Device and method for monitoring cerebral blood oxygen saturation

Abstract

The present invention relates to a device and method for monitoring the cerebral blood oxygen saturation. The device comprises a power supply and modulation module, a light source module, a light guide module, an optical detection module, and a data processing and analysis module; under the action of the power supply and modulation module, light emitted by the light source module is transmitted into an area to be monitored within the brain of a test subject by means of a transmission optical fiber of the light guide module; after the light optically interacts with the brain tissue in said area within the brain of the test subject, a portion of the light enters the transmission optical fiber; the transmitted light is received by the optical detection module and processed by the data processing and analysis module to calculate and obtain continuous blood oxygen saturation data. The device and method for monitoring the cerebral blood oxygen saturation of the present invention adopt a spectroscopy method with a relatively direct measurement principle, are designed and developed using an optical fiber recording technology with a deep measurement depth and a minor impact on the activities of the test subject, and thus can be used for real-time blood oxygen saturation monitoring in an animal brain including the deep brain structure.

Description

Brain blood oxygen saturation monitoring device and method

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS

[0002] This application claims priority to the Chinese patent application (application number 202410296935.2) filed on March 15, 2024, the entire contents of which are incorporated herein by reference. Technical Field

[0003] The present invention relates to the field of brain blood oxygen saturation monitoring, and more specifically to a device and method for real-time monitoring of brain blood oxygen saturation based on spectroscopy and optical fiber recording technology. Background Art

[0004] A large amount of neural activity in the brain relies on the brain's rich vascular network to provide energy, so brain metabolism, represented by blood oxygen saturation, can be used to reflect the neural activity of the corresponding brain area. Studies have shown that when neurons are excited, the blood oxygen saturation information in the vicinity will change synchronously, which is called the neurovascular coupling effect. Therefore, real-time measurement of blood oxygen saturation information in the animal brain can, on the one hand, serve as supplementary information to reflect the neural activity of the brain area, and on the other hand, it can be used to explore the metabolic mechanism by which stimuli such as drugs affect neural activity.

[0005] In current scientific research, functional near-infrared spectroscopy (fNIRS), functional magnetic resonance imaging (fMRI), and oxygen-sensitive fluorescent probes are primarily used to measure blood oxygenation in the brains of experimental animals. fNIRS utilizes the difference in absorption spectra between oxyhemoglobin (HbO) and deoxyhemoglobin (HbR) to calculate blood oxygen saturation at specific locations in the cerebral cortex by measuring the surface absorption coefficient of brain tissue to light of different wavelengths. fMRI utilizes the different magnetic field response characteristics of HbO and HbR to measure blood oxygen saturation distribution throughout the brain in vitro using an external, large magnetic field. Oxygen-sensitive fluorescent probes utilize fluorescent dyes whose fluorescence efficiency responds to oxygen. These are integrated into the tip of an optical fiber and implanted in a specific brain region to measure oxygen partial pressure in vivo.

[0006] Of the three common methods for measuring blood oxygen saturation, oxygen-sensitive fluorescent probes detect oxygen partial pressure within tissues rather than directly measuring blood oxygen saturation, and therefore cannot directly reflect metabolic changes in the circulatory system. fMRI requires a large magnetic field generator, which occupies a large area, is not portable, is incompatible with many experimental procedures, and is expensive. fNIRS spectroscopy can more conveniently reflect changes in blood oxygen saturation in specific brain regions. However, the surface testing characteristics of existing fNIRS devices and the low penetration of light in tissues limit their testing depth, making it difficult to measure deep brain structures and, therefore, unable to study more comprehensive brain activity.

[0007] SUMMARY OF THE INVENTION

[0008] The present invention aims to solve one of the technical problems existing in the related art at least to a certain extent.

[0009] An object of the present invention is to provide a blood oxygen saturation monitoring device based on spectroscopy and fiber optic recording technology, which can be used for real-time blood oxygen saturation monitoring of animal brains including deep brain structures.

[0010] Another object of the present invention is to provide a method for monitoring blood oxygen saturation using the above device.

[0011] To achieve the above-mentioned objectives, the present invention first provides a brain blood oxygen saturation monitoring device, comprising a power supply and modulation module, a light source module, a light guide module, an optical detection module, and a data processing and analysis module;

[0012] The power supply and modulation module controls the light source module to alternately emit light of at least two wavelengths, and sends an indication signal containing wavelength information and corresponding light emission time to the data processing and analysis module;

[0013] The light guide module has at least one transmission optical fiber, which is used to transmit the light emitted by the light source module as incident light to the area to be monitored in the brain of the subject, and to receive the outgoing light from the area to be monitored in the brain and transmit it to the optical detection module;

[0014] The optical detection module is used to convert the optical signal of the emitted light into an electrical signal and send it to the data processing and analysis module;

[0015] The data processing and analysis module processes the electrical signal transmitted by the optical detection module based on the indication signal transmitted by the power supply and modulation module, calculates the HbO and HbR concentration change information of the brain area to be monitored, and thereby calculates the blood oxygen saturation information of the brain area to be monitored.

[0016] It should be noted that the above-mentioned brain area to be monitored is located in a single brain region or multiple brain regions on the same side of the subject's brain.

[0017] In the present invention, brain region refers to brain functional partition, specifically partition 1-52 according to Brodmann partition, including but not limited to somatosensory cortex, primary motor cortex, somatosensory association cortex, premotor cortex, somatosensory association cortex, frontal lobe eye movement area, dorsolateral prefrontal cortex, frontopolar region, orbitofrontal region, insula, primary visual cortex, visual association cortex, inferior temporal gyrus, middle temporal gyrus, superior temporal gyrus, ventral posterior cingulate cortex, ventral anterior cingulate cortex, subgenual cortex, extrasplenial area, posterior entorhinal cortex, postsplenial cingulate cortex, dorsal posterior cingulate cortex, dorsal anterior cingulate cortex, anterior olfactory cortex, paraolfactory cortex, parahippocampal cortex, fusiform gyrus, temporal polar region, angular gyrus, supramarginal gyrus, primary auditory cortex, auditory association cortex, subcentral region, operculum, pars triangularis, dorsolateral prefrontal lobe, inferior frontal gyrus, posterior inferior crus, parainsular cortex, etc.

