CN119498831A - A blood oxygen detection method and system based on dual-channel non-invasive brain blood oxygen monitor - Google Patents
A blood oxygen detection method and system based on dual-channel non-invasive brain blood oxygen monitor Download PDFInfo
- Publication number
- CN119498831A CN119498831A CN202411528463.5A CN202411528463A CN119498831A CN 119498831 A CN119498831 A CN 119498831A CN 202411528463 A CN202411528463 A CN 202411528463A CN 119498831 A CN119498831 A CN 119498831A
- Authority
- CN
- China
- Prior art keywords
- blood oxygen
- light
- light intensity
- end detector
- concentration
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
- A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
- A61B5/14553—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases specially adapted for cerebral tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
- A61B5/14542—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue for measuring blood gases
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
- A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
- A61B5/14552—Details of sensors specially adapted therefor
-
- G—PHYSICS
- G06—COMPUTING OR CALCULATING; COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F17/00—Digital computing or data processing equipment or methods, specially adapted for specific functions
- G06F17/10—Complex mathematical operations
Landscapes
- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Medical Informatics (AREA)
- Surgery (AREA)
- Veterinary Medicine (AREA)
- Public Health (AREA)
- General Health & Medical Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Molecular Biology (AREA)
- Heart & Thoracic Surgery (AREA)
- Biomedical Technology (AREA)
- Pathology (AREA)
- Optics & Photonics (AREA)
- Biophysics (AREA)
- General Physics & Mathematics (AREA)
- Data Mining & Analysis (AREA)
- Theoretical Computer Science (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Mathematical Physics (AREA)
- General Engineering & Computer Science (AREA)
- Databases & Information Systems (AREA)
- Algebra (AREA)
- Pure & Applied Mathematics (AREA)
- Software Systems (AREA)
- Mathematical Optimization (AREA)
- Mathematical Analysis (AREA)
- Computational Mathematics (AREA)
- Neurology (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
本发明涉及血氧检测技术领域，具体公开了一种基于双通道无创脑血氧监护仪的血氧检测方法及系统，方法包括：获取第一光强信息和第二光强信息；其中，所述第一光强信息和所述第二光强信息分别由两组探测光穿透脑组织射出后得到；基于所述第一光强信息和所述第二光强信息，分别得到血红蛋白Hb的变化信息和氧合血红蛋白HbO2浓度的变化信息；基于所述第一光强信息和所述第二光强信息的光密度的变化，得到脑组织氧饱和度SctO2浓度数据；本发明利用光学传感技术，无需穿刺或植入设备，即可实时监测脑组织中的血氧水平，这种无创性特征大大降低了患者的痛苦和感染风险。
The present invention relates to the technical field of blood oxygen detection, and specifically discloses a blood oxygen detection method and system based on a dual-channel non-invasive brain blood oxygen monitor, the method comprising: obtaining first light intensity information and second light intensity information; wherein the first light intensity information and the second light intensity information are respectively obtained after two groups of detection lights penetrate brain tissue and are emitted; based on the first light intensity information and the second light intensity information, respectively obtain change information of hemoglobin Hb and change information of oxygenated hemoglobin HbO2 concentration; based on the change of optical density of the first light intensity information and the second light intensity information, obtain brain tissue oxygen saturation SctO2 concentration data; the present invention utilizes optical sensing technology, and can monitor the blood oxygen level in brain tissue in real time without puncture or implantation of equipment, and this non-invasive feature greatly reduces the patient's pain and infection risk.
Description
Technical Field
The invention belongs to the technical field of blood oxygen detection, and particularly relates to a blood oxygen detection method and system based on a double-channel noninvasive cerebral blood oxygen monitor.
Background
Traditional brain tissue blood oxygen monitoring methods often rely on invasive means, such as puncture or implanted sensors, which not only cause significant pain and discomfort to the patient, but also increase the risk of infection, requiring high levels of skill and strict disinfection procedures by the healthcare staff, greatly increasing the complexity and time costs of the procedure.
