CN112155543A - Hyperspectral imaging-based multi-physiological parameter detection device and method - Google Patents

Abstract

The invention discloses a multi-physiological parameter detection device and method based on hyperspectral imaging, which can realize two-dimensional imaging of changes in multiple physiological parameters such as tissue blood flow, tissue blood oxygen saturation, tissue oxygen uptake rate, tissue oxygen metabolism rate, etc. . The present invention uses lasers with multiple wavelengths to irradiate the near-infrared band light source to the surface of the measured tissue, uses a hyperspectral imager to non-contact scanning to obtain the light intensity changes of multiple wavelengths in the imaging area of the measured tissue, and uses the diffusion correlation spectrum and Based on the light intensity data matrix, diffuse optical spectroscopy calculates the changes of tissue blood flow and tissue oxygen saturation in each pixel, thereby realizing two-dimensional imaging of multiple physiological parameters. In addition, the present invention can use the hyperspectral imager to complete the measurement of light intensity changes at multiple wavelengths, which not only improves the detection accuracy of changes in multiple physiological parameters, but also facilitates the selection of detection wavelengths, and can realize multiple physiological parameters without involving optical switches. Variation in 2D imaging.

Description

A device and method for detecting multiple physiological parameters based on hyperspectral imaging

technical field

The invention relates to the technical field of biomedical engineering, in particular to a multi-physiological parameter detection device and method based on hyperspectral imaging.

Background technique

Tissue blood flow (Blood Flow, BF), tissue oxygen saturation (Oxygen Saturation, StO ₂ ), tissue oxygen uptake fraction (Oxygen Extraction Fraction, OEF) and tissue oxygen metabolism rate (MRO ₂ ) and many other physiological parameters, all were It is a parameter closely related to physiological and pathological states, an important indicator to measure whether the body is normal or not, and has key guiding significance in the diagnosis and treatment of brain diseases, breast cancer and cardiovascular diseases ^[1-2] . Among many physiological parameters, the detection of tissue blood flow and tissue oxygen saturation is particularly important, because other parameters related to tissue oxygen uptake and tissue oxygen metabolism can be derived and calculated on the basis of the two. Therefore, other relevant physiological parameters can be detected by satisfying the detection of tissue blood flow and tissue blood oxygen.

In terms of tissue blood flow detection, Laser Doppler (LD) has a low penetration depth, Magnetic Resonance Imaging (MRI) has low temporal resolution, and cannot perform real-time bedside diagnosis for a long time. Technology (Positron Emission Tomography, PET) has radiation damage. The near-infrared spectrum (650nm-950nm) has good penetration to biological tissues, and the main chromophores of biological tissues such as water, hemoglobin and fat have relatively weak absorption in the near-infrared band, which is beneficial to the detection of deep tissue blood flow . Based on this, Diffuse Correlation Spectroscopy (DCS) uses the near-infrared spectrum to illuminate the tissue surface, and calculates the motion state of red blood cells in the tissue by calculating the light intensity autocorrelation function of the scattered light spots on the tissue surface, and calculates the blood flow index ( Blood Flow Index, BFI), so as to achieve quantitative detection of changes in tissue blood flow (Blood Flow, BF) ^[3-5] . Compared with the existing blood flow detection technology, diffusion correlation spectroscopy has the advantages of non-invasive, real-time, long-term bedside detection, low cost, easy operation, etc., and can be widely used in the detection of deep tissue blood flow. In tissue blood oxygen detection, Near Infrared Spectroscopy (NIRS), also known as Diffuse Optical Spectroscopy (DOS), is relatively mature and has great advantages. The technology utilizes near-infrared spectral properties to achieve non-invasive measurement of hemoglobin (HbO ₂ ), deoxyhemoglobin (Hb) and blood oxygen saturation (StO ₂ ) in deep biological tissues, and is widely used in brain diseases, breast cancer and cardiovascular diseases in the early diagnosis of ^[6-7] .

