CN106618476B - A kind of eyeground blood flow method for detecting blood oxygen saturation based on face matrix LED - Google Patents
A kind of eyeground blood flow method for detecting blood oxygen saturation based on face matrix LED Download PDFInfo
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- 239000001301 oxygen Substances 0.000 title claims abstract description 70
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- INGWEZCOABYORO-UHFFFAOYSA-N 2-(furan-2-yl)-7-methyl-1h-1,8-naphthyridin-4-one Chemical compound N=1C2=NC(C)=CC=C2C(O)=CC=1C1=CC=CO1 INGWEZCOABYORO-UHFFFAOYSA-N 0.000 claims description 6
- 238000010521 absorption reaction Methods 0.000 claims description 6
- 108010002255 deoxyhemoglobin Proteins 0.000 claims description 6
- 238000001914 filtration Methods 0.000 claims description 5
- 108010064719 Oxyhemoglobins Proteins 0.000 claims description 3
- 210000003743 erythrocyte Anatomy 0.000 claims description 3
- 238000006213 oxygenation reaction Methods 0.000 claims description 3
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Abstract
The present invention relates to a kind of eyeground blood flow blood oxygen saturation detection device and method based on face matrix LED, which includes synchronous trigger source, data handling system, face matrix LED light source, spectroscope, connects mesh object lens, image-forming objective lens, CCD color cameras and the Baeyer filter on CCD color cameras；Face matrix LED light source is alternately composed in series by two kinds of wavelength LED light；Synchronous trigger source is used to send synchronizing signal to face matrix LED light source and CCD color cameras, when synchronizing signal is sent, the light that face matrix LED light source is simultaneously emitted by two kinds of wavelength reaches spectroscope, dichroic mirror light is to connecing mesh object lens and reach the eyeground of positive docking mesh object lens, light is again introduced into after fundus reflex to be connect mesh object lens and enters image-forming objective lens through spectroscope, and the collection of CCD color cameras, which passes through the speckle image of the light formation of two kinds of wavelength of image-forming objective lens and transmits it to data handling system, to be handled to obtain blood oxygen saturation.The present invention is high without any damage, the precision of the blood oxygen saturation of detection to human body.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to a fundus blood oxygen saturation detection method based on an area array LED.
Background
The blood oxygen saturation is the percentage of hemoglobin bound by oxygen, i.e. the percentage of oxygen content to oxygen capacity of hemoglobin, and is an important parameter of the respiratory cycle function, reflecting the blood oxygen balance of the human body. Some diseases can cause hypoxia to organs or tissues of a human body, cause abnormal metabolism of tissue cells and imbalance of homeostasis, seriously threaten human life, and the monitoring of the blood oxygen saturation of a patient can help to solve the problem. The fundus retina is part of the systemic microcirculation, it requires a supply of oxygen to maintain its normal metabolism, and it is sensitive to the reflection of blood oxygen changes, facilitating the monitoring of blood oxygen saturation.
At present, the blood oxygen saturation is mainly measured by an electrochemical method, the method comprises the steps of firstly taking blood from a human body (taking arterial blood), then carrying out electrochemical analysis on the blood by using a blood gas analyzer, directly measuring the arterial oxygen partial pressure (PaO2), and calculating the arterial oxygen saturation (SpO 2); however, this method requires arterial puncture or cannulation, is cumbersome, does not allow continuous monitoring, is a lesional oximetry, and is difficult to measure electrochemically at sites that are susceptible to injury. In addition, the method for monitoring the pulse blood oxygen saturation is easy to be interfered by light, such as sunlight and operating room light, the intensity of the obtained transmitted light is influenced if the light enters a detector during measurement, so that the accuracy of the blood oxygen saturation parameter is finally influenced, and the error of 3% can be achieved only when the value of a pulse oximeter is more than 83%.
Therefore, the existing methods for detecting the blood oxygen saturation have the problem of low detection precision, and improvement is needed.