In addition, although the existing noninvasive cerebral blood oxygen monitoring technology avoids the problems caused by invasive operation, the existing noninvasive cerebral blood oxygen monitoring technology is often limited to single-channel or shallow blood oxygen monitoring, and cannot provide comprehensive information of blood oxygen changes of deep and shallow brain tissues at the same time. This limits its application in complex clinical settings, especially in settings where accurate assessment of the blood oxygen status of different areas of brain tissue is required, such as emergency treatments, surgical procedures and intensive care phases.
In view of the above, the inventor proposes a blood oxygen detection method and system based on a dual-channel noninvasive cerebral blood oxygen monitor, which are used for solving the above problems.
Disclosure of Invention
The invention aims to provide a blood oxygen detection method and a system based on a dual-channel noninvasive cerebral blood oxygen monitor, which are used for solving the problem that the prior art is limited to single-channel or shallow blood oxygen monitoring and cannot provide comprehensive information of blood oxygen changes of deep and shallow brain tissues at the same time.
In order to achieve the above purpose, the present invention provides the following technical solutions:
A blood oxygen detection method based on a dual-channel noninvasive cerebral blood oxygen monitor comprises the following steps:
acquiring first light intensity information and second light intensity information, wherein the first light intensity information and the second light intensity information are respectively obtained after two groups of detection light penetrate brain tissue and are emitted;
Based on the first light intensity information and the second light intensity information, respectively obtaining change information of hemoglobin Hb and change information of oxygenated hemoglobin HbO 2 concentration;
and obtaining the concentration data of the oxygen saturation SctO 2 of the brain tissue based on the change amount of the optical density of the first light intensity information and the second light intensity information.
Preferably, the two groups of detection light are near infrared light NIR and red light respectively.
Preferably, the concentration check formula of the oxygen saturation SctO 2 of the brain tissue is:
In the above
Where R 1 represents the signal at the near-end detector for red light, R 2 represents the signal at the far-end detector for red light, N 1 represents the signal at the near-end detector for near-infrared light, and N 2 represents the signal at the far-end detector for near-infrared light.
Preferably, the concentration for SctO 2 is calculated as follows, let:
SctO 2 final check formula of concentration:
SctO2＝Ay2+By+C
Coefficients A, B, C were fitted by control experiments to give SctO 2 concentrations.
Preferably, the two detectors are a near-end detector and a far-end detector, respectively, and are used for receiving near-infrared light NIR and red light, the light intensity signal detected by the near-end detector is shallow tissue information in brain tissue, and the light intensity signal detected by the far-end detector is deep tissue information in brain tissue.
Preferably, the first light intensity information and the second light intensity information obtain variation information of hemoglobin Hb and variation information of concentration of oxyhemoglobin HbO 2 according to lambert-beer's law, where lambert-beer's law is defined as a ratio of intensities of incident light and emergent light, and the expression is:
I=I0e-εCL
Wherein I is the intensity of the light emitted by the incident light after passing through the medium, I 0 is the intensity of the light emitted by the light source, namely the intensity of the light emitted into the medium, E represents the molecular extinction coefficient of the medium, C represents the concentration of the medium, and L is the optical path, namely the optical path through which the incident light passes through the medium.
Preferably, the step optical density OD is the inverse of the absorbance ω, expressed as:
The absorbance ω is defined as the logarithm of the ratio of the incident light intensity before the light passes through the solution or a substance to the transmitted light intensity after the light passes through the medium, based on I 0, expressed as:
the optical density OD is the inverse of the absorbance, i.e., 1/ω, and is expressed as:
preferably, the calculation expression of the variation Δod of the optical density OD is:
In the above formula, l t0 represents the emergent light intensity detected by the detector at the time t 0, and It is the emergent light intensity detected at the time t;
calculation of Δod updates Δod' to be:
Where λ is the wavelength, as measured.
