CN113100760B - Cerebral blood oxygen saturation detection system and method free from scalp blood flow interference - Google Patents
Cerebral blood oxygen saturation detection system and method free from scalp blood flow interference Download PDFInfo
- Publication number
- CN113100760B CN113100760B CN202110563085.4A CN202110563085A CN113100760B CN 113100760 B CN113100760 B CN 113100760B CN 202110563085 A CN202110563085 A CN 202110563085A CN 113100760 B CN113100760 B CN 113100760B
- Authority
- CN
- China
- Prior art keywords
- light source
- detector
- light
- sensor
- module
- 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.)
- Active
Links
- 210000004761 scalp Anatomy 0.000 title claims abstract description 47
- 239000008280 blood Substances 0.000 title claims abstract description 41
- 210000004369 blood Anatomy 0.000 title claims abstract description 41
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 title claims abstract description 38
- 229910052760 oxygen Inorganic materials 0.000 title claims abstract description 38
- 239000001301 oxygen Substances 0.000 title claims abstract description 38
- 230000017531 blood circulation Effects 0.000 title claims abstract description 28
- 238000001514 detection method Methods 0.000 title claims abstract description 22
- 238000000034 method Methods 0.000 title claims abstract description 20
- 230000002490 cerebral effect Effects 0.000 title claims abstract description 14
- 238000012545 processing Methods 0.000 claims abstract description 28
- 238000010521 absorption reaction Methods 0.000 claims abstract description 13
- 210000001061 forehead Anatomy 0.000 claims abstract description 7
- 238000006243 chemical reaction Methods 0.000 claims abstract description 6
- 210000004556 brain Anatomy 0.000 claims description 25
- 210000005013 brain tissue Anatomy 0.000 claims description 22
- 102000001554 Hemoglobins Human genes 0.000 claims description 18
- 230000003287 optical effect Effects 0.000 claims description 15
- 108050008072 Cytochrome c oxidase subunit IV Proteins 0.000 claims description 13
- 102000000634 Cytochrome c oxidase subunit IV Human genes 0.000 claims description 13
- 108010001073 oxyhemoglobin oxidase Proteins 0.000 claims description 13
- 108010054147 Hemoglobins Proteins 0.000 claims description 6
- 238000004364 calculation method Methods 0.000 claims description 5
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 claims description 4
- 229910052710 silicon Inorganic materials 0.000 claims description 4
- 239000010703 silicon Substances 0.000 claims description 4
- 230000008033 biological extinction Effects 0.000 claims description 3
- 230000004044 response Effects 0.000 claims description 3
- 238000012937 correction Methods 0.000 claims description 2
- 230000004298 light response Effects 0.000 claims 2
- 239000000126 substance Substances 0.000 abstract description 17
- 210000003128 head Anatomy 0.000 abstract description 4
- 230000003321 amplification Effects 0.000 abstract description 3
- 238000003199 nucleic acid amplification method Methods 0.000 abstract description 3
- 108010064719 Oxyhemoglobins Proteins 0.000 description 7
- 238000010586 diagram Methods 0.000 description 4
- 230000008569 process Effects 0.000 description 4
- 238000004497 NIR spectroscopy Methods 0.000 description 3
- 230000036284 oxygen consumption Effects 0.000 description 3
- 206010021143 Hypoxia Diseases 0.000 description 2
- 238000004422 calculation algorithm Methods 0.000 description 2
- 238000013461 design Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 230000007954 hypoxia Effects 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 239000000758 substrate Substances 0.000 description 2
- 206010002091 Anaesthesia Diseases 0.000 description 1
- 208000002381 Brain Hypoxia Diseases 0.000 description 1
- 102100030497 Cytochrome c Human genes 0.000 description 1
- 108010075031 Cytochromes c Proteins 0.000 description 1
- 208000028389 Nerve injury Diseases 0.000 description 1
- 239000000853 adhesive Substances 0.000 description 1
- 230000001070 adhesive effect Effects 0.000 description 1
- 230000002411 adverse Effects 0.000 description 1
- 230000037005 anaesthesia Effects 0.000 description 1