[0018] The subject can be a mammal, and the mammal can be an animal selected from bovines, equines, felines, canines, lagomorphs, porcines, camelids, rodents and primates, including but not limited to cattle, horses, goats, sheep, cats, rabbits, pigs, camels, alpacas, rats, mice, guinea pigs, non-human primates (such as apes, monkeys, baboons, orangutans) and humans, preferably cattle, horses, dogs, goats, sheep, pigs, camels, rats, mice, monkeys and humans. Preferably, the mammal is an experimental animal, including but not limited to mice, rats, rabbits, guinea pigs, hamsters, monkeys, dogs, cats, pigs, sheep, horses, etc.

[0019] The outgoing light received by the transmission optical fiber is the light after the incident light transmitted from the transmission optical fiber to the area to be monitored in the brain is absorbed and reflected by the area to be monitored in the brain.

[0020] In the present invention, the light guide module may have only a single transmission optical fiber, the transmission optical fiber including a front end portion and a rear end portion, wherein the front end portion of the transmission optical fiber is configured as an implantation portion implanted in the area to be monitored in the brain;

[0021] The rear end portion of the transmission optical fiber is arranged outside the body of the subject to be tested as a retention portion;

[0022] The light source module and the optical detection module are connected to the rear end of the transmission optical fiber through a first optical fiber combiner.

[0023] In the present invention, the light guide module may also have at least two transmission optical fibers, and when having at least two transmission optical fibers, the transmission optical fibers will be respectively configured as an incoming transmission optical fiber and an outgoing transmission optical fiber, the incoming transmission optical fiber and the outgoing transmission optical fiber of the light guide module each include a front end portion and a rear end portion, and the front end portion of the incoming transmission optical fiber and the front end portion of the outgoing transmission optical fiber are respectively configured as implantation portions implanted in the area to be monitored in the brain;

[0024] The rear end portion of the incoming transmission optical fiber and the rear end portion of the outgoing transmission optical fiber are arranged outside the body of the subject to be tested as retention portions;

[0025] The light source module is connected to the rear end of the incoming transmission optical fiber; and the optical detection module is connected to the rear end of the outgoing transmission optical fiber.

[0026] Regardless of whether the light guide module is composed of a single transmission optical fiber or at least two transmission optical fibers, it is only necessary to implant the front end of the transmission optical fiber into the subject's body, and leave the rear end of the transmission optical fiber outside the subject's body. The remaining parts, including the power supply and modulation module, light source module, optical detection module, and data processing and analysis module, are all external. When testing is required, they are connected to the rear end of the transmission optical fiber according to the above connection relationship. This has two effects. One is that the operation is more convenient. During non-monitoring time, removing all external devices will not have a significant impact on the subject's activities. The other is that it can save costs. When conducting large-scale experiments, it is not necessary to configure the entire monitoring device for each subject separately.

[0027] To meet the need for a light source module capable of emitting light at multiple wavelengths, the light source module of the present invention comprises at least two fiber-coupled LEDs, each emitting light at a different central wavelength. Regardless of whether the light guide module comprises a single transmission fiber, two transmission fibers, or even more, each LED must be connected to the same transmission fiber. Therefore, the LEDs of the present invention are combined and connected to the transmission fiber via a second fiber combiner.

[0028] It should be noted that when the light guide module has only a single transmission optical fiber, the rear end of the transmission optical fiber is already connected to the first optical fiber combiner. At this time, the second optical fiber combiner is connected to the first optical fiber combiner. When the light guide module has at least two transmission optical fibers, the second optical fiber combiner is connected to the incoming transmission optical fiber.

[0029] In the present invention, the power supply and modulation module is driven by a reference voltage source, controls the analog switch to switch alternately according to the input control signal, drives multiple constant current sources to output current alternately, and the LEDs are electrically connected to the constant current sources in a one-to-one correspondence.

[0030] In the present invention, the optical detection module includes a photodetector coupled to the transmission optical fiber, a transimpedance amplifier, a voltage buffer module, an analog-to-digital conversion module and a computer. The light intensity signal transmitted by the transmission optical fiber is converted into a photocurrent signal by the photodetector, and then converted into an amplified voltage signal by the transimpedance amplifier. After being buffered by the voltage buffer module, it is transmitted to the computer through the analog-to-digital conversion module and stored on the computer to obtain an electrical signal of light intensity changing with time.

[0031] Another aspect of the present invention provides a method for monitoring brain blood oxygen saturation using the above-mentioned device, comprising the following steps:

[0032] S1. Under the action of the power supply and modulation module, the light emitted by the light source module is transmitted to the monitored area in the subject's brain through the transmission optical fiber of the light guide module;

[0033] S2. The outgoing light from the area to be monitored is received by the optical detection module, and is processed by the data processing and analysis module to calculate and obtain continuous blood oxygen saturation data.

[0034] It should be noted that, in the above method, the outgoing light from the area to be detected is a portion of the incident light after optical interaction with brain tissue in the area to be monitored.

[0035] In the present invention, in order to subsequently solve the blood oxygen saturation calculation equation, at least two wavelengths of light need to be emitted. Although emitting light of more wavelengths can obtain more information, for the sake of simplicity of calculation, the light source module of the present invention is composed of two fiber-coupled LEDs, and the two LEDs emit light of different wavelengths, respectively denoted as A and B.

[0036] The light guide module in the present invention can be composed of different numbers of transmission optical fibers, including a single transmission optical fiber and two or more transmission optical fibers. Different light guide module configurations use the same principles, but the subsequent blood oxygen saturation calculation equation is different.

[0037] Specifically, in a configuration in which the light guide module has a single transmission optical fiber, the transmission optical fiber is used to transmit the light emitted by the light source module as incident light to the area to be monitored in the brain of the subject, and is also used to receive the outgoing light from the area to be monitored in the brain and transmit it to the optical detection module;

[0038] The method for the data processing and analysis module to calculate the blood oxygen saturation information of the brain area to be monitored is:

[0039] First, based on the indication signal transmitted by the power supply and modulation module, the two wavelengths of light are identified and the continuous light intensity signals of the two independent wavelengths are obtained, which are recorded as I A (t) and I B (t);

[0040] Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value:

[0041] Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and ΔcHbR :

[0042] in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ;

[0043] Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

[0044] In another configuration of the light guide module, there is no substantial difference in whether the light guide module is composed of two transmission optical fibers or more transmission optical fibers, but the light guide module has at least one incoming transmission optical fiber and one outgoing transmission optical fiber.