Preferably, the modified lambert-beer law expression is:
ω'=εCL·lge+G
In the above formula, G represents the loss caused by scattering of the compensation photons in different directions in the transmission process, I is the light intensity emitted by the incident light after passing through the medium, I 0 is the light emitted by the light source, namely the light intensity of the incident light, E represents the molecular extinction coefficient of the medium, C represents the concentration of the medium, and L is the optical path, namely the optical path through which the incident light passes through the medium.
The invention also provides a blood oxygen detection system based on the dual-channel noninvasive cerebral blood oxygen monitor, which comprises:
The system uses a near infrared light NIR LED and a red light LED, wherein the near infrared light source is used for detecting deep tissues, and the red light source is used for detecting blood oxygen changes in shallow tissues;
The photon detection module is provided with a near-end detector and a far-end detector which are respectively positioned at different positions from the light source so as to detect emergent light intensity in shallow and deep tissues, wherein the near-end detector is close to the light source and detects blood oxygen information of the shallow brain tissues;
The data acquisition and processing module comprises a photon detection module signal acquisition and preprocessing unit and a data processing module, wherein the photon detection module signal acquisition and preprocessing unit is used for determining the concentration change of oxyhemoglobin HbO 2 and deoxyhemoglobin Hb of brain tissues through the calculation of absorbance and optical density under different wavelengths according to the lambert-beer law;
The data calculation and blood oxygen concentration deduction module corrects a random scattering path of photons in brain tissues by adopting a corrected lambert-beer law, combines detected near infrared and red light signals R 1、R2、N1、N2, wherein R 1 represents a signal of red light transmitted to a near-end detector, R 2 represents a signal of red light transmitted to a far-end detector, N 1 represents a signal of near infrared light transmitted to the near-end detector, N 2 represents a signal of near infrared light transmitted to the far-end detector, deduces brain tissue oxygen saturation SctO 2 by a double-channel absorbance model, and calculates brain tissue SctO 2 concentration under specific conditions by fitting an obtained empirical formula.
Compared with the prior art, the invention has the beneficial effects that:
The invention can monitor the blood oxygen level in brain tissues in real time by utilizing the optical sensing technology without puncturing or implanting equipment, and the noninvasive characteristic not only greatly reduces the pain and infection risk of patients, but also reduces the operation difficulty and disinfection work of medical staff and improves the convenience and safety of operation; the dual-channel arrangement enables the system to monitor blood oxygen changes of superficial and deep brain tissues simultaneously, and can capture dynamic changes of oxyhemoglobin HbO 2 and deoxyhemoglobin Hb in the brain tissues in real time, so that high-timeliness monitoring data are provided, and the system can accurately measure the concentration of oxyhemoglobin and deoxyhemoglobin through the light absorption difference of specific wavelengths when detecting the two substances through a dual-wavelength model. The sensitivity of the system can detect tiny blood oxygen changes, so that the system has remarkable advantages in detecting cerebral hypoxia state or cerebral blood supply abnormality of patients, and is particularly important for patients in emergency treatment, intraoperative monitoring and intensive care.
Drawings
FIG. 1 is a flow chart of a blood oxygen detection method based on a dual-channel noninvasive cerebral blood oxygen monitor of the present invention;
FIG. 2 is a schematic representation of the transmission of photons in brain tissue according to the present invention;
FIG. 3 is a graph of the absorption spectra of HbO 2 and Hb of the present invention over a wavelength range of 200nm to 1000nm for photons;
FIG. 4 is a dual light source dual wavelength model diagram of the present invention for detecting brain tissue SctO 2;
FIG. 5 is a block diagram of two sets of probe light compositions according to the present invention;
FIG. 6 is a block diagram of two detector assemblies of the present invention;
Fig. 7 is a block diagram of a blood oxygen detection system based on a dual-channel noninvasive cerebral blood oxygen monitor.