- 238000007405 data analysis Methods 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 230000000004 hemodynamic effect Effects 0.000 description 1
- 238000002329 infrared spectrum Methods 0.000 description 1
- 230000002452 interceptive effect Effects 0.000 description 1
- 230000002427 irreversible effect Effects 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000012544 monitoring process Methods 0.000 description 1
- 230000008764 nerve damage Effects 0.000 description 1
- 238000009659 non-destructive testing Methods 0.000 description 1
- 230000008557 oxygen metabolism Effects 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 239000000523 sample Substances 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 238000004088 simulation Methods 0.000 description 1
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
- A61B5/1455—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
Landscapes
- Health & Medical Sciences (AREA)
- Physics & Mathematics (AREA)
- Life Sciences & Earth Sciences (AREA)
- Biomedical Technology (AREA)
- Medical Informatics (AREA)
- Biophysics (AREA)
- Pathology (AREA)
- Engineering & Computer Science (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Heart & Thoracic Surgery (AREA)
- Optics & Photonics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Neurology (AREA)
- Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
Abstract
本发明公开了一种不受头皮血流干扰的脑血氧饱和度检测系统及方法，检测系统包括传感器和主机，传感器与主机通过线缆连接。传感器与头部前额皮肤紧贴，传感器上设置了第一光源、第一检测器、第二光源和第二检测器，且光源与各个检测器之间依次沿同一方向呈直线排列，检测器不仅可以拾取光源入射处头皮血流中生色团物质的吸收信息，还可以拾取光源出射处头皮血流中生色团物质的吸收信息。主机中设有电源模块、中央处理与存储模块、光源驱动模块、信号放大和A/D转换模块、用户信息输入模块和数据显示模块。本发明可以消除头皮血流干扰从而求得脑血氧饱和度。
The present invention discloses a cerebral blood oxygen saturation detection system and method that is not interfered by scalp blood flow. The detection system includes a sensor and a host, and the sensor and the host are connected by a cable. The sensor is in close contact with the forehead skin of the head, and a first light source, a first detector, a second light source and a second detector are arranged on the sensor, and the light source and each detector are arranged in a straight line in the same direction in sequence. The detector can not only pick up the absorption information of the chromophore substance in the scalp blood flow at the incident point of the light source, but also pick up the absorption information of the chromophore substance in the scalp blood flow at the exit point of the light source. The host is provided with a power module, a central processing and storage module, a light source driving module, a signal amplification and A/D conversion module, a user information input module and a data display module. The present invention can eliminate the interference of scalp blood flow to obtain cerebral blood oxygen saturation.
Description
Technical Field
The invention relates to the technical field of biomedical engineering, in particular to a brain blood oxygen saturation detection system and method free from scalp blood flow interference.
Background
The oxygen consumption of the brain accounts for about one fourth of the total oxygen consumption of a human body, the brain is highly sensitive to hypoxia, irreversible nerve injury can be caused by short-time hypoxia, and the incidence rate of cerebral hypoxia in the process of operation anesthesia is always high, so that the timely monitoring of oxygen supply and oxygen consumption of brain tissues of a patient in operation is very important.
Near infrared Spectroscopy (NIRS) is a brain blood oxygen nondestructive testing technology which has been developed in the last 20 years, and a forehead is irradiated by a near infrared light source with specific wavelength, according to the difference of absorption of main chromophore substances (oxyhemoglobin, reduced hemoglobin and cytochrome oxidase) in brain tissues on the near infrared spectrum, the absorption information of the brain tissues on light is obtained by measuring the emergent light intensity diffused by the brain tissues, and then the brain blood oxygen saturation can be obtained by adopting a related algorithm, so that the brain oxygen metabolism information can be continuously obtained in real time, and objective basis can be provided for clinical timely treatment of adverse events.