Hyperspectral imaging technology ^[8-9] combines spectral analysis and optical imaging, which can not only obtain the external structural information of the measured object, but also provide information on the change of the component content of the measured object with its high-resolution spectrum. . The present invention combines hyperspectral imaging technology with diffusion correlation spectroscopy and diffusion optical spectroscopy, and uses a hyperspectral imager to scan in a non-contact manner on the basis of diffusion correlation spectroscopy tissue blood flow measurement and diffusion optical spectroscopy tissue blood oxygen saturation measurement. Obtain the light intensity changes of multiple wavelengths in the imaging area of the measured tissue, and calculate the tissue blood flow changes and tissue oxygen saturation changes of each pixel on the basis of the light intensity data matrix, and then calculate the tissue oxygen uptake. Changes in other relevant physiological parameters such as fraction, tissue oxygen metabolism rate, etc., so as to realize two-dimensional imaging of multiple physiological parameters.

references:

[1] Le Oux P. “Physiological Monitoring of the Severe Traumatic Brain Injury Patient in the Intensive Care Unit,” Current Neurology and Neuroscience Reports, 13(3):331 (2013).

[2] Busch D R, Lynch J M, Winters M E, et al, “Cerebral Blood FlowResponse to Hypercapnia in Children with Obstructive Sleep Apnea Syndrome,” Sleep, 39(1):209-216 (2016).

[3] T. Durduran and A.G. Yodh, “Diffuse correlation spectroscopy for non-invasive, micro-vascular cerebral blood flow measurement,” Neuroimage 85, 51, Elsevier Inc. (2014).

[4] W.B. Baker et al., “Effects of exercise training on calf muscleoxygen extraction and blood flow in patients with peripheral artery disease,” J.Appl.Physiol.123(6),1599–1609(2017).

[5] Z.Li et al., “Calibration of diffuse correlation spectroscopy bloodflow index with venous-occlusion diffuse optical spectroscopy in skeletalmuscle,” J.Biomed.Opt.20(12),125005(2015).

[6] Giovannell M, Contini D, Pagliazzi M, et al., "BabyLux Device: ADiffuse Optical System Integrating Diffuse Correlation Spectroscopy and Time-Resolved Near-Infrared Spectroscopy for the Neuromonitoring of the PrematureNewborn Brain," Neurophotonics, 6(02) :025007(2019).

[7] A. Tank et al., "Diffuse optical spectroscopic imaging reveals distinct early breast tumor hemodynamic responses to metronomic and maximumtolerated dose regimens," Breast Cancer Res. 22(1), 1-10, (2020).

[8] Calin M A, Parasca S V, Savastru D, Manea D, "Hyperspectral Imaging in the Medical Field: Present and Future," Applied Spectroscopy Reviews, 49(6), 435-447 (2014).

[9] Ortega, Samuel, et al. “Detecting brain tumor in pathological slides using hyperspectral imaging,” Biomedical Optics Express 9(2), 818 (2018).

SUMMARY OF THE INVENTION

The present invention provides a multi-physiological parameter detection device and method based on hyperspectral imaging, which aims to organically integrate hyperspectral imaging technology, diffusion correlation spectroscopy technology and diffusion optical spectroscopy technology, in the diffusion correlation spectroscopy tissue blood flow measurement and the diffusion optical spectroscopy tissue On the basis of blood oxygen saturation measurement, two-dimensional imaging of multiple physiological parameters such as tissue blood flow and tissue oxygen saturation can be achieved by using a hyperspectral imager.

See the description below for details:

A device and method for detecting multiple physiological parameters based on hyperspectral imaging, the device comprising:

(1) The light source module is composed of a long coherent laser in the near-infrared band. The laser is output by fiber coupling. The near-infrared light generated by the laser is transmitted through the N-1 light source fiber and then irradiated to the surface of the tested tissue. Among them, the laser wavelength can adopt different wavelengths in the near-infrared band; the number of lasers is the same as the number of optical fiber input ends of the light source, both being N.

(2) The detection module is a hyperspectral imager, which is used to detect the scattered light intensity of the measured tissue after being irradiated by a light source. Specifically, the light intensity of the light source spectrum scattered by the measured tissue is measured by a hyperspectral imager, and the light intensity at different pixels at different wavelengths is collected by non-contact scanning; after completing one scan of the imaging area, continue In the next scan, the measurement of the light intensity of the measured tissue at different time points is realized in a continuous detection manner. Therefore, the hyperspectral imager can obtain the light intensity data matrix of different pixels in the imaging area of the measured tissue that changes with time at different wavelengths, so as to prepare for the subsequent data analysis and processing by the host computer.