Detailed Description
The following description of the embodiments of the present invention will be made clearly and completely with reference to the accompanying drawings, in which it is apparent that the embodiments described are only some embodiments of the present invention, but not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
Embodiment one:
referring to fig. 1 to 6, a blood oxygen detection method based on a dual-channel noninvasive cerebral blood oxygen monitor includes:
acquiring first light intensity information and second light intensity information, wherein the first light intensity information and the second light intensity information are respectively obtained after two groups of detection light penetrate brain tissue and are emitted;
Based on the first light intensity information and the second light intensity information, respectively obtaining change information of hemoglobin Hb and change information of oxygenated hemoglobin HbO 2 concentration;
and obtaining the concentration data of the oxygen saturation SctO 2 of the brain tissue based on the change amount of the optical density of the first light intensity information and the second light intensity information.
Specifically, the two groups of detection light are near infrared light NIR and red light respectively.
Specifically, the concentration check formula of the brain tissue oxygen saturation SctO 2 is:
In the above
Where R 1 represents the signal at the near-end detector for red light, R 2 represents the signal at the far-end detector for red light, N 1 represents the signal at the near-end detector for near-infrared light, and N 2 represents the signal at the far-end detector for near-infrared light.
Specifically, for the concentration of SctO 2, the following is calculated, let:
SctO 2 final check formula of concentration:
SctO2＝Ay2+By+C
Coefficients A, B, C were fitted by control experiments to give SctO 2 concentrations.
Specifically, the two detectors are a near-end detector and a far-end detector respectively, and are used for receiving near-infrared light NIR and red light, the light intensity signal detected by the near-end detector is shallow tissue information in brain tissue, and the light intensity signal detected by the far-end detector is deep tissue information in brain tissue.
Specifically, the first light intensity information and the second light intensity information obtain change information of hemoglobin Hb and change information of concentration of oxyhemoglobin HbO 2 according to lambert-beer's law, where lambert-beer's law is defined as a ratio of intensities of incident light and emergent light, and the expression is:
I=I0e-εCL
Wherein I is the intensity of the light emitted by the incident light after passing through the medium, I 0 is the intensity of the light emitted by the light source, namely the intensity of the light emitted into the medium, E represents the molecular extinction coefficient of the medium, C represents the concentration of the medium, and L is the optical path, namely the optical path through which the incident light passes through the medium.
Specifically, the optical density OD is the inverse of the absorbance ω, which is expressed as:
The absorbance ω is defined as the logarithm of the ratio of the incident light intensity before the light passes through the solution or a substance to the transmitted light intensity after the light passes through the medium, based on I 0, expressed as:
the optical density OD is the inverse of the absorbance, i.e., 1/ω, and is expressed as:
specifically, the calculation expression of the variation Δod of the optical density OD is:
In the above formula, l t0 represents the emergent light intensity detected by the detector at the time t 0, and It is the emergent light intensity detected at the time t;
calculation of Δod updates Δod' to be:
Where λ is the wavelength, as measured.
Specifically, the modified lambert-beer law expression in step S4 is:
ω'=εCL·lge+G
In the above formula, G represents the loss caused by scattering of the compensation photons in different directions in the transmission process, I is the light intensity emitted by the incident light after passing through the medium, I 0 is the light emitted by the light source, namely the light intensity of the incident light, E represents the molecular extinction coefficient of the medium, C represents the concentration of the medium, and L is the optical path, namely the optical path through which the incident light passes through the medium.
From the above, by utilizing the optical sensing technology, the blood oxygen level in brain tissues can be monitored in real time without puncturing or implanting equipment, and the noninvasive characteristic not only greatly reduces the pain and infection risk of patients, but also reduces the operation difficulty and disinfection work of medical staff, and improves the convenience and safety of operation;
The dual-channel arrangement enables the system to monitor blood oxygen changes of superficial and deep brain tissues simultaneously, and can capture dynamic changes of oxyhemoglobin HbO 2 and deoxyhemoglobin Hb in the brain tissues in real time, so that high-timeliness monitoring data are provided, and the system can accurately measure the concentration of oxyhemoglobin and deoxyhemoglobin through the light absorption difference of specific wavelengths when detecting the two substances through a dual-wavelength model. The sensitivity of the system can detect tiny blood oxygen changes, so that the system has remarkable advantages in detecting cerebral hypoxia state or cerebral blood supply abnormality of patients, and is particularly important for patients in emergency treatment, intraoperative monitoring and intensive care.