However, when the near infrared light irradiates the forehead, the chromophore substances (oxyhemoglobin, reduced hemoglobin and cytochrome oxidase) in the scalp blood inevitably have absorption effect on the near infrared light, so that the measured data are brain blood oxygen saturation and oxygen saturation in the scalp blood flow, and the hemodynamics in the scalp are easily affected by the external environment (such as temperature, sensor wearing tightness, etc.), thereby interfering with the detection result. Stven et al research shows that when scalp blood flow dynamics are changed, the measured cerebral oxygen saturation is changed greatly by the commercial cerebral blood oxygen detection instruments such as FORE-SIGHT ELITE, INVOS TM 5100C and the like, and the stability and accuracy of the detection result are affected.
Publication number CN110613462a discloses a method and apparatus for detecting tissue oxygen saturation that is not affected by individual differences, which corrects the effect of different outer layer tissue thickness on tissue oxygen saturation measurement, but cannot eliminate scalp blood flow interference. Patent number CN208435654U discloses an infrared light emitting probe for cerebral blood oxygen detection, which can better fit the scalp but cannot resist scalp blood flow disturbance.
In view of the above-mentioned shortcomings, it is necessary to study a cerebral blood oxygen detection system and method that is not interfered by scalp blood flow, so as to realize stable and accurate measurement.
Disclosure of Invention
Therefore, the invention aims to develop a brain blood oxygen saturation detection system and a brain blood oxygen saturation detection method which are not interfered by scalp blood flow, so as to stably and accurately measure the brain oxygen saturation.
In one aspect, the present invention provides a brain blood oxygen saturation detection system that is not disturbed by scalp blood flow, the system includes a sensor 10 and a host 60, the sensor 10 includes a light source and a detector, the host includes a power module 603, a central processing and storage module 601, a light source driving module 604, a signal amplifying and a/D conversion module 605, a user information input module 602 and a data display module 606, and the sensor 10 is connected to the host 60 through a cable.
The light source on the sensor 10 includes a first light source 102 and a second light source 104, and the two light sources have the same light emitting component, and the light emitting component is a light emitting diode or a laser diode capable of emitting multiple wavelengths, and 700-900nm near infrared light with a wavelength lambda 1、λ2,……λn is alternately generated.
The detectors on the sensor 10 include a first detector 103 and a second detector 105, and both detectors are composed of the same photo-responsive sensor, which is a photodiode, a silicon photodiode, or a charge-coupled device, wherein the response peak wavelength of the photodiode or the silicon photodiode is between 700-800 nm.
The first light source 102, the first detector 103, the second light source 104 and the second detector 105 are sequentially arranged in a straight line along the same direction, the distance between the first light source 102 and the first detector 103 is 2-5mm, the distance between the first detector 103 and the second light source 104 is 20-30mm, and the distance between the second light source 104 and the second detector 105 is 2-5mm.
In another aspect, the present invention also provides a method for detecting cerebral blood oxygen saturation without interference from scalp blood flow, using any one of the systems as described above, comprising the steps of:
The sensor 10 is fully attached to the forehead, the light source driving module 604 in the host 60 firstly lights the first light source 102 on the sensor, the first light source 102 sequentially emits near infrared light with the wavelength lambda 1,λ2,……λn, the near infrared light passes through the scalp and brain tissues to form corresponding emergent light, the first detector 103 and the second detector 105 on the sensor respectively receive corresponding emergent light signals, the optical signals are transmitted to the signal amplifying and A/D converting module 605 in the host 60 through the cable 40, and the optical signals are respectively obtained after amplifying and A/D converting AndThe light source driving module 604 in the host then lights the second light source 104 on the sensor, the second light source 104 sequentially emits near infrared light with wavelength lambda 1,λ2,……λn, the near infrared light passes through the scalp and brain tissue to form corresponding emergent light, the second detector 105 on the sensor receives corresponding emergent light signals, the optical signals are transmitted to the signal amplifying and A/D converting module 605 in the host 60 through the cable 40, and the optical signals are obtained after amplification and A/D conversion
The signal amplification and a/D conversion module 605 willAndThe brain blood oxygen saturation is transferred to the central processing and storage module 601, and the method of calculating the brain blood oxygen saturation in the central processing and storage module 601 is as follows.
First, the optical density value is calculated, and the calculation method is as shown in formula (1).
Where I Into (I) is the known incident optical power, I Out of is the outgoing optical power received by the detector after the incident light passes through the scalp and brain tissue, i=1, 2.
Due to optical densityComprises not only the absorption information of chromophore 301 (oxyhemoglobin, reduced hemoglobin and cytochrome oxidase) in brain tissue, but also the absorption information of chromophore substances (oxyhemoglobin, reduced hemoglobin and cytochrome oxidase) in scalp blood stream at the incidence position of light source and the absorption information of chromophore substances (oxyhemoglobin, reduced hemoglobin and cytochrome oxidase) in scalp blood stream at the emergence position of light source, so that the optical density value of brain tissueCalculated with formula (2):
Wherein the method comprises the steps of AndFor correction coefficients, the calculation method is as follows (3):
subsequently, brain tissue optical density values The concentration relationship with chromophore substances (oxyhemoglobin, reduced hemoglobin and cytochrome oxidase) in brain tissue can be explained by modified lambert-beer's law equation (4).
CHb、And C CiOx is obtained by a least square method, as in formula (5):
wherein i=1, 2, the term "n", The molar extinction coefficients of reduced hemoglobin, oxygenated hemoglobin and cytochrome oxidase under different wavelengths can be obtained by table look-up, C Hb,And C CtOx are respectively reduced hemoglobin, oxygenated hemoglobin, and cytochrome oxidase concentrations, DPF is a differential path factor, which can be obtained by table look-up or analog simulation, r 1 is the distance from the first light source to the first detector, r 2 is the distance from the first detector to the second light source, and r 3 is the distance from the second light source to the second detector.
Finally, cerebral blood oxygen saturation is calculated by formula (6):
The technical scheme of the invention has the following advantages:
A. The invention adopts a plurality of multi-wavelength light sources and photoelectric detectors, improves the detection sensitivity and the signal to noise ratio, adopts a light emitting diode or a laser diode as the light source, has stable luminous power and is easy to design.
B. The sensor is provided with a first light source, a first detector, a second light source and a second detector, the light sources and the detectors are sequentially arranged in a straight line along the same direction, the detectors can pick up the absorption information of chromophore substances (reduced hemoglobin, oxygenated hemoglobin and cytochrome oxidase) in scalp blood flow at the incidence position of the light sources, can pick up the absorption information of chromophore substances (reduced hemoglobin, oxygenated hemoglobin and cytochrome oxidase) in scalp blood flow at the emergence position of the light sources, and can effectively eliminate the influence of scalp blood flow interference at the incidence position and the emergence position of the light sources through a central processing and storage module calculation method.
C. When the system provided by the invention is used for detection, not only can the concentration information of oxyhemoglobin and reduced hemoglobin in brain tissues be obtained, but also the concentration information of cytochrome oxidase in brain tissues can be obtained, and the accuracy of calculating the cerebral blood oxygen saturation is further improved.
Drawings
FIG. 1 is a schematic diagram of a brain blood oxygen saturation detection system free from scalp blood flow interference according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of a sensor of a brain blood oxygen saturation detection system without scalp blood flow interference according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of a host structure of a brain blood oxygen saturation detection system without scalp blood flow interference according to an embodiment of the present invention;
Fig. 4 is a schematic diagram of a brain blood oxygen saturation calculation process without scalp blood flow interference according to an embodiment of the present invention.
In the figure, 10 sensors, 101 flexible supporting base materials, 102 first light sources, 104 second light sources, 103 first detectors, 105 second detectors, 201 forehead skin at the head, 202 chromophore substances in scalp blood flow at the first light sources 102, 203 chromophore substances in scalp blood flow near emergent light, 301 chromophore substances in brain tissues, 40 cables, 501 main light paths of the first detectors, 502 main light paths of the second detectors, 503 main light paths of the second detectors, 60 main computers, 601 central processing and storage modules, 602 user information input modules, 603 power supply modules, 604 light source driving modules, 605 signal amplifying and A/D conversion modules and 606 data display modules.
Detailed Description
The following description of the embodiments of the present invention will be made apparent and fully understood from the accompanying drawings, in which some, but not all embodiments of the invention are shown. Based on the embodiments of the present invention, other embodiments that may be obtained by those of ordinary skill in the art without making any inventive effort are within the scope of the present invention.
As shown in fig. 1, the present invention provides a brain blood oxygen saturation detection system that is not disturbed by scalp blood flow, and specifically includes a sensor 10, a host 60, and a cable 40 connecting the sensor and the host.
As shown in fig. 1 and 2, the sensor 10 of the present invention mainly includes three layers of flexible support substrates 101, a first light source 102, a second light source 104, a first detector 103, and a second detector 105.
The first light source 102 and the second light source 104 are light emitting diodes that can emit 3 kinds of near infrared light (λ 1＝735nm,λ2＝805nm,λ3 =850 nm). The first detector 103 and the second detector 105 are photodiodes, and the response peak wavelength of the photodiodes is between 700nm and 800 nm.
The first light source 102, the first detector 103, the second light source 104 and the second detector 105 are sequentially arranged in a straight line in the same direction. The distance r 1 between the first light source 102 and the first detector 103 is 5mm, the distance r 2 between the first detector 103 and the second light source 104 is 20mm, and the distance r 3 between the second light source 104 and the second detector 105 is 5mm.
As shown in fig. 1 and 3, the host 60 of the present invention is composed of a central processing and storage module 601, a user information input module 602, a power supply module 603, a light source driving module 604, a signal amplifying and a/D converting module 605, and a data display module 606. The central processing and storage module 601 is connected with the user information input module 602, the power module 603, the light source driving module 604, the signal amplifying and a/D converting module 605 and the data display module 606. The light source driving module 604 and the signal amplifying and a/D converting module 605 are connected with the sensor 10 through the cable 40, the light source driving module 604 controls the first light source 102 and the second light source 104 to emit light, the first detector 103 and the second detector 105 receive photoelectric signals and transmit the photoelectric signals to the signal amplifying and a/D converting module 605, and the processed signals are transmitted to the central processing and storage module 601 for data analysis processing to obtain brain blood oxygen saturation values and are displayed on the data display module 606.
As shown in fig. 1, the sensor is attached to the forehead skin 201 of the head by double-sided adhesive on the back of the flexible support substrate 101. The primary light path 501 from the first light source 102 to the first detector passes through the chromophore substance 202 in the scalp blood stream at the first light source 102, and the primary light path 503 from the first light source 102 to the second detector passes through the chromophore substance 202 in the scalp blood stream near the incident light, the chromophore substance 301 in the brain tissue, and the chromophore substance 203 in the scalp blood stream near the emergent light in this order. The primary light path 502 from the second light source 104 to the second detector passes through chromophore substances 203 in the scalp blood stream near the outgoing light.
Fig. 4 is a flow chart of calculating cerebral blood oxygen saturation without interference of scalp blood flow.
In the first step, the light source driving module 604 controls the 3 wavelengths of the first light source 102 to emit light alternately, and the light source passes through the scalp and brain tissue to form corresponding emergent light, the first detector 103 and the second detector 105 on the sensor respectively receive corresponding emergent light signals, and amplify the signals transmitted from the optical signals to the host 60 via the cable 40, and the a/D module 605 receives and processes 6 light intensity signalsAndThe light intensity signal is transmitted to the central processing and storage module 601, and the central processing module 601 performs the following formulaSequentially calculateAndAnd stored in the memory module.
In the second step, the light source driving module 604 controls the 3 wavelengths of the second light source 104 to emit light alternately, and the light source passes through the scalp and brain tissue to form corresponding emergent light, the second detector 105 on the sensor receives corresponding emergent light signals, and the signal amplifying and a/D converting module 605 which transmits the light signals to the host via the wires receives and processes the 3 light intensity signalsAndThe light intensity signal is transmitted to the central processing and storage module 601, and the central processing module is used for calculating the formulaSequentially calculate AndAnd stored in the memory module.
Third step, firstly, calling the memory moduleAndThe central processing module is used for processing the data according to the formulaRespectively calculateAndAnd stored in the memory module. Second, call in the memory moduleAndThe central processing module is used for processing the data according to the formulaRespectively calculateAndAnd is stored in the storage module. Finally, call the memory moduleAndThe central processing module is used for processing the data according to the formulaRespectively calculateAndAnd is stored in the storage module.
Fourth, calling the memory module AndThe central processing module is used for processing the data according to the formulaRespectively calculate AndAnd stored in the memory module.
Fifth step, calling the memory moduleAndThe central processing module is used for processing the data according to the formulaCan calculate C Hb,And C CtOx and stored in the storage module. Wherein the method comprises the steps ofAnd the DPF can be determined by looking up a table (whereinAndCan be referred to pages 66-67 in the article Performance Comparison of Several Published Tissue Near-Infrared Spectroscopy Algorithms in ANALYTICAL BIOCHEMISTRY, 1995, macher et al,AndSee, 1962, gelder et al, pages 593 of the article The extinction coefficient of cytochrome c, biochimica et Biophysica Acta, upper paper, and DPF is obtained, r 1＝5mm,r2＝20mm,r3 = 5mm, see, 2013, scholkmann, et al, page 2 of the article Journal of Biomedical Optics, upper paper "General equation for the differential pathlength factor of the frontal human head depending on wavelength and age").
Sixth, C Hb in the storage module is called,And C CtOx, the central processing module according to the formulaAnd calculating the cerebral blood oxygen saturation and storing in the storage module, and simultaneously transmitting to the display module for display.
The above examples are merely illustrative of preferred embodiments of the invention, which are not exhaustive of all details, nor are they intended to limit the invention to the particular embodiments disclosed. Various modifications and improvements of the technical scheme of the present invention will fall within the protection scope of the present invention as defined in the claims without departing from the design spirit of the present invention.
Claims (1)
1. The brain blood oxygen saturation detection method free of scalp blood flow interference is characterized by comprising a brain blood oxygen saturation detection system free of scalp blood flow interference, wherein the system comprises a sensor (10) and a host machine (60), the sensor comprises a light source and a detector, the host machine (60) comprises a power supply module (603), a central processing and storage module (601), a light source driving module (604), a signal amplifying and A/D conversion module (605), a user information input module (602) and a data display module (606), and the sensor (10) is connected with the host machine (60) through a cable (40);
The upper light source of the sensor (10) comprises a first light source (102) and a second light source (104), the two light sources are provided with the same light emitting component, the light emitting component is a light emitting diode or a laser diode capable of emitting a plurality of wavelengths, and 700-900nm near infrared light with the wavelength lambda 1、λ2,……λn is alternately generated;
The detector on the sensor (10) comprises a first detector (103) and a second detector (105), and the two detectors are composed of the same light response sensor, wherein the light response sensor is a photosensitive diode, a silicon photodiode or a charge coupled device, and the response peak wavelength of the photosensitive diode or the silicon photodiode is 700-800 nm;
The first light source (102), the first detector (103), the second light source (104) and the second detector (105) are sequentially arranged in a straight line along the same direction, the distance between the first light source (102) and the first detector (103) is 2-5mm, the distance between the first detector (103) and the second light source (104) is 20-30mm, and the distance between the second light source (104) and the second detector (105) is 2-5mm;
The detection method comprises completely attaching the sensor (10) to forehead, first lighting the first light source (102) on the sensor by the light source driving module (604) in the host (60), sequentially emitting near infrared light with wavelength lambda 1,λ2,……λn by the first light source (102), forming corresponding emergent light by passing through scalp and brain tissue, respectively receiving corresponding emergent light signals by the first detector (103) and the second detector (105) on the sensor, and transmitting the light signals to the signal amplifying and A/D converting module (605) in the host (60) via the cable (40), and respectively obtaining the light signals after amplifying and A/D converting AndThe light source driving module (604) in the host machine then lights the second light source (605) on the sensor, the second light source (104) sequentially emits near infrared light with the wavelength lambda 1,λ2,……λn, the near infrared light passes through the scalp and brain tissues to form corresponding emergent light, the second detector (105) on the sensor receives corresponding emergent light signals, the light signals are transmitted to the signal amplifying and A/D converting module (605) in the host machine (60) through the cable (40), and the light signals are obtained after being amplified and A/D convertedA signal amplifying and A/D converting module (605) to、AndThe brain blood oxygen saturation degree is transmitted to a central processing and storage module (601), and the method for calculating the brain blood oxygen saturation degree in the central processing and storage module (601) is as follows:
firstly, calculating the optical density value by the method shown as the formula (1),
(1)
Wherein, As the incident light power is known to be,Is that after the incident light passes through the scalp and brain tissue, the detector receives the emitted light power i=1, 2, &..n, j=1, 2,3;
Due to optical density Comprises not only the absorption information of chromophore (301) in brain tissue, but also the absorption information of chromophore in scalp blood stream at the incidence position of light source and the absorption information of chromophore in scalp blood stream at the emergent position of light source, so that the optical density value of brain tissueCalculated with formula (2):
(2)
Wherein the method comprises the steps of AndFor correction coefficients, the calculation method is as follows (3):
(3)
subsequently, brain tissue optical density values The concentration relationship with chromophore species in brain tissue is explained by modified lambert-beer law equation (4):
(4)
、 And The method is obtained by a least square method, as shown in formula (5):
(5)
wherein i=1, 2, the term "n", ,,The molar extinction coefficients of reduced hemoglobin, oxygenated hemoglobin and cytochrome oxidase at different wavelengths respectively;、 And Respectively, reduced hemoglobin, oxyhemoglobin and cytochrome oxidase concentration, DPF is differential path factor, r 1 is distance from the first light source (102) to the first detector (103), r 2 is distance from the first detector (103) to the second light source (104), r 3 is distance from the second light source (104) to the second detector (105);
Cerebral blood oxygen saturation is calculated by formula (6):
(6)。
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202110563085.4A CN113100760B (en) | 2021-05-24 | 2021-05-24 | Cerebral blood oxygen saturation detection system and method free from scalp blood flow interference |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202110563085.4A CN113100760B (en) | 2021-05-24 | 2021-05-24 | Cerebral blood oxygen saturation detection system and method free from scalp blood flow interference |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN113100760A CN113100760A (en) | 2021-07-13 |
| CN113100760B true CN113100760B (en) | 2024-11-29 |
Family
ID=76722993
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202110563085.4A Active CN113100760B (en) | 2021-05-24 | 2021-05-24 | Cerebral blood oxygen saturation detection system and method free from scalp blood flow interference |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN113100760B (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN113456070B (en) * | 2021-08-02 | 2024-11-29 | 中国科学院合肥物质科学研究院 | Detection system and method for noninvasively measuring tissue deoxygenation, oxygenation and carboxyhemoglobin |
| CN115956906A (en) * | 2023-01-17 | 2023-04-14 | 中国科学院合肥物质科学研究院 | Multi-light-source local brain tissue blood oxygen saturation detection system and detection method |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112043287A (en) * | 2020-09-30 | 2020-12-08 | 重庆大学 | Cerebral blood oxygen non-invasive monitoring method and monitoring device |
| CN214856724U (en) * | 2021-05-24 | 2021-11-26 | 中国科学院合肥物质科学研究院 | Cerebral blood oxygen saturation detection system free from interference of scalp blood flow |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106923814A (en) * | 2017-04-17 | 2017-07-07 | 吉林大学 | A kind of noninvasive cerebral blood flow (CBF) measuring system and measuring method |
| CN107080543A (en) * | 2017-04-27 | 2017-08-22 | 北京师范大学 | A kind of real-time Cerebral cortex blood oxygen signal harvester of new near-infrared |
| CN112641444A (en) * | 2020-12-10 | 2021-04-13 | 中国科学院深圳先进技术研究院 | Cerebral blood oxygen detection system and method |
-
2021
- 2021-05-24 CN CN202110563085.4A patent/CN113100760B/en active Active
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112043287A (en) * | 2020-09-30 | 2020-12-08 | 重庆大学 | Cerebral blood oxygen non-invasive monitoring method and monitoring device |
| CN214856724U (en) * | 2021-05-24 | 2021-11-26 | 中国科学院合肥物质科学研究院 | Cerebral blood oxygen saturation detection system free from interference of scalp blood flow |
Also Published As
| Publication number | Publication date |
|---|---|
| CN113100760A (en) | 2021-07-13 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US7613487B2 (en) | Instrument for noninvasively measuring blood sugar level | |
| CN110123339B (en) | Noninvasive blood glucose measuring device and method | |
| JP5175179B2 (en) | Improved blood oxygenation monitoring method by spectrophotometry | |
| TWI324686B (en) | Noninvasive measurement of glucose through the optical properties of tissue | |
| US5088493A (en) | Multiple wavelength light photometer for non-invasive monitoring | |
| CA2494030C (en) | Method for spectrophotometric blood oxygenation monitoring | |
| US20150241347A1 (en) | Nondispersive infrared micro-optics sensor for blood alcohol concentration measurements | |
| CN113100760B (en) | Cerebral blood oxygen saturation detection system and method free from scalp blood flow interference | |
| US20080198361A1 (en) | Method and Apparatus for Determining Blood Analytes | |
| EP2909624B1 (en) | Simple sugar concentration sensor and method | |
| JP2003194714A (en) | Measuring apparatus for blood amount in living-body tissue | |
| US9339240B2 (en) | System and method of resolving outliers in NIRS cerebral oximetry | |
| JP6125821B2 (en) | Oxygen saturation measuring apparatus and oxygen saturation calculating method | |
| Yadav et al. | Comparative study of different measurement sites using NIR based non-invasive glucose measurement system | |
| CN214856724U (en) | Cerebral blood oxygen saturation detection system free from interference of scalp blood flow | |
| Vazquez-Jaccaud et al. | Wavelength selection method with standard deviation: application to pulse oximetry | |
| JP4052461B2 (en) | Non-invasive measuring device for blood glucose level | |
| KR100883153B1 (en) | Non-invasive measuring device of blood sugar level | |
| JPH07255709A (en) | Concentration measuring instrument | |
| CN112672680B (en) | High dynamic range detector for gingivitis detection | |
| JP6412956B2 (en) | Biological light measurement device, analysis device, and method | |
| CN105997104B (en) | It is a kind of based on multi fiber beam in body noninvasive physiological parameter acquisition method and device in real time | |
| JP2007111461A (en) | Bio-optical measurement apparatus | |
| KR102335211B1 (en) | Method and apparatus for measuring blood component using self-reference point establishment | |
| JP5070387B2 (en) | Non-destructive measuring device for light scatterers |
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 | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |