Arrayed microcavity blood pressure detection system based on digital optical frequency dual combs

Abstract

Embodiments of the present application relate to the technical field of optical sensing, and provide an arrayed microcavity blood pressure detection system based on digital optical frequency dual combs. An input end of a light intensity modulator is connected to a laser and a waveform generator, separately, and an output end of the light intensity modulator, a polarization controller, and an on-chip optical microcavity array are sequentially connected; the light intensity modulator modulates single-frequency light on the basis of an electric modulation signal, to obtain an optical frequency dual-comb signal; the optical frequency dual-comb signal enters the on-chip optical microcavity array after passing through the polarization controller, the on-chip optical microcavity array is attached to a site of an artery to be measured, the on-chip optical microcavity array comprises a plurality of sensing units, each sensing unit generates an independent pulse signal, the on-chip optical microcavity array obtains a sensing signal on the basis of the optical frequency dual-comb signal and beating extrusion at the site of the artery to be measured, and a signal processing mechanism obtains blood pressure value information on the basis of the sensing signal. According to the detection system, the technical effect of improving the accuracy and convenience of blood pressure measurement can be achieved.

Description

An arrayed microcavity blood pressure detection system based on digital optical dual-comb Technical Field

[0001] The present application relates to the field of optical sensing technology, and in particular to an arrayed microcavity blood pressure detection system based on a digital optical frequency dual comb. Background Art

[0002] Blood pressure is an important parameter for measuring human health, as high blood pressure can cause a range of diseases, including coronary heart disease, angina pectoris, myocardial infarction, and diabetes. Continuous blood pressure monitoring data plays an important role in the treatment of high blood pressure.

[0003] In the existing technology, continuous measurement of blood pressure can only be achieved by invasive measurement methods based on intubation, which uses a pressure gauge to measure blood pressure at any arterial site. Other common methods such as the Korotkoff sound method and the oscillometric method are discrete in time, with a long measurement time interval, and require an inflatable cuff to apply external force to assist in the measurement. The wave velocity method for measuring blood pressure requires setting up two measurement points on the body surface, and measuring the time delay of the pulse wave at the two measurement points instead of the inflatable cuff for traditional blood pressure measurement to perform non-invasive and continuous blood pressure estimation. Generally, most methods using the wave velocity method will set up two measurement points at the heart and wrist, and long-distance measurements have high requirements for position stability and spatial dimensions.

[0004] The development trend of optical sensing requires demodulation systems to possess real-time detection, large multiplexing capacity, and high precision. This in turn places higher demands on the laser light sources used in sensing systems: high sweep rate, wide sweep range, and narrow instantaneous linewidth. Therefore, the current development of sensing is limited not only by the device itself but also by the light source. Optical frequency combs are a very promising new light source. However, conventional optical frequency combs are generated using mode-locked lasers, which have significant limitations in accuracy and speed and lack flexible adjustment. Furthermore, traditional dual-comb systems require two lasers, significantly increasing the complexity of the system.

[0005] Summary of the Invention

[0006] The purpose of the embodiments of the present application is to provide an arrayed microcavity blood pressure detection system and method based on a digital optical frequency dual comb, which can achieve the technical effect of improving the accuracy and convenience of blood pressure measurement.

[0007] In a first aspect, the embodiments of the present application provide an arrayed microcavity blood pressure detection system based on a digital optical frequency dual-comb, comprising a laser, a waveform generator, a light intensity modulator, a polarization controller, an on-chip optical microcavity array, and a signal processing mechanism;

[0008] The input end of the light intensity modulator is connected to the laser and the waveform generator respectively, and the output end of the light intensity modulator, the polarization controller, and the on-chip optical microcavity array are connected in sequence. The laser emits single-frequency light of a preset frequency. The waveform generator generates an electrical modulation signal based on a preset time domain signal. The preset time domain signal is obtained by inverse Fourier transforming and superimposing two sets of frequency comb signals with a preset comb tooth interval and a preset frequency difference.

[0009] The light intensity modulator modulates the single-frequency light based on the electrical modulation signal to obtain an optical frequency dual-comb signal; the optical frequency dual-comb signal passes through the polarization controller and enters the on-chip optical microcavity array; the on-chip optical microcavity array is aligned with the position of the artery to be measured, the on-chip optical microcavity array includes multiple sensing units, each of which generates an independent pulse signal; the on-chip optical microcavity array obtains a sensing signal based on the optical frequency dual-comb signal and the beating and squeezing of the position of the artery to be measured; and the signal processing mechanism obtains blood pressure value information based on the sensing signal.

[0010] In the above implementation process, the arrayed microcavity blood pressure detection system based on digital optical frequency dual comb obtains optical frequency dual comb signals through a laser, a waveform generator, and a light intensity modulator, fits the on-chip optical microcavity array to the position of the artery to be measured, and inputs the optical frequency dual comb signals into the on-chip optical microcavity array, obtains a sensing signal under the beating and squeezing of the position of the artery to be measured, and obtains blood pressure value information based on the sensing signal; the arrayed microcavity blood pressure detection system based on digital optical frequency dual comb uses a digital optical frequency dual comb as a light source, and has the advantages of high bandwidth, high precision, high speed and free adjustment. By using an arrayed optical microring, the time delay between two points can be measured within an extremely short distance, which improves the system stability on the one hand and saves space size on the other hand, making it more convenient; thus, the arrayed microcavity blood pressure detection system based on digital optical frequency dual comb can achieve the technical effect of improving the accuracy and convenience of blood pressure measurement.

[0011] Furthermore, the signal processing mechanism includes an erbium-doped fiber amplifier, and the erbium-doped fiber amplifier is connected to the on-chip optical microcavity array.

[0012] In the above implementation process, since the on-chip optical microcavity array itself has a certain loss plus the loss of packaging coupling, the signal is amplified by an erbium-doped fiber amplifier.

[0013] Furthermore, the signal processing mechanism further includes a coherent receiver, and the coherent receiver is connected to the erbium-doped fiber amplifier and the laser respectively.

[0014] Furthermore, the signal processing mechanism further includes an oscilloscope, and the oscilloscope is connected to the coherent receiver.

[0015] In the above implementation process, the amplified sensor signal enters the coherent receiver, and when the laser emits single-frequency light, the branched reference light is sent to the coherent receiver. The sensor signal and reference light enter the coherent receiver together for demodulation, and finally the frequency comb data is collected by the oscilloscope to restore the pulse wave waveform.

[0016] Furthermore, the sensing signal satisfies the following relationship:

[0017] Wherein, λ is the resonant wavelength of the microring resonator of the on-chip optical microcavity array, Δλ is the change in the resonant wavelength, Δl is the waveguide deformation, l is the total length of the original waveguide, Δn is the change in the waveguide refractive index, and n is the refractive index of the original waveguide.

[0018] Furthermore, the on-chip optical microcavity array includes two sensing units, each sensing unit generates a set of sensing signals, and blood pressure value information is obtained by analyzing the two sets of sensing signals and the continuous time difference between the two sets of sensing signals based on the wave velocity method.

[0019] Furthermore, the artery position to be measured is the radial artery position.

[0020] In a second aspect, an embodiment of the present application provides an arrayed microcavity blood pressure detection method based on a digital optical frequency dual comb, which is applied to the arrayed microcavity blood pressure detection system based on a digital optical frequency dual comb described in any one of the first aspects, and the detection method includes:

[0021] Emits single-frequency light of a preset frequency through a laser;

[0022] generating an electrical modulation signal by a waveform generator based on a preset time domain signal, wherein the preset time domain signal is obtained by inverse Fourier transforming and superimposing two sets of frequency comb signals having a preset comb tooth interval and a preset frequency difference;

[0023] modulating the single-frequency light based on the electrical modulation signal to obtain an optical frequency dual-comb signal;

[0024] transmitting the optical frequency dual-comb signal to an on-chip optical microcavity array to obtain a sensing signal, wherein the on-chip optical microcavity array is aligned with the position of the artery to be measured;

[0025] The blood pressure value information of the artery to be measured is obtained according to the sensing signal.

[0026] Furthermore, before the step of generating the electrical modulation signal based on the preset time domain signal by the waveform generator, the method further includes:

[0027] Generate two sets of frequency comb teeth with different comb tooth intervals and a preset frequency difference using a pseudo-random sequence code;

[0028] The two groups of frequency comb teeth are converted into two groups of time domain signals by inverse fast Fourier transform and superimposed to obtain a preset time domain signal.

[0029] Furthermore, after the step of obtaining blood pressure information of the artery to be measured according to the sensing signal, the method further includes:

[0030] The pulse waveform information is obtained by monitoring the frequency shift through a frequency comb according to the sensing signal.

[0031] Other features and advantages disclosed in the present application will be described in the following description, or some features and advantages can be inferred or determined without doubt from the description, or can be learned by implementing the above-mentioned technology disclosed in the present application.

[0032] In order to make the above-mentioned objects, features and advantages of the present application more obvious and easy to understand, preferred embodiments are given below and described in detail with reference to the accompanying drawings. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the following is a brief introduction to the drawings required for use in the embodiments of the present application. It should be understood that the following drawings only show certain embodiments of the present application and therefore should not be regarded as limiting the scope. For ordinary technicians in this field, other relevant drawings can be obtained based on these drawings without creative work.

[0034] FIG1 is a schematic structural diagram of an arrayed microcavity blood pressure detection system based on a digital optical frequency dual-comb according to an embodiment of the present application;

[0035] FIG2 is a schematic structural diagram of an on-chip optical microcavity array provided in an embodiment of the present application;

[0036] FIG3 is a flow chart of a method for detecting blood pressure using an arrayed microcavity based on a digital optical frequency dual-comb according to an embodiment of the present application;

[0037] FIG4 is a flow chart of another method for detecting blood pressure using an arrayed microcavity based on a digital optical frequency dual-comb according to an embodiment of the present application;

[0038] FIG5 is a schematic diagram of two sets of frequency combs provided in an embodiment of the present application;

[0039] FIG6 is a schematic diagram showing the principle of frequency comb demodulation according to an embodiment of the present application;

[0040] FIG7 is a schematic diagram of long-term stable measurement data provided by an embodiment of the present application;

[0041] FIG8 is a schematic diagram of two sets of pulse wave time differences provided by an embodiment of the present application;

[0042] FIG9 is a schematic diagram of blood pressure value information-time detection provided in an embodiment of the present application.

[0043] Icons: laser 100; waveform generator 200; optical intensity modulator 300; polarization controller 400; on-chip optical microcavity array 500; sensing unit 510; optical fiber 520; signal processing mechanism 600; erbium-doped fiber amplifier 610; coherent receiver 620; oscilloscope 630. DETAILED DESCRIPTION

[0044] The technical solutions in the embodiments of the present application will be clearly and completely described below in conjunction with the drawings in the embodiments of the present application. Obviously, the described embodiments are only a part of the embodiments of the present application, rather than all of the embodiments. The components of the embodiments of the present application generally described and shown in the drawings here can be arranged and designed in various different configurations. Therefore, the following detailed description of the embodiments of the present application provided in the drawings is not intended to limit the scope of the application for protection, but merely represents the selected embodiments of the present application. Based on the embodiments of the present application, all other embodiments obtained by those skilled in the art without making creative work are within the scope of protection of this application.

[0045] In this application, terms such as "upper," "lower," "left," "right," "front," "back," "top," "bottom," "inner," "outer," "center," "vertical," "horizontal," "transverse," and "longitudinal" indicate positions or locations based on the positions or locations shown in the accompanying drawings. These terms are primarily intended to better describe this application and its embodiments and are not intended to limit the devices, elements, or components indicated to having a specific orientation, or to being constructed or operated in a specific orientation.

[0046] Furthermore, some of the above terms may be used to express other meanings besides indicating a position or location. For example, the term "on" may also be used to indicate a dependency or connection in certain circumstances. Those skilled in the art will understand the specific meanings of these terms in this application based on the specific circumstances.

[0047] Furthermore, the terms "installed," "disposed," "provided with," "connected," and "connected" should be interpreted broadly. For example, they can refer to fixed connections, removable connections, or integral structures; mechanical connections or point connections; direct connections, indirect connections through an intermediary, or internal communication between two devices, elements, or components. Those skilled in the art will understand the specific meanings of these terms in this application based on the specific circumstances.

[0048] Furthermore, the terms "first," "second," etc., are primarily used to distinguish between different devices, elements, or components (which may or may not be of the same type and configuration), and are not intended to indicate or imply the relative importance or quantity of the devices, elements, or components indicated. Unless otherwise specified, "plurality" means two or more.

[0049] The arrayed microcavity blood pressure detection system and method based on a digital optical frequency dual-comb in the embodiments of the present application can be applied to continuous blood pressure monitoring. The arrayed microcavity blood pressure detection system based on a digital optical frequency dual-comb obtains an optical frequency dual-comb signal through a laser, a waveform generator, and a light intensity modulator, fits an on-chip optical microcavity array to the position of the artery to be measured, and inputs the optical frequency dual-comb signal into the on-chip optical microcavity array. A sensing signal is obtained under the beating and squeezing of the position of the artery to be measured, and blood pressure value information is obtained based on the sensing signal. The arrayed microcavity blood pressure detection system based on a digital optical frequency dual-comb uses a digital optical frequency dual-comb as a light source, and has the advantages of high bandwidth, high precision, high speed and free adjustment. In addition, by using an arrayed optical microring, the time delay between two points can be measured within an extremely short distance, which not only improves system stability but also saves space and is more convenient. Therefore, the arrayed microcavity blood pressure detection system based on a digital optical frequency dual-comb can achieve the technical effect of improving the accuracy and convenience of blood pressure measurement.

[0050] In recent years, with the rapid development of on-chip optical processes, light source technology, and optical information processing, it has become possible to use more sensitive and faster optical methods to achieve higher-quality sensing detection in fields such as biomedicine. The high integration and easy arraying characteristics of optical microcavities, combined with the highly flexible digital optical frequency comb, have achieved a more accurate and convenient blood pressure measurement compared to various traditional blood pressure detection methods.

[0051] Please refer to Figures 1 and 2. Figure 1 is a schematic diagram of the structure of an arrayed microcavity blood pressure detection system based on a digital optical frequency dual-comb provided in an embodiment of the present application, and Figure 2 is a schematic diagram of the structure of an on-chip optical microcavity array provided in an embodiment of the present application. The arrayed microcavity blood pressure detection system based on a digital optical frequency dual-comb includes a laser 100, a waveform generator 200, an optical intensity modulator 300, a polarization controller 400, an on-chip optical microcavity array 500, and a signal processing mechanism 600.

[0052] Exemplarily, the input end of the light intensity modulator 300 is connected to the laser 100 and the waveform generator 200 respectively, and the output end of the light intensity modulator 300, the polarization controller 400, and the on-chip optical microcavity array 500 are connected in sequence. The laser 100 emits single-frequency light of a preset frequency, and the waveform generator 200 generates an electrical modulation signal based on a preset time domain signal. The preset time domain signal is obtained by inverse Fourier transform and superposition of two sets of frequency comb signals with a preset comb tooth interval and a preset frequency difference.

[0053] Illustratively, the light intensity modulator 300 modulates single-frequency light based on an electrical modulation signal to obtain an optical frequency dual-comb signal; the optical frequency dual-comb signal enters the on-chip optical microcavity array 500 after passing through the polarization controller 400. The on-chip optical microcavity array 500 is adapted to the position of the artery to be measured. The on-chip optical microcavity array 500 includes multiple sensing units, each of which generates an independent pulse signal. The on-chip optical microcavity array 500 obtains a sensing signal based on the optical frequency dual-comb signal and the beating and squeezing of the artery to be measured, and the signal processing mechanism 600 obtains blood pressure value information based on the sensing signal.

[0054] Illustratively, the signal processing mechanism 600 includes an erbium-doped fiber amplifier 610 , which is connected to the on-chip optical microcavity array 500 .

[0055] For example, since the on-chip optical microcavity array 500 itself has a certain loss plus the loss of package coupling, the signal is amplified by an erbium-doped fiber amplifier.

[0056] Exemplarily, the signal processing mechanism 600 further includes a coherent receiver 620 , which is connected to the erbium-doped fiber amplifier 610 and the laser 100 , respectively.

[0057] Exemplarily, the signal processing mechanism 600 further includes an oscilloscope 630 , which is connected to the coherent receiver 620 .

[0058] For example, the amplified sensing signal enters the coherent receiver 620, and when the laser 100 emits single-frequency light, the branched reference light is sent to the coherent receiver 620. The sensing signal and the reference light enter the coherent receiver 620 together for demodulation, and finally the frequency comb data is collected by the oscilloscope 630 to restore the pulse wave waveform.

[0059] Exemplarily, the sensing signal satisfies the following relationship:

[0060] Where λ is the resonant wavelength of the microring resonator of the on-chip optical microcavity array, Δλ is the change in the resonant wavelength, Δl is the waveguide deformation, l is the total length of the original waveguide, Δn is the change in the waveguide refractive index, and n is the refractive index of the original waveguide.

[0061] Exemplarily, the on-chip optical microcavity array 500 includes two sensing units 510, each sensing unit 510 generates a set of sensing signals, and blood pressure value information is obtained by analyzing the two sets of sensing signals and the continuous time difference between the two sets of sensing signals based on the wave velocity method; optionally, the two ends of the on-chip optical microcavity array 500 are respectively connected to corresponding optical fibers 520.

[0062] Exemplarily, the artery position to be measured is the radial artery position.

[0063] Please refer to FIG3 , which is a flow chart of a method for detecting blood pressure in an arrayed microcavity based on a digital optical frequency dual-comb according to an embodiment of the present application. The method is applied to the arrayed microcavity based on a digital optical frequency dual-comb blood pressure detection system shown in FIG1 and FIG2 . The detection method includes the following steps:

[0064] S100: emits single-frequency light of preset frequency through laser;

[0065] S200: generating an electrical modulation signal based on a preset time domain signal by a waveform generator, wherein the preset time domain signal is obtained by inverse Fourier transforming and superimposing two sets of frequency comb signals having a preset comb tooth interval and a preset frequency difference;

[0066] S300: modulating the single-frequency light based on the electrical modulation signal to obtain an optical frequency dual-comb signal;

[0067] S400: Transmitting the optical frequency dual-comb signal to the on-chip optical microcavity array to obtain a sensing signal, and the on-chip optical microcavity array is aligned with the position of the artery to be measured;

[0068] S500: Obtaining blood pressure information at the artery to be measured based on the sensing signal.

[0069] Please refer to FIG4 , which is a flow chart of another arrayed microcavity blood pressure detection method based on a digital optical frequency dual comb provided in an embodiment of the present application.

[0070] Exemplarily, before the step of S200: generating an electrical modulation signal based on a preset time domain signal by a waveform generator, the method further includes:

[0071] S110: Generate two sets of frequency comb teeth with different comb tooth intervals and a preset frequency difference using a pseudo-random sequence code;

[0072] S120: Convert the two sets of frequency comb teeth into two sets of time domain signals through inverse fast Fourier transform and superimpose them to obtain a preset time domain signal.

[0073] For example, after the step of obtaining blood pressure information of the artery to be measured according to the sensing signal at S500, the method further includes:

[0074] S600: Obtain pulse waveform information by monitoring frequency shift through a frequency comb according to the sensing signal.

[0075] In some embodiments, the arrayed microcavity blood pressure detection system based on the digital optical frequency dual comb provided in the embodiments of the present application can use the on-chip optical microcavity array to perform parallel measurement of pulse waves at two locations of the radial artery. Since general single-wavelength lasers cannot meet the requirements of arrayed detection, a high-bandwidth, high-precision, high-speed, freely adjustable digital optical frequency dual comb is introduced for detection and demodulation; by collecting the pulse wave signal, the pulse wave time delay at two different locations that are close to each other is extracted, and combining the time difference with the mathematical model of blood pressure to obtain more accurate systolic and diastolic pressures; thus, the arrayed microcavity blood pressure detection system based on the digital optical frequency dual comb improves the current problems of discontinuous blood pressure measurement and the instability and poor convenience of the traditional wave velocity method.

[0076] In some embodiments, in conjunction with FIG. 1 to FIG. 4 , the present application provides an arrayed microcavity blood pressure detection method based on a digital optical frequency dual-comb. The specific working process is as follows:

[0077] The laser emits a single-frequency light with a frequency of f0, which enters the optical intensity modulator for modulation;

[0078] A computer uses a pseudo-random sequence code to generate two sets of frequency comb teeth with a bandwidth of 2 GHz and comb tooth spacings of 3.920 MHz and 3.913 MHz, respectively (the frequency difference is approximately 7 kHz), as shown in FIG5 , which is a schematic diagram of two sets of frequency comb teeth provided in an embodiment of the present application;

[0079] For example, FIG5 is a schematic diagram showing the increasing frequency difference between two groups of comb teeth in the simulation frequency domain;

[0080] The two sets of frequency combs (frequency domain signals) are converted into time domain signals through inverse fast Fourier transform and superimposed to generate a preset time domain signal. The code of the generated preset time domain signal is then imported into a 60GS / s signal generator to generate an electrical signal consistent with the code. This electrical signal serves as the modulation signal of the optical intensity modulator to modulate the signal light branched from the laser.

[0081] After passing through the optical intensity modulator, the optical frequency dual-comb signal (optical signal) appears in the frequency domain as a series of optical frequency comb teeth consistent with the previous design. The dual combs beat each other at the demodulation end, achieving down-conversion and reducing the demodulation bandwidth requirement, thereby increasing the sampling rate and improving the temporal resolution of pulse detection.

[0082] After passing through the polarization controller, the optical frequency dual-comb signal directly enters the on-chip optical microcavity array. Each sensing unit in the array can generate an independent pulse signal. The on-chip optical microcavity array follows the path of the radial artery and fits it. The pulsation of the radial artery squeezes the on-chip optical microcavity array, causing the microcavities of the on-chip optical microcavity array to deform under force, resulting in a change in refractive index and a shift in the resonance peak. Based on the microring resonance formula 2πnR=mλ, the following relationship can be derived:

[0083] Where λ is the resonant wavelength of the microring resonator, Δλ is the change in the resonant wavelength, Δl is the waveguide deformation, l is the total length of the original waveguide, Δn is the change in the waveguide refractive index, and n is the refractive index of the original waveguide.

[0084] The pulse waveform is restored by monitoring the frequency shift using a frequency comb, as shown in FIG6 , which is a schematic diagram of the principle of frequency comb demodulation provided in an embodiment of the present application;

[0085] For example, as shown in Figure 6, the vertical axis represents the frequency domain image of a single frame acquired after dual-comb beats. The amplitude information of the pulse wave at that moment is read out based on the resonance peak depression in the frequency domain (the amplitude intensity corresponds to the resonance peak offset). The comb tooth spacing represents the vertical resolution of the pulse wave. The horizontal axis represents the continuous pulse information under continuous long-term sampling. The sampling rate of each frame of the spectrum image is the horizontal resolution of the pulse wave. The thick solid line represents the restored pulse wave signal.

[0086] Because the sensing units of the on-chip optical microcavity array (taking two sensing units as an example) are placed in a certain order, and each sensing unit generates a set of sensing signals, there will be a corresponding time difference between the two sets of sensing signals. Based on the principle of the wave velocity method, the continuous time difference is analyzed and substituted into the wave velocity-blood pressure model formula to obtain the blood pressure value;

[0087] Since the chip itself has certain losses plus the loss of package coupling, it needs to be amplified by an erbium-doped fiber amplifier subsequently; the amplified optical signal and the previously branched reference light enter the coherent receiver for demodulation, and finally the frequency comb data is collected by the oscilloscope to restore the waveform. The principle is shown in Figures 7 and 8. Figure 7 is a schematic diagram of long-term stable measurement data provided by an embodiment of the present application, and Figure 8 is a schematic diagram of the time difference between two sets of pulse waves provided by an embodiment of the present application.

[0088] For example, the pulse wave velocity method is based on the Moens-Korteweg equation, which gives the relationship between the pulse wave velocity PWV and the elastic modulus Ein of the arterial wall, and the expression is:

[0089] Where h is the thickness of the arterial wall, ρ is the blood density, and r is the arterial radius. The elastic modulus Ein of the arterial wall is directly related to blood pressure, and the relationship is:

[0090] E in =E0e γP

[0091] Where P is mean blood pressure (MBP).

[0092] Combined with the Bramwell-Hill formula, we can further obtain the values ​​of systolic blood pressure (SBP) and diastolic blood pressure (DBP):

[0093] Where PTT is the propagation time, A is the empirical mean of individual-specific differences, which can be determined through extensive data analysis. SBP0, DBP0, and PTT0 are preset initial values ​​for systolic blood pressure, diastolic blood pressure, and propagation time, respectively, and can also be calibrated along with other initial values. By identifying the time difference between two points at each time using the frequency comb method, continuous noninvasive blood pressure measurement can be achieved. Figure 9 shows the average blood pressure over 10 seconds at one-hour intervals.

[0094] In some implementation scenarios, actual experiments have shown that the on-chip optical microcavity combined with the digital optical dual-comb system of the present invention can accurately detect pulses, accurately identifying characteristic parameter points such as the main wave, dicrotic wave, and descending isthmus of the pulse wave, as well as the time delay between the two sets of data. The use of the digital optical frequency comb system makes array-based pulse detection more convenient. Furthermore, by derivation of the above formula, accurate systolic and diastolic pulse pressures can be obtained, providing a more accurate and convenient optical array-based blood pressure measurement method.

[0095] In all embodiments of the present application, "big" and "small" are relative, "more" and "less" are relative, and "up" and "down" are relative. The expressions of such relative terms will not be elaborated in the embodiments of the present application.

[0096] It should be understood that the phrases “in this embodiment,” “in an embodiment of the present application,” or “as an optional implementation” mentioned throughout the specification mean that specific features, structures, or characteristics related to the embodiment are included in at least one embodiment of the present application. Therefore, “in this embodiment,” “in an embodiment of the present application,” or “as an optional implementation” appearing throughout the specification do not necessarily refer to the same embodiment. In addition, these specific features, structures, or characteristics may be combined in one or more embodiments in any suitable manner. Those skilled in the art should also be aware that the embodiments described in the specification are all optional embodiments, and the actions and modules involved are not necessarily required for the present application.

[0097] In the various embodiments of the present application, it should be understood that the size of the serial numbers of the above-mentioned processes does not necessarily mean the order of execution. The order of execution of each process should be determined by its function and internal logic, and should not constitute any limitation on the implementation process of the embodiments of the present application.

[0098] The above description is merely a specific embodiment of the present application, but the scope of protection of the present application is not limited thereto. Any modifications or substitutions that can be easily conceived by a person skilled in the art within the technical scope disclosed in the present application should be included in the scope of protection of the present application. Therefore, the scope of protection of the present application should be based on the scope of protection of the claims.

Claims

1. An arrayed microcavity blood pressure detection system based on digital optical frequency dual comb, characterized in that: The device comprises a laser, a waveform generator, a light intensity modulator, a polarization controller, an on-chip optical microcavity array and a signal processing mechanism; the input end of the light intensity modulator is respectively connected to the laser and the waveform generator, the output end of the light intensity modulator, the polarization controller and the on-chip optical microcavity array are connected in sequence, the laser emits a single-frequency light of a preset frequency, the waveform generator generates an electrical modulation signal based on a preset time domain signal, and the preset time domain signal is obtained by inverse Fourier transform and superposition of two groups of frequency comb signals with a preset comb tooth interval and a preset frequency difference; The light intensity modulator modulates the single-frequency light based on the electrical modulation signal to obtain an optical frequency dual-comb signal; the optical frequency dual-comb signal enters the on-chip optical microcavity array after passing through the polarization controller, the on-chip optical microcavity array fits the position of the artery to be measured, the on-chip optical microcavity array includes a plurality of sensor units, each of the sensor units generates an independent pulse signal, the on-chip optical microcavity array obtains a sensor signal based on the optical frequency dual-comb signal and the beating and squeezing of the position of the artery to be measured, and the signal processing mechanism obtains blood pressure value information based on the sensor signal.

2. The arrayed microcavity blood pressure detection system based on digital optical frequency dual comb according to claim 1 is characterized in that: The signal processing mechanism comprises an erbium-doped fiber amplifier, and the erbium-doped fiber amplifier is connected to the on-chip optical microcavity array.

3. The arrayed microcavity blood pressure detection system based on digital optical frequency dual comb according to claim 2 is characterized in that: The signal processing mechanism also includes a coherent receiver, which is connected to the erbium-doped fiber amplifier and the laser respectively.

4. The arrayed microcavity blood pressure detection system based on digital optical frequency dual comb according to claim 3 is characterized in that: The signal processing mechanism further includes an oscilloscope, which is connected to the coherent receiver.

5. The arrayed microcavity blood pressure detection system based on digital optical frequency dual comb according to claim 1 is characterized in that: The sensing signal satisfies the following relationship: Wherein, λ is the resonant wavelength of the microring resonator of the on-chip optical microcavity array, Δλ is the change in the resonant wavelength, Δl is the waveguide deformation, l is the total length of the original waveguide, Δn is the change in the waveguide refractive index, and n is the refractive index of the original waveguide.

6. The arrayed microcavity blood pressure detection system based on digital optical frequency dual comb according to claim 1 or 5, characterized in that: The on-chip optical microcavity array includes two sensing units, each of which generates a set of sensing signals. Blood pressure value information is obtained by analyzing the two sets of sensing signals and the continuous time difference between the two sets of sensing signals based on the wave velocity method.

7. The arrayed microcavity blood pressure detection system based on digital optical frequency dual comb according to claim 1 is characterized in that: The artery position to be measured is the radial artery position.

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