under the same tissue model, in which LiHong Wang et al. set the number of photons tracked to be 10 ⁇ 6, and Gardner et al. set the number of samples to be 10 ⁇ 5 , The results are compared as follows:
  • the MC simulation result is closer to the program result of LiHong Wang et al.
  • the MC simulation has a certain degree of uncertainty, and a small range of errors is usually acceptable.
  • the distribution of photons emitted in this model is as follows. It is worth noting that the light travels through the tissue, a banana-shaped path, and finally returns to the incident medium.
  • Figure 3 shows the radial and axial distribution of the diffusely reflected photons relative to the incident position. Analysis of Figure 3 shows that with the increase of the detection radius, the diffuse reflectance of the photons presents a trend that first stabilizes and then decreases.
  • the reason for the preliminary analysis is: A large part of the photons are diffusely reflected by the superficial tissues of the skin without entering the blood-bearing layer; the diffusely reflected and transmitted photons in the axial direction have a symmetrical distribution characteristic, that is, the photons that are emitted directly and horizontally. Is the least, most of the photons are emitted obliquely.
  • the lens may be a convex lens.
  • a 3D model can be firstly designed, a light source and an observation surface are established, light simulation is performed, and the results are analyzed, and the exit angle and the skin surface are 30°-50°. °(Convergence to the receiving tube) to optimize the direction of the optimal angle.
  • controllable array reflective photoelectric sensor module may further include a housing.
  • the aforementioned light emitting tube array, photoreceiving tube, light barrier and lens are all inside the housing, and the housing may be in the light emitting tube array.
  • the photoelectric receiving tube and the lens are slotted to allow light to pass through.