Disclosure of Invention
The invention aims to overcome the defects of the prior art and provides a fundus blood oxygen saturation detection method based on an area array LED, which can measure the blood oxygen saturation of the human fundus blood flow in a non-contact way without any damage to the human body, and has the advantages of high signal-to-noise ratio of the shot image, high spatial resolution and high precision of the detected blood oxygen saturation.
In order to solve the technical problems, the invention adopts the technical scheme that:
an area array LED-based fundus blood oxygen saturation detection method comprises the following steps:
s1, setting the acquisition speed and the exposure time of a CCD color camera to ensure that local concentration change causes movement when red blood cells enter and exit the imaging range of a pixel unitA change in the intensity of the modal speckle interference; directly facing the eyes to the ocular objective; s2. synchronization trigger source with frequency f0Sending n times of synchronous signals to the area array LED light source and the CCD color camera, triggering the area array LED light source n times and simultaneously sending out a wavelength lambda1And λ2The light reaches the spectroscope, the spectroscope reflects the light to the eye objective and reaches the eye ground, the light enters the eye objective again after being reflected from the eye ground and enters the imaging objective through the spectroscope, and simultaneously, the CCD color camera is triggered n times to collect the light with the wavelength of lambda which passes through the imaging objective1And λ2Wherein λ is the speckle image of light of (1), and1＝532nm，λ2＝632nm；
s3, enabling the wavelength of the light which is collected by the CCD color camera and passes through the imaging objective lens to be lambda1And λ2The speckle image formed by the light is transmitted to a data processing system to be processed so as to obtain the blood oxygen saturation of the fundus blood flow, and the method comprises the following steps:
s31, according to the distribution of the pixel points of the CCD color camera, the corresponding wavelength is lambda1And λ2The speckle image formed by the light is separated;
s32, the separated wavelength is lambda1And λ2The light respectively forms each pixel point in the speckle image to carry out fast Fourier transform so as to convert a time domain speckle intensity signal received by the CCD color camera into a frequency domain speckle intensity signal along a time sequence;
s33, filtering the frequency domain speckle intensity signal to separate a low-frequency signal reflecting background information and a high-frequency signal reflecting blood flow, wherein the low-frequency signal is a static speckle signal, and the high-frequency signal is a dynamic speckle signal;
s34, respectively carrying out inverse Fourier transform on the separated low-frequency signal and high-frequency signal to obtain static speckle signal intensity Is λ1And Is λ2Intensity of dynamic speckle Signal Id λ1And Id λ2；
S35, the light intensity transmitted through the biological tissue can be expressed as:
wherein I is the transmitted light intensity, I0Is the intensity of incident light,. epsilon0Light absorption coefficient as background information, C0Concentration of light-absorbing substance as background information, L is the optical path length, in the absence of blood flowAccording to the Beer-Lambert law, the transmitted light intensity is the original collected light intensity, but here, the transmitted light intensity is the average intensity of the original speckle signals, and the static speckle signal average intensity is approximately considered as the transmitted light intensity because the dynamic speckle signal intensity is much smaller than the static speckle signal intensity; therefore, formula (1) can be represented as formula (2):
wherein,is the light absorption coefficient of oxyhemoglobin,for oxygenation of the concentration of hemoglobin,. epsilonHbThe light absorption coefficient of deoxyhemoglobin, cHbThe concentration of deoxyhemoglobin;and epsilonHbAt a wavelength of λ1And λ2The light absorption coefficient is constant;
s36, calculating the formula (2) to obtain the content of oxyhemoglobinAnd the content C of deoxyhemoglobinHb；
S37, calculating the blood oxygen saturation of the fundus blood flow according to a blood oxygen saturation formula (4);
wherein, SO2Namely the blood oxygen saturation of the fundus blood flow.
The device used in the method for detecting the blood oxygen saturation of the fundus blood flow based on the area array LED comprises a synchronous trigger source, a data processing system, an area array LED light source, a spectroscope, an eye-catching objective lens, an imaging objective lens, a CCD color camera and a Bayer filter arranged on the CCD color camera; the area array LED light source is formed by alternately connecting LED lamps with two wavelengths in series; the synchronous trigger source is used for sending synchronous signals to the area array LED light source and the CCD color camera, when the synchronous signals are sent, the area array LED light source sends light with two wavelengths to the spectroscope, the spectroscope reflects the light to the eye objective lens and reaches the eye ground opposite to the eye objective lens, the light enters the eye objective lens again after being reflected from the eye ground and enters the imaging objective lens through the spectroscope, and the CCD color camera collects speckle images formed by the light with the two wavelengths passing through the imaging objective lens and transmits the speckle images to the data processing system for processing so as to obtain the blood oxygen saturation. The area array LED light source, the spectroscope and the ocular objective constitute an eyeground illumination light path system; the CCD color camera, the Bayer filter, the imaging objective lens, the spectroscope and the eye-catching objective lens form an eyeground imaging optical path system; the function of the objective lens and the imaging objective lens is to control the imaging focal length so as to shoot speckle images with high spatial resolution.
In the scheme, the area array LED light source formed by alternately connecting the LED lamps with the two wavelengths in series is arranged, and the synchronous trigger source sends out the synchronous signals to the area array LED light source and the CCD color camera, so that when the synchronous signals are sent out, the area array LED light source simultaneously sends out light with the two wavelengths, and the CCD color camera collects speckle images formed by the light with the two wavelengths and transmits the speckle images to the data processing system for processing so as to obtain the blood oxygen saturation. The invention relates to an area array LED-based fundus blood oxygen saturation detection device, which can measure the blood oxygen saturation of human fundus blood flow in a non-contact manner without any damage to a human body, can effectively inhibit the influence caused by the change of the position of eyes and the change of the blood oxygen content by collecting speckle images formed by light with two wavelengths, and has the advantages of high signal-to-noise ratio of shot images, high spatial resolution and high precision of the detected blood oxygen saturation.
Preferably, the data processing system is a computer.
Preferably, the area array LED light source consists of light with wavelength of lambda1532nm and λ2632nm LED lamps are alternately connected in series. The difference of absorption coefficients of the hemoglobin to the light with the two wavelengths is large, and the error generated during calculation is small, so that the accuracy of the detected blood oxygen saturation is improved.
The device used in the eyeground blood oxygen saturation detection method based on the area array LED is characterized in that an area array LED light source formed by alternately connecting LED lamps with two wavelengths in series is arranged, and a synchronous trigger source sends a synchronous signal to the area array LED light source and a CCD color camera, so that when the synchronous signal is sent, the area array LED light source simultaneously sends light with two wavelengths, the CCD color camera collects speckle images formed by the light with two wavelengths and transmits the speckle images to a data processing system for processing to obtain the blood oxygen saturation, the device can measure the blood oxygen saturation of the eyeground blood flow of a human body in a non-contact manner, has no damage to the human body, can effectively inhibit the influence caused by the change of the position of the eye and the change of the blood oxygen content by collecting the speckle images formed by the light with two wavelengths, and has high signal-to-noise ratio, high spatial resolution and high precision of the detected blood oxygen saturation; by using an area array LED light source with a wavelength of lambda1532nm and λ2The 632nm LED lamps are alternately connected in series, and the absorption coefficients of hemoglobin for light with the two wavelengths are greatly different, so that the calculation is carried outThe generated error is small, and the accuracy of the detected blood oxygen saturation is improved.
Compared with the prior art, the invention has the beneficial effects that:
the invention relates to a fundus blood oxygen saturation detection method based on an area array LED, which comprises the steps of collecting speckle images formed by eyes under the irradiation of light with two wavelengths, carrying out inverse Fourier transform on the collected speckle images through a data processing system 9 to obtain frequency domain speckle intensity signals, carrying out filtering processing on the frequency domain speckle intensity signals to obtain low-frequency signals and high-frequency signals, then respectively carrying out inverse Fourier transform on the low-frequency signals and the high-frequency signals to obtain static speckle signal intensity and dynamic speckle signal intensity, and finally calculating the blood oxygen saturation of the fundus blood according to Beer-Lambert law.
Drawings
Fig. 1 is a schematic diagram of a fundus blood oxygen saturation detection device based on an area array LED in the present embodiment, wherein arrows indicate light direction.
Fig. 2 is a schematic diagram of an arrangement of three color chips of a CCD color camera, in which only the arrangement of red and green is illustrated.
FIG. 3 is a graph of the response coefficient of the green, red and blue response chip of the CCD color camera to different wavelengths of light.
Fig. 4 is a schematic arrangement diagram of the area array LED light source in this embodiment.
Detailed Description
The present invention will be further described with reference to the following embodiments. Wherein the showings are for the purpose of illustration only and are shown by way of illustration only and not in actual form, and are not to be construed as limiting the present patent; to better illustrate the embodiments of the present invention, some parts of the drawings may be omitted, enlarged or reduced, and do not represent the size of an actual product; it will be understood by those skilled in the art that certain well-known structures in the drawings and descriptions thereof may be omitted.
The same or similar reference numerals in the drawings of the embodiments of the present invention correspond to the same or similar components; in the description of the present invention, it should be understood that if there is an orientation or positional relationship indicated by the terms "upper", "lower", "left", "right", etc. based on the orientation or positional relationship shown in the drawings, it is only for convenience of describing the present invention and simplifying the description, but it is not intended to indicate or imply that the referred device or element must have a specific orientation, be constructed in a specific orientation, and be operated, and therefore, the terms describing the positional relationship in the drawings are only used for illustrative purposes and are not to be construed as limiting the present patent, and the specific meaning of the terms may be understood by those skilled in the art according to specific circumstances.
Examples
The embodiment of the invention provides a fundus blood oxygen saturation detection method based on an area array LED, which comprises the following steps:
s1, setting the acquisition speed and the exposure time of a CCD color camera 1, so that when red blood cells enter and exit an imaging range of a pixel unit, the change of the interference intensity of dynamic speckles is caused by the local concentration change; the eye 6 is opposite to the ocular objective 5;
s2. synchronization trigger source 8 with frequency f0Sends n times of synchronous signals to the area array LED light source 7 and the CCD color camera 1, and triggers the area array LED light source 7 n times to send out a wavelength lambda at the same time1And λ2The light reaches the spectroscope 4, the spectroscope 4 reflects the light to the ocular objective 5 and reaches the fundus, the light after being reflected from the fundus enters the ocular objective 5 again and enters the imaging objective 3 through the spectroscope 4, and simultaneously, the CCD color camera 1 is triggered n times to collect the light with the wavelength of lambda passing through the imaging objective 31And λ2Light shape ofA speckle image of λ1＝532nm，λ2＝632nm；
S3, the wavelength of the light which is collected by the CCD color camera 1 and passes through the imaging objective lens 3 is lambda1And λ2The speckle image formed by the light is transmitted to a data processing system 9 for processing to obtain the blood oxygen saturation of the fundus blood flow, and the method comprises the following steps:
s31, according to the distribution of the pixel points of the CCD color camera 1, corresponding wavelength is lambda1And λ2The speckle image formed by the light is separated;
s32, the separated wavelength is lambda1And λ2The light respectively forms each pixel point in the speckle image to carry out fast Fourier transform so as to convert a time domain speckle intensity signal received by the CCD color camera 1 into a frequency domain speckle intensity signal along a time sequence;
s33, filtering the frequency domain speckle intensity signal to separate a low-frequency signal reflecting background information and a high-frequency signal reflecting blood flow, wherein the low-frequency signal is a static speckle signal, and the high-frequency signal is a dynamic speckle signal;
s34, respectively carrying out inverse Fourier transform on the separated low-frequency signal and high-frequency signal to obtain static speckle signal intensity Is λ1And Is λ2Intensity of dynamic speckle Signal Id λ1And Id λ2；
S35, the light intensity transmitted through the biological tissue can be expressed as:
wherein I is the transmitted light intensity, I0Is the intensity of incident light,. epsilon0Light absorption coefficient as background information, C0The light absorbing substance concentration as background information, L is the light path length;
according to Beer-Lambert's law, formula (1) can be expressed as formula (2):
wherein,is the light absorption coefficient of oxyhemoglobin,for oxygenation of the concentration of hemoglobin,. epsilonHbThe light absorption coefficient of deoxyhemoglobin, cHbThe concentration of deoxyhemoglobin;and epsilonHbAt a wavelength of λ1And λ2The light absorption coefficient is constant;
5S36, calculating the formula (2) to obtain the content of oxyhemoglobinAnd the content C of deoxyhemoglobinHb；
S37, calculating the blood oxygen saturation of the fundus blood flow according to a blood oxygen saturation formula (4);
wherein, SO2Namely the blood oxygen saturation of the fundus blood flow.
The schematic diagram of the device used for implementing the fundus blood oxygen saturation detection method based on the area array LED is shown in figure 1, and the device comprises a synchronous trigger source 8, a data processing system 9, an area array LED light source 7, a spectroscope 4, an eye objective 5, an imaging objective 3, a CCD color camera 1 and a Bayer filter 2 arranged on the CCD color camera 1; the area array LED light source 7 is formed by alternately connecting LED lamps with two wavelengths in series; the synchronous trigger source 8 is used for sending out synchronous signals to the area array LED light source 7 and the CCD color camera 1, when the synchronous signals are sent out, the area array LED light source 7 sends out light with two wavelengths simultaneously to the spectroscope 4, the spectroscope 4 reflects the light to the ocular objective 5 and reaches the ocular fundus facing the ocular objective 5, the light enters the ocular objective 5 again after being reflected from the ocular fundus and enters the imaging objective 3 through the spectroscope 4, and the CCD color camera 1 collects speckle images formed by the light with the two wavelengths passing through the imaging objective 3 and transmits the speckle images to the data processing system 9 for processing so as to obtain the blood oxygen saturation.
In the embodiment, an area array LED light source 7, a spectroscope 4 and an eye objective lens 5 form an eyeground illumination light path system 10; the CCD color camera 1, the Bayer filter 2, the imaging objective 3, the spectroscope 4 and the eye objective 5 form an eyeground imaging optical path system 11; the arrangement schematic diagram of the three-color chip of the CCD color camera is shown in fig. 2, a bayer filter 2 is installed on a CCD color camera 1, and light passes through the bayer filter 2 and is then divided into three colors of red, green and blue by the CCD chip on the CCD color camera 1, wherein the green optimal response wavelength is 532nm, the red optimal response wavelength is 632nm, and the response coefficient curve graph of the green, red and blue response chip (pixel point) of the CCD color camera 1 to different wavelengths of light is shown in fig. 3; the objective lens 5 and the imaging objective lens 3 are used for controlling the imaging focal length so as to shoot speckle images with high spatial resolution.
When the device is used for detecting the blood oxygen saturation of human fundus blood flow, an eye 6 is over against an ocular objective lens 5, a synchronous trigger source 8 sends out synchronous signals to an area array LED light source 7 and a CCD color camera 1, so that the area array LED light source 7 sends out light with two wavelengths simultaneously to reach a spectroscope 4, the spectroscope 4 reflects the light to the ocular objective lens 5 and reaches the eye 6, the light enters the ocular objective lens 5 again after being reflected by the eye 6 and enters an imaging objective lens 3 through the spectroscope 4, and the CCD color camera 1 collects a speckle pattern formed by the light with the two wavelengths passing through the imaging objective lens 3The corresponding wavelength is lambda according to the distribution of the pixel points of the CCD color camera 11And λ2Is detected, and the data processing system 9 separates the speckle image formed by the light of the wavelength lambda1And λ2The speckle images formed by the light of (1) are respectively processed to obtain the blood oxygen saturation level. The invention relates to an area array LED-based fundus blood oxygen saturation detection device, which can measure the blood oxygen saturation of human fundus blood flow in a non-contact manner without any damage to a human body, can effectively inhibit the influence caused by the change of the position of eyes and the change of the blood oxygen content by collecting speckle images formed by light with two wavelengths, and has the advantages of high signal-to-noise ratio of shot images, high spatial resolution and high precision of the detected blood oxygen saturation.
In this embodiment, the data processing system 9 is a computer.
Wherein, the area array LED light source 7 has the wavelength of lambda1532nm and λ2The 632nm LED lamps are alternately connected in series as shown in fig. 4. The difference of absorption coefficients of the hemoglobin to the light with the two wavelengths is large, and the error generated during calculation is small, so that the accuracy of the detected blood oxygen saturation is improved.
The invention relates to a fundus blood oxygen saturation detection method based on an area array LED, which comprises the steps of collecting speckle images formed by eyes under the irradiation of light with two wavelengths, carrying out inverse Fourier transform on the collected speckle images through a data processing system 9 to obtain frequency domain speckle intensity signals, carrying out filtering processing on the frequency domain speckle intensity signals to obtain low-frequency signals and high-frequency signals, then respectively carrying out inverse Fourier transform on the low-frequency signals and the high-frequency signals to obtain static speckle signal intensity and dynamic speckle signal intensity, and finally calculating the blood oxygen saturation of the fundus blood according to Beer-Lambert law.
It should be understood that the above-described embodiments of the present invention are merely examples for clearly illustrating the present invention, and are not intended to limit the embodiments of the present invention. Other variations and modifications will be apparent to persons skilled in the art in light of the above description. And are neither required nor exhaustive of all embodiments. Any modification, equivalent replacement, and improvement made within the spirit and principle of the present invention should be included in the protection scope of the claims of the present invention.
Claims (3)
1. An area array LED-based fundus blood oxygen saturation detection method is characterized in that a device used in the detection method comprises a synchronous trigger source (8), a data processing system (9), an area array LED light source (7), a spectroscope (4), an eye objective (5), an imaging objective (3), a CCD color camera (1) and a Bayer filter (2) arranged on the CCD color camera (1); the area array LED light source (7) is formed by alternately connecting LED lamps with two wavelengths in series; the synchronous trigger source (8) is used for sending a synchronous signal to the area array LED light source (7) and the CCD color camera (1), when the synchronous signal is sent out, the area array LED light source (7) simultaneously sends out light with two wavelengths to the spectroscope (4), the spectroscope (4) reflects the light to the ocular objective (5) and reaches the fundus opposite to the ocular objective (5), the light enters the ocular objective (5) again after being reflected from the fundus and enters the imaging objective (3) through the spectroscope (4), and the CCD color camera (1) collects speckle images formed by the light with the two wavelengths passing through the imaging objective (3) and transmits the speckle images to the data processing system (9) for processing so as to obtain the blood oxygen saturation;
the detection method comprises the following steps:
s1, setting the acquisition speed and the exposure time of a CCD color camera (1), so that when red blood cells enter and exit the imaging range of a pixel unit, the change of the local concentration causes the change of the interference intensity of dynamic speckles; the eye (6) is directly opposite to the eye objective (5);
s2. synchronization trigger source (8) with frequency f0Sends n times of synchronous signals to the area array LED light source (7) and the CCD color camera (1), triggers the area array LED light source (7) n times and simultaneously sends out a light with the wavelength of lambda1And λ2The light reaches the spectroscope (4), the spectroscope (4) reflects the light to the eye objective (5) and reaches the eye ground, the light enters the eye objective (5) again after being reflected from the eye ground and enters the imaging objective (3) through the spectroscope (4), and simultaneously, the CCD color camera (1) is triggered to collect the light with the wavelength of lambda which passes through the imaging objective (3) for n times1And λ2Wherein λ is the speckle image of light of (1), and1＝532nm，λ2＝632nm；
s3, enabling the wavelength of the light which is collected by the CCD color camera (1) and passes through the imaging objective lens (3) to be lambda1And λ2The speckle image formed by the light is transmitted to a data processing system (9) to be processed so as to obtain the blood oxygen saturation of the fundus blood flow, and the method comprises the following steps:
s31, according to the distribution of the pixel points of the CCD color camera (1), the corresponding wavelength is lambda1And λ2The speckle image formed by the light is separated;
s32, the separated wavelength is lambda1And λ2The light respectively forms each pixel point in the speckle image to carry out fast Fourier transform so as to convert a time domain speckle intensity signal received by the CCD color camera (1) into a frequency domain speckle intensity signal along a time sequence;
s33, filtering the frequency domain speckle intensity signal to separate a low-frequency signal reflecting background information and a high-frequency signal reflecting blood flow, wherein the low-frequency signal is a static speckle signal, and the high-frequency signal is a dynamic speckle signal;
s34, respectively carrying out inverse Fourier transform on the separated low-frequency signal and high-frequency signal to obtain the intensity of the static speckle signalAnddynamic speckle signal intensityAnd
s35, the light intensity transmitted through the biological tissue can be expressed as:
<mrow> <mi>I</mi> <mo>=</mo> <msub> <mi>I</mi> <mn>0</mn> </msub> <msup> <mi>e</mi> <mrow> <mo>-</mo> <msub> <mi>&epsiv;</mi> <mn>0</mn> </msub> <msub> <mi>C</mi> <mn>0</mn> </msub> <mi>L</mi> </mrow> </msup> <msup> <mi>e</mi> <mrow> <mo>-</mo> <msub> <mi>&epsiv;</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> </msub> <msub> <mi>C</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> </msub> <mi>L</mi> </mrow> </msup> <msup> <mi>e</mi> <mrow> <mo>-</mo> <msub> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> </msub> <msub> <mi>C</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> </msub> <mi>L</mi> </mrow> </msup> <mo>-</mo> <mo>-</mo> <mo>-</mo> <mrow> <mo>(</mo> <mn>1</mn> <mo>)</mo> </mrow> </mrow>
wherein I is the transmitted light intensity, I0Is the intensity of incident light,. epsilon0Light absorption coefficient as background information, C0The light absorbing substance concentration as background information, L is the light path length;
according to Beer-Lambert's law, formula (1) can be expressed as formula (2):
<mrow> <mtable> <mtr> <mtd> <mrow> <msup> <msub> <mi>I</mi> <mi>s</mi> </msub> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msup> <mo>=</mo> <mrow> <mo>(</mo> <msup> <msub> <mi>I</mi> <mi>s</mi> </msub> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msup> <mo>+</mo> <msup> <msub> <mi>I</mi> <mi>d</mi> </msub> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msup> <mo>)</mo> </mrow> <msup> <mi>e</mi> <mrow> <mo>-</mo> <msubsup> <mi>&epsiv;</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> <msub> <mi>C</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> </msub> <mi>L</mi> </mrow> </msup> <msup> <mi>e</mi> <mrow> <mo>-</mo> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> <msub> <mi>C</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> </msub> <mi>L</mi> </mrow> </msup> </mrow> </mtd> </mtr> <mtr> <mtd> <mrow> <msup> <msub> <mi>I</mi> <mi>s</mi> </msub> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msup> <mo>=</mo> <mrow> <mo>(</mo> <msup> <msub> <mi>I</mi> <mi>s</mi> </msub> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msup> <mo>+</mo> <msup> <msub> <mi>I</mi> <mi>d</mi> </msub> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msup> <mo>)</mo> </mrow> <msup> <mi>e</mi> <mrow> <mo>-</mo> <msubsup> <mi>&epsiv;</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <msub> <mi>C</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> </msub> <mi>L</mi> </mrow> </msup> <msup> <mi>e</mi> <mrow> <mo>-</mo> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <msub> <mi>C</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> </msub> <mi>L</mi> </mrow> </msup> </mrow> </mtd> </mtr> </mtable> <mo>-</mo> <mo>-</mo> <mo>-</mo> <mrow> <mo>(</mo> <mn>2</mn> <mo>)</mo> </mrow> </mrow>
wherein,is the light absorption coefficient of oxyhemoglobin,for oxygenation of the concentration of hemoglobin,. epsilonHbThe light absorption coefficient of deoxyhemoglobin, cHbThe concentration of deoxyhemoglobin;and epsilonHbAt a wavelength of λ1And λ2The light absorption coefficient is constant;
s36, calculating the formula (2) to obtain the content of oxyhemoglobinAnd the content C of deoxyhemoglobinHb；
<mrow> <mtable> <mtr> <mtd> <mrow> <msub> <mi>C</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> </msub> <mo>=</mo> <mfrac> <mn>1</mn> <mi>L</mi> </mfrac> <mfrac> <mrow> <msubsup> <mi>&epsiv;</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <mi>ln</mi> <mrow> <mo>(</mo> <mn>1</mn> <mo>+</mo> <mfrac> <msubsup> <mi>I</mi> <mi>d</mi> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> <msubsup> <mi>I</mi> <mi>s</mi> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> </mfrac> <mo>)</mo> </mrow> <mo>-</mo> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> <mi>O</mi> <mn>2</mn> </mrow> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> <mi>ln</mi> <mrow> <mo>(</mo> <mn>1</mn> <mo>+</mo> <mfrac> <msubsup> <mi>I</mi> <mi>d</mi> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <msubsup> <mi>I</mi> <mi>s</mi> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> </mfrac> <mo>)</mo> </mrow> </mrow> <mrow> <msubsup> <mi>&epsiv;</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <mo>-</mo> <msubsup> <mi>&epsiv;</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> </mrow> </mfrac> </mrow> </mtd> </mtr> <mtr> <mtd> <mrow> <msub> <mi>C</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> </msub> <mo>=</mo> <mfrac> <mn>1</mn> <mi>L</mi> </mfrac> <mfrac> <mrow> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> <mi>ln</mi> <mrow> <mo>(</mo> <mn>1</mn> <mo>+</mo> <mfrac> <msubsup> <mi>I</mi> <mi>d</mi> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <msubsup> <mi>I</mi> <mi>s</mi> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> </mfrac> <mo>)</mo> </mrow> <mo>-</mo> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <mi>ln</mi> <mrow> <mo>(</mo> <mn>1</mn> <mo>+</mo> <mfrac> <msubsup> <mi>I</mi> <mi>d</mi> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> <msubsup> <mi>I</mi> <mi>s</mi> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> </mfrac> <mo>)</mo> </mrow> </mrow> <mrow> <msubsup> <mi>&epsiv;</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <mo>-</mo> <msubsup> <mi>&epsiv;</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> <msub> <mi>&lambda;</mi> <mn>2</mn> </msub> </msubsup> <msubsup> <mi>&epsiv;</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> <msub> <mi>&lambda;</mi> <mn>1</mn> </msub> </msubsup> </mrow> </mfrac> </mrow> </mtd> </mtr> </mtable> <mo>-</mo> <mo>-</mo> <mo>-</mo> <mrow> <mo>(</mo> <mn>3</mn> <mo>)</mo> </mrow> </mrow>
S37, calculating the blood oxygen saturation of the fundus blood flow according to a blood oxygen saturation formula (4);
<mrow> <msub> <mi>SO</mi> <mn>2</mn> </msub> <mo>=</mo> <mfrac> <msub> <mi>C</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> </msub> <mrow> <msub> <mi>C</mi> <mrow> <msub> <mi>HbO</mi> <mn>2</mn> </msub> </mrow> </msub> <mo>+</mo> <msub> <mi>C</mi> <mrow> <mi>H</mi> <mi>b</mi> </mrow> </msub> </mrow> </mfrac> <mo>-</mo> <mo>-</mo> <mo>-</mo> <mrow> <mo>(</mo> <mn>4</mn> <mo>)</mo> </mrow> </mrow>
wherein, SO2Namely the blood oxygen saturation of the fundus blood flow.
2. An area array LED-based fundus blood oxygen saturation detection method according to claim 1, characterized in that the data processing system (9) is a computer.
3. An area array LED-based fundus blood oxygen saturation detection method according to any one of claims 1-2, characterized in that the area array LED light source (7) is composed of light with wavelength λ1532nm and λ2632nm LED lamps are alternately connected in series.
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