Embodiment two:
The monitor is particularly applied to a plurality of key fields of medical health, and in emergency medical treatment, the monitor can rapidly and noninvasively monitor the change of the blood oxygen level of brain tissues of a patient and provide instant brain hypoxia or brain blood supply abnormality early warning for doctors, thereby helping the doctors to make diagnosis and formulate a treatment scheme. This is especially important for the treatment of acute diseases such as cerebral apoplexy and craniocerebral injury, and can effectively reduce irreversible brain injury caused by delayed diagnosis.
Further, please refer to fig. 1 to 6:
1. Selecting a light source wavelength
In the experiment, near Infrared (NIR) light source and red light source were used, with 940nm and 660nm as detection wavelengths, respectively. The reason for this band is that oxyhemoglobin (HbO 2) has a higher absorption coefficient at 940nm wavelength, whereas de-oxyhemoglobin (Hb) has a higher absorption coefficient at 660 nm. By this combination, a differential effect can be obtained, accurately measuring the blood oxygen level of brain tissue.
2. Experimental objects
The experimental object is a healthy volunteer, and the change of the blood oxygen concentration of the experimental object under different breathing conditions is recorded by wearing a noninvasive cerebral blood oxygen monitor. Blood oxygen changes in brain tissue, such as normal breathing and breath-hold (transient cessation of breathing) conditions, are simulated by means of respiratory control.
3. Experimental procedure
And (3) data acquisition:
Volunteers sit down in a quiet environment and wear the monitor.
The light source module of the monitor emits light in a dual wavelength mode of 940nm and 660 nm.
The proximal sensor 1 records shallow tissue signals and the distal sensor 2 records deep tissue signals.
The experiment was divided into three phases, normal breath, breath-hold (30 seconds), breath-hold (50 seconds), normal breath recovery (20 seconds), normal breath recovery (60 seconds), and data recorded for each phase are shown in table 1 below:
TABLE 1
The fit yields A, B, C coefficients a=0.5, b=0.4, c=0.3, respectively
Calculation of SctO 2 concentration at normal breath:
SctO 2 (normal respiration) =0.5x0.848 2 +0.4X0.848+0.3 =0.998=99.8%
Calculation of SctO 2 concentration at breath hold (30 seconds):
SctO 2 (30 seconds of breath hold) =0.5x0.828 2 +0.4x0.828+0.3=0.982=98.2%
Calculation of SctO 2 concentration at breath hold (40 seconds):
SctO 2 (breath hold 50 seconds) =0.5x0.781 2 +0.4X0.781+0.3 =0.944=94.4%
SctO 2 concentration calculations at recovery of breath (20 seconds):
SctO 2 (20 seconds of recovery of breath) =0.5x0.807 2 +0.4x0.807+0.3=0.948=94.8%
SctO 2 concentration calculation at recovery of breath (60 seconds):
SctO 2 (60 seconds of recovery breath) =0.5× 0.831 2 +0.4X0.831+0.3 =0.978=97.8%
Analysis of results
The normal respiration state is SctO 2, the value is close to 99.8%, and the blood oxygen of brain tissues is sufficient and the metabolic activity is normal.
The SctO 2 value decreased to 94.4% for 50 seconds, reflecting an increase in oxygen consumption and a decrease in oxygenated hemoglobin concentration in brain tissue metabolism.
The resumption of respiration was carried out for 60 seconds with a SctO 2 value back up to 97.8%, showing that the brain tissue gradually regained oxygen supply as respiration resumed.
From the above, the system can effectively monitor the blood oxygen change of brain tissue under different respiratory states, and experimental results prove that the system can accurately monitor the oxygenation state of brain tissue based on the double-channel optical density change and can clearly reflect the concentration change of oxyhemoglobin and deoxyhemoglobin.
From the above, the system combines lambert-beer law and a modified optical density change model, and compensates the random propagation characteristic of photons in biological tissues. By detecting the optical density variation of the dual channels, errors caused by external light interference and patient position variation are reduced, and accuracy and stability of blood oxygen monitoring are ensured.
Embodiment III:
referring to fig. 7, the present invention further provides a blood oxygen detection system based on the dual-channel noninvasive cerebral blood oxygen monitor, which comprises:
The system uses a near infrared light NIR LED and a red light LED, N IR and red light can penetrate through scalp and skull and enter brain tissue respectively, the light source module selects a wavelength range of 600-950 nm, wherein the near infrared light source is used for detecting deep tissue, and the red light source is used for detecting blood oxygen change in shallow tissue;
The photon detection module is provided with a near-end detector and a far-end detector which are respectively positioned at different positions from the light source so as to detect emergent light intensity in shallow and deep tissues, wherein the near-end detector is close to the light source and detects blood oxygen information of the shallow brain tissues;
The data acquisition and processing module comprises a photon detection module signal acquisition and preprocessing unit and a data processing module, wherein the photon detection module signal acquisition and preprocessing unit is used for determining the concentration change of oxyhemoglobin HbO 2 and deoxyhemoglobin Hb of brain tissues through the calculation of absorbance and optical density under different wavelengths according to the lambert-beer law;
And the data calculation and blood oxygen concentration deduction module is used for correcting a random scattering path of photons in brain tissues by adopting a corrected lambert-beer law, deducting the oxygen saturation SctO 2 of the brain tissues by a double-channel absorbance model in combination with detected near infrared and red light signals R 1、R2、N1、N2, and calculating the concentration of the brain tissues SctO 2 under specific conditions by fitting an obtained empirical formula.
From the above, it is clear that the system does not require a complex operation procedure in daily monitoring, in a non-invasive manner and using an LED light source and a portable sensor. The medical staff only needs to simply attach the equipment on the scalp of the patient, and the system can automatically complete data acquisition and analysis, so that the workload of the medical staff is reduced, and the monitoring efficiency is improved.
In the description of the present specification, a description referring to the terms "one embodiment," "some embodiments," "examples," "specific examples," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the present invention. In this specification, schematic representations of the above terms are not necessarily for the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Furthermore, the different embodiments or examples described in this specification and the features of the different embodiments or examples may be combined and combined by those skilled in the art without contradiction.
In the drawings of the disclosed embodiments, only the structures related to the embodiments of the present disclosure are referred to, and other structures may refer to the general design, so that the same embodiment and different embodiments of the present disclosure may be combined with each other without conflict.
Although embodiments of the present invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made therein without departing from the principles and spirit of the invention, the scope of which is defined in the appended claims and their equivalents.
Claims (10)
1. The blood oxygen detection method based on the double-channel noninvasive cerebral blood oxygen monitor is characterized by comprising the following steps of:
acquiring first light intensity information and second light intensity information, wherein the first light intensity information and the second light intensity information are respectively obtained after two groups of detection light penetrate brain tissue and are emitted;
Based on the first light intensity information and the second light intensity information, respectively obtaining change information of hemoglobin Hb and change information of oxygenated hemoglobin HbO 2 concentration;
and obtaining the concentration data of the oxygen saturation SctO 2 of the brain tissue based on the change amount of the optical density of the first light intensity information and the second light intensity information.
2. The method for detecting blood oxygen based on the dual-channel noninvasive cerebral blood oxygen monitor of claim 1, wherein the two groups of detection light are near infrared light NIR and red light respectively.
3. The blood oxygen detection method based on the dual-channel noninvasive cerebral blood oxygen monitor of claim 1, wherein the concentration check formula of the cerebral tissue oxygen saturation SctO 2 is:
In the above
Where R 1 represents the signal at the near-end detector for red light, R 2 represents the signal at the far-end detector for red light, N 1 represents the signal at the near-end detector for near-infrared light, and N 2 represents the signal at the far-end detector for near-infrared light.
4. The blood oxygen detection method based on the dual-channel noninvasive cerebral blood oxygen monitor of claim 1, wherein the concentration of SctO 2 is calculated as follows:
SctO 2 final check formula of concentration:
SctO2＝Ay2+By+C
Coefficients A, B, C were fitted by control experiments to give SctO 2 concentrations.
5. The method for detecting blood oxygen based on the dual-channel noninvasive cerebral blood oxygen monitor of claim 3, wherein the two detectors are respectively a near-end detector and a far-end detector for receiving near-infrared light NIR and red light, the light intensity signal detected by the near-end detector is shallow tissue information in brain tissue, and the light intensity signal detected by the far-end detector is deep tissue information in brain tissue.
6. The method for detecting blood oxygen based on the dual-channel noninvasive cerebral blood oxygen monitor of claim 4, wherein the first light intensity information and the second light intensity information are obtained according to the lambert-beer law, the lambert-beer law is defined as the ratio of the intensity of incident light to the intensity of emergent light, and the expression is:
I=I0e-εCL
Wherein I is the intensity of the light emitted by the incident light after passing through the medium, I 0 is the intensity of the light emitted by the light source, namely the intensity of the light emitted into the medium, E represents the molecular extinction coefficient of the medium, C represents the concentration of the medium, and L is the optical path, namely the optical path through which the incident light passes through the medium.
7. The blood oxygen detection method based on the dual-channel noninvasive cerebral blood oxygen monitor of claim 1, wherein the optical density OD is the inverse of absorbance omega, and the expression of absorbance is:
The absorbance ω is defined as the logarithm of the ratio of the incident light intensity before the light passes through the solution or a substance to the transmitted light intensity after the light passes through the medium, based on I 0, expressed as:
the optical density OD is the inverse of the absorbance, i.e., 1/ω, and is expressed as:
8. the blood oxygen detection method based on the dual-channel noninvasive cerebral blood oxygen monitor of claim 1, wherein the calculation expression of the variation delta OD of the optical density OD is:
In the above formula, l t0 represents the emergent light intensity detected by the detector at the time t 0, and It is the emergent light intensity detected at the time t;
calculation of Δod updates Δod' to be:
Where λ is the wavelength, as measured.
9. The blood oxygen detection method based on the dual-channel noninvasive cerebral blood oxygen monitor of claim 1, wherein the modified lambert-beer law expression is:
ω′=εCL·lg e+G
In the above formula, G represents the loss caused by scattering of the compensation photons in different directions in the transmission process, I is the light intensity emitted by the incident light after passing through the medium, I 0 is the light emitted by the light source, namely the light intensity of the incident light, E represents the molecular extinction coefficient of the medium, C represents the concentration of the medium, and L is the optical path, namely the optical path through which the incident light passes through the medium.
10. Blood oxygen detecting system based on binary channels noninvasive cerebral blood oxygen monitor, characterized by comprising:
The system uses a near infrared light NIR LED and a red light LED, wherein the near infrared light source is used for detecting deep tissues, and the red light source is used for detecting blood oxygen changes in shallow tissues;
The photon detection module is provided with a near-end detector and a far-end detector which are respectively positioned at different positions from the light source so as to detect emergent light intensity in shallow and deep tissues, wherein the near-end detector is close to the light source and detects blood oxygen information of the shallow brain tissues;
The data acquisition and processing module comprises a photon detection module signal acquisition and preprocessing unit and a data acquisition and processing module, wherein the photon detection module signal acquisition and preprocessing unit is used for respectively determining the concentration change of oxyhemoglobin HbO 2 and deoxyhemoglobin Hb of brain tissues through the calculation of absorbance and optical density under different wavelengths according to the lambert-beer law;
The data calculation and blood oxygen concentration deduction module is used for correcting a random scattering path of photons in brain tissues by adopting a corrected lambert-beer law, combining detected near infrared and red light signals R 1、R2、N1、N2, wherein R 1 represents a signal of red light transmitted to a near-end detector, R 2 represents a signal of red light transmitted to a far-end detector, N 1 represents a signal of near infrared light transmitted to the near-end detector, N 2 represents a signal of near infrared light transmitted to the far-end detector, deducing brain tissue oxygen saturation SctO 2 by using a double-channel absorbance model, and calculating brain tissue SctO 2 concentration under specific conditions by fitting an obtained empirical formula.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202411528463.5A CN119498831A (en) | 2024-10-30 | 2024-10-30 | A blood oxygen detection method and system based on dual-channel non-invasive brain blood oxygen monitor |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202411528463.5A CN119498831A (en) | 2024-10-30 | 2024-10-30 | A blood oxygen detection method and system based on dual-channel non-invasive brain blood oxygen monitor |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN119498831A true CN119498831A (en) | 2025-02-25 |
Family
ID=94649951
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202411528463.5A Pending CN119498831A (en) | 2024-10-30 | 2024-10-30 | A blood oxygen detection method and system based on dual-channel non-invasive brain blood oxygen monitor |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN119498831A (en) |
-
2024
- 2024-10-30 CN CN202411528463.5A patent/CN119498831A/en active Pending
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US10463286B2 (en) | Determination of tissue oxygenation in vivo | |
| Amir et al. | Continuous noninvasive glucose monitoring technology based on “occlusion spectroscopy” | |
| Kamat | Pulse oximetry | |
| Schnapp et al. | Pulse oximetry: uses and abuses | |
| Mendelson | Pulse oximetry: theory and applications for noninvasive monitoring | |
| AU2003254135B2 (en) | Method for spectrophotometric blood oxygenation monitoring | |
| Kyriacou | Pulse oximetry in the oesophagus | |
| US20080208019A1 (en) | Modified Pulse Oximetry Technique For Measurement Of Oxygen Saturation In Arterial And Venous Blood | |
| US20080228053A1 (en) | Method and system for cerebral oxygenation level monitoring | |
| US20080004513A1 (en) | VCSEL Tissue Spectrometer | |
| US20130023744A1 (en) | Method for spectrophotometric blood oxygenation monitoring of organs in the body | |
| CN112043287A (en) | Cerebral blood oxygen non-invasive monitoring method and monitoring device | |
| CN109009064A (en) | A kind of intracranial pressure noninvasive monitoring device and method | |
| Gersten et al. | Probing brain oxygenation with near infrared spectroscopy | |
| Sondej et al. | Influence of cuff pressures of automatic sphygmomanometers on pulse oximetry measurements | |
| CN112806992B (en) | Tissue oxygen saturation monitoring system and method of self-adaptive spatial resolution spectrum | |
| Kirkpatrick et al. | Use of near infrared spectroscopy for the clinical monitoring of adult brain | |
| Nioka et al. | Fetal transabdominal pulse oximeter studies using a hypoxic sheep model | |
| CN110613462A (en) | Tissue oxygen saturation detection method and device free from individual difference | |
| CN119498831A (en) | A blood oxygen detection method and system based on dual-channel non-invasive brain blood oxygen monitor | |
| Ajmal et al. | Development of the relationship between hemoglobin concentration and PPG signal characteristics | |
| Du et al. | Design of a two-channel forehead PPG sensor | |
| Gersten et al. | Probing brain oxygenation waveforms with near infrared spectroscopy (NIRS) | |
| Lynn et al. | Pulse oximetry during cardiac catheterization in children with congenital heart disease | |
| Vaqar et al. | Spectroscopic Properties of Blood for Pulse Oximeter Design |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination |