WO2022252535A1 - Dispositif de mesure de paramètre physiologique, terminal et procédé - Google Patents

Dispositif de mesure de paramètre physiologique, terminal et procédé Download PDF

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WO2022252535A1
WO2022252535A1 PCT/CN2021/136061 CN2021136061W WO2022252535A1 WO 2022252535 A1 WO2022252535 A1 WO 2022252535A1 CN 2021136061 W CN2021136061 W CN 2021136061W WO 2022252535 A1 WO2022252535 A1 WO 2022252535A1
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polarization mode
light
polarization
mode
measured
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PCT/CN2021/136061
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English (en)
Chinese (zh)
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周勇
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深圳市脉度科技有限公司
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Priority to CN202180006565.9A priority Critical patent/CN114786577A/zh
Publication of WO2022252535A1 publication Critical patent/WO2022252535A1/fr

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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
    • A61B5/02—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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/02108—Measuring pressure in heart or blood vessels from analysis of pulse wave characteristics
    • 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
    • A61B5/0062—Arrangements for scanning
    • A61B5/0064—Body surface scanning
    • 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
    • A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
    • 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
    • A61B5/021—Measuring pressure in heart or blood vessels
    • 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
    • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
    • 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
    • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
    • A61B5/02416—Detecting, measuring or recording pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation
    • 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
    • A61B5/024—Detecting, measuring or recording pulse rate or heart rate
    • A61B5/02416—Detecting, measuring or recording pulse rate or heart rate using photoplethysmograph signals, e.g. generated by infrared radiation
    • A61B5/02427—Details of sensor
    • 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
    • A61B5/026—Measuring blood flow
    • A61B5/0261—Measuring blood flow using optical means, e.g. infrared light
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14546—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring analytes not otherwise provided for, e.g. ions, cytochromes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
    • A61B5/14552—Details of sensors specially adapted therefor

Definitions

  • the present application relates to the technical field of intelligent terminals, and in particular to a physiological parameter measurement device, terminal and method.
  • An optical blood measurement device generally includes a transmitting end and a detecting end, and is attached to a part of the user's body such as the wrist, finger, ear, forehead, cheek or eyeball, and the optical radiation is transmitted into this part of the body or passed through the body by the emitting end.
  • This part is reflected, and then the light attenuated by this part of the body is detected by the detection end to obtain a measurement signal.
  • These measurement signals can be used to analyze and determine physiological parameters such as blood oxygen saturation and pulse.
  • Optical-based blood measurement techniques rely on the principle that light passing through that part of the body can be absorbed, reflected or refracted causing attenuation.
  • this part of the body includes components such as skin, muscle, bone, fat, pigment, etc., and the attenuation of light due to these components is usually constant or considered to be basically constant during the measurement period, while blood vessels, especially arterial vessels The flow of blood in it causes changes in the attenuation of light.
  • the measurement signal can be divided into a time-invariant direct current (DC) signal and a time-varying alternating current (Alternating Current, AC) signal.
  • DC direct current
  • AC Alternating Current
  • PPG Photoplethysmography
  • pulse oximetry Pulse Oximetry
  • Pulse Oximetry uses the principle that the amount of light absorbed by arterial blood changes with the pulse of the artery, and measures blood oxygen saturation by detecting changes in the amount of light absorbed by blood, that is, the amount of oxygen in the blood
  • the volume of bound oxyhemoglobin as a percentage of the total volume of bound hemoglobin.
  • the ratio of the AC signal to the DC signal in the measurement signal is often very low, for example, the AC/DC ratio at the wrist is generally less than 1/1000.
  • the ratio of AC signals based on light reflected from blood vessels relative to DC signals based on light reflected from other components is very low.
  • factors such as background noise, electronic circuit disturbances, and device state shifts can also negatively affect the measurement results, especially in the case of low SNR.
  • the AC signal can be enhanced by increasing the intensity of the emitted light and increasing the sensitivity of the detector, but this will also enhance the DC signal while enhancing the AC signal, which increases the noise component in the measurement signal. To do this, it is necessary to increase the AC/DC ratio or increase the strength of the AC signal relative to the DC signal.
  • U.S. Patent No. 10813578 discloses that a reflector is arranged between the light source and the photodetector, and the reflector is used to reduce the light reflected to the photodetector through the non-perfusion layer such as the skin surface while increasing the optical path length in the perfusion layer such as blood vessels.
  • US patent US 10537270 discloses that a certain angle is formed between the light irradiation direction of the light source and the detection direction of the photodetector, thereby reducing the light reflected to the photodetector through the non-perfusion layer and increasing the optical path length in the perfusion layer.
  • the implementation of these prior art solutions involves complex structure and fine optical direction design, and it is difficult to adjust according to actual needs after the product leaves the factory, which is not conducive to large-scale applications such as adding to smart wearable devices.
  • non-invasive measurement technology can also obtain other physiological parameters relevant to the human body by means of optical measurement, such as pigmentation and distribution on the skin.
  • other physiological parameters relevant to the human body such as pigmentation and distribution on the skin.
  • a solution is needed that can effectively measure the physiological parameters of the user's body, such as blood parameters and pigment distribution, and has a good SNR and AC/DC ratio, and the structure is simple and easy to adjust. It can be applied, for example, in close proximity Smart wearable devices such as smart watches, smart bracelets, etc. on the user's wrist.
  • an embodiment of the present application provides a device for measuring a physiological parameter.
  • the physiological parameter measurement device includes: a transmitting module, wherein the transmitting module is configured to emit light of one or more wavelengths, wherein the light emitted by the transmitting module satisfies a first polarization mode and illuminates the target to be measured; A detection module, wherein the detection module is configured to filter light reflected by the measured object, wherein the light filtered by the detection module satisfies a second polarization mode; and a processor.
  • the processor is configured to determine the difference between the second polarization mode and the first polarization mode according to the physiological parameter to be measured of the measured target and the wavelength of the light emitted by the transmitting module A measurement signal is thereby optimized which is based on the light filtered by the detection module and which is used to determine the physiological parameter to be measured.
  • the technical solution described in the first aspect selectively enhances the influence of reflected light at a specific depth of the skin on the measurement signal through the filtering method based on the polarization mode, so as to facilitate obtaining physiological parameters related to the specific depth through the measurement signal.
  • the embodiment of the present application provides a method for measuring a physiological parameter.
  • the method includes: emitting light of one or more wavelengths through a transmitting module, wherein the light emitted by the emitting module satisfies a first polarization mode and irradiates the measured target; filtering the measured target through a detection module The reflected light, wherein the light filtered by the detection module satisfies a second polarization mode; and obtaining a measurement signal based on the light filtered by the detection module.
  • the measurement signal is used to determine the physiological parameter to be measured of the measured target.
  • the difference between the second polarization mode and the first polarization mode is determined according to the physiological parameter to be measured and the wavelength of the light emitted by the transmitting module, so as to optimize the measurement signal.
  • the technical solution described in the second aspect selectively enhances the influence of reflected light at a specific depth of the skin on the measurement signal through the filtering method based on the polarization mode, so as to facilitate obtaining physiological parameters related to the specific depth through the measurement signal.
  • the embodiment of the present application provides a physiological parameter measurement terminal.
  • the physiological parameter measurement terminal includes: a transmitting module, wherein the transmitting module is configured to emit light of one or more wavelengths, wherein the light emitted by the transmitting module satisfies the first polarization mode and illuminates the measured target;
  • the first detection module wherein the first detection module is configured to filter the light reflected by the measured object, wherein the light filtered by the first detection module satisfies the first polarization analysis mode, and the first measurement A signal is determined based on the light filtered by the first detection module; and a second detection module.
  • the second detection module is configured to filter the light reflected by the measured object, wherein the light filtered by the second detection module satisfies the second polarization analysis mode, and the second measurement signal is based on the The light filtered by the second detection module is determined.
  • the difference between the first polarization analysis mode and the first polarization mode is different from the difference between the second polarization analysis mode and the first polarization mode.
  • the technical solution described in the third aspect selectively enhances the influence of reflected light at a specific depth of the skin on the measurement signal through the filtering method based on the polarization mode, so as to facilitate obtaining physiological parameters related to the specific depth through the measurement signal.
  • the embodiment of the present application provides a physiological parameter measurement terminal.
  • the physiological parameter measurement terminal includes: a first emitting module, wherein the first emitting module is configured to emit light of a first wavelength, wherein the light emitted by the first emitting module satisfies a first polarization mode and illuminates The target to be measured; a second emitting module, wherein the second emitting module is configured to emit light of a second wavelength, wherein the light emitted by the second emitting module satisfies a second polarization mode and illuminates the detection target; and detection module.
  • the detection module is configured to filter the light reflected by the measured object, wherein the light filtered by the detection module satisfies the first polarization analysis mode. Wherein, the difference between the first polarization analysis mode and the first polarization mode is different from the difference between the first polarization analysis mode and the second polarization mode.
  • the technical solution described in the fourth aspect selectively enhances the influence of reflected light at a specific depth of the skin on the measurement signal through the filtering method based on the polarization mode, so as to facilitate obtaining physiological parameters related to the specific depth through the measurement signal.
  • the embodiment of the present application provides a physiological parameter measurement terminal.
  • the physiological parameter measurement terminal includes: a first emitting module, wherein the first emitting module is configured to emit light of one or more wavelengths, wherein the light emitted by the first emitting module satisfies the first polarization mode and irradiate the measured target; a second emitting module, wherein the second emitting module is configured to emit light of one or more wavelengths, wherein the light emitted by the second emitting module satisfies the second polarization mode and Illuminating the measured target; a first detection module, wherein the first detection module is configured to filter light reflected by the measured target, wherein the light filtered by the first detection module satisfies the first A polarization analysis mode; and a second detection module, wherein the second detection module is configured to filter the light reflected by the measured object, wherein the light filtered by the second detection module satisfies the second polarization analysis model.
  • the first polarization analysis mode matches
  • the technical solution described in the fifth aspect selectively enhances the influence of reflected light at a specific depth of the skin on the measurement signal through the filtering method based on the polarization mode, so as to facilitate obtaining physiological parameters related to the specific depth through the measurement signal.
  • the embodiment of the present application provides a device for measuring a physiological parameter.
  • the physiological parameter measurement device includes: a transmitting module, wherein the transmitting module is configured to emit light of one or more wavelengths, wherein the light emitted by the transmitting module satisfies a first polarization mode and illuminates the target to be measured; and a detection module, wherein the detection module is configured to filter the light reflected by the measured object, wherein the light filtered by the detection module satisfies the second polarization mode.
  • the first polarization mode is different from the second polarization mode
  • the emission module or the detection module is configured to adjust the difference between the second polarization mode and the first polarization mode so as to maximize The ratio of the AC signal to the DC signal in this measurement signal.
  • the technical solution described in the sixth aspect selectively enhances the influence of reflected light at a specific depth of the skin on the measurement signal through the filtering method based on the polarization mode, so as to facilitate obtaining physiological parameters related to the specific depth through the measurement signal.
  • Fig. 1 shows a schematic diagram of a device for measuring physiological parameters provided by an embodiment of the present application.
  • Fig. 2 shows a schematic flowchart of a method for measuring a physiological parameter provided by an embodiment of the present application.
  • Fig. 3 shows a structural block diagram of a terminal for measuring physiological parameters in an implementation manner provided by an embodiment of the present application.
  • Fig. 4 shows a structural block diagram of another implementation manner of a physiological parameter measurement terminal provided by the embodiment of the present application.
  • Fig. 5 shows a structural block diagram of another implementation manner of a physiological parameter measurement terminal provided by the embodiment of the present application.
  • the embodiment of the present application has a good SNR and AC/DC ratio, and the structure is simple and easy to adjust. It can be applied, for example, close to the user's wrist, etc.
  • a device, terminal and method for measuring physiological parameters are provided.
  • the physiological parameter measurement device includes: a transmitting module, wherein the transmitting module is configured to emit light of one or more wavelengths, wherein the light emitted by the transmitting module satisfies a first polarization mode and illuminates the target to be measured; A detection module, wherein the detection module is configured to filter light reflected by the measured object, wherein the light filtered by the detection module satisfies a second polarization mode; and a processor.
  • the processor is configured to determine the difference between the second polarization mode and the first polarization mode according to the physiological parameter to be measured of the measured target and the wavelength of the light emitted by the transmitting module A measurement signal is thereby optimized which is based on the light filtered by the detection module and which is used to determine the physiological parameter to be measured. In this way, the influence of the reflected light at a specific depth of the skin on the measurement signal is selectively enhanced through the filtering method based on the polarization mode, so as to facilitate the acquisition of physiological parameters related to the specific depth through the measurement signal.
  • any physiological detection through the skin such as measuring blood pressure, hemoglobin concentration, pulse, blood oxygen saturation, respiratory rate, blood perfusion through photoplethysmography or pulse wave Index, blood flow responsiveness, methemoglobin, carboxyhemoglobin, biliflavin, oxygen content, etc., or measure the above physiological parameters or any arbitrary Appropriate human body relevant physiological parameters.
  • the embodiment of the present application can be adjusted and improved according to the specific application environment, which is not specifically limited here.
  • the physiological parameter measuring device 100 includes a transmitting module 102 , a detecting module 104 and a processor 106 .
  • the emitting module 102 is configured to emit light of one or more wavelengths. The light emitted by the emitting module 102 satisfies the first polarization mode and illuminates the measured target.
  • the emission module 102 may include one or more light sources, and the detection module 104 may also include one or more photodetectors or photodetector arrays.
  • the measured target can be understood as a part of the user's body such as the user's wrist, fingers, ears, forehead, cheeks or eyeballs.
  • the dermis layer 120 is located below the epidermis layer 110, which together are the skin of that part of the user's body.
  • the physiological parameter measuring device 100 is close to a certain position on the user's wrist, the measured target is the skin of the user's wrist at this position, and the epidermis 110 and the dermis 120 respectively represent the epidermis and dermis of the skin at this position.
  • the detection module 104 is configured to filter light reflected by the detected object. The light filtered by the detection module 104 satisfies the second polarization mode.
  • FIG. 1 schematically shows three light paths L1 , L2 and L3 where the light emitted by the transmitting module 102 is reflected by the measured object and then received by the detection module 104 .
  • the light represented by the optical path L1 is reflected on the surface of the epidermis 110
  • the light represented by the optical path L2 is emitted in the epidermis 110
  • the light represented by the optical path L3 is reflected in the dermis 120 .
  • the optical paths L1 , L2 and L3 shown in FIG. 1 are only exemplary. In practice, the light emitted by the emitting module 102 may reach the detecting module 104 after being reflected by the measured object along any suitable optical path.
  • the physiological parameter measuring device 100 obtains a measurement signal, which is based on the light filtered by the detection module 104 and used to determine the physiological parameter to be measured of the measured target. Specifically, the light reflected by the measured object received by the detection module 104 is the light attenuated by the measured object, that is, the part of the body. Through conventional technical means such as photoelectric conversion and analog-to-digital conversion, it can be obtained Measure the signal.
  • the layers of the skin are the epidermis, dermis and subcutaneous tissue from the outermost layer.
  • the epidermis has no blood vessels and can be further divided into stratum corneum, transparent layer, granular layer, spiny cell layer and basal layer.
  • the basal layer is the innermost layer of the epidermis and connects with the dermis.
  • the basal layer contains heme, bilirubin, and melanin.
  • the activity of melanocytes determines the depth of skin color.
  • the metabolism of melanocytes within the normal range can protect cells from being reduced by ultraviolet rays and prevent ultraviolet rays from penetrating the skin and damaging deep cells.
  • the dermis is rich in blood vessels, and the subcutaneous layer is also rich in blood vessels.
  • the epidermis especially the stratum corneum, does not contain blood, the light reflected from the stratum corneum does not carry blood-related information, that is, it does not contribute to the AC signal of the measurement signal, but forms a DC signal.
  • the main components of the DC signal in the measurement signal are reflected light from the epidermis and backscattered light at the stratum corneum.
  • the light represented by the optical path L1 and the light represented by the optical path L2 are reflected light generated outside and inside the skin layer 110 respectively, that is to say, the light represented by the optical path L1 and the light path L2 will only form DC signal.
  • the light represented by the light path L3 is reflected light generated inside the dermis 120, and the dermis 120 is rich in blood vessels, so the light represented by the light path L3 may carry blood-related information and contribute to the AC signal. Therefore, in order to increase the ratio of the AC signal to the DC signal, that is, the AC/DC ratio, it is necessary to reduce the reflected light on the outside and inside of the epidermis and the backscattered light of the stratum corneum, taking the optical path L1 and the optical path L2 as examples, to the detection module. 104
  • the influence of the measurement signal obtained at the same time enhances the influence of the reflected light inside the dermis, taking the light path L3 as an example, on the measurement signal.
  • the incident linearly polarized light may be a combination of various linearly polarized lights after being reflected by blood vessels.
  • the reflected light outside and inside the epidermis and the backscattered light from the stratum corneum will have a large part or almost all of the same polarization mode as the incident light, while the reflected light inside the dermis is difficult to match with the polarization mode of the incident light.
  • the polarization mode of the incident light is consistent.
  • the reflection light outside and inside the epidermis and the light backscattered by the stratum corneum can be filtered to a relatively large extent by means of polarization-based filtering methods such as cross-polarization technology, while at the same time being filtered to a relatively small extent Filter out the reflected light inside the dermis, thereby increasing the influence of the reflected light inside the dermis on the measurement signal, thereby increasing the AC/DC ratio in the measurement signal, improving the SNR and improving the detection effect.
  • the innermost layer of the epidermis is the basal layer.
  • the basal layer contains melanocytes.