[0045] Thus, the light guide module has at least two transmission optical fibers, which are respectively configured as an incoming transmission optical fiber and an outgoing transmission optical fiber, wherein the incoming transmission optical fiber is used to transmit the light emitted by the light source module as incident light to the area to be monitored in the brain of the subject, and the outgoing transmission optical fiber is used to receive the outgoing light from the area to be monitored in the brain and transmit it to the optical detection module;

[0046] The method for the data processing and analysis module to calculate the blood oxygen saturation information of the brain area to be monitored is:

[0047] First, the light intensity of different wavelengths is identified by referring to the state of the indicator signal, and the continuous light intensity signals of two independent wavelengths are obtained, which are recorded as I A (t) and I B (t);

[0048] Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value:

[0049] Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR :

[0050] Where ρ is the distance between the incoming transmission fiber and the outgoing transmission fiber; is the molar absorption coefficient of substance i at wavelength λ, λ=(A, B), i=(HbO, HbR); DPF is the constant optical path difference factor that is only related to wavelength λ;

[0051] Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

[0052] When the light guide module has only one transmission optical fiber, the front end of the transmission optical fiber is arranged at the edge of the area to be detected in the brain and is facing the area to be detected; when the light guide module has two transmission optical fibers, the incoming transmission optical fiber and the outgoing transmission optical fiber are separately arranged on both sides of the area to be monitored in the brain along the long axis of the area to be monitored. The distance between the front end of the incoming transmission optical fiber and the front end of the outgoing transmission optical fiber depends on the length of the long axis of the area to be monitored, and can be measured by imaging techniques such as micro-CT, or estimated based on the depth and angle of implantation, with a value range of 50-5000μm.

[0053] Technical effect: The brain blood oxygen saturation monitoring device and method of the present invention adopts a spectroscopy method with a relatively direct measurement principle, and is designed and developed using fiber optic recording technology with a deep measurement depth and little impact on the activities of the subject. It can be used for real-time blood oxygen saturation monitoring of animal brains, including deep brain structures, and solves the problem of shallow measurement depth and indirect measurement principle of existing animal brain blood oxygen saturation measurement equipment, and proposes a new solution for animal brain blood oxygen saturation measurement. Compared with the existing technology, the present invention can achieve direct measurement of deep brain blood oxygen saturation of the subject to be tested, and obtain real-time metabolic information of the subject's specific brain area when the subject performs various behaviors. In addition, this device is compatible with other fiber optic recording devices, and uses the same fiber optic implantation method as mainstream fiber optic recording equipment, and the device has excellent versatility. BRIEF DESCRIPTION OF THE DRAWINGS

[0054] In order to more clearly illustrate the technical solutions in the present invention or the prior art, a brief introduction will be given below to the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0055] FIG1 is a schematic structural diagram of a brain blood oxygen saturation monitoring device according to the present invention.

[0056] FIG2 is a schematic diagram of an optional embodiment of the light guide module of the present invention and its optical relationship with peripheral modules.

[0057] FIG3 is a schematic diagram of another optional embodiment of the light guide module of the present invention and the optical relationship between the light guide module and the peripheral modules.

[0058] FIG4 is a schematic structural diagram of the power supply and modulation module in the present invention.

[0059] FIG5 is a schematic structural diagram of an optical detection module of the present invention.

[0060] FIG6 is a flowchart of data processing and analysis according to the present invention.

[0061] FIG7 a is a schematic diagram of the implantation positions of electrodes and optical fibers in a mouse hippocampus blood oxygen saturation test model;

[0062] FIG7 b is a graph showing changes in the inhaled oxygen content (top) and the blood oxygen saturation in the hippocampus (bottom) of mice;

[0063] FIG7 c is a graph showing changes in blood oxygen saturation in the hippocampus when electrical stimulation is performed using electrodes.

[0064] FIG8 is a schematic structural diagram of an electronic device of the present invention. Modes for Carrying Out the Invention

[0065] In order to make the purpose, technical solutions and advantages of the present invention clearer, the technical solutions of the present invention will be clearly and completely described below in conjunction with the drawings in the present invention. Obviously, the embodiments described are part of the embodiments of the present invention, not all of the embodiments, and they should not be understood as limitations on the present invention. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of the present invention. In the description of the present invention, it should be understood that the terms used are only for descriptive purposes and cannot be understood as indicating or implying relative importance.

[0066] It should be noted that although the flowcharts illustrate a logical order, those skilled in the art will appreciate that the steps shown or described may be performed in a different order than that shown in the flowcharts. The terms "first," "second," and so on used in the specification, claims, and drawings are used solely to distinguish between different objects and are not intended to describe a specific order or precedence.

[0067] Currently, functional near-infrared spectroscopy (fNIRS), functional magnetic resonance imaging (fMRI), and oxygen-sensitive fluorescent probes are primarily used to measure blood oxygen saturation in the brains of experimental animals. Of the three common methods for measuring blood oxygen saturation, oxygen-sensitive fluorescent probes detect the partial pressure of oxygen within tissues rather than directly measuring blood oxygen saturation, and therefore cannot directly reflect metabolic changes in the circulatory system. fMRI requires a large magnetic field generator, which occupies a large area, is unportable, incompatible with many experimental procedures, and is expensive. fNIRS spectral measurements can more conveniently reflect changes in blood oxygen saturation in specific brain regions. However, the surface testing characteristics of existing fNIRS devices and the low penetration of light in tissues result in low testing depths, making it difficult to measure deep brain structures and unable to be used to study more comprehensive brain activity information.

[0068] Therefore, in order to obtain blood oxygen saturation information of an animal's brain including deep brain structures, the present invention provides a brain blood oxygen saturation monitoring device and method.

[0069] In the following embodiments, although emitting light with more wavelengths can obtain more information, for the sake of simplicity in calculation, the light source module of the present invention is composed of two fiber-coupled LEDs, and the two LEDs emit light with different wavelengths.

[0070] Brain blood oxygen saturation monitoring device

[0071] Example 1:

[0072] 1 , this embodiment provides a brain blood oxygen saturation monitoring device, including a power supply and modulation module, a light source module, a light guide module, an optical detection module, and a data processing and analysis module.

[0073] The power supply and modulation module is shown in Figure 4. It is driven by a reference voltage source and controls the analog switch to switch on and off alternately according to the input control signal, driving the constant current sources of the two LEDs to output current alternately.

[0074] At the same time, the power supply and modulation module outputs an indication signal synchronized with the control signal to the data processing and analysis module, which is used to indicate which wavelength LED is turned on at the moment.