(3) The host computer module is a computer. Due to the need to process the near-infrared spectral light intensity data matrix obtained by the hyperspectral imager, the amount of data is large, and it needs to be completed by a workstation with higher computing power. First, the obtained light intensity data matrix is pre-processed, and the tissue blood flow changes and tissue oxygen saturation at each pixel are calculated based on the light intensity data matrix based on diffusion correlation spectroscopy and diffusion optical spectroscopy. Then, the changes of other related physiological parameters such as tissue oxygen uptake fraction and tissue oxygen metabolism rate are calculated, and then a two-dimensional image of multiple physiological parameters is obtained.

Further, the long coherent laser in the light source module of the present invention adopts optical fiber coupling output, its power is greater than 50mW, the coherence length is more than 10m, the wavelength range is 650nm-950nm, and the center wavelength can be selected as 685nm, 785nm or 830nm, Multimode fiber conduction. Among them, the number of lasers is N.

Further, the detection module of the present invention is a hyperspectral imager, the wavelength range is 400nm-1000nm, the spectral resolution is 3.5nm, the detection element is a CCD, the number of pixels is 1600×1200, and the frame frequency is 33fps-247fps. The hyperspectral imager is placed on the surface of the measured tissue during measurement, and does not contact the measured tissue. The distance between the two is determined by the size of the imaging area of the measured tissue and the focal length of the hyperspectral imager.

Further, the light source fiber described in the present invention is an N-to-1 multimode fiber, that is, there are N fibers at the input end of the light source that are respectively connected to N lasers, and the N fibers are combined into one port output during transmission, irradiating the laser beam. Tissue surface. Wherein, the core diameter of the multimode optical fiber used is 50 μm, 62.5 μm, 100 μm or more.

Further, the host computer of the present invention calculates the tissue blood flow index, the oxygenated hemoglobin concentration and the deoxyhemoglobin concentration changes based on the different degrees of light intensity attenuation under multiple different wavelengths, and on the basis of the two parameters, calculates the tissue blood flow. Flow changes, tissue oxygen saturation, tissue oxygen uptake fraction, tissue oxygen metabolism rate, so as to achieve two-dimensional imaging of multiple physiological parameters.

Further, the tissue blood flow index calculation formula of the present invention is:

In the formula, K _t =δ _t /<I> is the time speckle contrast, δ _t is the standard deviation of the light intensity, <I> is the average intensity of the light intensity, and <> represents the average over time.

Further, the relationship between tissue blood flow and blood flow index according to the present invention is as follows:

BF=γBFI

Among them, BF is the tissue blood flow, the unit is mL·100mL ^-1 ·min ^-1 ; BFI is the blood flow index, the unit is cm ² /s; γ is the proportionality constant, the unit is (mL·100mL ^-1 ·min ^{-1 )} )/(cm ² /s).

Further, the blood oxygen saturation calculation formula of the present invention is:

为氧合血红蛋白浓度，C_Hb为脱氧血红蛋白的浓度。In the formula,

is the concentration of oxyhemoglobin, and _CHb is the concentration of deoxyhemoglobin.

Further, the relationship between tissue oxygen metabolism rate, tissue oxygen saturation, and tissue blood flow described in the present invention is:

rMRO ₂ =rOEF×rBF

In the formula, r represents the relative change, that is, rMRO ₂ is the relative oxygen metabolism rate, rOEF is the relative oxygen uptake fraction, and rBF is the relative blood flow.

beneficial effect

The invention provides a multi-physiological parameter detection device and method based on hyperspectral imaging. The near-infrared band light source is irradiated to the surface of the measured tissue by means of lasers with multiple wavelengths, and the measured tissue imaging is obtained by non-contact scanning using a hyperspectral imager. The light intensity changes of multiple wavelengths in the area, and the tissue blood flow changes and tissue oxygen saturation changes of each pixel are calculated on the basis of the light intensity data matrix based on the diffusion correlation spectrum and the diffusion optical spectrum, so as to achieve multi-physiological 2D imaging of parameters. In addition, the measurement probe of this device is a hyperspectral imager, which can complete the measurement at different positions without contacting the measured tissue, and can complete the measurement of light intensity changes under multiple wavelengths, which is not only conducive to improving the changes in tissue blood flow And the detection accuracy of tissue oxygen saturation changes, but also helps to optimize the measurement wavelength. It should be noted that the present invention does not involve an optical switch, and the two-dimensional imaging of multiple physiological parameters can be realized without completing the switching of the optical path through the optical switch. The transformation lays the foundation.

Description of drawings

FIG. 1 is a schematic diagram of a multi-physiological parameter detection device system based on hyperspectral imaging;

Figure 2 is a schematic diagram of the light intensity data matrix measured by the hyperspectral imager;

In the accompanying drawings, the list of components represented by each number is as follows:

1: Laser (685nm) 2: Laser (785nm)

3: Laser (830nm) 4: N-1 light source fiber

5: Tested tissue 6: Hyperspectral imager

7: Cable 8: Computer

Detailed ways

In order to make the objectives, technical solutions and advantages of the present invention clearer, the embodiments of the present invention will be further described in detail below with reference to specific embodiments and accompanying drawings.

The present invention provides a multi-physiological parameter detection device based on hyperspectral imaging. FIG. 1 shows a system block diagram of the multi-physiological parameter detection device based on hyperspectral imaging according to the present invention, and the device includes:

Lasers (1), (2), (3), the wavelength can be selected between 650nm-950nm, the coherence length is greater than 10m, and the power is greater than 50mW. In the embodiments of the present disclosure, the center wavelengths of the lasers are listed as 685 nm, 785 nm, and 830 nm, respectively, and other wavelengths, such as wavelengths in the near-infrared band such as 808 nm, can be selected according to actual requirements.

The N-1 light source optical fiber (4) is a multimode optical fiber with a core diameter of 50 μm, 62.5 μm, 100 μm or more. The input end of the optical fiber is N optical fibers, which are respectively connected to N lasers. During transmission, the N optical fibers are combined into one port (ie, a fiber probe) for output, which illuminates the surface of the tissue to be measured.

The measured tissue (5) is the biological tissue to be measured, such as the human body parts such as the brain, breast, and skeletal muscle, but is not limited to the above-mentioned tissues.

A hyperspectral imager (6) has a wavelength range of 400nm-1000nm, a spectral resolution of 3.5nm, a detection element of a CCD, a number of pixels of 1600×1200, and a frame rate of 33fps to 247fps. The hyperspectral imager is placed on the surface of the measured tissue during measurement, and does not contact the measured tissue. The distance between the two is determined by the size of the imaging area of the measured tissue and the focal length of the hyperspectral imager.

Cable (7) for data transmission.

The computer (8), after preprocessing the obtained light intensity data matrix, calculates the tissue blood flow change and tissue blood oxygenation of each pixel on the basis of the light intensity data matrix based on the diffusion correlation spectrum and the diffuse optical spectrum Saturation changes, and then calculate the changes of other related physiological parameters such as tissue oxygen uptake fraction, tissue oxygen metabolism rate, etc., and then obtain a two-dimensional image of multiple physiological parameters and display them.

Further, the present invention also provides a multi-physiological parameter detection method based on hyperspectral imaging, and the detection of the changes of the multi-physiological parameters can be completed by using the device. Specific steps are as follows:

Step 1: Fix the fiber probe of the N-1 light source fiber on the surface of the tissue to be tested, and connect the N input ends of the light source fiber to N lasers respectively; place the hyperspectral imager above the surface of the tissue to be tested, not connected to the tissue to be tested. The tissue contact is measured, and the distance between the two is determined by modulating parameters such as the area of the imaging area and the focal length of the hyperspectral imager.

Step 2: After the optical fiber probe and the hyperspectral imager are fixed in the first step, turn on the laser and the hyperspectral imager. The imager detects the changes of light intensity scattered by the measured tissue after being irradiated by the light source. First, the spatial information and spectral information of the measured tissue are obtained through spatial scanning, that is, the information of each pixel in the imaging area and the light intensity of multiple wavelengths under each pixel; then, the time-dependent change of the above information is completed by continuous measurement. The measurement, that is, the change of light intensity with time under different wavelengths of each pixel is measured. Specifically, as shown in Figure 2, the three-dimensional coordinate axis in Figure 2 shows a schematic diagram of the light intensity data matrix measured by the hyperspectral imager, wherein the X axis represents the spatial horizontal orientation, the Y axis represents the spatial vertical orientation, and the time axis is the sampling time. . From this, it can be seen that the light intensity data of multiple wavelengths at different spatial locations change with time. Each pixel also contains information of multiple wavelengths, and the number of wavelengths contained is consistent with the number of wavelengths of the laser light source. The schematic diagram shows the wavelengths of 685 nm, 785 nm, and 830 nm used in the embodiments of the present disclosure.

Step 3: The computer analyzes and processes the light intensity signal transmitted in Step 2, derives the tissue blood flow index, oxygenated hemoglobin concentration and deoxyhemoglobin concentration changes at different pixels, and calculates tissue oxygen saturation and tissue oxygen uptake fraction. , tissue oxygen metabolism rate and other related physiological parameters changes, and then a two-dimensional image of multiple physiological parameters is obtained and displayed.

Further, according to the multi-physiological parameter detection device and method based on hyperspectral imaging of the present invention, the specific calculation process of tissue blood flow, tissue blood oxygen saturation, tissue oxygen uptake fraction and tissue oxygen metabolism rate is as follows:

Regarding the calculation of the tissue blood flow index, the calculation formula has been introduced as follows:

In the formula, K _t =δ _t /<I> is the time speckle contrast, δ _t is the standard deviation of the light intensity, <I> is the average intensity of the light intensity, and <> represents the average over time.

In this embodiment, the center wavelengths of the lasers are 685 nm, 785 nm, and 830 nm, respectively. When calculating the tissue blood flow index, the light intensity at any wavelength can be selected for calculation, or the tissue blood flow index at three wavelengths can be calculated separately, and then take Averaged as the final tissue blood flow index.

In order to calculate the relative tissue oxygen metabolic rate (rMRO ₂ ), the tissue blood flow index (BFI) and relative tissue blood flow (rBF) are first calculated here.

The relationship between tissue blood flow (BF) and tissue blood flow index (BFI) is as follows:

BF=γBFI

Among them, BF is blood flow, the unit is mL·100mL ^-1 ·min ^-1 ; BFI is the blood flow index, the unit is cm ² /s; γ is the proportionality constant, the unit is (mL·100mL ^-1 ·min ^-1 ) /(cm ² /s).

The formula for calculating relative blood flow (rBF) is as follows:

Among them, BF ₀ and BFI ₀ represent the blood flow and blood flow index at the initial time, respectively. Therefore, the tissue blood flow change can be obtained from the change of the tissue blood flow index.

According to the modified Lambert Beer's law, the formulas for calculating the changes in the concentration of oxyhemoglobin and deoxyhemoglobin are as follows:

为氧合血红蛋白浓度变化，ΔC_Hb(t)为脱氧血红蛋白的浓度变化，

分别代表氧合血红蛋白与脱氧血红蛋白在波长λ₁和λ₂下对应的摩尔消光系数，I(λ₁,t)与I(λ₁,t)分别代表在波长为λ₁和λ₂时刻为t时的光强，

与

分别代表波长λ₁与λ₂对应的路径差分因子。in,

is the change in the concentration of oxyhemoglobin, ΔC _Hb (t) is the change in the concentration of deoxyhemoglobin,

represent the molar extinction coefficients of oxyhemoglobin and deoxyhemoglobin at wavelengths λ ₁ and λ ₂ , respectively, I(λ ₁ ,t) and I(λ ₁ ,t) represent t at wavelengths λ ₁ and λ ₂ , respectively time light intensity,

and

represent the path difference factors corresponding to wavelengths λ ₁ and λ ₂ , respectively.

In this embodiment, the center wavelengths of the lasers are 685 nm, 785 nm, and 830 nm, respectively, and two wavelengths are arbitrarily selected to calculate changes in the concentration of oxyhemoglobin and deoxyhemoglobin. In addition, it is also possible to use 685nm and 785nm, 785nm and 830nm, and 685nm and 830nm to calculate the changes in the concentration of oxyhemoglobin and deoxyhemoglobin in the three groups, and then average them to obtain the final changes in the concentration of oxyhemoglobin and deoxyhemoglobin. .

Calculation formula for tissue oxygen saturation

Can be converted to:

为氧合血红蛋白浓度，C_Hb为脱氧血红蛋白的浓度，

与C_Hb(0)分别代表初始时刻(即t＝0时)氧合血红蛋白浓度和脱氧血红蛋白的浓度。In the formula,

is the concentration of oxyhemoglobin, C _Hb is the concentration of deoxyhemoglobin,

and _CHb (0) represent the oxyhemoglobin concentration and the deoxyhemoglobin concentration at the initial time (ie, t=0), respectively.

Regarding the calculation of fractional tissue oxygen uptake, the relative change rOEF is:

In the formula, SaO ₂ is the arterial blood oxygen saturation, SaO ₂ (0) and SaO ₂ (t) represent the arterial blood oxygen saturation at the initial time (ie t=0) and time t, respectively, StO ₂ (0) and StO ₂ (t) represents the tissue oxygen saturation at the initial time (ie, when t=0) and time t, respectively. Usually, it can be assumed that SaO ₂ =1, so the relative oxygen uptake fraction rOEF can be expressed as:

Regarding the calculation of tissue oxygen metabolism rate, the relationship between tissue oxygen metabolism rate, tissue oxygen saturation, and tissue blood flow has been introduced as follows:

rMRO ₂ =rOEF×rBF

In the formula, r represents the relative change, that is, rMRO ₂ is the relative oxygen metabolism rate, rOEF is the relative oxygen uptake fraction, and rBF is the relative blood flow.

Then, the relative tissue oxygen metabolic rate (rMRO ₂ ) can be obtained as:

In the formula, StO ₂ (0) and StO ₂ (t) represent the tissue oxygen saturation at the initial time (ie, when t=0) and time t, respectively, and rBF is the relative blood flow.

Finally, it should be noted that although the present invention is described with reference to the current preferred embodiments, those skilled in the art should understand that the above preferred embodiments are only used to illustrate the present invention, not to limit the present invention. Any modification, equivalent replacement, improvement, etc. made within the scope of the spirit and principle of the present invention shall be included in the protection scope of the group of the present invention.

Claims (10)

1. A multi-physiological-parameter detection device based on hyperspectral imaging is characterized by comprising a light source module, an N-1 light source optical fiber, a detection module and an upper computer;

the light source module is N near-infrared band long coherent lasers, different wavelengths are required among the lasers, the output is carried out in an optical fiber coupling mode, and N is more than or equal to 2;

the N-1 light source optical fiber is used for merging the spectrums output by the N lasers into one optical fiber probe and irradiating the near infrared light generated by output to the surface of the tested tissue;

the detection module is a hyperspectral imager and is used for receiving the scattered light spot intensity on the surface of the measured tissue body after being irradiated by a near infrared light source and adopting a non-contact measurement mode with the measured tissue;

the upper computer calculates the tissue blood flow index, the oxygen-containing hemoglobin concentration and the deoxyhemoglobin concentration of each pixel based on the difference of the light intensity attenuation degrees under different wavelengths, calculates the physiological parameter changes of the tissue blood oxygen saturation, the tissue oxygen uptake fraction and the tissue oxygen metabolic rate according to the three, and realizes the two-dimensional display of multiple physiological parameters.

2. The multi-physiological-parameter detection device based on hyperspectral imaging according to claim 1, characterized in that the long coherent laser has a coherence length of more than 10m and a wavelength range of 650nm to 950 nm; the N-1 light source optical fiber is a multimode optical fiber, and the core diameter is 50 μm, 62.5 μm, 100 μm or more.

3. The device for detecting multiple physiological parameters based on hyperspectral imaging according to claim 1 is characterized in that the hyperspectral imager has a wavelength range of 400nm to 1000nm, a spectral resolution of 3.5nm, a detection element of a CCD (charge coupled device), a pixel count of 1600 x 1200 and a frame rate of 33fps to 247 fps.

4. A hyperspectral imaging-based multi-physiological-parameter detection method is a hyperspectral imaging-based multi-physiological-parameter detection device, and is characterized by comprising the following steps:

(1) fixing a light source fiber probe on the surface of a measured tissue, placing a hyperspectral imager above the measured tissue, and determining the distance between the hyperspectral imager and the measured tissue according to the requirement;

(2) turning on a laser, irradiating the near infrared spectrum to the surface of the measured tissue through the conduction of a light source optical fiber, measuring the near infrared spectrum intensity of the corresponding position of the measured tissue by a hyperspectral imager in a non-contact manner, and uploading data to an upper computer; specifically, spatial information and spectral information of the tissue to be detected are obtained through spatial scanning, namely information of each pixel in an imaging area and light intensity of multiple wavelengths under each pixel; then, the measurement of the change of the spectral information along with the time is finished by adopting a continuous measurement mode, namely the change of the light intensity along with the time under different wavelengths of each pixel is measured;

(3) the computer calculates the light intensity data transmitted in the second step, and deduces the tissue blood flow index BFI and the change of the concentration of the oxygenated hemoglobin at different pixel positions

And change in deoxygenated hemoglobin concentration Δ C_Hb(t), further calculating to obtain tissue blood oxygen saturation StO₂(t), relative tissue oxygen uptake fraction rOEF, relative tissue oxygen metabolism rate rMRO₂The physiological parameters are changed, and then two-dimensional images of multiple physiological parameters are obtained and displayed.

5. The hyperspectral imaging-based multi-physiological-parameter detection method according to claim 4, wherein the tissue Blood Flow Index (BFI) is calculated by the formula:

in the formula, K_t＝_t/<I>For the purpose of temporal speckle contrast,_tin order to obtain the standard deviation of the light intensity,<I>is the average intensity of the light intensity,<>the representations are averaged over time.

6. The hyperspectral imaging-based multi-physiological-parameter detection method according to claim 4, wherein the calculation formula of the change of the oxygenated hemoglobin concentration and the deoxygenated hemoglobin concentration is as follows:

wherein,

for change in oxygenated hemoglobin concentration,. DELTA.C_Hb(t) isThe concentration of the deoxygenated hemoglobin is changed,

respectively represents oxyhemoglobin and deoxyhemoglobin at wavelength lambda₁And λ₂The lower corresponding molar extinction coefficient, I (. lamda.)₁T) and I (λ)₁And t) respectively represent at a wavelength of λ₁And λ₂The light intensity at the time t,

and

respectively represent the wavelength lambda₁And λ₂The corresponding path difference factor.

7. The hyperspectral imaging-based multi-physiological-parameter detection method according to claim 4, wherein the formula for calculating the tissue blood oxygen saturation level is

In the formula,

for oxyhemoglobin concentration, C_HbIn order to obtain the concentration of the deoxygenated hemoglobin,

and C_Hb(0) Respectively representing the oxyhemoglobin concentration and the deoxyhemoglobin concentration at the initial time (i.e., when t is 0).

8. The hyperspectral imaging-based multi-physiological-parameter detection method according to claim 4, wherein the calculation formula of the relative tissue oxygen uptake fraction is as follows:

wherein StO₂(0) Representing the tissue blood oxygen saturation at the initial time (i.e., when t is 0).

9. The hyperspectral imaging-based multi-physiological-parameter detection method according to claim 4, wherein the calculation formula of the relative tissue oxygen metabolism rate is as follows:

rMRO₂＝rOEF×rBF

wherein rBF is the relative tissue blood flow, and the specific calculation formula is as follows:

wherein, BF₀Representing the blood flow at the initial time of day,

BF is tissue blood flow, and is expressed as mL 100mL^-1·min^-1The specific calculation formula is as follows:

BF＝γBFI

wherein gamma is a proportionality constant having a unit of (mL 100 mL)^-1·min^-1)/(cm²S) is so

Wherein, BF₀And BFI₀Since the blood flow and the blood flow index at the initial time are represented, the change in tissue blood flow can be determined from the change in tissue blood flow index.

10. The hyperspectral imaging-based multi-physiological-parameter detection method according to claim 4, characterized in that: the distance between the light source optical fiber and the hyperspectral imager and the distance between the measured tissue imaging area and the hyperspectral imager influence the position and the depth of the change measurement of the multiple physiological parameters.

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