  • the activity of melanocytes determines the depth of skin color and the melanocytes play a role in protecting deep cells from ultraviolet rays.
  • the DC signal in the measurement signal is mainly composed of reflected light from the epidermis and backscattered light in the stratum corneum, part of it is also from the reflected light in the dermis.
  • the part of the reflected light from the dermis in the DC signal can be effectively filtered out through the filtering method based on the polarization mode, thereby enhancing the part of the reflected light from the epidermis in the DC signal, which is beneficial to the detection of physiological parameters specific to the epidermis Such as physiological parameters related to melanocytes.
  • the incident light is irradiated on the measured object and penetrates layer by layer, from the outermost stratum corneum of the epidermis to the innermost basal layer of the epidermis and then to the dermis, the light generated during the penetration of the incident light
  • the reflected light outside and inside the epidermis and the backscattered light from the stratum corneum will have a large part or almost all of the same polarization mode as the incident light, while the reflected light inside the dermis is difficult to match the polarization mode of the incident light.
  • the polarization modes are consistent.
  • the relationship between the polarization modes of the reflected light at different depths of the skin and the polarization modes of the incident light can be used to selectively enhance the influence of the reflected light at a specific depth of the skin on the measurement signal through the filtering method based on the polarization mode, which is beneficial Physiological parameters related to this specific depth are obtained by measuring the signal.
  • the light emitted by the transmitting module 102 satisfies the first polarization mode and the light filtered by the detection module 104 satisfies the second polarization mode.
  • the first polarization mode is the same or almost the same as the second polarization mode, it is equivalent to enhancing the part of the reflected light of the measured target that can be consistent with the polarization mode of the incident light, that is, the first polarization mode;
  • the difference between the first polarization mode and the second polarization mode is relatively large, for example, when it is an orthogonal polarization, it is equivalent to enhancing the part of the reflected light of the measured object that can be greatly different from the polarization mode of the incident light, that is, the first polarization mode.
  • the first polarization mode is linearly polarized light
  • the vibration plane of the linearly polarized light in the first polarization mode is 0 degree
  • the second polarization mode is also linearly polarized light
  • the vibration plane is 90 degrees. That is to say, the vibration plane of the linearly polarized light in the second polarization mode is rotated by 90 degrees relative to the vibration plane of the linearly polarized light in the first polarization mode, that is, an orthogonal polarization is formed.
  • the first polarization mode can be set to be linearly polarized light
  • the vibration plane of the linearly polarized light in the first polarization mode can be set to be 0 degrees
  • the second polarization mode can also be set to be linearly polarized light and the vibration plane can be set to 0 degrees
  • the second polarization mode is the same as the first polarization mode.
  • the transmitting module 102 has a light source and a polarizer (Polarizer), the light source generates light of one or more wavelengths, and the polarizer filters the light generated by the light source, only allowing The light vibrating in the direction passes through, so as to obtain the linearly polarized light in the first polarization mode; the detection module 104 has an analyzer (Analyzer), which is used to filter the light received by the detection module 104 .
  • the polarizer can be a polarizer, a Nicols, or any suitable device.
  • the analyzer can also be a polarizer or other suitable devices.
  • the first polarization mode is determined by the polarizer of the transmitting module 102
  • the second polarization mode is determined by the analyzer of the detection module 104.
  • the vibration direction of the polarizer and the vibration direction of the analyzer differ by 90 degrees, then means orthogonal polarizations.
  • the vibration direction and the vibration direction of the analyzer of the detection module 104 determine the filtering method for the light emitted by the transmitting module 102 and reflected by the measured object, and then selectively enhance the specific depth of the skin through the determined filtering method The influence of the reflected light on the measurement signal, such as increasing the AC/DC ratio in the measurement signal and improving the SNR effect.
  • this filtering method depends on the difference between the second polarization mode and the first polarization mode, such as the rotation angle of the vibration direction of the analyzer relative to the vibration direction of the polarizer, it can be adjusted by adjusting the second polarization mode relative to the first polarization mode.
  • the difference of a polarization mode for example, adjusts the second polarization mode or the first polarization mode to determine the filtering method.
  • the difference between the second polarization mode and the first polarization mode is a relative concept, that is to say, the respective values of the first polarization mode and the second polarization mode in the same spatial reference coordinate system are not important, while the first The difference between the polarization mode and the second polarization mode is what matters.
  • the reflected light in the dermis that is, the reflected light that may carry blood-related information also remains consistent with the first polarization mode such as the vibration direction of the polarizer (set to 0 degrees), then set For the second polarization mode, if the vibration direction of the analyzer is 90 degrees, it means that the reflected light that may carry blood-related information will be filtered out, so that the optimal AC/DC ratio may not be achieved. And by setting the second polarization mode such as the vibration direction of the analyzer to an intermediate value greater than 0 degrees and less than 90 degrees, such as 80 degrees or 60 degrees, it is possible to achieve the best AC/DC ratio.
  • the optical measurement obtained from the measured object can be optimized by making the difference of the second polarization mode with respect to the first polarization mode adjusted according to the wavelength of the light emitted by the transmitting module, thereby maximizing the AC/DC ratio in the measurement signal Signal, which is beneficial to obtain physiological parameters such as blood parameters.
  • the part of the signal from reflected light from the epidermis is useful for detecting physiological parameters specific to the epidermis, such as melanocyte-related physiological parameters.
  • the difference between the second polarization mode and the first polarization mode can be controlled so that the first polarization mode is substantially the same as the second polarization mode, specifically
  • the difference between the second polarization mode and the first polarization mode can be adjusted according to the wavelength of the light emitted by the transmitting module 102 so as to maximize the proportion of the DC signal in the measurement signal related to the pigment of the measured target.
  • the filtering method based on the polarization mode can be adjusted, that is, by adjusting the second polarization mode relative to the first polarization mode.
  • the differences in the modes are used to selectively enhance the influence of the reflected light at a specific depth of the skin on the measurement signal, which is beneficial to obtain the physiological parameters related to the specific depth through the measurement signal.
  • the relationship between the wavelength of the incident light and the depth of the skin can be understood as the maximum penetration depth equivalent to the depth of the skin that can be achieved under the premise of keeping the polarization mode of the incident light basically unchanged. lower limit or minimum wavelength.
  • based on empirical formulas, preset physiological models, or machine learning, how to determine the relative polarity of the second polarization mode relative to the first polarization mode when the wavelength of the light emitted by the emitting module or the incident light is known is known.
  • a polarization mode difference to maximize the AC/DC ratio in the measured signal can be expanded and adjusted according to actual needs and in combination with the development of conventional technical means, and are not specifically limited here.
  • both the first polarization mode and the second polarization mode are linearly polarized light and the difference between the second polarization mode and the first polarization mode is expressed as the rotation angle of the corresponding vibration direction
  • the rotation angle is between 0 degrees and 360 degrees or between 0 degrees and 180 degrees, so that a table of the correspondence between the rotation angle of the vibration direction and the wavelength of the incident light can be established.
  • the rotation angle of the vibration direction is set to 90 degrees, that is, orthogonally polarized; when the wavelength is set to 2000nm to 10000nm, the rotation angle of the vibration direction is set to 80 degrees; When the wavelength is greater than 10000 nm, the rotation angle of the vibration direction is set to 60 degrees.
  • the difference between the second polarization mode and the first polarization mode is expressed as the variation law of the polarization directions of the respective circularly polarized light or elliptically polarized light difference.
  • one of the first polarization mode and the second polarization mode may be set as linearly polarized light and the other as circularly polarized light or elliptically polarized light.
  • the processor 106 is used to execute operations or instructions related to determining the difference between the second polarization mode and the first polarization mode, for example, the processor 106 is configured to The wavelength of the emitted light is determined 102 to determine the difference of the second polarization mode relative to the first polarization mode to optimize the measurement signal.
  • the processor 106 may adopt any suitable circuit hardware, computing architecture, and software layer algorithm, which are not specifically limited here.
  • the physiological parameter to be measured is a blood-related parameter
  • the first polarization mode is different from the second polarization mode
  • the second polarization mode can be adjusted relative to the second polarization mode according to the wavelength of light emitted by the emitting module 102.
  • the difference of a polarization mode for example, setting the rotation angle of the vibration direction of the linearly polarized light as the second polarization mode relative to the vibration direction of the linearly polarized light as the first polarization mode is 90 degrees, thereby maximizing the The ratio of the AC signal to the DC signal.
  • Blood-related parameters include at least one of the following: blood pressure, hemoglobin concentration, pulse, oxygen saturation, respiratory rate, blood perfusion index, blood flow responsiveness, methemoglobin, carboxyhemoglobin, biliflavin, oxygen content, blood lipids, and blood sugar.
  • the blood-related parameter can also be any physiological parameter that can be obtained according to the blood-related information carried by the reflected light of the dermis, or can be any physiological parameter that can be deduced from the analysis of the AC signal in the measurement signal, which is not specifically limited. .
  • the physiological parameter to be measured is a pigment-related parameter
  • the first polarization mode is substantially the same as the second polarization mode
  • the second polarization mode can be adjusted according to the wavelength of the light emitted by the emitting module 102.
  • the difference of the first polarization mode for example, setting the rotation angle of the vibration direction of the linearly polarized light as the second polarization mode relative to the vibration direction of the linearly polarized light as the first polarization mode is 0 degrees, thereby maximizing the measurement signal
  • Pigment-related parameters include pigment distribution maps, pigment noise, or pigment-related background noise.
  • pigment-related parameters By obtaining pigment-related parameters, it can be used to draw the pigment distribution of this part of the user's body, which is beneficial to applications such as cancer detection.
  • the pigment-related background noise can be obtained, which can be used to screen and filter out the part of the DC signal corresponding to the pigment-related background noise in the measurement signal, thereby further improving the SNR.
  • the difference between the second polarization mode and the first polarization mode can also be adjusted according to the wavelength of the light emitted by the transmitting module 102 so as to maximize the epidermal layer-specific difference between the DC signal in the measurement signal and the measured target.
  • Physiological parameters specific to the epidermis may be, for example, physiological parameters associated with components within the spiny cell layer of the epidermis, such as spiny polygonal cells therein.
  • FIG. 2 shows a schematic flowchart of a method for measuring a physiological parameter provided by an embodiment of the present application.
  • the physiological parameter measurement method 200 includes the following steps.
  • S202 Emit light of one or more wavelengths through the emitting module, wherein the light emitted by the emitting module satisfies the first polarization mode and illuminates the measured target.
  • the structure and function of the transmitting module are similar to the transmitting module 102 shown in FIG. 1 , and will not be repeated here.
  • the structure and function of the detection module are similar to the detection module 104 shown in FIG. 1 , and will not be repeated here.
  • S206 Obtain a measurement signal based on the light filtered by the detection module, wherein the measurement signal is used to determine a physiological parameter to be measured of the measured target.
  • the difference between the second polarization mode and the first polarization mode is determined according to the physiological parameter to be measured and the wavelength of the light emitted by the transmitting module, so as to optimize the measurement signal.
  • the filter method based on the polarization mode can be adjusted, that is, by adjusting the second polarization mode relative to the first polarization mode.
  • the first polarization mode is different from the second polarization mode, and the difference between the second polarization mode and the first polarization mode can be adjusted according to the wavelength of the light emitted by the emitting module, such as setting
  • the rotation angle of the vibration direction of the linearly polarized light as the second polarization mode relative to the vibration direction of the linearly polarized light as the first polarization mode is 90 degrees, thereby maximizing the ratio of the AC signal to the DC signal in the measurement signal.
  • the first polarization mode is basically the same as the second polarization mode, and the difference between the second polarization mode and the first polarization mode can be adjusted according to the wavelength of the light emitted by the emitting module, for example, set
  • the rotation angle of the vibration direction of the linearly polarized light as the second polarization mode relative to the vibration direction of the linearly polarized light as the first polarization mode is set to be 0 degrees, thereby maximizing the DC signal in the measurement signal and the measured The proportion of the pigment-related fraction of the target.
  • the relationship between the polarization modes of the reflected light at different depths of the skin and the polarization mode of the incident light can be used to selectively enhance the influence of the reflected light at a specific depth of the skin on the measurement signal through the filtering method based on the polarization mode, which is beneficial to Physiological parameters related to this specific depth are obtained by measuring the signal.
  • FIG. 3 shows a structural block diagram of a terminal for measuring physiological parameters in an implementation manner provided by an embodiment of the present application.
  • the physiological parameter measurement terminal 300 includes a transmitting module 302 and two detection modules, namely a detection module 310 and a detection module 320 .
  • the emitting module 302 emits light of one or more wavelengths, and the light emitted by the emitting module 302 satisfies the first polarization mode and illuminates the measured target (not shown).
  • the emission module 302 may include one or more light sources, and the detection module 310 and the detection module 320 may each include one or more photodetectors or photodetector arrays.
  • the target to be measured can be understood as a part of the user's body such as the user's wrist, fingers, ears, forehead, cheeks or eyeballs, and this part of the user's body can be understood as including the epidermis and dermis.
  • the physiological parameter measurement terminal 300 is close to a certain position on the user's wrist, the measured target is the skin of the user's wrist at this position.
  • the detection module 310 is configured to filter the light reflected by the measured object, and the light filtered by the detection module 310 satisfies the first polarization analysis mode.
  • the detection module 320 is configured to filter the light reflected by the measured object, and the light filtered by the detection module 320 satisfies the second polarization analysis mode.
  • the light emitted by the transmitting module 302 satisfies the first polarization mode
  • the detection module 310 and the detection module 320 respectively filter the light reflected by the measured object according to the first polarization analysis mode and the second polarization analysis mode, Thereby the first measurement signal and the second measurement signal are respectively obtained.
  • the vibration plane of the linearly polarized light corresponding to the first polarization mode be 0 degrees
  • the vibration plane of the linearly polarized light corresponding to the first analyzing mode be 90 degrees
  • the vibration plane of the corresponding linearly polarized light is 45 degrees or any angle between 0 degrees and 90 degrees.
  • the detection module 310 using the first polarization analysis mode and the emission module 302 using the first polarization mode are equivalent to constitute orthogonal polarization, so that the polarization mode of the light reflected by the measured object is the same as the polarization mode of the incident light Parts where the polarization mode remains consistent are filtered out, such as reflected light outside and inside the epidermis and backscattered light from the stratum corneum. Reflected or scattered light that occurs at these skin depths is also linearly polarized and its vibration plane It is basically parallel to the vibration plane of the incident linearly polarized light, that is, it is 0 degrees, so it will be filtered out by the 90-degree first analyzer mode.
  • the detection module 320 using the second polarization analysis mode may obtain a higher degree than the first polarization analysis mode in some cases because it uses a certain intermediate value greater than 0 degrees but less than 90 degrees, such as 80 degrees or 60 degrees.
  • the detection module 310 has a higher AC/DC ratio.
  • the detection module 310 and the detection module 320 are arranged to filter the light reflected by the measured object according to the first polarization analysis mode and the second polarization analysis mode respectively, thereby obtaining the first measurement signal and the second measurement signal respectively, Then comparing the AC/DC ratio of the first measurement signal with the AC/DC ratio of the second measurement signal, a higher AC/DC ratio can be selected, thereby improving the measurement effect.
  • the difference between the first polarization analysis mode and the first polarization mode is 90 degrees
  • the difference between the second polarization analysis mode and the first polarization mode is an intermediate value greater than 0 degrees and less than 90 degrees value.
  • the difference between the first polarization analysis mode and the first polarization mode is different from the difference between the second polarization analysis mode and the first polarization mode, so that the AC/DC ratio of the first measurement signal is different Based on the AC/DC ratio of the second measurement signal, and by comparing the first measurement signal with the second measurement signal, a higher AC/DC ratio can be selected to improve the measurement effect.
  • the reflected light at different skin depths can be selectively enhanced The influence on the measurement signal, so that the first measurement signal highlights the physiological parameter related to the first depth, and makes the second measurement signal more prominent the physiological parameter related to the second depth.
  • the first measurement signal will highlight the light reflected in the dermis and the physiological parameters related to it, such as blood parameters, and the second polarization mode will be If the difference between the pattern and the first polarizing pattern is 0 degrees, the second measurement signal is more prominent in the physiological parameters of the epidermis, such as the physiological parameters related to melanocytes.
  • the difference between the first polarization analysis mode and the first polarization mode and the difference between the second polarization analysis mode and the first polarization mode respectively it is beneficial to obtain different measurement signals related to different skin penetration depths. physiological parameters.
  • the difference between the first polarization analysis mode and the first polarization mode is determined according to the first depth, and the difference between the second polarization analysis mode and the first polarization mode is determined according to the second depth;
  • the first measurement signal is used to determine the The physiological parameter related to the position of the target at the first depth, and the second measurement signal is used to determine the physiological parameter related to the position of the measured target at the second depth.
  • FIG. 3 only schematically shows the situation of two detection modules, and the situation of three detection modules or more detection modules can also be applied to the embodiment of the present application, especially the embodiment illustrated in FIG. 3 , these improvements Or expansion should also be understood as a part of the disclosure of this application.
  • FIG. 4 shows a structural block diagram of another implementation manner of a physiological parameter measurement terminal provided by the embodiment of the present application.
  • the physiological parameter measurement terminal 400 includes another two transmitting modules, namely a transmitting module 402 and a transmitting module 404 , and a detection module 410 .
  • the emitting module 402 and the emitting module 404 respectively emit light of one or more wavelengths.
  • the light emitted by the emitting module 402 satisfies the first polarization mode and illuminates the measured target (not shown).
  • the light emitted by the emitting module 404 satisfies the second polarization mode and illuminates the measured target.
  • Transmitting module 402 and transmitting module 404 may each include one or more light sources, while detection module 410 includes one or more photodetectors or an array of photodetectors.
  • the target to be measured can be understood as a part of the user's body such as the user's wrist, fingers, ears, forehead, cheeks or eyeballs, and this part of the user's body can be understood as including the epidermis and dermis.
  • the physiological parameter measurement terminal 400 is close to a certain position on the user's wrist, the measured target is the skin of the user's wrist at this position.
  • the detection module 410 is configured to filter the light reflected by the measured object, and the light filtered by the detection module 410 satisfies the first polarization analysis mode.
  • the emitting module 402 and the emitting module 404 respectively emit light satisfying the first polarization mode and the second polarizing mode, and the two kinds of incident light are reflected by the same measured object and filtered by the detection module 410 to obtain measurement signals.
  • the vibration plane of the linearly polarized light corresponding to the first polarization mode be 0 degrees
  • the vibration plane of the linearly polarized light corresponding to the second polarization mode be 45 degrees or between 0 degrees and 90 degrees Any angle between them, and the vibration plane of the linearly polarized light corresponding to the first analyzing mode is 90 degrees.
  • the emitting module 402 emits light of the first wavelength
  • the emitting module 404 emits light of the second wavelength
  • the second wavelength is used to set the difference between the second polarization analysis mode and the first polarization mode, so that the incident light of different wavelengths can achieve the best AC/DC ratio on the same measured object, thereby further improving the measurement effect.
  • a table of correspondence between the rotation angle of the vibration direction and the wavelength of the incident light can be established.
  • the rotation angle of the vibration direction is set as It is 90 degrees, that is, orthogonally polarized; when the wavelength is 2000nm to 10000nm, the rotation angle of the vibration direction is set to 80 degrees.
  • the first wavelength can be set as 900 nm and the vibration plane of the linearly polarized light corresponding to the first analyzing mode as 90 degrees, and
  • the vibration plane of the linearly polarized light corresponding to the second analyzing mode is set to be 80 degrees with the second wavelength being 3000 nm.
  • the incident light of the first wavelength and the incident light of the second wavelength can both achieve the best AC/DC ratio, and because the wavelengths are different, frequency domain analysis or frequency-based technical means can be used to analyze the measurement signal, thereby further Improve measurement results.
  • the difference between the first polarization analysis mode and the first polarization mode is determined according to the first wavelength
  • the difference between the first polarization analysis mode and the second polarization mode is determined according to the second wavelength.
  • FIG. 4 only schematically shows the situation of two transmitting modules, and the situation of three transmitting modules or more transmitting modules can also be applied to the embodiment of the present application, especially the embodiment illustrated in FIG. 4 , these improvements Or expansion should also be understood as a part of the disclosure of this application.
  • Fig. 5 shows a structural block diagram of another implementation manner of a physiological parameter measurement terminal provided by the embodiment of the present application.
  • a physiological parameter measurement terminal 500 includes two transmitting modules 502 and 504 and two detecting modules 510 and 520 .
  • the respective polarization modes of the transmitting modules 502 and 504 are the first polarization mode and the second polarization mode
  • the respective polarization modes of the detection modules 510 and 520 are the first analysis mode and the second analysis mode.
  • the first polarization analysis mode and the first polarization mode form a pair, and are used to obtain physiological parameters related to the first skin penetration depth.
  • the second polarization analysis mode and the second polarization mode form a pair, and are used to obtain physiological parameters related to the second skin penetration depth.
  • physiological parameters related to different skin penetration depths can be obtained.
  • the first measurement signal is based on the light filtered by the detection module 510
  • the second measurement signal is based on the light filtered by the detection module 520
  • the first measurement signal is used to determine the Physiological parameters related to the location of the depth
  • the second measurement signal is used to determine the physiological parameters related to the location of the measured target at the second depth.
  • Fig. 5 only schematically shows the situation of two transmitting modules and two detecting modules, that is, two pairs of transmitting modules and detecting modules, three pairs of transmitting modules and detecting modules or more
  • the paired transmitting module and detecting module can also be applied to the embodiment of the present application, especially the embodiment illustrated in FIG. 5 , and these improvements or extensions should also be understood as part of the disclosure of the present application.
  • the "polarization mode", “analyzer mode” or “polarization mode” mentioned in various embodiments of the present application should be understood as describing the vibration direction or vibration mode of a polarizer or an analyzer , such as the vibration plane or vibration direction of linearly polarized light, and the variation law of the polarization direction of circularly polarized light or elliptically polarized light.
  • a certain polarization mode is the same as the analyzer mode, it means that the corresponding vibration directions or vibration modes are the same.
  • the difference between the two polarization modes should be understood as a relative concept, for example, the rotation angle of the vibration direction of one linearly polarized light relative to the vibration direction of the other linearly polarized light.
  • the physiological parameter measurement device includes: a transmitting module, wherein the transmitting module is configured to emit light of one or more wavelengths, wherein the light emitted by the transmitting module satisfies a first polarization mode and illuminates the target to be measured; and a detection module, wherein the detection module is configured to filter the light reflected by the measured object, wherein the light filtered by the detection module satisfies the second polarization mode.
  • the first polarization mode is different from the second polarization mode
  • the emission module or the detection module is configured to adjust the difference between the second polarization mode and the first polarization mode so as to maximize The ratio of the AC signal to the DC signal in this measurement signal.
  • the difference between the second polarization mode and the first polarization mode can be changed, and the selective enhancement of the skin through the polarization mode-based filtering method can be realized.
  • the influence of reflected light at a specific depth on the measurement signal is beneficial to obtaining physiological parameters related to the specific depth through the measurement signal.
  • the "measured target” mentioned in various embodiments of the present application can be understood as a part of the user's body such as the user's wrist, fingers, ears, forehead, cheeks or eyeballs, or any The object of the disclosed physiological parameter measuring device, terminal and method.
  • the "physiological parameters to be measured” mentioned in various embodiments of the present application should be understood to include: any physiological detection through the skin, such as through photoplethysmography or Pulse wave measurement of blood pressure, hemoglobin concentration, pulse, blood oxygen saturation, respiratory rate, blood perfusion index, blood flow responsiveness, methemoglobin, carboxyhemoglobin, biliflavin, oxygen content, etc., or by measuring pulse wave transit time Or measure the pulse wave amplitude or pulse wave phase of different wavelengths to measure the above physiological parameters or any suitable physiological parameters related to the human body.
  • any physiological detection through the skin such as through photoplethysmography or Pulse wave measurement of blood pressure, hemoglobin concentration, pulse, blood oxygen saturation, respiratory rate, blood perfusion index, blood flow responsiveness, methemoglobin, carboxyhemoglobin, biliflavin, oxygen content, etc.
  • pulse wave transit time measure the pulse wave amplitude or pulse wave phase of different wavelengths to measure the above physiological parameters or any suitable physiological parameters related to the human body.
  • the specific embodiments provided in this application can be realized by any one or combination of hardware, software, firmware or solid-state logic circuits, and can be realized in combination with signal processing, control and/or special purpose circuits.
  • the equipment or apparatus provided by the specific embodiments of the present application may include one or more processors (for example, a microprocessor, a controller, a digital signal processor (DSP), an application specific integrated circuit (ASIC), a field programmable gate array (FPGA) ), etc.), these processors process various computer-executable instructions to control the operation of a device or device.
  • the device or apparatus provided in the specific embodiments of the present application may include a system bus or a data transmission system coupling various components together.
  • a system bus can include any one or combination of different bus structures, such as a memory bus or memory controller, a peripheral bus, a universal serial bus, and/or a process utilizing any of a variety of bus architectures device or local bus.
  • the device or device provided in the specific embodiments of the present application may be provided independently, or may be a part of a system, or may be a part of other devices or devices.
  • the specific embodiments provided in the present application may include or be combined with a computer-readable storage medium, such as one or more storage devices capable of providing non-transitory data storage.
  • the computer-readable storage medium/storage device can be configured to store data, programmers and/or instructions, which when executed by the processor of the device or device provided by the specific embodiments of the application, make these devices Or the device implements related operations.
  • a computer-readable storage medium/storage device may include one or more of the following characteristics: volatile, non-volatile, dynamic, static, read/write, read-only, random access, sequential access, location addressability, File addressability and content addressability.
  • the computer-readable storage medium/storage device may be integrated into the device or apparatus provided in the specific embodiments of the present application or belong to a public system.
  • Computer-readable storage media/storage devices may include optical storage devices, semiconductor storage devices, and/or magnetic storage devices, etc., and may also include random access memory (RAM), flash memory, read-only memory (ROM), erasable programmable Read Only Memory (EPROM), Electrically Erasable Programmable Read Only Memory (EEPROM), Registers, Hard Disk, Removable Disk, Recordable and/or Rewritable Compact Disc (CD), Digital Versatile Disc (DVD), Large Capacity storage media device or any other form of suitable storage media.
  • RAM random access memory
  • ROM read-only memory
  • EPROM erasable programmable Read Only Memory
  • EEPROM Electrically Erasable Programmable Read Only Memory
  • CD Hard Disk
  • DVD Digital Versatile Disc
  • Large Capacity storage media device or any other form of suitable storage media.

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Abstract

L'invention concerne un dispositif de mesure de paramètre physiologique (100), un terminal (300, 400, 500) et un procédé (200). Le dispositif de mesure de paramètre physiologique (100) comprend : un module de transmission (102, 302, 402, 404, 502, 504), qui est configuré pour transmettre la lumière d'une ou plusieurs longueurs d'onde, la lumière transmise par le module de transmission (102, 302, 402, 404, 502, 504) satisfaisant un premier mode de polarisation et irradiant une cible testée ; un module de mesure (104, 310, 320, 410, 510, 520), qui est configuré pour filtrer la lumière qui est réfléchie par la cible testée, la lumière filtrée par le module de mesure (104, 310, 320, 410, 510, 520) satisfaisant un second mode de polarisation ; et un processeur (106). Le processeur (106) est configuré pour déterminer, en fonction de paramètres physiologiques à mesurer de la cible testée et de la longueur d'onde de la lumière transmise par le module de transmission (102, 302, 402, 404, 502, 504), la différence du second mode de polarisation par rapport au premier mode de polarisation, pour ainsi optimiser un signal de mesure. Le signal de mesure est basé sur la lumière filtrée par le module de mesure (104, 310, 320, 410, 510, 520) et est utilisé pour déterminer les paramètres physiologiques à mesurer. En tant que tel, l'impact de la lumière réfléchie d'une profondeur spécifique de la peau sur le signal de mesure est sélectivement amélioré au moyen d'un moyen de filtrage basé sur le mode de polarisation, ce qui aide à obtenir, au moyen du signal de mesure, des paramètres physiologiques associés à une profondeur spécifique.
PCT/CN2021/136061 2021-06-04 2021-12-07 Dispositif de mesure de paramètre physiologique, terminal et procédé WO2022252535A1 (fr)

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US20090082642A1 (en) * 2006-06-13 2009-03-26 Elfi-Tech Ltd. System and method for measurement of biological parameters of a subject
CN105143448A (zh) * 2013-02-01 2015-12-09 丹尼尔·法卡斯 用于使用多模式光学测量三维地表征组织的方法和系统
CN104825131A (zh) * 2014-02-11 2015-08-12 首尔伟傲世有限公司 皮肤状况评估装置及使用该装置的皮肤状况评估方法
CN111148468A (zh) * 2017-08-17 2020-05-12 威尔图比有限公司 用于非侵入式监测生理测量结果的设备、系统和方法
CN111936040A (zh) * 2018-03-27 2020-11-13 皇家飞利浦有限公司 用于提取指示对象的至少一个生命体征的生理信息的设备、系统和方法
CN113520349A (zh) * 2021-06-04 2021-10-22 深圳市脉度科技有限公司 生理参数测量装置、终端及方法
CN113509152A (zh) * 2021-09-15 2021-10-19 深圳市脉度科技有限公司 一种检测皮肤生理参数的方法、装置及智能终端

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