[0075] The light source module consists of two fiber-coupled LEDs, which emit light with a central wavelength of 660nm and 810nm respectively. The two emit light alternately under the control of the power supply and modulation module.

[0076] The two LEDs are integrated through the second optical fiber combiner and connected to the transmission optical fiber through the first optical fiber combiner.

[0077] As shown in FIG2 , the light guide module has a single transmission optical fiber including a front end and a rear end.

[0078] The front end of the transmission optical fiber is configured as an implantation part implanted in the area to be monitored in the brain; the rear end of the transmission optical fiber is arranged outside the body of the subject to be tested as a retention part.

[0079] The light source module and the optical detection module are connected to the rear end portion of the transmission optical fiber through a first optical fiber combiner.

[0080] The optical detection module is shown in Figure 5 and consists of a photodetector (PD) coupled to a transmission fiber, a transimpedance amplifier (IV), a voltage buffer module (BUF), an analog-to-digital conversion module (ADC), and a computer (PC).

[0081] The input of this module is the signal light transmitted by the optical fiber, and the output is the value of the light intensity changing with time recorded on the PC end.

[0082] After the light intensity signal enters the module, it is first converted into a photocurrent signal by the PD, and then converted into an amplified voltage signal by the IV. After being buffered by the BUF, it is transmitted to the PC through the ADC and stored on the PC to obtain the electrical signal I(t) of the light intensity changing with time.

[0083] The data processing and analysis module processes the electrical signal transmitted by the optical detection module based on the indication signal transmitted by the power supply and modulation module, calculates the HbO and HbR concentration change information of the brain area to be monitored, and thereby calculates the blood oxygen saturation information of the brain area to be monitored.

[0084] Example 2:

[0085] This embodiment provides another brain blood oxygen saturation monitoring device, including a power supply and modulation module, a light source module, a light guide module, an optical detection module, and a data processing and analysis module.

[0086] The power supply and modulation module is shown in Figure 4. It is driven by a reference voltage source and controls the analog switch to switch on and off alternately according to the input control signal, driving the constant current sources of the two LEDs to output current alternately.

[0087] At the same time, the power supply and modulation module outputs an indication signal synchronized with the control signal to the data processing and analysis module, which is used to indicate which wavelength LED is turned on at the moment.

[0088] The light source module consists of two fiber-coupled LEDs, which emit light with a central wavelength of 660nm and 810nm respectively. The two emit light alternately under the control of the power supply and modulation module.

[0089] The two LEDs are combined through a second fiber combiner and connected to the incoming transmission fiber.

[0090] As shown in FIG3 , the light guide module has two transmission optical fibers, which are respectively configured as an incoming transmission optical fiber and an outgoing transmission optical fiber. The incoming transmission optical fiber and the outgoing transmission optical fiber of the light guide module each include a front end and a rear end.

[0091] The front end of the incoming transmission optical fiber and the front end of the outgoing transmission optical fiber are respectively configured as implantation parts implanted in the area to be monitored in the brain. The rear end of the incoming transmission optical fiber and the rear end of the outgoing transmission optical fiber are arranged as indwelling parts outside the body of the subject to be tested.

[0092] The light source module is connected to the rear end of the incoming transmission optical fiber; and the optical detection module is connected to the rear end of the outgoing transmission optical fiber.

[0093] The optical detection module is shown in Figure 5 and consists of a photodetector (PD) coupled to a transmission fiber, a transimpedance amplifier (IV), a voltage buffer module (BUF), an analog-to-digital conversion module (ADC), and a computer (PC).

[0094] The input of this module is the signal light transmitted by the optical fiber, and the output is the value of the light intensity changing with time recorded on the PC end.

[0095] After the light intensity signal enters the module, it is first converted into a photocurrent signal by the PD, and then converted into an amplified voltage signal by the IV. After being buffered by the BUF, it is transmitted to the PC through the ADC and stored on the PC to obtain the electrical signal I(t) of the light intensity changing with time.

[0096] The data processing and analysis module processes the electrical signal transmitted by the optical detection module based on the indication signal transmitted by the power supply and modulation module, calculates the HbO and HbR concentration change information of the brain area to be monitored, and thereby calculates the blood oxygen saturation information of the brain area to be monitored.

[0097] Brain blood oxygen saturation monitoring method

[0098] Example 3:

[0099] This embodiment provides a brain blood oxygen saturation monitoring method based on the brain blood oxygen saturation monitoring device of Example 1, including the following steps:

[0100] S1. Under the action of the power supply and modulation module, the light source module emits light with a central wavelength of 660nm and 810nm respectively, and transmits the light to the monitored area in the subject's brain through the transmission optical fiber of the light guide module;

[0101] S2, the light guide module has a single transmission optical fiber, which is used to transmit the light emitted by the light source module as incident light to the area to be monitored in the brain of the subject, and is also used to receive the outgoing light from the area to be monitored in the brain and transmit it to the optical detection module;

[0102] The incident light emitted by the transmission fiber is absorbed and scattered in the area to be monitored in the subject's brain, and a portion of it is transmitted back to the transmission fiber;

[0103] S3. The outgoing light is received by the optical detection module and processed by the data processing and analysis module to calculate and obtain continuous blood oxygen saturation data. The specific method is shown in Figure 6:

[0104] First, the light intensity of different wavelengths is identified by referring to the state of the indicator signal, and the continuous light intensity signals of two independent wavelengths are obtained, which are recorded as I 660 (t) and I 810 (t);

[0105] Then divide the two by the initial value I(t0) at the start of the measurement to calculate the relative optical density (ΔOD) compared to the initial value:

[0106] Then substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR :

[0107] is the molar absorption coefficient of substance i at wavelength λ, λ = (660, 810), i = (HbO, HbR); L is the constant optical path length factor that is only related to wavelength λ;

[0108] Finally, Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

[0109] Example 4:

[0110] This embodiment provides a brain blood oxygen saturation monitoring method based on the brain blood oxygen saturation monitoring device of Example 2, including the following steps:

[0111] S1. Under the action of the power supply and modulation module, the light source module emits light with a central wavelength of 660nm and 810nm respectively;

[0112] S2, the light guide module has two transmission optical fibers, which are respectively configured as an incoming transmission optical fiber and an outgoing transmission optical fiber, wherein the incoming transmission optical fiber is used to transmit the light emitted by the light source module as incident light to the area to be monitored in the brain of the subject, and the outgoing transmission optical fiber is used to receive the outgoing light from the area to be monitored in the brain and transmit it to the optical detection module;

[0113] The incident light emitted by the incoming transmission fiber is absorbed and scattered in the area to be monitored in the subject's brain, and a portion of it enters the outgoing transmission fiber;

[0114] S3. The outgoing light is received by the optical detection module and processed by the data processing and analysis module to calculate and obtain continuous blood oxygen saturation data. The specific method is shown in Figure 6:

[0115] First, the light intensity of different wavelengths is identified by referring to the state of the indicator signal, and the continuous light intensity signals of two independent wavelengths are obtained, which are recorded as I 660 (t) and I 810 (t);

[0116] Then divide the two by the initial value I(t0) at the start of the measurement to calculate the relative optical density (ΔOD) compared to the initial value:

[0117] Then substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR :

[0118] Wherein ρ is the distance between the incoming transmission fiber and the outgoing transmission fiber. The value of this distance can be obtained by, but is not limited to, measuring it using imaging techniques such as micro-CT, estimating it based on the depth and angle of implantation, etc.; is the molar absorption coefficient of substance i at wavelength λ, λ = (660, 810), i = (HbO, HbR); DPF is the constant optical path difference factor that is only related to wavelength λ;

[0119] Finally, Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

[0120] Verification of the effectiveness of brain blood oxygen saturation monitoring device and method

[0121] In order to verify the effectiveness of the device and method of the present invention, the following experiments were performed:

[0122] In the mouse hippocampus, changes in blood oxygen saturation are caused by neural activity induced by electrical stimulation. The stimulating electrode was implanted in the CA1 region of the mouse hippocampus, and two implanted optical fibers were implanted in the CA3 region on the same side to measure blood oxygen saturation (Figure 7a). By changing the proportion of oxygen in the inhaled gas of the mouse, the blood oxygen saturation in the CA3 region changed accordingly (Figure 7b). When electrical stimulation was performed in the CA1 region, fluctuations in blood oxygen saturation were detected in the CA3 region (Figure 7c), which is consistent with the literature conclusion that there is a projection relationship between the two regions.

[0123] The present invention does not require the prior expression of fluorescent substances in the subject's brain, nor does it require prior fluorescence treatment of the optical fiber. Typical fiber-optic recording devices inject excitation light through optical fibers into the brain of an animal containing a fluorescent substance. The fluorescent substance absorbs the excitation light and emits fluorescence. The fluorescence intensity measured by the light detector can reflect the concentration of the analyte. The present invention does not require any specific animal. It only requires the intracranial implantation of two universal optical fibers, which is more convenient to operate, avoids problems such as photobleaching, and can be used for a long time.

[0124] Compared to fNIRS, the present invention can measure blood oxygen saturation in deep brain structures, which are difficult to measure. Furthermore, established fNIRS equipment is mostly used to measure human brain activity, while mature equipment for animals, especially small animals such as mice, which are most commonly used in laboratories, is relatively rare. The present invention has a wider range of applications and is particularly suitable for measuring mice.

[0125] Compared to fMRI, the present invention is more convenient and less expensive. It can be installed in a research group laboratory without the need to borrow a public fMRI machine, which is more efficient and hassle-free. Furthermore, the present invention has better compatibility and avoids the problem of fMRI being difficult to use with other measurement equipment.

[0126] Compared to optical probes based on oxygen-sensitive fluorescent agents, the present invention measures blood oxygen saturation rather than oxygen partial pressure, providing a more direct reflection of the metabolic state of the target brain region. It also avoids photobleaching and allows for long-term measurement. Furthermore, the implantable consumable component of the present invention is a simple, disposable short optical fiber rather than a high-value oxygen-sensitive fluorescent probe, enabling batch implantation and continuous testing, enabling high-throughput experiments to be completed more efficiently and at a lower cost.

[0127] In addition, the implantable part of the present invention uses a short optical fiber consistent with the mainstream optical fiber recording equipment, which can be compatible with or even used in conjunction with the optical fiber recording equipment. It can not only support more complex experimental designs with more modal applications, but also can be flexibly modified as an optional module for existing optical fiber recording equipment. It has higher user communicability, making it easier to convert the original fluorescence recording equipment users into users of the present invention.

[0128] The present invention also includes the following embodiments:

[0129] 1. A method for monitoring brain blood oxygen saturation, comprising the following steps:

[0130] S1. transmitting incident light into the area to be monitored in the brain of the subject, wherein the incident light comprises light of at least two wavelengths;

[0131] S2. Receive and process the outgoing light from the area to be monitored to obtain continuous blood oxygen saturation data.

[0132] 2. The method according to embodiment 1, wherein the outgoing light from the area to be detected is a portion of the incident light after optical interaction with brain tissue in the area to be monitored.

[0133] 3. The method according to embodiment 1 or 2, wherein the treatment comprises the following steps:

[0134] Identify the two wavelengths of light and obtain the continuous light intensity signals of the two independent wavelengths, which are recorded as I A (t) and I B (t);

[0135] Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value:

[0136] Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR :

[0137] in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ;

[0138] Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

[0139] 4. A method according to any one of embodiments 1-3, wherein the optical signals in the incident light and the outgoing light are converted into electrical signals.

[0140] 5. The method according to any one of embodiments 1 to 4, wherein the subject is a mammal selected from the group consisting of bovines, equines, felines, canines, lagomorphs, porcines, camelids, rodents and primates, preferably cattle, horses, goats, sheep, cats, rabbits, pigs, camels, alpacas, rats, mice, guinea pigs, non-human primates (such as apes, monkeys, baboons, orangutans) and humans, more preferably cattle, horses, dogs, goats, sheep, pigs, camels, rats, mice, monkeys and humans; also preferably, experimental animals, for example, mice, rats, rabbits, guinea pigs, hamsters, monkeys, dogs, cats, pigs, sheep, horses, etc.

[0141] 6. A method according to any one of embodiments 1-5, wherein the area to be monitored in the brain is located in a brain region of the subject.

[0142] 7. The method according to embodiment 6, wherein the brain area to be monitored is located in a single brain region or multiple brain regions on the same side of the subject's brain.

[0143] 8. A method according to any one of embodiments 6-7, wherein the brain area is a brain functional partition, preferably a partition 1-52 according to Brodmann partition, more preferably selected from the group including the following items: somatosensory cortex, primary motor cortex, somatosensory association cortex, premotor cortex, somatosensory association cortex, frontal eye movement area, dorsolateral prefrontal cortex, frontopolar area, orbitofrontal area, insula, primary visual cortex, visual association cortex, inferior temporal gyrus, middle temporal gyrus, superior temporal gyrus, ventral posterior cingulate cortex, ventral anterior cingulate cortex, subgenual cortex, extrasplenial area, posterior entorhinal cortex, postsplenial cingulate cortex, dorsal posterior cingulate cortex, dorsal anterior cingulate cortex, anterior olfactory cortex, paraolfactory cortex, parahippocampal cortex, fusiform gyrus, temporal polar area, angular gyrus, supramarginal gyrus, primary auditory cortex, auditory association cortex, subcentral area, insular operculum, triangular area, dorsolateral prefrontal cortex, inferior frontal gyrus, inferior posterior crus, parainsular cortex, etc.

[0144] 9. An electronic device comprising a processor and a memory storing a computer program, wherein when the processor executes the computer program, a method comprising the following steps:

[0145] Obtaining incident light data transmitted into a region to be monitored in the brain of a subject and outgoing light data transmitted from the region to be monitored in the brain, wherein the incident light data and the outgoing light data each include wavelength information and corresponding luminescence time;

[0146] The output light data is processed by the following steps to obtain continuous blood oxygen saturation data:

[0147] Identify the two wavelengths of light and obtain the continuous light intensity signals of the two independent wavelengths, which are recorded as I A (t) and I B(t);

[0148] Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value:

[0149] Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR :

[0150] in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ;

[0151] Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

[0152] 10. The electronic device of embodiment 9, wherein the incident light comprises light of at least two wavelengths.

[0153] 11. The electronic device according to embodiment 9 or 10, wherein optical signals in the incident light and the outgoing light are converted into electrical signals.

[0154] 12. An electronic device according to any one of embodiments 9-11, wherein the outgoing light is a portion of the incident light after optical interaction with brain tissue in the area to be monitored.

[0155] 13. An electronic device according to any one of embodiments 9 to 12, wherein the subject is a mammal selected from the group consisting of bovines, equines, felines, canines, lagomorphs, porcines, camelids, rodents and primates, preferably cattle, horses, goats, sheep, cats, rabbits, pigs, camels, alpacas, rats, mice, guinea pigs, non-human primates (such as apes, monkeys, baboons, orangutans) and humans, more preferably cattle, horses, dogs, goats, sheep, pigs, camels, rats, mice, monkeys and humans; also preferably, experimental animals, for example, mice, rats, rabbits, guinea pigs, hamsters, monkeys, dogs, cats, pigs, sheep, horses, etc.

[0156] 14. An electronic device according to any one of embodiments 9-13, wherein the area to be monitored in the brain is located in a brain region.

[0157] 15. An electronic device according to embodiment 14, wherein the brain region is a single brain region or multiple brain regions on the same side of the subject's brain.

[0158] 16. An electronic device according to any one of embodiments 9-15, wherein the brain area is a brain functional partition, preferably a partition 1-52 according to Brodmann partition, and more preferably selected from the group including the following items: somatosensory cortex, primary motor cortex, somatosensory association cortex, premotor cortex, somatosensory association cortex, frontal eye movement area, dorsolateral prefrontal cortex, frontopolar region, orbitofrontal region, insula, primary visual cortex, visual association cortex, inferior temporal gyrus, middle temporal gyrus, superior temporal gyrus, ventral posterior cingulate cortex, ventral anterior cingulate cortex, subgenual cortex, extrasplenial area, posterior entorhinal cortex, postsplenial cingulate cortex, dorsal posterior cingulate cortex, dorsal anterior cingulate cortex, anterior olfactory cortex, paraolfactory cortex, parahippocampal cortex, fusiform gyrus, temporal polar region, angular gyrus, supramarginal gyrus, primary auditory cortex, auditory association cortex, subcentral region, insular operculum, triangular region, dorsolateral prefrontal cortex, inferior frontal gyrus, inferior posterior crus, parainsular cortex, etc.

[0159] 17. A non-transitory computer-readable storage medium having a computer program stored thereon, wherein when the computer program is executed by a processor, a method comprising the following steps:

[0160] Obtaining incident light data transmitted into a region to be monitored in the brain of a subject and outgoing light data transmitted from the region to be monitored in the brain, wherein the incident light data and the outgoing light data each include wavelength information and corresponding luminescence time, and the incident light includes light of at least two wavelengths;

[0161] The output light data is processed by the following steps to obtain continuous blood oxygen saturation data:

[0162] Identify the two wavelengths of light and obtain the continuous light intensity signals of the two independent wavelengths, which are recorded as I A (t) and I B (t);

[0163] Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value:

[0164] Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR :

[0165] in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ;

[0166] Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

[0167] 18. A computer program product, comprising a computer program, the computer program being storable on a non-transitory computer-readable storage medium, and wherein when the computer program is executed by a processor, the computer is capable of performing a method comprising the following steps:

[0168] Obtaining incident light data transmitted into a region to be monitored in the brain of a subject and outgoing light data transmitted from the region to be monitored in the brain, wherein the incident light data and the outgoing light data each include wavelength information and corresponding luminescence time, and the incident light includes light of at least two wavelengths;

[0169] The output light data is processed by the following steps to obtain continuous blood oxygen saturation data:

[0170] Identify the two wavelengths of light and obtain the continuous light intensity signals of the two independent wavelengths, which are recorded as I A (t) and I B (t);

[0171] Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value:

[0172] Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR :

[0173] in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ;

[0174] Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

[0175] FIG8 illustrates a schematic diagram of the physical structure of an electronic device. As shown in FIG8 , the electronic device may include: a processor 810, a communications interface 820, a memory 830, and a communication bus 840. The processor 810, the communications interface 820, and the memory 830 communicate with each other via the communication bus 840. The processor 810 may call the logic instructions in the memory 830 to execute the methods described in the above-mentioned embodiments 9-16.

[0176] In addition, the logic instructions in the above-mentioned memory 830 can be implemented in the form of a software functional unit and can be stored in a computer-readable storage medium when sold or used as an independent product. Based on this understanding, the technical solution of the present invention, or the part that contributes to the prior art, or the part of the technical solution, can be embodied in the form of a software product. The computer software product is stored in a storage medium and includes several instructions for enabling a computer device (which can be a personal computer, server, or network device, etc.) to perform all or part of the steps of the method described in each embodiment of the present invention. The aforementioned storage medium includes: various media that can store program codes, such as a USB flash drive, a mobile hard disk, a read-only memory (ROM), a random access memory (RAM), a magnetic disk or an optical disk.

[0177] The device embodiments described above are merely illustrative. The units described as separate components may or may not be physically separate, and the components shown as units may or may not be physical units, i.e., they may be located in one location or distributed across multiple network units. Some or all of the modules may be selected based on actual needs to achieve the objectives of the present embodiment. Persons of ordinary skill in the art will be able to understand and implement the present invention without inventive effort.

[0178] Through the description of the above embodiments, those skilled in the art can clearly understand that each embodiment can be implemented by means of software plus a necessary general hardware platform, or of course, by hardware. Based on this understanding, the essence of the above technical solution or the part that contributes to the existing technology can be embodied in the form of a software product. The computer software product can be stored in a computer-readable storage medium, such as ROM / RAM, a magnetic disk, an optical disk, etc., and includes a number of instructions for enabling a computer device (which can be a personal computer, a server, or a network device, etc.) to execute the methods described in each embodiment or certain parts of the embodiments.

[0179] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the various embodiments of the present invention. Industrial Applicability

[0180] The brain blood oxygen saturation monitoring device and method of the present invention adopts a spectroscopy method with a relatively direct measurement principle, and is designed and developed using fiber optic recording technology with a deep measurement depth and little impact on the activities of the subject. It can be used for real-time blood oxygen saturation monitoring of animal brains, including deep brain structures, and solves the problems of shallow measurement depth and indirect measurement principle of existing animal brain blood oxygen saturation measurement equipment, and proposes a new solution for animal brain blood oxygen saturation measurement. Compared with the existing technology, the present invention can achieve direct measurement of deep brain blood oxygen saturation of the subject to be tested, and obtain real-time metabolic information of the subject's specific brain area when the subject performs various behaviors. In addition, this device is compatible with other fiber optic recording devices, and uses the same fiber optic implantation method as mainstream fiber optic recording equipment, and the device has excellent versatility.

Claims

1. A brain blood oxygen saturation monitoring device, comprising a power supply and modulation module, a light source module, a light guide module, an optical detection module, and a data processing and analysis module; The power supply and modulation module controls the light source module to alternately emit light of at least two wavelengths, and sends an indication signal containing wavelength information and corresponding light emission time to the data processing and analysis module; The light guide module has at least one transmission optical fiber, which is used to transmit the light emitted by the light source module as incident light to the area to be monitored in the brain of the subject, and to receive the outgoing light from the area to be monitored in the brain and transmit it to the optical detection module; The optical detection module is used to convert the optical signal of the emitted light into an electrical signal and send it to the data processing and analysis module; The data processing and analysis module processes the electrical signal transmitted by the optical detection module based on the indication signal transmitted by the power supply and modulation module, calculates the HbO and HbR concentration change information of the brain area to be monitored, and thereby calculates the blood oxygen saturation information of the brain area to be monitored.

2. The brain blood oxygen saturation monitoring device according to claim 1, wherein: The light guide module has a single transmission optical fiber, the transmission optical fiber includes a front end portion and a rear end portion, wherein the front end portion of the transmission optical fiber is configured to be implanted in the area to be monitored in the brain; The rear end portion of the transmission optical fiber is arranged outside the body of the subject to be tested as a retention portion; The light source module and the optical detection module are connected to the rear end of the transmission optical fiber through a first optical fiber combiner.

3. The brain blood oxygen saturation monitoring device according to claim 1, wherein: The light guide module has at least two transmission optical fibers, which are respectively configured as an incoming transmission optical fiber and an outgoing transmission optical fiber. The incoming transmission optical fiber and the outgoing transmission optical fiber of the light guide module each include a front end portion and a rear end portion. The front end portion of the incoming transmission optical fiber and the front end portion of the outgoing transmission optical fiber are respectively configured as implantation portions implanted in the area to be monitored in the brain. The rear end portion of the incoming transmission optical fiber and the rear end portion of the outgoing transmission optical fiber are arranged outside the body of the subject to be tested as retention portions; The light source module is connected to the rear end of the incoming transmission optical fiber; and the optical detection module is connected to the rear end of the outgoing transmission optical fiber.

4. The brain blood oxygen saturation monitoring device according to any one of claims 1 to 3, wherein: The light source module is composed of at least two fiber-coupled LEDs, each of which emits light with a different central wavelength. The LEDs are integrated through a second fiber combiner and connected to a transmission optical fiber.

5. The brain blood oxygen saturation monitoring device according to claim 4, wherein: The power supply and modulation module is driven by a reference voltage source, controls the analog switch to switch alternately according to the input control signal, drives multiple constant current sources to output current alternately, and the LEDs are electrically connected to the constant current sources in a one-to-one correspondence.

6. The brain blood oxygen saturation monitoring device according to any one of claims 1 to 3, wherein: The optical detection module includes a photodetector coupled to a transmission optical fiber, a transimpedance amplifier, a voltage buffer module, an analog-to-digital conversion module, and a computer. The light intensity signal transmitted by the transmission optical fiber is converted into a photocurrent signal by the photodetector, and then converted into an amplified voltage signal by the transimpedance amplifier. After being buffered by the voltage buffer module, it is transmitted to the computer through the analog-to-digital conversion module and stored on the computer to obtain an electrical signal of light intensity changing with time.

7. A method for monitoring brain blood oxygen saturation based on spectroscopy using the device according to any one of claims 1 to 6, comprising the following steps: S1. Under the action of the power supply and modulation module, the light emitted by the light source module is transmitted to the monitored area in the subject's brain through the transmission optical fiber of the light guide module; S2. The outgoing light from the area to be monitored is received by the optical detection module and processed by the data processing and analysis module to calculate and obtain continuous blood oxygen saturation data.

8. The method according to claim 7, wherein: The light source module is composed of two fiber-coupled LEDs, and the two LEDs emit light with central wavelengths A and B respectively.

9. The method according to claim 7, wherein: The light guide module has a single transmission optical fiber, which is used to transmit the light emitted by the light source module as incident light to the area to be monitored in the brain of the subject, and is also used to receive the outgoing light from the area to be monitored in the brain and transmit it to the optical detection module; The method for the data processing and analysis module to calculate the blood oxygen saturation information of the brain area to be monitored is: First, based on the indication signal transmitted by the power supply and modulation module, the two wavelengths of light are identified and the continuous light intensity signals of the two independent wavelengths are obtained, which are recorded as I A (t) and I B (t); Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value: Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR : in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ; Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment 10. The method according to claim 7, wherein: The light guide module has at least two transmission optical fibers, which are respectively configured as an incoming transmission optical fiber and an outgoing transmission optical fiber, wherein the incoming transmission optical fiber is used to transmit the light emitted by the light source module as incident light to the area to be monitored in the brain of the subject, and the outgoing transmission optical fiber is used to receive the outgoing light from the area to be monitored in the brain and transmit it to the optical detection module; The method for the data processing and analysis module to calculate the blood oxygen saturation information of the brain area to be monitored is: First, the light intensity of different wavelengths is identified by referring to the state of the indicator signal, and the continuous light intensity signals of two independent wavelengths are obtained, which are recorded as I A (t) and I B (t); Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value: Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR : Where ρ is the distance between the incoming transmission fiber and the outgoing transmission fiber; is the molar absorption coefficient of substance i at wavelength λ, λ=(A, B), i=(HbO, HbR); DPF is the constant optical path difference factor that is only related to wavelength λ; Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment 11. The method according to any one of claims 7 to 10, wherein: The outgoing light from the area to be detected is a portion of the incident light after optical interaction with brain tissue in the area to be monitored.

12. The method according to any one of claims 7 to 10, wherein: Optical signals in the incident light and the outgoing light are converted into electrical signals.

13. The method according to any one of claims 7 to 10, wherein: The subject is a mammal selected from the group consisting of bovines, equines, felines, canines, lagomorphs, porcines, camelids, rodents, and primates, preferably cattle, horses, goats, sheep, cats, rabbits, pigs, camels, alpacas, rats, mice, guinea pigs, non-human primates, and humans, more preferably cattle, horses, dogs, goats, sheep, pigs, camels, rats, mice, monkeys, and humans; further preferably, experimental animals, for example, mice, rats, rabbits, guinea pigs, hamsters, monkeys, dogs, cats, pigs, sheep, and horses.

14. The method according to any one of claims 7 to 10, wherein: The brain region to be monitored is located in the brain region of the subject.

15. The method according to claim 14, wherein The brain region to be monitored is located in a single brain region or multiple brain regions on the same side of the subject's brain.

16. The method according to claim 14 or 15, wherein: The brain region is a functional brain region, preferably a region 1-52 according to Brodmann's region, more preferably selected from the group comprising somatosensory cortex, primary motor cortex, somatosensory association cortex, premotor cortex, somatosensory association cortex, frontal eye movement area, dorsolateral prefrontal cortex, frontopolar region, orbitofrontal region, insula, primary visual cortex, visual association cortex, inferior temporal gyrus, middle temporal gyrus, superior temporal gyrus, ventral posterior cingulate cortex, ventral anterior cingulate cortex, subgenual cortex, extrasplenial area, posterior entorhinal cortex, postsplenial cingulate cortex, dorsal posterior cingulate cortex, dorsal anterior cingulate cortex, anterior olfactory cortex, paraolfactory cortex, parahippocampal cortex, fusiform gyrus, temporal polar region, angular gyrus, supramarginal gyrus, primary auditory cortex, auditory association cortex, subcentral region, pars opercularis, pars triangularis, dorsolateral prefrontal cortex, inferior frontal gyrus, posterior inferior crus, and parainsular cortex.

17. An electronic device comprising a processor and a memory storing a computer program, wherein when the processor executes the computer program, the method comprises the following steps: Obtaining incident light data transmitted into a region to be monitored in the brain of a subject and outgoing light data transmitted from the region to be monitored in the brain, wherein the incident light data and the outgoing light data each include wavelength information and corresponding luminescence time; The output light data is processed by the following steps to obtain continuous blood oxygen saturation data: Identify the two wavelengths of light and obtain the continuous light intensity signals of the two independent wavelengths, which are recorded as I A (t) and I B (t); Divide the two by the initial value I(t0) at the beginning of the measurement to calculate the relative optical density compared with the initial value. Degrees (ΔOD): Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR : in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ; Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment 18. The electronic device according to claim 17, wherein: The incident light includes light of at least two wavelengths.

19. The electronic device according to claim 17, wherein: Optical signals in the incident light and the outgoing light are converted into electrical signals.

20. The electronic device according to any one of claims 17 to 19, wherein: The outgoing light is a portion of the incident light after optical interaction with brain tissue in the area to be monitored.

21. A non-transitory computer-readable storage medium having a computer program stored thereon, wherein when the computer program is executed by a processor, the method comprises the following steps: Obtaining incident light data transmitted into a region to be monitored in the brain of a subject and outgoing light data transmitted from the region to be monitored in the brain, wherein the incident light data and the outgoing light data each include wavelength information and corresponding luminescence time, and the incident light includes light of at least two wavelengths; The output light data is processed by the following steps to obtain continuous blood oxygen saturation data: Identify the two wavelengths of light and obtain the continuous light intensity signals of the two independent wavelengths, which are recorded as I A (t) and I B (t); Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value: Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR : in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ; Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment 22. A computer program product, comprising a computer program, the computer program being storable on a non-transitory computer-readable storage medium, and wherein when the computer program is executed by a processor, the computer is capable of performing a method comprising the following steps: Obtaining incident light data transmitted into a region to be monitored in the brain of a subject and outgoing light data transmitted from the region to be monitored in the brain, wherein the incident light data and the outgoing light data each include wavelength information and corresponding luminescence time, and the incident light includes light of at least two wavelengths; The output light data is processed by the following steps to obtain continuous blood oxygen saturation data: Identify the two wavelengths of light and obtain the continuous light intensity signals of the two independent wavelengths, which are recorded as I A (t) and I B (t); Divide the two by the initial value I(t0) at the start of the measurement and calculate the relative optical density (ΔOD) compared to the initial value: Substitute ΔOD into the formula to calculate the relative concentration change Δc of HbO and HbR HbO and Δc HbR : in is the molar absorption coefficient of substance i at wavelength λ, λ=(A,B), i=(HbO,HbR); L is the constant optical path factor that is only related to wavelength λ; Δc HbO and Δc HbR Substitute the initial hemoglobin concentration c Hb (t0) and initial blood oxygen saturation Get blood oxygen saturation data at each moment

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