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Abstract

一种可控阵列反射式光电传感器模组，用于检测人体生理信号，传感器模组包括发光管阵列（2-1,2-2）、光电接收管（1）、位于发光管阵列（2-1,2-2）和光电接收管（1）之间的档光板（3-1,3-2）以及位于发光管阵列（2-1,2-2）上的透镜（5-1,5-2），发光管阵列（2-1,2-2）用于发射光，光经过透镜（5-1,5-2）的聚焦，传输进入人体组织，经过漫反射、折射后由接收管（1）接收并转换为电信号，其中，发光管阵列（2-1,2-2）包括多个发光单元（2-1-1,2-1-2,2-1-3）。能够自适应待测部位的组织光学参数，提供最佳信噪比的信号获取方式。

Description

一种可控阵列反射式光电传感器模组 技术领域
本申请公开了一种可控阵列反射式光电传感器模组，涉及光电生理信号采集领域，可应用于血氧饱和度、心率、血压以及睡眠监测等多种场所。
背景技术
人体脉搏波中包含丰富的健康信息，稳定、可靠的脉搏波信号监测可以为身体健康状态的持续监测提供依据。从脉搏波中，可以分析出人体的血氧饱和度、脉率、心率变异性以及外周血管阻力等参数，反应了人体呼吸系统和心血管系统的健康状态。
目前，常用光电传感器来监测人体脉搏波信号，然而，对于不同个体，由于组织的散射系数、吸收系数等光学参数存在差异，以往固定LED-PD距离的方案存在缺陷，不能适应更广泛的群体；对于同一个个体，不同的部位，比如手指、手腕、胸口、额头等组织的光学参数各异，以往不同的部位需要做不同的传感器，适用性较弱。
为了解决上述问题，设计一种可控阵列反射式光电传感器模组，自适应待测部位的组织光学参数，提供最佳信噪比的信号获取方式，能够稳定获取生理信号是十分有必要的。
发明内容
针对现有技术上存在的不足，本申请设计一种可控阵列反射式光电传感器模组，用于检测人体生理信号，该传感器模组包括发光管阵列、光电接收管、位于发光管阵列和光电接收管之间的档光板以及位于发光管阵列上的透镜，发光管阵列用于发射光，光经过透镜的聚焦，传输进入人体组织，经过漫反射、折射后由接收管接收并转换为电信号，其中，发光管阵列包括多个发光单元。
本申请相对于现有技术而言，具有以下有益效果：本申请设计的发光管阵列在物理空间上关于光电接收管中心对称，控制逻辑上，工作的发光单元可以自由控制，基于这种有益设计，使得所述传感器模组能够自适应待测部位的组织光学参数，提供最佳信噪比的信号获取方式，该模组可以用于长时间连续脉搏波血氧饱和度、心率、血压监测，应用前景广阔。
附图说明
图1为根据本申请的实施例的光电容积脉搏波波形示意图。
图2为根据本申请的实施例的阵列式传感器模组不同发光单元采集的脉搏波波形示意图。
图3为根据本申请的实施例的光子漫反射的径向和轴向分布示意图。
图4为根据本申请的实施例的可控阵列反射式光电双光路传感器模组的顶视图。
图5(a)为根据本申请的实施例的可控阵列反射式光电双光路传感器模组的前视图。
图5(b)为根据本申请的另一实施例的可控阵列反射式光电双光路传感器模组的前视图。
图6为根据本申请的另一实施例的可控阵列反射式光电双光路传感器模组的顶视图。
具体实施方式
为使本申请实现的技术手段、创作特征、达成目的与功效易于明白了解，下面结合附图及具体实施方式，进一步阐述本申请。
光电容积脉搏波描记法(PPG)最早在1938年由Hertzma首次提出，其基本原理是利用一对发光管和光电接收管来检测脉搏波。其科学理论基础是郎伯-比尔定律(Lambert-Beer’S Law)。郎伯-比尔定律概述为：—束单色光照射到某个吸收介质表面，在通过一定厚度的介质后，由于一部分光能被介质吸收，透射光的强度就会相应地发生减弱。吸收介质的浓度越大，介质的厚度越大，则光强度的减弱越显著，数学表达式如公式(1-1)所示：
Figure PCTCN2019116012-appb-000001
A表示吸光度，I 0表示入射光的强度，I t表示透射光的强度，T表示透射比或透光度，K表示吸收系数或摩尔吸收系数，L表示吸收介质的厚度，c表示吸光物质的浓度。上式表明，吸光度A的变化与吸收介质的厚度L的变化成正比，即接收管接受到的光强的变化率可以反映血液的容积变化。
随着血管的搏动，血液的容积发生变化，导致血液的吸光量发生改变，动脉血液对光的吸收量产生变化，这一成分称为脉动分量或者交流量(AC)；通常认为人体某 些组织如皮肤、静脉血、肌肉、骨骼等对光的吸收量是恒定不变的，这一成分称为直流量(DC)。光电容积脉搏波描记法就是通过提取交流量来获得脉搏波信号的。
一个完整的光电容积脉搏波如图1所示，图中，OA为上升支，代表心脏收缩的快速射血过程，AE为下降支，反映心脏舒张血流减少的过程，结束点E也表示了下一个心动周期的开始。A点为主波峰值点，即心脏收缩期间压力最高的点。B代表潮波点，潮波又称作重搏前波，是主切动脉受左心室喷血冲击而形成的。收缩末期的最低点C为降中峡，之后血管舒张，降中峡之后出现一个短暂向上的波CD，称为重搏波，是由于主动脉瓣关闭，动脉血液短暂回流而形成的。
脉搏波的形态检测在健康参数算法设计过程中有着重要的作用，在待测部位找到形态学最优的探测方式可以有效提高信噪比，保证信号监测的稳定。
图2示出了根据本申请的实施例的阵列式传感器模组不同发光单元采集的脉搏波波形示意图。如图2所示，示意了4种不同的发光单元组合，分别是发光组合1～4，即：只点亮图中的数字1所在的发光单元的发光组合1，只点亮图中的数字2所在的发光单元的发光组合2，只点亮图中的数字3所在的发光单元的发光组合3，以及点亮图中的数字4所在的两个发光单元的发光组合4。可控阵列反射式光电传感器模组的发光单元选择不同的组合时，可以得到不同的光电脉搏波。例如，根据本申请的一个实施例，在如图2中上方所示的4种发光组合中，采用相同的波长λ 1的情况下，4种组合得到的脉搏波的图像如图2中下方的波形所示。当采用图2上方示意的发光组合1时，得到的脉搏波幅度较小，容易受影响，而采用图2上方示意的发光组合4时，接收管监测得到的脉搏波幅度较大，形态更稳定，可以更好地应对个体差异、检测部位差异等问题。因此，点亮与接收管的距离不同的发光单元，或者点亮不同位置或数量等的发光单元，会得到不同的监测信号。
本申请设计的一种可控阵列反射式光电传感器模组，用于基于光电容积脉搏波描记法检测人体生理信号如脉搏波、温度等，该模组包括发光管阵列，光电接收管，位于发光管和接收管之间的档光板以及位于发光管上的透镜，光从发光管阵列中发出，经过透镜的聚焦，传输进入人体组织，光子经过漫反射、折射后由接收管收集出射的光子并转换为电信号。
如图4所示，根据本申请的一些实施例，可控阵列反射式光电双光路传感器模组可以采用以下技术方案：该模组可以包括发光管阵列2-1,2-2，光电接收管1，位于发光管和接收管之间的档光板3-1,3-2以及位于发光管上的透镜5-1,5-2(见图5)，光 从发光管阵列2-1,2-2中发出，经过透镜5-1,5-2的聚焦，传输进入人体组织，光子经过漫反射、折射后由接收管1收集出射的光子并转换为电信号。发光管阵列包括n 2个发光单元，例如，根据本申请的一个实施例，典型值可以取n＝3,共9个发光单元，每个发光单元内有λ 1，λ 2，...λ m m种波长的光源，例如，典型值可以取m＝3，分别为绿光(570纳米)，红光(660纳米)，红外光(940纳米)，图中2-1-1，2-1-2，2-1-3分别代表了其中的3个发光单元内典型的3种不同波长的光源。发光管阵列2-1的光源2-1-1，2-1-2，2-1-3分在物理空间上关于光电接收管1中心对称，可以看到在发光管阵列2-2上有对应波长的光源。在控制逻辑上，工作的发光单元可以自由控制，典型的工作状态为发光单元以及光源2-1-1，2-1-2，2-1-3也关于光电接收管1中心对称。在该实施例中，不限制发光管阵列以及接收管的数量，可以根据所述的实施方式扩展。该可控阵列反射式光电传感器模组能够基于光电容积脉搏波描记法检测人体生理信号，例如脉搏波、温度等。
图5(a)和图5(b)显示了根据本申请的一些实施例的可控阵列反射式光电双光路传感器模组的前视图，其中图5(a)为平面型结构示意图，图5(b)为弧形结构示意图。档光板3-1,3-2包围光电接收器1，在档光板3-1,3-2的顶端有开口，发光管阵列2-1,2-2中光源发出的光线无法直接进入光电接收器1。该设计可以有效避免漏光问题引入的干扰，档光板3-1,3-2使发光管阵列2-1,2-2中光源发出的光经过透镜5-1,5-2聚焦后，进入皮肤经过漫反射后才能到达光电接收管1或者经过透镜5-3后进入光电接收管1，所述的透镜5-1，5-2，5-3上可以镀有波长选择性薄膜，用于选择不同波长，使得光源的特性更好。透镜材料可以是具有良好生物相容性的固化胶水或者玻璃。
图6示出了具有多个光电接收管的可控阵列反射式光电双光路传感器模组的实施例。如图6所示，该模组可以包括发光管阵列2-1，光电接收管1-1，1-2，1-3，1-4位于发光管和接收管之间的档光板3，光从发光管阵列2-1中发出，经过透镜聚焦，传输进入人体组织，光子经过漫反射、折射后由接收管1-1，1-2，1-3，1-4收集出射的光子并转换为电信号。可控发光管2-1阵列包括2 n个发光单元，典型值n＝3,共9个发光单元，每个发光单元内有λ 1，λ 2，...λ m m种波长的光源，典型值取m＝3，分别为绿光(570纳米)，红光(660纳米)，红外光(940纳米)，图中2-1-1，2-1-2，2-1-3分别代表了其中的3个发光单元内典型的3种不同波长的光源。光电接收管1-1，1-2，1-3，1-4关于发光管阵列2-1对称。在该实施例中，不限制发光管阵列以及接收 管的数量，可以根据所述的实施方式扩展，接收管的形式可以是弧面的结构位于发光管阵列光源经过组织漫反射后出射形成的光强最大圆环处。
发光管阵列2-1,2-2，光电接收管1的距离可以通过仿真计算，在静态的情况下，光在人体组织传播时，被组织层吸收、反射与散射。由于光在真空中的传播速度为3×10 8m/s，组织层的厚度为mm级，因此光子出射的时间为ps级，可以将这一过程近似为一个瞬态的过程。LiHong Wang和Gardner等人在同样的组织模型下进行蒙特卡洛(MC)模拟，其中LiHong Wang等人设定追踪的光子的样本数为10 ^6，Gardner等人选取的样本数为10 ^5，结果对比如下：
表1 对三层组织模型的MC模拟结果对比
  样本数 反射率 折射率
Gardner 10^5 23.81％ 9.74％
LiHong Wang 10^6 23.75％ 9.65％
本文程序 10^6 23.70％ 9.58％
MC模拟结果与LiHong Wang等人的程序结果更为接近，MC模拟作为基于统计学方法的计算机模拟方法，其结果具有一定的不确定性，小范围的误差通常是可以接受的。在该模型中光子出射的分布如下，值得注意的是，光经由组织，一种香蕉形的路径行走，最后回到入射介质。
图3表示了漫反射光子相对于入射位置的径向和轴向分布，分析图3可知，随着探测半径的增加，光子的漫反射率呈现了先平稳后减少的趋势，初步分析原因是，一大部分光子并未进入到含血层就受到了皮肤浅层组织的漫反射；轴向上漫反射和透射的光子都呈现了一种对称分布特性的特性，即径直出射和水平出射的光子是最少的，大部分光子都是斜向出射的，因此，透镜5-1,5-2设计的依据也是来源于此，改变了光源入射角的方向。根据本申请的一个实施例，该透镜可以是凸透镜，在透镜设计中，可以首先设计3D模型，建立光源与观察面，进行光线模拟，分析结果，根据使得出射角与皮肤面呈现30°～50°(向接收管收敛)的最优化角度方向进行优化。
此外，根据本申请的一些实施例，该可控阵列反射式光电传感器模组还可以包括外壳，前述发光管阵列、光电接收管、档光板和透镜都在外壳内部，该外壳可以在发光管阵列、光电接收管及透镜上方开槽，允许光线通过。
以上显示和描述了本申请的基本原理和主要特征和本申请的优点。本行业的技术人员应该了解，本申请不受上述实施例的限制，上述实施例和说明书中描述的只是说 明本申请的原理，在不脱离本申请精神和范围的前提下，本申请还会有各种变化和改进，这些变化和改进都落入要求保护的本申请范围内。本申请要求保护范围由所附的权利要求书及其等效物界定。

Claims (10)

  1. 一种可控阵列反射式光电传感器模组，用于检测人体生理信号，其特征在于，所述传感器模组包括发光管阵列、光电接收管、位于所述发光管阵列和所述光电接收管之间的档光板以及位于所述发光管阵列上的透镜，所述发光管阵列用于发射光，所述光经过透镜的聚焦，传输进入人体组织，经过漫反射、折射后由接收管接收并转换为电信号，其中，所述发光管阵列包括多个发光单元。
  2. 根据权利要求1所述的可控阵列反射式光电传感器模组，其特征在于，每个所述发光单元内包括m种不同波长的光源,其中，m为正整数。
  3. 根据权利要求2所述的可控阵列反射式光电传感器模组，其特征在于，每个所述发光单元内包括3种波长的光源，分别为绿光光源、红光光源和红外光光源。
  4. 根据权利要求1所述的可控阵列反射式光电传感器模组，其特征在于，所述多个发光单元发出的光的波长不完全相同。
  5. 根据权利要求1所述的可控阵列反射式光电传感器模组，其特征在于，所述发光管阵列包括n 2个发光单元,其中，n为正整数。
  6. 根据权利要求1所述的可控阵列反射式光电传感器模组，其特征在于，
    所述发光管阵列在物理空间上关于所述光电接收管中心对称，
    所述发光单元在物理空间上关于所述光电接收管中心对称。
  7. 根据权利要求1所述的传感器模组，其特征在于，在工作状态，所述发光单元发出的光的波长关于所述光电接收管中心对称。
  8. 根据权利要求1所述的可控阵列反射式光电传感器模组，其特征在于，所述发光管阵列上的透镜材料为具有良好生物相容性的固化胶水或者玻璃，透镜上镀有波长选择性薄膜。
  9. 根据权利要求1所述的可控阵列反射式光电传感器模组，其特征在于，所述可控阵列反射式光电传感器模组包括外壳，所述发光管阵列、所述光电接收管、所述档光板和所述透镜都在外壳内部。
  10. 根据权利要求1所述的可控阵列反射式光电传感器模组，其特征在于，所述外壳在所述发光管阵列、所述光电接收管及所述透镜上方开槽，允许光线通过。
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