CN108814620A - Flexible physiological information monitoring device - Google Patents
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- CN108814620A CN108814620A CN201810541996.5A CN201810541996A CN108814620A CN 108814620 A CN108814620 A CN 108814620A CN 201810541996 A CN201810541996 A CN 201810541996A CN 108814620 A CN108814620 A CN 108814620A
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- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
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Abstract
本公开涉及一种柔性生理信息监测装置。该装置包括：光源组件，向被检测对象发射光波；光电检测组件，对光波经被检测对象反射后的光信号光电转换，获取第一检测信号；处理组件，对第一检测信号信号处理，获取检测数据；衬底，由柔性材料制成，承载光源组件、光电检测组件和处理组件；光电检测组件包括围绕光源组件布置的多个检测部件，检测部件与光电检测组件之间的距离为使得光信号的光强与光波的光强的比值大于或等于第一阈值的第一距离。根据本公开的实施例，能够通过光电检测组件获得光波经反射后得到检测信号，经信号处理后获取检测数据，通过对检测数据的分析，可实时获取被测对象的生理信息。
The present disclosure relates to a flexible physiological information monitoring device. The device includes: a light source component, which emits light waves to the detected object; a photoelectric detection component, which photoelectrically converts the light signal reflected by the light wave from the detected object, to obtain the first detection signal; and a processing component, which processes the first detection signal and obtains Detection data; the substrate, made of flexible material, carries the light source assembly, the photoelectric detection assembly and the processing assembly; the photoelectric detection assembly includes a plurality of detection components arranged around the light source assembly, and the distance between the detection components and the photoelectric detection assembly is such that the light The ratio of the light intensity of the signal to the light intensity of the light wave is greater than or equal to the first distance of the first threshold. According to the embodiments of the present disclosure, it is possible to obtain a detection signal after light waves are reflected by the photoelectric detection component, and obtain detection data after signal processing. By analyzing the detection data, the physiological information of the measured object can be obtained in real time.
Description
Technical Field
The present disclosure relates to the field of medical detection technology, and in particular, to a flexible physiological information monitoring device.
Background
The detection of physiological information of the human body (for example, the detection of blood oxygen saturation) is an important link in medical treatment. The blood oxygen saturation is one of the most important physiological sign parameters of human body, and has extremely important reference value in the fields of clinical medicine, medical monitoring, medical research and the like. At present, the main means for detecting the blood oxygen saturation is to use a finger-clip type blood oxygen detector, and the detection parts are generally fingers, earlobes and the like.
With the increasing concern of people on their health, wearable medical equipment has a wider demand base, and the health medical equipment becomes a necessary consumer product. Non-invasive blood oxygen sensors are increasingly receiving attention. The existing blood oxygen sensor is based on the near infrared spectrum imaging technology, and in the practical application process, parameters such as blood oxygen, pulse and the like need to be monitored dynamically for a long time when a human body moves. However, since the detection site of the current blood oxygen sensor is limited, the information of blood oxygen in extreme environment cannot be obtained, for example, a pilot needs to dynamically measure the body characteristic parameters in real time in the flight process, but the current blood oxygen monitoring device cannot obtain the blood oxygen information of the pilot in the flight process.
Disclosure of Invention
In view of this, the present disclosure provides a flexible physiological information monitoring device.
According to an aspect of the present disclosure, there is provided a flexible physiological information monitoring device, the device comprising: the device comprises a light source assembly, a photoelectric detection assembly, a processing assembly and a substrate;
the light source component is used for emitting light waves to the detected object;
the photoelectric detection assembly is used for performing photoelectric conversion on an optical signal of the light wave reflected by the detected object to obtain a first detection signal;
the processing component is used for carrying out signal processing on the first detection signal to obtain detection data;
the substrate is made of flexible material and is used for carrying the light source assembly, the photoelectric detection assembly and the processing assembly;
the photoelectric detection assembly comprises a plurality of detection parts arranged around the light source assembly, the distance between the plurality of detection parts and the photoelectric detection assembly is a first distance, and the first distance is a distance which enables the ratio of the light intensity of the optical signal to the light intensity of the light wave to be larger than or equal to a first threshold value.
In one possible implementation, the light source assembly comprises at least two light emitting components, which respectively emit light waves of different central wavelengths or different spectra,
wherein the processing assembly is further configured to control at least two light emitting parts of the light source assembly to emit light in a predetermined order during a light emitting period,
wherein the response interval of the photodetection assembly covers a center wavelength of the light waves emitted by the at least two light emitting components or is within a spectral range of the light waves emitted by the at least two light emitting components.
In one possible implementation, the detecting data includes a blood oxygen saturation level of the detected object, the processing component performs signal processing on the first detecting signal, and acquiring the detecting data includes:
performing analog-to-digital conversion on a plurality of first detection signals of the plurality of detection parts, and performing summation processing to obtain digital detection signals;
carrying out differential operation on the digital detection signals to obtain the blood oxygen saturation of each light-emitting period;
from the blood oxygen saturation level of each light emitting period, the blood oxygen saturation level in the first period is determined.
In one possible implementation, the performing a differential operation on the digital detection signal to obtain the blood oxygen saturation level of each light emitting period includes:
respectively carrying out differential operation on digital detection signals corresponding to the light waves with different central wavelengths or different frequency spectrums according to the light emitting period so as to obtain the relation between the amplitude of the digital detection signals and the concentration of hemoglobin;
and acquiring the blood oxygen saturation of each light-emitting period according to the relation between the amplitude of the digital detection signal and the hemoglobin concentration.
In one possible implementation, determining the blood oxygen saturation level within the first time period from the blood oxygen saturation level of each lighting cycle comprises: an arithmetic average of blood oxygen saturation levels of all light emitting periods within a first period of time is determined as the blood oxygen saturation level of the detected object.
In one possible implementation, the first distance is determined by a monte carlo simulation method.
In a possible implementation manner, the photodetection assembly includes a plurality of detecting parts, and the plurality of detecting parts are all located on a circle that uses the position of the light source assembly as a center and uses the first distance as a radius.
In one possible implementation, the apparatus further includes: and the packaging layer is made of a flexible material, is used for packaging the light source assembly, the photoelectric detection assembly and the processing assembly and is jointed with the flexible substrate.
In one possible implementation, the apparatus further includes: and the receiving and sending component is used for sending the detection data to a terminal and receiving the instruction of the terminal.
In one possible implementation, the device includes a flexible blood oxygen monitoring device integrated into a wearable device to determine the blood oxygen saturation level of the subject.
The flexible physiological information monitoring device according to the aspects of the present disclosure can obtain a detection signal obtained by reflecting light waves emitted from the light source assembly by a body through the photoelectric detection assembly, obtain detection data after performing signal processing through the processing assembly, and obtain physiological information of a measured object, such as blood oxygen saturation and the like, in real time through analysis and processing of the detection data.
Other features and aspects of the present disclosure will become apparent from the following detailed description of exemplary embodiments, which proceeds with reference to the accompanying drawings.
Drawings
The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate exemplary embodiments, features, and aspects of the disclosure and, together with the description, serve to explain the principles of the disclosure.
FIG. 1 is a schematic diagram of a flexible physiological information monitoring device shown in accordance with an exemplary embodiment;
FIG. 2 is a side cutaway view of a flexible physiological information monitoring device shown in accordance with an exemplary embodiment;
FIG. 3 is a flow diagram illustrating signal processing of a first detection signal by a processing component according to an exemplary embodiment;
fig. 4 is a schematic diagram illustrating a flexible blood oxygen monitoring device integrated into a helmet in accordance with an exemplary embodiment.
Detailed Description
Various exemplary embodiments, features and aspects of the present disclosure will be described in detail below with reference to the accompanying drawings. In the drawings, like reference numbers can indicate functionally identical or similar elements. While the various aspects of the embodiments are presented in drawings, the drawings are not necessarily drawn to scale unless specifically indicated.
The word "exemplary" is used exclusively herein to mean "serving as an example, embodiment, or illustration. Any embodiment described herein as "exemplary" is not necessarily to be construed as preferred or advantageous over other embodiments.
Furthermore, in the following detailed description, numerous specific details are set forth in order to provide a better understanding of the present disclosure. It will be understood by those skilled in the art that the present disclosure may be practiced without some of these specific details. In some instances, methods, means, elements and circuits that are well known to those skilled in the art have not been described in detail so as not to obscure the present disclosure.
Fig. 1 is a schematic diagram of a flexible physiological information monitoring device according to an exemplary embodiment. As shown in fig. 1, a physiological information monitoring device according to an embodiment of the present disclosure includes a light source assembly 11, a photodetection assembly 12, a processing assembly 13, and a substrate 14.
The light source assembly 11 is used for emitting light waves to an object to be detected;
the photoelectric detection component 12 is configured to perform photoelectric conversion on an optical signal obtained by reflecting the optical wave by the detected object, and obtain a first detection signal;
the processing component 13 is configured to perform signal processing on the first detection signal to obtain detection data;
the substrate 14 is made of a flexible material for carrying the light source assembly 11, the photodetecting assembly 12 and the processing assembly 13;
the photo detection assembly 12 includes a plurality of detection components disposed around the light source assembly 11, and a distance between the plurality of detection components and the photo detection assembly 11 is a first distance, and the first distance is a distance such that a ratio of the light intensity of the reflected light signal to the light intensity of the light wave emitted by the light source assembly 11 is greater than or equal to a first threshold.
According to the flexible physiological information monitoring device disclosed by the embodiment of the disclosure, a detection signal obtained after light waves emitted by the light source assembly are reflected by a body can be obtained through the photoelectric detection assembly, detection data are obtained after the signal processing is carried out on the detection signal by the processing assembly, and the physiological information of a detected object, such as blood oxygen saturation and the like, can be obtained in real time through the analysis and processing of the detection data.
For example, a flexible physiological information detection device according to an embodiment of the present disclosure may include a flexible blood oxygen detection device. In the related art, the non-invasive blood oxygen detection based on photoelectric characteristics is realized by using the principle of absorptiometry measurement based on the Beer-Lambert law as a theoretical basis. For example, two light sources with different wavelengths can be controlled to alternately emit light, and the generated light waves reach the photoelectric detection assembly after being reflected by the tissue of the detection part (such as forehead and the like). Wherein the total light intensity of the light wave is equal to the sum of the light intensity absorbed by the tissue at the detected part, the transmitted light intensity and the reflected light intensity. The photoelectric detection component detects the intensity of light reflected after being absorbed by human bodies such as hemoglobin and the like, and volume wave signals are obtained. By analyzing and calculating the volume wave signals, physiological information such as pulse and blood oxygen saturation values can be obtained.
In one possible implementation, the light source assembly 11 and the photodetecting assembly 12 are both connected to the processing assembly 13, and in this example, the light source assembly 11 and the photodetecting assembly 12 are both connected to the processing assembly 13 by flexible wires.
FIG. 2 is a side cutaway view of a flexible physiological information monitoring device shown in accordance with an exemplary embodiment. As shown in fig. 2, the flexible physiological information monitoring device further comprises an encapsulation layer 15, wherein the encapsulation layer 15 is made of a flexible material, is used for encapsulating the light source assembly 11, the photoelectric detection assembly 12 and the processing assembly 13, and is combined with the substrate 14. The light source assembly 11, the photodetecting assembly 12 and the processing assembly 13 are disposed on the substrate 14. The substrate 14 may be a double-layer substrate to carry and cover the light source assembly 11, the photodetecting assembly 12, and the processing assembly 13.
In a possible implementation, the light source assembly 11 comprises at least two light emitting parts, which respectively emit light waves of different central wavelengths or different spectra. The light emitting part may be a Light Emitting Diode (LED), a Laser (LD), or the like capable of generating light waves of different wavelengths. In an example, the light source assembly 11 includes a light-emitting part 111 and a light-emitting part 112, the light-emitting part 111 and the light-emitting part 112 are integrated into a single body and may emit light waves of different central wavelengths or different spectra, for example, the light-emitting part 111 may emit light waves of a central wavelength of 620nm, the light-emitting part 112 may emit light waves of a central wavelength near the equal absorption points of oxyhemoglobin and deoxyhemoglobin, for example, the light-emitting part 112 may emit light waves of a central wavelength of 850 nm.
In one possible implementation, the processing assembly 13 is further configured to control at least two light emitting components of the light source assembly 11 to emit light in a predetermined sequence during the light emitting period. In the example, the light emitting part 111 and the light emitting part 112 emit light waves with a center wavelength of 620nm and light waves with a center wavelength of 850nm in sequence within a light emitting period of 1 ms. The lighting period can also be shorter, so that the two light-emitting components can emit light more closely at the same time, and the photoelectric detection component can detect the reflected light signals more closely at the same time.
In an embodiment of the present disclosure, the response interval of the photodetecting assembly 12 covers the center wavelength of the light waves emitted by the at least two light emitting components or is within the spectral range of the light waves emitted by the at least two light emitting components. In an example, all of the detection components of the photodetection assembly 12 may use silicon-based photodetectors having response wavelengths of 400nm-1100 nm. The light waves are reflected by the object to be detected and are received by the photo detection assembly 12 arranged around the light source assembly 11.
In a possible implementation manner, the photoelectric detection assembly 12 includes a plurality of detection components, the plurality of detection components are arranged around the light source assembly 11, a distance between each photoelectric detection component and the light source assembly 11 is a first distance, the first distance is determined by a monte carlo simulation method, when the distance between the light source assembly 11 and the detection components is the first distance, a ratio of light intensity of the light signal reflected by the detected object to light intensity of the light wave emitted by the light source assembly 11 is greater than a first threshold, that is, under the condition that the light intensity of the light wave emitted by the light source assembly 11 is constant, the light intensity of the light signal received by the detection components can meet detection requirements.
In one possible implementation, the monte carlo simulation method is one of the effective mathematical methods for simulating the transmission of photons in biological tissues, and is a statistical calculation method for simulating the random walking of photons in the biological tissues. To effectively reflect the real characteristics of biological tissue, a multi-layered biological tissue model can be used to simulate the situation of light transmission. The light beam is incident perpendicularly to the surface of the biological tissue, and the specular reflection and transmission occur at the upper and lower surfaces of the air and the tissue, for example, the transmission and specular reflection occur at the interface of the ith layer and the (i + 1) th layer, and photons are absorbed and scattered inside the biological tissue. In an example, the step length of the random walking of the photons in the biological tissue can be set, and the approximate path of the random walking of the photons can be simulated, so that the position at which the light intensity of the received reflected light wave is strongest can be obtained. In the example, the intensity of the reflected light waves is strongest at a distance of between 8mm and 1cm from the light source assembly 11.
In an example, the first distance may be 1cm, which is an intensity determined by the monte carlo simulation method to maximize a ratio of the intensity of the reflected light signal to the intensity of the light wave emitted from the light source assembly 11. The present disclosure does not limit the specific value of the first distance.
In one possible implementation manner, the plurality of detecting parts may be located on a circle with the position of the light source assembly 11 as a center and the first distance as a radius. In the example, the photodetection assembly 12 includes 4 detecting parts (detecting part 121, detecting part 122, detecting part 123, and detecting part 124), the 4 detecting parts are each located on a circle having a radius of 1cm centered on the position of the light source assembly 11, and the 4 detecting parts form 4 vertices of a rectangle on which the light source assembly 11 is located on a diagonal line. It should be understood that the number of the detecting components and the arrangement positions thereof can be set by those skilled in the art according to actual needs, and the disclosure is not limited thereto.
In the embodiment of the present disclosure, the processing component 13 may perform signal processing, storage and transmission on the plurality of first detection signals of the plurality of detection parts.
Fig. 3 is a flow chart illustrating signal processing of the first detection signal by the processing component 13 according to an exemplary embodiment. In the embodiment of the present disclosure, the detection data may be the blood oxygen saturation level of the detected object, the processing component 13 performs signal processing on the first detection signal, and acquiring the detection data includes:
in step S31, a plurality of first detection signals of the plurality of detection parts are subjected to analog-to-digital conversion and subjected to summation processing to obtain digital detection signals;
in step S32, a difference operation is performed on the digital detection signal to acquire a blood oxygen saturation level for each light emission period;
in step S33, the blood oxygen saturation level in the first period is determined from the blood oxygen saturation level of each light emitting cycle.
In one possible implementation manner, in step S31, the first detection signal may be a voltage signal, and the digital detection signal may be directly obtained after performing analog-to-digital conversion on the voltage signal. The first detection signal may also be a current signal, and the current signal may be converted into a voltage signal and then subjected to analog-to-digital conversion to obtain a digital detection signal. In addition, the voltage signal can be filtered and then subjected to analog-to-digital conversion.
In a possible implementation manner, the light source assembly 11 may include two light emitting components, where the two light emitting components sequentially emit light waves with different central wavelengths or different frequency spectrums within a light emitting period, the photodetection assembly 12 may include a plurality of detecting components, where the plurality of detecting components sequentially detect reflected light waves with different central wavelengths or different frequency spectrums within the light emitting period, and the processing assembly 13 may perform summation processing after performing analog-to-digital conversion on first detection signals detected by the plurality of detecting components, so as to obtain digital detection signals of light waves with different central wavelengths or different frequency spectrums within the light emitting period.
For example, the light emitting part 111 first emits light having a center wavelength λ during a light emitting period1After the reflected light waves are reflected, the plurality of detecting components detect the reflected light waves and respectively form first detecting signals, and the processing component 13 performs analog-to-digital conversion on all the first detecting signals and then performs summation processing to obtain the light waves with the central wavelength of lambda1Corresponding to the light wave of (a). Similarly, in the light emitting period, after the light emitting part 111 finishes emitting light, the light emitting part 112 emits light with the central wavelength λ2The processing component 13 obtains the light wave with the central wavelength lambda according to the processing method2Corresponding to the light wave of (a).
In one possible implementation, step S32 may include:
in step S321, performing differential operation on the digital detection signals corresponding to the light waves with different central wavelengths or different frequency spectrums according to the light emitting period to obtain a relationship between the amplitude of the digital detection signal and the hemoglobin concentration;
in step S322, the blood oxygen saturation level for each light emitting period is acquired from the relationship between the amplitude of the digital detection signal and the hemoglobin concentration.
In one possible implementation manner, in step S321, a differential operation may be performed on the digital detection signal. In the example, the k-th lighting period tkHas a digital detection signal amplitude of R (t)k) The (k + 1) th light emitting period tk+1Has a digital detection signal amplitude of R (t)k+1) After taking the natural logarithm of the amplitudes of the two digital detection signals, the difference operation is performed according to the following equation (1):
wherein, A (t)k+1)＝ln R(tk+1)，A(tk)＝lnR(tk)，tkAt the beginning of the kth lighting period, tk+1At the start of the (k + 1) th lighting period, muaAnd c is the absorption coefficient, i.e., the probability of a photon being absorbed in a unit path, and the speed of light.
In one possible implementation, only oxyhemoglobin (HbO) may be considered in measuring blood oxygen saturation2) And a deoxyhemoglobin (Hb) content, the hemoglobin concentration may include an oxyhemoglobin concentrationAnd the deoxyhemoglobin concentration CHb. Equation (1) can therefore be written as the following equation (2):
wherein, Delta Ak＝A(tk+1)-A(tk)，Δtk＝tk+1-tk， Is the extinction coefficient, epsilon, of oxyhaemoglobinHbIs the extinction coefficient of deoxyhemoglobin.
In a possible implementation manner, according to the above equation (2), the digital detection signals corresponding to the light waves with different central wavelengths or different frequency spectrums are respectively subjected to difference operation according to the light emitting period, so that the relationship between the amplitude of the digital detection signal corresponding to the light wave with the central wavelength or different frequency spectrums and the hemoglobin concentration can be obtained.
In one possible implementation, the center wavelength is λ based on equation (2) above1The digital detection signal corresponding to the light wave is subjected to differential operation to obtain the central wavelength lambda1The relationship (3) between the digital detection signal corresponding to the light wave and the hemoglobin concentration:
in one possible implementation, the center wavelength is λ based on equation (2) above2The digital detection signal corresponding to the light wave is subjected to differential operation to obtain the central wavelength lambda2The relationship (4) between the digital detection signal corresponding to the light wave of (a) and the hemoglobin concentration:
in one possible implementation, the blood oxygen saturation may be represented by the following equation (5):
wherein, SpO2Is the blood oxygen saturation.
Therefore, in step S322, the blood oxygen saturation level SpO of the kth light emitting period may be obtained according to equation (3) and equation (4)2(k)，SpO2(k) Can be expressed according to the following equation (6):
wherein,
in one possible implementation, when the center wavelength λ2For equal absorption points of oxyhemoglobin and deoxyhemoglobin, equation (6) can be approximated as the following equation (7):
according to the difference operation described in step S32, when the difference operation is performed on the digital detection signals of the (k + 1) th lighting period and the (k) th lighting period, uniform noise in the signals can be eliminated, so that the detection data of effective physiological information can be extracted from the noise, and the interference of relative motion noise between the photoelectric detection assembly 11 and the detected object can be eliminated.
In one possible implementation, in step S33, an arithmetic average of the blood oxygen saturation levels of all light emitting periods within the first period of time may be determined as the blood oxygen saturation level of the detected subject. Calculating the arithmetic average of the blood oxygen saturation levels of all the lighting periods in the first time period can eliminate the influence of possible misalignment of single measurement, and improve the measurement accuracy of the blood oxygen saturation levels in the first time period. In an example, the first time period includes N lighting periods, i.e., k has a value ranging from 1, 2, …, N, depending on the number of lighting periodsThe following equation (8) to determine the N SpOs2(k) As the oxygen saturation level of blood in the first time period
In one possible implementation, the first time period may be a cardiac cycle. In an example, the heart rate of the detected subject is 60 times/minute, i.e. the heart beats once per second, the cardiac cycle is 1 second. The lighting period may be 1ms, and the first period may include 1000 lighting periods, i.e., N1000. In an example, the oxygen saturation of blood within the first time periodMay be SpO2(1)、SpO2(2)、…、SpO2(1000) Is calculated as the average of the counts.
In one possible implementation, the first time period may contain a plurality of cardiac cycles. Determining blood oxygen saturation for a first period of timeIn the meantime, the blood oxygen saturation of each cardiac cycle can be calculated, and then the arithmetic mean value of the blood oxygen saturation of each cardiac cycle can be calculated, or the arithmetic mean value of the blood oxygen saturation of all the lighting cycles in the first time period can be directly calculated.
In an example, the cardiac cycle of the detected subject may be 1 second, the illumination period may be 1ms, and the first time period may comprise 3 cardiac cycles. The oxygen saturation for the cardiac cycle may be an arithmetic average of the oxygen saturation for 1000 light cycles within the cardiac cycle and the oxygen saturation for the first time period may be an arithmetic average of the oxygen saturation for 3 cardiac cycles. The blood oxygen saturation level in the first period may also be an arithmetic average of the blood oxygen saturation levels of 3000 light emitting cycles in the first period. The above two methods of calculating the arithmetic average value of the blood oxygen saturation of the light emitting period in the first period are equivalent. The present disclosure is not limited to the method of calculating the arithmetic mean.
In a possible implementation manner, the processing component 13 may be any processing device capable of performing signal processing, such as a single chip, a CPU, an MPU, and an FPGA, and the processing component 13 may be implemented by a dedicated hardware circuit, or by a general-purpose processing component in combination with executable logic instructions to perform the processing procedure of the processing component 13.
According to an embodiment of the present disclosure, the flexible physiological information monitoring device further comprises a power supply component, which can provide power for the processing component 13 and the light source component 11, and can also provide power for the photoelectric detection component 12 if the photoelectric detection component 12 needs to supply power.
In a possible implementation manner, the flexible physiological information monitoring device may further include a transceiver device, and the transceiver device may establish a communication connection with a terminal (e.g., a smart phone, etc.) in a bluetooth manner, an infrared manner, a wireless fidelity (WIFI) manner, and the like, so as to implement communication between the luminous flux detection device and the terminal.
The transceiver can send the detection data to the terminal for the terminal to record, process and analyze. At the same time, the transceiver device may also receive instructions from the terminal, causing the processing component 13 to execute the instructions.
In an embodiment of the present disclosure, the flexible physiological information monitoring device may further include a storage component, which may be configured to store the detection data and export the stored records of the detection data in batches when needed. Furthermore, the power supply assembly, the transceiver assembly and the memory assembly may be connected to the processing assembly 13 by flexible wires, or may be integrated in the processing assembly 13.
According to the embodiment of the present disclosure, the substrate 14 for carrying the light source assembly 11, the photodetection assembly 12 and the processing assembly 13 is made of a flexible material, and can be attached to the skin or integrated in a wearable device, in an example, the flexible physiological information monitoring device can be used as a flexible blood oxygen monitoring device, which can be attached to the skin or integrated in a wearable device, and the blood oxygen saturation can be determined according to the detected data, and the interference to the measured object is small, and the device can be used for a long time.
Fig. 4 is a schematic diagram illustrating a flexible blood oxygen monitoring device integrated into a helmet in accordance with an exemplary embodiment. In an embodiment of the present disclosure, the flexible blood oxygen monitoring device is integrated into a helmet, which may be a helmet of a pilot, that monitors the oxygen saturation of blood of the pilot during the pilot's driving of the aircraft.
In an example, the flexible blood oxygen monitoring device is fixed in a special lining fixed on a helmet, the size and the shape of the forehead of a pilot are different, and in order to reduce the loss in light wave transmission, the lining can be made of a biocompatible material with elasticity so as to be matched with the forehead of the pilot. A window with proper size is opened at the light transmitting position required by the light source component and the photoelectric detection component, so that light waves emitted by the light source component are incident to the forehead of a pilot with low loss, and light signals reflected by the forehead of the pilot are received by the photoelectric detection component to obtain detection signals. The processing component carries out signal processing on the detection signal of the photoelectric detection component to obtain detection data, so that the blood oxygen saturation of the pilot is determined according to the detection data.
The processing component can extract a periodic volume wave signal submerged by external environment interference (such as noise interference generated by a pilot during movement and noise interference generated by relative displacement between the detection device and human skin), so that the flexible blood oxygen monitoring device can effectively remove the noise interference in a working state and improve the detection precision of the blood oxygen saturation. In addition, the flexible blood oxygen monitoring device can comprise a transceiver, and the blood oxygen saturation information of the pilot can be transmitted to the main control console through the transceiver so as to provide reference for evaluating the physiological parameters of the pilot. The flexible blood oxygen monitoring device can also directly send the detection data to the main control console, and the main control console can determine the blood oxygen saturation degree of the pilot according to the detection data.
Through adopting this disclosed embodiment, can effectively integrate flexible physiological information monitoring devices to pilot's helmet in, carry out real-time monitoring to pilot's blood oxygen information in flight process to filtering noise interference acquires accurate oxyhemoglobin saturation information. The receiving and transmitting assembly is in wireless connection with the main control console, so that the main control console can master the physiological information of the pilot in real time, and corresponding evaluation is made for the physiological index of the pilot. The physiological information detection device has little interference to the pilot, and can continuously monitor the pulse wave blood oxygen saturation for a long time in the flight of the pilot, so that the main control console can obtain the physiological information of the pilot in real time.
Having described embodiments of the present disclosure, the foregoing description is intended to be exemplary, not exhaustive, and not limited to the disclosed embodiments. Many modifications and variations will be apparent to those of ordinary skill in the art without departing from the scope and spirit of the described embodiments. The terminology used herein is chosen in order to best explain the principles of the embodiments, the practical application, or technical improvements to the technology in the marketplace, or to enable others of ordinary skill in the art to understand the embodiments disclosed herein.
Claims (10)
1. A flexible physiological information monitoring device, comprising: the device comprises a light source assembly, a photoelectric detection assembly, a processing assembly and a substrate;
the light source component is used for emitting light waves to the detected object;
the photoelectric detection assembly is used for performing photoelectric conversion on an optical signal of the light wave reflected by the detected object to obtain a first detection signal;
the processing component is used for carrying out signal processing on the first detection signal to obtain detection data;
the substrate is made of flexible material and is used for carrying the light source assembly, the photoelectric detection assembly and the processing assembly;
the photoelectric detection assembly comprises a plurality of detection parts arranged around the light source assembly, the distance between the plurality of detection parts and the photoelectric detection assembly is a first distance, and the first distance is a distance which enables the ratio of the light intensity of the optical signal to the light intensity of the light wave to be larger than or equal to a first threshold value.
2. The apparatus of claim 1, wherein the light source assembly comprises at least two light emitting components that respectively emit light waves of different center wavelengths or different frequency spectra,
wherein the processing assembly is further configured to control at least two light emitting parts of the light source assembly to emit light in a predetermined order during a light emitting period,
wherein the response interval of the photodetection assembly covers a center wavelength of the light waves emitted by the at least two light emitting components or is within a spectral range of the light waves emitted by the at least two light emitting components.
3. The apparatus of claim 2, wherein the detection data comprises a blood oxygen saturation level of the subject, the processing component performs signal processing on the first detection signal, and obtaining the detection data comprises:
performing analog-to-digital conversion on a plurality of first detection signals of the plurality of detection parts, and performing summation processing to obtain digital detection signals;
carrying out differential operation on the digital detection signals to obtain the blood oxygen saturation of each light-emitting period;
from the blood oxygen saturation level of each light emitting period, the blood oxygen saturation level in the first period is determined.
4. The apparatus of claim 3, wherein differentiating the digital detection signal to obtain the blood oxygen saturation level for each light emitting period comprises:
respectively carrying out differential operation on digital detection signals corresponding to the light waves with different central wavelengths or different frequency spectrums according to the light emitting period so as to obtain the relation between the amplitude of the digital detection signals and the concentration of hemoglobin;
and acquiring the blood oxygen saturation of each light-emitting period according to the relation between the amplitude of the digital detection signal and the hemoglobin concentration.
5. The apparatus of claim 3, wherein determining the oxygen saturation level for the first time period based on the oxygen saturation level for each of the lighting cycles comprises:
an arithmetic average of blood oxygen saturation levels of all light emitting periods within a first period of time is determined as the blood oxygen saturation level of the detected object.
6. The apparatus of claim 1, wherein the first distance is determined by a monte carlo simulation method.
7. The apparatus of claim 1, wherein the photo detection assembly comprises a plurality of detection members, each of the plurality of detection members being located on a circle centered on the position of the light source assembly and having a radius of the first distance.
8. The apparatus of claim 1, further comprising: and the packaging layer is made of a flexible material, is used for packaging the light source assembly, the photoelectric detection assembly and the processing assembly and is jointed with the flexible substrate.
9. The apparatus of claim 1, further comprising: and the receiving and sending component is used for sending the detection data to a terminal and receiving the instruction of the terminal.
10. The device of any one of claims 1-9, wherein the device comprises a flexible blood oxygen monitoring device integrated into a wearable device for determining the oxygen saturation level of blood of the subject.
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Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110680342A (en) * | 2019-10-29 | 2020-01-14 | 成都智达和创信息科技有限公司 | Multispectral receiving and transmitting integrated sensor and non-contact type nondestructive blood glucose meter |
| CN110811639A (en) * | 2019-11-06 | 2020-02-21 | 浙江清华柔性电子技术研究院 | Total bilirubin detection patch and total bilirubin detection system |
| CN110974249A (en) * | 2019-12-13 | 2020-04-10 | 华中科技大学 | An epidermis-attached blood oxygen saturation detection system and its preparation |
| WO2020078287A1 (en) * | 2018-10-19 | 2020-04-23 | 杰能科技顾问有限公司 | Solar detection module and solar panel |
| CN112842365A (en) * | 2021-02-25 | 2021-05-28 | 清华大学 | Detection device and manufacturing method thereof |
| CN114468993A (en) * | 2021-02-11 | 2022-05-13 | 先阳科技有限公司 | Tissue component measuring method and device and wearable equipment |
| CN114468990A (en) * | 2021-02-11 | 2022-05-13 | 先阳科技有限公司 | Method, device and wearable device for detecting the composition of living tissue |
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| CN114916908A (en) * | 2021-02-11 | 2022-08-19 | 先阳科技有限公司 | Tissue component measuring method and device based on Raman spectrum and wearable equipment |
| CN116584930A (en) * | 2023-05-17 | 2023-08-15 | 西北工业大学 | A flexible heart rate blood oxygen monitoring system and preparation method thereof |
| CN116616701A (en) * | 2022-02-11 | 2023-08-22 | 中国科学院上海技术物理研究所 | A differential spectral sensor built into earphones and wearable devices |
| WO2025156356A1 (en) * | 2024-01-24 | 2025-07-31 | 深圳金亿帝医疗设备股份有限公司 | Sensor for non-invasive photoelectric reflection-based physiological parameter measurement and wearable device |
Citations (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN201481424U (en) * | 2009-09-03 | 2010-05-26 | 深圳市索莱瑞医疗技术有限公司 | Forehead type blood oxygen saturation probe |
| WO2013166463A1 (en) * | 2012-05-03 | 2013-11-07 | Vioptix, Inc. | Monte carlo and iterative methods for determination of tissue oxygen saturation |
| CN103610467A (en) * | 2013-11-05 | 2014-03-05 | 李鲁亚 | Parallel near-infrared photoelectric sensing device and system and method for detecting organs and tissue of animals |
| CN104173059A (en) * | 2014-09-04 | 2014-12-03 | 电子科技大学 | Optical non-intrusive shock monitor and detection method thereof |
| US8956289B2 (en) * | 2005-10-14 | 2015-02-17 | Konica Minolta Sensing, Inc. | Vital information measuring device |
| WO2016035881A1 (en) * | 2014-09-05 | 2016-03-10 | パナソニックヘルスケアホールディングス株式会社 | Method for quantifying glucose concentration and glucose concentration measurement device |
| CN105510238A (en) * | 2014-09-28 | 2016-04-20 | 天津先阳科技发展有限公司 | Multi-position diffusion spectral data processing, modeling, and predicting method and processing device |
| CN106137219A (en) * | 2016-08-04 | 2016-11-23 | 天津大学 | The absolute difference of dual wavelength adds and calculates arterial oxygen saturation method and device thereof |
| CN106798549A (en) * | 2017-02-27 | 2017-06-06 | 清华大学 | A kind of blood oxygen transducer based on flexible extending substrate |
| CN206414278U (en) * | 2016-08-23 | 2017-08-18 | 公安部第一研究所 | A kind of blood oxygen detection means |
| WO2018066519A1 (en) * | 2016-10-03 | 2018-04-12 | 国立大学法人大阪大学 | Electrode sheet |
-
2018
- 2018-05-30 CN CN201810541996.5A patent/CN108814620A/en active Pending
Patent Citations (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US8956289B2 (en) * | 2005-10-14 | 2015-02-17 | Konica Minolta Sensing, Inc. | Vital information measuring device |
| CN201481424U (en) * | 2009-09-03 | 2010-05-26 | 深圳市索莱瑞医疗技术有限公司 | Forehead type blood oxygen saturation probe |
| WO2013166463A1 (en) * | 2012-05-03 | 2013-11-07 | Vioptix, Inc. | Monte carlo and iterative methods for determination of tissue oxygen saturation |
| CN104411241A (en) * | 2012-05-03 | 2015-03-11 | 维奥普蒂克斯公司 | Tissue oximetry probe geometry for robust calibration and self-correction |
| CN103610467A (en) * | 2013-11-05 | 2014-03-05 | 李鲁亚 | Parallel near-infrared photoelectric sensing device and system and method for detecting organs and tissue of animals |
| CN104173059A (en) * | 2014-09-04 | 2014-12-03 | 电子科技大学 | Optical non-intrusive shock monitor and detection method thereof |
| WO2016035881A1 (en) * | 2014-09-05 | 2016-03-10 | パナソニックヘルスケアホールディングス株式会社 | Method for quantifying glucose concentration and glucose concentration measurement device |
| CN105510238A (en) * | 2014-09-28 | 2016-04-20 | 天津先阳科技发展有限公司 | Multi-position diffusion spectral data processing, modeling, and predicting method and processing device |
| CN106137219A (en) * | 2016-08-04 | 2016-11-23 | 天津大学 | The absolute difference of dual wavelength adds and calculates arterial oxygen saturation method and device thereof |
| CN206414278U (en) * | 2016-08-23 | 2017-08-18 | 公安部第一研究所 | A kind of blood oxygen detection means |
| WO2018066519A1 (en) * | 2016-10-03 | 2018-04-12 | 国立大学法人大阪大学 | Electrode sheet |
| CN106798549A (en) * | 2017-02-27 | 2017-06-06 | 清华大学 | A kind of blood oxygen transducer based on flexible extending substrate |
Non-Patent Citations (6)
| Title |
|---|
| LI, HAICHENG等: "Epidermal inorganic optoelectronics for blood oxygen measurement", 《ADVANCED HEALTHCARE MATERIALS》 * |
| MICHAEL S. PATTERSON: "Time resolved reflectance and transmittance for the noninvasive measurement of tissue optical properties", 《APPLIED OPTICS》 * |
| 孙喜庆，等: "《重力生理学理论与实践》", 31 January 2009 * |
| 李婷: "《生物医学光子传输》", 30 April 2015, 武汉大学出版社 * |
| 王伟，等: "基于差分因子的血氧饱和度算法研究", 《科技视界》 * |
| 王荣芳: "反射式血氧饱和度检测系统的研制", 《中国优秀硕士学位论文全文数据库 信息科技辑》 * |
Cited By (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2020078287A1 (en) * | 2018-10-19 | 2020-04-23 | 杰能科技顾问有限公司 | Solar detection module and solar panel |
| CN110680342A (en) * | 2019-10-29 | 2020-01-14 | 成都智达和创信息科技有限公司 | Multispectral receiving and transmitting integrated sensor and non-contact type nondestructive blood glucose meter |
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| CN110974249A (en) * | 2019-12-13 | 2020-04-10 | 华中科技大学 | An epidermis-attached blood oxygen saturation detection system and its preparation |
| CN114468990A (en) * | 2021-02-11 | 2022-05-13 | 先阳科技有限公司 | Method, device and wearable device for detecting the composition of living tissue |
| CN114468993A (en) * | 2021-02-11 | 2022-05-13 | 先阳科技有限公司 | Tissue component measuring method and device and wearable equipment |
| CN114468989A (en) * | 2021-02-11 | 2022-05-13 | 先阳科技有限公司 | Tissue component measuring method and device and wearable equipment |
| CN114916908A (en) * | 2021-02-11 | 2022-08-19 | 先阳科技有限公司 | Tissue component measuring method and device based on Raman spectrum and wearable equipment |
| CN114468993B (en) * | 2021-02-11 | 2023-03-10 | 先阳科技有限公司 | Tissue composition measurement method, device and wearable device |
| CN112842365A (en) * | 2021-02-25 | 2021-05-28 | 清华大学 | Detection device and manufacturing method thereof |
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| CN116584930A (en) * | 2023-05-17 | 2023-08-15 | 西北工业大学 | A flexible heart rate blood oxygen monitoring system and preparation method thereof |
| WO2025156356A1 (en) * | 2024-01-24 | 2025-07-31 | 深圳金亿帝医疗设备股份有限公司 | Sensor for non-invasive photoelectric reflection-based physiological parameter measurement and wearable device |
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