CN211484538U - Controllable array reflection type photoelectric sensor module - Google Patents
Controllable array reflection type photoelectric sensor module Download PDFInfo
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- CN211484538U CN211484538U CN201921409644.0U CN201921409644U CN211484538U CN 211484538 U CN211484538 U CN 211484538U CN 201921409644 U CN201921409644 U CN 201921409644U CN 211484538 U CN211484538 U CN 211484538U
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Abstract
The utility model discloses a controllable array reflection type photoelectric sensor module for detect human physiological signal, this sensor module include luminotron array, photoelectric receiving tube, be located the shelves light board between luminotron array and the photoelectric receiving tube and be located the lens on the luminotron array, and the luminotron array is used for the transmission light, and light passes through the focus of lens, and the transmission gets into human tissue, receives and converts the signal of telecommunication into by the receiving tube after diffuse reflection, refraction, and wherein, the luminotron array includes a plurality of luminescence unit. The utility model discloses can the self-adaptation await measuring the tissue optical parameter at position, provide the signal acquisition mode of best SNR.
Description
Technical Field
The utility model discloses a controllable array reflection type photoelectric sensor module relates to photoelectricity physiological signal collection field, can be applied to multiple places such as oxyhemoglobin saturation, rhythm of the heart, blood pressure and sleep monitoring.
Background
The human body pulse wave contains abundant health information, and stable and reliable pulse wave signal monitoring can provide a basis for continuous monitoring of the health state. From the pulse wave, parameters of the human body such as blood oxygen saturation, pulse rate, heart rate variability, peripheral vascular resistance and the like can be analyzed, and the health states of the respiratory system and the cardiovascular system of the human body are reflected.
At present, a photoelectric sensor is commonly used for monitoring human pulse wave signals, however, for different individuals, due to the fact that optical parameters such as scattering coefficients and absorption coefficients of tissues are different, the conventional scheme for fixing the LED-PD distance has defects and cannot be adapted to a wider group; for the same individual, different parts, such as fingers, wrists, chest, forehead and other tissues, have different optical parameters, and different sensors are needed for different parts in the past, so that the applicability is weak.
In order to solve the above problems, it is necessary to design a controllable array reflective photoelectric sensor module, which is adaptive to the tissue optical parameters of the site to be measured, provides a signal acquisition mode with an optimal signal-to-noise ratio, and can stably acquire physiological signals.
SUMMERY OF THE UTILITY MODEL
To exist not enough on the prior art, the utility model relates to a controllable array reflection type photoelectric sensor module for detect human physiological signal, this sensor module includes luminotron array, the photoelectric receiving tube, be located the shelves light board between luminotron array and the photoelectric receiving tube and be located the lens on the luminotron array, the luminotron array is used for transmitting the light, the light passes through the focus of lens, the transmission gets into human tissue, receive and convert into the signal of telecommunication by the receiving tube after diffuse reflection, refraction, wherein, the luminotron array includes a plurality of luminescence unit.
Compared with the prior art, the utility model, following beneficial effect has: the utility model discloses a luminotron array is about photoelectric receiving tube central symmetry in physical space, and on the control logic, the luminescence unit of work can freely be controlled, based on this kind of beneficial design, makes the sensor module can the self-adaptation tissue optical parameter at the position that awaits measuring, provides the signal acquisition mode of best SNR, and this module can be used for long-time continuous pulse ripples oxyhemoglobin saturation, rhythm of the heart, blood pressure monitoring, and application prospect is wide.
Drawings
Fig. 1 is a schematic diagram of a waveform of a photoplethysmograph pulse wave according to an embodiment of the present invention.
Fig. 2 is a schematic diagram of pulse wave waveforms collected by different light emitting units of the array sensor module according to the present invention.
Fig. 3 is a schematic view of the radial and axial distribution of diffuse reflection of photons according to an embodiment of the invention.
Fig. 4 is a top view of a controllable array reflective photoelectric dual optical path sensor module according to an embodiment of the present invention.
Fig. 5(a) is a front view of a controllable array reflective photoelectric dual optical path sensor module according to an embodiment of the present invention.
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 invention.
Fig. 6 is a top view of a controllable array reflective photoelectric dual optical path sensor module according to another embodiment of the present invention.
Detailed Description
In order to make the technical means, creation features, achievement purposes and functions of the present invention easy to understand, the present invention will be further explained with reference to the accompanying drawings and the detailed description thereof.
Photoplethysmography (PPG) was first proposed in 1938 by hertz, and its basic principle is to detect pulse waves using a pair of light emitting and light receiving tubes. The scientific theory is based on the Lambert-Beer' S Law. The lambert-beer law is summarized as: the monochromatic light beam is irradiated to the surface of an absorbing medium, and after passing through a medium with a certain thickness, the intensity of the transmitted light is reduced correspondingly as a part of the light energy is absorbed by the medium. The greater the concentration of the absorbing medium and the greater the thickness of the medium, the more significant the reduction in light intensity, the mathematical expression being shown in equation (1-1):
a represents the absorbance, I0Denotes the intensity of incident light, ItDenotes the intensity of transmitted light, T denotes the transmittance or transmittance, K denotes the absorption coefficient or molar absorption coefficient, L denotes the thickness of the absorbing medium, and c denotes the concentration of the light-absorbing substance. The above formula shows that the change of the absorbance A is directly proportional to the change of the thickness L of the absorption medium, namely, the change rate of the light intensity received by the receiving tube can reflect the volume change of the blood.
As the pulsation of a blood vessel occurs, the volume of blood changes, which changes the amount of light absorbed by the blood, and changes the amount of light absorbed by arterial blood, which is called a pulsating component or an Alternating Current (AC); it is generally considered that the absorption of light by certain tissues of the human body, such as skin, venous blood, muscle, bone, etc., is constant, and this component is called Direct Current (DC). Photoplethysmography is to extract the alternating current to obtain the pulse wave signal.
A complete photoplethysmogram is shown in fig. 1, in which OA is the ascending branch representing the systolic rapid ejection process, AE is the descending branch reflecting the diastolic flow reduction process, and end point E also represents the start of the next cardiac cycle. Point a is the main peak point, i.e. the point at which the pressure during systole is highest. B represents the tidal wave point, which is also called the prepulse wave and is formed by the impact of left ventricular ejection on the main incisor artery. The lowest point C at end systole is the descending isthmus, followed by vasodilation, after which a transient upward wave CD, called the dicrotic wave, occurs due to the aortic valve closing and a transient return of arterial blood.
The morphological detection of the pulse wave plays an important role in the design process of the health parameter algorithm, and the signal-to-noise ratio can be effectively improved and the stability of signal monitoring can be ensured by finding the optimal morphological detection mode at the part to be detected.
Fig. 2 shows schematic diagrams of pulse wave waveforms collected by different light emitting units of the array sensor module according to an embodiment of the present invention. As shown in fig. 2, 4 different combinations of light emitting units are illustrated, which are light emitting combinations 1 to 4, respectively, that is: only the light-emitting combination 1 of the light-emitting unit with the number 1 in the figure is lighted, and only the number 2 in the figure is lightedThe light emitting combination 2 of the light emitting units in the figure lights up only the light emitting combination 3 of the light emitting unit where the number 3 in the figure is located, and lights up the light emitting combination 4 of the two light emitting units where the number 4 in the figure is located. When the light-emitting units of the controllable array reflective photoelectric sensor module are selected to be combined differently, different photoelectric pulse waves can be obtained. For example, according to one embodiment of the present application, in 4 kinds of light emission combinations as shown in the upper part of fig. 2, the same wavelength λ is used1In the case of (3), the 4 combined pulse wave images are shown as the lower waveform in fig. 2. When the light-emitting combination 1 shown in the upper part of the figure 2 is adopted, the obtained pulse wave amplitude is small and is easy to be influenced, and when the light-emitting combination 4 shown in the upper part of the figure 2 is adopted, the pulse wave amplitude obtained by monitoring of the receiving tube is large, the form is more stable, and the problems of individual difference, detection part difference and the like can be better solved. Therefore, different monitoring signals are obtained by lighting the light emitting units at different distances from the receiving tube, or lighting the light emitting units at different positions, numbers, or the like.
The utility model discloses a controllable array reflection type photoelectric sensor module for detect human physiological signal like pulse wave, temperature etc. based on photoplethysmography, this module includes the luminotron array, the photoelectric receiving tube, be located the shelves light board between luminotron and the receiving tube and be located the lens on the luminotron, light is sent from the luminotron array, through the focus of lens, the transmission gets into human tissue, the photon is collected by the receiving tube after diffuse reflection, refraction and is converted into the signal of telecommunication.
As shown in fig. 4, according to some embodiments of the present invention, the controllable array reflective photoelectric dual optical path sensor module can adopt the following technical solutions: the module can comprise light emitting tube arrays 2-1,2-2, a photoelectric receiving tube 1, light baffle plates 3-1,3-2 positioned between the light emitting tubes and the receiving tube and lenses 5-1,5-2 positioned on the light emitting tubes (see figure 5), light is emitted from the light emitting tube arrays 2-1,2-2, is focused by the lenses 5-1,5-2 and is transmitted into human tissues, and emergent photons are collected by the receiving tube 1 and are converted into electric signals after the photons are subjected to diffuse reflection and refraction. The luminous tube array comprises n2A light-emitting unit, e.g. a rootAccording to an embodiment of the present invention, the typical value may be n ═ 3, 9 light emitting units in total, and λ may be provided in each light emitting unit1，λ2，...λmTypical values of the light sources with m wavelengths may be, for example, m — 3, which are green light (570 nm), red light (660 nm), and infrared light (940 nm), where 2-1-1, 2-1-2, 2-1-3 represent typical light sources with 3 different wavelengths in 3 light-emitting units. The light sources 2-1-1, 2-1-2, 2-1-3 of the light emitting tube array 2-1 are respectively symmetrical about the center of the photoelectric receiving tube 1 in physical space, and the light sources with corresponding wavelengths on the light emitting tube array 2-2 can be seen. In the control logic, the working light-emitting unit can be freely controlled, and the working state is typically that the light-emitting unit and the light sources 2-1-1, 2-1-2, 2-1-3 are also symmetrical about the center of the light-receiving tube 1. In this embodiment, the number of the light emitting tube arrays and the number of the receiving tubes are not limited, and the embodiment can be expanded. The controllable array reflective photoelectric sensor module can detect physiological signals of a human body, such as pulse waves, temperature and the like, based on a photoplethysmography.
Fig. 5(a) and 5(b) are front views illustrating a controllable array reflective photoelectric dual optical path sensor module according to some embodiments of the present invention, wherein fig. 5(a) is a schematic planar structure and fig. 5(b) is a schematic arc structure. The photoelectric receiver 1 is surrounded by the light blocking plates 3-1 and 3-2, the top ends of the light blocking plates 3-1 and 3-2 are provided with openings, and light rays emitted by the light sources in the light emitting tube arrays 2-1 and 2-2 cannot directly enter the photoelectric receiver 1. The design can effectively avoid interference caused by light leakage, the light blocking plates 3-1 and 3-2 enable light emitted by a light source in the light emitting tube arrays 2-1 and 2-2 to enter the photoelectric receiving tube 1 after being focused by the lenses 5-1 and 5-2 and entering the skin after being subjected to diffuse reflection or entering the photoelectric receiving tube 1 after passing through the lenses 5-3, and the lenses 5-1,5-2 and 5-3 can be plated with wavelength selective films for selecting different wavelengths, so that the characteristics of the light source are better. The lens material may be a cured glue or glass with good biocompatibility.
Fig. 6 shows an embodiment of a reflective photoelectric dual-optical-path sensor module with a controllable array having a plurality of photo-receiving tubes. As shown in FIG. 6, the module may includeThe light emitting tube array 2-1 and the photoelectric receiving tubes 1-1, 1-2, 1-3, 1-4 are arranged on the light baffle plate 3 between the light emitting tube and the receiving tube, light is emitted from the light emitting tube array 2-1, focused by the lens and transmitted into human tissue, and the emitted photons are collected and converted into electric signals by the receiving tubes 1-1, 1-2, 1-3, 1-4 after being subjected to diffuse reflection and refraction. The array of controllable light emitting tubes 2-1 comprises 2n9 light-emitting units with typical value n of 3, and each light-emitting unit has lambda1，λ2，...λmThe typical value of the light sources with m wavelengths is m ═ 3, which are respectively green light (570 nm), red light (660 nm), and infrared light (940 nm), and in the figure, 2-1-1, 2-1-2, 2-1-3 respectively represent the typical light sources with 3 different wavelengths in 3 light-emitting units. The photoelectric receiving tubes 1-1, 1-2, 1-3, 1-4 are symmetrical about the luminous tube array 2-1. In this embodiment, the number of the light emitting tube array and the receiving tubes is not limited, and may be expanded according to the described embodiment, and the receiving tubes may be in the form of a structure with a cambered surface and are located at the maximum light intensity ring formed by the light source of the light emitting tube array after being diffusely reflected by the tissue.
The distance between the luminotron arrays 2-1,2-2 and the photoelectric receiving tube 1 can be calculated by simulation, in a static state, when light propagates in human tissues, the light is absorbed, reflected and scattered by tissue layers, and the propagation speed of the light in vacuum is 3 × 108m/s, the thickness of the tissue layer is in the order of mm, so the time for the photons to exit is in the order of ps, and the process can be approximated as a transient process. Lihong Wang and Gardner et al performed Monte Carlo (MC) simulations in the same tissue model, where Lihong Wang et al set the number of samples of photons tracked to 10^6 and Gardner et al selected the number of samples to 10^5, and the results were compared as follows:
TABLE 1 comparison of MC simulation results for three-layer tissue models
| Number of samples | Reflectivity of light | Refractive index | |
| Gardner | 10^5 | 23.81％ | 9.74％ |
| LiHong Wang | 10^6 | 23.75％ | 9.65％ |
| Procedure in this text | 10^6 | 23.70％ | 9.58％ |
The results of the MC simulation are closer to those of the program of LiHong Wang et al, and the results of the MC simulation as a statistical method-based computer simulation method have certain uncertainty, and a small range of errors is generally acceptable. The distribution of photon emission in this model is as follows, notably the light travels via tissue, a banana-shaped path, and finally back to the incident medium.
FIG. 3 shows the radial and axial distribution of diffusely reflected photons with respect to the incident position, and analysis of FIG. 3 reveals that as the detection radius increases, the diffuse reflectance of photons tends to plateau and then decrease, a preliminary analysis being that a large fraction of photons are diffusely reflected by superficial skin tissue without entering the blood-bearing layer; the axially diffuse reflected and transmitted photons exhibit a symmetrical distribution, i.e. the photons emitted straight and horizontally are the least and most of the photons are emitted obliquely, so that the basis for the design of the lenses 5-1,5-2 is also that the direction of the incident angle of the light source is changed. According to the utility model discloses an embodiment, this lens can be convex lens, in the lens design, can design the 3D model at first, establishes light source and observation face, carries out light simulation, and the analysis result is optimized according to the optimization angular direction that makes emergence angle and skin face present 30 ~ 50 (to the receiver tube convergence).
In addition, according to some embodiments of the present application, the reflective type photo sensor module with a controllable array may further include a housing, the light emitting tube array, the photo receiving tube, the light blocking plate and the lens are all disposed inside the housing, and the housing may be slotted above the light emitting tube array, the photo receiving tube and the lens to allow light to pass through.
The basic principles and the main features of the invention and the advantages of the invention have been shown and described above. It will be understood by those skilled in the art that the present invention is not limited to the above embodiments, and that the foregoing embodiments and descriptions are provided only to illustrate the principles of the present invention without departing from the spirit and scope of the present invention. The scope of the invention is defined by the appended claims and equivalents thereof.
Claims (10)
1. A controllable array reflection type photoelectric sensor module is used for detecting physiological signals of a human body and is characterized in that the sensor module comprises a light emitting tube array, a photoelectric receiving tube, a light baffle plate and a lens, wherein the light baffle plate is located between the light emitting tube array and the photoelectric receiving tube, the lens is located on the light emitting tube array, the light emitting tube array is used for emitting light, the light is focused by the lens, transmitted into human body tissues, received by the receiving tube after diffuse reflection and refraction and converted into electric signals, and the light emitting tube array comprises a plurality of light emitting units.
2. The reflective type photo sensor module as claimed in claim 1, wherein each of said light emitting units includes m light sources with different wavelengths, wherein m is a positive integer.
3. The reflective type photo-sensor module as claimed in claim 2, wherein each of said light emitting units includes therein light sources of 3 wavelengths, which are a green light source, a red light source and an infrared light source.
4. The reflective type photo sensor module as claimed in claim 1, wherein the wavelengths of the light emitted from the light emitting units are not identical.
5. The reflective type photoelectric sensor module of claim 1, wherein the array of light emitting diodes comprises n2And each light-emitting unit is provided, wherein n is a positive integer.
6. The controllable array reflective photosensor module of claim 1,
the light emitting tube array is physically symmetrical with respect to the center of the photoelectric receiving tube,
the light emitting unit is physically and spatially symmetrical about the center of the photoelectric receiving tube.
7. The reflective photo sensor module as claimed in claim 1, wherein in the operating state, the wavelength of the light emitted from the light emitting unit is symmetric with respect to the center of the photo receiving tube.
8. The reflective type photo-sensor module as claimed in claim 1, wherein the lens material on the light emitting tube array is a cured glue or glass with good biocompatibility, and the lens is coated with a wavelength-selective film.
9. The reflective type photo-sensor module as claimed in claim 1, wherein the reflective type photo-sensor module comprises a housing, and the light emitting tube array, the photo-receiving tube, the light blocking plate and the lens are all disposed inside the housing.
10. The reflective photosensor module of claim 9, wherein the housing is recessed above the array of light emitting diodes, the photo receiver tubes and the lens to allow light to pass through.
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110367946A (en) * | 2019-08-28 | 2019-10-25 | 杭州兆观传感科技有限公司 | A kind of controllable array reflective photoelectric sensor mould group |
| CN114403823A (en) * | 2022-01-20 | 2022-04-29 | 杭州纳境科技有限公司 | Heart rate blood oxygen detection method and device and wearable device |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110367946A (en) * | 2019-08-28 | 2019-10-25 | 杭州兆观传感科技有限公司 | A kind of controllable array reflective photoelectric sensor mould group |
| CN110367946B (en) * | 2019-08-28 | 2024-08-27 | 杭州兆观传感科技有限公司 | Controllable array reflection type photoelectric sensor module |
| CN114403823A (en) * | 2022-01-20 | 2022-04-29 | 杭州纳境科技有限公司 | Heart rate blood oxygen detection method and device and wearable device |
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